MEDICAL DEVICE

专利摘要:
delivery system and sealing device the invention relates to a sealing device for the repair of cardiac and vascular defects or tissue opening, such as a patent foramen ovale (pfo) or shunt in the heart, the vascular system, etc., and in particular provides an occlusion device and transcatheter delivery to the occlusion system. the sealing device would improve compliance with heart anatomy and be easily deployed, repositioned, and retrieved at the opening site.
公开号:BR112014011156B1
申请号:R112014011156-1
申请日:2012-11-05
公开日:2021-06-01
发明作者:Steven J. Masters
申请人:W. L. Gore & Associates, Inc.；
IPC主号:

专利说明:

CROSS REFERENCE FOR RELATED APPLICATIONS
[001] This application is a continuation in part of Patent Application No. US 13/165,673, filed June 21, 2011, which is a continuation in part of Patent Application No. US 12/498,586, filed at 7 of July 2009, which claims priority United States Patent Provisional Application No. 61/219,120, filed June 22, 2009, each of which is incorporated by reference in its entirety. FIELD OF THE INVENTION
[002] The invention relates to a sealing device for the repair of cardiac and vascular defects or tissue opening, such as a patent foramen ovale (PFO) or shunt in the heart, the vascular system, etc., and in particular provides an occlusion device and transcatheter prosthesis delivery system. BACKGROUND OF THE INVENTION
[003] Sealing devices can be used for the occlusion of many types of tissue openings, such as septal defects, PFO, and the like.
[004] Tissue openings have traditionally been corrected by open heart surgery. In order to avoid the trauma and complications associated with open heart surgery, a variety of trans-catheter closure techniques have been implemented. In such techniques, an occlusion device is usually delivered through a catheter to the opening site or a defect. A device is placed inside the defect and permanently implanted.
[005] A variety of trans-catheter-delivered devices are known. These include devices that require mounting at the tissue opening site or require threading or "buttoning" of discrete device elements. Other devices include self-expanding devices. These self-expanding devices tend to be difficult to visualize, cumbersome to carry, difficult to position in place of a tissue opening, and spare. Many self-expanding devices do not conform to the heart's anatomy, which can lead to tissue erosion.
[006] An example of a self-expanding device includes an occlusion bag, a tube component, a guide catheter, a super-elastic wire, a release mechanism, and a delivery liner. The super-elastic yarn is attached to the release mechanism. The wire, release mechanism, occlusion bag, guide catheter and tube component are inserted into a delivery sheath carrying the opening. After delivery, the occlusion bag is placed inside the opening and the wire is implanted inside the bag. The bag and string are repositioned, if necessary, and the release mechanism is activated to release the string.
[007] Another example of a self-expanding device includes a defined tubular shape of the metal tissue device and optionally an occlusion fiber included in the hollow parts of the device. The metal fabric defines a bell-shaped medical device that can be collected by passage through a catheter for deployment into a channel in a patient's body.
[008] While these and other self-expanding devices are designed for trans-catheter delivery, they require assembly either before use or during use. They are also difficult to reposition or retrieve once implanted and provide poor compliance with cardiac anatomy. For these reasons, it would be desirable to provide an improved closure device for use in transcatheter techniques. Such sealing devices would in some embodiments have improved compliance with heart anatomy and be easily deployed, repositioned, and retrieved at the opening site.
[009] Self-expanding trans-catheter sealing devices can be delivered and deployed by a variety of means. Most trans-catheter delivery devices choose one of two basic systems for device implantation: pulling back an external catheter to release the device, or pushing the device free of the catheter with a rod. Each of these systems uses an identifier to trigger the mechanism used to deploy the device. An example of such a system includes a flexible urging member for urging the sealing device via a remotely located catheter and control means for advancing the urging member. In this example, the control means includes a threaded, tubular shaft connected to the urging member and a manually-rotatable threaded rotor mounted on the shaft. The rotor mate threads with the shaft threads, so that rotation of the rotor through a known angle will advance the shaft and pushing member a known distance.
[0010] An example of a system that uses a backward pull of the external shaft or catheter includes a handle that can selectively hold the components of the delivery system, in any configuration and positioning during device implantation. The outer catheter of such a system will be pulled back to release the actuating device from a sliding lever and a rotating finger ring on the handle of the delivery system.
[0011] While these and other delivery systems are designed devices for trans-catheter device implantation, they require the use of a threaded rotor, which can become difficult to rotate, or which require large forces to pull behind the external catheter to expose the entire length of the restricted device. Many deployment systems are either not reversible or very difficult to reverse once the deployment process has taken place. For these reasons, it would be desirable to provide an improved system for delivering a sealing device. Such a release system which, in some embodiments, has a handle capable of being operated with only a single hand and would be capable of performing multiple manipulations with minimal force or hand movement. SUMMARY OF THE INVENTION
[0012] Some embodiments provide a sealing device that has an expandable structure formed from a plurality of wires extending from a proximal end to a distal end of the frame with the wires forming a proximal and distal end with grommet of a sealing element at least partially encapsulating the expandable wire frame.
[0013] Some embodiments provide a handle for deploying a sealing device that has a housing with a slot and a length with a linear actuator located inside the groove and the linear actuator capable of independently advancing and retracting, at least , three components separated by actuator advance and retraction along the length of the groove.
[0014] Some embodiments provide an apparatus comprising a handle having a housing that has a slot with a length and a linear actuator situated within the slot of the linear actuator capable of independently advancing and retracting at least three separate components by advancing and retracting the actuator along the slot length. In some embodiments, the device also comprises a sealing device having an expandable structure formed from a plurality of wires extending from a proximal end to a distal end of the frame with the wires forming a proximal and distal end, with an eyelet of a sealing element, at least partially, encapsulating the expandable wire structure.
