CATHETER APPLIANCE

专利摘要:
catheter device. catheter apparatus, systems, and methods for performing renal neuromodulation through intravascular access are disclosed herein. one aspect of the present technology, for example, is directed to a treatment device having a multiple electrode array configured to be delivered to a renal blood vessel. the arrangement is selectively transformable between a dispensing or low profile state (for example, a generally straight shape) and a developed state (for example, a radially expanded shape, usually helical). the arrangement of multiple electrodes is dimensioned and shaped so that the electrodes or energy-dispensing elements contact an internal wall of the renal blood vessel, when the arrangement is in the developed state (for example, helical). electrodes or energy dispensing elements are configured for direct and / or indirect application of thermal and / or electrical energy to heat or otherwise electrically modulate nerve fibers that contribute to kidney function or vascular structures that feed or irrigate the fibers neural.
公开号:BR112013010002A2
申请号:R112013010002-8
申请日:2011-10-25
公开日:2020-03-10
发明作者:Mauch Kevin；Chang William；Goshgarian Justin；Rivera Leonila；Rothman Martin
申请人:Medtronic Ardian Luxembourg S.a.r.l；
IPC主号:

专利说明:

“CATHETER APPLIANCE”
CROSS REFERENCE TO RELATED ORDER (S)
This order claims the benefit of the following pending orders:
(a) US Provisional Order No. 61 / 406,531, filed on October 25, 2010;
(b) US Provisional Order No. 61 / 406,960, filed on October 26, 2010;
(c) US Provisional Order No. 61 / 572,290, filed on January 28, 2011;
(d) US Provisional Order No. 61 / 528,001, filed on August 25, 2011;
(e) US Provisional Order No. 61 / 528,086, filed on August 26, 2011;
(f) US Provisional Order No. 61 / 528,091, filed on August 26, 2011;
(g) US Provisional Order No. 61 / 528,108, filed on August 26, 2011;
(h) US Provisional Order No. 61 / 528,684, filed on August 29, 2011, and (i) US Provisional Order No. 61 / 546,512, filed on October 12, 2011.
All previous orders are hereby incorporated by reference in their entirety. In addition, the components and features of embodiments described in the applications incorporated by reference, can be combined with various components and features described and claimed in the present application.
TECHNICAL FIELD
The present technology refers generally to renal neuromodulation and the associated systems and methods. In particular, several embodiments are directed to multi-electrode radiofrequency (RF) catheter devices for intravascular renal neuromodulation and the associated systems and methods.
The sympathetic nervous system (SNS) is a mainly involuntary body control system typically associated with responses to stress. SNS fibers innervate tissue in almost every organ system in the human body and can affect characteristics such as pupil diameter, bowel motility, and urinary flow. Such regulation may have an adaptable utility in maintaining homeostasis or in preparing the body for a rapid response to environmental factors. Chronic activation of the SNS, however, is a common response to poor adaptation that can lead to the progression of many disease states. Excessive activation of the renal SNS in particular has been identified experimentally and in humans as a likely contributor to the complex pathophysiology of hypertension, volume overload states (eg, heart failure) and progressive kidney disease. For example, dilution of the radiolabel demonstrated increased rates of renal norepinephrine (NE) spread in patients with essential hypertension.
Hyperactivity of the cardiorenal sympathetic nerve can be particularly pronounced in patients with heart failure. For example, an exaggerated leakage of NE from the heart and kidneys to the plasma is often found in these patients. Activation of elevated SNS generally characterizes both end-stage and chronic kidney disease. In patients with end-stage renal disease, above-average plasma NE levels have been shown to be predictive of cardiovascular disease and various causes of death. This is also true for patients suffering from contrast or diabetic nephropathy. Evidence suggests that afferent sensory signals from diseased kidneys are the main contributors to initiating and maintaining high central sympathetic outflow.
The sympathetic nerves that supply the kidneys end in the blood vessels, the justaglomerular apparatus, and the renal tubules. Stimulation of renal sympathetic nerves can cause increased renin release, increased sodium reabsorption (Na +), and a reduction in renal blood flow. These components of neural regulation of renal function are considerably stimulated in disease states characterized by increased sympathetic tone and are likely to contribute to increased blood pressure in hypertensive patients. The reduction in renal blood flow and glomerular filtration rate as a result of efferent renal sympathetic stimulation is likely to be a mainstay of loss of renal function in cardiorenal syndrome (ie, renal dysfunction, as a progressive complication of chronic heart failure). Pharmacological strategies to thwart the consequences of efferent renal sympathetic stimulation include centrally acting sympatholytic drugs, beta-blockers (designed to reduce renin release), angiotensin-converting enzyme inhibitors and receptor blockers (designed to block the action of angiotensin II and activation of aldosterone resulting from the release of renin) and diuretics (designed to combat renal sympathetic mediated water and sodium retention). These pharmacological strategies, however, have significant limitations, including limited efficacy, compliance problems, side effects, and others. Therefore, there is a strong public health need for alternative treatment strategies.
BRIEF DESCRIPTION OF THE DRAWINGS
Various aspects of the present description can be better understood with reference to the following drawings. The components in the drawings are not necessarily to scale. Instead, the emphasis is placed on the clear illustration of the principles of the present description.
Figure 1 illustrates an intravascular renal neuromodulation system configured in accordance with an embodiment of the present technology.
Figure 2 illustrates the modulation of renal nerves with a multi-electrode catheter device, according to an embodiment of the present technology.
Figure 3A is a view of a distal portion of a catheter shaft and an array of multiple electrodes, in a dispensing state (eg, low profile or retracted configuration) within a renal artery used in conjunction with a guide catheter , according to an embodiment of the present technology.
Figure 3B is a view of the distal portion of the catheter shaft and the multiple electrode array of Figure 3A in a developed state (e.g., expanded configuration) within a renal artery according to an embodiment of the technology.
Figure 3C is a partial cross-sectional perspective view of a treatment device in a state developed within a renal artery according to an embodiment of the technology.
Figure 4A is a plan view of a treatment set for use in a treatment device according to an embodiment of the technology.
Figure 4B is an isometric view of the treatment set of Figure 4A.
Figure 4C is an end view of the helical structure of figure 4B showing the angular displacement of energy supply elements in a treatment set according to an embodiment of the technology.
Figure 4D is a side view of a vessel with lesions prophetically formed by a treatment set that overlap circumferentially and longitudinally, but do not overlap along a helical path.
Figure 5A-5D illustrates various embodiments of energy dispensing elements or devices for use with the treatment set of Figures 4A and 4B.
Figure 5E illustrates an embodiment of a treatment set in which the support structure is electrically conductive and serves as the energy dispensing element.
Figure 6A illustrates an embodiment of a treatment device that includes an elongated shaft that has different mechanical and functional regions configured according to an embodiment of the technology.
Figure 6B is a plan view of a groove pattern for use in the treatment device of Figure 6A.
Figure 6C is a perspective view of a distal portion of the treatment device of Figure 6A in a dispensing state (e.g., low profile or retracted configuration) outside a patient, according to one embodiment of technology.
Figure 6D is a perspective view of the treatment device of Figure 6C in a developed state (e.g., expanded configuration) on the outside of a patient.
Figure 6E is a partially schematic plan view of a distal region of the support structure of Figure 6A in a state developed in generally helical form.
Figure 6F is a partially schematic plan view of a distal portion of a state-developed treatment device in the form of a polygon according to another embodiment of the technology.
Figure 6G is a plan view of a groove pattern for use in the treatment device of Figure 6A according to another embodiment of the technology.
Figure 6H is a perspective view of a support structure for use in a treatment device configured in accordance with another embodiment of the technology.
Figure 61 is a plan view of an embodiment of a groove pattern for use in the support structure of Figure 6H.
Figure 6J is a plan view of a groove pattern for use with a treatment device configured in accordance with an embodiment of the technology.
Figures 6K and 6L show deformed grooves in the support structure of Figure 6H in a developed state, according to an embodiment of the technology.
Figure 6M is a plan view of a groove pattern for use with a treatment device configured in accordance with an embodiment of the technology.
Figure 6N is a plan view of a groove pattern for use with a treatment device configured in accordance with an embodiment of the technology.
Figure 60 is a schematic illustration of a portion of a treatment device that has a support structure, including the groove pattern of Figure 6N in a developed state within a patient's renal artery.
Figure 7A is a plan view of an orifice pattern for use with a treatment device configured in accordance with an embodiment of the technology.
Figure 7B is a perspective view of a distal portion of a treatment device, including a flexible region that has the orifice pattern of Figure 7A in a dispensing state on the outside of a patient.
Figure 8A is a broken perspective view in partial section of a treatment device, including the groove pattern of Figure 61 configured according to an embodiment of the technology.
Figures 8B-8D illustrate various configurations of a distal end of a support structure configured in accordance with the embodiments of the present technology.
Figure 9A illustrates a treatment device configured in accordance with an embodiment of the present technology in a developed state (e.g., expanded configuration) on the outside of a patient.
Figure 9B illustrates the treatment device of figure 9A, in a dispensing state (for example, low profile or retracted configuration).
Figure 9C illustrates another embodiment of a treatment device configured in accordance with an embodiment of the present technology in a developed state.
Figure 9D illustrates yet another embodiment of a device for treating a dispensing state.
Figure 9E illustrates the device of figure 9D in a developed state.
Figure 10A is a broken plan view of another device for treating a dispensing state on the outside of a patient, according to an embodiment of the technology.
Figure 10B is a detailed view of a distal portion of the device of Figure 10A in a developed state.
Figure 11A is a broken side view in partial section of a treatment device in a dispensing state according to another embodiment of the technology.
Figure 1 IB is a broken side view in partial section of the treatment device of Figure 11 A, in a developed state.
Figure 11C is a longitudinal cross-sectional view of a handle assembly for use in the device of Figure 11A according to an embodiment of the present technology.
Figure 11D is a longitudinal cross-sectional view of another handle assembly for use in the device of Figure 11A according to an embodiment of the present technology.
Figure 12A is a side view of a distal portion of a device for treating a dispensing state (e.g., low profile or retracted configuration) outside a patient, according to an embodiment of the present technology .
Figure 12B is a side view of the distal portion of the treatment device of Figure 12B in a developed state (e.g., expanded configuration) outside the patient.
Figure 13A is a broken side view in partial section of a treatment device in a dispensing state, according to an embodiment of the present technology.
Figure 13B is a broken side view in the partial section of the embodiment of Figure 13A in a state developed within a renal artery.
Figure 14A is a longitudinal broken cross-sectional view of another embodiment of a treatment device in a dispensing state, according to an embodiment of the present technology.
Figure 14B is a broken side view in partial section of the embodiment of Figure 14A in a state developed within a renal artery.
Figure 14C is a longitudinal cross-sectional view of a distal portion of another embodiment of a treatment device in a dispensing state, according to an embodiment of the present technology.
Figure 14D is a broken longitudinal cross-sectional view of the embodiment of Figure 14C in the state developed within a renal artery.
Figure 15A is a longitudinal cross-sectional view of a distal portion of another embodiment of a treatment device in a dispensing state, according to an embodiment of the present technology.
Figure 15B is a broken side view in partial section of the embodiment of Figure 15A in a state developed within a renal artery.
Figure 16A is a cross-sectional view of an embodiment of a treatment device in a dispensing state within a patient's renal artery, according to an embodiment of the present technology.
Figure 16B is a cross-sectional view of an embodiment of a device for treating a condition developed within a patient's renal artery, according to an embodiment of the present technology.
Figure 17A is a broken side view in partial section of a distal portion of a quick-change type of a treatment device configured in accordance with an embodiment of the present technology.
Figure 17B is a broken side view in partial section of a distal portion of a quick change type of a dispensing state treatment device, according to an embodiment of the present technology.
Figure 17C is a broken side view of a distal portion of the treatment device of Figure 17B in a developed state.
Figure 17C is a broken side view in partial section of a distal portion of another embodiment of a quick-change model of a treatment device, in accordance with an embodiment of the present technology.
Figure 17D is a broken side view in partial section of a distal portion of another type of quick-change treatment device, according to an embodiment of the present technology.
Figure 17E is a broken side view in partial section of a distal portion of yet another embodiment of a quick-change type of treatment device, in accordance with an embodiment of the present technology.
Figure 18 is an illustration of the theoretical blood flow in a renal artery according to an embodiment of the technology.
Figure 19A is a cross-sectional view of a treatment set, including a fluid redirection element within a renal artery according to an embodiment of the present technology.
Figure 19B is a side view of a support structure with a schematic illustration of a fluid redirect element in a dispensing state (eg, low profile or retracted configuration) outside a patient, according to an embodiment of the present technology.
Figure 20 is a graph representing an energy delivery algorithm that can be used in conjunction with the system in Figure 1, according to an embodiment of the technology.
Figures 21 and 22 are block diagrams illustrating the algorithms for evaluating a treatment according to embodiments of the present technology.
Figure 23 is a block diagram illustrating an algorithm for providing a return to the operator during the occurrence of a high temperature condition, according to an embodiment of the present technology.
Fig. 24 is a block diagram illustrating an algorithm for providing feedback to the operator during the occurrence of a condition of high impedance, according to an embodiment of the present technology.
Figure 25 is a block diagram illustrating an algorithm to provide return to the operator when a high degree of vessel constriction occurs according to an embodiment of the present technology.
Figure 26A is a block diagram illustrating an algorithm for providing return to the operator during the occurrence of an abnormal heart rhythm condition, in accordance with an embodiment of the present technology.
Figure 26B is a block diagram illustrating an algorithm for providing feedback to the operator during the occurrence of a low blood flow condition, in accordance with an embodiment of the present technology.
Figures 27A and 27B are screenshots illustrating representative generator display screens configured according to aspects of current technology.
Figure 28 is an illustration of a kit containing the components contained in the system of Figure 1, according to an embodiment of the technology.
Figure 29 is a conceptual illustration of the sympathetic nervous system (SNS) and how the brain communicates with the body, via the SNS.
Figure 30 is an enlarged anatomical view of nerves that innervate the left kidney to form the renal plexus around the left renal artery.
Figures 31A and 31B offer anatomical and conceptual views of a human body, respectively, representing efferent and afferent neural communication between the brain and the kidneys.
Figures 32A and 32B are, respectively, anatomical views of the arterial and venous vascularization of a human being.
DETAILED DESCRIPTION
The present technology is directed to devices, systems and methods to achieve renal neuromodulation electrically and / or thermally induced (that is, taking the nerve fibers that innervate the inert or inactive kidney or otherwise, totally or partially reduced in function) by access percutaneous transluminal intravascular. In particular, embodiments of the present technology refer to devices, systems and methods that incorporate a catheter treatment device that has a mobile multi-electrode arrangement between a dispensing or low profile state (e.g., a generally straight shape ) and a developed state (for example, a radially expanded form, generally helical). The electrodes or energy dispensing elements made by the array are configured to dispense energy (for example, electrical energy, radio frequency electrical energy (RF), pulsed electrical energy, thermal energy) to a renal artery after being advanced through the catheter to the along a percutaneous transluminal path (for example, a puncture of the femoral artery, iliac artery and the aorta, a radial artery, or other suitable intravascular path). The arrangement of multiple electrodes is dimensioned and shaped so that the electrodes or elements of energy supply contact an internal wall of the renal artery, when the arrangement is in the developed state (for example, helical) within the renal artery. In addition, the helical shape of the developed arrangement allows blood to flow through the helix, which is expected to help prevent renal artery occlusion during activation of the energy delivery element. In addition, the flow of blood into and around the array can cool the associated electrodes and / or the surrounding tissue. In some embodiments, the cooling of the energy dispensing elements allows the dispensing of higher energy levels at lower temperatures than can be achieved without cooling. This feature is expected to help create deeper and / or larger lesions during therapy, reduce the temperature of the intimate surface, and / or allow for longer periods of activation with reduced risk of overheating during treatment.
The specific details of various embodiments of the technology are described below with reference to Figures 1-32B. Although many of the embodiments are described below with respect to devices, systems, and methods for intravascular modulation of renal nerves using multiple electrode arrays, other applications and other embodiments, in addition to those described herein are within the scope of the technology . In addition, several other embodiments of the technology may have different configurations, components, or procedures than those described here. A person skilled in the art, in this sense, will understand that the technology may have other embodiments with additional elements, or the technology may have other embodiments without several of the features shown and described below with reference to Figures 1-32B.
As used herein, the terms distal and proximal define a position or direction with respect to the clinician or medical control device (for example, a handle set). Distally or distally they are a position away from or in a direction away from the clinician or medical control device. Proximal and proximally are a position close to or in a direction for the clinician or the medical control device.
I. Renal neuromodulation
Renal neuromodulation is the partial or total disability or effective disruption of the nerves that innervate the kidneys. In particular, renal neuromodulation comprises inhibiting, reducing and / or blocking neural communication along neural fibers (i.e., efferent and / or afferent nerve fibers) that innervate the kidneys. Such disability may be long-term (for example, permanent or for periods of months, years or decades) or short-term (for example, for periods of minutes, hours, days or weeks). Renal neuromodulation is expected to effectively treat a variety of clinical conditions characterized by increased global sympathetic activity, and in particular conditions associated with excess central sympathetic stimulation, such as hypertension, heart failure, acute myocardial infarction, metabolic syndrome, insulin resistance, diabetes , left ventricular hypertrophy, end-stage and chronic kidney disease, inadequate fluid retention in heart failure, cardiorenal syndrome, and sudden death. The reduction of afferent neural signals contributes to the systemic reduction of sympathetic tone / impulse and renal neuromodulation should be useful in the treatment of various conditions associated with systemic sympathetic overactivity or hyperactivity. Renal neuromodulation can potentially benefit a variety of organs and body structures innervated by sympathetic nerves. For example, a reduction in central sympathetic impulse can reduce the insulin resistance that afflicts patients with metabolic syndrome and Type II diabetes. In addition, osteoporosis can be sympathetically activated and can benefit from the lack of regulation of the sympathetic impulse that accompanies renal neuromodulation. A more detailed description of the relevant patient's anatomy and physiology is provided in Section IX below.
Several techniques can be used to neutralize partially or completely disabled neural pathways, such as those that innervate the kidney. The intentional application of energy (eg, electrical energy, thermal energy) to the tissue per energy dispensing element (s) may induce one or more desired effects of thermal heating in localized regions of the renal artery and adjacent regions of the renal plexus RP , which is intimately inside or adjacent to the renal artery adventitia. The intentional application of thermal warming effects can affect neuromodulation throughout all or part of the renal plexus RP.
The effects of thermal heating may include both thermal ablation and non-ablative thermal damage or alteration (for example, by means of continuous heating and / or resistive heating). The desired thermal heating effects may include raising the temperature of target neural fibers above a desired threshold to achieve non-ablative thermal change, or above a higher temperature to achieve ablative thermal change. For example, the target temperature may be higher than the body temperature (for example, approximately 37 ° C), but lower than about 45 ° C for non-ablative thermal change, or the target temperature may be about 45 ° C or higher to achieve ablative thermal change.
More specifically, exposure to thermal energy (heat) in excess of a body temperature of around 37 ° C, but below a temperature of about 45 ° C, can induce thermal change through moderate heating of neural fibers vascular structures that irrigate the target fibers. In cases where vascular structures are affected, the target neural fibers are not perfused resulting in neural tissue necrosis. For example, this can cause non-ablative thermal change in the fibers or structures. Exposure to heat above a temperature of about 45 ° C, or above about 60 ° C, can induce thermal change through substantial heating of the fibers or structures. For example, these higher temperatures can perform thermal ablation of the target neural fibers or vascular structures. In some patients, it may be desirable to reach temperatures that perform thermal ablation of the target neural fibers or vascular structures, but that are less than about 90 ° C, or less than about 85 ° C, or less than about 80 ° C, and / or less than about 75 ° C. Regardless of the type of heat exposure used to induce thermal neuromodulation, a reduction in the activity of the sympathetic renal nerve (RSNA) is expected.
II. Selected Embodiments of Catheter Apparatus having Multiple Electrode Arrays
Figure 1 illustrates a renal neuromodulation system 10 (system 10) configured in accordance with an embodiment of the present technology. System 10 includes an intravascular treatment device 12 operatively connected to a power source or energy generator 26. In the embodiment shown in Figure 1, treatment device 12 (e.g., a catheter) includes an elongated axis 16 that it has a proximal portion 18, a handle 34 in a proximal region of the proximal portion 18, and a distal portion 20 that extends distally from the proximal portion 18. The treatment device 12 further includes a therapeutic set or treatment section 21 in the distal portion 20 of axis 16. As explained in detail below, the therapeutic set 21 may include an arrangement of two or more electrodes or energy dispensing elements 24 configured to be delivered to a renal blood vessel (e.g., a renal artery ), in a low profile configuration. After dispensing at the target treatment site within the renal blood vessel, the therapeutic set 21 is further configured to be developed in an expanded state (for example, a helix or spiral configuration) for dispensing energy at the treatment site and providing thermally and / or electrically therapeutically effective renal neuromodulation. Alternatively, the developed state may be non-helical, provided that the developed state dispenses energy at the treatment site. In some embodiments, the therapeutic set 21 can be placed or transformed into the arrangement or state developed by means of a remote control, for example, via an actuator 36, such as a button, a pin, or a lever made by the handle 34. In other embodiments, however, the therapeutic set 21 can be transformed between the dispensing states and developed using other suitable mechanisms or techniques.
The proximal end of the therapeutic set 21 is carried by or attached to the distal portion 20 of the elongated axis 16. The distal end of the therapeutic set 21 can enclose the treatment device 12 with, for example, a non-traumatic rounded tip or cap. Alternatively, the distal end of the therapeutic set 21 can be configured to engage another element of the system 10 or treatment device 12. For example, the distal end of the therapeutic set 21 can define a passageway for engaging a guide wire (not shown) ) for dispensing the treatment device using excess wire (OTW) or quick change (RX) techniques. Further details on these arrangements are described below with reference to Figures 9A-17E.
The energy source or energy generator 26 (for example, an RF energy generator) is configured to generate a selected shape and magnitude of energy for dispensing to the target treatment site through the energy dispensing elements 24. The energy generator 26 can be electrically coupled to the treatment device 12 via a cable
28. At least one supply wire (not shown) passes along the elongated axis 16 or through a lumen on the elongated axis 16 to the energy supply elements 24 and transmits the treatment energy to the energy supply elements 24. In some embodiments, each energy supply element 24 includes its own power cord. In other embodiments, however, two or more energy supply elements 24 can be electrically coupled to the same power cable. A control mechanism, such as the pedal 32, can be connected (for example, pneumatically connected or electrically connected) to the power generator 26 to allow the operator to start, shut down and optionally adjust the various operational characteristics of the generator, including, but not limited to, energy dispensing. The system 10 may also include a remote control device (not shown) that can be positioned in a sterile field and operably coupled to the energy dispensing elements 24. The remote control device is configured to selectively enable / disable the electrodes. In other embodiments, the remote control device can be incorporated into the handle assembly 34. The energy generator 26 can be configured to dispense the treatment energy by means of an automated control algorithm 30 and / or under the control of the clinical. In addition, energy generator 26 may include one or more evaluation or feedback algorithms 31 to provide feedback to the clinician before, during and / or after therapy. Additional details on the appropriate control algorithms and evaluation / return algorithms are described below with reference to Figures 20-27.
In some embodiments, system 10 can be configured to provide a monopolar electric field dispensing through the energy dispensing elements 24. In such embodiments, a neutral or dispersive electrode 38 can be electrically connected to the energy generator 26 and connected to the patient's exterior (as shown in Figure 2). In addition, one or more sensors (not shown), such as one or more temperature sensors (for example, a thermocouple, thermistor, etc.), impedance, pressure, optical, flow, chemical, or other sensors, may be located in the vicinity of, or within the power supply elements 24 and connected to one or more power wires (not shown). For example, a total of two power wires can be included, where both wires can transmit the signal from the sensor and one wire could serve two purposes and also transmit the energy to the energy dispensing elements 24. Alternatively, one different number of supply wires can be used to transmit the energy to the energy dispensing elements 24.
The power generator 26 may be part of a device or monitor, which may include a processing circuit, such as a microprocessor, and a display. The processing circuit can be configured to execute stored instructions related to control algorithm 30. The monitor can be configured to communicate with the treatment device 12 (for example, via a cable 28) to control the power for the control elements. energy dispensing 24 and / or to obtain signals from energy dispensing elements 24 or any associated sensors. The monitor can be configured to provide indications of power levels or sensor data, such as audio, visual or other indications, or it can be configured to communicate information to another device. For example, energy generator 26 can also be configured to be operationally coupled to a catheter lab screen or system to display treatment information.
Figure 2 (with additional reference to Figure 30) illustrates modulation of renal nerves with an embodiment of system 10. The treatment device 12 allows access to the renal plexus RP through an intravascular pathway P, such as an access site percutaneous in the femoral (illustrated), brachial, radial, or axillary artery to a target treatment site within a respective RA renal artery. As illustrated, a section of the proximal portion 18 of the axis 16 is exposed outside the patient. By manipulating the proximal portion 18 of the 16 axis from the sometimes tortuous P intravascular path, the clinician can advance the 16 axis through the sometimes tortuous P intravascular path, and remotely manipulate the distal 20 portion of the 16 axis. Image orientation , for example, computed tomography (CT), fluoroscopy, intravascular ultrasound (IVUS), optical coherence tomography (OCT), or other appropriate guidance, or combinations thereof, can be used to assist the clinician's manipulation. In addition, in some embodiments, the image orientation components (for example, IVUS, OCT) can be incorporated into the treatment device 12 itself. After the therapeutic set 21 is properly positioned in the RA renal artery, it can be expanded radially or otherwise developed using the handle 34 or other suitable means, until the energy delivery elements 24 are in stable contact with the internal wall of the renal artery FROG. The intentional application of energy from the energy dispensing elements 24 is then performed on the tissue to induce one or more desired neuromodulation effects in localized regions of the renal artery and adjacent regions of the renal RP plexus, which was closely within, adjacent to, or in close proximity to the adventitia of the renal renal artery. The intentional application of energy can reach neuromodulation throughout or at least a portion of the renal plexus RP.
Neuromodulation effects are generally a function of, at least in part, power, time, contact between the energy dispensing elements 24 and the vessel wall, and blood flow through the vessel. Neuromodulation effects can include denervation, thermal ablation, and non-ablative thermal damage or alteration (for example, through continuous heating and / or resistive heating). Desired thermal warming effects may include raising the temperature of target neural fibers above a desired threshold to achieve non-ablative thermal change, or above a higher temperature to achieve ablative thermal change. For example, the target temperature can be higher than the body temperature (for example, approximately 37 ° C), but less than about 45 C for non-ablative thermal change, or the target temperature can be about 45 ° C or higher for ablative thermal change. Desired non-thermal neuromodulation effects may include altering the electrical signals transmitted on a nerve.
In some embodiments, the energy dispensing elements 24 of the therapeutic set 21 may be in the vicinity of, adjacent to, or carried by (e.g., adhered, top spun, rolled, and / or wrinkled) a support structure 22. The proximal end of the support structure 22 is preferably coupled to the distal portion 20 of the elongated axis 16 via a coupling (not shown). The coupling can be an integral component of the elongated shaft 16 (that is, it cannot be a separate part) or the coupling can be a separate part, such as a collar (for example, a radiopaque band) wrapped around an outer surface of the elongated axis 16 to fix the support structure 22 on the elongated axis 16. In other embodiments, however, the support structure 22 can be associated with the elongated axis 16 using a different arrangement and / or different characteristics.
In yet another embodiment, the energy dispensing elements 24 can form or define selected portions of, or the entirety of, support structure 22 itself. That is, as described in more detail below, the support structure 22 may be able to dispense energy. In addition, although in some embodiments, the therapeutic set 21 may operate with a single energy delivery element, it is noted that the therapeutic set 21 preferably includes a plurality of energy delivery elements 24, associated with or defining the support structure 22. When multiple energy dispensing elements 24 are provided, the energy dispensing elements 24 can dispense energy independently (that is, they can be used in a monopolar manner), either simultaneously, selectively, or sequentially, and / or it can dispense power between any desired combination of elements (ie, they can be used in a bipolar way). In addition, the clinician can optionally choose which element (s) of energy delivery 24 are used to deliver power in order to form a highly personalized lesion (s) within the renal artery with a variety of shapes or patterns.
Figure 3A is a cross-sectional view illustrating an embodiment of the distal portion 20 of the axis 16 and the therapeutic set 21 in a dispensing state (e.g., low profile or retracted configuration) within a renal artery RA, and Figures 3B and 3C illustrate the therapeutic set 21 in a developed state (e.g., expanded or helical configuration) within the renal artery. Referring first to Figure 3A, the retracted or dispensing arrangement of the therapeutic set 21 defines a low profile around the longitudinal geometric axis AA of the set such that the transverse dimension of the therapeutic set 21 is small enough to define a clearance distance between an arterial wall 55 and the treatment device 12. The dispensing state facilitates the insertion and / or removal of the treatment device 12 and, if desired, the repositioning of the therapeutic set 21 within the renal artery RA.
In the retracted configuration, for example, the geometry of the support structure 22 facilitates the movement of the therapeutic set 21 by means of a guide catheter 90 to the treatment site in the renal AR artery. In addition, in the retracted configuration, the therapeutic set 21 is sized and configured to fit within the renal artery RA and has a diameter that is less than an internal diameter of the renal artery 52 and a length (from a proximal end) of the therapeutic set 21a a distal end of the therapeutic set 21) which is less than a length of the renal artery 54. In addition, as described in more detail below, the geometry of the support structure 22 is also arranged to define ( in the dispensing state) a minimum transverse dimension around its central geometric axis, which is less than the internal diameter of the renal artery 52 and a maximum length in the direction of the central geometric axis, which is preferably less than the length of the renal artery 54. In one embodiment, for example, the minimum diameter of the therapeutic set 21 is approximately equal to the internal diameter of the ei elongated x 16.
The distal portion 20 of the axis 16 can flex substantially to gain entry into the respective left / right renal artery, following a path defined by a guide catheter, guide wire, or sheath. For example, flexion of the distal portion 20 can be provided by the guide catheter 90, such as a renal guide catheter with a preformed curve near the distal end, which directs the axis 16 along a desired path, from the location percutaneous insertion into the renal RA artery. In another embodiment, the treatment device 12 can be directed to the treatment site within the renal AR artery by coupling and tracking a guide wire (for example, the guide wire 66 in Figure 2), which is inserted into the renal artery RA and extends to the percutaneous access site. In operation, the guidewire is preferably dispensed to the first renal artery RA and the elongated axis 16 which includes a lumen of the guidewire is then passed over the guidewire to the renal artery RA. In some guidewire procedures, a tubular sheath 1291 (described in greater detail below with reference to Figures 16A and 16B), is passed over the guidewire (that is, the lumen defined by the dispensing sheath along the guide wire) in the renal RA artery. Once the 1291 dispensing sheath (Figure
16A) is placed in the RA renal artery, the guidewire can be removed and exchanged for a treatment catheter (for example, the treatment device 12) which can be dispensed through the dispensing sheath 1291 in the RA renal artery. In addition, in some embodiments, the distal portion 20 can be directed or directed in the renal artery RA through the handle assembly 34 (Figures 1 and 2), for example, by an actuating element 36 or by another member of control. In particular, flexing of the elongated axis 16 can be performed, as provided for in US Patent Application No. 12/545. 648, Apparatus, systems and methods for achieving intravascular, thermallyinduced renal neuromodulation by Wu et al., Which is incorporated herein by reference in its entirety. Alternatively, or in addition, the treatment device 12 and its distal portion 20 can be flexed by being inserted through a steerable guide catheter (not shown), which includes a preformed or steerable curve near its distal end, which can be adjusted or reshaped by manipulation from the proximal end of the guide catheter.
The maximum external dimension (for example, diameter) of any part of the treatment device 12, including the elongated axis 16 and the energy dispensing elements 24 of the therapeutic set 21 can be defined by an internal diameter of the guide catheter 90, through that device 12 is passed. In a particular embodiment, for example, an 8 French guide catheter having, for example, an internal diameter of approximately 0.091 inches (2.31 mm) can be used as a guide catheter for access to the renal artery. Allowing for a reasonable clearance tolerance between the energy delivery elements 24 and the guide catheter, the maximum external dimension of the therapeutic set 21 is generally less than or equal to about 0.085 inches (2.16 mm). For a therapeutic set that has a substantially helical support structure for transporting energy dispensing elements 24, the expanded or helical configuration preferably defines a maximum width of less than or equal to about 0.085 inches (2.16 mm) ). However, the use of a smaller French 5 guide catheter may require the use of smaller outside diameters along the treatment device 12. For example, a therapeutic set 21 having a helical support structure 22 that is being routed within a French 5 guide catheter preferably has an external dimension or maximum width of no more than about 0.053 inches (1.35 mm). In still other embodiments, it may be desirable to have a therapeutic set 21 with a maximum width substantially below 0.053 inches (1.35 mm), as long as there is sufficient clearance between the energy delivery elements and the guide catheter. In addition, in some embodiments, it may be desirable to have an arrangement in which the guide catheter and therapeutic set 21 define a diameter ratio of about 1.5: 1. In another example, the helical structure and the energy dispensing element 24, which are to be dispensed within a 6 French guide catheter, would have an external dimension of no more than 0.070 inches (1.78 mm). In still more examples, other suitable guide catheters can be used, and the external dimensions and / or arrangements of the treatment device 12 can vary accordingly.
After locating the therapeutic set 21 on the distal portion 20 of the axis 16 in the renal artery RA, the therapeutic set 21 is transformed from its dispensing state into its developed state or developed disposition. The transformation can be initiated using an arrangement of components of the device, as described here with respect to the particular embodiments and their different modes of development. As described in more detail below and according to one or more embodiments of the present technology, the therapeutic set can be developed by a control member, such as a tension or tension wire, guide wire, shaft, or stylus fitted internally or externally with the support structure of the therapeutic set to apply a deformation or molding force to the set to transform it into its developed state. As an alternative, the therapeutic set 21 can be self-expanding or developing in such a way that the removal that of a radial retention results in the development of the set. In addition, the modality used to transform the therapeutic set 21 from the dispensed state into the developed state can, in most embodiments, be reversed to transform the therapeutic set 21 back to the dispensed state from the developed state .
The further manipulation of the support structure 22 and the energy delivery elements 24 within the respective renal artery RA establishes the affixing of the energy delivery elements 24 against the tissue along an internal wall of the respective renal artery RA. For example, as shown in figures 3B and 3C, the therapeutic set 21 is expanded inside the renal artery RA in such a way that the energy delivery elements 24 are in contact with the wall of the renal artery 55. In some embodiments , manipulation of the distal portion 20 will also facilitate contact between the energy dispensing elements 24 and the renal artery wall. The embodiments of the support structures described herein (for example, the support structure 22) are expected to ensure that the contact force between the wall of the inner renal artery 55 and the energy dispensing elements 24 does not exceed one maximum value. In addition, support structures 22 or other suitable support structures described herein are preferably provided to provide consistent contact force against arterial wall 55, which can allow the formation of consistent lesions.
The alignment may also include the alignment of the geometric aspects of the energy delivery elements 24 with the renal artery wall 55. For example, in embodiments where the energy delivery elements 24 have a cylindrical shape with rounded ends, the alignment may include alignment of the longitudinal surface of the individual energy delivery elements 24 with the artery wall 55. In another example, an embodiment may include energy delivery elements 24 that have a structured shape or inactive surface, and the Alignment may include the alignment of the energy dispensing elements 24 so that the structured shape or inactive surface is not in contact with the artery wall 55.
As best seen in Figures 3B and 3C, in the developed state, the therapeutic set 21 defines a substantially helical support structure 22 in contact with the renal artery wall 55 along a helical path. An advantage of this arrangement is that pressure from the helical structure can be applied in a wide variety of radial directions, without applying pressure to a circumference of the vessel. Thus, the helical-shaped therapeutic set 21 is expected to provide stable contact between the energy dispensing elements 24 and the artery wall 55, when the wall moves in any direction. In addition, the pressure applied to the vessel wall 55 along a helical path is less likely to stretch or stretch the circumference of a vessel which can thus cause damage to the vessel tissue. Yet another feature of the expanded helical structure is that it can come into contact with the vessel wall in a wide variety of radial directions and maintain a sufficiently open lumen in the vessel allowing blood to flow through the helix during therapy.
As best seen in Figure 3B, in the developed state, the support structure 22 defines the maximum axial length of the therapeutic set 21, which is approximately equal to or less than a length of the renal artery 54 of a main renal artery (i.e., a section of a renal artery proximal to a bifurcation). Because this length may vary from patient to patient, it is anticipated that the support structure developed in helical form 22 can be manufactured in different sizes (for example, with different lengths L and / or diameters D, as shown in Figure 4A ) that may be appropriate for different patients. With reference to Figures 3B and 3C, in the developed state, the helical-shaped therapeutic set 21 provides circumferentially discontinuous contact between the energy dispensing elements 24 and the inner wall 55 of the renal artery RA. That is, the helical path can comprise a partial arc (ie, <360 °), a complete arc (ie, 360 °) or a more than complete arc (ie> 360 °) along the inner wall of a vessel on the longitudinal geometric axis of the vessel. In some embodiments, however, the arc is not substantially in the same plane perpendicular to the central geometric axis of the artery, but instead, preferably sets an obtuse angle with the central geometric axis of the artery.
A. Helical structure
Figure 4A is a plan view of an embodiment of a therapeutic or treatment set 21 for use with a treatment device (for example, treatment device 12) according to an embodiment of the technology, and Figure 4B is an isometric view of the therapeutic set 21 of Figure 4A. The energy dispensing elements 24 shown in Figures 4A and 4B are for illustrative purposes only, and it will be appreciated that the treatment set 21 may include a different number and / or arrangement of energy dispensing elements 24.
As shown in Figures 4A and 4B, a propeller can be characterized, at least in part, by its overall diameter D, the length L, a propeller angle α (an angle between a line tangent to the propeller and its geometric axis), pitch HP (longitudinal distance of a complete helical turn, measured parallel to its geometry axis), and the number of revolutions (number of times the propeller completes a 360 ° rotation around its geometry axis).
In particular, the developed or expanded configuration of the propeller can be characterized by its axial length L along the geometric axis of elongation, in the free space, for example, not limited by a vessel wall or other structure. As the helical support structure 22 expands radially from its dispensing state, its diameter D increases and its length L decreases. That is, when the helical structure develops, a distal end 22a moves axially towards the proximal end 22b (or vice versa). Thus, the length L developed is less than the unexpanded or dispensing length. In certain embodiments, only one of the distal end portion 22a or the proximal end portion 22b of the support structure 22 is fixedly connected to the elongated axis 16 or an extension thereof. In other embodiments, the support structure 22 can be transformed into its expanded configuration or developed by twisting the distal and proximal end portions 22a and 22b together.
With reference to Figure 4B, the developed helix-shaped support structure 22 optionally comprises a distal extension 26a distal to the helical portion which is relatively linear and can end with a non-traumatic (for example, rounded) tip 50. The extensions distal 26a including tip 50 can reduce the risk of blood vessel damage as the helical structure is expanded and / or as a dispensing sheath is retracted, and can facilitate alignment of the helical structure in a vessel as it expands. In some embodiments, the distal extension 26a is generally linear (but flexible) and has a length of less than about 40 mm (for example, between 2 mm and 10 mm). Tip 50 can be made from a polymer or metal, which is attached to the end of the structural element by means of adhesive, solder, pressing, overmolding, and / or white solder. In other embodiments, the tip 50 can be made from the same material as the structural element and manufactured into the tip 50 by machining or melting. In other embodiments, the distal extension 26a may have a different configuration and / or characteristics. For example, in some embodiments, tip 50 may comprise an energy delivery element or a radiopaque marker. In addition, distal extension 26a is an optional feature that cannot be included in all embodiments.
The helical structure can also optionally have a proximal extension 26b that is relatively linear compared to the helical region of the support structure 22. The proximal extension 26b, for example, can be an extension of the support structure 22 and it can be between 0 mm and 40 mm in length (for example, between 2 and 10 mm). Alternatively, the proximal extension 26b can be made up of a separate material (for example, a polymer fiber), with greater flexibility than the rest of the support structure 22. The proximal extension 26b is configured to provide a flexible connection between the region helical structure of the support structure 22 and the distal end of the elongated axis 16 (Figure 1). This characteristic is expected to facilitate the alignment of the developed helical support structure 22 with the vessel wall, reducing the force transferred from the elongated axis 16 to the helical region of the helical structure 22. This can be useful, for example, when the elongated axis it is tilted to one side of the vessel wall, or if the elongated axis moves in relation to the vessel wall, allowing the helical structure to remain positioned.
Referring again to Figures 4A and 4B together (and with reference to Figures 3A and 3B), the dimensions of the developed helical shape 22 are influenced by its physical characteristics and its configuration (for example, expanded versus not expanded), which in turn can be selected with the renal artery geometry in mind. For example, the axial length L of the developed helical structure can be selected to be no longer than a patient's renal artery (for example, length 54 of the renal renal artery RA of Figures 3A and 3B). For example, the distance between the access site and the renal artery ostium (for example, the distance from a femoral access site to the renal artery is typically about 40 cm to about 55 cm) is generally greater than that the length of a renal artery from the aorta and the most distal treatment site along the length of the renal artery, which is typically less than about 7 cm. Therefore, the elongated axis 16 (Figure 1) is predicted to be at least 40 cm and the helical structure is less than about 7 cm in its unexpanded length L. A length in an unexpanded configuration of no more than that about 4 cm can be suitable for use in a large patient population and provides a large contact area when in an expanded configuration and, in some embodiments, provides a large region for placing multiple energy delivery elements, however, a shorter length (for example, less than about 2 cm), in an unexpanded configuration, can be used in patients with shorter renal arteries. The helical structure 22 can also be designed to work with typical renal artery diameters. For example, the diameter 52 (Figure 3A) of the renal renal artery can vary between about 2 mm and about 10 mm. In a particular embodiment, the placement of the energy delivery elements 24 on the helical structure 22 can be selected according to an estimated location of the renal plexus RP in relation to the renal artery RA.
In another specific embodiment, a section structure or support of the therapeutic set 21, when allowed to develop completely into an unretracted configuration (that is, outside the body, as shown in Figures 4A and 4B), comprises a helical shape with a diameter D less than about 15 mm (for example, about 12 mm, 10 mm, 8 mm, or 6 mm), a length L less than or equal to about 40 mm (for example, less than about 25 mm, less than about 20 mm, less than about 15 mm), an α helix angle of one of between about 20 ° and 75 ° (for example, between about 35 ° and 55 °), a speed range between 0.25 and 6 (for example, between 0.75 and 2, between 0.75 and 1.25), and an HP pitch between about 5 mm and 20 mm (for example, between about 7 mm and 13 mm). In another example, the therapeutic set 21 can be configured to expand radially from its dispensing state with a diameter of about its central geometric axis, being about 10 mm for a dispensing state in which the energy dispensing elements 24 are in contact with the artery wall. The previous dimensions / angles are associated with specific embodiments of the technology, and it is noted that the therapeutic sets configured according to other embodiments of the technology may have different arrangements and / or configurations.
In some embodiments, the propeller-shaped support structure 22 may be generally cylindrical (i.e., a helical diameter may be generally consistent over a greater part of its length). It is also contemplated, however, that the structure 22 may have variations, such as a conical helical shape, a tapered structural element, the path clockwise or counterclockwise, consistent or varied pitch.
In one embodiment, the support structure 22 can include a solid structural element, for example, a wire, tube, coiled or twisted cable. The support structure 22 can be formed from biocompatible metals and / or polymers, including polyethylene terephthalate (PET), polyamide, polyimide, polyethylene amide block copolymer, polypropylene or polyether ether ketone (PEEK) polymers. In some embodiments, the support structure 22 may be electrically non-conductive, electrically conductive (for example, stainless steel, nitinol, silver, platinum, nickel-cobalt-chromium-molybdenum alloy), or a combination of electrically conductive materials and not conductive. In a particular embodiment, for example, the support structure 22 can be formed from a precast material, such as elastic tempered stainless steel or nitinol. In addition, in particular embodiments, structure 22 may be formed, at least in part, from radiopaque materials that are capable of being converted into an image by fluoroscopy to allow a clinician to determine whether the treatment set 21 is adequately placed and / or developed in the renal artery. Radiopaque materials can include, for example, barium sulfate, bismuth trioxide, bismuth subcarbonate, powdered tungsten, powdered tantalum, or various formulations of certain metals, including gold and platinum, and these materials can be incorporated directly into elements structural elements 22 or can form a total or partial coating of the helical structure 22.
In general, helical structure 22 can be designed to apply a desired external radial force to the renal artery wall 55 (Figures 3A and 3B), when inserted and expanded to contact the internal surface of the renal artery wall 55 (Figures 3A and 3B). The radial force can be selected to avoid damage caused by stretching or distending the renal renal artery when the helical structure 22 is expanded against the artery wall 55 within the patient. Radial forces that can avoid injuring the renal renal artery still provide an adequate stabilizing force, which can be determined by calculating the radial force exerted on an artery wall by normal blood pressure. For example, a suitable radial force can be less than or equal to about 300 mN / mm (for example, less than 200 mN / mm). Factors that can influence the applied radial force include the geometry and stiffness of the support structure
22. In a particular embodiment, the support structure 22 is about 0.003-0.009 inches (0.08-0.23 mm) in diameter. Depending on the composition of the support structure 22, the diameter of the structural element can be selected to facilitate the desired conformation and / or the radial force against the renal artery when expanded. For example, a support structure 22 formed from a harder material (for example, metal) can be more accurate compared to a support structure 22 formed from a highly flexible polymer to obtain flexibility and radial force profiles. similar. The pressure to the outside of the helical support structure 22 can be assessed in vivo, by an associated pressure transducer.
In addition, certain secondary processes, including heat treatment and annealing, can harden or soften the fiber material to affect strength and stiffness. In particular, for shape memory alloys, such as nitinol, these secondary processes can be varied in order to obtain different final properties for the same starting materials. For example, the elastic or softness zone can be increased to provide improved flexibility. Secondary processing of shape memory alloys influences the transition temperature, that is, the temperature at which the structure exhibits a desired stiffness and radial strength. In embodiments that use shape memory properties, such as shape memory nitinol, this transition temperature can be adjusted to normal body temperature (for example, about 37 ° C), or in a range between about 37 ° C and 45 ° C. In other embodiments that comprise superelastic nitinol, a transition temperature may be well below body temperature, for example, below 0 ° C. Alternatively, the helical structure can be formed at from an elastic or superelastic material, such as nitinol, which is thermally engineered into a desired helical shape. Alternatively, the helical structure 22 can be formed from various materials, such as one or more polymers and metals.
With reference again to figures 3B and 3C together, it should be understood that the support structure 22 of the treatment set 21, when it is not inserted in a patient, is capable of developing to a maximum diameter that is greater than the diameter in your dispensation state. In addition, the helix-shaped structure 22 can be dimensioned so that the maximum diameter is greater than the diameter of the lumen 52 of the renal artery RA. When inserted into the patient and transformed into the developed state, however, the helix-shaped structure 22 expands radially to encompass the lumen of the renal artery and, in its largest circumferential section, is approximately or slightly inferior (for example, in embodiments in which the energy delivery elements 24 fill a part of the space) than the diameter 52 of the renal artery RA. A small amount of distention of the vessel can be caused without undue damage and the structure 22 can expand in such a way that its largest circumferential section is slightly larger than the diameter 52 of the renal artery RA, or in such a way that one or more energy-dispensing elements 24 are lightly pressed to the wall 55 of the renal artery RA. A helical assembly or arrangement that causes a light and non-detrimental distension of an artery wall 55 can advantageously provide stable contact force between the energy delivery elements 24 and the artery wall 55 and / or maintain the energy delivery elements energy 24 in place, even with the artery moving with the respiratory movement and the pulsating blood flow. Since this diameter 52 of the renal renal artery varies from patient to patient, the treatment set 21 may be able to assume a range of diameters between the dispensing diameter and the maximum diameter.
As stated above, a characteristic of the therapeutic set developed 21 in the helical configuration is that the energy dispensing elements 24 associated with the helical structure can be placed in stable contact with the vessel wall reliably to create consistent lesions. In addition, several energy-dispensing elements 24 can be placed along the helical structure with the appropriate spacing to obtain a desired lesion configuration within the target vessel. Another feature of various embodiments of the therapeutic set 21 with the helical configuration described above is that the set can be expanded to fit within a relatively wide range of different vessel diameters and / or with various sinuosities.
B. Size and configuration of the energy supply elements
It should be understood that the embodiments provided herein can be used in conjunction with one or more energy dispensing elements 24. As described in greater detail below, the helical structure developed bearing the energy dispensing elements 24 is configured to provide a dispensation of therapeutic energy to the renal artery, without any repositioning. Illustrative embodiments of the energy supply elements 24 are shown in Figures 5A-5D. The energy dispensing elements 24 associated with the helical structure 22 may be separate elements, or may be an integral part of the helical structure 22. In some patients, it may be desirable to use the energy dispensing element (s) 24 to create a single lesion, or multiple focal lesions that are spaced around the circumference of the renal artery. A single focal lesion with desired longitudinal and / or circumferential dimensions, one or more full circle lesions, multiple focal lesions circumferentially spaced in a common longitudinal position, spiral shaped lesions, interrupted spiral lesions, generally linear lesions, and / or multiple discrete focal lesions longitudinally spaced in a common circumferential position, alternatively or additionally, can be created. In still other embodiments, the energy dispensing elements 24 can be used to create the lesions with a variety of other geometric shapes or patterns.
According to the size, shape and number of the energy dispensing elements 24, the formed lesions can be spaced around the circumference of the renal artery and the same formed lesions can also be spaced apart along the longitudinal geometric axis of the renal artery . In particular embodiments, it is desirable, for each lesion formed, to cover at least 10% of the circumference of the vessel to increase the likelihood of affecting the renal plexus. In addition, to achieve denervation of the kidney, it is considered desirable for the pattern of the lesion formed, as seen from a proximal or distal end of the vessel, to extend at least approximately all the way around the circumference of the renal artery. In other words, each of the lesions formed covers an arc of circumference, and each of the lesions, as seen from one end of the vessel, slopes or overlaps adjacent or other lesions in the pattern to create both an actual circumferential lesion or a virtually circumferential lesion. The lesions formed defining a real circumferential lesion are located in a single plane perpendicular to a longitudinal geometric axis of the renal artery. A virtually circumferential lesion is defined by multiple lesions that may not be located on a single perpendicular plane, although more than one lesion in the pattern may be formed. At least one of the lesions formed comprising the virtually circumferential lesion is axially spaced from other lesions. In a non-limiting example, a virtually circumferential lesion may comprise six lesions created in a single helical pattern along the renal artery such that each of the lesions spans an arch that extends over at least one-sixth of the vessel's circumference such that the pattern resulting from lesions completely covers the circumference of the vessel when viewed from one end of the vessel. In other examples, however, a virtually circumferential lesion may comprise a different number of lesions. It is also desirable that each of the lesions is deep enough to penetrate into and beyond the adventitia to thereby affect the renal plexus. However, lesions that are too deep (for example,> 5 mm) are at risk of interfering with tissue and tissue structures (for example, a renal vein) not targeted so that a controlled depth of energy treatment is also desirable.
As shown in Figures 4A and 4B, the energy dispensing elements 24 can be distributed over the helical structure 22 in a desired arrangement. For example, the axial distances between the energy delivery elements 24 can be selected so that the edges of the lesions formed by individual energy delivery elements 24 on the renal artery wall 55 are overlapped or not overlapped. One or both of the axial distances xx or yy can be from about 2 mm to about 1 cm. In a particular embodiment, axial distances xx or yy can range from about 2 mm to about 5 mm. In another embodiment, the energy supply elements 24 can be spaced about 30 mm apart. In yet another embodiment, the energy supply elements 24 are spaced about 11 mm apart. In yet another embodiment, the energy dispensing elements 24 are spaced about 17.5 mm apart. In addition, the axial distance xx can be less, almost equal to, or greater than the axial distance yy.
The spacing of the energy supply elements 24 can be characterized by a distance of helical length zz, that is, the distance between energy supply elements along the path of the helical structure 22. The distance of the helical length zz can be chosen with based on the size of the lesions created by the energy dispensing elements 24 so that the lesions either overlap or do not overlap. In some embodiments, the energy dispensing elements 24 are both longitudinally and circumferentially displaced from each other. Figure 4C, for example, is an end view of the helical structure 22 showing the displacement or angular separation of the energy delivery elements 24 from each other around the circumference of the developed helical structure 22. In particular, the energy delivery element 24c is displaced from the energy dispensing element 24a by angle 150 and displaced from the energy dispensing element 24b by angle 152. The angles of displacement can be selected so that when energy is applied to the renal artery via dispensing elements of energy 24a, 24b, and 24c, the lesions may or may not overlap circumferentially.
Figure 4D is a side view of a vessel with lesions formed 340 that circumferentially and / or longitudinally overlap, but do not overlap along a helical path. More specifically, lesions 340 can be formed by energy dispensing elements 24 to have a circumferential overlap 341, as seen from one end of the vessel (for example, Figure 4C) and / or a longitudinal overlap 342, but may not produce a helical length overlap, instead forming a helical length slit 343. For example, the energy dispensing elements 24 can take the form of electrodes for applying an electric RF energy field to a vessel wall and be configured to produce lesions that are about 5 mm in diameter, with the electrodes spaced by a helical length of about 6 to 7 mm. Depending on the number and placement of the energy dispensing elements 24, a helical lesion pattern with any appropriate number of turns can be formed. As such, the treatment device 12 can employ a single application of energy to form a complex lesion pattern. It should be noted that the embodiments illustrated in Figures 4A-4C are exemplary, may be schematic in nature, may not correlate exactly with one another, and are presented only for the purpose of clarifying certain aspects of the technology. As such, the number and spacing of the energy delivery elements 24 are different in each of Figures 4A-4C, and the lesions formed by the illustrated embodiments cannot create a sufficient overlap pattern to achieve a virtually circumferential lesion such as described above, in particular when energy is applied to only one development of the treatment set 21 without repositioning.
With reference again to Figure 3B, the individual energy dispensing elements 24 are connected to the energy generator 26 (Figure 1), and are sized and configured to contact an internal wall of the renal artery. In the illustrated embodiment, the energy supply element 24 can be operated in a monopolar or unipolar manner. In this arrangement, a return path for the applied RF electric field is established, for example, by an external dispersive electrode (shown as element 38 in Figures 1 and 2), also called an indifferent electrode or neutral electrode. The monopolar application of RF electric field energy serves to heat ohmically or resistively the tissue in the vicinity of the electrode. The application of the RF electric field thermally damages the tissue. The aim of treatment is to thermally induce neuromodulation (for example, necrosis, thermal change or ablation) in the targeted neural fibers. Thermal damage forms an injury to the vessel wall. Alternatively, an RF electric field can be dispensed with a pulsed or oscillating intensity that does not thermally damage the tissue so that neuromodulation in the target nerves is achieved by the electrical modification of the nerve signals.
The active surface area of the energy dispensing element 24 is defined as the energy transmission area of the element 24, which can be placed in close contact against the fabric. Too much contact area between the energy dispensing element and the vessel wall can create excessively high temperatures or around the interface between the fabric and the energy dispensing element, in order to create excess heat production at this interface. This excess heat can create an injury that is too large circumferentially. This can also lead to unwanted thermal application on the vessel wall. In some cases, too much contact can also lead to small, shallow lesions. Too little contact between the energy supply element and the vessel wall can result in superficial heating of the vessel wall, thereby creating a lesion that is very small (for example, <10% of the vessel's circumference) and / or very little shallow.
The active contact surface area (ASA) between the energy dispensing element 24 and the inner wall of the vessel (eg, renal artery wall 55) has a major influence on the efficiency and control of the generation of an energy field thermally through the vessel wall to thermally affect target neural fibers in the renal plexus. While the ASA of the energy dispensing element is important for creating lesions of desired size and depth, the relationship between the ASA and the total surface area (TSA), the energy dispensing element 24 and the electrode 46 is also important. The relationship between ASA and TSA influences the formation of the lesion in two ways: (1) the degree of resistive heating through the electric field, and (2) the effects of blood flow or other convective cooling elements, such as saline. injected or infused. For example, an RF electric field causes the formation of the lesion, through resistive heating of the tissue exposed to the electric field. The greater the ratio of ASA to TSA (that is, the greater the contact between the electrode and the tissue), the greater the resistive heating, for example, the greater the lesion that is formed. As discussed in more detail below, the blood flow along the non-contact portion of the electrode (TSA minus ASA) provides conductive and convective cooling of the electrode, thereby losing excess thermal energy and the interface between the vessel wall and the electrode. If the ASA to TSA ratio is too high (for example, more than 50%), resistive heating of the tissue can be too aggressive and not enough thermal energy is lost, resulting in the generation of excessive heat and increased potential for damage stenotic, thrombus formation and undesirable lesion size. If the ratio of ASA to TSA is very low (for example, 10%), then there is very little resistive heating of the tissue, resulting in superficial heating and smaller, shallower lesions. In a representative embodiment, the ASA of the energy dispensing elements 24 of the contact tissue can be expressed as
0.25 TSA <ASA <0.50 TSA
An ASA to TSA ratio greater than 50% can still be effective without generating excessive heat, compensating with a reduced power dispensing algorithm and / or using electrode convective cooling by exposure to blood flow. As discussed further below, electrode cooling can be achieved by injecting or infusing cooling fluids, such as saline (eg, room temperature, saline or cooled saline) over the electrode and into the bloodstream.
Various size restrictions for an energy delivery element 24 can be imposed for clinical reasons by the desired maximum dimensions of the guide catheter, as well as by the size and anatomy of the lumen of the renal artery itself. In some embodiments, such as those shown in Figures 13 and 25, the maximum outer diameter (or cross-sectional dimension for non-circular cross-section) of the energy dispensing element 24 may be the largest diameter found along the length of the elongated axis 16 distal to the handle assembly 34. As previously discussed, for clinical reasons, the maximum external diameter (or cross-sectional dimension) of the energy dispensing element 24 is limited by the maximum internal diameter of the guide catheter through the which the elongated axis 16 is to be passed through the intravascular path 14. Assuming that an 8 French guide catheter (which has an internal diameter of approximately 0.091 inches (2.31 mm)) is, from a clinical point of view, the largest desired catheter to be used to access the renal artery, and which allows reasonable clearance tolerance between the 24 eoc energy dispensing element Before guiding, the maximum diameter of electrode 46 is restricted to about 0.085 inches (2.16 mm). If a 6 French guide catheter is used instead of an 8 French guide catheter, then the maximum diameter of the energy dispensing element 24 is restricted to about 0.070 inches (1.78 mm), for example, about 0.050 inches (1.27 mm). In case a 5 French guide catheter is used, then the maximum diameter of the energy delivery element 24 is restricted to about 0.053 inches (1.35 mm).
Based on these restrictions and the energy dispensing considerations mentioned above, the energy dispensing element 24 can have an outside diameter of about 0.049 to about 0.051 inches (1.24 mm 1.30 millimeters). The energy delivery elements 24 can also have a minimum outside diameter of about 0.020 inches (0.51 mm) to provide sufficient cooling and lesion size. In some embodiments, the energy dispensing element 24 can be from about 1 mm to about 3 mm in length. In some embodiments where the energy dispensing element 24 is a resistive heating element, the energy dispensing element 24 has a maximum outside diameter of about 0.049-, 051 inches (1.24 mm-1.30 mm) and a length of about 10 mm to 30 mm. An embodiment of energy supply elements 24, for example, provides a multiple arrangement of 4-6 electrodes arranged on a support structure (for example, a tubular structure). The energy dispensing elements 24, for example, can be gold electrodes or, alternatively, platinum, platinum-iridium, or other suitable material. In a particular embodiment, the electrodes can measure about 0.030 inches ID x 0.0325 inches OD x 0.060 inches in length (0.76 mm x 0.83 mm x 1.52 mm). In yet another particular embodiment, the electrodes can measure 0.029 inches ID x 0.033 inches OD x 0.060 inches in length (0.72 mm x 0.83 mm x 1.52 mm). In yet another particular embodiment, the electrodes can measure 0.038 inches ID x 0.042 inches OD x 0.060 inches in length (0.97 mm x 1.07 mm x 1.52 mm). In addition, the electrodes can be suitably electrically isolated from the support structure with the power cable arrangement of each of the electrodes wrapped in a polymer, in order to provide a compact packed electrode arrangement set on the support structure 22.
In other embodiments, the outer diameter of the treatment device 12 can be defined by one or more energy supply elements 24 and can be further defined by elements, such as, for example, control wire 168, as shown in Figure 8A. For example, particular embodiments can be used with an 8 French guide catheter, and can comprise energy dispensing element (s) 24, with a diameter between about 0.049-0.053 inches (1.24 mm to 1.35 mm ) and a control wire, with a diameter between about 0.005 to 0.015 inches (0.13 mm to 0.38 mm) in diameter. In other embodiments, however, the arrangement and / or dimensions of the energy supply elements 24 and / or control wires may vary.
In certain embodiments, the helical structure 22 can be formed of an electrically conductive material. For example, helical structure 22 can be made from cable wire or nitinol tube. As shown in Figure 5E, wire conductors 19 can connect the helical structure 22 to the energy generator 26. The helical structure 22 forms a contact region with the renal artery wall and acts as the energy dispensing element 24. In this configuration , the helical structure 22 is capable of producing a continuous helical lesion. The helical structure 22 which is configured to be an energy supply element 24 can optionally comprise sensors 33 positioned over, at, and / or in the vicinity of the helical structure 22 and can be electrically connected to the supply wires 35.
In other embodiments, the electrically conductive helical structure 22 is insulated, at least in part. That is, the helical conductive structure is partially covered with an electrically insulating material and the uncovered portions of the helical structure 22 serve as one or more conductive energy dispensing elements 24. The energy dispensing elements 24 can be of any size, shape or number, and can be positioned relative to each other, as provided herein.
The energy dispensing element 24 can be configured to dispense thermal energy, that is, to heat and conduct thermal energy to the fabric. For example, the energy supply elements can be an electrically resistive element, such as a thermistor or a coil made of electrically resistive wire, so that when electrical current passes through the energy supply element, heat is produced. An electrically resistive wire can be, for example, an alloy such as nickel-chromium, with a diameter of, for example, between 48 and 30 AWG. The resistive wire can be electrically insulated, for example, with polyimide enamel.
In certain embodiments, the energy dispensing elements 24 can be repositioned angularly with respect to the renal artery during treatment. Returning to Figures 1 and 2, for example, this angular repositioning can be achieved by compressing the therapeutic set 21 and rotating the elongated axis 16 of the treatment device 12 via the handle set 34. In addition to the angular or circumferential repositioning of the elements energy dispensing 24, the energy dispensing elements 24 can optionally also be repositioned along the length or longitudinal dimension of the renal artery. This longitudinal repositioning can be achieved, for example, by translating the elongated axis 16 of the treatment device 12 through the handle assembly 34, and can occur before, after or simultaneously with the angular repositioning of the energy supply elements 24 Referring to Figure 3B, the repositioning of the energy delivery elements 24 in both longitudinal and angular dimensions puts the energy delivery elements 24 in contact with the inner wall 55 of the renal artery RA in a second treatment site for the treatment of renal plexus RP. In operation, energy can then be dispensed through the energy dispensing elements 24 to form a second focal lesion at this second treatment site. For embodiments in which the multiple energy delivery elements 24 are associated with the helical structure, the initial treatment may result in two or more injuries, and repositioning may allow additional injuries to be created.
