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    • 专利摘要:
    catheter orifice showing a flow interruption feature. there is a peripheral catheter with a catheter for reducing the rate of exit of an infusion component inside the catheter. there is the provision of pluralities of lateral diffusion holes close to the top portion of the catheter. some examples also include pluralities of diffusion orifices in annularly positioned stages being provided in the pointed portion of an intravenous catheter for an alignment of the infusion stream sent from the diffusion orifices. the internal surface of each diffusion orifice is angled at an additional angle relative to the internal surface of the catheter lumen so that an infusion component inside the lumen leaves the catheter through the diffusion holes and an angle that will be less than 90 <198>.
    公开号:BR112013003367B1
    申请号:R112013003367
    申请日:2011-08-02
    公开日:2020-02-04
    发明作者:Jason Mckinnon Austin；m adams Chad；O'bryan Jeff
    申请人:Becton Dickinson Co；
    IPC主号:
    专利说明:

    “PERIPHERAL CATHETER UNDERSTANDING CATHETER HOUSING AND A PLURALITY OF HOLES”
    Background of the Invention [001] The present invention relates, in general terms, to vascular infusion systems and components, including catheter assemblies and devices used with catheter assemblies. In particular, the present invention relates to systems and methods aimed at improving the efficiency of the placement of catheter orifices in order to provide with more accentuated infusion flow rates, lower pressures in the system, and reduction of the outflow velocities of the catheter. In addition, the present invention relates to improving the energy dissipation of the fluid jets being expelled through the holes present in the catheter.
    [002] Vascular access devices are used to introduce fluid into a patient's anatomy. For example, vascular access devices, such as catheters, are usually used for infusing fluid, such as saline, various types of medication, and / or complete parenteral nutrition with a patient, with blood drawn from the patient. patient, and / or the monitoring of various parameters related to the patient's vascular system.
    [003] A variety of clinical circumstances, including major trauma, major surgical procedures, major burns, and certain disease conditions, such as pancreatitis and diabetic ketoacidosis, can lead to severe drops in circulatory volume . These falls can be due to both the present loss of blood and an internal fluid imbalance. In these clinical conditions, it is often necessary to infuse blood and / or another type of fluid quickly with the patient to prevent the occurrence of serious consequences.
    [004] In addition, the ability to inject large amounts of fluid quickly can be desirable for certain medical and diagnostic procedures. For example, some diagnostic reproduction procedures use the contrast enhancement of current media to improve conspicuity in an attempt to expand
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    2/29 if the field of diagnoses prematurely. These procedures require viscous contrast media to be injected through a specialized injection propulsion pump intravenously at very high flow rates, which establishes a contrast cake or a small potion of contrast media in the patient's bloodstream. resulting in an improvement in image quality.
    [005] Propulsion injection procedures generate high pressures inside the infusion system, requiring the presence of specialized vascular access devices, extensive adjustments, adjustments for media transfer, pumping syringes, and pre-filled or bulky syringes for contrast media. As the infusion rate and concentration (and therefore the viscosity) of the contrast media continue to be increased, the cake density also increases resulting in better image quality via computed tomography (CT) attenuation. Therefore, a current trend regarding medical care is to increase the density of the cake relevant to the contrast media by increasing both the concentration of the contrast media and the rate at which a media is infused into the patient, all these aspects ultimately make the system pressure requirements higher.
    [006] Intravenous infusion rates can be set either routinely at up to 999 cubic centimeters per hour (cc / hr), or quickly, usually between around 999 cc / hr and 90000 cc / hr (1, 5 liters per minute) or even higher. For some diagnostic procedures using viscous contrast media, an injection rate of around 1 to 10 ml / second is necessary to ensure sufficient cake concentration. Propulsion injections of viscous media for this injection rate produce significant return pressures within the infusion system that commonly result in the failure of the components of the infusion system.
    [007] Traditionally, an immediate infusion therapy gives rise to the use of an intravenous catheter attached to a peristaltic pump and a fluid source. An infusion is made in a patient via a portion of the pointed end of the catheter inserted into the patient's vascular system with the pump forcing fluid through the catheter in direction
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    3/29 the patient's vein. The current ready-made infusion therapies make use of a catheter and a pointed end of the catheter with geometries identical to those used via routine, traditional infusion rates. These geometries include a thinning tip of the catheter so that the fluid can be accelerated as it moves through the pointed end towards the patient's vascular system. This acceleration of the infusion fluid is undesirable for several reasons.
    [008] For example, the thinned catheter generates a much higher back pressure for the rest of the catheter set. This effect is undesirable due to the limitations of the pumping capacity of the infusion pump as well as the limited structural integrity of the components and subcomponents of the infusion system. For example, if the back pressure becomes too high, the efficiency of the silly may decrease and certain seals or connections present inside the infusion system may fail. In addition, the acceleration of the fluid at the pointed end of the catheter results in a rewinding force that can lead to the displacement of the pointed end of the catheter inside the patient's vein, displacing the catheter and / or damaging the patient's vein and / or the injection site. The acceleration of the fluid also increases the speed of the jet under infusion close to the pointed end of the catheter. In some procedures, the jet of fluid can be broken into the patient's vein wall leading to an overflow or infiltration. Not only does this present itself as something uncomfortable and painful for the patient, the infiltration can also prevent the patient from receiving the necessary therapy.
    [009] Consequently, problems remain to be resolved regarding the increase in the speed of exit of an infusion during ready infusion procedures. In this way, the present specification introduces systems and methods aimed at reducing the rate of exit of an infusion, while preserving the increase in the infusion rate, as desired during prompt infusion procedures. In addition, the present specification introduces modifications to the system to increase momentum transfer in the jet streams of fluid leaving the catheter.
    Brief Summary of the Invention [010] The systems and methods of the present specification have been developed
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    4/29 to meet problems and technical needs that have not been fully resolved by the current infusion systems and methods available. In this way, these systems and methods were developed to provide safe and effective immediate infusion procedures.
    [011] One aspect of the present invention provides with an improved vascular access device for use in combination with a vascular infusion system capable of delivering rapid infusion to the patient's vascular system. The vascular access device generally includes an intravenous catheter configured to access a patient's vascular system. The intravenous catheter is attached to the vascular infusion system via a section of the intravenous tubing. The material of the intravenous catheter can include a polymer or metallic material compatible with the infusion procedures.