[0015] Additional features and advantages of the invention will be presented in the description or may be learned by practicing the invention. These features and other advantages of the invention will be realized and attained by the structure particularly pointed out in the written description and claims of this document, as well as the accompanying drawings.
[0016] It is to be understood that both the above general description and the following detailed description are exemplary and explanatory and are intended to provide a further explanation of the invention as claimed. All references, patents and publications, including figures and drawings included therewith, are incorporated by reference in their entirety. BRIEF DESCRIPTION OF THE DRAWINGS
[0017] The accompanying drawings are included to provide a further understanding of the invention and are incorporated in and constitute a part of this specification, illustrate embodiments of the invention and, together with the description, serve to explain the principles of the invention.
[0018] In the drawings:
[0019] FIG. 1 is a perspective view of an implanted sealing device connected to the distal end of a delivery system.
[0020] FIG. 2A is a view of an expanded structure of a sealing device.
[0021] FIG. 2B is an end view of an eyelet of a sealing device.
[0022] FIG. 2C is an end view of a structure of a sealing device.
[0023] Figs. 3A-C are views of the components of a winding jig.
[0024] FIG. 4A is a side view of a roll-up jig.
[0025] FIG. 4B is a top view of a roll-up jig.
[0026] FIG. 5A is a side view of an expanded covered sealing device.
[0027] FIG. 5B is a side view of a partially expanded covered sealing device.
[0028] FIG. 6 is a side view of a self centered embodiment of a sealing device.
[0029] FIG. 7 is a side view of an implanted sealing device.
[0030] FIG. 8 is a perspective view of a delivery system that includes an implant identifier and an attached sealing device.
[0031] FIG. 9A-D are flowcharts describing the operation of the delivery system.
[0032] FIG. 10 is a perspective view of an implementation of the sealing device.
[0033] FIG. 11 is a perspective view of an assembly of a cable for implementing the sealing device.
[0034] FIG. 12A is a top-down view of an embodiment of a first linear actuator. side view of a
[0035] FIG. 12B is an embodiment of a first linear actuator.
[0036] FIG. 12C is an embodiment of a first linear actuator. a side view of a
[0037] FIG. 12D is an embodiment of a first linear actuator. a side view of a
[0038] FIG. 13A is a perspective view of an embodiment of a lock release actuator.
[0039] FIG. 13B is a perspective view of an embodiment of a lock release actuator in the activated position.
[0040] FIG. 14A is a perspective view of an embodiment of a spring.
[0041] FIG. 14B is an end view of an embodiment of a first linear actuator.
[0042] FIG. 15 is an end view of an embodiment of a first molded component spring linear actuator.
[0043] FIG. 16 is a perspective view of a spring member.
[0044] FIG. 17 is a schematic of a template base assembly including template winding, wire weight and guide wire.
[0045] FIG. 18A, 18B and 18C are schematic diagrams of a manufacturing mandrel and an embodiment of a locking closed circuit.
[0046] FIG. 19 is a perspective view of a base template with an attached self centered template petal attached.
[0047] FIG. 20A is a perspective view of a wire frame of a sealing device in a designed configuration.
[0048] FIG. 20B is a side view of a wire frame of a sealing device shown elongated along a mandrel.
[0049] FIG. 21 is a view of a wire structure of a sealing device.
[0050] FIG. 22A is a side view of a wire frame of a fastener shown elongated along a mandrel.
[0051] FIG. 22B is an illustration of an embodiment of a base template.
[0052] FIG. 23A is an end in view of a sealing device.
[0053] FIG. 23B is a side view of the sealing device of FIG. 23A in an elongated configuration on a mandrel.
[0054] FIG. 24A is a perspective view of a base template.
[0055] FIG. 24B is a side view of a lock cycle forming tool.
[0056] FIGs. 25A and 25B show elements of a wireframe forming device and a wireframe of a sealing device.
[0057] FIGs. 26A-C illustrate an anchoring member and method of attaching the anchoring member of a sealing device.
[0058] FIG. 27 is an end view of a sealing device wire frame with an anchoring member attached.
[0059] FIG. 28 is a side view of a sealing device covered with the anchoring member attached.
[0060] FIGs. 29A-C are illustrations of anchor components forming tools.
[0061] FIG. 30 is a perspective view of an anchoring member.
[0062] FIG. 31 is a perspective view of a wire structure with the anchoring members attached.
[0063] FIG. 32 is a perspective view of a tortuous path and template for winding an elongated waist sealing device.
[0064] FIG. 33 is an end view of an embodiment of a wire frame of the sealing device with an attached anchor.
[0065] FIG. 34 is a side view of an embodiment of a sealing device that includes an extended distal grommet.
[0066] FIG. 35 illustrates an embodiment of a hockey stick collar. DETAILED DESCRIPTION OF ILLUSTRATED EMBODIMENTS
[0067] Some embodiments provide a sealing device having an expandable frame formed from a plurality of wires extending from a proximal end of the frame to a distal end of the frame, with the wires forming a proximal and distal end. , with eyelet of a sealing element, at least partially encapsulating the expandable wire structure.
[0068] Figure 1 shows an embodiment of sealing device 100. Sealing device 100 will be discussed in detail in a later section. Sealing device 100 can housed within third tube 104. Third tube 104 contains device 100, first tube 102, second tube 108, retrieval cable 110 sealing and circular locking 111. Third tube 104 can be manufactured from Pebax®, or any other material with suitable mechanical properties and biocompatible. The choice of material with radiopacity may also be an option. Third tube 104 can be fabricated with or without a braid reinforcement to provide torsional strength and strength suitable for the chosen application. Third tube 104 can also be designed with or without a radiopaque labeling band. Third tube 104 design and materials may be chosen for other properties such as torqueability, targeting and reduction of vascular trauma. One skilled in the art will appreciate that there are a wide variety of potential materials that can be used to facilitate the present invention. Third tube 104 can be any size, but is, in some embodiments, 10Fr. with an inside diameter of about 0.048 mm and an outside diameter of about 0.33 mm. Third tube 104 can be used with or without a guide wire and may include a quick-change port 103. In some embodiments the tip of the first tube 104 is curved to aid navigation and delivery of the site sealing device 100 of access to the defect or without a guide wire.