In certain embodiments, the lesions created by repositioning the helix-shaped support structure 22 are angularly and longitudinally displaced from the initial lesion (s) over the angular and longitudinal dimensions of the renal renal artery, respectively . The composite injury pattern created along the renal renal artery by the initial energy application and all subsequent energy applications after any repositioning of the energy delivery element (s) 24 can effectively result in discontinuous injury (i.e. , is formed from multiple treatment sites longitudinally and angularly spaced).
In an alternative embodiment, the energy supply element 24 can be in the form of an electrically conductive wire. As shown in Figure 5D, for example, a conductive wire 500 can be wound around the helical structure 22 to form a spiral electrode 24 '. The spiral electrode 24 'can provide increased surface area 10 for energy dispensing. For example, the spiral electrode
24 'can form a generally continuous helical lesion in a single application of energy. The spiral electrode 24 'can be wound in any way on the helical structure 22, depending on the desired lesion. For example, the spiral electrode 24 'can form a continuous path along a length of the helix or the spiral structure can form one or more discrete short electrodes separated by non-conductive sections. In other embodiments, the portions of the spiral electrode 24 'can be positioned on the helical structure to contact the vessel wall when the helical structure is expanded, while other portions 20 of the spiral electrode 24' can be positioned far away of the vessel wall when the helical structure is expanded to allow the lesions to be discontinuous. In addition, in such an arrangement, the regions of the 24 'spiral electrode that do not come into contact with the renal artery can contribute to the cooling of the 24' energy dispensing elements, as described in more detail below. The positioning and number of conductive portions that form the energy delivery elements 24 'can be selected according to a desired injury pattern.
In embodiments shown in Figures 5A and 5B, the energy dispensing elements 24 preferably comprise metal electrodes with rounded ends and a lumen. The helical support structure of nitinol 22 is preferably electrically insulated (for example, with PET) and the electrodes 24 are mounted on the insulation. Power wires 25 connect the electrodes to a power source (not shown 5) and dispense energy (eg, RF electric current) to the electrodes 24. The rounded ends reduce mechanical irritation of the vessel wall and provide a current density more consistent when energy is dispensed compared to electrodes with square or sharper ends. The energy dispensing elements 24 may alternatively comprise other shapes as noted, such as a spiral electrode 24 'described above with reference to Figure 5D. In another embodiment, the structural element 510 that forms the helical structure 22 can be the 24 'energy dispensing element itself, as seen, for example, in Figure 5C.
III. Selected embodiments of renal denervation systems
Representative embodiments provided for in the present invention include features that can be combined with each other and with features of other described embodiments. In an effort to provide a succinct description of these embodiments, not all of the characteristics of an actual implementation are described in the specification. It should be appreciated that in the development of any such real implementation, as in any engineering or design project, numerous specific implementation decisions must be made to achieve the specific goals of the developers, such as compliance with system and business-related restrictions , which can vary from one implementation to another.
Figure 6A illustrates an embodiment of a treatment device 112, including an elongated shaft 116 that has several mechanical and functional regions configured in accordance with an embodiment of the technology. The elongated axis 116 of treatment device 112, for example, includes a distal region with a therapeutic or treatment set 121 for dispensing and developing in a renal artery site for treatment and, in particular, for renal denervation. Arranged at a proximal end of the elongated shaft 116 is a handle assembly 134 for handling the elongated shaft 116 and therapeutic assembly 121. More specifically, handle assembly 134 is configured with an actuator 136 (shown schematically), to provide the remote operation of a control member (e.g., control wire 168 of Figures 6E or 8A) to control or transform therapeutic set 121 between a dispensing state and a developed state. Further details on suitable handle assemblies can be found, for example, in US Patent Application No. 12 / 759,641, Handle Assemblies for intravascular treatment devices and associated system and methods ”by Clark et al., Which is incorporated herein by reference in its entirety.
The treatment device 112 is configured to deliver the therapeutic set 121 to a treatment site in a dispensing state (for example, low profile) in which the set 121 is substantially linear (for example, straight) such that the energy dispensing elements (not shown) carried by a support structure 122 of the treatment set 121 are substantially aligned axially along the support member 122. Once located at the treatment site within the renal artery, the handle assembly 134 is operated to activate a control member that transforms the therapeutic set 121 from the dispensing state to a developed state. In one embodiment, for example, the control member comprises a control wire 168 (Fig. 8 A) placed within an inner lumen of the tubular support structure 122. One end of the control wire 168 can be attached at or near the distal end of support structure 122, and the opposite end of control wire 168 ends within handle assembly 134. As mentioned earlier, handle assembly 134 is configured to manipulate control wire 168 to transform the therapeutic set 121 between the states of dispensation and developed. The traction on the control wire 168 provides an axially directed force that acts on the support structure 122. Under the influence of the traction force on the control wire 168 and, in operation within a patient under the influence of a radial restriction of the renal artery wall of the patient, the support structure 122 deforms in order to develop in helical geometry to bring the energy supply elements in stable contact with the renal artery wall.
In order to provide the desired deformation during development, the support structure 122 can be a tubular member that has a plurality of grooves, cuts, through holes, and / or openings formed or selectively eliminated on the support structure 122. The structure tubular support rod 122 may have a number of characteristics in general similar to those of the support structure 22 described above. For example, support structure 122 may be formed from biocompatible metals and / or polymers, including PET, polyamide, polyimide, block copolymer of polyethylene amide, polypropylene, or PEEK polymers, and the grooves are preferably laser cutting on the tubular structure in a desired configuration. In particular embodiments, the support structure 122 may be electrically non-conductive, electrically conductive (for example, stainless steel, nitinol, silver, platinum, nickel-cobaltochrome-molybdenum alloy), or a combination of electrically conductive and non-conductive materials conductors. In a particular embodiment, the support structure 122 can be formed from a precast material, such as elastic tempered stainless steel or nitinol. In addition, in some embodiments, the support structure 122 may be formed, at least in part, from radiopaque materials that are capable of being converted into an image by fluoroscopy to allow a clinician to determine whether the support structure 122 it is properly placed and / or developed in the renal artery. Radiopaque materials can include barium sulfate, bismuth trioxide, bismuth subcarbonate, powdered tungsten, tantalum and powder, or various formulations of certain metals, including gold, platinum and platinum-iridium, and these materials can be incorporated directly into the structure support structure 122 or can form a partial or total covering of the support structure 122.
The location, orientation and / or configuration of grooves, cuts, through holes and / or openings formed or arranged on the support structure 122 define the deformation of the structure. In addition, the grooves, cuts, through holes and / or openings can be varied along the tubular structure 122 in order to define the variable regions of deformation along the structure. In the embodiment illustrated in Figure 6A, for example, the tubular structure 122 includes a distal deflection region 122a, an intermediate orientation region 122b proximal to the distal deflection region 122a, and a transition or flexible region 122c proximal to the region of orientation 122b. As will be described in more detail below, the deflection region 122a is configured to have a substantially helical geometry in development. Orientation region 122b is configured to locate or request deflection region 122a away from a longitudinal geometric axis B of elongated axis 116 and towards a renal artery wall. The transition region 122c is configured to provide flexibility to the treatment device 112, as the elongated axis 112 is advanced through the sometimes tortuous intravascular path, from the percutaneous access site to the target treatment site within the respective renal artery ( as described above with reference to figure 2). Further details on the various mechanical and functional aspects of the different regions of the 112 treatment device are described below.
Figure 6B is a plan view of a groove pattern configured in accordance with an embodiment of the technology. Referring to Figures 6A and 6B together, for example, the deflection regions 122 can be defined by a plurality of substantially equal length transverse grooves 128, arranged along the spiral-shaped support structure 122. Orientation region 122b can be defined by a plurality of axially spaced transverse grooves 130 in which at least two grooves differ in length. In addition, as best seen in Figure 6A, the orientation regions 122b may have an axial length less than the deflection region 122a. The transition region 122c is located proximally to the orientation region 122b and has an axial length greater than each of the deflection regions 122a and the orientation region 122b. In the illustrated embodiment, the transition region 122c can include a continuous spiral cut or slit 132 with a variable pitch along the support structure 122. In one embodiment, for example, the spiral cut pitch 132 can increase proximally along the elongated axis 116. Further details on the various mechanical and functional aspects of the regions of the treatment device 112 are described below.
Figure 6C is a perspective view of treatment device 112, including support structure 122 in a dispensing state (e.g., low profile or retracted configuration) outside a patient, according to a shape of realization of the present technology, and Figure 6D is a perspective view of the support structure 122 in a developed state (e.g., expanded configuration). For ease of understanding, the support structure 122 in Figures 6C and 6D is shown without energy supply elements disposed on the support structure 122.
Referring to Figures 6C and 6D together, the support structure 122 comprises a tubular member having a central lumen, to define a longitudinal geometric axis B-B. As previously described, support structure 122 includes a generally flexible proximal transition region 122c, an intermediate orientation region 122b, and a distal deflection region 122a. The support structure 122 is selectively transformable between the dispensing state (Figure 6C) and the developed state (Figure 6D), by applying a force that has at least one axial component proximally directed and, preferably applied at or near the end distal 126a to transform distal deflection region 122a and intermediate orientation region 122b. In one embodiment, for example, an axial force applied at or near the distal end 126a directed at least partially, in the proximal direction 122a deflects the distal deflection region of the support structure 122 such that the support structure is formed helix-shaped, as shown in Figure 6D (for example, inside the renal artery) to bring one or more energy delivery elements (not shown) in contact with the inner wall of the renal artery.
The deflection region
As mentioned above, to provide the support structure 122 with the desired deflection and developmental configuration, the deflection region 122 includes a plurality of grooves 128a, 128b, 128c, ... 128n. Again, the plurality of grooves 128a-128n are selectively formed, spaced, and / or oriented around the longitudinal geometric axis BB in such a way that the distal deflection region 122a deviates from the region in a predictable manner, in order to form a helical geometry in the state developed within the renal artery. Outside the renal artery or other lumen that can radially limit the deflection of distal region 122a, distal region 122a can define a non-helical geometry in its fully expanded configuration, such as, for example, a substantially circular geometry, as shown in Figure 6E. As shown therein, the control wire 168 is disposed in the central lumen of the support structure 122, and is anchored at or near the distal ends 126a. When the control wire 168 is placed under tension in the proximal direction, at least a portion of the deflection region 122a (in the absence of any restriction in the radial direction) deviates from the substantially linear shape of Figure 6C to form the substantial circular shape of Figure 6E . More specifically, referring to Figures 6C-6E together, a portion of the deflection region 122a deviates in such a way that the deflection grooves 128a-n deform and close or approximately close (as shown schematically in Figure 6E) and provide the contact between the edges of the support structure 122 framing a central region in each groove 128. More details on the configuration of the grooves are described below.
The deflection region 122a is arranged to deviate about a center of curvature Z to define a first radius of curvature r with respect to a first surface 122d of the support member 122, and a second radius of curvature R with respect to a second surface. 122e. The second radius of curvature R is greater than the first radius of curvature r, with the difference being the width or diameter d of the support element 122 measured on its outer surface. Under a radial restriction of, for example, the inner wall of a renal artery, the deflection region 122a deforms to define a substantially helical developed shape (as shown in Figure 6D) instead of the substantially circular shape defined in the absence of restriction radial (as shown in Figure 6E). Thus, the proportions of the substantially helical shape developed (for example, the diameter and pitch of the helix) may vary according to the inner diameter of the lumen (for example, the lumen of the renal artery), within which the deflection region 122a is deformed.
The arrangement and configuration of the grooves 128a-128n (Figure 6C) further define the geometry of the flexible distal region 122a. Figure 6F, for example, schematically illustrates a groove pattern for grooves 128, according to an embodiment of the technology to illustrate the spacing and orientation of the groove over the deflection region 122a of the support member 122. Despite only four grooves 128a-d are shown in Figure 6F, it will be appreciated that the deflection region 122a can have any number of desired grooves 128. With reference to Figures 6E and 6F together, the centers of the grooves 128 are arranged and spaced along a progressive geometric axis C- C. The progressive geometric axis CC defines a progressive angle Θ with the longitudinal geometric axis BB of the support structure. 122 (Figure 6 A) to define an angular spacing of γ around the center of curvature Z (Figure 6E), in the developed state without restrictions. The centers of the grooves 128a-128d are shown to be substantially equidistantly spaced at a distance x. Alternatively, however, the center spacing between the grooves can vary (xl, x2, etc.) along the progressive geometric axis CC. Each slot 128 further defines a maximum arc length L around the longitudinal axis B-B and a maximum slot width W in the direction of the longitudinal axis B-B
The total number of grooves 128 in region 122a under deflection, multiplied by the width of groove W at a specific length defines the first radius of curvature r of the deflected portion of deflection region 122 (when placed in a developed state without restriction). In a particular embodiment, for example, each groove ma has a width W ranging from about 0.0005 to 0.010 inches (0.01 to 0.25 mm) and an arc length L groove of about 0 .0005 to 0.010 inches (0.01 to 0.25 mm) in order to define a first radius of curvature r, in a deflected state without restriction that varies between about 3.5 to 6 mm (7 to 12 mm) diameter). Minimizing the first radius of curvature r to a maximum application of axial force across the deflection region 122a of the support member 122 defines the flexibility of the deflection region 122a. Consequently, the smaller the first radius of curvature r, the greater the flexibility: the greater the first radius of curvature r, the greater the stiffness. Thus, the flexibility and / or stiffness of the deflection region 122a of the support member 122 can be defined by selecting the number and / or the width of the grooves in the distal region 122a. In one embodiment, for example, the 122nd deflection region can include about 2-100 grooves, each having a groove width W ranging from about 0.0005 to 0.010 inches (0.01 to 0, 25 mm) and a groove arc length L of about 0.0005 to 0.010 inches (0.01 to 0.25 mm) in order to define a first radius of curvature r, in a deflected state without restriction that varies between about 3.5 to 6 mm (7 to 12 mm in diameter).
Since the first radius of curvature r of deflection region 122a is directly related to the number of grooves 128, the number of grooves 128 can be reduced in number, so as to provide a non-continuous radius of curvature of a segment of the region deflection 122a so that the segment is substantially polygonal. Figure 6G, for example, is a schematic plan view of a treatment device 112 'configured in accordance with another embodiment of the technology. The deflection region 122'a of the treatment device 112 'may include a low or reduced number of deflection grooves 128 (for example, three grooves 128a-c are shown), so that the deflection region 122'a defines a substantially polygonal geometry when under a tensile load at its distal end (i.e., from control wire 168). In other embodiments, a different number of grooves 128 can be used to selectively form a desired geometry for the 112 'treatment device.
With reference again to Figures 6B and 6C and as noted earlier, the deflection region 122 is defined by a plurality of deflection grooves 128 in which each groove 128 extends substantially perpendicular to the longitudinal geometric axis BB of the support structure 122 with the grooves 128 being of substantially similar arc length. In addition, with reference to Figure 6F, the centers of the grooves 128 of the deflection region 122 are generally spaced apart along a progressive geometric axis CC which is distorted from the longitudinal geometric axis BB in such a way that the grooves 128 of the region of deflection 122a progress in a generally spiral form along the support structure 122 in the axial direction (as best seen in Figure 6C). The plurality of grooves 128 of the deflection region 122 are selectively formed, spaced and / or oriented around the longitudinal geometric axis BB so that the deflection region 122a deviates or deforms in a predictable manner, so as to preferably form a geometry helical when in a developed state (for example, inside the renal artery).
Referring again to Figure 6B, for example, the deflection region 122a includes a pattern of deflection grooves 128 arranged according to an embodiment of the technology to illustrate the spacing and orientation of the groove on the support member 122 (figure 6A ). The centers of the deflection slots 128 are arranged and spaced along the progressive geometric axis C-C. The progressive geometric axis CC defines a progressive angle θι with the longitudinal geometric axis B-B of the support structure 122 (figure 6A). The progressive angle 0j defines and, more particularly, corresponds directly to a pitch angle of the helical geometry defined by the support structure 122, when in a developed state. The progressive angle Θ] can range from, for example, about zero degrees (0 ° C) to about six degrees (6 ° C), for example, half a degree (0.5 °), two degrees (2 °) , etc. The centers of the deflection grooves 128 are shown to be substantially spaced evenly. In other embodiments, however, the spacing of the center between grooves 128 may vary along the progressive geometric axis C-C. The total number of grooves 128 that define the deflection region 122a can be about 2-100 grooves (for example, about 80 grooves). In a particular embodiment, the total axial length of the deflection region 122a is about one inch (2.54 cm). In other embodiments, however, the deflection region 122a may have a different number of grooves 128 and / or the grooves may have different dimensions or arrangements.
In one embodiment, each of the deflection grooves 128 comprises a substantially rectangular central region 129a which extends generally perpendicular to and around the longitudinal central geometric axis BB of axis 116. The elongated lateral walls of the central region 129a define a width of groove W between them (for example, about 0.0015 inches (0.038 mm)) to define a maximum slit that can be closed when groove 128 deforms during the deflection of region 122a. Each groove 128 further comprises the side regions 129b in communication or adjacent to the central region 129a. In one embodiment, the side regions 129b are substantially circular and have a diameter (for example, 0.0060 inches (0.15 mm)), to define stress relief regions at the ends of the grooves 128. The spacing between the centers of the substantially circular side regions 129b define an arc length L (for example, about 0.040 inches (1.02 mm)) around the longitudinal geometric axis of structure 122. In some embodiments, these side regions 129b can be formed as elliptical cuts at an angle not perpendicular to the longitudinal geometric axis BB of the support structure 122, 122 ', 122.
Alternative deflection groove configurations are possible. For example, the deflection grooves can be more specifically formed to provide desired flexibility and deflection in the deflection region 122a of the support member 122. Figures 6H and 61, for example, illustrate a deflection region 122a having deflection grooves 128 ' configured according to another form of technology realization. In this embodiment, the deflection grooves 128 'extend substantially perpendicular to the progressive geometric axis C-C and are substantially symmetrical about the progressive geometric axis C-C. The grooves 128 ', for example, may be, in general, I-shaped and include a central region 129a that extends perpendicular to the progressive geometric axis C-C with two enlarged side regions 129b arranged over the central groove region 129a. In addition, the walls of the support structure 122 forming the perimeter of each of the side regions 129b define a substantially rectangular geometry, preferably extending substantially parallel to the longitudinal geometric axis BB of the support structure 122 with the corners of the shaped openings rectangular being rounded. The central region 129a of the grooves 128 'can include a substantially circular cut out region 129c formed in communication with the side regions 129b. Alternatively, in some embodiments, the central region 129c of the grooves 128 'may be generally rectangular and not include a circular cutout.
As best seen in Figure 61, the distal grooves 128 'extend around the longitudinal geometric axis BB of the support structure 122 with an arc length L of, for example, less than about 0.05 inches (1.27 mm), for example, about 0.04 inches (1.02 mm). The side regions 129b define the maximum width W of the deflection groove 128 'to be, for example, about 0.03 inches (0.76 mm). The circular portion 129c of the central region 129a is contiguous with or in communication with the lateral regions and includes a central circular cutout 129c, with a diameter of, for example, about 0.01 inches (0.25 mm). The central region 129a defines a minimum width of, for example, about 0.02 inches (0.51 mm) in the longitudinal direction of the support structure. In a particular embodiment, the total number of grooves 128 'in the distal region is less than 30 grooves (for example, 25 grooves), the groove spacing is about 0.03-0.04 inches (0.76-1 , 02 mm), and the grooves are equally spaced in the distal deflection region 122. In other embodiments, however, the distal region may have a different number of grooves and / or the grooves may have a different arrangement (for example , different dimensions, different or not equal spacing between grooves, etc.)
Alternative groove, cut and / or opening configurations can provide desired flexibility, stress relief or other performance characteristics. Figure 6J, for example, is an alternative slot arrangement 128, which can be used, for example, both in the deflection region 122a and in the orientation region 122b (described in more detail below) of the support structure 122. The illustrative slot 128 includes a central region 129'a, which extends substantially perpendicular and about the longitudinal geometric axis BB of the support structure 122. The opposite side walls of central region 129'a are generally arched, each defining a radius of curvature (for example, about 0.06 inches (1.52 mm)) with a maximum WWW slot between them (for example, about 0.005 inches (0.13 mm)) to define the maximum slot slot that can be partially or totally closed during the deflection of the support structure 122. In addition, arranged around the longitudinal geometric axis BB of the support structure 122 are the lateral regions 129'b in communication, or contiguous with the region the central 129'a. The side regions 129'b are substantially circular and each has a diameter (for example, 0.005 inches (0.13 mm)) to define regions to relieve tension. The spacing between the centers of the curved side regions 129'b defines a length LLL (for example, about 0.04 inches (1.02 mm)) around the longitudinal geometric axis BB of the support structure 122. These side regions 129 'b can be formed, for example, as elliptical cuts at an angle not perpendicular to a longitudinal axis of the axis.
The configuration of a groove in the deflection region 122a and / or orientation region 122b of the elongated axis can impact the flexibility of the support structure 122. For example, as shown in figures 6K and 6L, the insertion (or absence) of the circular cutout 129c in the central region 129a of a groove 128, 128 ', 128 ”can vary the number of points of contact between the side walls of the grooves arranged around the axis of the groove bisector. Figure 6K, for example, illustrates a portion of distal region 122a in a folded or offset configuration. The central circular cutout 129c provides two points of contact 602 between the side walls of the central region 129a and a point of contact between each of the side regions 129b and the central circular cutout 129c. In contrast and referring to Figure 6L, the absence of a central circular cutout 129c provides a single point of contact 602 between the walls of the central region 129c when along a deviated portion of the distal region 122 ”.
It should also be noted that, in order to facilitate the manufacture of the support members 122, 122 ', 122, the deflection grooves 128, 128', 128 described above can be formed perpendicular or generally perpendicular to both the longitudinal geometric axis BB and to the progressive geometric axis CC, without impairing the ability of the support member 122, 122 ', 122 to form the desired helical geometry when in a developed state.
In addition, as described above with reference to Figure 6E, when the support structure 122 is transformed from the dispensing state to the developed state, the grooves 128, 128 ”, 128 'are deformed in such a way that the walls defining the central regions 129a, 129 a (as shown, for example, in Figures 6B, 61, and 6J) approach each other to narrow the widths of the corresponding slot W, WW, WWW up to and including the total slot closure, in which one or more pairs of opposite contact points touch each other (as shown schematically in Figure 6E and described above with reference to figures 6K and 6L).
The orientation region
Referring again to Figures 6A-6D and as discussed earlier, disposed close to the deflection region 122a is the orientation region 122b defined by a plurality of orientation grooves 130. It may be desirable to control the orientation of the helical geometric axis in relation to the axis longitudinal geometric shape BB of the support structure 122. For example, in a therapeutic set incorporating the support structure 122, it may be desirable to direct the therapeutic set in a selected direction away from the longitudinal geometric axis BB in such a way that at least one portion of the deflection region 122a is displaced laterally from the proximal end 126b of the support structure 122 and / or a distal end of the elongated axis 116. As best seen in Figure 6D, for example, the orientation region 122b may include grooves or orientation openings 130 that are formed, spaced and / or oriented to provide a directional axis BB which is inclined (for example, from about 45 degrees (45 °) to about 90 degrees (90 °)) in relation to the longitudinal geometric axis BB and orients the geometry in a helical shape of the deflection region 122a adjacent to the renal artery wall with the helical geometric axis directed axially along the renal artery.
Orientation grooves 130 can have a variety of different layouts / configurations. Referring to Figure 6B (and with reference to Figure 6M), for example, the centers of the orientation grooves 130 are arranged and spaced along a DD orientation axis that is radially offset from the progressive CC axis (for example, about 90 ° around the longitudinal geometric axis BB of the support structure 122). The DD-oriented geometry axis can generally extend parallel to the longitudinal geometric axis BB, or, alternatively, it can be inclined at an angle selected in relation to the longitudinal geometric axis BB (as described in greater detail below with reference to Figure 6 N). In the illustrated embodiment, the centers of the orientation grooves 130 are shown to be substantially spaced evenly. In other embodiments, however, the spacing between the individual grooves 130 can vary along the D-D orientation axis. Each slot 130 defines a maximum arc length LL around the longitudinal geometric axis B-B and a maximum slot width WW in the direction of the longitudinal geometric axis B-B.
With reference to Figure 6B, in one embodiment, the guide grooves 130 can include groups of grooves of different arc lengths LL around the longitudinal geometric axis B-B. For example, the orientation grooves 130 can include a first group of orientation grooves 130a having a first arc length, a second group of orientation grooves 130b having a second arc length less than the first arc length of the first group of orientation grooves 130a, and a third group of orientation grooves 130c having a third arc length less than the second arc length of group 130b. For example, in a particular embodiment, the first group of orientation grooves 130 has an arc length of about 0.038 inches (0.97 mm), the second group of orientation grooves 130b has an arc length of about 0.034 inches (0.86 mm), and the third group of orientation grooves 130c has an arc length of about 0.03 inches (0.76 mm). In other embodiments, however, the guiding grooves 130 may have different sizes and / or arrangements in relation to one another. For example, in some embodiments, one or more groups of guiding grooves 130 may have different groove widths (in addition to, or instead of, different arc lengths).
In one embodiment, the total number of grooves 130 defining the orientation region 122b is less than 20 grooves (for example, about 5-15 grooves, about 6-12 grooves, etc.) equally spaced along the orientation region 122b. In addition, in a particular embodiment, the total axial length of the orientation region 122b is about 0.2 to 0.25 inches (5.08 to 6.35 mm). In other embodiments, the orientation region 122b may have a different number of grooves and / or different arrangement and / or dimensions.
Alternative orientation slot configurations are possible. For example, referring again to the pattern shown in Figure 61, the orientation grooves 130 'can be substantially elongated by defining an arc length LL', preferably at most around the longitudinal geometric axis BB and a maximum groove width WW in the direction of the longitudinal geometric axis BB. In a particular embodiment, for example, each orientation groove 130 'has a width W that ranges from about 0.0005 to 0.010 inches (0.01 mm to 0.03 mm) and a length of groove arc LL 'from about 0.0005 to 0.010 inches (from 0.01 mm to 0.03 mm) in order to define a first radius of curvature r, in a deflected state without restriction ranging from about 7 to 12 mm. In other embodiments, however, the guiding grooves 130 'can have other dimensions and / or arrangements.
In the illustrated embodiment, the orientation grooves 130 'generally extend perpendicular to the D-D orientation axis and are substantially symmetrical with respect to the D-D orientation axis. The guiding grooves 130 'are, in general, I-shaped having a central region 131a that extends perpendicular to the D-D guiding axis with the two enlarged side regions 131B arranged over the central groove region 131a for strain relief. In this embodiment, the walls of the support structure 122 forming the perimeter of each of the side regions 131b can define, for example, a substantially rectangular geometry that extends substantially parallel to the longitudinal geometric axis BB of the support structure 122 with the corners of the rectangular shaped openings being rounded (not shown). In addition, the central regions 131a of the individual guiding grooves 130 'may be generally rectangular, or may have another suitable shape.
Each of the orientation grooves 130 'shown in Figure 61 can include a substantial rectangular central region 131a that extends substantially perpendicular and about the longitudinal geometric axis BB of the support structure 122. The elongated lateral walls of the central region 131a define a slot between them (for example, about 0.0015 inches (0.038 mm)) to define a maximum closing slot of the groove during deflection of the structure 122. Each groove 130 'can also include the side regions 131b arranged around the longitudinal geometric axis BB and in communication, or contiguous with the central region 131a. The side regions 131b define a substantially rectangular geometry, preferably extending substantially parallel to the longitudinal geometric axis B-B of the support structure 122 with the corners of the rectangular shaped openings being rounded to define stress relief regions. The spacing between the centers of the substantially rectangular side regions 131b defines an arc length L (e.g., about 0.04 inches (1.02 mm)) about the longitudinal geometric axis B-B of the support structure 122. Alternatively, the lateral regions 131b can be formed as elliptical cuts at a non-perpendicular angle to the longitudinal geometric axis B-B of the support structure 122, 122 122,
In some embodiments, the total number of grooves 130 'in the orientation region is generally less than 10 grooves, for example, five grooves, the groove spacing can be, for example, from about 0.03 to 0.04 inches (0.76 mm to 1.02 mm), and the slots 130 can be evenly spaced. In addition, in some embodiments, the geometry axis DD can generally be parallel to the longitudinal geometry axis BB and radially displaced from the progressive geometry axis CC at a minimum arc length distance, for example, of about 0.01 inches (0.25 mm) at an angle ranging from about 50 ° to less than 90 ⁰ about the longitudinal axis BB of the support structure 122.
In yet another embodiment, the guiding grooves 130 can be arranged along an orientation axis which is substantially inclined with respect to the longitudinal axis BB. Figure 6N, for example, is a plan view of a groove pattern configured in accordance with another embodiment of the technology. In this embodiment, the guide grooves 130 are disposed on an axis direction D ₂ -D ₂ can be inclined relative to the longitudinal axis by BB ₂ 0 angle ranging from, e.g., about from 0 degrees (0 ⁰ C) to about 45 degrees (45 °). The angularly oriented geometry axis D ₂ -D ₂ provides an orientation region 122b that has a tapered helical geometry by developing support structure 122. Figure 60, for example, is a schematic illustration of a portion of a treatment that has a supportive structure, including the groove pattern of Figure 6N in a state developed within a patient's renal artery.
The flexible / transition region
Referring again to Figure 6A, arranged proximally to the orientation region 122b is the flexible or transition region 122c. As noted above, the flexible region 122c can include, for example, the transitional spiral or helical groove or cut 132 with a variable pitch over its length. The variable pitch of the spiral cut 132 along the length of the flexible region 122c provides the support structure 122 with variable flexibility along the length of the elongated axis 116. In one embodiment, for example, the transitional cut 132 extends over an axial length of, for example, about 170 millimeters starting near the orientation region 122b. In other embodiments, however, the transitional cut 132 can be of a different length.
As shown in Figures 6C and 6D, in some embodiments, the transitional cut step 132 can vary over the length of the transitional cut to define multiple different transition regions (four transition regions 132a, 132b, 132c, and 132d are shown in Figure 6C). More specifically, in one embodiment, the cut 132 defines a first transitional portion 132a having a first pass forming, for example, five turns on the tubular support structure 122 at a spacing of 0.02 inches (0.51 mm) and in transitions to a second transitional portion 132b having a second pass defined by, for example, five turns with a spacing of 0.040 inches (1.02 mm). Cut 132 continues to define a third transitional portion 132a having a third pass defined by, for example, ten turns with a spacing of 0.06 inches (1.52 mm) and transitions to a fourth pass defined by, for example, 20 revolutions at a spacing of 0.08 inches (2.03 mm). It should be noted, in the example above, that considering each sequential transitional portion 132 so from the distal end to the proximal end of the transition region 122c, the pitch pitch of the groove increases and the flexibility of the support structure tubular 122 decreases.
The transitional cut 132 can have a generally constant width, for example, of about 0.0005 inches (0.01 mm) along its length, or the width of the transitional cut 132 can vary along its length. The transitional cut 132 may also include at each end of a substantially circular void contiguous with or in communication with the transitional cut. In other embodiments, however, the transitional cut 132 may have a different layout and / or different dimensions. For example, instead of having gradual pitch increases, the transitional cut 132 may have a pitch increasing continuously from the distal end to the proximal end of the transition region 122c.
Alternative groove, cut and / or opening configurations can provide the desired flexibility, stress relief, or other performance characteristics in the flexible region 122c instead of the transition cut 132. In some embodiments, for example, the opening or holes can be selectively formed on the elongated axis 116 to provide the desired flexibility. The individual openings or holes in the flexible region 122c can, for example, have centers arranged along a geometric axis that extends parallel to the longitudinal central geometric axis BB of the support structure 122. Figures 7A and 7B, for example, illustrate the structure support 122 with an alternative arrangement for the flexible region 122c, which have through holes or openings 132'a, 132'b, 132'c that each extend through the tubular support structure 122. The openings 132 ', for For example, they may be alternately arranged on geometrical axes that are angularly spaced from each other around the longitudinal geometrical axis BB of the support structure 122. In the illustrated embodiment, for example, opening 132'b is angled 90 ° in in relation to the axially adjacent openings 132'a and 132'c. In other embodiments, however, the openings 132 'may have a different arrangement.
Figure 8A is a broken perspective view in partial section of a treatment device 100 including a catheter that has an elongated axis 116 with a distal region 120 that has a support structure 122 for dispensing and developing a therapeutic or treatment 121 at a target treatment site in a lumen and, in particular, for carrying out renal denervation within the renal artery. Arranged at a proximal end of the elongated axis 116 is a handle assembly 134, shown schematically, for manipulating the elongated axis 116 and the therapeutic assembly 21. More specifically, handle set 134 is configured to provide remote operation of a control member 168 (e.g., a control wire), to control or transform therapeutic set 121 between a dispensing state and a developed state (shown in Figure 8A).
System 100 is configured to dispense therapeutic set 121 at the treatment site in a dispensing state (not shown), in which therapeutic set 121 is substantially linear (e.g., straight) in such a way that the energy dispensing elements 124 are substantially axially aligned along the support member 122. Power supply wires 25 can be arranged along an external surface of the support member 122 and coupled to each of the power supply elements 124 for power supply treatment of the respective energy dispensing elements 124. Once located at the treatment site within the renal artery, actuation of the control member 168, transforms the therapeutic set 121 from the dispensing state to the developed state, as shown. In the illustrated embodiment, the control wire 168 is disposed within the tubular support structure 122. An end of the control member 168 can be affixed to or near the distal end 126a of the support structure 122 (for example, terminating at a tip member 174). The opposite end of the control member 168 can terminate inside the handle assembly 134 and be operatively connected to an actuator to transform the therapeutic assembly 121 between the dispensing state and the developed state.
The traction on the control member 168 can provide a proximal and / or axially directed force towards the distal end 126a of the support structure 122. For example, under the influence of the traction force on the control member 168, the distal region 122b of the structure deflector support plate 122. The distal deflection region 122a preferably includes a plurality of grooves 128 (only two are shown as 128'a and 128'b). As described above, the grooves 128'a and 128'b are arranged along a progressive geometric axis. The grooves 128'a and 128'b formed in the distal region 122a of the support structure require the deflection of the distal region 122a, in order to form one or more curved portions, each having a radius of curvature preferably defined by the number of grooves of deflection 128, by the width of the individual groove, by the groove configuration, and / or by the groove arrangement. As the distal region 122a continues to deflect, it expands radially by placing one or more of the separate and spaced energy elements 124 in contact with the inner wall 55 of the renal artery. The support structure 122, when subjected to the traction of the control wire 168 and the radial restrictions of the vessel wall 55, is configured to form a substantially helical shape, in order to axially space and radially displace the energy dispensing elements 124 among themselves. Furthermore, due to the fact that the deflection region 122a of the support structure 122 is configured to form a helical geometry inside the renal artery, when under a traction load, the treatment set 121 is not expected to radially overload the wall 55 of the renal artery. Instead, the support structure 122 deforms to form the propeller under a continuously increasing tensile load.
As discussed above, the progressive angle of the geometric axis (e.g., progressive geometric axis C-C) along which the deflection grooves 128, 128 ', 128 are eliminated defines the helical angle of the resulting developed arrangement. In one embodiment, the amount of traction to fully develop the therapeutic set 121 is typically less than, for example, about 1.5 Ibf (pounds-force) (0.68 kgf) applied to the distal end 126a of the set therapeutic 121, for example, between about 1 Ibf (0.45 kgf) and about 1.5 Ibf (0.68 kgf). In the helically developed state of Figure 8 A, the grooves 128 'are arranged along the internal surface of the propeller with the supply wires 25 for the energy supply elements 24 arranged on an external surface of the propeller, so as to form a backbone of the set. The supply wires 25 may extend along the length of the treatment device 112 to a suitably configured energy generator (not shown).
The support structure 122 of the therapeutic set 121 includes a proximal portion that defines an orientation region 122b of the set to locate the therapeutic set adjacent to the renal artery wall. As shown in Figure 8A, the proximal region of the support structure 122 includes a plurality of orientation grooves 130. In operation, during the actuation of the handle assembly 134 to place the control wire 168 under tension, the orientation region 122b deflects in a radially outward direction within the renal artery 121 to locate the therapeutic assembly in contact with the arterial wall 55. More specifically, the grooves 130 'deform under the tensile force, in order to deflect the region of orientation 122b radially towards out from the longitudinal geometric axis BB of the support structure 122. In the fully developed state, the helical geometry resulting from the therapeutic assembly 121 at the distal end of the support structure 122 is preferably displaced from the longitudinal geometric axis BB at the proximal end of the support structure support 122 such that the helical axis Η- H and the longitudinal axis al
B-B of the support structure 122 are non-coaxial. The geometry axes H-H, B-B can be parallel to each other or, alternatively, inclined to each other.
The proximal end of the support structure 122 can be coupled to a separate member forming the elongated axis 116 of the device 112. Alternatively, the support structure 122 and the elongated axis 116 can be a single unitary member extending proximally from the end distal 126a for the handle assembly 134. In one embodiment, the tubular support structure 122 is formed from a metallic material with shape memory (e.g., nitinol). In addition, in one embodiment, the support structure 122 may have an axial length of less than five inches (12.7 cm) and, more specifically, about two inches (5.08 cm); an outer diameter of about 0.020 inches (0.57 mm) and, more specifically, ranging from about 0.016 inches (0.41 mm) to about 0.018 inches (0.46 mm), with a tubular wall thickness less than 0.005 inches (0.13 mm) and, more particularly, about 0.003 inches (0.08 mm). In various embodiments, the elongated shaft 116 can be formed from stainless steel metal tube that has an outside diameter of, for example, about 0.020 (0.57 mm) to about 0.060 inches (1.52 mm). In coupling the proximal support structure 122 of the elongated axis 116, a joint 119 can be provided between them to provide the desired transfer of torque from the elongated axis 116 of the support structure 122 during navigation to the treatment site. More specifically, each of the ends of the support structure 122 and the elongated axis 116 can respectively include notches that allow the ends of the tubular members to interconnect with each other, as shown in the hinge assembly 120. In some embodiments arranged around joint 119 is a stainless steel sleeve which is driven into the joint to provide additional support for joint 119.
As mentioned above, the control member 168 can be a control rod or wire that extends the axial length of the catheter device 112 at or near the distal end 126a of the support structure 122 for the handle assembly 134. The control cable 168 can be composed of ultra high molecular weight (UHMW) fiber, such as, for example, high strength gel spun fiber, sold under the trademark SPECTRA or another sufficiently strong polyethylene fiber. Alternatively, nitinol, a synthetic para-aramid fiber marketed under the trademark KEVEAR, or other types of mono- or multifilament can be used as long as they are compatible with the application and can transfer the traction force to the distal end of the therapeutic set 121 along the length of the treatment device 112.
To provide the desired tractive force at the distal end of the therapeutic assembly 121, the control wire 168 can be anchored at or near the distal end 126a of the support structure 122. Figures 8B8D, for example, illustrate various anchoring configurations for the control wire 168. More specifically, as shown in Figure 8B, the distal end 126a of the support structure includes a groove adjacent to the axial opening to tie and anchor control wire 168 therethrough. In an alternative anchoring arrangement shown in Figure 8C, the control wire 168 extends through the axial opening at the distal end 126a. The control wire 168 can be enclosed in a coil material 174 to stop the control wire 168 from sliding proximally in the distal portion of the support structure 122. Figure 8D illustrates another tip 174 is configured according to an embodiment of the description. In this arrangement, the control wire 168 can be triple knotted to provide an enlarged surface of the control wire 168, on which the coating of the polymer material is formed at one end.
With reference again to Figure 8A, the control wire 168 can extend through the elongated axis 116 to the handle assembly 134. During operation of the handle assembly 134 to pull and release the control wire 168, by transforming the therapeutic set between developed and dispensed states, friction occurs between the moving control wire 168 and the interior of the relatively stationary elongated axis. An embodiment of the control wire assembly 168 is configured to minimize the frictional contact between the control wire 168 and the interior of the elongated shaft 116. For example, as shown in Figure 8A, sleeve 170 can be eliminated and connected to the control wire 168 to provide a relatively low friction outer surface. The sleeve 170 preferably has an axial length that is less than that of the elongated shaft 116 and, more preferably, covers a substantially proximal portion of the control wire 168 within the elongated shaft 116. During operation of the handle assembly 134 for pulling and releasing the control wire 168, the tubular sleeve 170 is configured to move with the control wire 168 and acts as a support surface against the interior of the elongated shaft 116, thereby reducing the friction between the control wire 168 and the elongated axis 116.
In various embodiments, a control member can be configured to be outside the support structure of the treatment set, which carries the energy supply elements. For example, the support structure of the treatment assembly can preferably be either rolled up or wrapped around the control member. In such arrangements, the control member engages a part of the support structure to apply a force that converts the support structure and the treatment set between its dispensed and developed state.
Figures 9A and 9B, for example, illustrate a distal portion of a treatment device 212 configured in accordance with other embodiments of the present technology. More specifically, the Figures
9A and 9B illustrate a treatment assembly 221 having a tubular support structure 222 helically wound around a control member 268 with a plurality of energy supply elements 224 arranged around support structure 222. Support structure 222 it may include a number of features generally similar to the support structures 22 and 122 described above.
In the illustrated embodiment, the distal region or portion 222a of support structure 222 terminates at an end piece (e.g., a tapered or bullet-shaped tip 250) or, alternatively, a collar, shaft, or cap. Tip 250 may include a rounded distal portion to facilitate non-traumatic insertion of treatment device 212 into the renal artery. The proximal region or portion 222b of the support structure 222 is coupled and attached to an elongated axis 216 of the treatment device 212. The elongated axis 216 defines a central passage for the passage of a control member 268. The control member 268 can be, for example, a solid wire made of a metal or polymer. The control member 268 extends from the elongated axis 216 and is attached to the distal region 222a of the support structure 222 at the tip 250. In addition, the control member 268 slid through the elongated axis 216 to an actuator 236 in a handle assembly 234.
In this embodiment, the control member 268 is configured to move distally and proximally through the elongated axis 216, so as to move the distal region 222a of the support structure 222 accordingly. Distal and proximal movement of the distal region 222a, respectively, elongate and shorten the axial length of the helix of the support structure 222 in order to transform the treatment set 221 between a dispensing state (Figure 9B) and developed (Figure 9A), from so that the energy delivery elements 224 move a radial distance Y to engage the walls of the renal artery (not shown).
In an alternative embodiment, the treatment set cannot be attached to a control member in the distal region of the tubular support structure. Figure 9C, for example, illustrates another embodiment of a treatment device 212 'and a treatment assembly 221' which has a helical shaped support structure 222 with a plurality of energy supply elements 224 arranged around of the helical support structure 222. The distal end region 222a of the support structure 222 is coupled to a collar element 274 that includes a sized and shaped passage to slide the control member 268 that ends in an end piece 250. In this embodiment, the control member 268 comprises control wire extending from the elongated axis 216, and moves distally and proximally through the elongated axis 216, and the collar element 274. A stop member 275 can be connected to the control wire 268 proximal to the collar element 274.
The control wire 268 facilitates the expansion and / or contraction of the helical support structure 222 when it is pulled or pushed to shorten or lengthen the helical support structure 222. For example, the act of pulling (i.e., an increase in traction ) the control wire 268 can trigger the expansion of the helical structure 222, while the act of pushing (i.e., an increase in compression) the control wire 268 can extend the helical support structure 222 to a compressed configuration. In some embodiments, the helical structure 222 has elastic or superelastic properties so that, when the force is removed, the helical structure 222 elastically returns to a relaxed state. The force can be applied to the end piece 250, or to the stop member 275 to transform the treatment set 221 'between the dispensing and developed states. For example, control wire 268 can be pushed distally such that stop member 275 engages and distally moves collar element 274 to extend support structure 222 and reduce its diameter by placing it in a dispensation status. Alternatively, the control wire 268 can be pulled proximally to make the end piece 250 engage and 5 proximally move the collar element 274 in order to reduce the helical support structure 222 and increase its diameter by placing it in a developed state.
When the helical support structure 222 has a preformed helical shape memory, the helical support structure 10 222 expands elastically to its preformed shape when the collar element 274 is not engaged with the stop member 275 or with end piece 250. In this way, helical support structure 222 can expand to contact the inner wall of the renal artery with relatively consistent force. In addition, in some embodiments, the force exerted on the renal arterial wall by the preformed helical structure 222 may be less dependent on operator control in handle assembly 234 (Figure 9A).
Figures 9D and 9E show another embodiment of a treatment device 212. In this embodiment, the control member 268 'comprises a hollow tube that defines an internal passage for the guide wire 266 to facilitate the insertion of the assembly of treatment 221 through an intravascular pathway to a renal artery. Thus, the treatment device 212 is configured for an OTW or RX dispensation as described herein. Control member 268 'defines an internal lumen 25 extending through the control member and composed of, for example, a polyimide tube with a wall thickness of less than about 0.003 inches (0.08 mm) (for example, for example, about 0.001 inches (0.02 mm)) and a lumen, with a diameter less than about 0.015 inches (0.38 mm) (for example, about 0.014 inches (0.36 mm)). In addition to engaging and trailing along guide wire 266, device 212 transforms the configuration of treatment set 221 between the dispensing state and the developed state in a manner similar to that of treatment device 212 shown and described with respect to Figures 9 A and 9B.
Figures 10A and 10B are side views of another embodiment of a treatment device 310 having an OTW configuration and including a tubular control member 368 defining a guide wire lumen that extends substantially the entire length of the device. The control member 368 is configured to slide a guide wire 366 in such a way that the treatment device 310 can be controlled along the guide wire 366 using over-the-wire techniques. The control member 368 is slidably disposed within an elongated axis 316. In one embodiment, the control member 368 is allowed to slide relative to the elongated axis 316 within a thin-walled sleeve (not shown) which is connected to an internal surface of the elongated shaft 316 using thermal or adhesive bonding methods. The thin-walled glove can be formed from a polymeric material such as, but not limited to, polyimide. In other embodiments, however, treatment device 310 cannot include the glove.
Treatment device 310 also includes a treatment set 312 that extends between a distal part of the elongated axis 316 and a distal portion of the control member 368. Treatment set 312 can be developed at the target site within the vasculature and includes multiple (e.g., six) energy dispensing elements 324 (e.g., electrodes) for dispensing energy from an energy generator 326 to a vessel wall. In some embodiments, the energy supply elements or electrodes 324 can be equally spaced along the length of the support structure 322. In other embodiments, however, the number and / or arrangements of the energy supply elements 324 may vary. The axial length of the support structure 322 can be between, for example, about 17 mm to 20 mm. In other embodiments, however, the support structure 322 can be of a different length, as long as the structure sufficiently supports the number of electrodes in a desired electrode spacing pattern.
The energy dispensing elements 324 can be a series of separate band electrodes spaced along the support structure 322. Band or tubular electrodes can be used in some embodiments, for example, because they have lower energy requirements for ablation in relation to the flat or disk electrodes. In other embodiments, however, flat or disc electrodes are also suitable for use. In yet another embodiment, electrodes having a spiral or coiled shape can be used. In one embodiment, the individual power dispensing elements 324 can have a length ranging from about 1-5 mm, and the spacing between each of the power dispensing elements 324 can vary from about 1-10 mm . In other embodiments, however, the energy dispensing elements 324 can have different dimensions and / or arrangements.
The energy dispensing elements 324 can be formed from any suitable metallic material (for example, gold, platinum, an alloy of platinum and iridium, etc.). In one embodiment, for example, energy dispensing elements 324 can be 99.95% pure gold with an internal diameter ranging from about 0.025 inches (0.64 mm) to 0.030 inches (0.76 mm) ), and an outside diameter ranging from about 0.030 inches (0.76 mm) to 0.035 inches (0.89 mm). Electrodes of smaller or larger dimensions, that is, diameter and length, are also suitable for use here.
Each energy dispensing element or electrode 324 is electrically connected to generator 326 via a conductor or wire (not shown) that extends through an elongated shaft lumen 316. Each electrode 324 can be welded or otherwise electrically coupled to the distal end of its power supply wire and each wire can extend through the elongated axis 316, for the entire length of the axis such that its proximal end is coupled to the generator 326.
The support structure 322 can comprise a shape memory component, which extends at least the length of the set 312. The shape support structure 322 is used to develop or transform the treatment set 312 from a state of dispensing shown in Figure 10A (i.e., a substantially linear shape) to a developed state shown in Figure 10B (i.e., a spiral or predefined helical shape). More particularly, the support frame shape memory component 322 can be constructed from a shaped memory material that is preformed or precast in the developed state. Certain materials with shape memory have the ability to return to a predefined or predetermined shape when subjected to certain thermal conditions. When shape memory materials, such as nickel-titanium (nitinol) or shape memory polymers or electroactive polymers are at a relatively low temperature, items formed from it can generally be deformed quite easily in a new form that they preserve until exposed to a relatively higher transformation temperature, which in embodiments of this document is above the normal body temperature of 37 ° C, which then returns the items to the pre-defined form or pre-determined that they had before deformation. In some embodiments, the support structure 322 can be formed from such material with shape memory, inserted into the body in a low profile stretched deformed state, and resumed to a predefined remembered shape once the support structure shape memory 322 is exposed to an in vivo transformation temperature. Thus, the shape memory support structure 322 has at least two phases of size or shape, a coil configuration generally linear or stretched, of a profile low enough for dispensing at the treatment site as shown in figure 10A and a spiral or helical configuration that places the energy dispensing elements 324 in contact with the vessel wall 55, which is shown as a dashed line in Figure 10B. The dispensing state can also be achieved by mechanical stretching of the support structure with shape 322 by the operator or by means of a pulling device. Referring to Figure 10A, in one embodiment, a dispensing diameter D1 of 322 memory support structure can be between about 1 and 2 mm to accommodate dispensing to a target vessel, such as a renal artery.
Treatment set 312 may also include an insulating component (not shown) that works to electrically insulate the shape memory support structure 322 from the energy dispensing element 324. The insulating component, for example, may include a sheath tubular defining a lumen that is formed from an electrically insulating material, such as the block copolymer of polyethylene amide. In one embodiment, the insulating component can have an outer diameter of approximately 0.027 inches (0.69 mm) and an inner diameter of approximately 0.023 inches (0.59 mm). The insulating component is configured to accommodate the 322 shaped memory support structure, as well as housing wires to provide additional protection therefor, and electrodes 324 are connected to or placed around the insulating component. A distal end of the insulating component can be connected to a distal end of the axis of the guide wire 368 by any appropriate method, such as an adhesive, a glove, or another mechanical method. In an embodiment shown in Figure 10A, the distal end of the insulating component is preferably attached to the distal end of the guide wire axis 368 by means of a cyanoacrylate adhesive and a polymer sleeve surrounding and joining the distal ends, for form a tapered distal tip 350 of treatment set 312. In other embodiments, however, the insulating component may have a different arrangement in relation to treatment set 312.
Both the shape support structure 322 and the insulating component preferably extend along the length of the treatment set 312 and extend proximally at the distal end of the shaft 316, for example, at least an inch or two, so that the proximal end of the shaped support structure 322 is sufficiently removed from the energy dispensing elements 324, to avoid any thermal effect therefrom.
As the shape support structure 322 of treatment set 312 assumes the developed configuration, the distal end of the insulating component proximally retracts so that treatment set 312 radially expands in contact with the vessel wall, a since the distal end of the insulating component is coupled to the distal end of the inner tubular axis 368. The control member 368 also slightly proximally retracts within the elongated axis 316, in order to allow the development of the treatment set 312.
In each of the previously described embodiments of the therapeutic or treatment devices, the control member is configured as a wire, a tubular axis or other internal member that applies a force at or near the distal end of the support structure to alter the configuration of the therapeutic set between a dispensing state and a developed state. In other embodiments, however, an actuation force can be applied at or near the proximal end of the therapeutic set to transform the configuration of the set.
Figures 11A and 11B, for example, illustrate an embodiment of a treatment device 612 configured to apply a deformation force to a proximal end of the treatment set. The treatment device 612 includes an elongated tubular shaft 616 having a proximal end coupled to a handle assembly 634 and a distal end coupled to a treatment assembly 621. The illustrated treatment assembly 621 includes a tubular support structure 622 carrying a plurality of power supply elements 624. Power supply wires (omitted for clarity) extend either internally or externally along the support structure 622 to provide treatment energy to the power supply elements 624. The proximal end 622b of the the support structure 622 is arranged inside and fixed to the distal end of the elongated tubular axis 616. The support structure 622 defines a helical shape preferably wound around a tubular control member 668 having an internal lumen for the passage of a guide wire 666, which can extend distally beyond treatment set 621 and next beyond the handle assembly 634. Thus, the treatment device 612 is configured for an on-the-wire dispensing. The distal end of the support structure 622a is coupled to a distal region of the tubular control member 668. The control member 668 extends proximally to the elongated axis 616 and is attached to an internal surface of the handle assembly 634. Therefore, the distal end 622a of support structure 622 can remain at a fixed distance from handle assembly 634.
The elongated shaft 616 extends proximally in the handle assembly 634, and is coupled to an actuator 636. In one embodiment, the actuator 636 provides linear displacement or direct longitudinal translation of the elongated shaft 616. The actuator 636 is shown schematically as a set of cursor in the crease. In operation, the proximal translation of the actuator 636 translates the axial axis 616 proximally in relation to the handle assembly 634 and thus to the inner member 668. The distal end of the elongated axis 616 applies a pulling force to the fixed proximal end 622b of the support structure 622. Because the distal end 622a of the support structure 622 is attached to the control member 668, proximal translation of the proximal end 622a of the support structure 622 elongates the structure in order to place the treatment set 612 in a low profile dispensing state (Figure 11A). The distal translation of the actuator 636 results in the compression of the support structure 622 axially in order to place the treatment set 612 in a developed state (as best seen in Figure 11B).
Alternative configurations of the handle assembly 634 can provide the desired axial translation of the elongated shaft 616. Figure 11C, for example, illustrates an alternative arrangement of the handle assembly 634, which provides a pivot-type actuator 636 'to axially translate the elongated shaft 616 The actuator 636 'can include a pivot connection with the elongated shaft 616. Therefore, angular rotation of the actuator 636' over the pivot connection linearly translates the elongated shaft 616. The amount of angular rotation of the actuator 636 'can be controlled by the distance between the elongated axis 616 and the pivot point. Figure 11D illustrates another alternative configuration of handle assembly 634 including a gear-type actuator 636 for linearly translating the elongated shaft 616. In one embodiment, for example, actuator 636 includes a connected thumb button or roller to a small gear. The elongated shaft 616 can be connected to a larger gear fitted with the smaller gear in such a way that the smaller gear rotates, which in turn rotates the larger gear and moves the elongated shaft 616. The difference in gear sizes allows rotation of the small roller create a large translation of the elongated shaft 616.
In previously described embodiments of the treatment device, the treatment set of the devices has been changed between a dispensing state and a developed state, pushing or pulling either a proximal end or a distal end of the support structure according to the configuration. It should be understood that the treatment device can be configured to selectively apply a force to or near both the proximal and distal end of the support structure such that a clinician can select the end for relevant movement, depending, for example, on the limitations around the support structure.
In several alternative configurations, the treatment set can be mobile between the dispensing states and developed by any insertion or retraction of a control member (for example, an insertion element, the stylus, the preformed member, etc.) for a distal treatment section or portion of a tubular support structure. Figures 12A and 12B, for example, are side views in perspective of a portion of a treatment device 700 configured in accordance with an additional embodiment of the technology. More specifically, Figure 12A illustrates the treatment device 700 in a dispensing state (for example, low profile or retracted configuration) outside a patient, and Figure 12B illustrates the treatment device 700 in a developed state (for example, example, expanded configuration). Referring to Figures 12A and 12B together, treatment device 700 includes an elongated shaft 701 having a distal portion 702, and a treatment section 704 at distal portion 702. Treatment device 700 also includes a plurality of energy dispensing 706 carried by treatment section 704. Treatment device 700 further includes a control member 708 (shown schematically in broken lines), coupled to treatment device 700 and slidably movable in relation to treatment section 704. As will be described in more detail below, treatment section 704 or control member 708 comprises a preformed helical shape, and the other part of treatment section 704 and control member 708 comprises a substantially linear shape. Treatment section 704 and control member 708 are movable relative to each other in order to change treatment device 700 between a low profile dispensing state (Figure 12A) and an expanded dispensing state having the pre-helical shape formed (Figure 12B). For purposes of illustration, control member 708 is shown in both Figures 12A and 12B. As described in greater detail below, in various embodiments, control member 708 can be either inserted or removed from treatment section 704 to change treatment device 700 between dispensing and developed states.
For example, in an embodiment described below, control member 708 may include a stylus, stiffening mandrel, stretching member or a procedural guide wire extending over at least a portion of the length of treatment device 700 and configured to stretch a helically shaped preformed treatment section 704 of treatment device 700 during dispensing. More specifically, the control member 708 facilitates the expansion and / or contraction of the treatment section 704 when the control member 708 is pulled or pushed, respectively, in relation to the treatment section 704. In another embodiment, a member preformed control device (e.g., preformed member or stylus) can provide a helical shape with a relatively flexible distal portion 702 of treatment device 700.
Figures 13A-15B address different embodiments of treatment devices, including features generally similar to the treatment device 700 described above with reference to Figures 12A and 12B. Figures 13A and 13B, for example, are seen in cross section of a treatment device 712, including a treatment section or assembly 721 having a plurality of energy dispensing elements 724 carried by a relatively flexible tubular support structure 722 that defines a central lumen 729. The tubular support structure 722 includes a distal end 722a that has an axial opening for the passage of a guide wire 766 (figure 13A) extending through the lumen 729. The tubular support structure 722 has a proximal end 722b coupled to or affixed to the distal end of an elongated tubular axis 716. The elongated axis 716 defines a central lumen for housing the guide wire 766. Consequently, the present configuration provides an over-the-wire dispensing from a location access point in which the guide wire 766 is initially inserted to a treatment site (for example, inside a renal artery), and the transport device bandage 712 is installed on the guide wire 766. Inserting the substantially linear and straight guide wire 766 through the flexible tubular support structure 722, keeps the tubular support structure 722 in a linear shape, normally, in order to place the set of treatment 721 in a low profile dispensation state for dispensing to the renal artery treatment site. The guide wire 766 may have a constant stiffness along its length or it may have a variable stiffness or flexibility along its length, so as to provide increased flexibility, for example, in the proximal to distal direction.
Once the treatment device 712 is dispensed over the guide wire 766 to a desired position within the renal artery, the guide wire 766 is completely retracted from the treatment device 712 and an elongated control member 768 (Figure 13B) is inserted at a proximal end of the device 712 and advanced distally through the elongated axis 716 to the central lumen 729 of the tubular support structure 722. The distal region of the control member 768 may have a predefined developed shape (for example, a helical shape ), when the restriction is removed to define the developed state of the treatment set 721. The control member 768 can be made of a superelastic nitinol material that has a predefined or preformed helical shape. Alternatively, the control member can be made of material with shape memory.
Control member 768 is sufficiently elastic to be stretched for insertion at the proximal end of the device, for example, in handle 734. Control member 768 can be inserted directly into elongated axis 716. Alternatively, control member 768 it can first be housed inside a more rigid insertion tube 769 (Figure 13B) to stretch out the control wire 768 and facilitate the insertion of the control member 768 into the catheter device 712. In this embodiment, the set of treatment 721 can be inserted at the proximal end of the elongated axis 716, and, once located at the treatment site within the renal artery, insertion tube 769 can be retracted to allow control member 768 to develop. As shown in Figure 13B, the control member 768 imparts a force to the tubular support structure 722, thereby deforming it to an expanded helical configuration and developing treatment set 721 to locate the power supply elements 724 against the renal artery wall.
In a particular embodiment, a plurality of electrical dispensing elements 724 are configured as multiple electrodes 724 mounted on a flexible and slightly extensible tube 722 (for example, a tube made of polyethylene block copolymer amide, such as PEBAX ® 5533D , or a material of less hardness). In other embodiments, the tubular support structure 722 can be constructed from other polymers, for example, PET, polyamide, polyimide, PEBAX, polypropylene, or PEEK polymers that provide the desired flexibility. In one embodiment, the tubular support structure 722 has an inner diameter of about 0.03 inches (0.76 mm) and an outer diameter of about 0.04 inches (1.02 mm) and a length of about 4 cm. Electrodes 724 can be cylindrical electrodes and, in one embodiment, can have an inside diameter of about 0.042 inches (1.07 mm), an outside diameter of about 0.046 inches (1.17 mm), and a length about 1 mm. The electrodes 724 can be spaced 3 to 5 mm apart and connected to the tubular support structure 722 using an adhesive. Conductive power supply wires per electrode 725 can extend proximally along and outside the tubular support structure 722.
In various embodiments, the proximal end 722b of the flexible support structure 722 with the electrodes 724 is placed over the distal end of the elongated tubular axis 716 and glued in place. The elongated shaft 716, for example, can include a polyamide tube. In one embodiment, shaft 716 has an inside diameter of about 0.025 inches (0.64 mm) and an outside diameter of about 0.03 inches (0.76 mm) with a length of about 100 cm. In other embodiments, the elongated shaft has an inner diameter of 0.026 inches (0.66 mm) and an outer diameter of 0.028 inches (0.71 mm) and / or other appropriate dimensions. A tubular outer sheath 717 may encircle shaft 716 and abut or overlap proximal end 722a of tubular support structure 722.
Control member 768 for developing treatment set 721 may include, for example, a precast nitinol wire with a helical configuration along the distal region of control member 768. In one embodiment, the control member 768 has a diameter of about 0.015 inches (0.38 mm) and tapers distally to a tip with a diameter of 0.008 inches (0.20 mm). Several different diameters of preformed control members 768 can be made to accommodate different diameters of renal arteries with each having a diameter ranging from about 4.0 mm to about 8.0 mm. Control member 768 may have a memory transformation temperature so that it is slightly above the body temperature (e.g., austenite finish temperature A _f = 42 ° C). Control member 768 is more collapsible at temperatures below A _f , and therefore the helical region can be manually stretched relatively easily. Therefore, the control member 768 can then be inserted directly into the proximal end of the catheter without the need for a rigid insertion tube 769. Since the distal region of the control member 768 is positioned within the tubular support structure 722 surrounded by multiple electrodes 824, raising the temperature of the memory control member 768 above the Af will allow it to assume the helical configuration, deform the tubular support structure 722 and press the electrodes 724 into the arterial wall that allows ablation to occur of the fabric. Once the ablation is complete and the power source 26 is turned off, the surrounding blood flow can cool electrodes 724 and the control member
768 below A _f , allowing control member 768 to become more collapsible for catheter removal. Those skilled in the art will understand that various methods can be used to heat control member 768 to transform its shape.
In the embodiment shown in Figure 13B, the control member 768 is arranged on the optional insertion tube 769. The insertion tube
769 can be made from a variety of materials including interlaced polyimide, PEEK and / or stainless steel and can be sized so that the insertion tube 769 can easily slide through the elongated shaft 716. The pre-control member molded 768 has a total axial dispensing length that is greater than the axial length of the insertion tube 769 so that the guide wire 766 can be advanced and retracted from the proximal end of the catheter device 712.