    [012] In some embodiments, a pointed portion of the intravenous catheter is modified to include a plurality of diffusion orifices. The pointed portion, in general, consists of a tapered profile, where the outer and inner surface of the pointed end tapers towards the far end of the catheter. The thin external surface provides a smooth transition between the narrow diameter of the pointed opening of the catheter and the wide diameter of the catheter tubing. Thus, as the pointed end of the catheter is introduced into the patient's vein, the thin outer surface facilitates easy insertion of the catheter through the access hole. The internal thinned surface, in general, comes to be provided for adjusted contact with the external surface of an introduction needle housed inside the catheter lumen. The introduction needle is provided to create an opening in the patient's vein through which the pointed end of the catheter is inserted. The thin internal surface ensures a hermetic seal between the internal surface of the catheter and the external surface of the needle. Following the placement of the catheter, the insertion needle is removed.
    [013] As the infusion passes through the thinned portion of the inner surface, the fluid flow of the infusion is accelerated due to the decrease in volume through the thinned pointed end. Thus, in some modalities, there is the strength
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    5/29 forming a plurality of diffusion holes through the thickness of the intravenous catheter wall in order to provide with a plurality of paths through the intravenous catheter wall. Thus, as the infusion flows through the catheter towards the pointed end of the catheter, a portion of the flow volume through the catheter is deflected through the diffusion holes instead of through the main opening of the pointed end of the catheter. To this end, the pressure inside the infusion system is reduced compared to systems that incorporate standard intravenous catheters. In addition, the plurality of diffusion orifices reduces the velocity of the jet emitted by the pointed end of the catheter, providing conditions at intensified flow rates as required for some diagnostic procedures without additional damage to the vein wall.
    [014] In some embodiments, the diffusion holes are arranged at the pointed end of the catheter in a sequence in stages so that an upstream diffusion hole is misaligned with a downstream hole. For this purpose, the fluid flow of an infusion operating from a downstream diffusion port is not affected by the fluid flow of an infusion operating from an upstream diffusion port. This feature provides an increase in flow efficiency through the downstream diffusion orifices.
    [015] In some embodiments of the present invention, a first set of diffusion holes is arranged in a first annular ring close to an axial position upstream of the pointed end of the catheter. A second set of diffusion orifices is additionally arranged in a second annular ring next to an axial position of the pointed end of the catheter which is located downstream of the first annular ring. In some embodiments, the holes in the first annular ring begin to sag from the holes in the second annular ring so that they are generally misaligned. In other embodiments, the holes in the first annular ring begin to be axially misaligned from the holes in the second annular ring at around 15 ° to about 60 °. Finally, in some embodiments, the holes in the first annular ring begin to sag axially from the holes in the second annular ring at around 45 °.
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    6/29 [016] In some embodiments, the diffusion holes are provided through the catheter wall at a predetermined hole angle. Specifically, the diffusion holes of the present invention include an inner wall surface that can be angled with respect to the inner wall of the catheter lumen. In some embodiments, the internal surface of the diffusion orifice is oriented at an angle of around 15 ° to about 75 ° in relation to the internal surface of the catheter lumen. In some embodiments, the hole angle of the diffusion orifice is selected in order to optimize the flow efficiency through the diffusion orifice, the tension of the catheter inside the vein, the centralized positioning of the pointed end of the catheter inside the vein, and reducing pressure in the system and the jet speed of the pointed end inside the infusion system.
    [017] In some modalities, one or more diffusion holes are positioned close to the far end of a catheter housing component. Specifically, the diffusion holes include a flow interruption feature. For example, in some embodiments, the flow interruption feature consists of the association of two or more diffusion orifices where the axis of each orifice is oriented to cross the axis of another orifice in the external space of the catheter housing. For this purpose, the streams of fluid jets leaving these holes will collide and interrupt the streams of jets. The resulting streams of dispersed jets lose energy and momentum more quickly than they do in the case of a single jet stream, decreasing the impact tension near the vessel walls.
    [018] In some embodiments, the flow interruption characteristic of the diffusion orifices includes the presence of a flow deregulator. Specifically, in some embodiments, the flow deregulator includes a wedge-shaped extension next to the orifice. In other types of modalities, the flow deregulator includes an internal projection. For example, in some embodiments, the internal projection is positioned close to the surface of the inner wall of the hole. In some embodiments, the orifice has a substantial drop shape. In some embodiments, the hole has an elongated geometry. The flow deregulator will interrupt the jet stream flowing through the diffusion orifice both by breaking it and by flattening its shape. By con
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    7/29 sequence, a stream leaving the diffusion orifice will have a thinner cross section or an interrupted and spread flow. The resulting interrupted jet stream will lose energy and momentum more quickly than it does for a single jet stream, decreasing tension and impact near vessel walls.
    [019] The present invention also includes methods for the manufacture of an intravenous catheter for the diffusion of an infusion component. Some methods include steps to provide an intravenous catheter and the formation of orifices in stages through the thickness of the intravenous catheter wall. Some methods of the present invention also include the use of a laser drill providing several holes in stages.
    Brief Description of the Different Views of the Drawings [020] In order to easily understand how the characteristics mentioned above and other aspects and advantages of the invention are obtained, we have a more particular description of the invention briefly described above with reference to its specific modalities which are illustrated in the attached drawings. These drawings detail only the typical modalities of the invention and should not be considered as limiting its scope.
    [021] Figure 1 comprises a perspective view of an infusion system according to a representative embodiment of the present invention.
    Figure 2 consists of a detailed perspective view of a catheter according to a representative embodiment of the present invention;
    Figure 3A consists of a perspective view of a pointed end of the catheter according to a representative embodiment of the present invention;
    Figure 3B consists of a side view of the cross section of the pointed end of the catheter of Figure 3A according to a representative embodiment of the present invention;
    Figure 4A consists of a perspective view of a pointed end of the catheter according to a representative embodiment of the present invention;
    Figure 4B consists of a side view of the cross section of one end
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    8/29 pointed of the catheter according to a representative embodiment of the present invention;
    Figure 5 comprises a graphical representation of the velocities of the pointed end of the jet for various flow rates according to the representative embodiments of the present invention;
    Figure 6 consists of a graphical representation of the system pressures for different flow rates according to the representative embodiments of the present invention;
    Figure 7A consists of a perspective view of a pointed end of the catheter in accordance with representative embodiments of the present invention;
    Figure 7B consists of a perspective view of a pointed end of the catheter in accordance with representative embodiments of the present invention;
    Figure 8 consists of a perspective view of a pointed end of the catheter according to the representative embodiments of the present invention;
    Figure 9 consists of a side view of the cross section of the pointed end of the catheter of Figure 8;
    Figure 10A consists of a perspective view of a pointed end of the catheter in accordance with representative embodiments of the present invention;
    Figure 10B consists of a side view of the cross section of the pointed end of the catheter of Figure 10A;
    Figure 11A consists of a perspective view of the pointed end of the catheter in accordance with representative embodiments of the present invention;
    Figure 11B consists of a side view of the cross section of the pointed end of the catheter of Figure 11A;
    Figures 12 to 19 comprise diffusion orifice shapes in accordance with representative embodiments of the present invention;
    Figure 20 comprises a side view of the cross section of a pointed end of the catheter according to the representative embodiments of the present invention;
    Figure 21 consists of a perspective view of a pointed end of the catheter in accordance with representative embodiments of the present invention.