[0069] Also shown in Figure 1 is the first tube 102. As noted above, the first tube 102 can be housed within the third tube 104. The first tube 102 can be any size outside diameter, but in some ways of embodiment is sized to fit within the lumen of the third tube 104. The first tube 102 can be fabricated from Pebax®, or any other material with suitable mechanical properties and biocompatible. In some embodiments the first tube 102 is a triple lumen catheter. Lumens can be of any geometric shape, but are, in some embodiments, substantially round or oval or a combination of both. First tube 102 can be used to position and aid delivery of sealing device 100. First tube 102 can be used in conjunction with second tube 108 to cause sealing device 100 to protrude from the distal tip of the third tube 104 of sealing device 100 has once reached the location of the defect. The first tube 102 may also have the function of retaining the sealing device 100 to the delivery system, until implantation of the final device. First tube 102 has an opening 109 at the most distal end to allow the locking circuit 111 to protrude during device deployment. The opening 109 and protruding locking loop 11 provide connection with the device's delivery system. Loop 11 is shown in its extended position before retaining its predefined shape. The first tube 102 can be coated or surface treated to improve the biocompatibility of the material or alter or improve surface friction.
[0070] First tube 102 may house the second tube 108. The second tube 108 is essentially tubular with an oval cross-section and may have an outside diameter suitable to fit within the first tube 102. In some embodiments, the second tube has an outside diameter range from about 1.27 x 0.68 millimeters and would be flared at the distal end. Second tube 108 can be fabricated from any suitable biocompatible material, including polymers or metals. In some embodiments, the second tube is made from PEEK (polyether). Second tube 108 can be used to assist in the delivery and implantation of the sealing device 100 from a defect site. Second tube 108 is threaded through sealing device grommet 100 to maintain sealing device 100 in the delivery system and to provide stability when deploying sealing device 100. Sealing device grommet will be discussed further below.
[0071] Recovery cord 110 is wound through two of the smaller lumens of the first tube 102 and through the proximal hole of the sealing device 100 to provide connection with the supply system and a method of recovery once the sealing device has been deployed. Recovery cord 110 extends through the length of first tube 102 with the ends terminating in the identifier used to implant sealing device 100. Recovery cord 110 can be fabricated from any biocompatible material, of sufficient strength and size. In some embodiments, the recovery cord is ePTFE (expanded polytetrafluoroethylene).
[0072] As shown in Figure 2A, the sealing device 100 is formed by a wire frame 200. When situated for delivery, wire frame 200 is in an extended position over the second tube 108 and the third tube frame 104 Wire 200 can be any size suitable for an application, but in some embodiments it is sized with finished outer diameters of 15, 20, 25, or 30 mm. The wire structure 200 is formed from continuous strands. Any number of strands can be used to build the 200 wire frame. In some embodiments five strands are used to build the five wire frame. The wireframe 200 can be constructed of wires that have elastic properties that allow the wireframe 200 to be retracted for catheter based delivery or delivery and self expandable to a "memory" induced configuration once positioned in a defect. The elastic yarn can be a spring yarn, or a shape memory NiTi (nitinol) alloy yarn or a super-elastic NiTi alloy yarn. The elastic yarn can also be of a NiTi-filled-design type containing a different metal to the core. In some embodiments wireframe 200 is constructed of a full-drawn type of NiTi wire containing a radiopaque metal in the center. After implantation, the wire structure resumes its implanted shape without permanent deformation.
[0073] Wire frame 200 and other wire frames shown are formed from elastic wire materials having outside diameters between 0.12 and 0.4 mm. In some embodiments, the size of the outer diameter of the wire is about 0.3 mm. When formed, wireframe 200 has a distal bumper 208, distal hole 204, loop 206, an optional center hole 203, and proximal hole 202. Figure 2B shows the position of the elastic threads during grommet formation 202, 203 and 204 of the wire frame 200.
[0074] Figure 2C shows a disc formed when wireframe 200 is deployed. The elastic strands that form frame 200 form 212 wire petals during deployment. The pre-set elastic yarn configuration of 200 wire frame allows the frame to twist during deployment. This twist forms petals 212. Implanted petals 212 forms the outer diameter 214 of wire frame 200. Implanted petals 212, when covered with sealing member 106, form proximal and distal discs, to be discussed later. Petals 212 are perfectly formed to have overlapping zones 216 to improve sealing characteristics. The radius of petals 212 can be maximized to minimize sharp bending angles in the elastic yarn and to minimize unsupported sections of petals 212 which improve the device's sealing qualities, reduce bending fatigue of the yarn and help reduce bending forces. charging the device. Deployed petals 212 form a disk on either side of the center of hole 203. The unfolded configuration will be discussed later.