In the above described embodiments using the flexible tubular support structure 722 and the insertion tube 769 for dispensing and developing the therapeutic set, the guide wire is completely removed from the tubular support structure 722 before the insertion of the pre-control member molded 768, because there is only a single lumen on the elongated catheter axis to receive the guide wire 766 and the control member 768. Other embodiments of treatment devices, however, include an elongated axis with multiple lumens to provide multiple passages in which it maintains a control member, a guidewire, the supply wires, and / or an injectable fluid (for example, contrast, medication, or saline). Therefore, such treatment devices provide an on-wire dispensing and development of a treatment set with an insertable member without the need to completely remove the catheter guidewire.
Figures 14A and 14B, for example, are seen in broken longitudinal cross-section of a treatment device 812 configured in accordance with another embodiment of the present technology. As shown in Figure 14A, treatment device 812 includes a treatment set 821 having a plurality of energy supply elements 824 carried by a relatively flexible tubular support structure 822 that defines a central lumen 829. The tubular support structure 822 includes a distal end 822a which has an axial opening 823 for the passage of a guide wire 866 extending through the central lumen 829. The tubular support structure 822 has a proximal end 822b coupled or attached to the distal end of a tubular axis elongated axis 816. The elongated axis 816 can define a first inner lumen 813 to house guide wire 866. Guide wire 866 exits proximally from a conventional hub / luer socket located, for example <in handle 834. Therefore, the illustrated configuration provides an OTW dispensing from the access point to the treatment site. Insertion of the substantially linear guide wire 866 through the flexible tubular support structure 822 stretches the tubular support structure 822 in order to place the treatment set 821 into a low profile dispensing state for dispensing to the treatment site in the renal artery.
The tubular shaft 816 further includes a second internal lumen 814 to house a control member 868 for the development of the treatment set 821. The tubular shaft 816 can have multiple lumens to hold the shape insertion members, the feed wires, and / or an injectable fluid (for example, contrast, medication, or saline). Figures 14A and 14B show two lumens 813, 814 formed within the integral tubular axis 816. Alternatively, the first and second lumens 813, and 814 can be defined by the separate tubular axes disposed within the external tubular axis 816. Within the second inner lumen 814 of the tubular shaft 816, the control member 868 can be maintained in a substantially linear configuration. Once the treatment device 812 is placed in a desired position within a renal artery, guide wire 866 can be retracted from tubular support structure 822 to the first lumen 813, and control member 868 can be advanced distally in the central lumen 829 of the tubular support structure 822. Because each of the control member 868 and the guide wire 866 has independent lumens in which they reside, guide wire 866 only needs to be retracted sufficiently proximally to exit tubular support structure 822 from treatment set 821 to allow control member 868 to fill support structure 822 and develop treatment set 821. In various embodiments, for example, guide wire 866 it can be retracted 10-20 cm (for example, about 15 cm) to release tubular support structure 822 for the development of treatment set 821.
The control member 868 can have a predefined developed shape, which defines a helical shape, when the constraint is removed to define the developed state of the treatment set 821. The control member 868 can be made of a superelastic nitinol material that has a predefined helical shape. Once located within the support structure 822, the elastic control member 868 can impart a force on the tubular support structure 822 deforming to an expanded helical configuration (for example, as shown in Figure 14B), in order to develop the 821 treatment set and locate the 824 energy delivery elements against the renal artery wall.
In other embodiments of the device with the elongated multi-lumen axis, a tubular support structure can include at least two or more lumens or independent passages. For example, Figures 14C and 14D illustrate a treatment device 912 including a treatment set 921 with a plurality of energy dispensing elements 924. The tubular support structure 922 defines at least two internal lumens. A first lumen 928 can include an axial opening at its distal end and can be adapted to accept a guide wire 966 with a diameter less than about 0.015 inches (0.38 mm) for insertion and retraction of the first lumen 928. Therefore, support structure 922 can be dispensed within a renal artery using an OTW approach as discussed above. In other embodiments, the distal ends 922a of the tubular support structure 922 can end at a rounded distal tip to facilitate the non-traumatic insertion of the treatment device into the renal artery. A second lumen 930 is adapted to hold a development member 968 having a predefined distal region that defines a helical shape in a developed state.
The therapeutic set 921 can be placed in a low profile dispensing state (for example, as shown in Figure 14C) by inserting the guide wire 966 through the first lumen 928 of the support structure 922 for dispensing into a renal artery. The substantially linear guide wire 966 can overcome the predefined helical shape in the flexible development member 968 to maintain the therapeutic set
921 in the dispensing state. The guide wire 966 may be of constant rigidity along its length or, alternatively, may have varying rigidity or flexibility along its length, in order to provide greater rigidity, for example, in the proximal to distal direction. Once the treatment set 921 is positioned at the target treatment site of the renal artery, the treatment set 921 can be developed by retracting the guide wire 966 out of the first lumen 928 of the support structure 922 such that it is usually located inside the elongated axis 916 (for example, within one of a plurality of lumens formed within the elongated axis 916). With the guide wire 966 removed from the support structure 922, the development element 968 can impart a deformation force to the tubular support structure
922 which deforms to the helical shape, in order to develop the therapeutic set 921 (for example, as shown in Figure 14D). Accordingly, guide wire 966 provides a control member for changing the therapeutic set between the dispensing and developed states. Optionally, the first lumen 928 can be used to disperse a fluid, distally, such as saline to cool the energy dispensing element 924 during energy dispensing.
In another embodiment, the development member 968 can be retractable to control the dispensing and development states of treatment set 921 and the guide wire 966 or other stretch stylus can remain in the first lumen 928 during development. In such an arrangement, the guide wire 966 may be sufficiently rigid to place the treatment set 921 in the low profile configuration for dispensing, but flexible enough to allow the development member 968 to confer a force on the set 921 to place the structure support 922 and treatment set 921 in the development configuration.
Figures 15A and 15B illustrate yet another embodiment of a treatment device 1012 that allows a guide wire 1066 to remain at least partially inserted on an elongated axis 1016 during treatment. As shown in Figure 15A, treatment device 1012 includes a single lumen in each of a tubular support structure 1022 and elongated axis 1016. Treatment device 1012 includes a treatment set 1021, having a plurality of treatment elements. energy dispensing 1024 mounted on the tubular support structure 1022 which defines a single central lumen 1029. The support structure 1022 can be covered with an electrical insulator, for example, with a thermal shrinkage tube of a polymer such as PET. The tubular support structure 1022 may also include a distal end 1022a having an axial opening 1023 to allow the guide wire 1066 to protrude beyond distal end 1022a. In some embodiments, the distal end 1022a may end in a rounded distal portion (for example, as shown in the dashed lines). The tubular support structure 1022 can have a proximal end 1022b coupled to the distal end of the elongated axis 1016. The central lumen 1029 of the support structure 1022 can extend through the elongated axis 1016 to receive the guide wire 1066, and allow dispensing OTW. In operation, inserting the substantially linear guide wire 1066 through the tubular support structure 1022 stretches the tubular support structure 1022 in order to place the treatment set 1021 in a low profile dispensing state (for example, as shown in Figure 15A) for dispensing to the treatment site in the renal artery.
The tubular support member 1022 can be made of an elastic or superelastic material, for example, nitinol tubes or polymer-composite tubes including nitinol braided or coiled filaments. In various embodiments, the support structure 1022 can have an internal diameter of less than or equal to about 0.015 inches (0.38 mm), for example, about 0.010 inches (0.25 mm), and a wall thickness less than about 0.005 inches (0.13 mm), for example, about 0.003 inches (0.76 mm). The tubular support structure 1022 can also be made from a material with shape memory, for example, nitinol which has a preformed helical developed shape. As an alternative to using a preformed shape, tubular support structure 1022 may include a pre-molded inner member (e.g., inner tube) or an outer frame structure (not shown), which requests the support structure tubular 1022 for a helical development configuration.
With the guide wire 1066 arranged in the central lumen 1029, the guide wire 1066 provides a stretching force on the tubular support structure 1022 in order to define the low profile or retracted dispensing configuration shown in Figure 15 A. The guide wire 1066 it can be of constant stiffness along its length or, alternatively, it can have variable stiffness or flexibility along its length, in order to provide increased flexibility (for example, in the proximal to distal direction). To develop treatment set 1021, guide wire 1066 can be retracted proximally to elongated axis 1016 in order to remove guide wire 1066 from support structure 1022. As shown in Figure 15B, in the absence of a stretching, the support structure 1022 can develop in a helical configuration. Thus, the 1066 guidewire acts as a control member to change the configuration of the treatment set 1021 between the dispensing and developed states.
Although the embodiments of the catheter or treatment devices, described above, include a treatment set arrangement and a control member for placing the set in a low-profile dispensing state, the catheter devices may further include an outer sheath which can be eliminated and retracted over the treatment set to change its dispensing and developed settings. For example, as shown in Figures 16A and 16B, a treatment device 1212 can be used in conjunction with a dispensing sheath 1291 that forms a sheath around a treatment set 1221 and an elongated axis 1216. As noted, in certain embodiments, it may be advantageous to use a 1290 guide catheter of a particular size, to facilitate the insertion of the treatment device 1221 through the femoral artery. A 1291 dispensing sheath can be used in conjunction with the 1290 guide catheter to gain access to a renal artery and dispense an expandable helical structure contained 1222. Alternatively, the 1291 dispensing sheath can be used in conjunction with a guide wire (not shown) ), as previously described. When used in conjunction with a 1290 guide catheter, an elongated shaft 1216 working length can be from about 40 cm to about 125 cm. If, for example, a 55 cm long guide catheter is used, then this working length can be from about 70 cm to about 80 cm. If a 90 cm long 1290 guide catheter is used, then this working length can be from about 105 cm to about
115 cm. In a representative embodiment, where no 1290 guide catheter is used, then this working length can be from about 40 cm to about 50 cm. In still other embodiments, a variety of other dimensions and / or different arrangements can be used.
In the embodiment shown, the treatment set
1221 includes a helical structure 1222 that can be maintained in a low profile dispensing configuration by the dispensing sheath 1291. Removal of the dispensing sheath 1291 allows the helical support structure 1222 to develop and place the energy dispensing elements 1224 in contact with the renal artery wall. The development of the support structure 1222 can be passive (for example, the structure has a pre-defined developed shape) or active (for example, the development is facilitated by a pre-molded stylus or a traction wire). Regardless of the type of expansion, the helical support structure
1222 can be coupled to a control member (for example, a control wire), which compresses the helical structure before removing or repositioning the treatment device 1212. In certain embodiments, depending on the positioning and number of elements of energy dispensing 1224, helical support structure 1222 can be progressively repositioned within the renal artery to provide a plurality of locations for energy dispensing. Figure 16B shows the embodiment of a catheter with a helical structure 1222 of Figure 16A with the retracted dispensing sheath 1291 that allows the helical structure 22 to expand elastically to its configuration developed in a renal artery. It should be noted that, in Figure 16A, sheath 1291 and treatment set 1221 are designed in large dimensions for clarity.
In a particular embodiment, a sheath can be used to hold the components of the treatment set together, in particular as the device is navigated through the treatment site within the renal artery. Referring to Figures 9A and 9B, treatment set 221 can include a support structure or column 222 of nitinol material with a plurality of electrodes 224 disposed there. The nitinol support structure 222 can be helically wound over an interlaced polyamide inner member 268. In the dispensing state of treatment set 221 of Figure 9B, support structure 222 may be adjacent to inner member 268 along its length . In order to minimize the substantial separation between the support structure 222 and the inner member 268 when the treatment set 221 is bent or bent during dispensing, a sheath can be placed on the treatment set 221. Sheaths can also be developed with the treatment sets described above with reference to Figures 10A11B and other suitable treatment sets described herein.
The sheath can also be used to support a treatment set, in its dispensing configuration, even when the treatment set has a forming insert member placed in the lumen of the flexible tubular support structure. For example, with reference to Figures 13A and 13B, a sheath (not shown) can be arranged on the support structure 722. After the retraction of the guide wire 766 and the insertion of a control member 768 in the lumen of the support structure 722 , the sheath prevents the treatment set 721 from developing to its full transverse dimension. To allow the 721 assembly to fully develop to the desired helical configuration, the sheath can be retracted. Alternatively or additionally, the tubular support structure 722 is preferably sufficiently rigid to allow guidable insertion into the treatment site without the use of the molding member or stylus, but flexible enough to take the form of the inserted control member 768, once that the sheath is removed. In addition, alternatively or
100 additionally, the insertable control member 768 can be sheathed to minimize or eliminate premature development of the treatment set after insertion of the control member. Therefore, once the sheath is removed, the insert 768 can expand to its full development configuration.
In still other embodiments, with reference to Figures 13A and 13B, stylus 768 is positioned at the distal end of treatment set 721 of device 712 when the device is at the treatment site (for example, inside the renal artery) . In this embodiment, for example, stylus 768 is sheathed in a low profile configuration during insertion by insertion tube 769. Insertion tube 769 is removed from preformed stylus 768 after insertion, allowing stylus 768 assume its helical shape, as described above. In this embodiment, stylus 768 can provide a structure and a desired level of stiffness for device 712 to help guide and position device 712 during dispensing and then give it the desired helical arrangement during development.
In some over-the-wire embodiments of the treatment catheter device described above, the guide wire is described as extending within the elongated axis of the catheter from at least the distal end of the treatment set to a proximal location of the set of handle. To disengage the guide wire catheter, it is necessary to retract the total length of the proximal guide wire from the access site. Thus, the axial length of the guide wire may be greater than that of the elongated axis of the catheter and its distal treatment set. In order to provide operation and manipulation of a shorter guidewire, and in particular to minimize the retraction distance to disengage the guidewire catheter, it may be desirable to have a treatment catheter device that provides a quick change configuration. The quick-change examples described below with reference to
101
Figures 17A-17E can also be used with any of the treatment devices described here, which use a guide wire and OTW dispensing techniques.
Figure 17A, for example, is a broken side view in partial section of a distal portion of a treatment device 1410 with a quick-change configuration in accordance with an embodiment of the technology. Treatment device 1410 includes treatment set 1421 helically arranged around a tubular control member 1468 that defines an internal lumen for passage along a guide wire 1466. Tubular control member 1468 extends proximally within of the elongated axis 1416 of the treatment device 1410, which is shown at least partially arranged within a guide catheter 1490. In order to provide a quick-change configuration in which the guide wire 1466 extends, at least partially in parallel and extremly to the elongated axis 1416, the tubular control member 1468 includes an opening 1470 proximal to the treatment set 1421, but distal from a handle assembly (not shown) for the exit of the guide wire 1466. The elongated axis 1416 also includes preferably an opening 1472 for the exit of the guide wire 1466 and passage for the catheter 1490. Since the guide wire 1466 does not need to extend proximally through the elongated axis 1416 for the handle assembly (not shown), its total length can be reduced.
Figures 17B and 17C illustrate another embodiment of a treatment device 1600 with a quick-change configuration in accordance with another embodiment of the technology. More specifically, Figure 17B is a broken side view in partial section of a distal portion of the treatment device 1600, in a dispensing state, and Figure 17C is a broken side view of the treatment device 1600 in a developed state. In relation to figures 17B and
102
17C together, treatment device 1600 includes a treatment set 1621 having a tubular support structure 1622, with a plurality of energy dispensing elements 1624 arranged around support structure 1622. Support structure 1622 extends proximally within at least a portion of the elongated axis 1616 of the treatment device 1600. Energial feed wires 625 preferably extend within the tubular support structure 1622 to supply power from an external generator source (not shown) for each of the energy dispensing elements 1624. The tubular support structure 1622 extends distally over a spiral or helical tubular member 1680 and terminates along an outer surface of the tubular element 1680 and is preferably connected to a distal region 1680a of tubular member 1680.
Tubular member 1680 provides treatment set 1621 with an inner member disposed within the helix defined by support structure 1622 which can be used to control the distal region of support structure 1622 to change support structure 1622 of the treatment set 1621 between a dispensing configuration and a developed one. The treatment device 1600 further includes a control member 1668 coupled to a proximal region of the tubular member 1680 to push distally and proximally pull the inner member 1680, so as to move, respectively, the distal end 1622a of the tubular support structure 1622 in the distal and proximal directions in relation to the distal end of the axis 1616. Distal movement of the distal end of the support structure 1622a 1622 elongates an axial length of the support structure in a helical shape 1622 and places the treatment set 1621 in the dispensing configuration (such as seen in Figure 17B). Likewise, the proximal movement of the distal end 1622a of the support structure 1622 shortens an axial length of the shaped support structure
103 helical 1622 to place treatment set 1621 in the developed configuration shown in Figure 17C. In one embodiment, the control member 1668 can be configured as a symmetrical rod. For example, the symmetrical rod may extend axially within the elongated axis 1616 and, in some embodiments, within an independent lumen on the elongated axis 1616 separated from a lumen carrying the power supply wires 1625 to the treatment set 1621.
The inner tubular member 1680 defines an inner lumen for the passage of a guide wire 1666. Therefore, the inner tubular member 1680 includes an axial opening with a distal end region 1680a for the passage of the guide wire 1666. The proximal end region 1680b of the inner tubular member 1680 is configured for a proximal passage and exit of the guide wire 1666. The proximal region 1680b can end, for example, in an elongated oblique opening 1682 for exit of the guide wire 1666. In some embodiments, the region proximal 1680b of the inner member 1680 can be affixed to the distal end of the symmetrical member 1668 in such a way that the symmetrical member 1668 can control the axial distance between the exit of the guide wire 1682 and the elongated axis 1668. In addition, in some embodiments , the distal end of the symmetrical member 1668 may include an angled or tapered end to increase the cross-sectional area of the symmetrical member 1668 p for connection to the inner tubular member 1680. Because the arrangement of the inner element 1680 and the symmetrical member 1668 maintains the outlet opening of the guide wire external to the elongated axis 1616, the arrangement provides a quick-change configuration.
In particular, the outlet opening of the guide wire 1682 provides that the guide wire 1666 can extend in parallel and external to the elongated axis 1616. Thus, manipulation of the guide wire 1666 does not require that the guide wire 1666 extends proximally within the entire length of the elongated axis 1616 and beyond, for example, through a handle assembly. Per
Therefore, in some embodiments, the length of the guide wire 1666 may be reduced in length, for example, about 180 cm. In addition, to the extent that it may be desired to disengage treatment set 1621 from guide wire 1666, guide wire 1666 only needs to be retracted in an amount sufficient to proximally retract the distal end of the guide wire from the outlet opening 1682 guide wire.
In one embodiment, the elongated axis 1616 is configured to engage the proximal region of the inner tubular member 1680 in the developed configuration of treatment set 1621. More specifically, the distal region of the elongated axis 1616 is formed to form a coupling of fit with the outer portion of the proximal end 1680b of the tubular member 1680 in the developed configuration. As shown in Figure 17C, the symmetrical member 1668 is fully retracted in order to develop the treatment set 1621. The retraction of the symmetrical member 1668 locates the proximal end 1680b adjacent to the distal end of the elongated axis 1616. The distal end of the elongated axis 1616 preferably includes a taper so that the inner lumen for the power supply wires 1625 and the linear portion of the tubular support structure 1622 extend distally beyond the inner lumen housing the symmetrical member 1668. The taper (for example, the trimmed or oblique notch) at the distal end of the elongated axis 1616 is dimensioned and shaped to receive the proximal end 1680b of the inner tubular member when located adjacent to the elongated axis 1616.
In one embodiment, treatment set 1621 may have a maximum dispensing length ranging from, for example, about 8 mm to about 50 mm, for example, about 15 mm to about 50 mm. In a developed configuration, the treatment set 1621 can have a maximum axial length of, for example, about 45 mm. The tubular member 1680 can have an axial length that
105 ranges from about 2-50 cm with an opening 1682 having an axial length of, for example, about 2-8 mm. Symmetrical rod 1668 can be configured to change the axial distance between the distal end of the elongated axis 1616 and the opening 1682 of the inner tubular member 1680 over a distance of, for example, about 1 mm to 30 mm. The elongated axis 1616 and the guide wire 1666 can extend parallel to each other within a surrounding guide catheter 1690. Catheter device 1612 can be configured such that opening 1682 is located inside or outside guide catheter 1690 .
An alternative embodiment of the treatment device 1710 is shown in Figure 17D. In this embodiment, treatment set 1721 includes a tubular support structure 1722 that has a proximal portion, which extends proximally to the elongated axis to carry the power supply wires to the 1724 energy dispensing elements arranged on the structure of support 1722. Extending parallel to the proximal portion of the tubular support structure 1722 is a control member 1768, which includes a symmetrical rod. Also preferably, extending parallel to the symmetrical control member 1768 is a tubular member 1780 that defines an internal lumen for the passage of a guide wire 1766. Each of the distal end region 1722a of the support structure 1722 and the member of symmetrical rod 1768 is preferably attached to the tubular member 1780 so that the axial movement of the symmetrical member 1768 moves the distal end of the tubular support structure 1722 and the tubular member 1780 along the guide wire 1766. The tubular support structure 1722 is , preferably helically wound around the tubular member 1780 such that the tubular member 1780 is internal to the helix defined by the support member 1722. The distal and proximal movement of the distal region 1722a respectively extends and reduces the axial length of the support structure tubular helical
106
1722 to place the treatment set 1721 in the dispensing and developed configurations. Proximal to the treatment set 1721, distal from the handle assembly along the tubular member 1780 is an opening 1782 to provide a quick-change configuration.
Since the symmetrical member 1768 and the distal end 1722a of the tubular support structure are attached to the tubular member 1780, the tubular support structure 1722 cannot be rotated around the tubular member 1780 and its axial opening through which the guide wire goes by. Consequently, to provide a distal end 1722a, which rotates around the guide wire lumen of the member 1780, the symmetrical member 1768 and the distal end 1722a of the tubular support member 1722a are coupled to, but separable from, the tubular member 1780 as seen for example, in Figure 17E. More specifically, the tubular member 1780 is preferably detachable, or independently rotatable in relation to the tubular support structure 1722 and the symmetrical member 1768. In this way, a rotating distal region of the treatment set 1721 can rotate around the guide wire 1766 In addition, since the distal region of treatment set 1721 can rotate around tubular member 1780, the output of the proximal guide wire 1782 can be fixed relative to treatment set 1721 so that the quick change setting does not interfere with the rotation of the treatment set.
In the embodiment shown in Figure 17E, the sleeve 1785 is provided to which the distal end of the tubular support structure 1722 and the symmetrical member 1768 are attached. The glove 1785 also defines an internal passage for slidingly receiving the member 1780. The glove 1785 provides a set of the treatment set that axially slides and rotates over the tubular member 1780. The configuration also provides the rotation of the support structure 1722 and the symmetrical member 1768 of the assembly in relation to the tubular member 1780, maintaining the shape, preferably, generally helical without the support structure 1722 enclosing around the tubular member 1780 and
107 losing the desired shape / configuration when handling the treatment set inside the vessel.
IV. Applying energy to the fabric through the energy dispensing element
Referring again to figure 1, energy generator 26 can provide a continuous or pulsed RF electric field to energy dispensing elements 24. Although continuous dispensing of RF energy is desirable, the application of RF energy to pulses can allow for applying relatively higher energy levels (for example, greater potency), for more or less long total duration times, and / or improving controlled intravascular renal neuromodulation therapy. Pulsed energy can also allow the use of a smaller electrode.
Although many of the embodiments described here refer to electrical systems configured for dispensing RF energy, it is contemplated that the desired treatment can be carried out by other means, for example, by coherent or incoherent light; direct thermal modification (for example, with a heated or cooled fluid or resistive heating element or cryogenic applicator), microwave, ultrasound (including focused high intensity ultrasound); laser diode, radiation, a tissue heating fluid, and / or a cryogenic refrigerant.
As previously discussed, the energy supply can be monitored and controlled through data collected with one or more sensors, such as temperature sensors (for example, thermocouples, thermistors, etc.), impedance sensors, pressure sensors, optical sensors, flow sensors, chemical sensors, etc., which can be incorporated in or on the energy dispensing elements 24, the support structure 22, and / or in / on the adjacent areas on the distal portion 20. A sensor can be incorporated into the power supply element (s) 24 in a way that specifies whether the sensor (s) is (are) in
108 contact with the tissue at the treatment site and / or is facing the blood flow. The ability to specify the position of the sensor in relation to the flow of blood and tissue is highly significant, since a temperature gradient through the electrode from the side facing the blood flow to the side in contact with the vessel wall it can be up to about 15 ° C. Significant gradients through the electrode in other sensing data (eg flow, pressure, impedance, etc.) are also expected.
The sensor (s) can, for example, be incorporated into the side of one or more energy dispensing elements 24 that contact the vessel wall at the treatment site during the dispensing of energy and power or can be incorporated into the opposite side of one or more energy dispensing elements 24 that are directed towards the blood flow during energy dispensing, and / or can be incorporated (s) within certain regions of the energy dispensing elements 24 (for example, distal, proximal, quadrants, etc.) In some embodiments, several sensors may be provided at various positions along the electrode or element arrangement energy and / or blood flow. For example, a plurality of circumferentially and / or longitudinally spaced sensors can be provided. In one embodiment, a first sensor can contact the vessel wall during treatment, and a second sensor can face the blood flow.
In addition, or alternatively, several microsensors can be used to acquire the data corresponding to the energy dispensing elements 24, the vessel wall and / or the blood flowing through the energy dispensing elements 24. For example, micro thermocouples and / or impedance sensors can be implemented to acquire the data along the energy dispensing elements of 24 or other parts of the treatment device. The sensor data can be acquired or monitored before, simultaneously with, or after the
109 energy dispensing or between energy pulses, when applicable. The monitored data can be used in a closed loop to better control therapy, for example, to determine whether to continue or stop treatment, and this can facilitate controlled dispensing of increased or reduced potency or longer duration therapy. long or shorter.
V. Blood flow around the energy dispensing elements
The non-target tissue may be protected by a blood flow inside the respective renal artery that serves as a heat sink by conduction and / or by convection that carries excess thermal energy. For example, with reference to Figures 1 and 18 together, since the blood flow is not blocked by the elongated axis 16, the helical shaped therapeutic set 21 and the energy dispensing elements 24 it carries, the natural circulation of the blood in the respective renal artery serves to remove excess thermal energy from the non-target tissue and the energy dispensing element. The removal of excess thermal energy through the blood flow also allows for higher power treatments, in which more power can be delivered to the target tissue, as the thermal energy is transported out of the electrode and non-target tissue. In this way, thermal energy delivered intravascularly, heats the target neural fibers located near the vessel wall, to modulate the target neural fibers, while the blood flow inside the respective renal artery protects the non-target tissue of the vessel wall. excessive or undesirable thermal damage.
It may also be desirable to provide enhanced cooling, inducing additional native blood flow through the energy dispensing elements 24. For example, techniques and / or technologies can be applied by the clinician to increase perfusion through the renal artery, or to the energy supply elements 24 themselves. These
110 techniques include positioning partial occlusion elements (e.g., balloons) within upstream vascular bodies, such as the aorta, or within a portion of the renal artery to improve flow through the energy dispensing element.
Figure 18, for example, illustrates the hypothetical blood flow in a renal artery. The blood flow (F) is thought to be laminar, for example, to display a flow gradient such that in an area closer to the center of the artery, for example, area 2214, the blood flow F can be faster in relation to areas closer to the renal artery wall 55, for example, areas 2215. Thus, the blood flow F closest to the location of the energy dispensing elements 24 is relatively slow. Because the cooling of the energy dispensing elements 24 is mediated by the blood flow, improved cooling can be achieved by redirecting the blood flow F in the renal artery, so that the blood flowing around the energy dispensing elements 24 is relatively faster.
19A illustrates an embodiment in which a fluid redirecting element 2220 is positioned within the center of the renal artery. Thus, the flowing blood, represented by arrows 2216, including the faster flowing blood, is redirected to the energy dispensing elements 24. The fluid redirecting element can be of any biocompatible material, such as a polymer, which is positioned to stimulate blood flow towards the energy dispensing elements 24 carried by a 3422 mesh structure.
Referring to Figures 19A and 19B together, the fluid redirection element 2220 may extend from the distal end region 20 of the elongated axis 16, generally along the geometric axis AA of the elongated axis 16. For embodiments where a guide wire (not shown) is used, the fluid redirection element
111
2220 may include an integral passage (not shown) of an internal member dimensioned and shaped to accommodate the guide wire. In addition, in some embodiments, an axial length of the fluid redirection element 2220 can be at least 25%, or at least 50%, or at least 75% of an axial length of the 2220 mesh structure in the expanded configuration . In any case, in order to maximize the redirected blood flow, the fluid redirection element 2220 may extend at least sufficiently within the 3422 mesh structure, so that an imaginary geometric axis through the dispensing elements energy 24 and orthogonal to the geometric axis AA intersects fluid redirection element 2220. The diameter 2228 of fluid redirection element 2220 can be expandable in such a way that, in its unexpanded state it is generally compatible with insertion, repositioning and the removal of the 3422 mesh structure and in its expanded state is configured to redirect blood flow to the areas closest to the renal artery wall, for example, areas 2215. As shown in Figure 19B, in a retracted configuration, the mesh structure 3422 may conform to the shape of the fluid redirection element 2220. Diameter 2228 may be slightly greater than, approximately equal to, or less than an elongated shaft diameter 16. In one embodiment, the diameter 2228 may be less than about 2.18 millimeters.
In addition, or as an alternative, the passive use of blood flow, as a heat sink, active cooling can be provided to remove excess thermal energy and protect non-target tissues. For example, an infused thermal fluid can be injected, infused, or otherwise dispensed into the vessel in an open circuit system. Infused thermal fluids used for active cooling can, for example, include saline solution (temperature
112 or cold) or some other biocompatible fluid. The thermal fluid infused (s) can, for example, be introduced by means of the treatment device 12 by means of one or more infusion lumens and / or ports. When introduced into the bloodstream, the thermal fluid infused (s) can, for example, be introduced via a guide catheter into a location upstream of the 24 or elsewhere in relation to the fabric for which protection is required. The dispensing of a thermal fluid infused in the vicinity of the treatment site (through an open circuit system and / or through a closed circuit system) may, for example, allow the application of the increased / high power treatment, it can allow the maintenance of a lower temperature on the vessel wall during energy dispensing, it can facilitate the creation of deeper or larger lesions, it can facilitate the reduction of treatment time, it can allow the use of a smaller electrode size, or a combination of these.
As a result, treatment devices configured in accordance with embodiments of the technology may include features for an open circuit cooling system, such as a lumen in fluid communication with an infusion source and a pumping mechanism (e.g. manual injection or a motorized pump) for injection or infusion of saline solution or some other infused with biocompatible thermal fluid from outside the patient, through the elongated axis 16 and towards the energy dispensing elements 24 into the patient's bloodstream during energy dispensing. In addition, the distal end region 20 of the elongated axis 16 may include one or more ports for injection or infusion of saline directly at the treatment site.
SAW. System Use
A. Intravascular dispensing, deflection, and placement of the delivery device
113 treatment
As mentioned earlier, any of the embodiments of the treatment devices described herein can be dispensed using OTW or RX techniques. When dispensed in this way, the elongated axis 16 includes a passage or passage accommodating a lumen of a guide wire. Alternatively, any of the treatment devices 12 described herein can be developed using a conventional guide catheter or pre-curved renal guide catheter (for example, as shown in Figures 3A and 3B). When a guide catheter is used, the femoral artery is exposed and cannulated at the base of the femoral triangle, using conventional techniques. In an exemplary approach, a guidewire is inserted through the access site and passed using the image orientation through the femoral artery, the iliac artery and the aorta, and any left or right renal artery. A guide catheter can be passed over the guide wire into the accessed renal artery. The guide wire is then removed. Alternatively, the renal guide catheter, which is specifically formed and configured to access a renal artery, can be used to avoid using a guide wire. Alternatively, the treatment device can be routed from the femoral artery to the renal artery using angiographic guidance and without the need for a guide catheter.
When a guide catheter is used, at least three dispensing approaches can be implemented. In one approach, one or more of the aforementioned dispensing techniques can be used to position a guide catheter within the renal artery distal only from the entrance to the renal artery. The treatment device is then routed through the guide catheter into the renal artery. Once the treatment device is correctly positioned inside the renal artery, the guide catheter is retracted from the renal artery to the abdominal aorta. In this approach, the guide catheter must be dimensioned and configured to
114 accommodate the passage of the treatment device. For example, a 6 French guide catheter can be used.
In a second approach, a first guide catheter is placed at the entrance to the renal artery (with or without a guide wire). A second guide catheter (also called a dispensing sheath) is passed through the first guide catheter (with or without the help of a guide wire) in the renal artery. The treatment device is then routed through the second guide catheter in the renal artery. Once the treatment device is correctly positioned inside the renal artery, the second guide catheter is retracted, leaving the first guide catheter at the entrance to the renal artery. In this approach, the first and second guide catheters must be sized and configured to accommodate the passage of the second guide catheter into the first guide catheter (that is, the inner diameter of the first guide catheter must be larger than the outer diameter of the second guide catheter ). For example, an 8 French guide catheter can be used for the first guide catheter, and a 5 French guide catheter can be used for the second guide catheter.
In a third approach, a renal guide catheter is placed inside the abdominal aorta, immediately proximal to the entrance of the renal artery. The treatment device 12, as described herein, is passed through the guide catheter and into the accessed renal artery. The elongated axis passes non-traumatically through the guide catheter in response to forces applied to the elongated axis 16 through the handle assembly 34.
B. Applied Energy Control
1. Overview
Referring again to Figure 1, a treatment administered using system 10 constitutes energy dispensing through the energy dispensing elements or electrodes 24 to the inner wall of a renal artery for a predetermined period of time (for example, 120 seconds ). Multiple treatments (eg 4-6) can be
115 administered in both the left and right renal arteries to achieve the desired coverage. A technical goal of treatment may be, for example, heat the tissue to a desired depth (for example, at least about 3 mm) at a temperature that would damage to a nerve (e.g., about 65 ⁰ C). A clinical objective of the procedure is typically for neuromodular (injury, for example) a sufficient number of renal nerves (efferent or afferent nerves, of the sympathetic renal plexus) to cause a reduction in sympathetic tone. If the technical goal of a treatment is met (for example, the tissue is heated to about 65 ° C to a depth of about 3 mm), the likelihood of an injury to the renal nerve tissue is high. The greater the number of technically successful treatments, the greater the likelihood of modulating a sufficient proportion of renal nerves and thus the greater the likelihood of clinical success.
During treatment, there may be a number of conditions that are indicative of a possibility that the treatment may not be successful. In certain embodiments, based on indications of these states, the operation of the system 10 can be interrupted or modified. For example, certain indications may result in the interruption of energy supply and an appropriate message may be displayed, such as on the display 33. Factors that may result in a message on the display and / or the termination or modification of a treatment protocol include , but are not limited to, indications of an impedance, a blood flow, and / or measurement or temperature variation that is outside of accepted and expected limits and / or ranges that can be predetermined or calculated. A message can indicate information, such as a type of patient condition (for example, an abnormal condition of the patient), the type and / or value of the parameter that is outside an acceptable or expected limit, an indication of the suggested action by a clinician, or an indication that dispensing
116 energy was interrupted. However, if no unexpected or aberrant measurements are observed, energy can continue to be delivered at the target site, according to a profile scheduled for a specified period of time, resulting in a complete treatment. After a treatment is completed, the energy dispensing is stopped and a message indicating the completion of the treatment can be displayed.
However, a treatment can be completed without initiating an indication of an abnormal condition of the patient, and yet an event or combination of events can occur that alters (for example, decreases) the likelihood of a technically successful treatment. For example, an electrode that is dispensing energy may move or inadvertently be placed in sufficient contact between the electrode and the wall of a renal artery, thus resulting in insufficient injury depth or temperature. Therefore, even when treatment is terminated without an indication of the patient's abnormal condition, it can be difficult to assess the technical success of the treatment. Likewise, to the extent that indications of the patient's abnormal conditions can be communicated by system 10, it can be difficult to understand the causes of the patient's abnormal conditions (such as temperature and / or impedance values that are outside the expected ranges ).
As mentioned above, one or more evaluation / return algorithms 31 can be provided and run on a component based on the system 10 processor, such as one or more components provided with generator 26. In such implementations, the one or more evaluation / return algorithms 31 may be able to provide a user with a significant return that can be used in the evaluation of a given treatment and / or that can be used in learning the importance of certain types of abnormal patient conditions and how to reduce the occurrence of such conditions. For example, if a
117 a certain parameter (for example, an impedance or temperature value) causes or indicates that the treatment did not proceed as expected and (in some cases), may have resulted in a technically unsuccessful treatment, system 10 can provide return (for example, through display 33) to alert the clinician. The alert for the clinician can range from a simple unsuccessful treatment notification to a recommendation that a specific treatment parameter (for example, the impedance value (s) during treatment, the placement of energy delivery elements 24 within the patient, etc.) is modified in a later treatment. System 10 can therefore learn from completed treatment cycles and modify subsequent treatment parameters based on learning how to improve effectiveness. Non-exhaustive examples of measurements from one or more evaluation / return algorithms 31 may consider including measurements related to temperature change (s) over a specified period of time, a maximum temperature, a maximum average temperature, a temperature minimum, the temperature at a predetermined or calculated time in relation to a predetermined or calculated temperature, an average temperature over a specified time, a maximum blood flow, a minimum blood flow, a blood flow at a predetermined time, or calculated in relation to a predetermined or calculated blood flow, an average blood flow over time, a maximum impedance, a minimum impedance, an impedance to a predetermined or calculated time in relation to a predetermined or calculated impedance, a change in impedance over a specified period of time, or an impedance change in relation to a m udance of temperature over a specified period of time. Measurements can be taken at one or more predetermined times, time intervals, calculated times and / or times when or in relation to when a measured event occurs.
118
It will be appreciated that the preceding list merely provides a series of examples of different measurements, and other appropriate measurements can be used.
2. Applied Energy Control
With the treatments described here for target tissue dispensing therapy, it can be beneficial for the energy to be delivered to the target neural structures in a controlled manner. Controlled energy dispensing will allow the heat treatment zone to extend into the renal fascia, reducing the delivery of unwanted energy or thermal effects to the vessel wall. Controlled energy dispensing can also result in more consistent, predictable and effective global treatment. Therefore, generator 26 desirably includes a processor including a memory component with instructions for executing an algorithm 30 (see Figure 1), for controlling the energy and power delivery to the energy dispensing device. Algorithm 30, a representative embodiment of which is represented in Figure 3, can be implemented as a conventional computer program, to be executed by a processor coupled to generator 26. A clinician using the step-by-step instructions can also implement algorithm 30 manually.
Operational parameters monitored according to the algorithm may include, for example, temperature, time, impedance, power, blood flow, flow speed, volumetric flow rate, blood pressure, heart rate, etc. . Discrete temperature values can be used to trigger changes in power or energy supply. For example, high temperature values (for example, 85 ° C) may indicate tissue desiccation, in which case the algorithm may decrease or interrupt the energy and power delivery to avoid undesirable thermal effects on the target or non-target tissue. Additional time or alternatively can be used to prevent unwanted thermal change
119 of the non-target tissue. For each treatment, a defined time (for example, 2 minutes) is checked to prevent indefinite power supply.
Impedance can be used to measure changes in tissue. Impedance indicates the electrical property of the treatment site. In thermal inductive embodiments, when an electric field is applied to the treatment site, the impedance will decrease as the tissue cells become less resistant to the current flow. If too much energy is applied, tissue desiccation or coagulation can occur near the electrode, which would increase impedance as cells lose water retention and / or the electrode surface area decreases (for example, through clot accumulation ). Thus, an increase in the impedance of the tissue can be indicative or predictive of undesirable thermal alteration of the target or non-target tissue. In other embodiments, the impedance value can be used to assess the contact of the energy supply element (s) 24 with the tissue. For multiple electrode configurations (for example, when the power supply element (s) 24 includes (in) two or more electrodes) a relatively small difference between the impedance values of the individual electrodes can be indicative of a good contact with the fabric. For a single electrode configuration, a stable value can be indicative of good contact. In this way, the impedance information of one or more electrodes can be provided to a downstream monitor, which in turn can provide an indication to a clinician related to the contact quality of the dispensing element (s) energy 24 with the tissue.
Additionally or in an alternative form, potency is an effective parameter to control and control the delivery of therapy. Power is a function of voltage and current. Algorithm 30 can customize the voltage and / or current to achieve a desired power.
The derivatives of the above mentioned parameters (for example,
120 change rates) can also be used to cause changes in power or energy supply. For example, the rate of change in temperature can be controlled so that power output is reduced in the event that a sudden rise in temperature is detected.
As seen in Figure 20, when a clinician initiates treatment (for example, using the pedal 32 shown in Figure 1), the control algorithm 30 includes instructions for the generator 26 to gradually adjust its power output to a first level of Pi power (for example, 5 watts) for a first time period ti (for example, 15 seconds). The increase in power during the first period of time is generally linear. As a result, generator 26 increases its power output at a generally constant rate P / t. Alternatively, the power increase can be non-linear (for example, exponential or parabolic) with a variable rate of increase. Once Pi and ti are reached, the algorithm can keep Pi until a new time t ₂ for a predetermined period of time t ₂ - (for example, 3 seconds). At t ₂ , the power is increased by a predetermined increment (for example, 1 watt) to P ₂ over a predetermined period of time, t ₃ - t ₂ (for example, 1 second). This power ramp in predetermined increments of about 1 watt for predetermined periods of time, can continue until a maximum power Pmax is reached, or some other condition is met. In one embodiment, Pmax is 8 watts. In another embodiment, Pmax is 10 watts. Optionally, the power can be maintained at the maximum power Pmax for a desired period of time, or up to the desired total treatment time (for example, up to about 120 seconds).
In Figure 20, algorithm 30 illustratively includes a power control algorithm. However, it should be understood that the algorithm 30 in an alternative form may include an algorithm for controlling
121 temperature. For example, the power can be increased gradually until a desired temperature (or temperatures) is obtained over a desired period (or duration). In another embodiment, a combination of feed control and temperature control algorithms can be provided.
As discussed, algorithm 30 includes monitoring certain operating parameters (for example, temperature, time, impedance, power, flow speed, volumetric flow, blood pressure, heart rate, etc.). Operating parameters can be monitored continuously or periodically. The algorithm 30 checks the monitored parameters against the predetermined parameter profiles to determine whether the parameters individually or in combination are within the ranges defined by the predetermined parameter profiles. If the monitored parameters are within the ranges defined by the predetermined parameter profiles, then the treatment can continue in the production of controlled power. If the monitored parameters are outside the ranges defined by the predetermined parameter profiles, algorithm 30 adjusts the output of the controlled power accordingly. For example, if the target temperature (for example, 65 ° C) is reached, then the energy supply is kept constant until the total treatment time (for example, 120 seconds) expires. If a first temperature threshold (for example, 70 ° C) is reached or exceeded, then power is reduced, in predetermined increments (for example, 0.5 watts, 1.0 watts, etc.) until a target temperature is reached. If a second power threshold (for example, 85 ° C) is reached or exceeded, thereby indicating an undesirable condition, then the power dispensing can be terminated. The system can be equipped with various audible and visual alarms to alert the operator to the right conditions.
The following is a non-exhaustive list of events in which algorithm 30 can adjust and / or stop / discontinue power production.
122 commanded:
(1) The measured temperature exceeds a maximum temperature limit (for example, from about 70 to about 85 ° C).
(2) The average temperature derived from the measured temperature exceeds an average temperature threshold (for example, about 65 ° C).
(3) The measured rate of change in temperature exceeds a rate of change threshold.
(4) The temperature rise over a period of time is less than a minimum threshold for temperature change while generator 26 has non-zero production. Poor contact between the energy supply element (s) 24 and the arterial wall can cause such a condition.
(5) The measured impedance exceeds or is outside an impedance threshold (for example, <20 Ohms or> 500 Ohms).
(6) The measured impedance exceeds a relative threshold (for example, the impedance decreases from an initial or baseline value and then increases above that baseline value) (7) The measured power exceeds a power threshold (for example,> 8 Watts or> 10 Watts).
(8) The measured duration of the energy supply exceeds a time threshold (for example,> 120 seconds).
Advantageously, the magnitude of the maximum power delivered during the treatment of renal neuromodulation according to the present technology can be relatively low (for example, less than about 15 watts, less than about 10 watts, less than about 8 watts, etc. ), as compared, for example, with the power levels used in electrophysiology treatments to achieve cardiac tissue ablation (for example, power levels greater than about 15 watts, greater than about 30 watts, etc.). ) Since the power levels relatively
123 lows can be used to achieve such renal neuromodulation, the flow rate and / or the total injection volume of intravascular infused needed to keep the energy and / or non-target tissue delivery element at or below a desired temperature during power dispensation (e.g., at or below about 50 ⁰ C, for example, or at or below about 45 ° C) can also be relatively lower than would be needed for higher levels of used power, for example, in electrophysiology treatments (for example, power levels greater than about 15 Watts). In embodiments in which active cooling is used, the relative reduction in flow and / or the total volume of intravascular infusion of the infused can advantageously facilitate the use of intravascular infusion in high-risk patient groups that would be contraindicated where higher levels of potency and thus correspondingly higher rates / volumes of infused used (eg, patients with heart disease, heart failure, renal failure and / or diabetes mellitus).
C. Technical evaluation of a treatment
Fig. 21 is a block diagram of a treatment algorithm 2180 configured in accordance with an embodiment of the present technology. The 2180 algorithm is configured to evaluate the events in a treatment, determine the probability of technical success of the treatment and display a message of agreement to provide feedback to the system 10 operator (or other appropriate treatment system). If the treatment is determined to have a predetermined probability of sub-optimal technical success, a message indicating that the treatment should not proceed as can be seen. Alternative implementations can classify a treatment in various ranges of success probabilities, such as the probability of success on a scale of 1 to 5. Similarly, in certain implementations, the 2180 algorithm can assess whether a treatment belongs to a high probability of success. category of
124 success, a very low probability of success category, or somewhere in between.
The variables that characterize a treatment and that can be used by the 2180 algorithm to evaluate a treatment include, but are not limited to: the time (that is, the duration of the treatment), the potency, the temperature change, the maximum temperature, average temperature, blood flow, standard deviation of temperature or impedance, change in impedance, or combinations of these or other variables. For example, some or all of the variables can be provided for the 2180 algorithm as 2182 treatment data. In this generalized representation of a 2180 algorithm, the 2180 treatment data can be evaluated based on a cascade or a series of different categories or degrees criteria 2184. Favorable evaluation of treatment data 2182, given one of criteria 2184 may result in the display (block 2186) of a message indicating that the treatment was successful or acceptable. Failure of treatment data 2182 to be considered acceptable in view of criterion 2184 may result in treatment data falling to the next evaluation criterion 2184.
In the represented embodiment, the failure of the treatment data to be considered acceptable, considering all the criteria 2184 can result in an additional evaluation to be carried out, such as the analysis and scoring step described 2188. The exit from the analysis and scoring (for example, a 2190 score) can be assessed (block 2192). Based on this assessment 2192, the treatment can be considered acceptable, and the corresponding screen displayed (block 2186), or not acceptable, and a screen 2194 indicating that the treatment did not proceed as expected. In still other embodiments, the 2180 algorithm may include an automatic action (for example, an automatic reduction in the level of power supplied to the energy source), in response to an indication that the
125 treatment did not proceed as expected.
Although Figure 21 represents a generalized and simplified implementation of a treatment evaluation algorithm, Figure 22 shows a more detailed example of an embodiment of a treatment evaluation algorithm of 2200. The treatment evaluation algorithm 2200 can be calculated after the completion of a treatment (block 2202), which can be 120 seconds in length (as illustrated) or some other suitable period of time, and using derived data and / or measurements during the course of treatment.
In the embodiment shown, it is considered likely that the highest probability of a treatment less than ideal occurs when an electrode is not in consistent contact with the vessel wall. As a result, decision blocks 2204, 2206, 2208, and 2210 of the flowchart are associated with different criteria and filter out treatments that appear to have one or more criteria outside a predetermined range (that is, they do not have a high probability of success) based on data observed or measured 2202 over the course of complete treatment. In the represented embodiment, these treatments are not traced out in decision blocks 2204, 2206, 2208, 2210 and introduce a linear discriminant analysis (LDA) 2212 to better evaluate the treatment. In other embodiments, other appropriate analyzes may be performed instead of the represented LDA. Values attributed to each stage (that is, the evaluation by a respective criterion) and 2214 coefficients used in the LDA can be derived from data collected from various treatments and / or from the experience acquired in animal studies.
In the represented embodiment, the first decision block 2204 assesses the response of the initial energy supply temperature by verifying whether the change in the average temperature in the first 15 seconds is greater than 14 ° C. In an implementation, the
126 average temperature refers to the average over a short period of time (for example, 3 seconds), which essentially filters out large fluctuations at high frequency caused by the pulsating blood flow. As will be appreciated, an increase in temperature at the treatment electrode is a result of the conduction of heat from the tissue to the electrode. If an electrode is not in sufficient contact with the vessel wall, energy is delivered to the blood flowing around it and the temperature of the electrode is not increased as much. With this in mind, if the average temperature change in the first 15 seconds is greater than, for example, 14 ° C, this initial temperature response may indicate sufficient electrode contact, contact force, and / or blood flow at least at the beginning of the treatment and, if no indication that the treatment should not proceed as expected is found during the rest of the treatment, there is a high probability that the treatment was less than optimal or technically unsuccessful. Thus, a positive response in decision block 2204 results in a Completion of Treatment 2220 message being displayed. However, if the change in average temperature in the first 15 seconds is less than or equal to, for example, 14 ° C, this initial temperature response may indicate that the electrode may not have had sufficient contact with the vessel wall. . Thus, a negative answer in decision block 2204 results in criteria 2206 for further evaluation.
During decision block 2206, the warmest temperature is assessed by checking whether the maximum average temperature is greater than, for example, 56 ° C. Raising the temperature above a threshold level (for example, 56 ° C ), regardless of duration, may be sufficient to allow technical success. Thus, a temperature above the threshold may be sufficient to indicate the formation of a successful lesion, despite the fact that in decision block 2204 the initial temperature rise did not indicate sufficient contact. For example, the electrode may not
127 have had enough contact initially, but then the contact could have been made at least long enough to cause the vessel wall to heat up in such a way that the temperature sensor on the electrode reads above 56 ° C. A positive result in decision block 2206 results in a Completion of Treatment 2220 message being displayed. However, a negative result in decision block 2206 indicates that the maximum mean temperature has not increased enough. The 2200 algorithm therefore passes to decision block 2208 for further evaluation.
During decision block 2208, the average temperature is evaluated during a period when the power is maintained at the maximum value (that is, the ramp-up period is eliminated from the calculation of the average value). In one embodiment, this assessment consists of determining whether the average real-time temperature is above 53 ° C during the period of 45 seconds to 120 seconds. In this way, this criterion checks to determine if the temperature was above a threshold for a certain duration. If decision block 2208 generates a positive determination, then, despite the fact that the response of the initial temperature and the maximum mean temperature was insufficient to indicate technical success (that is, decision blocks 2204 and 2206 failed), the average temperature during the last 75 seconds indicates sufficient contact for a sufficient time. For example, it is possible that a sufficient injury is made and the average maximum temperature measured at the electrode was not greater than 56 ° C, because there is no high blood flow pulling the heat from the electrode. Thus, a positive result in decision block 2208 results in a Completion of Treatment 2220 message being displayed. However, a negative result in decision block 2208 indicates that the average real-time temperature in the extended power phase was not sufficient and the 2200 algorithm proceeds to decision block 2210 for further evaluation of the treatment.
128
During decision block 2210, the change in impedance is evaluated by checking whether the percentage of change in impedance over a predetermined period of time (for example, 45 seconds to 114 seconds) is greater than a predetermined value (for example, example, 14%) of the initial impedance. The initial impedance is determined as the impedance shortly after the start of treatment (for example, in 6 seconds) to eliminate possible misinterpretations in impedance measurement before this period (for example, due to the injection of contrast). As will be appreciated, the tissue impedance for radiofrequency electrical current (RF) decreases with increasing tissue temperature until the tissue is heated enough to cause it to dehydrate at which point its impedance starts to rise. Therefore, a decrease in tissue impedance may indicate an increase in tissue temperature. The percentage of change in impedance in real time during the extended power phase can be calculated as follows:
% ΔΖ during SS = 100 * (Z ^ * ⁱ⁰ - (average ZRT during SS ~ J (1)
If decision block 2210 generates a positive determination, then, despite the fact that the last three decision blocks did not demonstrate that there was a sufficient increase in temperature (that is, decision blocks 2204, 2206, and 2208 failed), changing the impedance may indicate that the tissue has been heated sufficiently, but the temperature sensor on the electrode has not increased enough. For example, too high blood flow can cause the electrode temperature to remain relatively low, even if the tissue has been heated. Thus, a positive result in a decision block 2210 results in a Completion of Treatment 2220 message being displayed. However, a negative result in a decision block 2210 results in the algorithm 2200 proceeding to execute an LDA 2212.
129
In LDA 2212, a combination of events is evaluated together with an importance ranking for each event. In the represented embodiment, for example, the criteria evaluated in decision blocks 2204, 2206, 2208, 2210 are included in LDA 2212. In addition, in this implementation, three additional criteria can be included: (1) standard deviation of the average temperature (which can provide an indication of the degree of sliding movement caused by breathing), (2) the standard deviation of temperature in real time (which can provide an indication of variable blood flow and / or contact force and / or intermittent contact), and (3) adjusted change in mean impedance at the end of treatment (which can further characterize the change in impedance and provide an indication of a change in tissue temperature). If this analysis determines the combination of variables to have a significant impact on the reduction of technical success (for example, an LDA score <0 in decision block 2222), then an Unexpected Treatment 2224 message is displayed. Otherwise, a Completion of Treatment 2220 message is displayed.
It should be noted that the various parameters described above are only representative examples associated with an embodiment of the 2200 algorithm, and one or more of these parameters may vary in other embodiments. In addition, the specific values described above in relation to particular portions of the treatment can be modified / changed in other embodiments based, for example, on different device configurations, electrode configurations, treatment protocols, etc.
As described above, the 2200 algorithm is configured to evaluate a treatment and display a message indicating that the treatment is complete or, alternatively, that the treatment did not proceed as expected. Based on the message describing the treatment assessment, the clinician (or the system using automated techniques) can
130 then decide whether additional treatments may be needed and / or whether one or more parameters should be modified in subsequent treatments. In the examples described above, for example, the 2200 algorithm can evaluate a set of situations, usually related to poor contact between the electrode and the vessel wall to help determine whether the treatment was less than ideal. For example, poor contact can occur when an electrode slides back and forth according to the patient's breathing and artery movements, when an electrode moves when the patient moves, when the catheter is moved inadvertently, when a catheter no 10 is deflected to the degree necessary to apply sufficient contact or contact force between the electrode and the vessel wall, and / or when an electrode is placed in a precarious position. In addition, as described above, if a particular parameter or set of parameters may have contributed to or resulted in less than optimal treatment, system 10 (figure 15 1) can provide feedback to alert the clinician to modify one or more treatment parameters during subsequent treatment. Such evaluation and resumption of treatment is expected to help clinicians learn to improve their placement technique to obtain better contact and to reduce the frequency of treatments technically to no avail.
D. Return related to high temperature conditions
While the previous one describes the generalized evaluation of the technical success of a treatment, another form of return that can be useful for the system 10 operator (Fig. 1) is a return related to specific types of patient or treatment conditions. For example, system 10 can generate a message related to high temperature conditions. In particular, during a treatment while energy is being dispensed, the temperature of the tissue may rise above a specified level. A temperature sensor (for example, a thermocouple, thermistor, etc.) positioned at or near the electrode provides an indication
131 of the electrode temperature and, to some extent, an indication of the tissue temperature. The electrode does not heat up directly as energy is delivered to the tissue. Instead, the fabric is heated and the heat leads to the electrode and the temperature sensor on the electrode. In an implementation, system 10 can stop energy delivery if the real-time temperature rises above a predefined maximum temperature (for example, 85 ° C). In such a case, the system may generate a message indicating the high temperature condition. However, depending on the circumstances, the different actions of the clinician may be appropriate.
If the fabric becomes too hot, the established temperature limits can be exceeded. The implications of high tissue temperature are that an acute artery constriction or a bulge of the artery wall can occur. This can happen immediately or within a short period of time (for example, about 50 seconds to about 100 seconds), after the occurrence of high temperatures it is noticed and a message is generated. In such an occurrence, the clinician may be instructed to convert the treatment site into an image to look for a constriction or protrusion before beginning another treatment.
Fig. 23, for example, is a block diagram illustrating a 2250 algorithm to provide feedback to the operator when a high temperature condition is detected according to an embodiment of the present technology. In one implementation, the 2250 algorithm runs in response to a high temperature condition (block 2252) and evaluates (decision block 2254) data from the treatment, to determine whether the high temperature condition involved a situation that includes instability sudden or if she didn't. Sudden instability can be caused, for example, by a sudden movement of the patient or the catheter, thus causing the electrode to be pushed harder (ie, the contact force is increased) in the vessel wall, which also can be accompanied by a
132 move to another location. In the event that sudden instability is not detected in decision block 2254, a first message may be displayed (block 2256), such as an indication that an elevated temperature has been detected as an instruction for converting the image of the treatment site, to determine if the site has been damaged. In the event that sudden instability is detected in decision block 2254, an alternative message may be displayed (block 2258) that, in addition to indicating the occurrence of high temperatures and instructing the clinician to convert the treatment site into an image, can also indicate the possibility that the electrode may have moved from its original location. Such a return can lead the doctor to compare the previous images and avoid re-treating both the original site or the site to which the electrode was moved.
E. Return associated with high impedance
As with high temperature, in certain circumstances, system 10 (figure 1) can generate a message related to the occurrence of high impedance. As will be appreciated, the impedance of RF current passing from a treatment electrode through the body to a dispersive return electrode can provide an indication of the characteristics of the tissue that is in contact with the treatment electrode. For example, an electrode positioned in the blood stream in the renal artery can measure a lower impedance than an electrode contacting the vessel wall. In addition, as the tissue temperature increases, its impedance decreases. However, if the fabric gets too hot, it can dry out and its impedance can increase. During a treatment, as the tissue is gradually heated, it is expected that the impedance will decrease. A significant increase in impedance can be a result of an unwanted situation, such as tissue drying or electrode movement. In certain implementations, system 10 can be configured to cease power supply if increased impedance
133 in real time is higher than a predefined maximum change in impedance from the starting impedance.
Fig. 24, for example, is a block diagram illustrating a 2270 algorithm for providing feedback to the operator when a high impedance condition occurs, in accordance with an embodiment of the present technology. In the represented embodiment, the 2270 algorithm evaluates the treatment data and determines whether the detection of a high impedance event (block 2272) was likely to involve a situation in which (a) the tissue temperature was elevated and desiccation it was likely, (b) the electrode moved, or (c) there was poor electrode contact or no electrode contact with the vessel wall. Algorithm 170 evaluates the data to determine which, if any, of these three situations occurred and displays one of the three messages 2274, 2276, or 2278 accordingly.
According to an embodiment of the 2270 algorithm, after detecting a high impedance (block 2272), the average maximum temperature during treatment is evaluated (decision block 2280). If this temperature is above a certain threshold (for example, equal to or greater than 60 ° C), then the high impedance can be attributed to the high temperature of the tissue which results in desiccation. In this case, message 2274 can be displayed instructing the clinician to check for a constriction or lump (that is, to convert the treatment site into an image) and to avoid treating the same site again. Conversely, if the temperature is below the threshold (for example, below 60 ° C), the 2270 algorithm proceeds to decision block 2282.
In the represented embodiment, in decision block 2282, algorithm 2270 evaluates whether the high impedance event occurred at the beginning of the treatment (for example, during the first 20 seconds of energy supply) when the power is relatively low. If so, it is unlikely that the tissue temperature was high and more likely that the electrode initially had
134 little or no contact and subsequently established a better contact, causing the impedance to jump. In this case, message 2276 can be displayed instructing the clinician to try to establish better contact and repeat treatment, in the same location. However, if the event occurs after treatment (for example, more than 20 seconds have elapsed), the 2270 algorithm proceeds to decision block 2284.
During decision block 2284, algorithm 2270 evaluates when the high impedance event occurred during treatment. For example, if the event occurred after a predetermined period of time (for example, 45 seconds), when the power reached high levels, the algorithm proceeds to decision block 2286. However, if the event occurred when the power is being ramp up and not at its highest point (for example, between 20 seconds and 45 seconds), the algorithm proceeds to decision block 2288.
During decision block 2286, algorithm 2270 calculates the percentage change in impedance (% ΔΖ) at the time of the high impedance event compared to the impedance at a given time (for example, 45 seconds). This is the period when the power is maintained at a high level. In one embodiment, the percentage change in impedance is calculated as:
= 100 * I ----------------------- (2)
If% ΔΖ is greater than or equal to a predetermined value (for example, 7%) then it may be possible that the tissue has started to dry out due to the high temperature. In this case, message 2274 can be displayed instructing the clinician to check for a constriction or lump (that is, to convert the image of the treatment site) and to avoid treating the same site again. Otherwise, desiccation of the tissue is less likely and it is more likely that the electrode moved to cause the high impedance event. In this case, message 2278 can be displayed notifying the clinician that the
135 electrode may have moved. In case the electrode has moved or may have been moved, the tissue temperature is unlikely to reach a high level. Therefore, it is expected that treatment in the same place can be done if there is no place or other limited places to carry out another treatment.
During decision block 2288, algorithm 2270 can determine whether a sudden instability has occurred. If such instability was present, it is likely that the electrode moved. In this case, message 2278 may be displayed notifying the clinician that the electrode may have moved. As discussed above, the clinician can exercise caution and avoid treating the original location or the location to which the electrode moved, or the clinician may choose to treat at the same location if no other sites or a limited number of sites are available for further treatment. Otherwise, if no sudden instability occurred, it is more likely that the electrode had poor contact. In this case, message 2276 can be displayed instructing the clinician to try to establish better contact and that treatment from the same location is safe.
The same objective of detecting high impedance conditions can be achieved through alternative measurements and calculations. For example, in another embodiment of the 2270 algorithm, the temperature and impedance data is taken over a sampling time interval (for example, 20 seconds). In a shorter time interval (for example, every 1.5 seconds), the standard deviation of the impedance and temperature data is calculated. The first standard temperature for an interval is calculated as the standard deviation of the temperature divided by the standard deviation of the temperature in the initial time interval. If the standard deviation of the impedance measurements is greater than or equal to a predetermined value (for example, 10 Ohms) and the first standard temperature is greater than a predetermined threshold (for example, 3), then the 2270 algorithm can display the message 2276, indicating poor electrode contact. At the