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    9/29
    Detailed Description of the Invention [022] The modalities of the present invention will be better understood with reference to the drawings, where the reference numerals indicate functionally similar or identical elements. It can be readily understood that the components of the present invention, described in a generic way and illustrated through the figures in this report, will be positioned and designed in a wide variety of different configurations. In this way, the following more detailed description, represented by the figures, is not intended to restrict the scope of the invention in the manner as claimed, however, consisting only of a mere representation of its preferred modalities.
    [023] The systems and methods of the present invention are generally designed to be used in combination with a vascular infusion system capable of rapidly delivering an infusion component to a patient's vascular system. Referring to Figure 1, a vascular infusion system 110 is presented, according to a representative embodiment of the present invention. Infusion systems of this type are usually configured to work at internal pressures up to 2000 psi. Many systems operate in the 75 to 2000 psi range, while specific devices of this type work in the range of 100, 200, and 300 psi. The vascular infusion system 100 comprises a vascular access device 112 coupled to an injection pump 120 via a coiled extension assembly 130. In some embodiments, the infusion system 100 further comprises a safety device 140 positioned between the device vascular access valve 112 and the injection pump 120. In some embodiments, a safety device 140 is provided for automatic absorption of the fluid path of the infusion system 100, thus preventing excessive pressure build-up in the downstream infusion components.
    [024] An injection pump 120 generally consists of a fluid pumping apparatus configured to rapidly deliver an infusion component, such as blood, medications, and CT scanning contrast agents to the patient's vascular system . Desirable infusion components may also include
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    10/29 different fluids often showing high viscosity as needed for medical and diagnostic procedures. In some embodiments, the injection pump 120 consists of a propulsion injector capable of providing an infusion component to a patient at flow rates of around 10 mL / hour to around 1200 mL / minute. In some embodiments, a high rate of infusion flow is desirable for medical procedures where it is required to intensify the bolus density of an infusion component close to the patient's vascular system. For example, a trend in diagnostic reproduction procedures is the increased use of contrast media, which require viscous contrast media to be more rapidly propelled to the patient at a higher flow rate, resulting in an improvement in image quality. . Thus, in some embodiments, an injection pump 120 and a vascular access device 112 are selected to achieve a desirable infusion flow rate in a compatible manner.
    [025] A wound extension set 130 comprises, in general, a flexible or semi-flexible polymer tubing configured to supply with an infusion component from the injector pump 120 to the vascular access device 112. The extension set 130 includes a first coupler 132 aimed at connecting the extension set 130 to a downstream device 112 or 140. The extension set 130 further includes a second coupler 134 for connecting the extension set 130 to the injector pump 120. The coiled configuration of extension set 120 generally prevents unwanted absorption or seizure of set 130 during infusion procedures. However, a person skilled in the art will appreciate that extension set 130 can include any type of configuration capable of efficiently delivering an infusion component from an injector pump 120 to the patient via a vascular access device 112. In some embodiments, extension set 130 is coupled between a syringe and a vascular access device, with the infusion component being manually injected into the patient. In other embodiments, the infusion system comprises only a syringe and a vascular access device, coming in accordance with the present invention.
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    11/29 [026] The vascular access device 112 generally comprises an intravenous peripheral catheter. An intravenous peripheral catheter 114 coming in accordance with the present invention comprises in bulk a truncated or short catheter (usually 13 mm to 52 mm) inserted into a small peripheral vein. Such catheters generally comprise a diameter of approximately one gauge catheter 14 or smaller. The short length of the catheter 114 facilitates convenient placement of the catheter, making it more likely to be dislodged prematurely from the vein due to the patient's movement and / or the rewinding forces experienced during intravenous procedures. In addition, unlike central or intermediate peripheral catheters, intravenous peripheral catheters 114, in accordance with the present invention, comprise a thinning tip of a catheter 146 accommodating the use of an introducing needle to aid in the insertion of the catheter 114.
    [027] An insertion needle is typically inserted through catheter 114 so that a pointed end of the needle extends beyond the tapered pointed end 146. The tapered geometry of the tapered pointed end 146 conforms closely to the outer surface of the introduction needle. Both the outer and inner surfaces of the pointed end 146 are thinned towards the far end of the catheter 114. The outer surface of the pointed end 146 is thinned to provide a smooth transition from a smaller profile of the introducing needle to a larger profile the outside diameter of the catheter. The insertion of the insertion needle into the patient's vein provides an opening in the vein through which the thin, pointed end 146 of catheter 114 comes to be inserted. The thin, external surface of the pointed end 146 allows easy insertion of catheter 114 into the opening. Once the intravenous peripheral catheter 114 is inserted into the patient's vein, the introducing needle (not shown) is removed from the lumen of catheter 114 allowing infusion through catheter 114.
    [028] The tapered inner surface of the pointed end 146 provides a secure seal between the inner surface of the pointed end 146 of the catheter and the outer surface of the introducing needle (not shown). Additionally, the super
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    12/29 thinned internal surface of the pointed end 146 leads to an acceleration of the infusion component within the lumen of the catheter as the infusion component flows near and through the pointed end 146 of the catheter. The specifications referring to the geometries of the thinned inner surface of the pointed end 146 are provided in connection with Figures 3B and 4B below. Following the infusion procedure, the peripheral intravenous catheter 114 is simply removed from the vein and discarded.
    [029] A desired infusion component is typically supplied to catheter 114 via a section of intravenous tubing 116 coupled to catheter 114. In some embodiments, a y-adapter 118 is attached to an end of tubing 116 opposite catheter 114, allowing for that the vascular access device 112 will be coupled to the rest of the vascular infusion system 100. A technician specialized in the field will observe possible variations and specific aspects of the available vascular access devices 112 commonly used in medical and research areas. For example, in some embodiments, catheter 114, coming in accordance with the present invention, may include additional access locations, clamps, parallel intravenous lines, valves, couplers, introduction needles, and / or materials as needed for fit a specific application.