[0075] The construction of wire structure 200 can be accomplished by a variety of means, including the winding machine with automatic wire tension or manually, winding with weights suspended from each of the wires during construction. Shown in Figures 3A-C, center pin 300 and button 304 are introduced, which can be used to aid in the construction of wire structure 200. One skilled in the art will recognize that there are many materials suitable for use as a fabrication aid or tooling. In some embodiments a material used in forming a center pin 300 would be high strength cobalt steel. In some embodiments corrosion resistant tool steel is used in forming a 304 button and winding jig. The roll-up template will be discussed later. Shown in detail in Figure 3A, the keyed center pin 300 may have slot 302, which may be used to secure an elastic thread, during construction of the device. Keyed center pin 300 can be used to guide an elastic thread through opening 306 in button 304, the features of which are illustrated in Figures 3B-C. In some embodiments, the button 304 is formed with an indentation 308 at the bottom to fit snugly into the winding bracket. An elastic thread held in slot 302 and inserted through opening 306 in button 304 can form a damper 208 and loop 206. In some embodiments the keyed center pin 300 is also used in forming grommets 202, 203 and 204. During In constructing the device, after forming bumpers 208, the elastic strands can be wound around the keyed center pin 300 to form a distal eyelet 202. Other eyelets, 203 and 204 may be formed in a similar manner. Once the keyed center pin 300 is inserted into the button 304 an elastic thread can be inserted into slots in a winding jig.
[0076] A winding jig can be used to protect and form the elastic strands during construction and processing of the sealing device 100. A typical winding jig can be constructed as commonly known in the art. The materials used to construct such a jig winding have been discussed above. An exemplary template is shown in Figures 4A and 4B. Figure 4A illustrates a side view of winding guide 400. Figure 4B shows a top view of winding jig 400. Winding jig 400 contains an opening 402 that can be molded and sized to hold the center of keyed pin 300 and the 304 button during device construction. Grooves 404 in the surface of the template are used to protect and form the elastic strands into petals 212. Grooves 404 can be of any diameter, but, in some embodiments, are sized to accommodate an outer diameter of the elastic strand. In one embodiment shown in Figure 5A, the winding template assembly can be used to form a central eyelet 203, a petal and proximal eyelet assembly 204. O-shaped wire may be constrained in the winding template assembly, heated and transformed in its form to define as commonly known in the arts.
[0077] Figure 5A shows an embodiment of the sealing device 100, which is an assembly composed of wire frame 200 and sealing member 106. Sealing member 106 can be bonded to wire frame 200 through a sealing agent. Link. Wireframe 200 can be coated with a bonding agent, for example, fluorinated ethylene propylene (FEP) or other suitable adhesive. The adhesive can be applied through contact coating, powder coating, dip coating, spray coating, or any other suitable means. In some embodiments, FEP adhesive is applied by electrostatic powder coating. The sealing member 106 can be constructed from a variety of materials, such as DACRON®, polyester, polyethylene, polypropylene, fluorinated polymers, polyurethane, foam films, silicone, nylon, silk, thin sheets of super elastic materials, woven materials , polyethylene terephthalate (PET), collagen, pericardium tissue, or any other biocompatible material. In some embodiments, the sealing element 106 can be formed of a thin porous ePTFE (polytetrafluoroethylene) substrate. The sealing member 106 is designed to improve the defect closure characteristics of the sealing device 100 by providing defect blocking and a medium for growing cell.
[0078] Also shown in Figure 5A are proximal, distal and center grommets (202, 203 and 204), respectively covered with sealing member 106 and wrapped with a film. Eyelets 202, 203 and 204 may be wrapped with a film to encourage adhesion of sealing member 106 to the device. The film used to wrap grommets 202, 203, and 204 can be any thin biocompatible material but, in some embodiments, is a material composed of multiple layers of thin porous ePTFE that can be laminated with one or more layers of non- porous FEP.
[0079] Figure 5B illustrates an embodiment of the sealing device 100, which includes a sealing element 508 that partially covers wire frame 200. Partially covered device may have either the distal or proximal bulb covered in part or completely, with a sealing element 508.
[0080] In some embodiments the device is a self-centering device 600. Shown in Figure 6, the self-centering device 600 comprises a wire structure 602 similar to that of the wire structure 200. The self-centering device 600 is a composite assembly of 602 wire frame and 604 frame sealing member. 602 wire can be constructed with the same techniques and a material as 200 wire frame but does not have a center ring. Wireframe comprises 602 distal bumper 606, covered distal hole 608, covered proximal hole 610, 612 and locking loop. The pre-set elastic strand configuration of wireframe 602 allows the frame to twist over the implant and create a centering region 614 of the device 600 during implantation. During implantation, region 614 may center on the defect forming a disk composed of petals on either side of region 614 and the defect.
[0081] Figure 7 shows a fully deployed sealing device 100. During implantation, the restriction of the third tube 104 is removed from the device 100 and the device returns to its predefined shape. During implantation and locking, locking loop 111 is released from the restriction of the first tube 102 and returns to its predefined shape, coiling from the proximal hole 202. In this way, the device is locked in an implanted state. Figure 7 also illustrates the position of the proximal and distal discs, elements 702 and 704, relative to the proximal, center, and distal eyelets 202, 203, and 204, respectively.
[0082] Figure 19 shows a base jig and other manufacturing aids used to manufacture an embodiment shown in Figures 20A and 20B and described in Example 4. As shown in Figures 20A and 20B of the sealing device 40 is formed from wires of structure 43. Wire 40 can be of any size suitable for an application, but can be sized with outer peripheral edge diameters of, for example, 15, 20, 25, or 30 mm. The warp structure 40 is formed from continuous strands. Any number of strands can be used to construct wire structure 40. Figures 20A and 20B show a device formed from 5 continuous strands. Figure 20A shows a device in an deployed configuration while 20B shows a device in an extended configuration. Wireframe 40 can be constructed of wires that have elastic properties that allow wireframe 40 to be retracted for catheter based delivery or thoracoscopic delivery and self-expand to a "memory" induced configuration once positioned in a defect. The elastic yarn can be a spring yarn, or a shape memory NiTi (nitinol) alloy yarn or a super-elastic NiTi alloy yarn. The elastic yarn can also be of a NiTi-filled-design type containing a different metal to the core. Wireframe 40 can be constructed of a type designed filled with NiTi wires containing a radiopaque metal in the center. After implantation, the wire structure resumes its implanted shape without permanent deformation.