136 However, if the standard deviation of the impedance measurement is outside the acceptable range, but the first standard temperature is within the acceptable range, then message 2278 will be displayed to alert the clinician that electrode instability exists.
According to another embodiment of the algorithm 2270, the impedance of two or more electrodes 24 (for example, positioned in the treatment region 22 of the catheter 12 of Figure 1) can each provide an independent impedance reading. During the dispensation of the therapeutic set 22 to the treatment site (for example, inside the renal artery), the impedance readings of the electrodes 24 are typically different, due to the anatomy of the vasculature, as the catheter 12 will conform to the path of less resistance, often bending in the curves of the vasculature just to contact a wall of the renal artery. In some embodiments, once the therapeutic set 22 is in position for treatment, the therapeutic set 22 can be expanded circumferentially to contact the entire circumferential surface of a segment of the renal artery wall. This expansion can place multiple electrodes 24 in contact with the renal artery wall. As the therapeutic set 22 is expanded to the treatment configuration and the electrodes 24 make increased contact with the renal artery wall, the impedance values of the individual electrodes 24 may increase and / or approach the same value. With good and stable contact, fluctuations in the impedance value also reduce, as described above. The power generator 26 can continuously monitor the individual impedance values. The values can then be compared to determine when the contact was actually made, as an indication of successful treatment. In other embodiments, a moving average of impedance can be compared to a predetermined range of variability of impedance values with limits
137 defined to guide stability measurements.
F. Return related to vasoconstriction
In other embodiments, system 10 can generate a message related to the occurrence of vasoconstriction. In particular, while treatment is being dispensed, blood vessels may contract to a smaller than ideal diameter. The constricted blood vessels can lead to reduced blood flow, increased temperatures at the treatment site, and increased blood pressure. Vasoconstriction can be measured by sampling the amplitude (the envelope) of temperature data in real time. The current envelope can be compared with a previous envelope sample take (for example, 200 ms before). If the difference between the current envelope and the previous time point envelope is less than a predetermined value (for example, less than -0.5 ° C, or in other words, there is a reduction of less than 0.5 degrees at the present envelope value compared to the envelope value at the previous time point), then measurements are taken at a point in the future (for example, within 5 seconds). If the average temperature difference at the future time point and the current time point is greater than a given temperature threshold (for example, more than 1 ° C), then a 2500 algorithm can determine that an undesirably high level constriction exists, and it can cease / alter the energy supply. In such a case, system 10 can generate a message indicating the condition of high constriction. However, depending on the circumstances, the different actions of the clinician may be appropriate.
Figure 25, for example, is a block diagram illustrating a 2500 algorithm to provide feedback to the operator when a high degree of vessel constriction is detected according to an embodiment of the present technology. In an implementation, the 2500 algorithm runs in response to a high level of constriction (for example, constricted vessels
138 at or below a certain diameter) (Block 2502) and evaluates (decision block 2504) data from the treatment, to determine whether the high level of constriction involved a situation that included sudden instability or if it did not. An indication of sudden instability may indicate that electrode 24 has moved.
In the event that sudden instability is not detected in decision block 2504, a first message may be displayed (block 2506), such as an indication that a high level of constriction has been detected and an instruction for a clinician to reduce the potency of the treatment. In other embodiments, the energy level can be automatically changed in response to the detected level of constriction. In the event that sudden instability is detected in decision block 2504, an alternative message may be displayed (block 2508), which, in addition to indicating the occurrence of constriction at the high level and instructions to the clinician, may also indicate the possibility that electrode 24 may have moved from its original location. Such a return can lead the clinician to change or stop treatment.
G. Return related to cardiac factors
1. Return related to abnormal heart rate
Like other physiological conditions mentioned above, in certain circumstances, system 10 can generate a message related to the occurrence of an abnormal heart rate. In particular, while treatment is being dispensed, heart rate may exceed or fall below desirable conditions (for example, chronic or temporary procedural bradycardia). Instant heart rate can be determined by measuring temperature and impedance in real time. More specifically, a real-time temperature reading can be filtered, for example, between 0.5 Hz and 2.5 Hz using a second order Butterworth filter. Local maximums of the filtered signal are determined. Local maximums are the detected peaks of the temperature signal
139 real. The instantaneous beat rate is the interval between the peaks, as the signal peaks correspond to the periodic change of the cardiac cycle.
In an implementation, system 10 can stop / change energy delivery if the heart rate falls outside a desirable range. In such a case, the system may generate a message indicating the adverse heart rate condition. However, depending on the circumstances, the different actions of the clinician may be appropriate.
Fig. 26A, for example, is a block diagram illustrating a 2600 algorithm for providing instructions / return to the operator after detecting an abnormal heart rate condition, in accordance with an embodiment of the present technology. In one implementation, for example, the 2600 algorithm can be executed in response to an abnormal heart rate condition (for example, above or below a predetermined threshold) (Block 2602). In decision block 2604, algorithm 2600 evaluates treatment data to determine whether the abnormal heart rate condition involved a situation that includes sudden instability. An indication of sudden instability may indicate that the electrode has moved.
In the event that sudden instability is not detected in decision block 2604, a first message may be displayed to the clinician (block 2606), such as an indication that an abnormal heart rate has been detected and an instruction for the clinician to reduce the power of the treatment. In other embodiments, the energy level can be changed automatically in response to the detected adverse heart rate. In the event that sudden instability is detected in decision block 2604, an alternative message may be displayed (block 2608), which, in addition to indicating the occurrence of abnormal heart rate and instructions to the clinician, may also indicate the possibility that the electrode may have moved from its original location. Such a return may lead the clinician to alter or
140 cease treatment.
2. Return related to low blood flow
System 10 can also be configured to generate a message related to low blood flow conditions. For example, if the blood flow drops below a certain level during treatment (or if the vessels are undesirably narrow), the convective heat removed from the electrode 24 and the tissue surface is reduced. Excessively high tissue temperatures can lead to the negative results described above, such as thrombosis, carbonization, unreliable lesion size, etc. Reducing the power of the generator 26 to prevent the tissue from reaching an unacceptable temperature can lead to insufficient depth of injury, and the nerves may not be heated to sufficient ablation temperatures. An algorithm can be used to measure blood flow or heat loss to the bloodstream. In one embodiment, blood flow can be measured with a flow meter or a Doppler sensor placed in the renal artery in a separate catheter or treatment catheter 12. In another embodiment, heat loss or thermal decay can be measured by dispensing energy (for example, RF energy) to raise the temperature of tissue, blood, or substrate. The power can be turned off and the algorithm can include temperature control, as a measure of thermal decay. Rapid thermal decay can represent sufficient blood flow, while gradual thermal decay can represent low blood flow. For example, in one embodiment, the 2610 algorithm can indicate a low blood flow if the slope of real-time temperature measurements over the starting temperature exceeds a preset limit (for example, 2.75) and the average temperature is higher than a preset temperature (eg 65 ° C). In other embodiments, thermal decay and / or blood flow can be characterized by measuring
141 temperature fluctuations from dispensing an RF or heat resistive electrode. At a given temperature, or amplitude / magnitude of power delivery, a narrow range of oscillation can indicate a relatively low thermal decay / blood flow.
Fig. 26B, for example, is a block diagram illustrating an algorithm 2610 to provide feedback to the operator / instructions when a low blood flow condition occurs, in accordance with an embodiment of the present technology. In one implementation, the 2610 algorithm runs in response to a detected low blood flow condition (for example, flow below a predetermined threshold) (Block 2612). In block 2614, algorithm 2610 evaluates treatment data to determine whether low blood flow conditions involved a situation that includes sudden instability. In the event that sudden instability is not detected in decision block 2614, a first message may be displayed (block 2616), such as an indication that low blood flow has been detected and an instruction to a clinician to reduce the potency of the treatment . In the event of sudden instability being detected, an alternative message may be displayed (block 2618), which, in addition to indicating the occurrence of low blood flow and instructions to the clinician, may also indicate the possibility that the electrode may have moved from its original location. As mentioned above, this return can lead the clinician to change or stop treatment.
In other embodiments, if the blood flow or thermal decay values are less than a normal or predetermined threshold, the 2610 energy dispensing threshold may automatically include changing one or more treatment or catheter conditions or characteristics, to improve blood flow. For example, in one embodiment, the 2610 algorithm can respond to a low blood flow by pulsating the energy supplied to the dispensing element.
142 energy 264, instead of providing continuous energy. This can allow the lower blood flow to more adequately remove heat from the tissue surface, while still creating a lesion deep enough for the ablation of a nerve.
In another embodiment, the 2610 algorithm may include the response to a low blood flow by cooling the electrodes, as described in more detail in International Patent Application No. PCT / US2011 / 033491, filed on April 26 of 2011, and US Patent Application No. 12 / 874,457, filed on August 30, 2010. Previous applications are incorporated herein by reference in their entirety.
In another embodiment, the 2610 algorithm can respond to low blood flow, requiring a manual increase in blood flow to the region. For example, a non-occlusive balloon can be inflated in the abdominal aorta, which increases pressure and flow in the renal artery. The balloon can be incorporated into the treatment catheter or a separate catheter.
H. Return display
Figures 27A and 27B are screenshots illustrating representative generator display screens configured according to aspects of current technology. Figure 27A, for example, is a 2700 display screen for tracking increased impedance during treatment. Display 2700 includes a graphic display 2710 that tracks impedance measurements in real time over a selected period of time (for example, 100 seconds). This 2710 graphic display, for example, can be a dynamic bearing display that is updated at periodic intervals to provide an operator with both instantaneous and historical impedance measurement tracking. The display 2710 may also include an impedance display 2720 with the current impedance, as well as an indication of standard deviation 2722 for the impedance. In one embodiment, the standard deviation indication 2722 is configured
143 to flash when this value is greater than 10. This indication can alert the operator of a contrast injection that is affecting the measurement or that the electrode may be unstable. Further information on contrast injection indications is described below.
Figure 27B, for example, is another representative display screen 2730 with additional information for an operator. In this example, the display display 2730 is configured to alert the operator of a contrast injection and that the system is waiting for the contrast to clear before starting (for example, disable RF for approximately 1 to 2 seconds, until the contrast disappear). In another embodiment, the display display 2730 can be configured to provide other alert messages (for example, POSSIBLE INSTALLABLE ELECTRODE, etc.). Additional information provided on display screens 2710 and 2730 described above is expected to improve the evaluation. before RF ON, and improve treatment efficiency and effectiveness.
The additional information described above with reference to Figures 27A and 10B can be generated based on the algorithms described in this document, or other suitable algorithms. In one embodiment, for example, an algorithm can continuously check for contrast / stability injection during pre-RF ON. If the electrode is stable and there is no contrast for> 1 second, the baseline impedance Z is set equal to the average impedance Z over 1 second. In a particular example, the real-time impedance is compared to two standard deviations from the average impedance value within a window of one second. In another specific example, the impedance in real time can be compared to a fixed number (for example, determining whether the standard deviation is greater than 10). In yet other examples, other provisions can be used.
If the real-time impedance measurement is within this range, no message is displayed. However, if the time impedance
144 real is not within two standard deviations from the mean, the electrode may not be stable (ie, bypass, movement, etc.) and one or both of the message (s) described above with reference to Figures 27A and 27B can be displayed to the user (for example, WAITING FOR CONTRAST TO CLEAN, POSSIBLE UNSTABLE ELECTRODE). As an example, for contrast injection detection, in addition to the standard deviation of the impedance, the algorithm can be configured to take into account the standard deviation of a real-time temperature measurement to look for real-time temperature excursions below of a starting body temperature. The exact value for cutting the temperature excursion may vary. In a particular example, the system is configured such that if there is an increase in impedance (for example, the standard deviation> 10) accompanied by a drop in temperature in real time, the system will mark an event detected by contrast that leads to CONTRAST WAIT TO CLEAN message to be displayed to the operator. In other examples, however, other algorithms and / or intervals can be used to determine the contrast injection events and / or the electrode stability. In addition, in some embodiments, the system can change / adjust various treatment parameters based on detected conditions without displaying such messages to the clinician.
VII. Pre-packaged kit for the transportation, distribution and sale of the disclosed devices and Systems
As illustrated in Figure 28, one or more of the components of the system 10 shown in Figure 1, can be packaged together in a kit 276 for convenient dispensing and use by the client / clinical operator. Suitable components for packaging include, treatment device 12, cable 28 to connect treatment device 12 to energy generator 26, neutral or dispersive electrode 38, and one or more guiding catheters (for example, a renal guiding catheter ). Cable 28 can
145 can also be integrated into the treatment device 12 in such a way that both components are packaged together. Each component can have its own sterile packaging (for components that require sterilization) or the components can have dedicated sterile compartments within the kit packaging. This kit can also include step-by-step instructions 280 for use that provide the operator with the technical characteristics of the product and operating instructions for using the system 10 and the treatment device 12, including all methods of insertion, dispensing , placement and use of the treatment device 12 described herein.
VIIL Additional clinical uses of the disclosed technology
Although certain embodiments of the current techniques concern at least partially denervating a patient's kidney to block afferent and / or efferent neural communication from within a renal blood vessel (for example, the renal artery), the devices, methods and The systems described in this document can also be used for other intravenous treatments. For example, the catheter system mentioned above, or selected aspects of such a system, can be placed in other peripheral blood vessels to dispense energy and / or electrical fields to achieve a neuromodulatory effect by altering the nerves adjacent to these other peripheral blood vessels. There are a number of arterial vessels arising from the aorta that travel alongside a rich collection of nerves in target organs. The use of arteries to access and modulate these nerves can have clear therapeutic potential in a number of disease states. Some examples include the nerves surrounding the celiac trunk, superior mesenteric artery and inferior mesenteric artery.
Sympathetic nerves near or surrounding the arterial blood vessel known as the celiac trunk can pass through the celiac ganglion and follow branches of the celiac trunk in the innervation of the stomach,
146 small intestine, abdominal blood vessels, liver, bile ducts, gallbladder, pancreas, adrenal glands and kidneys. The modulation of these nerves in whole or in part, (through selective modulation) may allow the treatment of conditions, including, but not limited to, pancreatitis, diabetes, obesity, hypertension, obesity-related hypertension, hepatitis, hepatic syndrome -renal, gastric ulcers, gastric motility disorders, irritable bowel syndrome, and autoimmune disorders such as Crohn's disease.
The sympathetic nerves near or surrounding the arterial blood vessel known as the inferior mesenteric artery can pass through the inferior mesenteric ganglion and follow the branches of the inferior mesenteric artery in the innervation of the colon, rectum, bladder, sexual organs, and external genitalia. The modulation of these nerves in whole or in part (through selective modulation) may allow the treatment of conditions, including, but not limited to, GI motility disorders, colitis, urinary retention, overactive bladder, incontinence, infertility, polycystic ovary, premature ejaculation, erectile dysfunction, dyspareunia, and vaginismus.
Although arterial access and treatments received have been provided for here, the apparatus, methods and systems described can also be used to dispense treatment from a peripheral vein or lymphatic vessel.
IX. Additional Discussion of Relevant Anatomy and Physiology
The following discussion provides more details on the patient's pertinent anatomy and physiology. This section is intended to complement and expand on the previous discussion on relevant anatomy and physiology, and to provide additional context regarding the disclosed technology and therapeutic benefits associated with renal denervation. For example, as mentioned earlier, various properties of the renal vasculature can inform the design of treatment devices and the associated methods
147 for obtaining renal neuromodulation through intravascular access, and impose the requirements of specific projects for such devices. Specific design requirements may include access to the renal artery, facilitating contact between the stable energy-dispensing elements of such devices and a luminal surface or wall of the renal artery, and / or effectively modulating the renal nerves with the neuromodulatory apparatus.
A. The Sympathetic Nervous System
The sympathetic nervous system (SNS) is a branch of the autonomic nervous system, along with the enteric nervous system and the parasympathetic nervous system. It is always active at a basal level (called sympathetic tone) and becomes more active during periods of stress. As in other parts of the nervous system, the sympathetic nervous system operates through a series of interconnected neurons. Sympathetic neurons are often considered to be part of the peripheral nervous system (PNS), although many are within the central nervous system (CNS). Sympathetic neurons in the spinal cord (which is part of the central nervous system) communicate with peripheral sympathetic neurons through a series of sympathetic ganglia. Within the ganglia, sympathetic neurons in the spinal cord join peripheral sympathetic neurons through synapses. Sympathetic neurons in the spinal cord are therefore called presynaptic (or pre-ganglionic) neurons, while peripheral sympathetic neurons are called postsynaptic (or postganglionic) neurons.
At synapses within the sympathetic ganglia, pre-ganglionic sympathetic neurons release acetylcholine, a chemical messenger that binds and activates nicotinic acetylcholine receptors on post-ganglion neurons. In response to this stimulus, post-ganglionic neurons mainly release norepinephrine (norepinephrine). Prolonged activation can trigger the release of adrenaline through the adrenal medulla.
Once released, norepinephrine and epinephrine bind receptors
148 adrenergics in peripheral tissues. Binding to adrenergic receptors elicits a neuronal and hormonal response. Physiological manifestations include dilation of the pupils, increased heart rate, occasional vomiting, and increased blood pressure. Increased sweating is also seen, due to the binding of cholinergic receptors to the sweat glands.
The sympathetic nervous system is responsible for the positive and negative regulation of many homeostatic mechanisms in living organisms. SNS fibers innervate tissues in almost every organ in the system, providing at least some regulatory function for things as diverse as pupil diameter, intestinal motility, and urinary flow. This response is also known as the body's sympathoadrenal response, as the sympathetic pre-ganglionic fibers that end in the adrenal medulla (but also all other sympathetic fibers) secrete acetylcholine, which activates the secretion of adrenaline (epinephrine) and norepinephrine to a degree minor (norepinephrine). Therefore, this response that acts mainly on the cardiovascular system is mediated directly through impulses transmitted through the sympathetic nervous system and indirectly through catecholamines secreted from the adrenal medulla.
Science typically looks at the NHS as a system of automatic regulation, that is, one that operates without the intervention of conscious thought. Some evolutionary theorists suggest that the sympathetic nervous system operated on early organisms to maintain survival as the sympathetic nervous system is responsible for preparing the body for action. An example of this preparation is in the moments before waking up, when the sympathetic flow increases spontaneously, in preparation for action.
1. The sympathetic chain
As illustrated in Figure 29, the SNS provides a nerve network that allows the brain to communicate with the body. Nerves
149 sympathetic cells originate within the spine, towards the middle of the spinal cord in the column of intermediolateral cells (or lateral horn), starting at the first thoracic segment of the spinal cord and are thought to extend to the second or third segments of the lumbar. Because its cells begin in the thoracic and lumbar regions of the spinal cord, the SNS is said to have a thoracolumbar outlet. The axons of these nerves leave the spinal cord through the small root / anterior root. They pass near the (sensory) ganglion of the spine, where they enter the anterior branches of the spinal nerves. However, unlike somatic innervation, they quickly separate through white branch connectors that connect to both the paravertebral ganglia (which is located near the spine) and the pre-vertebral ganglia (which is close to the aortic bifurcation) extending to the along the spine.
In order to reach the target organs and glands, axons must travel long distances in the body, and to achieve this, many axons relay the message to a second cell through synaptic transmission. The ends of the axons connect through a space, the synapse, to the dendrites of the second cell. The first cell (the presynaptic cell) sends a neurotransmitter across the synaptic cleft, where it activates the second cell (the postsynaptic cell). The message is then transported to its final destination.
In SNS and other components of the peripheral nervous system, these synapses are made in places called ganglia. The cell that sends its fiber is called a pre-ganglion cell, while the cell whose fiber exits the ganglion is called a post-ganglion cell. As mentioned earlier, the pre-ganglion cells of the SNS are located between the first thoracic segment (Tl) and the third lumbar segment (L3) of the spinal cord. Post-ganglion cells have their cell bodies in the ganglion and send their axons to target organs or glands.
The ganglia not only include the sympathetic trunks, but
150 also the cervical ganglia (upper, middle and lower), which sends sympathetic nerve fibers to the head and the organs of the thorax and the celiac and mesenteric ganglia (which send sympathetic fibers to the intestine).
2. Innervation of the Kidneys
As Figure 30 shows, the kidney is innervated by the renal plexus RP, which is closely associated with the renal artery. The renal plexus RP is an autonomous plexus that surrounds the renal artery and integrates the adventitia of the renal artery. The renal plexus RP extends along the renal artery until it reaches the substance of the kidney. Fibers that contribute to the renal PR plexus arise from the celiac ganglion, the superior mesenteric ganglion, the aorticorenal ganglion and the aortic plexus. The renal plexus RP, also referred to as the renal nerve, is predominantly composed of sympathetic components. There is no (or at least very reduced) parasympathetic innervation of the kidney.
Ganglion neuronal cell bodies are located in the column of intermediolateral cells of the spinal cord. Preganglionic axons pass through the paravertebral ganglion (they do not synapse) to take the minor splanchnic nerve, the least splanchnic nerve, first splanchnic lumbar nerve, second splanchnic lumbar nerve, and displace it to the celiac ganglion, the upper mesenteric ganglion, and the upper mesenteric ganglion, and aorticorenal ganglion. Postganglionic neuronal cell bodies leave the celiac ganglion, the superior mesenteric ganglion, and the aorticorenal ganglion to the renal plexus RP and are distributed to the renal vasculature.
3. Neural renal sympathetic activity
Messages travel through the SNS in a bidirectional flow. Efferent messages can cause a change in different parts of the body simultaneously. For example, the sympathetic nervous system can accelerate the heart rate; widen bronchi; decrease motility (movement) of the large intestine; constrict blood vessels;
151 increase peristalsis in the esophagus, dilate the pupil, piloerection (causes chills) and perspiration (sweat) and raise blood pressure. Afferent messages transmit signals from various organs and sensory receptors in the body to other organs, and in particular the brain.
High blood pressure, heart failure and chronic kidney disease are some of the many disease states that result from chronic activation of the SNS, especially the renal sympathetic nervous system. Chronic activation of the SNS is an inadequate response that drives the progression of these diseases. Pharmaceutical management of the renin-angiotensin-aldosterone system (RAAS) has been a long-standing, but somewhat ineffective, approach to reducing over-activity of the NHS.
As mentioned above, the renal sympathetic nervous system has been identified as a major contributor to the complex pathophysiology of hypertension, states of volume overload (eg, heart failure) and progressive kidney disease, both experimentally and in humans. Studies using radiolabel dilution methodology to measure excess kidney norepinephrine for plasma revealed increased rates of renal norepinephrine (NE) overflow in patients with essential hypertension, particularly in young hypertensive individuals, which in conjunction with increased NE overflow of the heart, is consistent with the hemodynamic profile typically seen in early hypertension and is characterized by an increase in heart rate, cardiac output and renovascular resistance. It is now known that essential hypertension is generally neurogenic, often accompanied by pronounced sympathetic nervous system hyperactivity.
The activation of cardiorenal sympathetic nerve activity is even more pronounced in heart failure, as demonstrated by an exaggerated increase in NE overflow from the heart and
152 kidneys for plasma in this group of patients. In line with this notion is the recent demonstration of a strong negative predictive value of renal sympathetic activation in all causes of mortality and heart transplantation in patients with congestive heart failure, which is independent of sympathetic activity in general, the glomerular filtration rate , and the left ventricular ejection fraction. These results support the notion that treatment regimens that are designed to reduce renal sympathetic stimulation have the potential to improve survival in patients with heart failure.
Both chronic and end-stage kidney diseases are characterized by elevated sympathetic nerve activation. In patients with end-stage kidney disease, above-average plasma norepinephrine levels have been shown to be predictive of both death from all causes and death from cardiovascular disease. This is also true for patients suffering from diabetes or contrast nephropathy. There is convincing evidence suggesting that afferent sensory signals from diseased kidneys are the main contributors to initiating and maintaining high central sympathetic overflow in this group of patients, which facilitates the occurrence of the known adverse consequences of chronic sympathetic overactivity, such as hypertension, ventricular hypertrophy left ventricular arrhythmias, sudden cardiac death, insulin resistance, diabetes and metabolic syndrome.
(I) Efferent renal sympathetic activity
The sympathetic nerves to the kidneys end in the blood vessels, the justaglomerular apparatus and the renal tubules. Stimulation of renal sympathetic nerves causes increased renin release, increased sodium reabsorption (Na +), and reduced renal blood flow. These components of neural regulation of renal function are considerably stimulated in disease states characterized by
153 increased sympathetic tone and clearly contribute to increased blood pressure in hypertensive patients. The reduction in renal blood flow and glomerular filtration rate as a result of efferent renal sympathetic stimulation is like a cornerstone of the loss of renal function in cardiorenal syndrome, which is renal dysfunction, as a progressive complication of chronic heart failure, with a clinical course that usually varies according to the patient's clinical status and treatment. Pharmacological strategies to thwart the consequences of efferent renal sympathetic stimulation include sympatholytic centrally acting drugs, beta-blockers (designed to reduce renin release), angiotensin-converting enzyme inhibitors and receptor blockers (designed to block the action of angiotensin II and activation of aldosterone resulting from the release of renin) and diuretics (designed to combat renal sympathetic mediated water and sodium retention). However, current pharmacological strategies have significant limitations, including limited effectiveness, compliance issues, side effects and others.
(II) The activity of the afferent sensory renal nerve
The kidneys communicate with integral structures in the central nervous system through renal sensory afferent nerves. Various forms of kidney damage can induce the activation of afferent sensory signals. For example, renal ischemia and reduced pulse volume or renal blood flow, or an abundance of adenosine enzyme can trigger the activation of afferent neural communication. As shown in Figures 31A and 31B, this afferent communication can be from the kidney to the brain or it can be from one kidney to the other kidney (via the central nervous system). These afferent signals are centrally integrated and can result in increased sympathetic overflow. This sympathetic impulse is directed to the kidneys, activating RAAS and inducing increased renin secretion, sodium retention, volume retention and vasoconstriction. Super friendly activity
154 also influences other organs and body structures innervated by sympathetic nerves, such as the heart and peripheral vasculature, resulting in adverse described effects of sympathetic activation, several aspects of which also contribute to the increase in blood pressure.
Physiology therefore suggests that (i) modulating tissues with efferent sympathetic nerves will reduce inadequate renin release, salt retention and decreased renal blood flow, and that (ii) modulation of tissue with sensory nerves afferents will reduce the systemic contribution to hypertension and other disease states associated with increased central sympathetic tone through its direct effect on the posterior hypothalamus as well as the contralateral kidney. In addition to the central hypotensive effects of afferent renal denervation, a desirable reduction in central sympathetic overflow to several other sympathetically innervated organs such as the heart and vasculature is anticipated.
B. Additional clinical benefits of renal denervation
As stated above, renal denervation is likely to be valuable in the treatment of various clinical conditions characterized by increased total sympathetic and particularly renal activity, such as hypertension, metabolic syndrome, insulin resistance, diabetes, left ventricular hypertrophy, kidney disease chronic terminal, inadequate fluid retention in heart failure, cardiorenal syndrome, and sudden death. Since the reduction of afferent neural signals contributes to the systemic reduction of sympathetic tone / impulse, renal denervation can also be useful in the treatment of other conditions associated with systemic sympathetic hyperactivity. In this way, renal denervation can also benefit other organs and body structures innervated by sympathetic nerves, including those identified in Figure 29. For example, as discussed earlier, reducing the central sympathetic impulse can reduce the insulin resistance that afflicts people with metabolic syndrome and the
155 Type II diabetics. In addition, patients with osteoporosis are also sympathetically activated and can also benefit from negative regulation of the sympathetic impulse that accompanies renal denervation.
C. Achieving intravascular access to the renal artery
According to current technology, neuromodulation of the left and / or right RP renal plexus, which is closely associated with the left and / or right renal artery, can be achieved through intravascular access. As Figure 32A shows, blood moved by contractions of the heart is transported from the heart's left ventricle through the aorta. The aorta descends through the chest and branches to the left and right renal arteries. Below the renal arteries, the aorta forks into the right and left iliac arteries. The right and left iliac arteries descend, respectively, between the right and left legs and join the right and left femoral arteries.
As illustrated in Figure 32B, blood accumulates in veins and returns to the heart, through the femoral veins to the iliac veins and into the inferior vena cava. The inferior vena cava branches into the right and left renal veins. Above the renal veins, the inferior vena cava rises to transmit blood to the right atrium of the heart. From the right atrium, blood is pumped through the right ventricle into the lungs, where it is oxygenated. From the lungs, oxygenated blood is transported into the left atrium. From the left atrium, oxygenated blood is transported back through the left ventricle to the aorta.
As will be described in greater detail later, the femoral artery can be accessed and cannulated to the base of the femoral triangle just below the midpoint of the inguinal ligament. A catheter can be inserted percutaneously into the femoral artery through this access route, passed through the iliac artery and aorta, and placed in the left and right renal arteries. This comprises an intravascular path that offers access
156 minimally invasive to the respective renal artery and / or other renal blood vessels.
The shoulder, upper arm, and wrist region provide other locations for introducing the catheter into the arterial system. For example, catheterization of the radial or axillary brachial artery can be used in selected cases. Catheters introduced through these access points can be passed through the left subclavian artery (or through the subclavian and brachiocephalic arteries on the right side), through the aortic arch, down into the descending aorta and into the renal arteries using angiographic techniques standard.
D. Properties and Characteristics of the renal vasculature
Since neuromodulation of the left and / or right RP renal plexus can be achieved according to current technology through intravascular access, the properties and characteristics of the renal vasculature may impose restrictions and / or inform the design of devices, systems, and methods to achieve such renal neuromodulation. Some of these properties and characteristics may vary between the patient population and / or within a given patient over time, as well as in response to disease states, such as hypertension, chronic kidney disease, vascular disease, end-stage kidney disease , insulin resistance, diabetes, metabolic syndrome, etc. These properties and characteristics, as explained in the present invention, may have an influence on the effectiveness of the procedure and the specific design of the intravascular device. Properties of interest may include, for example, material / mechanical, spatial, dynamic / hemodynamic and / or thermodynamic properties.
As previously discussed, a catheter can be advanced or percutaneously through the left or right renal artery through a minimally invasive intravascular path. However, access
157 minimally invasive renal arteries can be challenging, for example, because, compared to some other arteries that are routinely accessed through a catheter, renal arteries are often extremely tortuous, may be relatively small in diameter, and / or may be of relatively short length. In addition, renal artery atherosclerosis is common in many patients, especially those with cardiovascular disease. Renal artery anatomy can also vary significantly from patient to patient, which makes minimally invasive access even more difficult. Significant interpatient variation can be seen, for example, in relative tortuosity, diameter, length and / or the load of the atherosclerotic plaque, as well as the angle of departure, in which a renal artery branches from the aorta. Apparatus, systems and methods to achieve renal neuromodulation through intravascular access must account for these and other aspects of the anatomy of the renal artery and its variation in the entire patient population when minimally invasively accessing a renal artery.
In addition to complicating renal arterial access, details of renal anatomy also complicate the establishment of stable contact between neuromodulatory devices and a luminal wall or wall of a renal artery. When the neuromodulator apparatus includes an energy delivery element, such as an electrode, consistent positioning and adequate contact force applied by the energy delivery element to the vessel wall is important for predictability. However, navigation is impeded by the tight space within a renal artery, as well as the tortuousness of the artery. In addition, establishing consistent contact is complicated by the patient's movement, breathing, and / or the cardiac cycle, as these factors can cause significant movement of the renal artery in relation to the aorta, and the cardiac cycle can transiently distend the renal artery (or (ie make the artery wall pulse).
Even after accessing a renal artery and facilitating contact
158 stable between the neuromodulator apparatus and a luminal surface of the artery, nerves in and around the adventitia of the artery must be safely modulated through the neuromodulator apparatus. Effective application of heat treatment within a renal artery is not trivial, given the potential clinical complications associated with such treatment. For example, the intima and media of the renal artery are highly vulnerable to thermal injury. As discussed in more detail below, the thickness of the intima and media of the vessel lumen from its adventitia means that the target renal nerves may be several millimeters away from the luminal surface of the artery. Sufficient energy must be provided or heat removed from the target renal nerves to modulate the target renal nerves without excessive cooling or heating of the vessel wall, as the wall is frozen, desiccated, or otherwise potentially undesirable. A potential clinical complication associated with overheating is the formation of blood clotting thrombi that flows through the artery. Since this thrombus can cause a renal infarction, thereby causing irreversible damage to the kidney, heat treatment from within the renal artery must be applied carefully. Thus, fluid mechanics and complex thermodynamic conditions present in the renal artery during treatment, especially those that can impact the heat transfer dynamics at the treatment site, can be important in the application of energy (for example, heating of thermal energy) and / or the removal of heat from the tissue (for example, cooling of thermal conditions) from within the renal artery.
The neuromodulator device must also be configured to allow for the adjustable positioning and repositioning of the energy supply element inside the renal artery, since the location of the treatment can also influence clinical efficacy. For example, it may be tempting to apply a complete circumferential treatment from within the renal artery, since the renal nerves can be spaced
159 circumferentially around a renal artery. In some situations, a full-circle injury likely to result from continuous circumferential treatment can potentially be related to renal artery stenosis. Therefore, the formation of more complex lesions along a longitudinal dimension of the renal artery through the mesh structures described herein and / or the repositioning of the neuromodulator apparatus to multiple treatment sites may be desirable. It should be noted, however, that an advantage of creating a circumferential ablation can outweigh the potential for renal artery stenosis, or the risk can be mitigated with certain embodiments, or in certain patients and creating circumferential ablation may be an objective . In addition, variable positioning and repositioning of the neuromodulatory system may prove to be useful in circumstances where the renal artery is particularly tortuous or where proximal vessels are branched out of the main renal artery vessel, making treatment of certain sites challenging. The manipulation of a renal artery device must also consider the mechanical trauma imposed by the device in the renal artery. Movement of a device in an artery, for example through insertion, manipulation, negotiation of curves and so on, can contribute to perforation, dissection, intimate stripping, or the rupture of the internal elastic lamina.
Blood flow through a renal artery may be temporarily blocked for a short period of time, with minimal or no complications. However, occlusion for a significant amount of time should be avoided, to avoid kidney damage, such as ischemia. It may be beneficial to avoid occlusion together, or, if occlusion is beneficial for the embodiment, limit the duration of the occlusion, for example, to 2-5 minutes.
Based on the challenges described above of (1) renal artery intervention, (2) consistent and stable placement of the treatment element
160 against the vessel wall, (3) the effective application of a treatment to the entire vessel wall, (4) positioning and potential repositioning of the treatment device to allow treatment at multiple sites, and (5) prevention or limitation of duration of the occlusion of blood flow, several independent and dependent properties of the renal vasculature, which may be of interest include, for example, (a) the diameter of the vessels, length of the vessel, thickness of intima-media, coefficient of friction, and tortuosity , (b) stiffness, distensibility, and the modulus of elasticity of the vessel wall; (c) systolic peak, final diastolic blood flow velocity, as well as the mean diastolic-systolic peak blood flow velocity, and the average volumetric blood flow rate / max, (d) the specific heat capacity of blood and / or the vessel wall, the thermal conductivity of blood and / or the vessel wall, and / or thermal convectivity of blood flow through a vessel wall treatment site and / or radiation heat transfer ( e) the movement of the renal artery relative to the aorta induced by breathing, by the patient's movement, and / or by the pulsatility of blood flow and (f), as well as the angle of departure of a renal artery in relation to the aorta. These properties will be discussed in more detail in relation to the renal arteries. However, depending on the devices, systems and methods used to obtain renal neuromodulation, such properties of the renal arteries can also guide and / or restrict design characteristics.
As mentioned above, a device placed inside a renal artery must conform to the geometry of the artery. The diameter of the renal artery vessels, Dra, is typically in the range of about 2-10 mm, with most of the patient population having a Dra of about 4 mm to about 8 mm and averaging about 6 mm. Renal artery vessel length, Lra, between its ostium at the aorta / renal artery junction and its distal branches, is generally in the range of about 5-70 mm, and a significant portion of the patient population is
161 in a range of about 20-50mm. Once the target renal plexus is incorporated into the adventitia of the renal artery, the intima-media thickness, IMT, (ie, the radial distance to the outside from the luminal surface of the artery to the adventitia containing target neural structures) it is also notable and is usually in a range of about 0.5-2.5 mm, with an average of about 1.5 mm. Although a certain depth of treatment is important to reach the target neural fibers, the treatment should not be too deep (for example,> 5 mm from the inner wall of the renal artery), in order to avoid non-target tissue and anatomical structures, such as the renal vein.
An additional property of the renal artery that may be of interest is the degree of renal movement relative to that of the aorta, induced by breathing and / or the pulsatility of blood flow. A patient's kidney, which is located at the distal end of the renal artery, can move as much as 4 cranially with respiratory excursion. This can provide significant movement to the renal artery connecting the aorta and kidney, which requires the neuromodulator device a unique balance of stiffness and flexibility to maintain contact between the heat treatment element and the vessel wall during breathing cycles. . In addition, the angle of departure between the renal artery and the aorta can vary significantly between patients, and can also vary dynamically within a patient, for example, due to kidney movement. The starting angle can generally be in the range of about 30 ° -135 °.
X. Conclusion
The above detailed descriptions of the embodiments of the technology are not intended to be exhaustive or to limit the technology to the precise form described above. Although the specific embodiments of, and examples for, the technology are described above for illustrative purposes, several equivalent modifications are possible within the scope of the technology, such as
162 how people skilled in the relevant technique will recognize. For example, while the steps are presented in a given order, alternative embodiments may perform the steps in a different order. The various embodiments described herein can also be combined to provide additional embodiments.
From the foregoing, it is noted that the specific embodiments of the technology have been described here for purposes of illustration, but well-known structures and functions have not been presented or described in detail to avoid unnecessarily obscuring the description of the embodiments of the technology. Where context allows, plural or singular terms may also include the term plural or singular, respectively.
In addition, unless the word or is expressly limited to meaning only a single item exclusive of the other items, in reference to a list of two or more items, then the use of or in such a list is to be interpreted as including (a ) any single item on the list, (b) all items on the list, or (c) any combination of items on the list. In addition, the term comprise is used throughout to mean including at least the recited function (s) in such a way that any larger number of the same feature and / or additional types of other features are not prevented . It will also be appreciated that specific embodiments have been described here for purposes of illustration, but that various modifications can be made without deviating from the technology. In addition, while the advantages associated with certain embodiments of the technology have been described in the context of the embodiments, other embodiments may also exhibit such advantages, and not all embodiments necessarily have to present such advantages as being within the scope of technology. Therefore, the dissemination and associated technology may cover other embodiments not
163 expressly shown or described here.
Disclosure can be defined by one or more of the following clauses:
1. A catheter device, comprising:
an elongated flexible tubular member extending along a longitudinal geometric axis, in which the elongated tubular member has a proximal portion, a distal portion, and a central lumen therein, and in which the tubular member comprises:
a deflection region in the distal portion, where the deflection region includes a plurality of grooves in a wall of the tubular member and substantially transversal to the longitudinal geometric axis, and an orientation region adjacent to the deflection region and between the deflection region and a distal end of the proximal portion of the elongated tubular member, wherein the orientation region includes a plurality of grooves in the wall of the tubular member and substantially transverse to the longitudinal geometric axis;
where the tubular member is selectively transformable between:
a first state in which the deflection region is generally linear extending along the longitudinal geometric axis, and a second state in which the deflection region comprises a generally helical structure and the orientation region has an elbow shape, so that the distal end of the proximal portion of the tubular member goes through an interior of the helix;
a plurality of energy delivery elements carried by the deflection region and including at least a first energy delivery element and a second energy delivery element, where, when the tubular member is in the second state, the first and second elements energy supply systems are axially and radially spaced from each other around the longitudinal geometric axis, and
164 is a control member operatively engaged with the tubular member to control the movement of the flexible tubular member between the first state and the second state.
2. The catheter apparatus of clause 1, in which, in the second state, the deflection region defines a helical geometric axis generally parallel to the longitudinal geometric axis and on which the helical structure rotates to define a plurality of revolutions and a helical diameter of the helical structure, and wherein the helical structure has a distal end and a proximal end spaced along the helical geometric axis to define a helix length.
3. The catheter apparatus of clause 2, in which the orientation region is configured to substantially axially align the helical geometric axis with the longitudinal geometric axis when the tubular member is in the second state, and in which the grooves in the orientation region are radially displaced about the longitudinal geometric axis from the grooves in the deflection region.
4. The catheter apparatus of clause 1, in which the helical structure comprises at least two revolutions to define at least two points of contact for engaging a wall of a peripheral blood vessel.
5. The catheter apparatus of clause 1, in which:
the grooves in the deflection region are elongated deflection grooves generally parallel to each other along the tubular member, where the deflection grooves extend completely through the wall of the tubular element, and the grooves in the guide region are orientation grooves elongated generally parallel to each other along the tubular member, and where the guiding grooves extend completely through the wall of the tubular member.
165
6. The catheter apparatus of clause 1, in which:
central points of each of the orientation grooves in the orientation region are spaced along a first progressive geometric axis extending along the length of the tubular member 5, and ^x central points of each of the deflection grooves in the deflection region are spaced along a second progressive geometric axis extending along the length of the tubular member and radially displaced in relation to the longitudinal geometric axis of the first progressive geometric axis.
7. The catheter apparatus of clause 6, in which in the first state:
the first progressive geometric axis is substantially parallel to the longitudinal geometric axis, and the second progressive geometric axis defines an angle of about 0.5 degrees (0.5 °) with respect to a line parallel to the longitudinal geometric axis.
8. The catheter apparatus of clause 6, in which, in the first state:
Progressive the first axis is substantially parallel to the longitudinal axis and the second axis defines a progressive angle of about two degrees (2 ^o) in relation to a line parallel to the longitudinal axis.
9. The catheter apparatus of clause 6, in which, in the first state, the first progressive geometric axis defines an angle between about 45 degrees (45 °) and 90 degrees (90 °) with respect to a line parallel to the axis longitudinal geometric.
10.0 catheter apparatus of clause 1, in which the plurality
166 of grooves in at least one of the deflection and orientation regions comprises at least one circumferentially elongated opening around the longitudinal geometric axis over an angle of about 300 °.
11.0 catheter apparatus of clause 10, in which at least one opening defines an arc length of about 0.04 inches (1.02 mm).
12. The catheter apparatus of clause 10, in which at least one opening includes a central region and two end regions arranged around and contiguous with the central region, and in which the central region and the two end regions each define one, a width of the opening that extends in the direction of the longitudinal geometric axis, the width defined by the two end regions, being greater than the width defined by the central region.
13.0 clause 12 catheter apparatus, in which each of the two end regions is substantially circular.
14. The catheter apparatus of clause 12, in which each of the two end regions and the central region is substantially rectangular and in which the two end regions are elongated parallel to the longitudinal geometric axis and the central region is elongated perpendicular to the longitudinal geometric axis.
15. The catheter apparatus of clause 12, in which each of the two end regions is substantially rectangular and elongated parallel to the longitudinal geometric axis, and the central region defines a circular portion centered on the opening.
16. The catheter apparatus of clause 1, in which the plurality of grooves in the deflection region comprise 30 or less deflection grooves, and in which the individual deflection grooves are spaced apart by about 0.03 inches (0.76 mm) to about 0.04
167 inches (1.02 millimeters).
17. The catheter apparatus of clause 1, in which the control member comprises a wire disposed in the central lumen, and in which the wire has a first end portion coupled to the distal portion of the tubular element such that the increase in traction in the control wire selectively transforms the deflection region of the tubular member between the first state and the second state.
18. The catheter apparatus of clause 17, further comprising a handle assembly in the proximal portion of the tubular member, and in which a second end portion of the wire is operatively coupled to the handle to apply traction to the wire.
19. A catheter device, comprising:
an elongated axis that has a proximal portion and a distal portion, where the distal portion of the axis is configured for the intravascular delivery of a renal artery from a human patient;
a sliding control wire disposed within the axis and attached to or near the distal portion of the axis;
a therapeutic set in the distal portion of the elongated axis, the therapeutic set, including a plurality of energy dispensing elements, including at least one first energy dispensing element and a second energy dispensing element, and wherein the therapeutic set is transformable, through the control wire, between:
a retracted configuration, in which the therapeutic set defines a dispensing profile of about 0.085 inches (2.16 mm) or less, around a central geometric axis, and an expanded configuration, in which the first and second dispensing elements of energy are axially and radially spaced from each other along and around the central geometric axis,
168 respectively.
20. The catheter apparatus of clause 19, additionally comprising a tip member in the distal portion of the elongated axis, in which the control wire is coupled to the tip member, and in which the tip member is configured for non-traumatic insertion into the renal artery.
21.0 the catheter apparatus of clause 19, in which it additionally comprises a manipulation set in the proximal portion of the axis and operatively coupled to the control wire, in which the manipulation set is configured to transition the therapeutic set between the retracted and expanded configurations .
22. The catheter apparatus of clause 19, in which the distal region includes a plurality of grooves formed in the distal portion of the elongated axis, in which the grooves are generally parallel to each other and, generally transverse to the central geometric axis, when the therapeutic set is in the retracted configuration.
23. The catheter apparatus of clause 19, wherein the control wire comprises ultra high molecular weight polyethylene.
24. The catheter apparatus of clause 19, in which the distal region comprises a groove, and in which the control wire is anchored in the groove.
25. The catheter apparatus of clause 19, additionally comprising a coil in the distal region, and in which the control wire is anchored in the coil.
26. The catheter apparatus of clause 19, in which a distal end of the control wire is tied and coated with a polymer material.
27. The clause 19 catheter apparatus, in which:
the support structure is configured to vary between a substantially linear structure in the
169 retracted configuration, and a helical structure in the expanded configuration, which defines a helical geometric axis generally parallel with the central geometric axis and on which the helical structure rotates to define a plurality of revolutions and a helical diameter of the helical structure , and wherein the helical structure comprises a distal portion and a proximal portion spaced along the helical geometric axis to define a helix length, and the control wire is configured to operatively engage the support structure to control the movement of the support structure. support between the retracted configuration and the expanded configuration.
28. The catheter apparatus of clause 27, in which the control wire is substantially aligned along the helical axis and operationally coupled to the distal end of the helical structure in such a way that the axial translation of the control wire along the axis helical controls movement of the support structure between the retracted configuration and the expanded configuration.
29. The catheter apparatus of clause 28, in which the axial translation of the control wire in the distal direction reduces the radial distance of the first and second energy supply elements from the central geometric axis.
30. The catheter apparatus of clause 29, in which the axial translation of the control wire in the distal direction increases the length of the helix and reduces the helical diameter.
31.0 catheter apparatus of clause 27, in which the helical structure is configured to rotate in relation to the control wire.
32. The catheter apparatus of clause 27, comprising a stop member disposed along the helical axis to limit axial translation of the control wire.
33. The clause 27 catheter apparatus, in which the
The control comprises a central lumen, and the catheter apparatus further comprises a guide wire disposed in the central lumen of the control wire for the location of the support structure at a target treatment site along the renal artery.
34. A catheter device, comprising:
an elongated axis that has a proximal portion and a distal portion, where the distal portion of the axis is configured for the intravascular delivery to a renal artery of a human patient;
a treatment section for the distal portion of the elongated axis and a control member slidably arranged therethrough, and a plurality of energy dispensing elements carried by the treatment section, one of which between the treatment section and the member The control section comprises a preformed helical shape and the other one between the treatment section and the control member comprises a substantially straight shape, wherein the treatment section is transformable between a substantially straight dispensing configuration and a treatment configuration with the preformed helical shape to position the energy supply elements in stable contact with a renal artery wall.
35. The clause 34 catheter apparatus, in which:
the treatment section comprises a preformed helical member that has a central lumen; and the control member comprises a stretch member configured to be received in the central lumen.
36. The clause 34 catheter apparatus, in which:
the treatment section comprises a conformable central lumen, and
171 the control member comprises a precast helical structure configured to be received in the central lumen and to give a helical shape to the treatment segment.
37. The catheter apparatus of clause 34, in which the treatment section has a first stiffness and the control member has a second stiffness greater than the first stiffness.
38. The catheter apparatus of clause 34, in which at least one of the control member or the treatment section comprises a material with shape memory.
39. The clause 34 catheter apparatus, further comprising a retractable sheath, at least partially around at least one of the control member or the treatment section, when the treatment section is in the dispensing configuration.
40. The clause 34 catheter apparatus, further comprising a dispensing guide wire removably positioned in the treatment section and configured to dispense the treatment section in the renal artery.
41. The clause 34 catheter apparatus, in which the distal portion of the elongated axis, the treatment section, and the energy delivery elements are sized and configured for intravascular delivery in the renal artery via a 6 French or smaller guide catheter .
42. A catheter device, comprising:
an elongated axis that has a proximal portion and a distal portion, where the distal portion of the axis is configured for the intravascular delivery to a renal artery of a human patient;
a precast section of the distal portion of the elongated axis, wherein the elongated rod and the precast section comprise a central lumen configured to receive a control member; and a plurality of energy dispensing elements
172 carried by the precast section, where the precast section is transformable between a low profile configuration in which the control member is positioned within the central lumen, and an expanded configuration, in which the control member is at least partially retracted from the precast section and the precast section is helically shaped to position the energy supply elements in stable contact with a renal artery wall.
43. The catheter apparatus of clause 42, in which the control member comprises a stretching member configured to be received in the central lumen, and in which, in the dispensing configuration, the stretching member confers a generally linear low profile shape to the distal portion of the elongated axis.
44. The catheter apparatus of clause 42, in which the precast section comprises a self-expanding helical structure.
45. The catheter apparatus of clause 42, further comprising a guide wire configured to dispense the precast section for the patient's renal artery.
46. The catheter apparatus of clause 45, in which the guide wire comprises the control member, and in which, in the expanded configuration, the guide wire is at least partially removed or removed from the central lumen of the precast section.
47. The catheter apparatus of clause 42, in which the pre-formed section comprises a nitinol cable.
48. The catheter apparatus of clause 42, in which the pre-shaped section is composed of a material with shape memory.
49. The catheter apparatus of clause 42, wherein the precast section comprises a plurality of external supports configured to provide a helical shape for the precast section.
173
50. The clause 42 catheter apparatus, in which the distal portion of the elongated axis, the precast section, and the energy delivery elements are sized and configured for intravascular delivery in the renal artery using a 6 French or smaller.
51.0 clause 42 catheter apparatus, further comprising a retractable sheath, at least partially around the precast section when the precast section is in the low profile configuration, where the retractable sheath is configured to make a fold transitional from a patient's aorta to the renal artery.
52. A catheter device, comprising:
an elongated axis that has a proximal portion and a distal portion, where the distal portion of the axis is configured for the intravascular delivery to a renal artery of a human patient;
a conformable portion on the distal portion of the axis and a molding member disposed through the conformable portion, wherein the conformable portion is movable between a dispensing arrangement when the molding member is removed from the central lumen, and a treatment arrangement, when the molding member is received inside the central lumen; and a plurality of electrodes carried by the conformable portion.
53. The catheter apparatus of clause 52, further comprising a dispensing guide wire configured to dispense the conformable portion in the renal artery.
54. The catheter apparatus of clause 52, in which the elongated axis comprises:
a guide wire lumen configured to receive the guide wire, and a control member lumen configured to receive the molding member, and wherein the guide wire lumen and the member lumen
174 of control fuse within the central lumen.
55. The catheter apparatus of clause 52, wherein the molding member comprises a helical structure.
56. The catheter apparatus of clause 52, further comprising a retractable molding member sheath, at least partially around the molding member and configured to compress the molding member in a generally stretched configuration when the conformable portion is in disposition low profile.
57. The catheter apparatus of clause 52, wherein the conformable portion has a first stiffness and the molding member has a second stiffness greater than the first stiffness.
25. A catheter device, comprising:
an elongated axis that has a proximal portion and a distal portion;
a treatment section in the distal portion of the elongated axis and a control member coupled to the treatment section and movable in a sliding way in relation to the treatment section; and a plurality of energy dispensing elements carried by the treatment section, where one of the treatment section and the control member comprises a preformed helical shape and the other among the treatment section and the control member comprises a substantially straight shape, and in which the treatment section and the control member are movable with respect to each other to change the treatment device between a low profile dispensing configuration and an expanded configuration with the preformed helical shape.
59. The clause 58 catheter apparatus, in which:
the treatment section comprises a pre-helical member
176 a movable moldable region between a dispensing state and a developed state, in which the plurality of energy dispensing elements is carried through the moldable region;
a control member operatively coupled to at least a portion of the therapeutic set and arranged along the central geometric axis such that the first and second energy delivery elements are axially and radially spaced from each other around the control member, and in which the proximal movement of the control member in relation to the distal portion of the therapeutic set places the therapeutic set in the dispensing state, and the distal movement of the control member in relation to the distal portion of the therapeutic set places the therapeutic set in the developed state.
65. The catheter apparatus of clause 1, wherein the control member comprises a tubular member defining a central lumen and the central lumen is configured to receive a guidewire.
66. The catheter apparatus of clause 64, additionally comprising an axis that has a lumen of guide wire in the distal portion, in which the control member is received slidingly in the lumen of the guide wire and configured to advance and retract in relation to to the therapeutic set.
67. The clause 64 catheter apparatus, wherein the therapeutic assembly comprises a preformed helical structure.
68. The catheter apparatus of clause 64 in which the control member comprises a stylus.
69. A catheter device, comprising:
an elongated tubular axis that defines at least one lumen;
a therapeutic set disposed distally from the axis
177 elongated, the therapeutic set defining a central geometric axis and having a distal portion and a proximal portion axially spaced along the central geometric axis, the therapeutic set including a plurality of energy-dispensing elements, including at least a first element energy supply and according to an energy supply element; and a mobile support member between a dispensing arrangement and a developed arrangement;
a control member coupled to the distal portion of the therapeutic set and arranged along the central geometric axis in such a way that the first and second energy delivery elements are axially and radially spaced from each other around the control member, in which distal movement the control member in relation to the elongated axis places the therapeutic set in a dispensing arrangement; and proximal movement of the control member in relation to the elongated axis places the therapeutic set in a developed arrangement, and a guide set coupled to the therapeutic set and arranged along the central geometric axis of the therapeutic set, in which the guide set comprises a tubular member that has an opening arranged in the proximal portion of the therapeutic set for the insertion and removal of a guidewire.
70. The catheter apparatus of clause 69, wherein the therapeutic set comprises a plurality of spiral members arranged around the inner member.
71.0 clause 69 catheter apparatus, in which the dispensing arrangement of the therapeutic set defines a dispensing profile of about 0.085 inches (2.16 mm).
72. The clause 69 catheter apparatus, in which a
The distal end of the elongated axis further comprises a trimmed or oblique notch dimensioned and shaped to nest with a proximal end of the control member.
73. The catheter apparatus of clause 69, in which the elongated axis comprises a first lumen and a second lumen, and in which the control member is slidably arranged in the first lumen, and a plurality of cables for dispensing elements of energy are arranged in the second lumen.
74. A catheter device for intravascular modulation of renal nerves, the catheter device comprising:
an elongated axis that has a proximal portion and a distal portion, where the distal portion of the axis is configured for the intravascular delivery of a renal artery from a human patient;
a helical structure disposed in or near the distal portion of the elongated axis, where the helical structure is configured to oscillate between a low profile configuration and a developed configuration, and at least two energy supply elements associated with the helical structure, in that the energy delivery elements are configured to thermally inhibit neural communication along the renal artery, and that the two energy delivery elements are fixed around the helical structure in such a way that in the developed configuration, the helical structure and the energy dispensing elements define a dispensing profile of 0.085 inches (2.16 mm) or less, and in which, in the developed configuration, the energy dispensing elements of the helical structure are configured to maintain stable contact with an artery wall renal.
75. The clause 74 catheter apparatus, further comprising
179 a movable control member in relation to the helical structure to change the helical structure between the low profile configuration and the developed configuration.
76. The clause 74 catheter apparatus, in which the control member defines a central lumen, and in which the central lumen is configured to receive a guidewire to locate the helical structure at a target location within a patient's renal artery .
77. The clause 74 catheter apparatus, further comprising a dispensing sheath at least partially, around the helical structure in the low profile configuration.
78. The catheter apparatus of clause 74, wherein the elongated axis comprises a lumen of the guide wire, and the catheter apparatus further comprises a guide wire positioned in the lumen of the guide wire and extending to a treatment site in the renal artery.
79. The clause 74 catheter apparatus, wherein the helical structure comprises an interlaced cable.
80. The catheter apparatus of clause 74, wherein the helical structure comprises a tubular support structure that has a central lumen.
81.0 the catheter apparatus of clause 74, in which the helical structure comprises an electrically conductive material and in which the electrically conductive material comprises a portion of the energy dispensing element.
82. The catheter apparatus of clause 81, in which the electrically conductive material is covered only in part, by an electrically insulating material.
83. A catheter device, comprising:
an elongated axis comprising an external axis and an internal axis, where the elongated axis has a proximal portion and a portion
180 distal, and in which the distal portion of the elongated axis is configured for the intravascular delivery to a renal artery of a human patient;
a treatment section on the distal part of the elongated axis, where the treatment section extends between a distal end of the external axis and a distal end of the internal axis, and where the distal end of the treatment section is slidably coupled to the end distant from the internal axis, through a double lumen glove;
a plurality of energy dispensing elements carried by the treatment section; and a precast section coupled to the treatment section, where the precast section is configured to give a shape to the treatment section, thus changing the treatment section from a stretched dispensing configuration to a configuration developed for placing the energy dispensing elements in contact with the tissue in a treatment location.
84. The clause 83 catheter apparatus, in which the treatment section also includes an insulator placed between the energy dispensing elements and the precast section to electrically insulate the energy dispensing elements from the precast section , and in which the insulator is formed from a material that allows the transfer of thermal energy between the energy supply elements and the shape memory component.
85. The catheter apparatus of clause 83, in which the insulator is formed from a thermoplastic material with ceramic filler mixed in it.
86. The clause 83 catheter apparatus, in which:
the energy supply elements are electrically connected to a power source by means of at least one wire that has a proximal end coupled to the power source and an end
181 distal coupled to the energy supply element; and the at least one wire is a bifilar wire that includes a first copper conductor, a second copper or nickel conductor, and insulation around each of the first and second conductors to electrically insulate one from the other.
87. The catheter apparatus of clause 86, in which the treatment section comprises a series of band electrodes.
88. The catheter apparatus of clause 86, in which the configuration developed from the precast section comprises a propeller.
89. The catheter apparatus of clause 83, in which the pre-formed section comprises nitinol.
90. The catheter apparatus of clause 89, in which the precast section comprises a solid wire covered by a thin layer of insulating material.
91. The catheter apparatus of clause 83, in which the pre-shaped section has a lumen sized through it to accommodate a guidewire.
92. The clause 83 catheter apparatus, in which the pre-molded section is polymeric.
93. The catheter apparatus of clause 83, in which the pre-shaped section comprises a material with shape memory that is configured to undergo a shape transformation at a shape transformation temperature between about 40 ° C and about 45 ° C.
94. The catheter apparatus of clause 83, further comprising an insulator coupled to the precast section, in which the insulator comprises a tubular sheath which has an insulating lumen.
95. The catheter apparatus of clause 94, in which a proximal end of the insulator is affixed to an internal surface of the outer sheath and the distal end of the insulator is arranged in the double-lumen sleeve.
182
96. The catheter apparatus of clause 83, additionally comprising a guide wire axis inside the double lumen sleeve.
97. A catheter device, comprising:
an elongated tubular axis that defines at least one lumen;
a therapeutic set disposed distally from the elongated axis, the therapeutic set that defines a central geometric axis and which has a distal portion and a proximal portion axially spaced along the central geometric axis, the therapeutic set including a plurality of energy delivery elements, including at least a first energy supply element and a second energy supply element; and a mobile support member between a dispensing arrangement and a developed arrangement;
a tubular axis member coupled to the distal portion of the therapeutic set and arranged along the central geometric axis such that the axial movement of the first and second energy dispensing elements of the tubular axis member in relation to the elongated axis places the therapeutic set in one of a dispensing arrangement and a developed arrangement, and a guide wire disposed inside the tubular shaft member.
98. A catheter apparatus for treating a human patient by means of renal denervation, the catheter apparatus comprising:
an elongated tubular axis;
a therapeutic set having a central geometric axis and a distal portion and a proximal portion axially spaced along the central geometric axis, the therapeutic set comprising a support structure selectively transformable between a dispensing arrangement and a developed arrangement a plurality of elements of energy dispensing
183 carried by the support structure, and a control member received slidingly on the axis and operationally coupled to a distal portion of the therapeutic set, in which the proximal movement of the control member places the therapeutic set in the developed arrangement, and distal movement of the limb control system places the therapeutic set in the dispensing arrangement.
99. The catheter apparatus of clause 98, in which the therapeutic set 10 comprises six elements of energy dispensing.
100. The clause 98 catheter apparatus, in which the elongated tubular axis and the control member define a central lumen, and in which the central lumen is configured to receive a guidewire to locate the therapeutic set at a target location within a renal artery of the patient.