    [030] Referring to Figure 2, a catheter 214 is presented according to a representative embodiment of the present invention. Catheter 214 generally comprises a catheter adapter 218 configured to accommodate a tubular housing component 220. Catheter adapter 218 further includes an inlet receptacle 230 coupled to a section of intravenous tubing 216. The section of intravenous tubing 216 comes be further coupled to the upstream infusion components, as shown and described in connection with Figure 1 above.
    [031] The catheter adapter 218 facilitates the delivery of an infusion component inside the intravenous tubing 216 to the patient via a tubular housing component 220. An internal lumen of the catheter adapter 218 is in fluid communication with both an internal lumen intravenous tubing 216 and an internal lumen of the component and tubular housing 220. In some embodiments, the catheter adapter 218
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    13/29 further comprises an access receptacle 222. Access receptacle 222 is generally provided to allow direct access to the internal lumen of catheter adapter 218. In some embodiments, access receptacle 222 is accessed via a needle and syringe to deliver an infusion component to the patient via the tubular housing component 220. In other embodiments, an introducing needle or guiding wire is inserted into the access receptacle 222 and propelled through the inner lumen of the tubular housing component 220. In some embodiments, a pointed end portion of the introducing needle or guidewire (not shown) extends beyond the pointed end portion 240 of the tubular housing component 220. For however, the pointed end portion of the introducing needle or guidewire may provide an opening to the vascular system of the patient into which the tubular housing component 220 is introduced. Following the placement of the tubular housing component 220 into the patient's vein, the introducing needle or guidewire is removed from the access receptacle 222 thus establishing a fluid communication between the tubular housing component 220, the catheter adapter 218 and the intravenous tubing 216.
    [032] In some embodiments, the tubular housing component 220 comprises an intravenous catheter. The intravenous catheter generally comprises a flexible or semi-flexible biocompatible material, as commonly used in the art. In some embodiments, intravenous catheter 220 consists of a polymeric material, such as polypropylene, polystyrene, polyvinyl chloride, polytetrafluoroethylene, and the like. In other modalities, the intravenous catheter 220 consists of metallic material, such as surgical steel, titanium, cobalt steel and the like [033] The tubular housing component 220 can take any length, with the length being selected based on the application of catheter 214. For some applications, the tubular housing component 220 is inserted into the patient's peripheral vein. In other types of applications, the tubular housing component 220 is inserted into the patient's central vein. For quick infusion applications, the pointed end portion 240 of the tubular housing component 220 has been modified to include
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    14/29 are of a plurality of diffusion orifices 250. The diffusion orifices 250 are generally provided for diverting fluid from the main flow channel through the internal lumen of the tubular housing component 220. For this purpose, the orifices Diffusion 250 effectively delay the jet of the infusion component functioning from the pointed end of the catheter 240 during rapid infusion procedures. In addition, the plurality of infusion holes 250 increases the accumulated area of the opening of the pointed end of the catheter 242 releasing the general pressure present in the vascular infusion system 100.
    [034] Now having Figure 3A as a reference, there is the presentation of an end portion 320 away from the intravenous catheter 314, coming according to a representative embodiment of the present invention. As previously discussed, an outer surface of the pointed end 340 of the intravenous catheter 314 is modified to include a plurality of side orifices 350. The side orifices 350 are generally positioned next to the thinned pointed end 340 of the catheter 314 to provide an access through which the infusion component present inside the catheter 314 can function. The surface area of the side holes 350 combines with the surface area of the lumen opening 342 to increase the overall surface area through which an infusion component can function from the pointed end 340 of the intravenous catheter 314. The side holes 350 they are arranged in an annular manner at the pointed end 340 of the intravenous catheter 314 in order to align the adjacent holes along a common axis 360. For this purpose, an upstream hole 356 is directly aligned with the downstream holes 358.
    [035] Referring now to Figure 3B, we have a cross-sectional view of the intravenous catheter 314 of Figure 3a. As previously discussed, a portion 334 of the inner surface of the pointed end 340 is thinned leading to an acceleration of fluid flow 390 through the pointed end 340. The side holes 350 of the intravenous catheter 314 are formed through the catheter wall 354 so that an inner surface 364 of each orifice 350 is oriented at an angle 370 of approximately 90 ° to an inner surface 382 of catheter lumen 380. The side orifices 350 are generally positioned within the thinned portion 34 of the
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    15/29 pointed end 340 so that the speed of the fluid flow 390 increases through the thinned portion 334 of the infusion component 394 allowing operation through the side holes 350. As the infusion component works through the side holes 350, the pressure fluid inside the lumen 380 decreases. In addition, as the infusion component continues to function through the side holes 350, the jet speed of the pointed end of the infusion component also decreases.
    [036] Computational analysis of fluid dynamics in side orifices 350 at a 90 ° angle reveals that only a first half 374 of each orifice cross section 350 comes to be used by fluid flow 390. In some embodiments, a second half 376 of the cross-section of the side holes at 90 ° 350 comprises a recirculation margin 392. Therefore, in some embodiments, the side hole configuration at 90 ° 350 can demonstrate approximately an efficiency of approximately fifty percent through each side hole 350.
    [037] Referring again to Figure 4A, a distant end portion 420 of an intravenous catheter 414 is presented according to a representative embodiment of the present invention. Intravenous catheter 414 has been altered to include a plurality of diffusion holes in stages 450. One skilled in the art will note that the number and dimensions of diffusion holes 350 and 450 can be varied and adjusted to arrive at a flow rate. desired, a reduction in the speed of the pointed-tip jet, a reduction in vascular damage, and an increase in cake density. The diffusion orifices 350 and 450 are provided, in general, by means of manufacturing methods known in the art. For example, in some embodiments, the plurality of diffusion holes 350 and 450 is made available by means of a laser drill.
    [038] In some embodiments, a selected formation of diffusion orifices 450 increases the distance between adjacent orifices 450 structurally reinforcing the pointed end 440 of intravenous catheter 414, compared to some linear orifice formations. In other embodiments, a selected formation of the diffusion holes 450 aligns current lines from the diffusion holes 450
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    16/29 reducing the energy needed to divert the bulky mainstream flow from catheter lumen 490 into the diffusion holes 450.
    [039] For example, in some embodiments of the present invention, the diffusion orifices 450 came to be positioned in a staged configuration, according to the presentation provided. Consequently, an upstream hole 450 ends up misaligned with an adjacent downstream hole 458. In addition, downstream hole 458 is misaligned with an adjacent downstream hole 460. In some embodiments, upstream hole 456 is directly aligned with the downstream orifice 460 along a common axis 480. In other embodiments, each of the orifices, the upstream orifice 456, the downstream orifice 458 and the downstream orifice 460 are misaligned, so that none of them will be aligned along a common axis. In some embodiments, an upstream hole 456 begins to sag axially from a downstream hole 458 at around 15 ° to about 60 °. Finally, in some embodiments, an upstream hole 456 begins to sag axially from a downstream hole 458 by approximately 45 °.