[0083] Wire frame 40 and other wire frames shown are formed from elastic wire materials having outside diameters between 0.12 and 0.4 mm. When formed, wire structure 40 comprises a first eyelet 41, a second eyelet 42, a plurality of strands 43, a closed teardrop shape with an inner area 44 and inner peripheral edge 46 and an outer peripheral edge 45. end view of an implanted device, outer peripheral edge 45 is shown as the outermost edge of wireframe 40. Inner peripheral edge 46 of wireframe 40 is illustrated by the innermost edge of inner space 44 of the shape. of closed tear. In the unfolded configuration a thread and tear shape will nest closed or interspersed with each other in the form of thread on the thread side of the device. In an implanted configuration, the inner peripheral edge 46 will be at least part center within a cardiac defect or other tissue gap.
[0084] The wire frame 40 can be covered with a sealing element as described above.
[0085] Figure 21 illustrates an embodiment of the wire structure described in example 5. The embodiment comprises a proximal 610 and distal end 608 grommet with at least five strands 602, and a self-centering waist portion 614 similar to described above in relation to Figure 6. such an embodiment may be fabricated from similar materials and methods as described above.
[0086] In some embodiments a sealing device can be made by providing two frames sealing the device and inside the seat one another, then covering the resulting structure as described above. Such a device is described in example 6. Embodiments such as this can be fabricated with similar materials and methods as described above and hereinafter described. This technique can be used with any of the wire frames described herein.
[0087] An embodiment is illustrated in fig. 22A and described in example 8. Fig. 22A illustrates a wire structure 51 of a sealing device. The embodiment of fig. 22A comprises a proximal 608 and distal end 610 grommet, a plurality of strands 602, the strands forming a wire structure 51, a self-centering waist portion 614, a reniform shape with an inner open area 53 (not shown) with a inner peripheral edge 54 and an outer peripheral edge 55. The self-centered waist portion 614 of this variant forms a reniform with an inner open area 53 when in the deployed configuration. In a top view of an implanted device, the outer peripheral edge 55 is shown as the outermost edge of the wireframe 51. The inner peripheral edge 54 of the wireframe 51 is illustrated by the innermost edge of the inner open area 53 of the reniform form. In an implanted configuration, the inner peripheral edge 54 will be at least part center within a cardiac defect or other tissue gap.
[0088] The wire structure 51 as illustrated in fig. 22A, has a relatively short long period before implantation. A delivery configuration length to deployed radius ratio is about 2.5. Such a device can be formed of similar materials as described above and can be covered with a sealing element also described above.
[0089] A locking closed circuit 43 (illustrated in Fig. 18.) can be manufactured separately from the wire structure of the sealing device. The locking loop 43 can be formed of any material suitable for forming a wire structure of the sealing device. The locking loop 43 can be made of a different material, or have a different wire diameter than the wire structure of the sealing device. Locking loop component 43 is fabricated with a grommet 49 similar to grommets in the sealing devices described herein. Locking loop 43 can be attached to any wireframe sealing device before or post sealing member attachment. Any suitable method of attaching the separate timing ring component to the sealing device may be used. A method of manufacturing a locking loop component is described below in Example 9.
[0090] Figures 23A and B illustrate an embodiment comprising a proximal 608 and distal port 610, a plurality of wires 52, the wires forming a wire structure 61, a self-centering waist part 614, a reniform shape with an open area inner 53 (not shown) with an inner peripheral edge 54 and an outer peripheral edge 55 and a sealing member 604. The self-centering waist portion 614 of this embodiment forms a reniform with an inner open area 53, when in the projected configuration. . In a top view of an implanted device, the outer peripheral edge 55 is shown as the outermost edge of the wireframe 51. The inner peripheral edge 54 of the wireframe 51 is illustrated by the innermost edge of the inner open area 53 of the reniform form. In an implanted configuration, the inner peripheral edge 54 will be at least part center within a cardiac defect or other tissue gap. Some embodiments can be built with two structures described above. Some embodiments can be constructed with two wound frames in opposite directions or with two wound frames in the same direction. This and other wire frames can be constructed with the grommets configured either as shown with grommets or facing the center area of the frame along the inner diameter of the device. Materials suitable for use as a sealing member 604 have been discussed above. One or more sealing members may be attached to the frame in this and other embodiments described as discussed above. One or more sealing members in this and other embodiments may be attached to the interior or interior surface of the wire structure and alternately to the exterior of the structure. In some embodiments, the sealing member may be attached to only portions of the wireframe, leaving certain portions of the wireframe more degrees of freedom of movement. In some embodiments, the sealing member is attached to the cover on one side, portions or the entire wire structure.
[0091] Another embodiment is shown in Figure 25B. This embodiment can be constructed with similar materials as described above. The embodiment comprises a wire structure 78, first and second grommets (73 and 75, respectively), a sealing disc 77, a plug region 79 and optionally a sealing member 604 (not shown). The embodiment can be constructed from any of the previously described wire frames. The sealing disk portion 77 of the embodiment is adapted to cover a wide range of opening sizes, while the plug region 79 is adapted to conform to the anatomy into which it is inserted along its entire length. Sealing disk portion 77 has minimal deformation under radial pressure changes or radial pressure exerted on the sealing disk engagement region 79 77 and plug region 79 have substantial directional independence due to the flexibility of the waist portion 614. The longitudinal axis of the first eyelet 73 may be compensated with respect to the longitudinal axis of the second significant eyelet 75.