权利要求:
Claims (30)
[1]
1. Catheter device, characterized by the fact that it comprises:
an elongated axis that has a proximal portion and a distal portion, where the distal portion of the axis is configured for the intravascular delivery to a renal artery of a human patient;
a treatment section for the distal portion of the elongated axis and a control member slidably arranged therethrough, and a plurality of energy dispensing elements carried by the treatment section, one of which between the treatment section and the member The control section comprises a preformed helical shape and the other of the treatment section and the control member comprises a substantially straight shape, and the treatment section is transformable between a substantially straight dispensing configuration and a treatment configuration with the preformed helical shape for positioning the energy delivery elements in stable contact with a renal artery wall.
[2]
2. Catheter apparatus according to claim 1, characterized by the fact that:
the treatment section comprises a preformed helical member that has a central lumen; and the control member comprises a stretch member configured to be received in the central lumen.
[3]
3. Catheter apparatus according to claim 1, characterized by the fact that:
the treatment section comprises a conformable central lumen, and the control member comprises a precast helical structure configured to be received in the central lumen and to give a helical shape to the treatment segment.
[4]
4. Catheter apparatus according to claim 1, characterized in that the treatment section has a first stiffness and the control member has a second stiffness greater than the stiffness.
[5]
5. Catheter apparatus according to claim 1, characterized by the fact that at least one of the control member or the treatment section comprises a material with shape memory.
[6]
6. Catheter apparatus according to claim 1, characterized in that it additionally comprises a retractable sheath, at least partially around at least one of the control member or the treatment section, when the treatment section is in the dispensing configuration.
[7]
7. Catheter apparatus according to claim 1, characterized by the fact that it additionally comprises a dispensing guide wire positioned removably in the treatment section and configured to dispense the treatment section in the renal artery.
[8]
8. Catheter apparatus according to claim 1, characterized by the fact that the distal portion of the elongated axis, the treatment section, and the energy delivery elements are sized and configured for intravascular delivery in the renal artery through a catheter guide 6 French or smaller.
[9]
9. Catheter apparatus, characterized by the fact that it comprises:
an elongated axis that has a proximal portion and a distal portion, where the distal portion of the axis is configured for the intravascular delivery to a renal artery of a human patient;
a precast section of the distal portion of the elongated axis, wherein the elongated rod and the precast section comprise a central lumen configured to receive a control member; and a plurality of energy dispensing elements carried by the precast section, wherein the precast section is transformable between a low profile configuration in which the control member is positioned within the central lumen, and an expanded configuration, in that the control member is at least partially retracted from the precast section and the precast section is helically shaped to position the energy delivery elements in stable contact with a renal artery wall.
[10]
10. Catheter apparatus according to claim 9, characterized in that the control member comprises a drawing member configured to be received in the central lumen, and in which, in the dispensing configuration, the drawing member gives a shape low profile generally linear for the distal portion of the elongated axis.
[11]
11. Catheter apparatus according to claim 9, characterized in that the precast section comprises a self-expanding helical structure.
[12]
12. Catheter device according to claim 9, characterized in that it additionally comprises a guide wire configured to dispense the precast section for the patient's renal artery.
[13]
13. Catheter apparatus according to claim 12, characterized in that the guide wire comprises the control member, and in which, in the expanded configuration, the guide wire is at least partially removed or removed from the central lumen of the pre section -framed.
[14]
14. Catheter apparatus according to claim 9, characterized in that the precast section comprises a nitinol cable.
[15]
15. Catheter apparatus according to claim 9, characterized by the fact that the precast section is composed of a material with shape memory.
[16]
16. Catheter apparatus according to claim 9, characterized in that the precast section comprises a plurality of external supports configured to provide a helical shape for the precast section.
[17]
17. Catheter apparatus according to claim 9, characterized by the fact that the distal portion of the elongated axis, the pre-molded section, and the energy delivery elements are sized and configured for intravascular delivery in the renal artery through a guide catheter 6 French or less.
[18]
18. The catheter apparatus according to claim 9, characterized by the fact that it additionally comprises a retractable sheath, at least partially around the precast section when the precast section is in the low profile configuration, in which the retractable sheath is configured to make a transitional fold from a patient's aorta to the renal artery.
[19]
19. Catheter apparatus, characterized by the fact that it comprises:
an elongated axis that has a proximal portion and a distal portion, where the distal portion of the axis is configured for the intravascular delivery to a renal artery of a human patient;
a conformable portion on the distal portion of the shaft and a molding member eliminated through the conformable portion, where the conformable portion is movable between a dispensing arrangement when the molding member is removed from the central lumen, and a treatment arrangement, when the molding member is received inside the central lumen; and a plurality of electrodes carried by the conformable portion.
[20]
20. Catheter apparatus according to claim 19, characterized in that it additionally comprises a dispensing guide wire configured to dispense the conformable portion in the renal artery.
[21]
21. The catheter apparatus according to claim 19, characterized by the fact that the elongated axis comprises:
a guide wire lumen configured to receive the guide wire, and a control member lumen configured to receive the molding member, and wherein the guide wire lumen and the control member lumen merge within the central lumen.
[22]
22. The catheter apparatus according to claim 19, characterized in that the molding member comprises a helical structure.
[23]
23. The catheter apparatus according to claim 19, characterized in that it further comprises a retractable molding member sheath, at least partly around the molding member and configured to compress the molding member in a generally stretched configuration when the conformable portion is in the low profile arrangement.
[24]
24. The catheter apparatus according to claim 19, characterized in that the conformable portion has a first stiffness and the molding member has a second stiffness greater than the first stiffness.
[25]
25. Catheter apparatus, characterized by the fact that it comprises:
an elongated axis that has a proximal portion and a distal portion;
a treatment section in the distal portion of the elongated axis and a control member coupled to the treatment section and movable in a sliding way in relation to the treatment section; and a plurality of energy dispensing elements carried by the treatment section, where one of the treatment section and the control member comprises a preformed helical shape and the other among the treatment section and the control member comprises a substantially straight shape, and in which the treatment section and the control member are movable with respect to each other to change the treatment device between a low profile dispensing configuration and an expanded configuration with the preformed helical shape.
[26]
26. Catheter apparatus according to claim 25, characterized by the fact that:
the treatment section comprises a preformed helical member that has a central lumen; and the control member comprises a stretch member configured to be received in the central lumen.
[27]
27. Catheter apparatus according to claim 25, characterized by the fact that:
the treatment section comprises a conformable central lumen, and the control member comprises a pre-shaped helical structure to be received in the central lumen and to give a helical shape to the central lumen.
[28]
28. The catheter apparatus according to claim 25, characterized by the fact that the distal portion of the elongated axis, the treatment section, and the energy delivery elements are sized and configured for intravascular delivery in a renal artery via a 6 French or smaller guide catheter.
[29]
29. The catheter apparatus according to claim 25, characterized in that it additionally comprises a retractable sheath, at least partly around at least one section of
5 treatment or the control member, when the treatment section is in the low profile dispensing configuration.
[30]
30. Catheter apparatus according to claim 25, characterized by the fact that it also comprises a dispensing guide wire positioned removably through the treatment section and configured
10 to dispense the portion conforming to a renal nerve treatment site.