    [040] The diffusion holes 450 are annularly arranged in the thinned portion of the pointed end 440 of the intravenous catheter 414 in a staged configuration, as discussed above. A first annular ring 402 comprises a plurality of diffusion holes 450 forming a first ring upstream of diffusion holes. In some embodiments, the holes in the first annular ring 402 are axially spaced equal distances from the adjacent holes in the first annular ring 402. In other embodiments, a non-uniform axial spacing is applied next to the holes in the first annular ring 402. In in some embodiments, a second annular ring 404 is provided downstream of the first annular ring 402, with the diffusion holes of the second annular ring 404 beginning to yield positioned relative to the diffusion holes of the second annular ring 404.
    [041] A gap 424 is provided between the adjacent holes of the first annular ring 402. In some embodiments, the gap 424 is provided to accommodate the width of the downstream hole 458, so that the downstream hole 458 and the gap 424 are present there
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    17/29 along a common axis (not shown). Furthermore, a downstream clearance 428 is provided to accommodate the width of an upstream hole 466, so that the upstream hole 466 and the downstream clearance 428 are aligned along a common axis (not shown) . The axial alignment of the upstream gap 424 and the downstream hole 458 prevents the ripple effect due to the absence of a diffusion hole directly upstream of the downstream hole 458. Similarly, the axial alignment of the downstream gap 428 and the upstream hole 466 prevents the wave effect due to the absence of a diffusion orifice directly downstream from the orifice 466.
    [042] The staged configuration of the first, second and third rings 402, 404 and 406 provides with an elongated clearance 426 forming a space between an upstream diffusion hole 452 of the first annular ring and a downstream diffusion hole 454, aligned axially, from the third annular ring 406. The length of the elongated clearance 426 generally provides with a sufficient distance between an upstream diffusion port 452 and a downstream diffusion port 454, so that the fluid pressure of a component of infusion from the upstream orifice 452 is approximately equal to the fluid pressure of an infusion component from the downstream orifice 454. In this way, the staged configuration of the diffusion orifices 450 ensures equal flow efficiency from the diffusion orifices upstream and downstream 452 and 454.
    [043] In some embodiments, the diffusion holes 450 are formed through the catheter wall 474 so that an inner surface 464 of each orifice 450 is oriented at an angle 470 that is acute to an internal thinned surface 482 of the lumen 490 catheter, as shown in Figure 4B. In some embodiments, the 470 angle is between about 15 ° and about 75 °. In other embodiments, the 470 angle is approximately 45 °.
    [044] As set forth below, diffusion orifices and diffusion orifice formations decrease the fluid outlet force by operating from a pointed end of the catheter. Attention now turns to the geometry of diffusion orifices (also referred to simply in this report as orifices), and specifically to geometries that further decrease the fluid outlet force by operating from a
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    18/29 pointed end of the catheter. Figures 2-4B generically detail the circular diffusion holes. However, in some modalities, one or more of the diffusion holes may be non-circular. As shown in Figure 7A, a circular orifice 509 of a catheter 502 expels a substantially cylindrical stream of fluid 511 into a patient's vascular system. In general, this 511 jet is concentrated, direct and slowly breaks into the vein. It follows that the non-circular orifice 510, illustrated according to Figure 7B, expels a jet of fluid 513 having a substantially non-circular cross section, and therefore a greater surface area. The increase in the surface area of the jet 513 increases the moment transfer rate between the jet 513 and the intravenous environment compared to that referring to the more cylindrical jet 511 of Figure 7A. In this way, the jet 513 acting from the non-circular orifice 510 disperses and decelerates more quickly, representing a lower risk of leakage near the vein walls.
    [045] In addition to the use of non-circular orifice geometries, the interruption of flow can be further facilitated by the inclusion of a flow interruption feature next to the diffusion orifice. By a flow interruption characteristic, it refers to a characteristic of the orifice that substantially breaks, thinning or slowing the jet of fluid leaving an orifice so that the jet will lose speed more quickly inside the vein. The flow interruption characteristics comprise orifice characteristics that facilitate the rupture of the flow of a jet of fluid as it passes through the orifice and / or comes to leave the orifice. Flow interruption features include a flow deregulator, elongated orifice geometries, and orifice orientation so that the flow axis of two or more orifices will collide. We have the illustration through Figures 20-21 of non-limiting examples of orifice interruption characteristics including two or more orifices whose flow axes collide.
    [046] As indicated, a type of flow interruption characteristic consists of a flow deregulator. A flow deregulator comprises a deviation in the geometry of the orifices from a rounded orifice, a circular orifice, or an orifice
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    19/29 elliptical. In this way, flow deregulators include internal projections and highlighted extensions. A non-limiting example of an orifice having a flow deregulator consists of an orifice substantially configured as a drop including an outlined extension. Another non-limiting example of an orifice featuring a flow deregulator consists of an orifice having one or more internal projections. An internal projection refers to a portion of an orifice periphery that projects towards the inner portion of the orifice. In this way, there is an area of cross-section of the orifice where a straight line interposed above the cross-section can cross the perimeter of the orifice more than twice, as illustrated in Figure 12. Non-limiting examples of such types of internal projections are illustrated in Figures 8-16.
    [047] Referring now to Figures 8-9, a remote end portion 514 of an intravenous catheter 502 is shown according to a representative embodiment of the present invention. The intravenous catheter 502 has been modified to include a plurality of non-circular diffusion holes 508 and 510 in addition to the distal lumen opening 504. The number and dimensions of the diffusion holes 508 and 510 can be varied and adjusted to if a desired flow rate is reached, a reduction in the jet speed of the pointed end, a reduction in vascular damage, and an increase in the density of the bolus. According to the illustration, at least a portion of each diffusion orifice is located next to the thinned portion 506 of the pointed end of the catheter so that all of the fluid is introduced close to the pointed end of the patient's catheter. In other embodiments, a diffusion orifice is positioned entirely on the outside of the thinning portion of the pointed end of the catheter, but close to the distant portion 514 of catheter 502.