[0092] FIG. 34 is a side view of an embodiment of a sealing device 510 that includes a distal eyelet that extends a distance from the distal bulb of the device. Device 510, including distal orifice 511, is shown covered by a sealing member 512. In some implementations, distal bulb 513 is formed to have a concavity, which causes distal orifice 511 to extend beyond the distal bulb. 513 of the device, rather than remaining relatively flat with the distal bulb 513 of the device. As such, when implanted within a patient's left atrial appendage, the distal bulb 513 of device 510 extends farther into the left atrium than if orifice 511 were not enlarged.
[0093] In some embodiments, the spaced bulb 53 provides greater strength and stability, so that device 510 can be more easily retrieved after it has been previously implanted. In particular, as force is transmitted from device 510 to retrieve the device and pull the device back into the catheter, the enlarged distal hole 511 can help prevent the distal bulb petals of the device from collapsing distally (against the fit extended 511) and connector, so that the device can be more easily pulled back into the catheter. Extended distal grommet 511 can help provide recovery for device 510 after it has been released, in several embodiments. By enlarging the distal hole 511 as shown in FIG. 34, the distal orifice may remain out of the way as the rest of the device is pulled back into the catheter, without the re-entry connection into the catheter.
[0094] Device 510 can be constructed using techniques described here, and distal hole 511 can be pulled out, set on a mandrel, and heat set. The wires can be wound over a mandrel to create a proximal eyelet, and can be extended at an angle through and along a lobe of a mounting jig, and can return to the mandrel at an approximately perpendicular angle to the mandrel, and wrapped around the mandrel in a distal direction from the proximal grommet to create the enlarged distal hole 511. In some cases, the proximal and distal grommets can be pulled apart to aid in the formation of the distal concave ampoule 513.
[0095] Anchoring components or fastening devices can be attached to any of the embodiments. Examples of anchorage complements (80 and 96) are shown in Figures 26A and 30. Figure 26A illustrates an anchorage member 80 with fasteners configured to pierce, puncture, or protrude into tissue adjacent to the device, during or after implantation. Anchor member 96 in Figure 30 illustrates fasteners configured with flat ends designed to grip or enclose adjacent tissue, without substantially protrusion into tissue.
[0096] Figure 33 shows an end view of a device that includes one or more anchors 500, each attached to the wire frame of the device 499. In the example of Figure 33, three anchors 500 are shown, but in other examples, two, four, five, six, or more 500 anchors can be used. In some embodiments, each petal of the device includes at least one anchor 500. In some embodiments, one or more petals of the device includes two or more anchors. In some embodiments, one or more petals of the device does not include an anchor 500. In various embodiments, one or more of the anchors 500 may be covered by a non-permeable membrane or sealing element, as described herein, or alternative can be discovered, as shown in Figure 33. In some embodiments the membrane is a polytetrafluoroethylene membrane.
[0097] In various embodiments, the anchors 500 can be attached at any appropriate location on the wireframe of the device. In some embodiments, anchors 500 are attached to the distal bulb of the device. Each anchor 500 can be any of the types of wires discussed herein, and can include a first leg 501 and a second leg 502, each of which extends from the wire structure of the device. The anchor can extend from the wire frame at any suitable angle. In the example shown in Figure 33, the first part and second legs 501, 502 extend generally parallel to each other and then converge to form a looped end 503 of the anchor.
[0098] When used to occlude a patient's left atrial appendage, after implantation each of the 500 anchors can be located inside the patient's left atrium, and can interact with the left atrial appendage tissue to anchor the device in position . As can be seen with reference to Figure 33, anchors 500 are devoid of sharp edges, and instead include the aforementioned bent end 503. As such, anchors 500 can avoid or minimize puncture of the left atrium interior wall when the interface with the tissue of the left atrial appendage.
[0099] As shown in Figure 35, in some embodiments, anchor 500 may include first leg 501 and second leg 502 and 503 loop ends, similar to the shape of the area where the axis of a hockey stick transitions to the blade of the hockey stick.
[00100] In some examples (see Figure 35), anchors 500 include a first leg 501 and a second leg 502 connected together by a loop end 503. The loop end 503 expands laterally with respect to the first and second legs 501, 502, such that loop 503 defines a substantially open opening 504. In some embodiments, the transitions between legs 501, 502 and loop 503 are smooth arcs and open opening 504 is generally oval in configuration. Some embodiments include other transition configurations (eg right angle transitions) and/or other loop configurations (eg rectangular loops or circular loops). In some embodiments, first portion 501 and second leg 502 extend generally parallel to each other and most of loop 503 is in a plane P that defines an angle A with respect to first leg 501 and second leg. leg 502. In some embodiments, angle A can range from about 45 to about 135 degrees. In some embodiments, angle A can range from about 75 to about 155 degrees. In the exemplary embodiment shown in Figure 35, plane P defines an angle a with respect to the first leg 501 and the second leg 502 of about 90 degrees.
[00101] In some embodiments, the first leg 501 and the second leg 502 are substantially parallel to each other along their lengths. In some embodiments, the first leg 501 and the second leg 502 are substantially the same length. Anchors 500 can be of any suitable length, and in some embodiments, anchor 500 can be of different lengths. In some embodiments, first portion 501 and second leg 502 may be more widely spaced or less spaced apart from each other. The first leg 501 and the second leg 502 may, in some embodiments, not be parallel to each other, and instead may diverge, when extending from the wire structure of a first part of the anchoring device and , then converge toward the open end 503. The anchors 500 can be attached to the framework from one or more locations in the framework and are attached in any suitable way, including the manner discussed below with reference to Example 11. embodiment, the fasteners do not protrude into the fabric. Other anchoring components can be envisioned including anchoring components configured to have both piercing and gripping capabilities. Such an anchoring member may look similar to what is shown in Figure 30, but instead of having a wire loop arm, have a single wire arm with a bent end so that they can be pressed or positioned to be or in the same flat, as the single wire arm or protrude from the plane thus being available for punching or punching fabric. Anchoring components must be plugged into any hole in the device. Anchoring components can be configured to bend in any direction. Single or multiple anchoring components can be affixed to any device frame or wire in any combination. Said attachment points can be designed to release tissue for repositioning and/or retrieval. In addition, when the sealing device is in the delivery configuration, barbs can be collected in order to prevent capture of catheter components during device withdrawal.