类似技术:

---

公开号 | 公开日 | 专利标题

---

US11116572B2|2021-09-14|Catheter apparatuses having multi-electrode arrays for renal neuromodulation and associated systems and methods

---

EP2629690B1|2019-07-31|Catheter apparatuses having expandable mesh structures for renal neuromodulation

---

US8612022B1|2013-12-17|Neuromodulation catheters and associated systems and methods

---

AU2011239313A1|2012-05-10|Catheter apparatuses having multi-electrode arrays for renal neuromodulation and associated systems and methods

---

US20220079666A1|2022-03-17|Catheter apparatuses having multi-electrode arrays for renal neuromodulation and associated systems and methods

---

AU2015202315A1|2015-05-21|Catheter apparatuses having expandable mesh structures for renal neuromodulation and associated systems and methods

同族专利:

---

公开号 | 公开日

---

EP2632376B1|2020-02-12|

---

TW201223585A|2012-06-16|

---

CN103027745B|2016-03-16|

---

EP2632378A1|2013-09-04|

---

US20160113713A1|2016-04-28|

---

US20120143293A1|2012-06-07|

---

CN105902311B|2020-07-28|

---

US20120116382A1|2012-05-10|

---

KR20130103763A|2013-09-24|

---

US8956352B2|2015-02-17|

---

US20180228539A1|2018-08-16|

---

JP2016097310A|2016-05-30|

---

MX2013004235A|2013-05-30|

---

CN202654228U|2013-01-09|

---

WO2012061164A1|2012-05-10|

---

BR112013010007A2|2017-10-24|

---

CA2816040A1|2012-05-10|

---

JP2013540563A|2013-11-07|

---

JP2013544131A|2013-12-12|

---

TW201223583A|2012-06-16|

---

TWI586399B|2017-06-11|

---

TWI559951B|2016-12-01|

---

IL225258D0|2013-06-27|

---

KR20140022772A|2014-02-25|

---

CN103027745A|2013-04-10|

---

US11116572B2|2021-09-14|

---

BR112013010000A2|2017-10-24|

---

RU2013118108A|2014-12-10|

---

US10076382B2|2018-09-18|

---

US8998894B2|2015-04-07|

---

MX2013004437A|2013-07-17|

---

AU2011239316A1|2012-05-10|

---

RU2013123775A|2014-12-10|

---

CN105902311A|2016-08-31|

---

WO2012061161A1|2012-05-10|

---

KR101912960B1|2018-10-29|

---

IL225569D0|2013-06-27|

---

EP2632378B1|2018-10-17|

---

IL225259D0|2013-06-27|

---

CN202665687U|2013-01-16|

---

CN103027746A|2013-04-10|

---

RU2013118107A|2014-12-10|

---

CA2811264A1|2012-05-10|

---

KR20130108401A|2013-10-02|

---

AU2011239320A1|2012-05-10|

---

JP2013544133A|2013-12-12|

---

MX2013004241A|2013-05-30|

---

CA2811245A1|2012-05-10|

---

EP3100696A1|2016-12-07|

---

EP2632377B1|2020-01-15|

---

TW201223584A|2012-06-16|

---

WO2012061159A1|2012-05-10|

---

AU2011239320B2|2015-01-15|

---

CN202654229U|2013-01-09|

---

EP2632376A1|2013-09-04|

---

EP2632377A1|2013-09-04|

---

CA2811264C|2020-02-25|

---

US20120116383A1|2012-05-10|

---

CN103027747A|2013-04-10|

---

JP6148314B2|2017-06-14|

引用文献:

---

公开号 | 申请日 | 公开日 | 申请人 | 专利标题

---

---

US1031990A|1912-01-08|1912-07-09|Ralph R Essig|Toy.|

---

US1026408A|1912-01-24|1912-05-14|Alfred H Koeller|Wind-shield.|

---

GB1456509A|1973-02-20|1976-11-24|Dow Corning Ltd|Bonding silicone rubber to wood and masonry|

---

US4154246A|1977-07-25|1979-05-15|Leveen Harry H|Field intensification in radio frequency thermotherapy|

---

US4169464A|1977-12-16|1979-10-02|Cordis Corporation|Catheter for selective catheterization of aortic branches|

---

US4419819A|1982-01-29|1983-12-13|Medtronic, Inc.|Method of making biomedical lead with lobed lead anchor|

---

US4488561A|1983-06-27|1984-12-18|Medtronic, Inc.|Pacing lead with insertable memory coil|

---

EP0132344A3|1983-07-20|1986-01-22|Purdue Research Foundation|Improved catheter based cardiac output sensor|

---

US4618600A|1984-04-19|1986-10-21|Biotechnology Research Associates, J.V.|Novel polypeptide diuretic/vasodilators|

---

US4649936A|1984-10-11|1987-03-17|Case Western Reserve University|Asymmetric single electrode cuff for generation of unidirectionally propagating action potentials for collision blocking|

---

US4602624A|1984-10-11|1986-07-29|Case Western Reserve University|Implantable cuff, method of manufacture, and method of installation|

---

JPH0527556B2|1984-11-12|1993-04-21|Riso Kagaku Corp|

---

JPS6323215B2|1984-12-25|1988-05-16|Sumitomo Electric Industries|

---

US4706671A|1985-05-02|1987-11-17|Weinrib Harry P|Catheter with coiled tip|

---

US4660571A|1985-07-18|1987-04-28|Cordis Corporation|Percutaneous lead having radially adjustable electrode|

---

US4998923A|1988-08-11|1991-03-12|Advanced Cardiovascular Systems, Inc.|Steerable dilatation catheter|

---

US5449343A|1985-07-30|1995-09-12|Advanced Cardiovascular Systems, Inc.|Steerable dilatation catheter|

---

US4709698A|1986-05-14|1987-12-01|Thomas J. Fogarty|Heatable dilation catheter|

---

US4796643A|1986-09-30|1989-01-10|Telectronics N.V.|Medical electrode leads|

---

US5231995A|1986-11-14|1993-08-03|Desai Jawahar M|Method for catheter mapping and ablation|

---

US5365926A|1986-11-14|1994-11-22|Desai Jawahar M|Catheter for mapping and ablation and method therefor|

---

US4834724A|1987-04-06|1989-05-30|Geiss Alan C|Device for aspirating fluids from a body cavity or hollow organ|

---

US4781682A|1987-08-13|1988-11-01|Patel Piyush V|Catheter having support flaps and method of inserting catheter|

---

US5154705A|1987-09-30|1992-10-13|Lake Region Manufacturing Co., Inc.|Hollow lumen cable apparatus|

---

US4819661A|1987-10-26|1989-04-11|Cardiac Pacemakers, Inc.|Positive fixation cardiac electrode with drug elution capabilities|

---

US4860769A|1987-11-12|1989-08-29|Thomas J. Fogarty|Implantable defibrillation electrode|

---

US4957118A|1988-01-15|1990-09-18|Jay Erlebacher|Electrode lead|

---

US4890623A|1988-03-14|1990-01-02|C. R. Bard, Inc.|Biopotential sensing device and method for making|

---

WO1989011889A1|1988-06-06|1989-12-14|Sumitomo Electric Industries, Ltd.|Catheter|

---

GB8814898D0|1988-06-22|1988-07-27|Evans J M|Catheters & methods of manufacture|

---

EP0352955A3|1988-07-22|1990-05-09|Baxter International Inc.|Metal hot tip catheter with fused tip and temperature feedback loop|

---

US4921484A|1988-07-25|1990-05-01|Cordis Corporation|Mesh balloon catheter device|

---

US5249585A|1988-07-28|1993-10-05|Bsd Medical Corporation|Urethral inserted applicator for prostate hyperthermia|

---

US4995868A|1988-10-12|1991-02-26|Bard Limited|Catheter|

---

US4920979A|1988-10-12|1990-05-01|Huntington Medical Research Institute|Bidirectional helical electrode for nerve stimulation|

---

US4955377A|1988-10-28|1990-09-11|Lennox Charles D|Device and method for heating tissue in a patient's body|

---

US5011488A|1988-12-07|1991-04-30|Robert Ginsburg|Thrombus extraction system|

---

AU4945490A|1989-01-06|1990-08-01|Angioplasty Systems Inc.|Electrosurgical catheter for resolving atherosclerotic plaque|

---

US5779698A|1989-01-18|1998-07-14|Applied Medical Resources Corporation|Angioplasty catheter system and method for making same|

---

US4976711A|1989-04-13|1990-12-11|Everest Medical Corporation|Ablation catheter with selectively deployable electrodes|

---

SE8902630L|1989-07-31|1991-02-01|Radi Medical Systems|CATS, CONTROL AND COMBINATION THEREOF|

---

US5211651A|1989-08-18|1993-05-18|Evi Corporation|Catheter atherotome|

---

US5156610A|1989-08-18|1992-10-20|Evi Corporation|Catheter atherotome|

---

US5282484A|1989-08-18|1994-02-01|Endovascular Instruments, Inc.|Method for performing a partial atherectomy|

---

US5071424A|1989-08-18|1991-12-10|Evi Corporation|Catheter atherotome|

---

US5002067A|1989-08-23|1991-03-26|Medtronic, Inc.|Medical electrical lead employing improved penetrating electrode|

---

US5133365A|1989-09-14|1992-07-28|Cardiac Pacemakers, Inc.|Implantable tapered spiral endocardial lead for use in internal defibrillation|

---

US5016808A|1989-09-14|1991-05-21|Cardiac Pacemakers, Inc.|Implantable tapered spiral endocardial lead for use in internal defibrillation|

---

US5209723A|1990-01-08|1993-05-11|The Curators Of The University Of Missouri|Multiple lumen catheter for hemodialysis|

---

US5158564A|1990-02-14|1992-10-27|Angiomed Ag|Atherectomy apparatus|

---

US5052998A|1990-04-04|1991-10-01|Zimmon David S|Indwelling stent and method of use|

---

US5071407A|1990-04-12|1991-12-10|Schneider Inc.|Radially expandable fixation member|

---

US6623516B2|1992-08-13|2003-09-23|Mark A. Saab|Method for changing the temperature of a selected body region|

---

US5054501A|1990-05-16|1991-10-08|Brigham & Women's Hospital|Steerable guide wire for cannulation of tubular or vascular organs|

---

US5188602A|1990-07-12|1993-02-23|Interventional Thermodynamics, Inc.|Method and device for delivering heat to hollow body organs|

---

US5163928A|1991-01-07|1992-11-17|Franklin Electronic Publishers, Incorporated|Self-centering catheter|

---

US5345936A|1991-02-15|1994-09-13|Cardiac Pathways Corporation|Apparatus with basket assembly for endocardial mapping|

---

US5228442A|1991-02-15|1993-07-20|Cardiac Pathways Corporation|Method for mapping, ablation, and stimulation using an endocardial catheter|

---

US5156151A|1991-02-15|1992-10-20|Cardiac Pathways Corporation|Endocardial mapping and ablation system and catheter probe|

---

US5425364A|1991-02-15|1995-06-20|Cardiac Pathways Corporation|Flexible strip assembly without feedthrough holes and device utilizing the same|

---

US5329923A|1991-02-15|1994-07-19|Lundquist Ingemar H|Torquable catheter|

---

AU660444B2|1991-02-15|1995-06-29|Ingemar H. Lundquist|Torquable catheter and method|

---

WO1992015356A1|1991-03-01|1992-09-17|Baxter International Inc.|Cardiovascular catheter having discrete regions of varying flexibility|

---

US5188619A|1991-04-24|1993-02-23|Gene E. Myers Enterprises, Inc.|Internal thoractic artery catheter|

---

DE4113703C2|1991-04-26|1995-05-04|Thomas Osypka|Guide catheter with pre-bent end area|

---

US5330496A|1991-05-06|1994-07-19|Alferness Clifton A|Vascular catheter assembly for tissue penetration and for cardiac stimulation and methods thereof|

---

IT1245528B|1991-05-06|1994-09-29|Mini Ricerca Scient Tecnolog|CATHETER FOR ANGIOPLASTIC AND METHOD FOR ITS OBTAINING.|

---

WO1992020291A1|1991-05-24|1992-11-26|Applied Medical Resources, Inc.|Articulating tissue cutter assembly|

---

AT169233T|1991-09-05|1998-08-15|Mayo Foundation|BENDING TUBULAR DEVICE FOR MEDICAL APPLICATIONS|

---

US5741429A|1991-09-05|1998-04-21|Cardia Catheter Company|Flexible tubular device for use in medical applications|

---

US5697882A|1992-01-07|1997-12-16|Arthrocare Corporation|System and method for electrosurgical cutting and ablation|

---

US5683366A|1992-01-07|1997-11-04|Arthrocare Corporation|System and method for electrosurgical tissue canalization|

---

CA2106410C|1991-11-08|2004-07-06|Stuart D. Edwards|Ablation electrode with insulated temperature sensing elements|

---

US5628775A|1991-11-08|1997-05-13|Ep Technologies, Inc.|Flexible bond for sleeves enclosing a bendable electrode tip assembly|

---

CA2082315C|1991-11-13|1997-03-18|Harold I. Pearsall|Catheter|

---

US5358514A|1991-12-18|1994-10-25|Alfred E. Mann Foundation For Scientific Research|Implantable microdevice with self-attaching electrodes|

---

US6149620A|1995-11-22|2000-11-21|Arthrocare Corporation|System and methods for electrosurgical tissue treatment in the presence of electrically conductive fluid|

---

DE69331929T2|1992-01-22|2003-01-09|Winston Thomas R|MEDICAL CATHETER|

---

US5354297A|1992-02-14|1994-10-11|Boaz Avitall|Biplanar deflectable catheter for arrhythmogenic tissue ablation|

---

US5327905A|1992-02-14|1994-07-12|Boaz Avitall|Biplanar deflectable catheter for arrhythmogenic tissue ablation|

---

US5263493A|1992-02-24|1993-11-23|Boaz Avitall|Deflectable loop electrode array mapping and ablation catheter for cardiac chambers|

---

US5300099A|1992-03-06|1994-04-05|Urologix, Inc.|Gamma matched, helical dipole microwave antenna|

---

US5239999A|1992-03-27|1993-08-31|Cardiac Pathways Corporation|Helical endocardial catheter probe|

---

AU4026793A|1992-04-10|1993-11-18|Cardiorhythm|Shapable handle for steerable electrode catheter|

---

AU4280393A|1992-04-10|1993-11-18|Cardiorhythm|Intracardiac electrical potential reference catheter|

---

US5318525A|1992-04-10|1994-06-07|Medtronic Cardiorhythm|Steerable electrode catheter|

---

WO1993020886A1|1992-04-13|1993-10-28|Ep Technologies, Inc.|Articulated systems for cardiac ablation|

---

US5345031A|1992-04-16|1994-09-06|The Trustees Of Princeton University|Reduction of aromatic halide content|

---

US5300068A|1992-04-21|1994-04-05|St. Jude Medical, Inc.|Electrosurgical apparatus|

---

US5263492A|1992-04-30|1993-11-23|Guy Voyce|Recording goniometer|

---

US5324284A|1992-06-05|1994-06-28|Cardiac Pathways, Inc.|Endocardial mapping and ablation system utilizing a separately controlled ablation catheter and method|

---

DE9390317U1|1992-06-26|1995-02-09|Schneider Usa Inc|Catheter with expandable wire mesh tip|

---

US5772590A|1992-06-30|1998-06-30|Cordis Webster, Inc.|Cardiovascular catheter with laterally stable basket-shaped electrode array with puller wire|

---

US5484400A|1992-08-12|1996-01-16|Vidamed, Inc.|Dual channel RF delivery system|

---

US5542916A|1992-08-12|1996-08-06|Vidamed, Inc.|Dual-channel RF power delivery system|

---

WO1994007446A1|1992-10-05|1994-04-14|Boston Scientific Corporation|Device and method for heating tissue|

---

US5399164A|1992-11-02|1995-03-21|Catheter Imaging Systems|Catheter having a multiple durometer|

---

WO1994010922A1|1992-11-13|1994-05-26|Ep Technologies, Inc.|Cardial ablation systems using temperature monitoring|

---

US5441483A|1992-11-16|1995-08-15|Avitall; Boaz|Catheter deflection control|

---

CA2109980A1|1992-12-01|1994-06-02|Mir A. Imran|Steerable catheter with adjustable bend location and/or radius and method|

---

SE9203733D0|1992-12-11|1992-12-11|Siemens Elema Ab|defibrillation|

---

US5256141A|1992-12-22|1993-10-26|Nelson Gencheff|Biological material deployment method and apparatus|

---

US5387233A|1993-01-11|1995-02-07|Incontrol, Inc.|Intravenous cardiac lead with improved fixation and method|

---

IT1266217B1|1993-01-18|1996-12-27|Xtrode Srl|ELECTROCATHETER FOR MAPPING AND INTERVENTION ON HEART CAVITIES.|

---

US5358493A|1993-02-18|1994-10-25|Scimed Life Systems, Inc.|Vascular access catheter and methods for manufacture thereof|

---

US6719755B2|1996-10-22|2004-04-13|Epicor Medical, Inc.|Methods and devices for ablation|

---

US6311692B1|1996-10-22|2001-11-06|Epicor, Inc.|Apparatus and method for diagnosis and therapy of electrophysiological disease|

---

US20040260278A1|1996-10-22|2004-12-23|Anderson Scott C.|Apparatus and method for ablating tissue|

---

US7052493B2|1996-10-22|2006-05-30|Epicor Medical, Inc.|Methods and devices for ablation|

---

US5476495A|1993-03-16|1995-12-19|Ep Technologies, Inc.|Cardiac mapping and ablation systems|

---

US5636634A|1993-03-16|1997-06-10|Ep Technologies, Inc.|Systems using guide sheaths for introducing, deploying, and stabilizing cardiac mapping and ablation probes|

---

WO1994021168A1|1993-03-16|1994-09-29|Ep Technologies, Inc.|Cardiac mapping and ablation systems|

---

JP3345786B2|1993-03-17|2002-11-18|ジャパンゴアテックス株式会社|Flexible tube and method of manufacturing the same|

---

US5383856A|1993-03-19|1995-01-24|Bersin; Robert M.|Helical spiral balloon catheter|

---

US5523092A|1993-04-14|1996-06-04|Emory University|Device for local drug delivery and methods for using the same|

---

US5716410A|1993-04-30|1998-02-10|Scimed Life Systems, Inc.|Temporary stent and method of use|

---

US5611777A|1993-05-14|1997-03-18|C.R. Bard, Inc.|Steerable electrode catheter|

---

US5693082A|1993-05-14|1997-12-02|Fidus Medical Technology Corporation|Tunable microwave ablation catheter system and method|

---

EP0706345B1|1993-07-01|2003-02-19|Boston Scientific Limited|Imaging, electrical potential sensing, and ablation catheters|

---

US5860974A|1993-07-01|1999-01-19|Boston Scientific Corporation|Heart ablation catheter with expandable electrode and method of coupling energy to an electrode on a catheter shaft|

---

US5487757A|1993-07-20|1996-01-30|Medtronic Cardiorhythm|Multicurve deflectable catheter|

---

US5545200A|1993-07-20|1996-08-13|Medtronic Cardiorhythm|Steerable electrophysiology catheter|

---

US5634899A|1993-08-20|1997-06-03|Cortrak Medical, Inc.|Simultaneous cardiac pacing and local drug delivery method|

---

US5405374A|1993-08-25|1995-04-11|Medtronic, Inc.|Transvenous defibrillation lead and method of use|

---

US5807395A|1993-08-27|1998-09-15|Medtronic, Inc.|Method and apparatus for RF ablation and hyperthermia|

---

US5980516A|1993-08-27|1999-11-09|Medtronic, Inc.|Method and apparatus for R-F ablation|

---

US5680860A|1994-07-07|1997-10-28|Cardiac Pathways Corporation|Mapping and/or ablation catheter with coilable distal extremity and method for using same|

---

US5427118A|1993-10-04|1995-06-27|Baxter International Inc.|Ultrasonic guidewire|

---

JPH09509069A|1993-10-14|1997-09-16|イーピーテクノロジーズ，インコーポレイテッド|Electrode element for damage pattern formation|

---

US5582609A|1993-10-14|1996-12-10|Ep Technologies, Inc.|Systems and methods for forming large lesions in body tissue using curvilinear electrode elements|

---

WO1995010322A1|1993-10-15|1995-04-20|Ep Technologies, Inc.|Creating complex lesion patterns in body tissue|

---

WO1995010225A1|1993-10-15|1995-04-20|Ep Technologies, Inc.|Multiple electrode element for mapping and ablating|

---

US5545193A|1993-10-15|1996-08-13|Ep Technologies, Inc.|Helically wound radio-frequency emitting electrodes for creating lesions in body tissue|

---

US5575810A|1993-10-15|1996-11-19|Ep Technologies, Inc.|Composite structures and methods for ablating tissue to form complex lesion patterns in the treatment of cardiac conditions and the like|

---

CA2102250A1|1993-11-02|1995-05-03|Robert S. Schwartz|Flexible catheter guidewire|

---

US5571147A|1993-11-02|1996-11-05|Sluijter; Menno E.|Thermal denervation of an intervertebral disc for relief of back pain|

---

US5575766A|1993-11-03|1996-11-19|Daig Corporation|Process for the nonsurgical mapping and treatment of atrial arrhythmia using catheters guided by shaped guiding introducers|

---

US5564440A|1993-11-03|1996-10-15|Daig Corporation|Method for mopping and/or ablation of anomalous conduction pathways|

---

US5690611A|1994-07-08|1997-11-25|Daig Corporation|Process for the treatment of atrial arrhythima using a catheter guided by shaped giding introducers|

---

US5497774A|1993-11-03|1996-03-12|Daig Corporation|Guiding introducer for left atrium|

---

US5672174A|1995-08-15|1997-09-30|Rita Medical Systems, Inc.|Multiple antenna ablation apparatus and method|

---

US5507743A|1993-11-08|1996-04-16|Zomed International|Coiled RF electrode treatment apparatus|

---

US5599346A|1993-11-08|1997-02-04|Zomed International, Inc.|RF treatment system|

---

DE69419172T2|1993-11-10|2000-02-24|Medtronic Cardiorhythm San Jos|ELECTRODE ARRANGEMENT FOR CATHETER|

---

US5730127A|1993-12-03|1998-03-24|Avitall; Boaz|Mapping and ablation catheter system|

---

US5487385A|1993-12-03|1996-01-30|Avitall; Boaz|Atrial mapping and ablation catheter system|

---

US6099524A|1994-01-28|2000-08-08|Cardiac Pacemakers, Inc.|Electrophysiological mapping and ablation catheter and method|

---

US5462545A|1994-01-31|1995-10-31|New England Medical Center Hospitals, Inc.|Catheter electrodes|

---

US5505201A|1994-04-20|1996-04-09|Case Western Reserve University|Implantable helical spiral cuff electrode|

---

US6283960B1|1995-10-24|2001-09-04|Oratec Interventions, Inc.|Apparatus for delivery of energy to a surgical site|

---

US5882333A|1994-05-13|1999-03-16|Cardima, Inc.|Catheter with deflectable distal section|

---

US5617854A|1994-06-22|1997-04-08|Munsif; Anand|Shaped catheter device and method|

---

US6405732B1|1994-06-24|2002-06-18|Curon Medical, Inc.|Method to treat gastric reflux via the detection and ablation of gastro-esophageal nerves and receptors|

---

US6273886B1|1998-02-19|2001-08-14|Curon Medical, Inc.|Integrated tissue heating and cooling apparatus|

---

US6009877A|1994-06-24|2000-01-04|Edwards; Stuart D.|Method for treating a sphincter|

---

WO1996000036A1|1994-06-27|1996-01-04|Ep Technologies, Inc.|System for controlling tissue ablation using temperature sensors|

---

US5810802A|1994-08-08|1998-09-22|E.P. Technologies, Inc.|Systems and methods for controlling tissue ablation using multiple temperature sensing elements|

---

US5476498A|1994-08-15|1995-12-19|Incontrol, Inc.|Coronary sinus channel lead and method|

---

US5609151A|1994-09-08|1997-03-11|Medtronic, Inc.|Method for R-F ablation|

---

US5519172A|1994-09-13|1996-05-21|W. L. Gore & Associates, Inc.|Jacket material for protection of electrical conductors|

---

US5545475A|1994-09-20|1996-08-13|W. L. Gore & Associates|Microfiber-reinforced porous polymer film and a method for manufacturing the same and composites made thereof|

---

US5509909A|1994-10-06|1996-04-23|Moy; Grant G.|Bent chest tube assembly|

---

US5885278A|1994-10-07|1999-03-23|E.P. Technologies, Inc.|Structures for deploying movable electrode elements|

---

US5722401A|1994-10-19|1998-03-03|Cardiac Pathways Corporation|Endocardial mapping and/or ablation catheter probe|

---

US5554114A|1994-10-20|1996-09-10|Micro Therapeutics, Inc.|Infusion device with preformed shape|

---

GB9501424D0|1995-01-25|1995-03-15|Carrie Len|Epidural catheter|

---

IT1278372B1|1995-02-15|1997-11-20|Sorin Biomedica Cardio Spa|CATHETER, PARTICULARLY FOR THE TREATMENT OF HEART ARRHYTHMIA.|

---

DE19507929A1|1995-02-24|1996-09-05|Biotronik Mess & Therapieg|Electrode system for measuring the monophasic action potential|

---

US6436056B1|1996-02-28|2002-08-20|Boston Scientific Corporation|Polymeric implements for torque transmission|

---

CA2212808C|1995-02-28|2007-12-04|James C. Wang|Polymeric implements for torque transmission|

---

EP0814729B1|1995-03-10|2000-08-09|Impra, Inc.|Endoluminal encapsulated stent and methods of manufacture|

---

US5676662A|1995-03-17|1997-10-14|Daig Corporation|Ablation catheter|

---

NL1000183C2|1995-04-20|1996-10-22|Clemens Josephus Jacobs|Catheter.|

---

WO1996034646A1|1995-05-01|1996-11-07|Medtronic Cardiorhythm|Dual curve ablation catheter and method|

---

US5681280A|1995-05-02|1997-10-28|Heart Rhythm Technologies, Inc.|Catheter control system|

---

EP1011495B1|1995-05-04|2005-11-09|Sherwood Services AG|Cool-tip electrode thermosurgery system|

---

US5899892A|1996-05-31|1999-05-04|Scimed Life Systems, Inc.|Catheter having distal fiber braid|

---

AU5956896A|1995-06-02|1996-12-18|Guided Medical Systems, Inc.|Composite guide catheter of adjustable shape|

---

US6090104A|1995-06-07|2000-07-18|Cordis Webster, Inc.|Catheter with a spirally wound flat ribbon electrode|

---

US6322558B1|1995-06-09|2001-11-27|Engineering & Research Associates, Inc.|Apparatus and method for predicting ablation depth|

---

US5673695A|1995-08-02|1997-10-07|Ep Technologies, Inc.|Methods for locating and ablating accessory pathways in the heart|

---

US5827272A|1995-08-07|1998-10-27|Medtronic Cardiorhythm|Simplified torquing electrode catheter|

---

US5707400A|1995-09-19|1998-01-13|Cyberonics, Inc.|Treating refractory hypertension by nerve stimulation|

---

US6283951B1|1996-10-11|2001-09-04|Transvascular, Inc.|Systems and methods for delivering drugs to selected locations within the body|

---

US5700282A|1995-10-13|1997-12-23|Zabara; Jacob|Heart rhythm stabilization using a neurocybernetic prosthesis|

---

US5843050A|1995-11-13|1998-12-01|Micro Therapeutics, Inc.|Microcatheter|

---

US5823955A|1995-11-20|1998-10-20|Medtronic Cardiorhythm|Atrioventricular valve tissue ablation catheter and method|

---

SE9504333D0|1995-12-04|1995-12-04|Pacesetter Ab|Guidewire assembly|

---

US5931830A|1995-12-07|1999-08-03|Sarcos L.C.|Hollow coil guide wire apparatus for catheters|

---

DE19546941A1|1995-12-15|1997-06-19|Biotronik Mess & Therapieg|Single electrode for two-chamber pacemaker systems, especially for DDD pacemaker systems|

---

US5895398A|1996-02-02|1999-04-20|The Regents Of The University Of California|Method of using a clot capture coil|

---

US5695506A|1996-02-06|1997-12-09|Devices For Vascular Intervention|Catheter device with a flexible housing|

---

WO1997029800A1|1996-02-13|1997-08-21|Cardiovascular Dynamics, Inc.|Hybrid catheter shaft|

---

US5807249A|1996-02-16|1998-09-15|Medtronic, Inc.|Reduced stiffness, bidirectionally deflecting catheter assembly|

---

US6036687A|1996-03-05|2000-03-14|Vnus Medical Technologies, Inc.|Method and apparatus for treating venous insufficiency|

---

US6032077A|1996-03-06|2000-02-29|Cardiac Pathways Corporation|Ablation catheter with electrical coupling via foam drenched with a conductive fluid|

---

US5755760A|1996-03-11|1998-05-26|Medtronic, Inc.|Deflectable catheter|

---

US5997526A|1996-03-25|1999-12-07|The Uab Research Foundation|Shape memory catheter|

---

JP3529537B2|1996-03-25|2004-05-24|テルモ株式会社|Electrode catheter|

---

WO1997036541A1|1996-04-02|1997-10-09|Cordis Webster, Inc.|Electrophysiology catheter with a bullseye electrode|

---

US5755761A|1996-04-26|1998-05-26|Pharmatarget, Inc.|Atrial pacing catheter and method having multiple electrodes in the right atrium and coronary sinus|

---

US6042578A|1996-05-13|2000-03-28|Schneider Inc.|Catheter reinforcing braids|

---

US6546280B2|1996-06-18|2003-04-08|Cook Incorporated|Indwelling catheter|

---

US6223070B1|1998-03-16|2001-04-24|Cook, Inc.|Indwelling catheter|

---

US5727555A|1996-06-18|1998-03-17|Cook Incorporated|Indwelling catheter|

---

US5827242A|1996-06-21|1998-10-27|Medtronic, Inc.|Reinforced catheter body and method for its fabrication|

---

US5899890A|1996-06-21|1999-05-04|Medtronic, Inc.|Flow-directed catheter system and method of use|

---

US5944710A|1996-06-24|1999-08-31|Genetronics, Inc.|Electroporation-mediated intravascular delivery|

---

US6161048A|1997-06-26|2000-12-12|Radionics, Inc.|Method and system for neural tissue modification|

---

US6246912B1|1996-06-27|2001-06-12|Sherwood Services Ag|Modulated high frequency tissue modification|

---

US5983141A|1996-06-27|1999-11-09|Radionics, Inc.|Method and apparatus for altering neural tissue function|

---

US5882346A|1996-07-15|1999-03-16|Cardiac Pathways Corporation|Shapable catheter using exchangeable core and method of use|

---

US5972019A|1996-07-25|1999-10-26|Target Therapeutics, Inc.|Mechanical clot treatment device|

---

US5826576A|1996-08-08|1998-10-27|Medtronic, Inc.|Electrophysiology catheter with multifunction wire and method for making|

---

US5800494A|1996-08-20|1998-09-01|Fidus Medical Technology Corporation|Microwave ablation catheters having antennas with distal fire capabilities|

---

US5697928A|1996-09-23|1997-12-16|Uab Research Foundation|Cardic electrode catheter|

---

US5891134A|1996-09-24|1999-04-06|Goble; Colin|System and method for applying thermal energy to tissue|

---

NL1004160C2|1996-10-01|1998-04-02|Cordis Europ|Ablation catheter with inductively heated heater.|

---

CA2377583A1|1999-07-19|2001-01-25|Epicor, Inc.|Apparatus and method for ablating tissue|

---

US5827268A|1996-10-30|1998-10-27|Hearten Medical, Inc.|Device for the treatment of patent ductus arteriosus and method of using the device|

---

US5893885A|1996-11-01|1999-04-13|Cordis Webster, Inc.|Multi-electrode ablation catheter|

---

US6091995A|1996-11-08|2000-07-18|Surx, Inc.|Devices, methods, and systems for shrinking tissues|

---

US5941893A|1996-12-02|1999-08-24|Angiotrax, Inc.|Apparatus for transluminally performing surgery|

---

US5954719A|1996-12-11|1999-09-21|Irvine Biomedical, Inc.|System for operating a RF ablation generator|

---

US5910129A|1996-12-19|1999-06-08|Ep Technologies, Inc.|Catheter distal assembly with pull wires|

---

US6076012A|1996-12-19|2000-06-13|Ep Technologies, Inc.|Structures for supporting porous electrode elements|

---

US6048329A|1996-12-19|2000-04-11|Ep Technologies, Inc.|Catheter distal assembly with pull wires|

---

SE9700373L|1997-02-04|1998-07-13|Stig Bengmark|Probe for providing fluid communication with the small intestine|

---

US5730741A|1997-02-07|1998-03-24|Eclipse Surgical Technologies, Inc.|Guided spiral catheter|

---

US5873865A|1997-02-07|1999-02-23|Eclipse Surgical Technologies, Inc.|Spiral catheter with multiple guide holes|

---

JP2002515801A|1997-02-12|2002-05-28|オーレイテックインターヴェンションズインコーポレイテッド|Concave tip for arthroscopic surgery|

---

US6355016B1|1997-03-06|2002-03-12|Medtronic Percusurge, Inc.|Catheter core wire|

---

US6086582A|1997-03-13|2000-07-11|Altman; Peter A.|Cardiac drug delivery system|

---

US5954761A|1997-03-25|1999-09-21|Intermedics Inc.|Implantable endocardial lead assembly having a stent|

---

JP3274384B2|1997-03-31|2002-04-15|株式会社パイオラックス|Indwelling catheter and its insertion device|

---

WO1998043530A1|1997-03-31|1998-10-08|Biosense Inc.|Deflectable catheter|

---

US5879295A|1997-04-02|1999-03-09|Medtronic, Inc.|Enhanced contact steerable bowing electrode catheter assembly|

---

US5876373A|1997-04-04|1999-03-02|Eclipse Surgical Technologies, Inc.|Steerable catheter|

---

US5972026A|1997-04-07|1999-10-26|Broncus Technologies, Inc.|Bronchial stenter having diametrically adjustable electrodes|

---

US7027869B2|1998-01-07|2006-04-11|Asthmatx, Inc.|Method for treating an asthma attack|

---

US5865815A|1997-04-25|1999-02-02|Contimed, Inc.|Prostatic obstruction relief catheter|

---

US6078840A|1997-04-30|2000-06-20|Medtronic, Inc.|Medical electrical lead having improved fixation|

---

AU7274598A|1997-04-30|1998-11-24|Latis, Inc.|Light delivery catheter and method for the use thereof|

---

WO1998050098A1|1997-05-08|1998-11-12|Microvena Corporation|Improved multi-durometer catheter|

---

US5952671A|1997-05-09|1999-09-14|Micron Technology, Inc.|Small electrode for a chalcogenide switching device and method for fabricating same|

---

JP2002515813A|1997-05-23|2002-05-28|バイオセンス・インコーポレイテッド|Catheter with obliquely extending lumen|

---

US5895378A|1997-05-29|1999-04-20|Target Therapeutics, Inc.|Flow-directed catheter having multiple tapers and radio-opaque markers|

---

US6152912A|1997-06-10|2000-11-28|Target Therapeutics, Inc.|Optimized high performance spiral-wound vascular catheter|

---

US5951539A|1997-06-10|1999-09-14|Target Therpeutics, Inc.|Optimized high performance multiple coil spiral-wound vascular catheter|

---

WO1999000060A1|1997-06-26|1999-01-07|Advanced Coronary Intervention|Electrosurgical catheter for resolving obstructions by radio frequency ablation|

---

US6565562B1|1997-06-27|2003-05-20|Baylis Medical Company Inc.|Method for the radio frequency perforation and the enlargement of a body tissue|

---

US6024740A|1997-07-08|2000-02-15|The Regents Of The University Of California|Circumferential ablation device assembly|

---

US6164283A|1997-07-08|2000-12-26|The Regents Of The University Of California|Device and method for forming a circumferential conduction block in a pulmonary vein|

---

US6500174B1|1997-07-08|2002-12-31|Atrionix, Inc.|Circumferential ablation device assembly and methods of use and manufacture providing an ablative circumferential band along an expandable member|

---

US6117101A|1997-07-08|2000-09-12|The Regents Of The University Of California|Circumferential ablation device assembly|

---

US6012457A|1997-07-08|2000-01-11|The Regents Of The University Of California|Device and method for forming a circumferential conduction block in a pulmonary vein|

---

US6514249B1|1997-07-08|2003-02-04|Atrionix, Inc.|Positioning system and method for orienting an ablation element within a pulmonary vein ostium|

---

WO1999002096A1|1997-07-08|1999-01-21|The Regents Of The University Of California|Circumferential ablation device assembly and method|

---

US6869431B2|1997-07-08|2005-03-22|Atrionix, Inc.|Medical device with sensor cooperating with expandable member|

---

WO1999006095A2|1997-07-29|1999-02-11|Ep Technologies, Inc.|Improved catheter distal end assemblies|

---

US6125302A|1997-09-02|2000-09-26|Advanced Bionics Corporation|Precurved modiolar-hugging cochlear electrode|

---

US6078841A|1998-03-27|2000-06-20|Advanced Bionics Corporation|Flexible positioner for use with implantable cochlear electrode array|

---

WO1999011313A1|1997-09-04|1999-03-11|Alcon Laboratories, Inc.|Flexible tube with circular grooves of varying width and depth|

---

EP0900547B1|1997-09-05|2007-05-30|Biosense Webster, Inc.|Steerable catheter for detecting and revascularizing ischemic myocardial tissue|

---

US5871531A|1997-09-25|1999-02-16|Medtronic, Inc.|Medical electrical lead having tapered spiral fixation|

---

US5891114A|1997-09-30|1999-04-06|Target Therapeutics, Inc.|Soft-tip high performance braided catheter|

---

US6048338A|1997-10-15|2000-04-11|Scimed Life Systems, Inc.|Catheter with spiral cut transition member|

---

WO1999020324A1|1997-10-20|1999-04-29|Bersin Robert D|Helical spiral balloon catheter|

---

US6156046A|1997-11-07|2000-12-05|Prolifix Medical, Inc.|Methods and systems for treating obstructions in a body lumen|

---

EP1030610A1|1997-11-07|2000-08-30|Prolifix Medical, Inc.|Methods and systems for treating obstructions in a body lumen|

---

US6120500A|1997-11-12|2000-09-19|Daig Corporation|Rail catheter ablation and mapping system|

---

US6120476A|1997-12-01|2000-09-19|Cordis Webster, Inc.|Irrigated tip catheter|

---

US5935124A|1997-12-02|1999-08-10|Cordis Webster, Inc.|Tip electrode with multiple temperature sensors|

---

US6917834B2|1997-12-03|2005-07-12|Boston Scientific Scimed, Inc.|Devices and methods for creating lesions in endocardial and surrounding tissue to isolate focal arrhythmia substrates|

---

US6273876B1|1997-12-05|2001-08-14|Intratherapeutics, Inc.|Catheter segments having circumferential supports with axial projection|

---

US6280441B1|1997-12-15|2001-08-28|Sherwood Services Ag|Apparatus and method for RF lesioning|

---

KR19990072499A|1998-02-19|1999-09-27|리페르트 존|Catheter guidewire apparatus with location specific flexibility|

---

US6142993A|1998-02-27|2000-11-07|Ep Technologies, Inc.|Collapsible spline structure using a balloon as an expanding actuator|

---

US6308090B1|1998-03-09|2001-10-23|Irvine Biomedical, Inc.|Devices and methods for coronary sinus mapping|

---

US5951471A|1998-03-09|1999-09-14|Irvine Biomedical, Inc.|Catheter-based coronary sinus mapping and ablation|

---

US6132456A|1998-03-10|2000-10-17|Medtronic, Inc.|Arrangement for implanting an endocardial cardiac lead|

---

US6071729A|1998-04-02|2000-06-06|Jeffries; Thomas W.|Disruption of the cytochrome C gene in xylose-fermenting yeast|

---

US6314325B1|1998-04-07|2001-11-06|William R. Fitz|Nerve hyperpolarization method and apparatus for pain relief|

---

WO1999052421A1|1998-04-13|1999-10-21|Prolifix Medical, Inc.|Guidewire for precision catheter positioning|

---

US6219577B1|1998-04-14|2001-04-17|Global Vascular Concepts, Inc.|Iontophoresis, electroporation and combination catheters for local drug delivery to arteries and other body tissues|

---

US6064902A|1998-04-16|2000-05-16|C.R. Bard, Inc.|Pulmonary vein ablation catheter|

---

US5968085A|1998-04-20|1999-10-19|Medtronic, Inc.|Pacing lead with integral guidance using ultrasound|

---

EP0951920B1|1998-04-22|2004-10-20|BIOTRONIK Mess- und Therapiegeräte GmbH & Co Ingenieurbüro Berlin|Electrode cable for attachement to a vessel wall|

---

US6511492B1|1998-05-01|2003-01-28|Microvention, Inc.|Embolectomy catheters and methods for treating stroke and other small vessel thromboembolic disorders|

---

US6592581B2|1998-05-05|2003-07-15|Cardiac Pacemakers, Inc.|Preformed steerable catheter with movable outer sleeve and method for use|

---

US6146381A|1998-05-05|2000-11-14|Cardiac Pacemakers, Inc.|Catheter having distal region for deflecting axial forces|

---

US6096036A|1998-05-05|2000-08-01|Cardiac Pacemakers, Inc.|Steerable catheter with preformed distal shape and method for use|

---

US6074339A|1998-05-07|2000-06-13|Medtronic Ave, Inc.|Expandable braid device and method for radiation treatment|

---

US6327505B1|1998-05-07|2001-12-04|Medtronic, Inc.|Method and apparatus for rf intraluminal reduction and occlusion|

---

US6231572B1|1998-05-29|2001-05-15|Applied Medical Resources Corporation|Electrosurgical catheter apparatus and method|

---

US6094596A|1998-06-19|2000-07-25|Angeron Corporation|Transvenous defibrillation lead system for use in middle cardiac vein|

---

WO1999065561A1|1998-06-19|1999-12-23|Cordis Webster, Inc.|Method and apparatus for transvascular treatment of tachycardia and fibrillation|

---

US6322559B1|1998-07-06|2001-11-27|Vnus Medical Technologies, Inc.|Electrode catheter having coil structure|

---

US6302903B1|1998-07-07|2001-10-16|Medtronic, Inc.|Straight needle apparatus for creating a virtual electrode used for the ablation of tissue|

---

US6179860B1|1998-08-19|2001-01-30|Artemis Medical, Inc.|Target tissue localization device and method|

---

US6610083B2|1998-08-24|2003-08-26|Radiant Medical, Inc.|Multiple lumen heat exchange catheters|

---

US6228109B1|1998-08-31|2001-05-08|Lily Chen Tu|Methods for treating atherosclerosis and vulnerable plaques|

---

US6123702A|1998-09-10|2000-09-26|Scimed Life Systems, Inc.|Systems and methods for controlling power in an electrosurgical probe|

---

US6053913A|1998-09-10|2000-04-25|Tu; Lily Chen|Rapid exchange stented balloon catheter having ablation capabilities|

---

US6102890A|1998-10-23|2000-08-15|Scimed Life Systems, Inc.|Catheter having improved proximal shaft design|

---

US10967045B2|1998-11-02|2021-04-06|Secretary of State for Health and Social Care|Multicomponent meningococcal vaccine|

---

US6701176B1|1998-11-04|2004-03-02|Johns Hopkins University School Of Medicine|Magnetic-resonance-guided imaging, electrophysiology, and ablation|

---

US7313444B2|1998-11-20|2007-12-25|Pacesetter, Inc.|Self-anchoring coronary sinus lead|

---

AT267032T|1998-12-14|2004-06-15|Tre Esse Progettazione Biomedi|CATHETER SYSTEM FOR IMPLEMENTING INTRAMYOCARDIAL THERAPEUTIC TREATMENT|

---

US6210408B1|1999-02-24|2001-04-03|Scimed Life Systems, Inc.|Guide wire system for RF recanalization of vascular blockages|

---

DE60021063T2|1999-03-09|2006-05-11|Thermage, Inc., Hayward|TREATMENT FOR TREATMENT OF TISSUE|

---

US6129750A|1999-03-23|2000-10-10|Cardiac Pacemakers, Inc.|Fixation mechanism for a coronary venous pacing lead|

---

US6161049A|1999-03-26|2000-12-12|Urologix, Inc.|Thermal therapy catheter|

---

US6702811B2|1999-04-05|2004-03-09|Medtronic, Inc.|Ablation catheter assembly with radially decreasing helix and method of use|

---

US20010007070A1|1999-04-05|2001-07-05|Medtronic, Inc.|Ablation catheter assembly and method for isolating a pulmonary vein|

---

US20050010095A1|1999-04-05|2005-01-13|Medtronic, Inc.|Multi-purpose catheter apparatus and method of use|

---

US6325797B1|1999-04-05|2001-12-04|Medtronic, Inc.|Ablation catheter and method for isolating a pulmonary vein|

---

US20040044350A1|1999-04-09|2004-03-04|Evalve, Inc.|Steerable access sheath and methods of use|

---

US6939346B2|1999-04-21|2005-09-06|Oratec Interventions, Inc.|Method and apparatus for controlling a temperature-controlled probe|

---

WO2000066211A1|1999-04-30|2000-11-09|Usaminanotechnology, Inc.|Catheter and guide wire|

---

WO2000066017A1|1999-05-04|2000-11-09|Curon Medical, Inc.|Electrodes for creating lesions in tissue regions at or near a sphincter|

---

US6758830B1|1999-05-11|2004-07-06|Atrionix, Inc.|Catheter positioning system|

---

EP3369453B1|1999-05-11|2020-03-18|Atrionix, Inc.|Medical device positioning system including a balloon anchor wire|

---

EP1244392A1|1999-09-28|2002-10-02|Novasys Medical, Inc.|Treatment of tissue by application of energy and drugs|

---

US6692490B1|1999-05-18|2004-02-17|Novasys Medical, Inc.|Treatment of urinary incontinence and other disorders by application of energy and drugs|

---

DE29909082U1|1999-05-25|1999-07-22|Starck|Stimulation, sensing and / or defibrillation electrode and balloon catheter for inserting the electrode|

---

US7171263B2|1999-06-04|2007-01-30|Impulse Dynamics Nv|Drug delivery device|

---

US6890329B2|1999-06-15|2005-05-10|Cryocath Technologies Inc.|Defined deflection structure|