    [048] Referring now to Figure 9, a cross-sectional view of the catheter 502 is shown along the central part of the diffusion holes 508 and 510. According to the illustration, the holes 508 and 510 are oriented to an angle 528, with respect to the central axis 512 of the catheter lumen and the surface away from the orifice 524 (the angle of the orifice away), identical to the angle 526 between the central axis 512 of the catheter lumen and the surface away from the orifice 524 ( the near orifice angle). In others
    Petition 870190115460, of 10/11/2019, p. 31/43
    20/29 modalities, the angles of the distant orifice 528 and of the close orifice 526 differ in order to provide with a more diffuse jet of fluid coming from the orifice. For example, if the orifice angle 528 is greater than the nearby orifice angle 526, the fluid seeping into the orifice collides and interrupts the outlet jet, increasing the energy dissipation of the resulting jet. In other embodiments, the orifice angle 528 is less than the nearby orifice angle 526 so that the jet of fluid leaving the orifice expands and disperses as it passes through the orifice.
    [049] The fluid passing through the catheter 508 generally moves downward from the lumen towards the lumen opening of the catheter 504. The internal surface of the lumen includes one or more internal orifice openings 530, through where part of the fluid enters. As the fluid moves through the orifice, the heights and geometries of the inner wall surface 520 of the orifice modify the jet of fluid that exits through the outer orifice opening 532. In addition, the shapes of the openings in the inner and outer orifices 530 and 532 affect the fluid jet outlet. In some embodiments, the shape of the opening of the internal orifice differs from the shape of the opening of the external orifice to modify the fluid stream leaving with marked dissipation properties.
    [050] Continuing with reference to Figures 8-9, the flow of fluid leaving the diffusion orifices 508 and 510 is interrupted by means of two flow deregulators associated with each diffusion orifice. Specifically, the orifices 508 and 510 include a droplet shape, or a droplet-shaped cross section, having a protruding extension 509 and 511. The protruding extension increases the surface area of the expelled jet to increase flow interruption. The orifices 508 and 510 additionally comprise an internal projection 516 and 518 positioned on the inner wall surface of the diffusion orifice. The internal projection extends internally towards an internal portion of the orifice. As the fluid flows quickly through the orifice, the internal projection interrupts the direct flow, creating turbulence inside the jet expelled through the orifice. Turbulence inside the jet may cause the jet to rupture, be expanded, or to be delayed, and in the final analysis the rate of momentum may eventually be transferred from the jet to the intravenous environment.
    Petition 870190115460, of 10/11/2019, p. 32/43
    21/29 [051] Figures 10A to 16 illustrate additional modalities of internal projections that lead to the rupture inside a jet of fluid leaving a diffusion orifice. Referring now to Figures 10A and 10B, a diffusion orifice 542 in a catheter 540 includes an inner projection 544. With the inner projection 544 being arranged on the inner wall surface 548 of orifice 542 near the outlet of the orifice. In this way, the flow of fluid passing through the orifice 542 is interrupted by the internal projection that forces the fluid flow paths 546 inside the orifice 542 to collide with each other, creating turbulence, and creating an increase in dispersion and expansion of the trajectory of the expanded jet 547 of the jet of fluid being expelled.
    [052] Referring now to Figures 11A and 11B, there is an illustration of a catheter 550, according to some modalities, showing a diffusion orifice 552 containing an internal projection 554 on the inner wall surface 558 of orifice 552. The internal projection 554 extends between the internal and external orifice openings. The fluid flowing through orifice 552 has a larger surface area than would be the case when flowing through a circular orifice, with the outlet jet breaking more rapidly into the vein environment.
    [053] Reference is made to Figures 12 to 16, which detail the geometries of holes showing at least one internal projection. These structures protrude towards an internal portion of the orifice, so that an area of cross-section of the orifice is present where a straight line interposed above the cross-section may cross the perimeter of the orifice more than twice. This situation is illustrated in Figure 12. Figure 12 is again taken as a reference, illustrating a cross section of an orifice 570 showing an internal projection. A line, which is not a constant part of the structural component of the orifice, merely illustrated for the sake of clarity, is presented across the perimeter of the orifice at four points 575, 576, 577, and 578. Consequently, structure 572 qualifies as a internal projection as a function of the straight line 577 crossing the perimeter of the hole more than twice.
    [054] In some embodiments, as in Figure 13, an orifice 580 includes two internal projections 582 and 584. In other embodiments, as in Figure 14, an orifice 590 includes
    Petition 870190115460, of 10/11/2019, p. 33/43
    22/29 three internal projections 592, 594, and 596. In still other modalities, a hole includes more than three internal projections. As an internal projection increases the surface area of the resulting fluid stream, it follows that each increased internal projection increases the surface area itself in the same way. Consequently, the number and dimensions of the internal projections arranged in a diffusion orifice can be varied and adjusted to achieve a desired jet break, a jet thinning, and a jet delay. Additionally, in some embodiments, as shown in Figure 15, an orifice 600 may include an internal non-rounded projection 602, such as a square projection. Alternatively, in other types of modalities, the internal projection can assume the triangular, trapezoidal, rectangular shape, etc. Furthermore, in some embodiments, multiple internal projections 612 are arranged adjacent to each other or substantially adjacent to each other, such as those described in hole 610 pertinent to Figure 16, constituting a serrated edge of the hole.
    [055] Referring now to Figures 17, an elongated diffusion orifice 620 is illustrated as having a length 624 greater than a width 622. As noted above, non-circular diffusion orifices have a larger surface area with fluid flowing through it showing greater energy dissipation properties. However, diffusion orifices having very substantial lengths in relation to the thickness of the peripheral catheter act as cuts within the catheter casing and can weaken the catheter casing. Consequently, in the case of peripheral catheters, there may be the inclusion of one or more elongated diffusion holes close to the distant portion of the catheter housing containing an orifice length 624 that is between 1.2 to 3.0 times the width of the catheter. orifice 622. In other embodiments, the orifice length is between 1.3 and 2.5 times the orifice width. In other embodiments, the length of the hole is between 1.4 and 2.2 times the width of the hole.
    [056] Figures 18 and 19 illustrate other elongated holes 630 and 640 showing cuneiform extensions 6365 and 646, according to some modalities. Specifically, Figure 18 illustrates an orifice 630 having a generic drop shape that
    Petition 870190115460, of 10/11/2019, p. 34/43
    23/29 aims to facilitate insertion with a patient. The orifice is elongated, having a length 636 and 632 generally larger than the width 634. Orifice 630 includes a main portion of orifice 632 and a cuneiform extension 636, which includes two straight or semi-straight surfaces 635 and 637 if extending from the main housing portion 632 directed to a point 638 away from the main housing portion 632. In some embodiments, hole 630 is oriented so that point 638 of the cuneiform extension is close to the side near the hole. As the catheter is inserted through a patient's skin, the skin can naturally be absorbed into the orifice. Once the catheter is advanced, the straight surfaces 635 and 637 gradually force the skin out of the orifice 630 preventing the protrusion of the skin from occurring if the side close to the orifice comprises a wide flat perpendicular surface in the direction of the insertion. Figure 19 details another type of drop-shaped orifice with a rounded cuneiform extension 646, a main portion of orifice 644, and an orifice width, according to some modalities. The rounded cuneiform extension 646 reduces the total length 644 and 647 of the orifice 640 to increase the strength of the catheter housing.