[00102] Figure 8 shows a perspective view of the device 100 connected to a delivery system that includes first tube102, third tube 104, and a sealing handle for implanting a sealing device 100. Figure 8 further illustrates a handle linear actuator 802, a flush port 804, the second linear actuator 806, the snap release actuator 808, a housing 810, and a slot with a length in the housing 812. First linear actuator 802 may have a variety of configurations that will be discussed later.
[00103] Figures 9A-D are flowcharts describing the movements of the various components of the delivery system and connected sealing device 100 during use. Seal loading device 100 for the delivery system prior to use is depicted in Figure 9A. The components of the handle delivery system are shown in Figures 8, 10 and 11. A physician can wash the delivery system by attaching a syringe or other suitable instrument to flush port 804 and fill the system with any other suitable material. saline wash or. The first linear actuator 802 can then be displaced in slot 812 in housing 810 against a spring of 1100. Spring 1100 can be configured as shown, or it can be formed as a leaf spring, a spring pitch, or any spring. way known in the art. This action rotates the mandrel control lever 1000, shown in Figure 11, about a sliding rod 1102 to the side of the housing 810. This same movement moves the first linear actuator 802 free from the distal notch 1104 in the sizing insert 1103 and prevents second tube 108 to translate, either proximal or distal. Sizing insert 1103 can be of any material with suitable mechanical properties.
[00104] Typical handles, handle components, tools or catheters used to deliver medical devices may comprise commonly known materials such as amorphous thermoplastic commodities that include polymethyl methacrylate (PMMA or acrylic), polystyrene (PS), acrylonitrile butadiene styrene (ABS ), Polyvinyl Chloride (PVC), Modified Glycol Polyethylene Terephthalate (PETG), Cellulose Acetate Butyrate (CAB); semi-crystalline plastic commodities that include polyethylene (PE), high density polyethylene (HDPE), Low Density Polyethylene (LDPE or LLDPE), polypropylene (PP), polymethylpentene (PMP); Amorphous Engineering Thermoplastics including Polycarbonate (PC), Polyphenylene Oxide (PPO), Modified Polyphenylene Oxide (Mod PPO), Polyphenylene Ether (PPE), Modified Polyphenylene Ether (Mod PPE), Thermoplastic Polyurethane (TPU); Semi-crystalline engineering thermoplastics including Polyamide (PA or Nylon), Polyoxymethylene (POM or Acetal), Polyethylene Terephthalate (PET, Polyester Thermoplastic), Polybutylene Terephthalate (PBT, Polyester Thermoplastic), Ultra High Molecular Weight Polyethylene (UHMW-PE ); High performance thermoplastics including polyimide (PI, Plastic imidized), Polyamide imide (PAI, Plastic imidized), polybenzimidazole (PBI, plastic imidized); Amorphous high performance thermoplastics including Polysulfone (PSU), Polyetherimide (PEI), Polyethersulfone (PES), Polyaryl Sulfone (PAS); Semi crystalline high performance thermoplastics which include Polyphenylene Sulfide (PPS), Poly-ether-ether-ketone (PEEK); and semi-crystalline high performance thermoplastic, Fluoropolymers that include fluorinated ethylene propylene (FEP), Ethylene Chlorotrifluroethylene (ECTFE), ethylene, ethylene Tetrafluoroethylene (ETFE), polychlorotrifluoroethylene (PCTFE), polytetrafluoroethylene (PTFE), polyvinylidene fluoride (PVDF), perfluoroalkoxy (PFA). Other commonly known materials of the medical grade include organosilicon elastomeric polymers, polyether block or thermoplastic copolyether amide (PEBAX) and metals such as stainless steel and nickel/titanium alloys.
[00105] A distal notch 1104 and proximal notch 1106 at 1103 insert sizing can be used to assist in positioning the first linear actuator 802 in the housing groove 812. The distance between the two notches, 1104 and 1106, respectively, can be the length of the sealing device 100 when this is stretched along the second tube 108 prior to loading to the delivery system. Sizing Insert 1103 can be sized to accommodate a variety of device lengths, and in some embodiments is about 22 cm long, with a distance between the proximal end of distal notch 1104 and a proximal end of proximal notch 1106 from about 6.25-13.32 cm. Notches 1104 and 1106 can be of any shape, but in some embodiments they are rectangular.
[00106] The first linear actuator 802 is then moved to a midpoint in the groove 812 to the proximal end of the body 810. This action causes the first tube 102 to move proximally and the proximal end sealing device 100 to move. closely, thereby elongating Sealing Device 100. First linear actuator 802 may be of any shape (lever, ball), but, in some embodiments, is shaped to accommodate a physician's thumb. First linear actuator 802 can be constructed of any material with suitable mechanical properties, but in some embodiments it is a material similar to insert sizing 1103. In some embodiments, first linear actuator 802 includes undercut teeth formed in the portion. top of the first 802 linear actuator for securing 110 rope. Teeth can be made in any tortuous path or have any desired shape to create resistance for 110 rope during loading, implantation or retrieval of sealing device 100. Corresponding protruding teeth ( not shown) can be formed on the undersurface of the lockout retrieval cord 803. These teeth can engage and retain the retrieval cord securely. Other methods commonly known in the art for securing a small diameter rope can also be used and will be discussed in detail in the following section.