---

US6546272B1|1999-06-24|2003-04-08|Mackinnon Nicholas B.|Apparatus for in vivo imaging of the respiratory tract and other internal organs|

---

US7840278B1|1999-06-25|2010-11-23|Puskas John D|Devices and methods for vagus nerve stimulation|

---

US6620172B1|1999-07-01|2003-09-16|Medsource Technologies, Inc.|Entraining biological calculi|

---

US6364904B1|1999-07-02|2002-04-02|Scimed Life Systems, Inc.|Helically formed stent/graft assembly|

---

US6605061B2|1999-07-14|2003-08-12|Tricardia, L.L.C.|Catheter for drug injection in cardiovascular system|

---

US6625195B1|1999-07-20|2003-09-23|Joseph Reid Henrichs|Vertical cavity surface emitting laser that uses intracavity degenerate four wave mixing to produce phase-conjugated and distortion free collimated laser light|

---

US6508804B2|1999-07-28|2003-01-21|Scimed Life Systems, Inc.|Catheter having continuous lattice and coil reinforcement|

---

US6611720B2|1999-08-12|2003-08-26|Irvine Biomedical Inc.|High torque catheter possessing multi-directional deflectability and methods thereof|

---

US6442415B1|1999-08-12|2002-08-27|Magnetic Moments, L.L.C.|Contrast-enhanced coronary artery and coronary artery bypass graft imaging using an aortic root catheter injection with either magnetic resonance angiography or computed tomographic angiography|

---

US6246914B1|1999-08-12|2001-06-12|Irvine Biomedical, Inc.|High torque catheter and methods thereof|

---

US6385472B1|1999-09-10|2002-05-07|Stereotaxis, Inc.|Magnetically navigable telescoping catheter and method of navigating telescoping catheter|

---

US6607520B2|1999-09-15|2003-08-19|The General Hospital Corporation|Coiled ablation catheter system|

---

US6749560B1|1999-10-26|2004-06-15|Circon Corporation|Endoscope shaft with slotted tube|

---

US6613046B1|1999-11-22|2003-09-02|Scimed Life Systems, Inc.|Loop structures for supporting diagnostic and therapeutic elements in contact with body tissue|

---

US6529756B1|1999-11-22|2003-03-04|Scimed Life Systems, Inc.|Apparatus for mapping and coagulating soft tissue in or around body orifices|

---

US6745080B2|1999-11-22|2004-06-01|Scimed Life Systems, Inc.|Helical and pre-oriented loop structures for supporting diagnostic and therapeutic elements in contact with body tissue|

---

US6542781B1|1999-11-22|2003-04-01|Scimed Life Systems, Inc.|Loop structures for supporting diagnostic and therapeutic elements in contact with body tissue|

---

EP2712567A1|1999-11-22|2014-04-02|Boston Scientific Limited|Loop structures for supporting diagnostic and therapeutic elements in contact with body tissue|

---

US6711444B2|1999-11-22|2004-03-23|Scimed Life Systems, Inc.|Methods of deploying helical diagnostic and therapeutic element supporting structures within the body|

---

US6454775B1|1999-12-06|2002-09-24|Bacchus Vascular Inc.|Systems and methods for clot disruption and retrieval|

---

DE10042330A1|1999-12-22|2002-03-14|Hans Sachse|Small intestine probe, wall-reinforced|

---

US8140170B2|2005-09-12|2012-03-20|The Cleveland Clinic Foundation|Method and apparatus for renal neuromodulation|

---

US6885888B2|2000-01-20|2005-04-26|The Cleveland Clinic Foundation|Electrical stimulation of the sympathetic nerve chain|

---

US6628976B1|2000-01-27|2003-09-30|Biosense Webster, Inc.|Catheter having mapping assembly|

---

US6859431B1|2000-01-28|2005-02-22|Ciena Corporation|System and method for calculating protection routes in a network prior to failure|

---

US6514226B1|2000-02-10|2003-02-04|Chf Solutions, Inc.|Method and apparatus for treatment of congestive heart failure by improving perfusion of the kidney|

---

US6540734B1|2000-02-16|2003-04-01|Advanced Cardiovascular Systems, Inc.|Multi-lumen extrusion tubing|

---

US6770070B1|2000-03-17|2004-08-03|Rita Medical Systems, Inc.|Lung treatment apparatus and method|

---

US20010031981A1|2000-03-31|2001-10-18|Evans Michael A.|Method and device for locating guidewire and treating chronic total occlusions|

---

US6652517B1|2000-04-25|2003-11-25|Uab Research Foundation|Ablation catheter, system, and method of use thereof|

---

AU6682401A|2000-06-13|2001-12-24|Atrionix Inc|Surgical ablation probe for forming a circumferential lesion|

---

EP2275175B1|2000-07-13|2016-08-24|ReCor Medical, Inc.|Thermal treatment apparatus with ultrasonic energy application|

---

US6482221B1|2000-08-21|2002-11-19|Counter Clockwise, Inc.|Manipulatable delivery catheter for occlusive devices |

---

US6584362B1|2000-08-30|2003-06-24|Cardiac Pacemakers, Inc.|Leads for pacing and/or sensing the heart from within the coronary veins|

---

US6656195B2|2000-09-22|2003-12-02|Medtronic Xomed, Inc.|Flexible inner tubular members and rotary tissue cutting instruments having flexible inner tubular members|

---

US6985774B2|2000-09-27|2006-01-10|Cvrx, Inc.|Stimulus regimens for cardiovascular reflex control|

---

US6522926B1|2000-09-27|2003-02-18|Cvrx, Inc.|Devices and methods for cardiovascular reflex control|

---

US7158832B2|2000-09-27|2007-01-02|Cvrx, Inc.|Electrode designs and methods of use for cardiovascular reflex control devices|

---

US6845267B2|2000-09-28|2005-01-18|Advanced Bionics Corporation|Systems and methods for modulation of circulatory perfusion by electrical and/or drug stimulation|

---

US7306591B2|2000-10-02|2007-12-11|Novasys Medical, Inc.|Apparatus and methods for treating female urinary incontinence|

---

US6640120B1|2000-10-05|2003-10-28|Scimed Life Systems, Inc.|Probe assembly for mapping and ablating pulmonary vein tissue and method of using same|

---

US6926669B1|2000-10-10|2005-08-09|Medtronic, Inc.|Heart wall ablation/mapping catheter and method|

---

US6802857B1|2000-10-11|2004-10-12|Uab Research Foundation|MRI stent|

---

US7104987B2|2000-10-17|2006-09-12|Asthmatx, Inc.|Control system and process for application of energy to airway walls and other mediums|

---

US7198635B2|2000-10-17|2007-04-03|Asthmatx, Inc.|Modification of airways by application of energy|

---

US6616624B1|2000-10-30|2003-09-09|Cvrx, Inc.|Systems and method for controlling renovascular perfusion|

---

US6579308B1|2000-11-28|2003-06-17|Scimed Life Systems, Inc.|Stent devices with detachable distal or proximal wires|

---

US6676657B2|2000-12-07|2004-01-13|The United States Of America As Represented By The Department Of Health And Human Services|Endoluminal radiofrequency cauterization system|

---

US6554827B2|2000-12-11|2003-04-29|Scimed Life Systems, Inc.|Radio frequency ablation system|

---

US20020087151A1|2000-12-29|2002-07-04|Afx, Inc.|Tissue ablation apparatus with a sliding ablation instrument and method|

---

US6527739B1|2000-12-29|2003-03-04|Advanced Cardiovascular Systems, Inc.|Spiraled balloon arrangement for treatment of a tortuous vessel|

---

WO2002054941A2|2001-01-11|2002-07-18|Rita Medical Systems Inc|Bone-treatment instrument and method|

---

US6480747B2|2001-01-16|2002-11-12|Quetzal Biomedical, Inc.|Cardiac electrode catheter and method of manufacturing same|

---

US6451045B1|2001-02-22|2002-09-17|Alsius Corporation|Heat exchange catheter having a helically wrapped heat exchanger|

---

US6564096B2|2001-02-28|2003-05-13|Robert A. Mest|Method and system for treatment of tachycardia and fibrillation|

---

DE10114725A1|2001-03-21|2002-09-26|Biotronik Mess & Therapieg|Intravascular lead|

---

US6648883B2|2001-04-26|2003-11-18|Medtronic, Inc.|Ablation system and method of use|

---

US6663627B2|2001-04-26|2003-12-16|Medtronic, Inc.|Ablation system and method of use|

---

US7959626B2|2001-04-26|2011-06-14|Medtronic, Inc.|Transmural ablation systems and methods|

---

JP4279559B2|2001-04-27|2009-06-17|シー・アール・バード・インコーポレーテッド|Electrophysiological catheter for mapping and / or ablation|

---

US6909920B2|2001-04-27|2005-06-21|Medtronic, Inc.|System and method for positioning an implantable medical device within a body|

---

US6972016B2|2001-05-01|2005-12-06|Cardima, Inc.|Helically shaped electrophysiology catheter|

---

US6585718B2|2001-05-02|2003-07-01|Cardiac Pacemakers, Inc.|Steerable catheter with shaft support system for resisting axial compressive loads|

---

US20020169444A1|2001-05-08|2002-11-14|Mest Robert A.|Catheter having continuous braided electrode|

---

WO2002089908A1|2001-05-10|2002-11-14|Super Dimension Ltd.|Steerable multiple electrode catheter and method|

---

US6716207B2|2001-05-22|2004-04-06|Scimed Life Systems, Inc.|Torqueable and deflectable medical device shaft|

---

JP4257199B2|2001-07-05|2009-04-22|プリシジョンバスキュラーシステムズ，インコーポレイテッド|Soft tip medical device capable of torsion|

---

US6738674B2|2001-07-25|2004-05-18|Oscor Inc.|Implantable coronary sinus lead with mapping capabilities|

---

US20030050635A1|2001-08-22|2003-03-13|Csaba Truckai|Embolization systems and techniques for treating tumors|

---

US7778703B2|2001-08-31|2010-08-17|Bio Control Medical Ltd.|Selective nerve fiber stimulation for treating heart conditions|

---

WO2003024309A2|2001-09-19|2003-03-27|Urologix, Inc.|Microwave ablation device|

---

US6850801B2|2001-09-26|2005-02-01|Cvrx, Inc.|Mapping methods for cardiovascular reflex control devices|

---

JP3607231B2|2001-09-28|2005-01-05|有限会社日本エレクテル|High frequency heating balloon catheter|

---

US7517349B2|2001-10-22|2009-04-14|Vnus Medical Technologies, Inc.|Electrosurgical instrument and method|

---

US6614658B2|2001-11-05|2003-09-02|International Business Machines Corporation|Flexible cable stiffener for an optical transceiver|

---

CA2468531C|2001-11-29|2010-06-01|Medwaves, Inc.|Radio-frequency-based catheter system with improved deflection and steering mechanisms|

---

US20070066972A1|2001-11-29|2007-03-22|Medwaves, Inc.|Ablation catheter apparatus with one or more electrodes|

---

EP1453425B1|2001-12-03|2006-03-08|Ekos Corporation|Catheter with multiple ultrasound radiating members|

---

US20030125790A1|2001-12-27|2003-07-03|Vitaly Fastovsky|Deployment device, system and method for medical implantation|

---

US7488338B2|2001-12-27|2009-02-10|Boston Scientific Scimed, Inc.|Catheter having an improved torque transmitting shaft|

---

US6893436B2|2002-01-03|2005-05-17|Afx, Inc.|Ablation instrument having a flexible distal portion|

---

US6817999B2|2002-01-03|2004-11-16|Afx, Inc.|Flexible device for ablation of biological tissue|

---

US6486679B1|2002-01-21|2002-11-26|Kenneth David Holt|Wide-band ratiometric radio frequency bridge|

---

US7967816B2|2002-01-25|2011-06-28|Medtronic, Inc.|Fluid-assisted electrosurgical instrument with shapeable electrode|

---

US6814733B2|2002-01-31|2004-11-09|Biosense, Inc.|Radio frequency pulmonary vein isolation|

---

US7311705B2|2002-02-05|2007-12-25|Medtronic, Inc.|Catheter apparatus for treatment of heart arrhythmia|

---

WO2006020920A2|2003-01-29|2006-02-23|Medtronic, Inc.|Catheter apparatus for treatment of heart arrhythmia|

---

US7236821B2|2002-02-19|2007-06-26|Cardiac Pacemakers, Inc.|Chronically-implanted device for sensing and therapy|

---

ITBS20020039U1|2002-03-20|2003-09-22|Fogazzi Di Venturelli Andrea &|CATHETER WITH FLEXIBLE COOLED ELECTRODE|

---

US6736835B2|2002-03-21|2004-05-18|Depuy Acromed, Inc.|Early intervention spinal treatment methods and devices for use therein|

---

AU2008205550B2|2002-03-22|2012-11-01|Cardinal Health 529, Llc|Rapid-exchange balloon catheter shaft and method|

---

US7520863B2|2002-03-22|2009-04-21|Cordis Corporation|Guidewire with deflectable tip having improved torque characteristics|

---

WO2003082080A2|2002-03-27|2003-10-09|Cvrx, Inc.|Electrode structures and methods for their use in cardiovascular reflex control|

---

US20040147903A1|2002-04-05|2004-07-29|Lucas Latini|Microcatheter having tip relief region|

---

US8150520B2|2002-04-08|2012-04-03|Ardian, Inc.|Methods for catheter-based renal denervation|

---

US8131371B2|2002-04-08|2012-03-06|Ardian, Inc.|Methods and apparatus for monopolar renal neuromodulation|

---

US7617005B2|2002-04-08|2009-11-10|Ardian, Inc.|Methods and apparatus for thermally-induced renal neuromodulation|

---

US8347891B2|2002-04-08|2013-01-08|Medtronic Ardian Luxembourg S.A.R.L.|Methods and apparatus for performing a non-continuous circumferential treatment of a body lumen|

---

US8145317B2|2002-04-08|2012-03-27|Ardian, Inc.|Methods for renal neuromodulation|

---

EP2218479A3|2006-06-28|2013-06-05|Medtronic Ardian Luxembourg S.à.r.l.|Methods and systems for thermally-induced renal neuromodulation|

---

US8150519B2|2002-04-08|2012-04-03|Ardian, Inc.|Methods and apparatus for bilateral renal neuromodulation|

---

US20070129761A1|2002-04-08|2007-06-07|Ardian, Inc.|Methods for treating heart arrhythmia|

---

US7162303B2|2002-04-08|2007-01-09|Ardian, Inc.|Renal nerve stimulation method and apparatus for treatment of patients|

---

US7653438B2|2002-04-08|2010-01-26|Ardian, Inc.|Methods and apparatus for renal neuromodulation|

---

EP1496956B1|2002-04-11|2011-04-06|Medtronic Vascular, Inc.|Devices for transluminal or transthoracic interstitial electrode placement|

---

DE10218427A1|2002-04-24|2003-11-06|Biotronik Mess & Therapieg|Ablation device for cardiac tissue, in particular for creating a circular lesion around a vascular mouth in the heart|

---

AUPS226402A0|2002-05-13|2002-06-13|Advanced Metal Coatings Pty Limited|An ablation catheter|

---

US6746474B2|2002-05-31|2004-06-08|Vahid Saadat|Apparatus and methods for cooling a region within the body|

---

US6748953B2|2002-06-11|2004-06-15|Scimed Life Systems, Inc.|Method for thermal treatment of type II endoleaks in arterial aneurysms|

---

JP3813112B2|2002-06-26|2006-08-23|テルモ株式会社|Catheter and medical tubing|

---

US7115134B2|2002-07-22|2006-10-03|Chambers Technology, Llc.|Catheter with flexible tip and shape retention|

---

CA2493013C|2002-07-25|2011-07-19|Boston Scientific Limited|Medical device for navigation through anatomy and method of making same|

---

US7058456B2|2002-08-09|2006-06-06|Concentric Medical, Inc.|Methods and devices for changing the shape of a medical device|

---

US6780183B2|2002-09-16|2004-08-24|Biosense Webster, Inc.|Ablation catheter having shape-changing balloon|

---

US7282213B2|2002-09-30|2007-10-16|Medtronic, Inc.|Method for applying a drug coating to a medical device|

---

US6871085B2|2002-09-30|2005-03-22|Medtronic, Inc.|Cardiac vein lead and guide catheter|

---

US20050033137A1|2002-10-25|2005-02-10|The Regents Of The University Of Michigan|Ablation catheters and methods for their use|

---

US20040082947A1|2002-10-25|2004-04-29|The Regents Of The University Of Michigan|Ablation catheters|

---

WO2004039273A2|2002-10-31|2004-05-13|C.R. Bard, Inc.|Electrophysiology catheter with biased tip|

---

DE10252325B4|2002-11-11|2012-10-25|Admedes Schuessler Gmbh|Radiofrequency thermal ablation probe and method of making the same|

---

US20050004515A1|2002-11-15|2005-01-06|Hart Charles C.|Steerable kink resistant sheath|

---

US7404824B1|2002-11-15|2008-07-29|Advanced Cardiovascular Systems, Inc.|Valve aptation assist device|

---

ITBS20020107A1|2002-11-25|2004-05-26|Invatec Srl|METAL TUBE WITH AT LEAST ONE PART OF LENGTH WITH VARIABLE FLEXIBILITY.|

---

DE10257146A1|2002-12-06|2004-06-24|Admedes Schuessler Gmbh|Thermal ablation probe for minimal invasive body tissue high frequency thermal treatment has temperature sensor on star shaped flexible arms with adjustable protrusion from insulating sheath|

---

US7890188B2|2002-12-19|2011-02-15|Cardiac Pacemakers, Inc.|Implantable lead for septal placement of electrode with fixation mechanism in the pulmonary artery|

---

US6945956B2|2002-12-23|2005-09-20|Medtronic, Inc.|Steerable catheter|

---

US6847848B2|2003-01-07|2005-01-25|Mmtc, Inc|Inflatable balloon catheter structural designs and methods for treating diseased tissue of a patient|

---

US6960207B2|2003-01-21|2005-11-01|St Jude Medical, Daig Division, Inc.|Ablation catheter having a virtual electrode comprising portholes and a porous conductor|

---

US7013169B2|2003-01-27|2006-03-14|Cardiac Pacemakers, Inc.|Dual steer preshaped catheter|

---

US6941953B2|2003-02-20|2005-09-13|Medwaves, Inc.|Preformed catheter set for use with a linear ablation system to produce ablation lines in the left and right atrium for treatment of atrial fibrillation|

---

US6923808B2|2003-02-24|2005-08-02|Boston Scientific Scimed, Inc.|Probes having helical and loop shaped inflatable therapeutic elements|

---

US7097643B2|2003-03-03|2006-08-29|Sinus Rhythm Technologies, Inc.|Electrical block positioning devices and methods of use therefor|

---

US7276062B2|2003-03-12|2007-10-02|Biosence Webster, Inc.|Deflectable catheter with hinge|

---

US7293562B2|2003-03-27|2007-11-13|Cierra, Inc.|Energy based devices and methods for treatment of anatomic tissue defects|

---

US6939348B2|2003-03-27|2005-09-06|Cierra, Inc.|Energy based devices and methods for treatment of patent foramen ovale|

---

US7186251B2|2003-03-27|2007-03-06|Cierra, Inc.|Energy based devices and methods for treatment of patent foramen ovale|

---

US7001369B2|2003-03-27|2006-02-21|Scimed Life Systems, Inc.|Medical device|

---

US7597704B2|2003-04-28|2009-10-06|Atritech, Inc.|Left atrial appendage occlusion device with active expansion|

---

US7221979B2|2003-04-30|2007-05-22|Medtronic, Inc.|Methods and apparatus for the regulation of hormone release|

---

JP4212949B2|2003-05-06|2009-01-21|朝日インテック株式会社|Chemical injection device|

---

WO2004105807A2|2003-05-27|2004-12-09|Venture Manufacturing, Llc|Balloon centered radially expanding ablation device|

---

US8177779B2|2004-06-02|2012-05-15|Boston Scientific Scimed, Inc.|Controllable pressure cryogenic balloon treatment system and method|

---

US7149574B2|2003-06-09|2006-12-12|Palo Alto Investors|Treatment of conditions through electrical modulation of the autonomic nervous system|

---

US7789877B2|2003-07-02|2010-09-07|St. Jude Medical, Atrial Fibrillation Division, Inc.|Ablation catheter electrode arrangement|

---

US7670335B2|2003-07-21|2010-03-02|Biosense Webster, Inc.|Ablation device with spiral array ultrasound transducer|

---

US7763012B2|2003-09-02|2010-07-27|St. Jude Medical, Cardiology Division, Inc.|Devices and methods for crossing a chronic total occlusion|

---

DE202004021943U1|2003-09-12|2013-05-13|Vessix Vascular, Inc.|Selectable eccentric remodeling and / or ablation of atherosclerotic material|

---

US9713730B2|2004-09-10|2017-07-25|Boston Scientific Scimed, Inc.|Apparatus and method for treatment of in-stent restenosis|

---

US7435248B2|2003-09-26|2008-10-14|Boston Scientific Scimed, Inc.|Medical probes for creating and diagnosing circumferential lesions within or around the ostium of a vessel|

---

US7416549B2|2003-10-10|2008-08-26|Boston Scientific Scimed, Inc.|Multi-zone bipolar ablation probe assembly|

---

US7480532B2|2003-10-22|2009-01-20|Cvrx, Inc.|Baroreflex activation for pain control, sedation and sleep|

---

US7254451B2|2003-11-20|2007-08-07|Medtronic, Inc.|Implantable lead including sensor|

---

CN1882288A|2003-11-25|2006-12-20|导管治疗有限公司|A modular catheter|

---

US8460286B2|2004-01-16|2013-06-11|St. Jude Medical, Atrial Fibrillation Division, Inc.|Conforming electrode|

---

AU2005207078B2|2004-01-26|2011-03-17|Cathrx Ltd|A catheter assembly with an adjustable loop|

---

US7637903B2|2004-02-09|2009-12-29|Cryocor, Inc.|Catheter articulation segment with alternating cuts|

---

US7231260B2|2004-05-06|2007-06-12|Boston Scientific Scimed, Inc.|Intravascular self-anchoring electrode body with arcuate springs, spring loops, or arms|

---

US7285116B2|2004-05-15|2007-10-23|Irvine Biomedical Inc.|Non-contact tissue ablation device and methods thereof|

---

WO2005113057A1|2004-05-17|2005-12-01|C. R. Bard, Inc.|Articulated catheter|

---

US20060004346A1|2004-06-17|2006-01-05|Begg John D|Bend relief|

---

NZ552920A|2004-08-04|2009-12-24|Intergraph Software Tech Co|Method of preparing a composite image with non-uniform resolution real-time composite image comparator|

---

JPWO2006016481A1|2004-08-10|2008-05-01|株式会社カネカ|Medical catheter tube and manufacturing method thereof|

---

US20060041881A1|2004-08-19|2006-02-23|Adkasthala Bheema P|Universal upgrade architecture|

---

WO2006031541A1|2004-09-09|2006-03-23|Vnus Medical Technologies, Inc.|Methods and apparatus for treatment of hollow anatomical structures|

---

US7542808B1|2004-09-17|2009-06-02|Cardiac Pacemakers, Inc.|Lead and catheter assembly|

---

US7458971B2|2004-09-24|2008-12-02|Boston Scientific Scimed, Inc.|RF ablation probe with unibody electrode element|

---

US20060074403A1|2004-09-29|2006-04-06|Nasser Rafiee|Curved catheter comprising a solid-walled metal tube with varying stiffness|

---

US7524318B2|2004-10-28|2009-04-28|Boston Scientific Scimed, Inc.|Ablation probe with flared electrodes|

---

WO2006052940A2|2004-11-05|2006-05-18|Asthmatx, Inc.|Medical device with procedure improvement features|

---

WO2006052905A2|2004-11-08|2006-05-18|Cardima, Inc.|System and method for performing ablation and other medical procedures using an electrode array with flex circuit|

---

EP1656963B1|2004-11-10|2007-11-21|Creganna Technologies Limited|Stent delivery catheter assembly|

---

JP2008520364A|2004-11-17|2008-06-19|バイオセンス・ウェブスター・インコーポレイテッド|Real-time evaluation system for tissue ablation|

---

US7989042B2|2004-11-24|2011-08-02|Boston Scientific Scimed, Inc.|Medical devices with highly flexible coated hypotube|

---

WO2006065926A1|2004-12-15|2006-06-22|Cook Incorporated|Multifilar cable catheter|

---

US7402151B2|2004-12-17|2008-07-22|Biocardia, Inc.|Steerable guide catheters and methods for their use|

---

US8983582B2|2004-12-20|2015-03-17|Advanced Cardiovascular Systems, Inc.|Methods and apparatuses for positioning within an internal channel|

---

US20060135953A1|2004-12-22|2006-06-22|Wlodzimierz Kania|Tissue ablation system including guidewire with sensing element|

---

US20060174129A1|2005-01-31|2006-08-03|Cyril Brignone|Authentication method and system for tagged items|

---

US8007440B2|2005-02-08|2011-08-30|Volcano Corporation|Apparatus and methods for low-cost intravascular ultrasound imaging and for crossing severe vascular occlusions|

---

AU2006220221A1|2005-03-02|2006-09-08|Cathrx Ltd|A heat treatment catheter|

---

CN2782017Y|2005-03-08|2006-05-24|深圳市惠泰医疗器械有限公司|Electrical physiological electrode conduit|

---

WO2006105121A2|2005-03-28|2006-10-05|Minnow Medical, Llc|Intraluminal electrical tissue characterization and tuned rf energy for selective treatment of atheroma and other target tissues|

---

US7727187B2|2005-04-04|2010-06-01|Cook Incorporated|Scored catheter device|

---

US7806871B2|2005-05-09|2010-10-05|Boston Scientific Scimed, Inc.|Method and device for tissue removal and for delivery of a therapeutic agent or bulking agent|

---

US7646544B2|2005-05-14|2010-01-12|Batchko Robert G|Fluidic optical devices|

---

WO2007117359A2|2006-02-21|2007-10-18|Worley Seth J|Coronary sinus lead for pacing the left atrium|

---

US7850685B2|2005-06-20|2010-12-14|Medtronic Ablation Frontiers Llc|Ablation catheter|

---

US8465451B2|2005-06-22|2013-06-18|Covidien Lp|Methods and apparatus for introducing tumescent fluid to body tissue|

---

US7717853B2|2005-06-24|2010-05-18|Henry Nita|Methods and apparatus for intracranial ultrasound delivery|

---

EP3434232A1|2005-06-29|2019-01-30|ZOLL Circulation, Inc.|Devices, systems and methods for rapid endovascular cooling|

---

KR100721402B1|2005-07-07|2007-05-23|와이더댄 주식회사|Cell broadcasting service system using digital multimedia broadcasting and method of cell broadcasting service therefor|

---

US7390894B2|2005-07-07|2008-06-24|Mayo Foundation For Medical Education And Research|Glutathione S-transferase sequence variants|

---

AU2006268238A1|2005-07-11|2007-01-18|Medtronic Ablation Frontiers Llc|Low power tissue ablation system|

---

US7623899B2|2005-09-16|2009-11-24|Biosense Webster, Inc.|Catheter with flexible pre-shaped tip section|

---

US7647124B2|2005-11-15|2010-01-12|Medtronic, Inc.|Delivery catheter|

---

US7729782B2|2005-11-15|2010-06-01|Medtronic, Inc.|Delivery catheter|

---

WO2007059277A1|2005-11-16|2007-05-24|William Cook Europe Aps|Cannula|

---

US20070156114A1|2005-12-29|2007-07-05|Worley Seth J|Deflectable catheter with a flexibly attached tip section|

---

US7993334B2|2005-12-29|2011-08-09|Boston Scientific Scimed, Inc.|Low-profile, expanding single needle ablation probe|

---

US7620451B2|2005-12-29|2009-11-17|Ardian, Inc.|Methods and apparatus for pulsed electric field neuromodulation via an intra-to-extravascular approach|

---

US20070225781A1|2006-03-21|2007-09-27|Nidus Medical, Llc|Apparatus and methods for altering temperature in a region within the body|

---

US7747334B2|2006-03-23|2010-06-29|Cardiac Pacemakers, Inc.|Left ventricular lead shapes|

---

US7579550B2|2006-03-31|2009-08-25|Boston Scientific Scimed, Inc.|Flexible device shaft with angled spiral wrap|

---

US8246574B2|2006-04-21|2012-08-21|Abbott Laboratories|Support catheter|

---

US8019435B2|2006-05-02|2011-09-13|Boston Scientific Scimed, Inc.|Control of arterial smooth muscle tone|

---

US8977333B2|2006-05-08|2015-03-10|Cathrx Ltd|Shape-imparting mechanisms for catheter assemblies|

---

EP1857134A1|2006-05-15|2007-11-21|JOANNEUM RESEARCH Forschungsgesellschaft mbH|Catheter having an oblong slit|

---

US20070265667A1|2006-05-15|2007-11-15|Dirk Muessig|Semi-automatic atrial defibrillation system, implantable atrial defibrillator and portable communication device|

---

CA2652089A1|2006-05-19|2007-11-29|Conmed Endoscopic Technologies, Inc.|Steerable medical instrument|

---

US8103356B2|2006-05-23|2012-01-24|Vertech, Inc.|High frequency epidural neuromodulation catheter without needle for effectuating RF treatment|

---

AU2007261046A1|2006-06-20|2007-12-27|Aortx, Inc.|Torque shaft and torque drive|

---

US7708704B2|2006-07-31|2010-05-04|Codman & Shurtleff, Pc|Interventional medical device component having an interrupted spiral section and method of making the same|

---

US20080064957A1|2006-09-07|2008-03-13|Spence Paul A|Ultrasonic implant, systems and methods related to diverting material in blood flow away from the head|

---

US7785289B2|2006-10-17|2010-08-31|Boston Scientific Scimed, Inc.|Catheter with flexible, non-kinking elongate member|

---

EP2954868A1|2006-10-18|2015-12-16|Vessix Vascular, Inc.|Tuned rf energy and electrical tissue characterization for selective treatment of target tissues|

---

US8317773B2|2006-11-07|2012-11-27|Angio Dynamics, Inc.|Catheter with open faced sloped end portion|

---

US8915926B2|2006-11-08|2014-12-23|Advanced Bionics Ag|Pre-curved electrode array loading tools|

---

WO2008064399A1|2006-11-28|2008-06-05|Cathrx Ltd|Catheter steering/insertion mechanism|

---

AU2007231733B2|2006-11-28|2014-03-13|Cathrx Ltd|A catheter steering system|

---

US7993481B2|2006-12-28|2011-08-09|St. Jude Medical, Atrial Fibrillation Division, Inc.|Catheter with embedded components and method of its manufacture|

---

US8043288B2|2006-12-28|2011-10-25|St. Jude Medical, Atrial Fibrillation Division, Inc.|Virtual electrode ablation catheter with electrode tip and variable radius capability actuated with at least one rack and pinion mechanisms|

---

US20080183265A1|2007-01-30|2008-07-31|Cardiac Pacemakers, Inc.|Transvascular lead with proximal force relief|

---

WO2008101244A2|2007-02-18|2008-08-21|Via Biomedical, Inc.|Guiding catheter support devices and methods|

---

JP2010525913A|2007-05-09|2010-07-29|コーニンクレッカフィリップスエレクトロニクスエヌヴィ|Sensor probe for measuring physical properties inside the body lumen|

---

US8103359B2|2007-05-17|2012-01-24|Cardiac Pacemakers, Inc.|Systems and methods for fixating transvenously implanted medical devices|

---

US8630704B2|2007-06-25|2014-01-14|Cardiac Pacemakers, Inc.|Neural stimulation with respiratory rhythm management|

---

US7863897B2|2007-09-07|2011-01-04|The General Hospital Corporation|Method and apparatus for characterizing the temporal resolution of an imaging device|

---

US8475449B2|2007-12-10|2013-07-02|Medtronic Ablation Frontiers Llc|RF energy delivery system and method|

---

US20090157048A1|2007-12-18|2009-06-18|Boston Scientific Scimed, Inc.|Spiral cut hypotube|

---

US8118809B2|2007-12-21|2012-02-21|St. Jude Medical, Atrial Fibrillation Division, Inc.|Flexible conductive polymer electrode and method for ablation|

---

WO2009121017A1|2008-03-27|2009-10-01|The Regents Of The University Of California|Balloon catheter for reducing restenosis via irreversible electroporation|

---

US8401650B2|2008-04-10|2013-03-19|Electrocore Llc|Methods and apparatus for electrical treatment using balloon and electrode|

---

JP5345678B2|2008-05-15|2013-11-20|ボストンサイエンティフィックサイムド，インコーポレイテッド|A device that adjusts the cryogenic ablation area by treating the tissue with cryogenic ablation|

---

US8437832B2|2008-06-06|2013-05-07|Biosense Webster, Inc.|Catheter with bendable tip|

---

US8100859B2|2008-06-24|2012-01-24|Cook Medical Technologies Llc|Bent obturator|

---

US8123739B2|2008-08-19|2012-02-28|Cook Medical Technologies Llc|Drainage catheter and method for catheterizing a patient|

---

US10842555B2|2008-08-20|2020-11-24|Prostacare Pty Ltd|Catheter for treating tissue with non-thermal ablation|

---

US20100069882A1|2008-09-18|2010-03-18|Boston Scientific Scimed, Inc.|Medical device with preferential bending|

---

AU2009310635B2|2008-10-31|2015-02-12|Cathrx Ltd|A catheter assembly|

---

US8720448B2|2008-11-07|2014-05-13|Hansen Medical, Inc.|Sterile interface apparatus|

---

US20150105659A1|2008-11-11|2015-04-16|Covidien Lp|Energy delivery device and methods of use|

---

US20160374748A9|2008-11-11|2016-12-29|Covidien Lp|Energy Delivery Device and Methods of Use|

---

US8317810B2|2008-12-29|2012-11-27|St. Jude Medical, Atrial Fibrillation Division, Inc.|Tissue puncture assemblies and methods for puncturing tissue|

---

US8475450B2|2008-12-30|2013-07-02|Biosense Webster, Inc.|Dual-purpose lasso catheter with irrigation|

---

US20100168739A1|2008-12-31|2010-07-01|Ardian, Inc.|Apparatus, systems, and methods for achieving intravascular, thermally-induced renal neuromodulation|

---

US8652129B2|2008-12-31|2014-02-18|Medtronic Ardian Luxembourg S.A.R.L.|Apparatus, systems, and methods for achieving intravascular, thermally-induced renal neuromodulation|

---

EP2395933B1|2009-02-12|2016-05-04|UMC Utrecht Holding B.V.|Ablation catheter for electrically isolating cardiac tissue|

---

JP5784506B2|2009-02-20|2015-09-24|ボストン サイエンティフィック サイムド，インコーポレイテッドＢｏｓｔｏｎ Ｓｃｉｅｎｔｉｆｉｃ Ｓｃｉｍｅｄ，Ｉｎｃ．|Manipulable catheter having a transition region with intermediate stiffness|

---

US8929969B2|2009-04-14|2015-01-06|Medtronic Ablation Frontiers Llc|Catheter assembly and associated method|

---

US20120035615A1|2009-05-22|2012-02-09|Advanced Bionics, Llc|Composite Stylet|

---

US20100312056A1|2009-06-03|2010-12-09|Gyrus, ACMI, Inc.|Endoscope shaft|

---

CA2764859C|2009-06-24|2018-09-25|Shifamed, Llc|Steerable medical delivery devices and methods of use|

---

US20110028962A1|2009-07-31|2011-02-03|Randell Werneth|Adjustable pulmonary vein ablation catheter|

---

WO2011015218A1|2009-08-06|2011-02-10|Ls Medcap Gmbh|Catheter with two fenestrations|

---

WO2011019838A2|2009-08-14|2011-02-17|Boston Scientific Scimed, Inc.|Systems and methods for making and using medical ablation systems having mapping catheters with improved anchoring ability|

---

CN201469401U|2009-08-21|2010-05-19|刘小青|Spiral renal-artery-around renal sympathetic nerve radio-frequency ablation electrode catheter|

---

US9439721B2|2009-08-25|2016-09-13|Medtronic Ablation Frontiers Llc|Bi-modal linear and loop ablation catheter, and method|

---

US9387035B2|2009-08-25|2016-07-12|Medtronic Ablation Frontiers Llc|Bi-modal catheter steering mechanism|

---

EP2496165B1|2009-11-04|2017-01-11|Emcision Limited|Lumenal remodelling device|

---

US8376991B2|2009-11-09|2013-02-19|St. Jude Medical, Atrial Fibrillation Division, Inc.|Device for reducing axial shortening of catheter or sheath due to repeated deflection|

---

CN106618731B|2009-11-11|2020-08-07|努瓦拉公司|Systems, devices, and methods for treating tissue and controlling stenosis|

---

US8920415B2|2009-12-16|2014-12-30|Biosense Webster Ltd.|Catheter with helical electrode|

---

US8608735B2|2009-12-30|2013-12-17|Biosense Webster Ltd.|Catheter with arcuate end section|

---

US20110263921A1|2009-12-31|2011-10-27|Anthony Vrba|Patterned Denervation Therapy for Innervated Renal Vasculature|

---

CA2792153C|2010-03-23|2018-05-15|Boston Scientific Neuromodulation Corporation|Helical radial spacing of contacts on a cylindrical lead|

---

CA2793737A1|2010-03-24|2011-09-29|Shifamed Holdings, Llc|Intravascular tissue disruption|

---

US20110264086A1|2010-04-14|2011-10-27|Frank Ingle|Renal artery denervation apparatus employing helical shaping arrangement|

---

EP2566559B1|2010-05-05|2019-12-18|Cook Medical Technologies LLC|Turbulator for promoting uptake of a treatment agent|

---

CN102883768B|2010-05-11|2014-11-19|导管治疗有限公司|A catheter shape release mechanism|

---

EP2389974B1|2010-05-25|2014-04-23|Miracor Medical Systems GmbH|A balloon catheter for introduction into a body vessel, in particular the coronary sinus|

---

US9408661B2|2010-07-30|2016-08-09|Patrick A. Haverkost|RF electrodes on multiple flexible wires for renal nerve ablation|

---

US9084609B2|2010-07-30|2015-07-21|Boston Scientific Scime, Inc.|Spiral balloon catheter for renal nerve ablation|

---

US9358365B2|2010-07-30|2016-06-07|Boston Scientific Scimed, Inc.|Precision electrode movement control for renal nerve ablation|

---

AU2011239313A1|2010-10-25|2012-05-10|Aboytes, Maria G.|Catheter apparatuses having multi-electrode arrays for renal neuromodulation and associated systems and methods|

---

MX2013004235A|2010-10-25|2013-05-30|Medtronic Ardian Luxembourg|Catheter apparatuses having multi-electrode arrays for renal neuromodulation and associated systems and methods.|

---

US9028485B2|2010-11-15|2015-05-12|Boston Scientific Scimed, Inc.|Self-expanding cooling electrode for renal nerve ablation|

---

US9192435B2|2010-11-22|2015-11-24|Boston Scientific Scimed, Inc.|Renal denervation catheter with cooled RF electrode|

---

EP2645955B1|2010-12-01|2016-10-26|Boston Scientific Scimed, Inc.|Expandable angular vascular electrode for renal nerve ablation|

---

WO2012100095A1|2011-01-19|2012-07-26|Boston Scientific Scimed, Inc.|Guide-compatible large-electrode catheter for renal nerve ablation with reduced arterial injury|

---

US20120191086A1|2011-01-20|2012-07-26|Hansen Medical, Inc.|System and method for endoluminal and translumenal therapy|

---

CN103442659A|2011-01-28|2013-12-11|美敦力阿迪安卢森堡有限公司|Ablation catheter equipped with shape memory material|

---

EP2491883B1|2011-02-24|2014-06-18|VascoMed GmbH|Catheter and catheter arrangement|

---

WO2012130337A1|2011-04-01|2012-10-04|Flux Medical N.V.|System, device and method for ablation of a vessel's wall from the inside|

---

CN102125725A|2011-04-06|2011-07-20|湖南依微迪医疗器械有限公司|Catheter for endovascular treatment on hypertension|

---

EP2693969B1|2011-04-08|2016-02-03|Covidien LP|Microwave device for treating tissue|

---

CN102125460B|2011-04-15|2012-11-28|深圳市惠泰医疗器械有限公司|Renal artery radio frequency ablation catheter as well as manufacturing method and application method thereof|

---

WO2012149167A2|2011-04-26|2012-11-01|Christopher Gerard Kunis|Method and device for treatment of hypertension and other maladies|

---

CN102198015B|2011-05-03|2013-11-06|上海微创电生理医疗科技有限公司|Retractable spiral laminar ring type electrode catheter|

---

CN102274075A|2011-05-03|2011-12-14|上海微创电生理医疗科技有限公司|Multipolar punctiform electrode catheter for heat-induced kidney neuroregulation|

---

EP2706939A4|2011-05-09|2015-05-27|Cyberheart Inc|Renovascular treatment device, system and method for radiosurgicauy alleviating hypertension|

---

US20120290053A1|2011-05-11|2012-11-15|St. Jude Medical, Inc.|Renal nerve stimulation lead, delivery system, and method|

---

US8909316B2|2011-05-18|2014-12-09|St. Jude Medical, Cardiology Division, Inc.|Apparatus and method of assessing transvascular denervation|

---

WO2012158864A1|2011-05-18|2012-11-22|St. Jude Medical, Inc.|Apparatus and method of assessing transvascular denervation|

---

JP5166576B2|2011-07-07|2013-03-21|シャープ株式会社|GaN-based semiconductor device manufacturing method|

---

AU2012287189B2|2011-07-22|2016-10-06|Boston Scientific Scimed, Inc.|Nerve modulation system with a nerve modulation element positionable in a helical guide|

---

US20130035681A1|2011-08-04|2013-02-07|Boston Scientific Scimed, Inc.|Novel catheter for contiguous rf ablation|

---

US20130053792A1|2011-08-24|2013-02-28|Ablative Solutions, Inc.|Expandable catheter system for vessel wall injection and muscle and nerve fiber ablation|

---

EP2747690B1|2011-08-24|2019-01-23|Boston Scientific Scimed, Inc.|Device and methods for nerve modulation|

---

JP6188159B2|2011-08-26|2017-08-30|サイマップ ホールディング リミテッド|System and method for locating and identifying functional nerves governing arterial walls and catheter thereof|

---

US8702619B2|2011-08-26|2014-04-22|Symap Holding Limited|Mapping sympathetic nerve distribution for renal ablation and catheters for same|

---

WO2013030806A1|2011-09-01|2013-03-07|Perseus-Biomed Inc.|Method and system for tissue modulation|

---

CA2847846A1|2011-09-14|2013-03-21|Boston Scientific Scimed, Inc.|Ablation device with multiple ablation modes|

---

EP2760532B1|2011-09-30|2019-08-28|Covidien LP|Energy delivery device|

---

US8498686B2|2011-10-04|2013-07-30|Biosense Webster , Ltd.|Mapping catheter with spiral electrode assembly|

---

US20130090637A1|2011-10-05|2013-04-11|St. Jude Medical, Inc.|Catheter device and method for denervation|

---

US20130090578A1|2011-10-10|2013-04-11|Boston Scientific Scimed, Inc.|Device and methods for renal nerve modulation|

---

EP2765942B1|2011-10-10|2016-02-24|Boston Scientific Scimed, Inc.|Medical devices including ablation electrodes|

---

WO2013055537A1|2011-10-11|2013-04-18|Boston Scientific Scimed, Inc.|Ablation catheter with insulated tip|

---

WO2013055815A1|2011-10-11|2013-04-18|Boston Scientific Scimed, Inc.|Off -wall electrode device for nerve modulation|

---

US20130090649A1|2011-10-11|2013-04-11|Boston Scientific Scimed, Inc.|Device and methods for renal nerve modulation|

---

US9364284B2|2011-10-12|2016-06-14|Boston Scientific Scimed, Inc.|Method of making an off-wall spacer cage|

---

US20130096550A1|2011-10-18|2013-04-18|Boston Scientific Scimed, Inc.|Ablative catheter with electrode cooling and related methods of use|

---

US9162046B2|2011-10-18|2015-10-20|Boston Scientific Scimed, Inc.|Deflectable medical devices|

---

US20130123770A1|2011-11-14|2013-05-16|Boston Scientific Scimed, Inc.|Ablation catheter with cryothermal balloon|

---

US9119632B2|2011-11-21|2015-09-01|Boston Scientific Scimed, Inc.|Deflectable renal nerve ablation catheter|

---

EP2783651A4|2011-11-21|2014-10-01|Denerve Inc|Renal artery ablation catheter and system|

---

CN202386778U|2011-11-29|2012-08-22|北京天助畅运医疗技术股份有限公司|Radio-frequency melting device|

---

CN102488552B|2011-12-15|2015-04-15|四川锦江电子科技有限公司|Manageable spiral electrophysiology catheter|

---

CN202426649U|2011-12-22|2012-09-12|王涛|Ringlike multi-point radio-frequency ablation electrode|

---

EP2793989A1|2011-12-22|2014-10-29|Boston Scientific Scimed, Inc.|Handle having hub with rotating infusion sideport|

---

CN104135958B|2011-12-28|2017-05-03|波士顿科学西美德公司|By the apparatus and method that have the new ablation catheter modulation nerve of polymer ablation|

---

US20130172880A1|2011-12-29|2013-07-04|Boston Scientific Scimed, Inc.|Renal nerve modulation devices and methods for renal nerve modulation|

---

US20130172879A1|2011-12-29|2013-07-04|Boston Scientific Scimed, Inc.|Renal nerve modulation medical devices|

---

US9050106B2|2011-12-29|2015-06-09|Boston Scientific Scimed, Inc.|Off-wall electrode device and methods for nerve modulation|

---

EP2804554A1|2012-01-17|2014-11-26|Boston Scientific Scimed, Inc.|Renal nerve modulation devices and methods for making and using the same|

---

US8571654B2|2012-01-17|2013-10-29|Cyberonics, Inc.|Vagus nerve neurostimulator with multiple patient-selectable modes for treating chronic cardiac dysfunction|

---

CN202538132U|2012-02-06|2012-11-21|北京中孵友信医药科技股份有限公司|Snakelike intracavitary catheter|

---

US20130253628A1|2012-03-22|2013-09-26|Boston Scientific Scimed, Inc.|Device and methods for renal nerve modulation|

---

CN202537649U|2012-04-10|2012-11-21|北京中孵友信医药科技股份有限公司|Intracavity catheter with global location function|

---

US9439598B2|2012-04-12|2016-09-13|NeuroMedic, Inc.|Mapping and ablation of nerves within arteries and tissues|

---

US20130274730A1|2012-04-12|2013-10-17|Boston Scientific Scimed, Inc.|Ablation catheter and methods for nerve modulation|

---

EP2836151B1|2012-04-13|2016-10-26|Covidien LP|Energy delivery device|

---

EP2838459A1|2012-04-16|2015-02-25|Boston Scientific Scimed, Inc.|Helical tubing devices for fluid renal nerve modulation|

---

WO2013158676A2|2012-04-16|2013-10-24|Boston Scientific Scimed, Inc.|Renal nerve modulation catheter design|

---

US9113929B2|2012-04-19|2015-08-25|St. Jude Medical, Cardiology Division, Inc.|Non-electric field renal denervation electrode|

---

WO2013165920A1|2012-04-29|2013-11-07|Synecor Llc|Intravascular electrode arrays for neuromodulation|

---

US10660703B2|2012-05-08|2020-05-26|Boston Scientific Scimed, Inc.|Renal nerve modulation devices|

---

US9439722B2|2012-05-09|2016-09-13|Biosense Webster Ltd.|Ablation targeting nerves in or near the inferior vena cava and/or abdominal aorta for treatment of hypertension|

---

AU2013260174B2|2012-05-11|2016-01-07|Medtronic Af Luxembourg S.A.R.L.|Multi-electrode catheter assemblies for renal neuromodulation and associated systems and methods|

---

US9717555B2|2012-05-14|2017-08-01|Biosense Webster , Ltd.|Catheter with helical end section for vessel ablation|

---

DE102012104705A1|2012-05-31|2013-12-05|Stefan G. Spitzer|Catheter system for performing denervation of sympathetic nerve at adventitia of wall of e.g. kidney artery of patient, has electrodes arranged at free ends of respective wires to deliver respective radio frequency energies|

---

CN102772249B|2012-06-19|2015-01-21|深圳市惠泰医疗器械有限公司|Radiofrequency ablation electrode catheter of renal artery rail|

---

CN102743225B|2012-07-18|2014-04-02|深圳市惠泰医疗器械有限公司|Radiofrequency ablation controlled electrode catheter for renal artery|

---

CN104540465A|2012-08-24|2015-04-22|波士顿科学西美德公司|Intravascular catheter with a balloon comprising separate microporous regions|

---

EP3123973A1|2012-08-28|2017-02-01|Boston Scientific Scimed, Inc.|Renal rf ablation system with a movable virtual electrode and related methods of use|

---

WO2014036160A2|2012-08-28|2014-03-06|Boston Scientific Scimed, Inc.|Renal nerve modulation and ablation catheter electrode design|

---

CN202761434U|2012-08-29|2013-03-06|中国人民解放军第三军医大学第一附属医院|Kidney sympathetic denervation multifunctional ablation catheter system|

---

CN102885649B|2012-08-29|2015-01-21|中国人民解放军第三军医大学第一附属医院|Radio frequency cable controlled ablation catheter system for removing sympathetic nerve from kidney|

---

CN102908188B|2012-08-29|2015-04-08|中国人民解放军第三军医大学第一附属医院|Radio frequency ablation catheter system for denervation of renal sympathetic nerves|

---

WO2014056460A1|2012-08-29|2014-04-17|第三军医大学第一附属医院|Multifunctional ablation catheter system for renal sympathetic denervation|

---

CN102908189B|2012-08-29|2015-04-08|中国人民解放军第三军医大学第一附属医院|Multifunctional ablation catheter system for denervation of renal sympathetic nerves|

---

CN202843784U|2012-08-29|2013-04-03|中国人民解放军第三军医大学第一附属医院|Renal sympathetic nerve ablation catheter system|

---

CN102885648B|2012-08-29|2015-03-18|中国人民解放军第三军医大学第一附属医院|Sympathetic nerve denervation ablation catheter system for kidneys|

---

US20140094787A1|2012-09-28|2014-04-03|Boston Scientific Scimed, Inc.|Flexible renal nerve modulation device|

---

US9301795B2|2012-10-29|2016-04-05|Ablative Solutions, Inc.|Transvascular catheter for extravascular delivery|

---

US8740849B1|2012-10-29|2014-06-03|Ablative Solutions, Inc.|Peri-vascular tissue ablation catheter with support structures|