    [057] Reference is now made to Figure 20, illustrating a cross-sectional view of a catheter 700 featuring a catheter head 702 comprising two diffusion holes 704 and 706. According to the illustration, the two holes are oriented so that the jet of fluid leaving the first orifice 704 will collide with the jet of fluid leaving the second orifice 706. Consequently, the angle between the lumen and the first orifice axis 708 is, in general, greater than the angle between the lumen and the second axis of the orifice 710, so that the orientations of the two axes cause the jets of expelled fluids to collide. Once these jets of fluid collide, the force and orientation of each act causes the interruption next to the other jet, dispersing the fluid, slowing it down, and / or causing turbulence within the area resulting from the interrupted flow 716.
    [058] To effectively reach collisions, the location of the collision may be closer to the surface of the catheter than the distance between the location
    Petition 870190115460, of 10/11/2019, p. 35/43
    24/29 of the holes next to the catheter housing 702 and a wall of the vein, so that the impact actually occurs, instead of the two jets coming to impact the vein wall. Consequently, in some modalities, the collision location is configured to be a distance away from the external surface of the catheter, with this distance becoming less than the total thickness of the catheter housing 702. In other modalities, the the distance is less than 150% of the thickness of the catheter housing 702. In other modalities, the distance is less than 200% of the thickness of the catheter housing 702. In still other modalities, the distance is less at 300% of the thickness of the catheter housing 702. Also, in other modalities, the distance is less than 50% of the thickness of the catheter housing 702. Furthermore, in some modalities, the angle 718 present between the first axis orifice 708 and the second orifice axis 710 is between 15 to 90 degrees.
    [059] In some embodiments, the flow can be interrupted by colliding the flow leaving a first diffusion orifice and the flow leaving a second smaller diffusion orifice. For example, one or more small diffusion holes are included at the pointed end of the catheter, and oriented so that the fluid leaving them will collide with the fluid leaving a wider diffusion orifice. In this way a greater number of holes can be included in the pointed end of the catheter without substantially weakening the pointed end with numerous holes of the same size.
    [060] Additionally, in some embodiments, the fluid leaving a diffusion orifice collides with the fluid leaving two or more other diffusion orifices. Referring now to Figure 21, which illustrates a catheter 720 containing three diffusion holes 722, 724, and 726, each having an orifice axis 728, 730, and 732, respectively, which leads to the fluid leaving the they will collide with the fluid leaving one of the other holes. Thus, in some modalities, the three holes are located in a generally triangular arrangement. In the other modalities, the three orifices are located in a generally linear arrangement, so that a jet starting from an upstream orifice collides with a jet coming from the downstream orifice.
    Petition 870190115460, of 10/11/2019, p. 36/43
    The resultant current still collides with a jet coming from some other orifice downstream. In addition, in some embodiments, the configuration of the diffusion orifice formation comprises an array of orifices oriented so that the outlet jets in each nearby orifice will collide with at least one jet leaving another orifice. For this, the sum of the outgoing jets will produce an infusion of fluid containing less impact energy and less risk to the vessel walls.
    [061] In some embodiments, a simple diffusion orifice includes more than one flow interruption feature. Examples of these flow interruption characteristics are described in this report, including at least internal projections, cuneiform extensions, an elongated orifice geometry, and orifice axis orientations that result in collisions with other jets of fluids. For example, in some embodiments, an orifice includes an internal projection and has an axis orientation that collides with the orientation of another orifice. In addition, in some embodiments, the orifice also includes a cuneiform extension. In other embodiments, other combinations of flow interruption characteristics are combined to provide a diffusion orifice configuration and diffusion holes in a more efficient and less dangerous catheter.
    [062] From the previous description, it can be seen that one or more flow interruption characteristics may come to be included in one or more catheter diffusion holes next to a pointed catheter end. The flow interruption feature can substantially interrupt, thin, or delay a jet of fluid leaving an orifice so that the jet will lose speed more quickly inside the vein producing less damage to the vessel walls. In particular, the flow interrupting characteristics are particularly advantageous when used in a ready-to-diffuse therapy that makes use of extremely high infusion speeds by rapidly introducing a fluid bolus into the patient through the pointed end of the catheter. During these procedures, one or more of the characteristics of interrupting the flow of a diffusion orifice may increase comfort in terms of infusion in the patient, reducing pain, allowing for higher infusion speeds, and preventing damage
    Petition 870190115460, of 10/11/2019, p. 37/43
    26/29 to the vessels.
    EXAMPLES [063] To reduce the amount of contrast media required to make a diagnosis, the concentration of contrast media per unit of blood volume needs to be increased by increasing the flow rate of contrast media without having increased speed at the pointed end of the catheter. The elements of the present invention achieve these required objectives, as the following examples demonstrate.
    Example 1: Comparison with Jet Speed at the Pointed Edge [064] The jet speeds near the pointed end of a standard catheter are adjusted to exceed 1000 inches / sec for a volumetric flow rate adjustment of 5ml / sec, results in a wide force applied to a patient's vein wall. This force is invaluable for patients being provided with non-exceptional vein structures, increasing the possibility of leakage or profound damage from increased flow rates.
    [065] Jet velocities at the pointed end for a standard 22 GA X 1.00 (Current V_tip) catheter were compared with a 22 GA X 1.00 catheter (V_tip Ex. 1 V_tip Ex.4) modified to include a plurality of diffusion holes, as described in connection with Figures 4A and 4B above. Quadruplicate samples from the modified catheter were tested for flow rates of 1 ml / sec, 2 ml / sec, 3 ml / sec, 4 ml / sec, and 5 ml / sec. The jet speed at the pointed end was then recorded for each sample and compared with the jet speed of the standard catheter for each flow rate. The experiment demonstrated that the overall jet velocity at the pointed end of the modified catheter decreased by 36% compared to the standard catheter. The results of the experiment are shown in Figure 5.
    Example 2: Comparison with System Pressure [066] The internal pressures inside an infusion system were compared between an infusion system using a standard 22 GA X 1.00 catheter and an infusion system using a catheter 22 GA X 1.00 (P_inj # 1 and P_inj # 2) modified to
    Petition 870190115460, of 10/11/2019, p. 38/43
    27/29 include a plurality of diffusion holes, in connection with the description provided by Figures 4A and 4B above.
    [067] The system pressure was measured both inside each infusion pump (P_inj Current, P_inj 1 and P + inj 2) and in the internal lumen of each catheter (P_sept Current, P_Sept 1 and P_sept2). The system pressure was tested and recorded at flow rates of 1 ml / sec, 2 ml / sec, 3 ml / sec, 4 ml / sec, and 5 ml / sec. The system pressures for each flow rate were then graduated, as shown in Figure 6.
    [068] The results of the experiment demonstrated an increase in the volumetric flow rate through a decrease in system pressure by approximately 30%, with the greatest reduction in pressure being indicated inside the lumen of the modified catheters.
    Example 3: Computational Analysis of Fluid Dynamics [069] Computational analysis of fluid dynamics was conducted for a standard 22 GA X 1.00 catheter modified to include a plurality of diffusion holes containing approximately 45 ° holes in relation to the surface of the catheter's inner wall. The analysis revealed a 6% increase in the displacement of the volumetric flow from the main stream inside the diffusion orifices, compared to a standard 22 GA X 1.00 catheter presenting a plurality of diffusion orifices containing 90 ° holes in relation to the surface of the internal wall of the catheter. The analysis also revealed a significant increase in the flow of fluid 492 through the cross-section of the diffusion orifice 450, compared to what occurs for orthogonal orifices of the standard catheter. While the diffusion orifices 450 of the present invention did show a slight recirculation margin 494, this recirculation margin 494 has significantly weakened compared to the recirculation margin 392 of the standard catheter. A representative presentation of fluid flow 492 is shown through Figure 4B.
    Example 4: Catheter Stabilization and Vein Centralization [070] In standard peripheral intravenous catheters, the internal lumen of the catheter tapers towards the pointed end of the catheter resulting in a rewinding force acting as the infusion component continues to accelerate through the cons
    Petition 870190115460, of 10/11/2019, p. 39/43
    28/29 trition. This force is concomitant with the force experienced when holding a fire hose. Like a fire hose, a pointed catheter end under a compression rewinding force is unstable and can oscillate violently inside the vein (also known as catheter falconing) causing damage to the vein, as previously discussed. If the axial direction of the infusion component is rotated enough, through the diffusion holes, then the rewinding force will become negative, pushing the pointed end of the catheter, tensioning it; this tensioned condition of the pointed end of the catheter will provide greater stability to the inserted catheter. Therefore, in some modalities, the bore angle is strategically selected to balance the increase in flow through the diffusion orifices and the decrease in rewinding force near the pointed end of the catheter by reducing the axial direction of the component. infusion flowing through the diffusion holes.
    [071] The hole angle also affects the placement of the catheter inside the vein. For example, when inserted into a vein, the venous catheter, in general, extends through the skin towards the vein at an angle of approximately 30 °. For this purpose, the pointed end of the venous catheter usually contacts or accommodates, against the internal wall of the vein opposite to the catheter insertion site. As the fluid flow increases, the high velocity of the jet coming from the pointed end of the catheter is exerted directly on the internal wall of the vein. However, when the pointed end of the venous catheter is changed to include diffusion receptacles, the bypass infusion component expelled from these diffusion receptacles pushes the pointed end of the catheter beyond the vein wall resulting in a centralized positioning in the pointed end of the catheter inside the vein. In this way, the velocity of the jet coming from the pointed end is directed into the fluid stream of the vein instead of into the vein wall.
    [072] The present invention can be embodied in other specific formats without deviating from its structures, methods, or other essential characteristics as described in a broad way by this report followed by a framework of claims.
    Petition 870190115460, of 10/11/2019, p. 40/43
    29/29
    The described modalities should be considered in all senses only as illustrative, and not restrictive. The scope of the invention comes to be indicated, therefore, through the attached claims table instead of the description made by this report. All changes that fall within the scope and scope equivalent to the claims framework must be included within that scope.
    权利要求:
    Claims (7)
    [1]
    1. Peripheral catheter (700), comprising:
    catheter housing (702) showing a near end, a far end, a lumen extending between the near and far ends, and a wide lumen opening, with the catheter housing still truncated enough to access a peripheral vein of a patient;
    a plurality of holes (704, 706) positioned at the far end of the catheter housing, each hole being formed through a wall thickness of the catheter housing and in communication with the lumen;
    CHARACTERIZED by the fact that a first orifice (704) and a second orifice (706) are oriented so that a first jet of fluid leaving the first orifice collides with a second jet of fluid leaving the second orifice.
    [2]
    2. Peripheral catheter according to claim 1, CHARACTERIZED by the fact that the first orifice and the second orifice are oriented so that the first jet of fluid collides with the second jet of fluid at a first distance from a surface outside of the catheter housing, the first distance being less than the wall thickness.
    [3]
    3. Peripheral catheter according to claim 1, CHARACTERIZED by the fact that the first orifice and the second orifice are oriented so that an angle between an axis of the first orifice and an axis of the second orifice is between 15 and 90 degrees.
    [4]
    4. Peripheral catheter according to claim 1, CHARACTERIZED by the fact that at least one of the plurality of orifices includes a cuneiform extension.
    [5]
    5. Peripheral catheter, according to claim 1, CHARACTERIZED by the fact that at least one of the plurality of holes includes an internal projection next to an internal wall surface of the hole.
    [6]
    6. Peripheral catheter, according to claim 1, CHARACTERIZED by the fact that at least one of the orifices has a substantial drop shape.
    [7]
    7. Peripheral catheter, according to claim 1, CHARACTERIZED by the fact that at least one of the holes has an elongated geometry.
    类似技术:
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    法律状态:
    2018-12-26| B06F| Objections, documents and/or translations needed after an examination request according [chapter 6.6 patent gazette]|
    2019-08-13| B06U| Preliminary requirement: requests with searches performed by other patent offices: procedure suspended [chapter 6.21 patent gazette]|
    2020-01-07| B09A| Decision: intention to grant [chapter 9.1 patent gazette]|
    2020-02-04| B16A| Patent or certificate of addition of invention granted [chapter 16.1 patent gazette]|Free format text: PRAZO DE VALIDADE: 20 (VINTE) ANOS CONTADOS A PARTIR DE 02/08/2011, OBSERVADAS AS CONDICOES LEGAIS. |
    优先权:
    申请号 | 申请日 | 专利标题
    US12/853,804|US8496629B2|2008-04-22|2010-08-10|Catheter hole having a flow breaking feature|
    PCT/US2011/046311|WO2012021336A1|2010-08-10|2011-08-02|A catheter hole having a flow breaking feature|
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