---

US10286182B2|2012-11-12|2019-05-14|Boston Scientific Scimed, Inc.|Renal catheter shaft design|

---

EP2759314A1|2013-01-28|2014-07-30|Biotronik AG|Catheter for renal nerve modulation|

---

US20140249524A1|2013-03-01|2014-09-04|Boston Scientific Scimed, Inc.|System and method for performing renal nerve modulation|

---

US20140303617A1|2013-03-05|2014-10-09|Neuro Ablation, Inc.|Intravascular nerve ablation devices & methods|

---

US9693821B2|2013-03-11|2017-07-04|Boston Scientific Scimed, Inc.|Medical devices for modulating nerves|

---

US9956033B2|2013-03-11|2018-05-01|Boston Scientific Scimed, Inc.|Medical devices for modulating nerves|

---

US9256079B2|2013-03-12|2016-02-09|Micro-G Lacoste, Inc.|Polarized beam director and method|

---

US20140276755A1|2013-03-12|2014-09-18|Boston Scientific Scimed, Inc.|Medical systems and methods for modulating nerves|

---

US9808311B2|2013-03-13|2017-11-07|Boston Scientific Scimed, Inc.|Deflectable medical devices|

---

US10265122B2|2013-03-15|2019-04-23|Boston Scientific Scimed, Inc.|Nerve ablation devices and related methods of use|

---

US9333113B2|2013-03-15|2016-05-10|Abbott Cardiovascular Systems Inc.|System and method for denervation|

---

US9827039B2|2013-03-15|2017-11-28|Boston Scientific Scimed, Inc.|Methods and apparatuses for remodeling tissue of or adjacent to a body passage|

---

WO2014176785A1|2013-05-03|2014-11-06|上海安通医疗科技有限公司|Nerve regulation device|

---

JP6580034B2|2013-06-05|2019-09-25|メタベンション インコーポレイテッド|Target nerve fiber regulation|

---

CN105682594B|2013-07-19|2018-06-22|波士顿科学国际有限公司|Helical bipolar electrodes renal denervation dominates air bag|

---

US9913684B2|2013-08-23|2018-03-13|Oscor Inc.|Steerable ablation catheter for renal denervation|

---

US20150126992A1|2013-11-05|2015-05-07|Mogul Enterprises, Inc|Helical DeNervation Ablation Catheter Apparatus|

---

JP2015119831A|2013-12-24|2015-07-02|テルモ株式会社|Ablation catheter|

---

CN106572875A|2014-02-07|2017-04-19|沃夫医药公司|Methods and systems for ablation of the renal pelvis|

---

US20150223877A1|2014-02-12|2015-08-13|Perseus-Biomed Inc.|Methods and systems for treating nerve structures|

---

CN105012009B|2014-04-22|2018-09-28|上海微创电生理医疗科技有限公司|A kind of renal artery radiofrequency ablation electrode catheter|

---

EP3148467A1|2014-05-28|2017-04-05|Boston Scientific Scimed, Inc.|Nerve modulation devices with cooling capabilities|

---

CN105167840A|2014-06-20|2015-12-23|上海安通医疗科技有限公司|Multi-electrode renal artery radiofrequency ablation catheter|

---

CN105326562A|2014-06-24|2016-02-17|上海安通医疗科技有限公司|Catheter device for regulating renal nerves|

---

JP2016086999A|2014-10-31|2016-05-23|テルモ株式会社|Ablation catheter|

---

US20180000540A1|2014-12-17|2018-01-04|Cathrx Ltd|An improved catheter and method of manufacture thereof|

---

US9795780B2|2014-12-18|2017-10-24|Abbott Cardiovascular Systems Inc.|System for denervation|

---

US9737361B2|2014-12-18|2017-08-22|Abbott Cardiovascular Systems Inc.|System and method for a catheter|

---

CN205433879U|2015-12-08|2016-08-10|上海安通医疗科技有限公司|Radiofrequency ablation catheter for renal arteries|

---

CN205433878U|2015-12-08|2016-08-10|上海安通医疗科技有限公司|Radiofrequency ablation catheter for renal arteries|

---

CN205433876U|2016-02-06|2016-08-10|郭宇|Smooth silk screw of orthopedics takes out instrument|US8016823B2|2003-01-18|2011-09-13|Tsunami Medtech, Llc|Medical instrument and method of use|

---

US6702811B2|1999-04-05|2004-03-09|Medtronic, Inc.|Ablation catheter assembly with radially decreasing helix and method of use|

---

US7220257B1|2000-07-25|2007-05-22|Scimed Life Systems, Inc.|Cryotreatment device and method|

---

US9433457B2|2000-12-09|2016-09-06|Tsunami Medtech, Llc|Medical instruments and techniques for thermally-mediated therapies|

---

US8444636B2|2001-12-07|2013-05-21|Tsunami Medtech, Llc|Medical instrument and method of use|

---

US8774913B2|2002-04-08|2014-07-08|Medtronic Ardian Luxembourg S.A.R.L.|Methods and apparatus for intravasculary-induced neuromodulation|

---

US7653438B2|2002-04-08|2010-01-26|Ardian, Inc.|Methods and apparatus for renal neuromodulation|

---

US20140018880A1|2002-04-08|2014-01-16|Medtronic Ardian Luxembourg S.A.R.L.|Methods for monopolar renal neuromodulation|

---

US10765473B2|2010-11-08|2020-09-08|Baylis Medical Company Inc.|Electrosurgical device having a lumen|

---

DE202004021943U1|2003-09-12|2013-05-13|Vessix Vascular, Inc.|Selectable eccentric remodeling and / or ablation of atherosclerotic material|

---

US9713730B2|2004-09-10|2017-07-25|Boston Scientific Scimed, Inc.|Apparatus and method for treatment of in-stent restenosis|

---

US20050153309A1|2003-12-22|2005-07-14|David Hoon|Method and apparatus for in vivo surveillance of circulating biological components|

---

US8019435B2|2006-05-02|2011-09-13|Boston Scientific Scimed, Inc.|Control of arterial smooth muscle tone|

---

ES2407329T3|2006-10-18|2013-06-12|Vessix Vascular, Inc.|System to induce desirable temperature effects on body tissue|

---

EP2954868A1|2006-10-18|2015-12-16|Vessix Vascular, Inc.|Tuned rf energy and electrical tissue characterization for selective treatment of target tissues|

---

US9974607B2|2006-10-18|2018-05-22|Vessix Vascular, Inc.|Inducing desirable temperature effects on body tissue|

---

US7655004B2|2007-02-15|2010-02-02|Ethicon Endo-Surgery, Inc.|Electroporation ablation apparatus, system, and method|

---

WO2009009398A1|2007-07-06|2009-01-15|Tsunami Medtech, Llc|Medical system and method of use|

---

US9924992B2|2008-02-20|2018-03-27|Tsunami Medtech, Llc|Medical system and method of use|

---

US8768469B2|2008-08-08|2014-07-01|Enteromedics Inc.|Systems for regulation of blood pressure and heart rate|

---

US8721632B2|2008-09-09|2014-05-13|Tsunami Medtech, Llc|Methods for delivering energy into a target tissue of a body|

---

US8396548B2|2008-11-14|2013-03-12|Vessix Vascular, Inc.|Selective drug delivery in a lumen|

---

EP2355737B1|2008-11-17|2021-08-11|Boston Scientific Scimed, Inc.|Selective accumulation of energy without knowledge of tissue topography|

---

US8157834B2|2008-11-25|2012-04-17|Ethicon Endo-Surgery, Inc.|Rotational coupling device for surgical instrument with flexible actuators|

---

US9254168B2|2009-02-02|2016-02-09|Medtronic Advanced Energy Llc|Electro-thermotherapy of tissue using penetrating microelectrode array|

---

CN102497832B|2009-09-08|2015-09-09|显著外科技术公司|For case assembly and the using method thereof of electro-surgical device, electrosurgical unit|

---

US20110098704A1|2009-10-28|2011-04-28|Ethicon Endo-Surgery, Inc.|Electrical ablation devices|

---

US9161801B2|2009-12-30|2015-10-20|Tsunami Medtech, Llc|Medical system and method of use|

---

EP2544616B1|2010-03-11|2017-09-06|Medtronic Advanced Energy LLC|Bipolar electrosurgical cutter with position insensitive return electrode contact|

---

US9277955B2|2010-04-09|2016-03-08|Vessix Vascular, Inc.|Power generating and control apparatus for the treatment of tissue|

---

US9192790B2|2010-04-14|2015-11-24|Boston Scientific Scimed, Inc.|Focused ultrasonic renal denervation|

---

US8473067B2|2010-06-11|2013-06-25|Boston Scientific Scimed, Inc.|Renal denervation and stimulation employing wireless vascular energy transfer arrangement|

---

US8920417B2|2010-06-30|2014-12-30|Medtronic Advanced Energy Llc|Electrosurgical devices and methods of use thereof|

---

US9463062B2|2010-07-30|2016-10-11|Boston Scientific Scimed, Inc.|Cooled conductive balloon RF catheter for renal nerve ablation|

---

US9408661B2|2010-07-30|2016-08-09|Patrick A. Haverkost|RF electrodes on multiple flexible wires for renal nerve ablation|

---

US9155589B2|2010-07-30|2015-10-13|Boston Scientific Scimed, Inc.|Sequential activation RF electrode set for renal nerve ablation|

---

US9084609B2|2010-07-30|2015-07-21|Boston Scientific Scime, Inc.|Spiral balloon catheter for renal nerve ablation|

---

US9358365B2|2010-07-30|2016-06-07|Boston Scientific Scimed, Inc.|Precision electrode movement control for renal nerve ablation|

---

MX2013004235A|2010-10-25|2013-05-30|Medtronic Ardian Luxembourg|Catheter apparatuses having multi-electrode arrays for renal neuromodulation and associated systems and methods.|

---

US8974451B2|2010-10-25|2015-03-10|Boston Scientific Scimed, Inc.|Renal nerve ablation using conductive fluid jet and RF energy|

---

US9439708B2|2010-10-26|2016-09-13|Medtronic Ardian Luxembourg S.A.R.L.|Neuromodulation cryotherapeutic devices and associated systems and methods|

---

US9023040B2|2010-10-26|2015-05-05|Medtronic Advanced Energy Llc|Electrosurgical cutting devices|

---

US9220558B2|2010-10-27|2015-12-29|Boston Scientific Scimed, Inc.|RF renal denervation catheter with multiple independent electrodes|

---

EP2637590A4|2010-11-09|2014-04-16|Aegea Medical Inc|Positioning method and apparatus for delivering vapor to the uterus|

---

US9028485B2|2010-11-15|2015-05-12|Boston Scientific Scimed, Inc.|Self-expanding cooling electrode for renal nerve ablation|

---

US9668811B2|2010-11-16|2017-06-06|Boston Scientific Scimed, Inc.|Minimally invasive access for renal nerve ablation|

---

US9089350B2|2010-11-16|2015-07-28|Boston Scientific Scimed, Inc.|Renal denervation catheter with RF electrode and integral contrast dye injection arrangement|

---

US9326751B2|2010-11-17|2016-05-03|Boston Scientific Scimed, Inc.|Catheter guidance of external energy for renal denervation|

---

US9060761B2|2010-11-18|2015-06-23|Boston Scientific Scime, Inc.|Catheter-focused magnetic field induced renal nerve ablation|

---

US9192435B2|2010-11-22|2015-11-24|Boston Scientific Scimed, Inc.|Renal denervation catheter with cooled RF electrode|

---

US9023034B2|2010-11-22|2015-05-05|Boston Scientific Scimed, Inc.|Renal ablation electrode with force-activatable conduction apparatus|

---

US20120157993A1|2010-12-15|2012-06-21|Jenson Mark L|Bipolar Off-Wall Electrode Device for Renal Nerve Ablation|

---

WO2012100095A1|2011-01-19|2012-07-26|Boston Scientific Scimed, Inc.|Guide-compatible large-electrode catheter for renal nerve ablation with reduced arterial injury|

---

US9233241B2|2011-02-28|2016-01-12|Ethicon Endo-Surgery, Inc.|Electrical ablation devices and methods|

---

US9254169B2|2011-02-28|2016-02-09|Ethicon Endo-Surgery, Inc.|Electrical ablation devices and methods|

---

US9427281B2|2011-03-11|2016-08-30|Medtronic Advanced Energy Llc|Bronchoscope-compatible catheter provided with electrosurgical device|

---

WO2012166467A1|2011-05-27|2012-12-06|Stryker Corporation|Assembly for percutaneously inserting an implantable medical device, steering the device to a target location and deploying the device|

---

US9220433B2|2011-06-30|2015-12-29|Biosense Webster , Ltd.|Catheter with variable arcuate distal section|

---

CN103813745B|2011-07-20|2016-06-29|波士顿科学西美德公司|In order to visualize, be directed at and to melt transcutaneous device and the method for nerve|

---

AU2012287189B2|2011-07-22|2016-10-06|Boston Scientific Scimed, Inc.|Nerve modulation system with a nerve modulation element positionable in a helical guide|

---

US9662169B2|2011-07-30|2017-05-30|Biosense WebsterLtd.|Catheter with flow balancing valve|

---

US20130035681A1|2011-08-04|2013-02-07|Boston Scientific Scimed, Inc.|Novel catheter for contiguous rf ablation|

---

US9820811B2|2011-08-26|2017-11-21|Symap Medical , Ltd|System and method for mapping the functional nerves innervating the wall of arteries, 3-D mapping and catheters for same|

---

CN103284693B|2012-08-24|2014-12-24|苏州信迈医疗器械有限公司|Instrument for locating and identifying nerves in vessel wall, and application method thereof|

---

US8702619B2|2011-08-26|2014-04-22|Symap Holding Limited|Mapping sympathetic nerve distribution for renal ablation and catheters for same|

---

JP6188159B2|2011-08-26|2017-08-30|サイマップ ホールディング リミテッド|System and method for locating and identifying functional nerves governing arterial walls and catheter thereof|

---

US9750565B2|2011-09-30|2017-09-05|Medtronic Advanced Energy Llc|Electrosurgical balloons|

---

US9662060B2|2011-10-07|2017-05-30|Aegea Medical Inc.|Integrity testing method and apparatus for delivering vapor to the uterus|

---

EP2765942B1|2011-10-10|2016-02-24|Boston Scientific Scimed, Inc.|Medical devices including ablation electrodes|

---

US9420955B2|2011-10-11|2016-08-23|Boston Scientific Scimed, Inc.|Intravascular temperature monitoring system and method|

---

WO2013055815A1|2011-10-11|2013-04-18|Boston Scientific Scimed, Inc.|Off -wall electrode device for nerve modulation|

---

US9364284B2|2011-10-12|2016-06-14|Boston Scientific Scimed, Inc.|Method of making an off-wall spacer cage|

---

US9079000B2|2011-10-18|2015-07-14|Boston Scientific Scimed, Inc.|Integrated crossing balloon catheter|

---

US9162046B2|2011-10-18|2015-10-20|Boston Scientific Scimed, Inc.|Deflectable medical devices|

---

CN108095821B|2011-11-08|2021-05-25|波士顿科学西美德公司|Orifice renal nerve ablation|

---

EP2779929A1|2011-11-15|2014-09-24|Boston Scientific Scimed, Inc.|Device and methods for renal nerve modulation monitoring|

---

US9119632B2|2011-11-21|2015-09-01|Boston Scientific Scimed, Inc.|Deflectable renal nerve ablation catheter|

---

US9192766B2|2011-12-02|2015-11-24|Medtronic Ardian Luxembourg S.A.R.L.|Renal neuromodulation methods and devices for treatment of polycystic kidney disease|

---

SG11201402610QA|2011-12-09|2014-10-30|Metavention Inc|Therapeutic neuromodulation of the hepatic system|

---

US9131980B2|2011-12-19|2015-09-15|Medtronic Advanced Energy Llc|Electrosurgical devices|

---

US9265969B2|2011-12-21|2016-02-23|Cardiac Pacemakers, Inc.|Methods for modulating cell function|

---

WO2013096922A1|2011-12-23|2013-06-27|Vessix Vascular, Inc.|Methods and apparatuses for remodeling tissue of or adjacent to a body passage|

---

CN104135958B|2011-12-28|2017-05-03|波士顿科学西美德公司|By the apparatus and method that have the new ablation catheter modulation nerve of polymer ablation|

---

US9050106B2|2011-12-29|2015-06-09|Boston Scientific Scimed, Inc.|Off-wall electrode device and methods for nerve modulation|

---

US10213187B1|2012-01-25|2019-02-26|Mubin I. Syed|Method and apparatus for percutaneous superficial temporal artery access for carotid artery stenting|

---

WO2013134492A1|2012-03-08|2013-09-12|Medtronic Ardian Luxembourg Sarl|Neuromodulation and associated systems and methods for the treatment of sexual dysfunction|

---

WO2013134479A1|2012-03-08|2013-09-12|Medtronic Ardian Luxembourg Sarl|Neuromodulation and associated systems and methods for the management of pain|

---

AU2013230781B2|2012-03-08|2015-12-03|Medtronic Af Luxembourg S.A.R.L.|Ovarian neuromodulation and associated systems and methods|

---

WO2013134472A1|2012-03-08|2013-09-12|Medtronic Ardian Luxembourg S.A.R.L.|Renal neuromodulation methods and systems for treatment of hyperaldosteronism|

---

WO2013134733A2|2012-03-08|2013-09-12|Medtronic Ardian Luxembourg Sarl|Biomarker sampling in the context of neuromodulation devices and associated systems and methods|

---

US11013549B2|2012-03-08|2021-05-25|Medtronic Ardian Luxembourg S.A.R.L.|Gastrointestinal neuromodulation and associated systems and methods|

---

US9439598B2|2012-04-12|2016-09-13|NeuroMedic, Inc.|Mapping and ablation of nerves within arteries and tissues|

---

US20130296840A1|2012-05-01|2013-11-07|Medtronic Ablation Frontiers Llc|Systems and methods for detecting tissue contact during ablation|

---

US10660703B2|2012-05-08|2020-05-26|Boston Scientific Scimed, Inc.|Renal nerve modulation devices|

---

AU2013260174B2|2012-05-11|2016-01-07|Medtronic Af Luxembourg S.A.R.L.|Multi-electrode catheter assemblies for renal neuromodulation and associated systems and methods|

---

US9427255B2|2012-05-14|2016-08-30|Ethicon Endo-Surgery, Inc.|Apparatus for introducing a steerable camera assembly into a patient|

---

US9717555B2|2012-05-14|2017-08-01|Biosense Webster , Ltd.|Catheter with helical end section for vessel ablation|

---

CN104470579B|2012-06-06|2018-06-01|洋红医疗有限公司|Artificial kidney valve|

---

US9226792B2|2012-06-12|2016-01-05|Medtronic Advanced Energy Llc|Debridement device and method|

---

CN102772249B|2012-06-19|2015-01-21|深圳市惠泰医疗器械有限公司|Radiofrequency ablation electrode catheter of renal artery rail|

---

US8951296B2|2012-06-29|2015-02-10|Medtronic Ardian Luxembourg S.A.R.L.|Devices and methods for photodynamically modulating neural function in a human|

---

US9295842B2|2012-07-05|2016-03-29|Mc10, Inc.|Catheter or guidewire device including flow sensing and use thereof|

---

CA2934245A1|2014-01-03|2015-07-09|Mc10, Inc.|Catheter or guidewire device including flow sensing and use thereof|

---

US9168094B2|2012-07-05|2015-10-27|Mc10, Inc.|Catheter device including flow sensing|

---

US9545290B2|2012-07-30|2017-01-17|Ethicon Endo-Surgery, Inc.|Needle probe guide|

---

CN103565514B|2012-08-01|2015-05-06|四川锦江电子科技有限公司|Double-control bent spiral electrophysiological catheter|

---

US10314649B2|2012-08-02|2019-06-11|Ethicon Endo-Surgery, Inc.|Flexible expandable electrode and method of intraluminal delivery of pulsed power|

---

US9277957B2|2012-08-15|2016-03-08|Ethicon Endo-Surgery, Inc.|Electrosurgical devices and methods|

---

CN104540465A|2012-08-24|2015-04-22|波士顿科学西美德公司|Intravascular catheter with a balloon comprising separate microporous regions|

---

EP3123973A1|2012-08-28|2017-02-01|Boston Scientific Scimed, Inc.|Renal rf ablation system with a movable virtual electrode and related methods of use|

---

US10232164B2|2012-09-11|2019-03-19|G & H Technologies, Llc|Electrical discharge irrigator apparatus and method|

---

US10898705B2|2012-09-11|2021-01-26|G&H Technologies, Llc|Electrical discharge irrigator apparatus and method|

---

US9173696B2|2012-09-17|2015-11-03|Boston Scientific Scimed, Inc.|Self-positioning electrode system and method for renal nerve modulation|

---

US9333035B2|2012-09-19|2016-05-10|Denervx LLC|Cooled microwave denervation|

---

US10398464B2|2012-09-21|2019-09-03|Boston Scientific Scimed, Inc.|System for nerve modulation and innocuous thermal gradient nerve block|

---

WO2014047454A2|2012-09-21|2014-03-27|Boston Scientific Scimed, Inc.|Self-cooling ultrasound ablation catheter|

---

CN104812325A|2012-09-26|2015-07-29|波士顿科学国际有限公司|Catheter having rib and spine structure supporting multiple electrodes for renal nerve ablation|

---

US10286184B2|2012-10-01|2019-05-14|Qmax, Llc|Helical balloon catheter|

---

US11234760B2|2012-10-05|2022-02-01|Medtronic Advanced Energy Llc|Electrosurgical device for cutting and removing tissue|

---

JP6074051B2|2012-10-10|2017-02-01|ボストン サイエンティフィック サイムド，インコーポレイテッドＢｏｓｔｏｎ Ｓｃｉｅｎｔｉｆｉｃ Ｓｃｉｍｅｄ，Ｉｎｃ．|Intravascular neuromodulation system and medical device|

---

CN102940525A|2012-10-17|2013-02-27|上海安通医疗科技有限公司|Multi-pole helicoidal radiofrequency ablation conduit|

---

US9044575B2|2012-10-22|2015-06-02|Medtronic Adrian Luxembourg S.a.r.l.|Catheters with enhanced flexibility and associated devices, systems, and methods|

---

US9399115B2|2012-10-22|2016-07-26|Medtronic Ardian Luxembourg S.A.R.L.|Catheters with enhanced flexibility and associated devices, systems, and methods|

---

KR102038632B1|2012-11-06|2019-10-30|삼성전자주식회사|surgical instrument, supporting device, and surgical robot system adopting the same|

---

KR102219632B1|2014-07-11|2021-02-25|펄노보 메디컬 워시 컴퍼니, 리미티드|Multi-pole synchronous pulmonary artery radiofrequency ablation catheter|

---

US11241267B2|2012-11-13|2022-02-08|Pulnovo MedicalCo., Ltd|Multi-pole synchronous pulmonary artery radiofrequency ablation catheter|

---

US9827036B2|2012-11-13|2017-11-28|Pulnovo MedicalCo., Ltd.|Multi-pole synchronous pulmonary artery radiofrequency ablation catheter|

---

CN102908191A|2012-11-13|2013-02-06|陈绍良|Multipolar synchronous pulmonary artery radiofrequency ablation catheter|

---

US9095321B2|2012-11-21|2015-08-04|Medtronic Ardian Luxembourg S.A.R.L.|Cryotherapeutic devices having integral multi-helical balloons and methods of making the same|

---

WO2014081947A1|2012-11-21|2014-05-30|Syed Mubin I|System for the intravascular placement of a medical device|

---

CN103830001B|2012-11-23|2016-12-21|四川锦江电子科技有限公司|Controllable bending spiral ablation catheter|

---

GB2508905A|2012-12-14|2014-06-18|Gyrus Medical Ltd|Endoscopic instrument with bypass lead|

---

RU2649527C2|2013-02-05|2018-04-03|Хандок Инк.|Nerve block catheter|

---

US10076384B2|2013-03-08|2018-09-18|Symple Surgical, Inc.|Balloon catheter apparatus with microwave emitter|

---

US9956033B2|2013-03-11|2018-05-01|Boston Scientific Scimed, Inc.|Medical devices for modulating nerves|

---

US9693821B2|2013-03-11|2017-07-04|Boston Scientific Scimed, Inc.|Medical devices for modulating nerves|

---

US10583231B2|2013-03-13|2020-03-10|Magenta Medical Ltd.|Blood pump|

---

US9283040B2|2013-03-13|2016-03-15|The Spectranetics Corporation|Device and method of ablative cutting with helical tip|

---

US9456872B2|2013-03-13|2016-10-04|The Spectranetics Corporation|Laser ablation catheter|

---

US10039874B2|2013-03-13|2018-08-07|Magenta Medical Ltd.|Renal pump|

---

US10383691B2|2013-03-13|2019-08-20|The Spectranetics Corporation|Last catheter with helical internal lumen|

---

US9808311B2|2013-03-13|2017-11-07|Boston Scientific Scimed, Inc.|Deflectable medical devices|

---

EP2967714A4|2013-03-14|2016-10-19|Baylis Medical Co Inc|Electrosurgical device having a lumen|

---

US9943353B2|2013-03-15|2018-04-17|Tsunami Medtech, Llc|Medical system and method of use|

---

US9848948B2|2013-03-15|2017-12-26|Biosense WebsterLtd.|Catheter adapted for use with guide wire for accessing vessels|

---

US9827039B2|2013-03-15|2017-11-28|Boston Scientific Scimed, Inc.|Methods and apparatuses for remodeling tissue of or adjacent to a body passage|

---

US20140275993A1|2013-03-15|2014-09-18|Medtronic Ardian Luxembourg S.a.r.I.|Devices, Systems, and Methods for Specialization of Neuromodulation Treatment|

---

CN105142553A|2013-03-15|2015-12-09|美敦力阿迪安卢森堡有限公司|Direct heat ablation catheter|

---

JP2014180574A|2013-03-15|2014-09-29|Tidal Wave Technology Inc|Ablation catheter device and method|

---

US9333113B2|2013-03-15|2016-05-10|Abbott Cardiovascular Systems Inc.|System and method for denervation|

---

US9066726B2|2013-03-15|2015-06-30|Medtronic Ardian Luxembourg S.A.R.L.|Multi-electrode apposition judgment using pressure elements|

---

WO2014151273A1|2013-03-15|2014-09-25|Medtronic Ardian Luxembourg S.A.R.L.|Treatment device with electrode contact surface configured for enhancing uniformity of electrical energy distribution and associated devices and methods|

---

US9179974B2|2013-03-15|2015-11-10|Medtronic Ardian Luxembourg S.A.R.L.|Helical push wire electrode|

---

US9297845B2|2013-03-15|2016-03-29|Boston Scientific Scimed, Inc.|Medical devices and methods for treatment of hypertension that utilize impedance compensation|

---

US10265122B2|2013-03-15|2019-04-23|Boston Scientific Scimed, Inc.|Nerve ablation devices and related methods of use|

---

CN104095679A|2013-04-12|2014-10-15|上海微创电生理医疗科技有限公司|Multiple-electrode ablation catheter|

---

WO2014174662A1|2013-04-26|2014-10-30|テルモ株式会社|Ablation catheter|

---

US10010364B2|2013-05-02|2018-07-03|Halcyon Medical, Inc.|Devices and methods for detection and treatment of the aorticorenal ganglion|

---

WO2014176785A1|2013-05-03|2014-11-06|上海安通医疗科技有限公司|Nerve regulation device|

---

US10548663B2|2013-05-18|2020-02-04|Medtronic Ardian Luxembourg S.A.R.L.|Neuromodulation catheters with shafts for enhanced flexibility and control and associated devices, systems, and methods|

---

JP2016523125A|2013-05-30|2016-08-08|グラハム エイチ． クリーシー|Local nervous stimulation|

---

US11229789B2|2013-05-30|2022-01-25|Neurostim Oab, Inc.|Neuro activator with controller|

---

JP6580034B2|2013-06-05|2019-09-25|メタベンション インコーポレイテッド|Target nerve fiber regulation|

---

CN103284788B|2013-06-19|2015-06-10|上海安通医疗科技有限公司|Radiofrequency ablatograph and radiofrequency ablation system|

---

CN105473091B|2013-06-21|2020-01-21|波士顿科学国际有限公司|Renal denervation balloon catheter with co-movable electrode supports|

---

CN105473092B|2013-06-21|2019-05-17|波士顿科学国际有限公司|The medical instrument for renal nerve ablation with rotatable shaft|

---

US9707036B2|2013-06-25|2017-07-18|Boston Scientific Scimed, Inc.|Devices and methods for nerve modulation using localized indifferent electrodes|

---

JP6366123B2|2013-06-26|2018-08-01|国立大学法人東京農工大学|Insert system|

---

CN105358084B|2013-07-01|2018-11-09|波士顿科学国际有限公司|Medical instrument for renal nerve ablation|

---

CN105377169B|2013-07-11|2019-04-19|波士顿科学国际有限公司|Device and method for neuromodulation|

---

EP3019106A1|2013-07-11|2016-05-18|Boston Scientific Scimed, Inc.|Medical device with stretchable electrode assemblies|

---

CN105682594B|2013-07-19|2018-06-22|波士顿科学国际有限公司|Helical bipolar electrodes renal denervation dominates air bag|

---

CN105392435B|2013-07-22|2018-11-09|波士顿科学国际有限公司|Renal nerve ablation catheter with twisting sacculus|

---

CN105555220B|2013-07-22|2019-05-17|波士顿科学国际有限公司|Medical instrument for renal nerve ablation|

---

DE112013007275T5|2013-07-25|2016-04-14|GM Global Technology Operations LLC|Dynamic sensor array|

---

WO2015027096A1|2013-08-22|2015-02-26|Boston Scientific Scimed, Inc.|Flexible circuit having improved adhesion to a renal nerve modulation balloon|

---

US9907570B2|2013-08-23|2018-03-06|Oscor Inc.|Steerable medical devices|

---

US9913684B2|2013-08-23|2018-03-13|Oscor Inc.|Steerable ablation catheter for renal denervation|

---

JP2016531612A|2013-09-30|2016-10-13|メドトロニック アーディアン ルクセンブルク ソシエテ ア レスポンサビリテ リミテ|Intravascular neuromodulation device having a spiral track and related methods|

---

US9326816B2|2013-08-30|2016-05-03|Medtronic Ardian Luxembourg S.A.R.L.|Neuromodulation systems having nerve monitoring assemblies and associated devices, systems, and methods|

---

US9895194B2|2013-09-04|2018-02-20|Boston Scientific Scimed, Inc.|Radio frequencyballoon catheter having flushing and cooling capability|

---

US20150073515A1|2013-09-09|2015-03-12|Medtronic Ardian Luxembourg S.a.r.I.|Neuromodulation Catheter Devices and Systems Having Energy Delivering Thermocouple Assemblies and Associated Methods|

---

CN105530885B|2013-09-13|2020-09-22|波士顿科学国际有限公司|Ablation balloon with vapor deposited covering|

---

JP2015073691A|2013-10-08|2015-04-20|テルモ株式会社|Medical device|

---

CN105592778B|2013-10-14|2019-07-23|波士顿科学医学有限公司|High-resolution cardiac mapping electrod-array conduit|

---

US11246654B2|2013-10-14|2022-02-15|Boston Scientific Scimed, Inc.|Flexible renal nerve ablation devices and related methods of use and manufacture|

---

EP3057520A1|2013-10-15|2016-08-24|Boston Scientific Scimed, Inc.|Medical device balloon|

---

US9770606B2|2013-10-15|2017-09-26|Boston Scientific Scimed, Inc.|Ultrasound ablation catheter with cooling infusion and centering basket|

---

WO2015057961A1|2013-10-18|2015-04-23|Boston Scientific Scimed, Inc.|Balloon catheters with flexible conducting wires and related methods of use and manufacture|

---

US10433902B2|2013-10-23|2019-10-08|Medtronic Ardian Luxembourg S.A.R.L.|Current control methods and systems|

---

WO2015061621A1|2013-10-24|2015-04-30|Medtronic Ardian Luxembourg S.A.R.L.|Catheter apparatuses for pulmonary artery neuromodulation|

---

US20160302857A1|2013-10-24|2016-10-20|Medtronic Ardian Luxembourg S.A.R.L.|Catheter apparatuses for modulation of nerves in communication with the pulmonary system and associated systems and methods|

---

US10390881B2|2013-10-25|2019-08-27|Denervx LLC|Cooled microwave denervation catheter with insertion feature|

---

EP3060153A1|2013-10-25|2016-08-31|Boston Scientific Scimed, Inc.|Embedded thermocouple in denervation flex circuit|

---

US20150126992A1|2013-11-05|2015-05-07|Mogul Enterprises, Inc|Helical DeNervation Ablation Catheter Apparatus|

---

US9987073B2|2013-11-19|2018-06-05|Covidien Lp|Electrosurgical coagulation instrument including a suction pipe and a collapsible tip|

---

US9764113B2|2013-12-11|2017-09-19|Magenta Medical Ltd|Curved catheter|

---

US10314647B2|2013-12-23|2019-06-11|Medtronic Advanced Energy Llc|Electrosurgical cutting instrument|

---

JP6382989B2|2014-01-06|2018-08-29|ボストン サイエンティフィック サイムド，インコーポレイテッドＢｏｓｔｏｎ Ｓｃｉｅｎｔｉｆｉｃ Ｓｃｉｍｅｄ，Ｉｎｃ．|Medical device with tear resistant flexible circuit assembly|

---

US20150209107A1|2014-01-24|2015-07-30|Denervx LLC|Cooled microwave denervation catheter configuration|

---

US11000679B2|2014-02-04|2021-05-11|Boston Scientific Scimed, Inc.|Balloon protection and rewrapping devices and related methods of use|

---

WO2015119890A1|2014-02-04|2015-08-13|Boston Scientific Scimed, Inc.|Alternative placement of thermal sensors on bipolar electrode|

---

CN106572875A|2014-02-07|2017-04-19|沃夫医药公司|Methods and systems for ablation of the renal pelvis|

---

US10813686B2|2014-02-26|2020-10-27|Medtronic Advanced Energy Llc|Electrosurgical cutting instrument|

---

BR112016024049A2|2014-04-15|2017-08-15|Qmax Llc|catheter for use with a guidewire and method for performing a medical procedure within a body lumen|

---

CN105012009B|2014-04-22|2018-09-28|上海微创电生理医疗科技有限公司|A kind of renal artery radiofrequency ablation electrode catheter|

---

EP3134018A1|2014-04-24|2017-03-01|Medtronic Ardian Luxembourg S.à.r.l.|Neuromodulation catheters having braided shafts and associated systems and methods|

---

US10610292B2|2014-04-25|2020-04-07|Medtronic Ardian Luxembourg S.A.R.L.|Devices, systems, and methods for monitoring and/or controlling deployment of a neuromodulation element within a body lumen and related technology|

---

KR101672879B1|2014-04-29|2016-11-07|재단법인 아산사회복지재단|Catheter assembly|

---

CN106659531A|2014-05-07|2017-05-10|毕达哥拉斯医疗有限公司|Controlled tissue ablation techniques|

---

CN106794031B|2014-05-22|2020-03-10|埃杰亚医疗公司|Integrity testing method and apparatus for delivering vapor to uterus|

---

US9993290B2|2014-05-22|2018-06-12|Aegea Medical Inc.|Systems and methods for performing endometrial ablation|

---

US10405924B2|2014-05-30|2019-09-10|The Spectranetics Corporation|System and method of ablative cutting and vacuum aspiration through primary orifice and auxiliary side port|

---

US20150355413A1|2014-06-04|2015-12-10|Corning Incorporated|Integrated torque jacket systems and methods for oct|

---

CN104068930A|2014-06-04|2014-10-01|远见企业有限公司|Renal denervation ablation catheter with pre-bent catheter body|

---

JP6342247B2|2014-07-18|2018-06-13|オリンパス株式会社|Ultrasonic energy treatment device|

---

EP3171764A1|2014-07-22|2017-05-31|Koninklijke Philips N.V.|Intravascular devices, systems, and methods having a core wire with multiple flattened sections|

---

WO2016033543A1|2014-08-28|2016-03-03|Medtronic Ardian Luxembourg S.A.R.L.|Methods for assessing efficacy of renal neuromodulation and associated systems and devices|

---

CN107072708B|2014-09-23|2020-02-18|韩德卡洛斯医药株式会社|Catheter and method of manufacturing the same|

---

WO2016054379A1|2014-10-01|2016-04-07|Medtronic Ardian Luxembourg S.A.R.L.|Systems and methods for evaluating neuromodulation therapy via hemodynamic responses|

---

CN105615990B|2014-10-29|2019-07-23|上海微创电生理医疗科技股份有限公司|A kind of electrophysiologicalcatheter catheter|

---

US9981119B2|2014-10-29|2018-05-29|Edwards Lifesciences Corporation|Bi-directional cannula|

---

WO2016075536A2|2014-11-14|2016-05-19|Medtronic Ardian Luxembourg S.A.R.L.|Catheter apparatuses for modulation of nerves in communication with the pulmonary system and associated systems and methods|

---

KR20170107428A|2014-11-19|2017-09-25|어드밴스드 카디악 테라퓨틱스, 인크.|Ablation devices, systems and methods of using a high-resolution electrode assembly|

---

JP6673598B2|2014-11-19|2020-03-25|エピックス セラピューティクス，インコーポレイテッド|High resolution mapping of tissue with pacing|

---

CA2969448A1|2014-12-01|2016-06-09|PAVmed Inc.|Self-anchoring catheters and methods of use|

---

US10667736B2|2014-12-17|2020-06-02|Medtronic Ardian Luxembourg S.A.R.L.|Systems and methods for assessing sympathetic nervous system tone for neuromodulation therapy|

---

US9737361B2|2014-12-18|2017-08-22|Abbott Cardiovascular Systems Inc.|System and method for a catheter|

---

EP3360497A1|2015-02-03|2018-08-15|Shanghai Golden Leaf Med Tec Co., Ltd|Radio-frequency ablation catheter having spiral structure and device thereof|

---

US10376308B2|2015-02-05|2019-08-13|Axon Therapies, Inc.|Devices and methods for treatment of heart failure by splanchnic nerve ablation|

---

US10188456B2|2015-02-18|2019-01-29|Medtronic Xomed, Inc.|Electrode assembly for RF energy enabled tissue debridement device|

---

CA2975389A1|2015-02-18|2016-08-25|Medtronic Xomed, Inc.|Rf energy enabled tissue debridement device|

---

US10376302B2|2015-02-18|2019-08-13|Medtronic Xomed, Inc.|Rotating electrical connector for RF energy enabled tissue debridement device|

---

CN107530004A|2015-02-20|2018-01-02|Mc10股份有限公司|The automatic detection and construction of wearable device based on personal situation, position and/or orientation|

---

US11077301B2|2015-02-21|2021-08-03|NeurostimOAB, Inc.|Topical nerve stimulator and sensor for bladder control|

---

CN104667410B|2015-03-12|2017-07-25|深圳橙果医疗科技有限公司|Spine epidural minimally-invasive catheter system|

---

US9636244B2|2015-04-09|2017-05-02|Mubin I. Syed|Apparatus and method for proximal to distal stent deployment|

---

PL3282988T3|2015-04-13|2021-05-17|Carlos Fernando Bazoberry|Radiofrequency denervation needle|

---

EP3282927B1|2015-04-14|2020-08-26|Koninklijke Philips N.V.|Intravascular devices and methods having a polymer jacket formed around communication lines wrapped around a core member|

---

US10383685B2|2015-05-07|2019-08-20|Pythagoras Medical Ltd.|Techniques for use with nerve tissue|

---

JP2017006337A|2015-06-19|2017-01-12|ソニー株式会社|Medical assist device and method, and medical assist system|

---

US11051875B2|2015-08-24|2021-07-06|Medtronic Advanced Energy Llc|Multipurpose electrosurgical device|

---

KR101748032B1|2015-09-03|2017-06-14|한국과학기술원|Method and System for Renal Denervation using Integrated Circuit embedded multi electrode|

---

CN105193498B|2015-09-18|2019-03-08|先健科技有限公司|Ablation catheter apparatus|

---

US10207110B1|2015-10-13|2019-02-19|Axon Therapies, Inc.|Devices and methods for treatment of heart failure via electrical modulation of a splanchnic nerve|

---

US10492936B2|2015-10-30|2019-12-03|Ram Medical Innovations, Llc|Apparatus and method for improved access of procedural catheter in tortuous vessels|

---

US9980838B2|2015-10-30|2018-05-29|Ram Medical Innovations Llc|Apparatus and method for a bifurcated catheter for use in hostile aortic arches|

---

US11020256B2|2015-10-30|2021-06-01|Ram Medical Innovations, Inc.|Bifurcated “Y” anchor support for coronary interventions|

---

US10779976B2|2015-10-30|2020-09-22|Ram Medical Innovations, Llc|Apparatus and method for stabilization of procedural catheter in tortuous vessels|

---

US10327929B2|2015-10-30|2019-06-25|Ram Medical Innovations, Llc|Apparatus and method for stabilization of procedural catheter in tortuous vessels|

---

US20170143405A1|2015-11-20|2017-05-25|Covidien Lp|Apparatuses, systems and methods for treating ulcerative colitis and other inflammatory bowel diseases|

---

US10716612B2|2015-12-18|2020-07-21|Medtronic Advanced Energy Llc|Electrosurgical device with multiple monopolar electrode assembly|

---

JP6570181B2|2016-01-12|2019-09-04|清明 本間|Catheter and catheter system|

---

US10448994B2|2016-01-13|2019-10-22|Abbott Cardiovascular Systems Inc.|Method of manufacturing a shaping structure for denervation|

---

CN108781314A|2016-02-22|2018-11-09|Mc10股份有限公司|System, apparatus and method for personal data and power transmission|

---

WO2017147253A1|2016-02-26|2017-08-31|The Johns Hopkins University|Methods for selective treatment of renal sympathetic nerves|

---

WO2017160808A1|2016-03-15|2017-09-21|Advanced Cardiac Therapeutics, Inc.|Improved devices, systems and methods for irrigated ablation|

---

US10118696B1|2016-03-31|2018-11-06|Steven M. Hoffberg|Steerable rotating projectile|

---

EP3442457A4|2016-04-14|2020-01-01|Brandner, Theresa|Medical devices utilizing shape memory alloys and associated systems and methods|

---

US10524859B2|2016-06-07|2020-01-07|Metavention, Inc.|Therapeutic tissue modulation devices and methods|

---

US11160542B2|2016-06-09|2021-11-02|Haimachek, Inc.|Collector for detection and reversible capturing of cells from body fluids in vivo|

---

WO2017214402A1|2016-06-09|2017-12-14|Boston Scientific Scimed, Inc.|Infusion catheter|

---

US10173031B2|2016-06-20|2019-01-08|Mubin I. Syed|Interchangeable flush/selective catheter|

---

CA3031766A1|2016-07-29|2018-02-01|Howard Levin|Devices, systems, and methods for treatment of heart failure by splanchnic nerve ablation|

---

US10447347B2|2016-08-12|2019-10-15|Mc10, Inc.|Wireless charger and high speed data off-loader|

---

WO2018061002A1|2016-09-29|2018-04-05|Magenta Medical Ltd.|Blood vessel tube|

---

EP3496642B1|2016-10-04|2021-11-17|St. Jude Medical, Cardiology Division, Inc.|Devices for estimating tip-tissue coupling of an ablation catheter tip|

---

US20180092682A1|2016-10-05|2018-04-05|Medtronic Ardian Luxembourg S.A.R.L.|Spiral electrode for neuromodulation therapy|

---

EP3556409B1|2016-10-25|2022-01-05|Magenta Medical Ltd.|Ventricular assist device|

---

US10231784B2|2016-10-28|2019-03-19|Medtronic Ardian Luxembourg S.A.R.L.|Methods and systems for optimizing perivascular neuromodulation therapy using computational fluid dynamics|

---

WO2018081396A1|2016-10-31|2018-05-03|Cook Medical Technologies Llc|Medical device with a shape-memory alloy coated inner surface|

---

CN110049792B|2016-11-23|2022-01-18|马真塔医药有限公司|Blood pump|

---

US10548566B2|2016-12-08|2020-02-04|Metal Industries Research & Development Centre|System and method for tracking signal of wire in a blood vessel|

---

CN106691383A|2016-12-27|2017-05-24|天津恒宇医疗科技有限公司|High-passing-ability OCT imaging catheter|

---

US10828091B2|2016-12-28|2020-11-10|Biosense WebsterLtd.|Catheter with tapered support member for variable arcuate distal assembly|

---

WO2018164766A1|2017-03-06|2018-09-13|Ram Medical Innovations Llc|Apparatus and method for improved access of procedural catheter in tortuous vessels|

---

US11116450B2|2017-03-09|2021-09-14|Biosense WebsterLtd.|Electrode assembly having spines with controlled flexibility|

---

US10918832B2|2017-03-27|2021-02-16|Biosense WebsterLtd|Catheter with improved loop contraction and greater contraction displacement|

---

WO2018200865A1|2017-04-27|2018-11-01|Epix Therapeutics, Inc.|Determining nature of contact between catheter tip and tissue|

---

US20190008577A1|2017-07-05|2019-01-10|Medtronic Ardian Luxembourg S.A.R.L.|Methods for treating sleep disorders in patients via renal neuromodulation|

---

US10945788B2|2017-07-05|2021-03-16|Medtronic Ardian Luxembourg S.A.R.L.|Methods for treating depression in patients via renal neuromodulation|

---

AU2018204841A1|2017-07-05|2019-01-24|Medtronic Ardian Luxembourg S.A.R.L.|Methods for treating post-traumatic stress disorder in patients via renal neuromodulation|

---

US11071557B2|2017-10-19|2021-07-27|Medtronic Vascular, Inc.|Catheter for creating pulse wave within vasculature|

---

US10765475B2|2017-10-31|2020-09-08|Biosense WebsterLtd.|All-in-one spiral catheter|

---

WO2019094365A1|2017-11-07|2019-05-16|Neurostim Oab, Inc.|Non-invasive nerve activator with adaptive circuit|

---

US10561461B2|2017-12-17|2020-02-18|Axon Therapies, Inc.|Methods and devices for endovascular ablation of a splanchnic nerve|

---

US10905808B2|2018-01-10|2021-02-02|Magenta Medical Ltd.|Drive cable for use with a blood pump|

---

US10959669B2|2018-01-24|2021-03-30|Medtronic Ardian Luxembourg S.A.R.L.|Systems and methods for assessing the efficacy of neuromodulation therapy|

---

US20190223754A1|2018-01-24|2019-07-25|Medtronic Ardian Luxembourg S.A.R.L.|Systems, devices, and methods for assessing efficacy of renal neuromodulation therapy|

---

US11253189B2|2018-01-24|2022-02-22|Medtronic Ardian Luxembourg S.A.R.L.|Systems, devices, and methods for evaluating neuromodulation therapy via detection of magnetic fields|

---

US20190223949A1|2018-01-24|2019-07-25|Medtronic Ardian Luxembourg S.A.R.L.|Multielectrode catheter|

---

US20190223944A1|2018-01-24|2019-07-25|Medtronic Ardian Luxembourg S.A.R.L.|Controlled irrigation for neuromodulation systems and associated methods|

---

US10786306B2|2018-01-24|2020-09-29|Medtronic Ardian Luxembourg S.A.R.L.|Denervation therapy|

---

US11007075B2|2018-02-18|2021-05-18|Ram Medical Innovations, Inc.|Vascular access devices and methods for lower limb interventions|

---

US11167095B2|2018-03-08|2021-11-09|Spiration, Inc.|Variable pitch flexible needle|

---

US10893927B2|2018-03-29|2021-01-19|Magenta Medical Ltd.|Inferior vena cava blood-flow implant|

---

US11071585B2|2018-09-14|2021-07-27|Biosense WebsterLtd.|Systems and methods of ablating cardiac tissue|

---

US11266817B2|2018-10-25|2022-03-08|Medtronic Vascular, Inc.|Cavitation catheter|

---

CN113423462A|2018-10-26|2021-09-21|丹拿·凯米|Device and method for treating gastrointestinal tract diseases through oropharynx minimally invasive|

---

US11045628B2|2018-12-11|2021-06-29|Biosense WebsterLtd.|Balloon catheter with high articulation|

---

JP6808709B2|2018-12-25|2021-01-06|清明 本間|Catheter and catheter system|

---

EP3782668B1|2019-01-24|2021-08-11|Magenta Medical Ltd.|Housing for an impeller|

---

KR102227910B1|2019-05-13|2021-03-12|인제대학교 산학협력단|Multiple electrode wire and system containing the same|

---

WO2021186599A1|2020-03-18|2021-09-23|日本ライフライン株式会社|Ablation system|

---

CN111544110B|2020-05-06|2021-07-20|安进医疗科技（北京）有限公司|Endoscopic surgery electrode assembly|

---

KR102296026B1|2020-12-03|2021-09-02|주식회사 딥큐어|Electrode device|

---

KR102347531B1|2021-06-08|2022-01-07|주식회사 딥큐어|Electrode unit and electrode device comprising the same|

法律状态:
2020-03-24| B06F| Objections, documents and/or translations needed after an examination request according [chapter 6.6 patent gazette]|

---

2020-06-02| B06U| Preliminary requirement: requests with searches performed by other patent offices: procedure suspended [chapter 6.21 patent gazette]|

---

2020-09-15| B11B| Dismissal acc. art. 36, par 1 of ipl - no reply within 90 days to fullfil the necessary requirements|

---

2021-10-13| B350| Update of information on the portal [chapter 15.35 patent gazette]|

优先权:

---

申请号 | 申请日 | 专利标题

---

US40653110P| true| 2010-10-25|2010-10-25|

---

US61/406531|2010-10-25|

---

US40696810P| true| 2010-10-26|2010-10-26|

---

US61/406960|2010-10-26|

---

US201161572290P| true| 2011-01-28|2011-01-28|

---

US61/572290|2011-01-28|

---

US201161528001P| true| 2011-08-26|2011-08-26|

---

US201161528108P| true| 2011-08-26|2011-08-26|

---

US201161528091P| true| 2011-08-26|2011-08-26|

---

US201161528086P| true| 2011-08-26|2011-08-26|

---

US61/528086|2011-08-26|

---

US61/528001|2011-08-26|

---

US61/528108|2011-08-26|

---

US61/528091|2011-08-26|

---

US201161528684P| true| 2011-08-29|2011-08-29|

---

US61/528684|2011-08-29|

---

US201161546512P| true| 2011-10-12|2011-10-12|

---

US61/546512|2011-10-12|

---

PCT/US2011/057756|WO2012061161A1|2010-10-25|2011-10-25|Catheter apparatuses having multi-electrode arrays for renal neuromodulation and associated systems and methods|

---