[00107] The first linear actuator 802 is then moved more closely until the device is placed in the third tube 104. During this action, a spring 100 pushes the first linear actuator 802 and the mandrel control lever 1000 to the left of the groove. 812 and inwardly proximal notch 1106 at insertion sizing 1103. Second tube 108 is free to move proximally with device 100 and first seal tube 102. As the first linear actuator 802 is moved proximally, the second tube 108, device 100 and first tube 102 seal slides or translate into the third tube 104. After the first linear actuator 802 is in its most proximal position, the system can be moved. new washed with saline solution as described above.
[00108] Some embodiments of the first linear actuator 802 are shown in Figures 12A-D. Figure 12A shows a perspective view of the reciprocating linear actuator 1108, in the latched recovery cord position. 1108 linear actuator is similar in construction to 802 linear actuator, but features an 1110 ring retrieval cable and 1112 locking groove safety rope. Figure 12B shows an alternative embodiment 114, which is configured with a rotary knob 1116 that extends beyond the sides of the linear actuator to facilitate easy manipulation. Wheel 1116 is screwed onto a post with 1118 thread around which the safety rope is wrapped. Personification 1114 also contains an 1120 rope groove through which the safety rope is guided before securing it post around thread 1118. Figure 12C illustrates yet another embodiment 1122 that uses a side mounted thumb wheel threaded 1124 around the which retrieval wire is wound and secured to actuator 1122 by the act of inserting threaded post 1124 into a threaded hole (not shown) on the side of actuator 1122. Prior to threading retrieval cord around threaded post 1124, retrieval cord is inserted through the slot of a retrieval cord 126. Yet another embodiment 1128 is shown in Figure 12D. Embodiment 1128, shows an 1130 molded thumb wheel linear actuator. The 1130 rotary knob extends slightly beyond the edges of the linear actuator to facilitate manipulation of the linear actuator. The retrieval cord is inserted through slot cable 1132 and wrapped around a threaded post (not shown). The molded thumb wheel 1130 is then fixed to the threaded post securing the safety rope.
[00109] The implantation of the sealing device 100 into a defect is described in Figure 9B. The first linear actuator 802 is moved distally until a stop is reached. This movement causes first tube 102 and second tube 108 to move distally within third tube 104. Linear actuator 802 is then moved to the right in slot 812, against spring 1001. When linear actuator 802 is moved to the right, chuck control lever 1000 rotates around a sliding rod 102. This action causes the linear actuator 802 to be freed from the proximal notch 1106 in the insertion sizing 1103. After this action, the linear actuator 802 is still translated distally. This causes the first tube 102 and proximal eyelet 202 of the sealing device 100 to move distally. Also affected by this action is the distal end of the device 100, which is sealed from moving. The first tube 102 guides the device away from the third tube 104 to implant the device into a defect. Moving linear actuator 802 distally to the end of slot 812 results in the entire sealing device being implanted. One skilled in the art will recognize that the steps described above could be locked and reversed at certain points to allow optimal positioning of the sealing device 100.
[00110] Device lockout is described in the flow diagram shown in Figure 9C. The safety rope lock 803 would be uninstalled from the first linear actuator 802. A physician would seize the second linear actuator 806 by holding on unlocking actuator 808 and pressing it into the middle of housing 810. The second linear actuator 806 can be any size or shape, but in some embodiments it is sized to fit into a groove 1002 in the longitudinal surface of the housing 810 linear actuator 806 is provided with the lock release actuator 808 by means of a snap fit. Any attachment means would suffice to secure 808 unlocking actuator to linear 806 actuator, such as glue, a solder, or a molded part construction. Suitable materials for both the second linear actuator 806 and the snap release actuator 808 can be any material with suitable mechanical properties, but are, in some embodiments, similar to the aforementioned handle components. 808 Unlock Actuator is designed to allow a user to grip the device safely. Gripping can be aided by lugs on the side sides of the 808 unlocking actuator. These lugs can be made of a material similar to that of the 808 unlocking actuator or can be made of a material with a high coefficient of friction or a more compatible material than that of the 808 unlocking actuator. These protrusions can also be made with a grid, a roughness, a raised design, or surface grooves, in conjunction with one or more of the materials listed above to further aid in tightening the device. These surface features of the locking release actuator 808 can also be used to aid grip, without the use of pinch protrusions, and can be applied directly to the side surface of the second linear actuator 806. Slot 1002 can be configured to have a point end carry the second linear actuator 806 in a more distal position until the release of locking of the sealing device. An exemplary stop is shown in Figures 10 and 11 in the form of an area of corrugated cardboard, but it can also be any form of mechanical stop. Slot 1002 can be any length, but, in some embodiments, is long enough to translate proximal movement over the width of the second linear actuator 806, plus about 3.18 centimeters. The 1002 slot can be any shape that could accommodate the second 806 linear actuator.
[00111] An alternative embodiment of the second linear actuator 806 is shown in Figures 13A and 13B. Instead of holding the 808 unlocking actuator and activating the second 806 linear actuator, a 1300 rotary unlocking actuator is gripped and rotated to affect unlocking. The rotary unlock actuator 1300 may contain a 1302 window which would prevent forward movement of the first linear actuator 802. When rotated, unlock actuator 1300 allows the same actions as unlock actuator 806 shown in Figure 10.
[00112] Once the second linear actuator 808 is gripped, a physician can move the second linear actuator 806 proximally. This action results in proximal movement of third tube 104, mandrel control lever 1000, insert sizing 1103 and second tube 108. Second tube 108 proximal movements between grommets of the device. An alternative method to achieve this action would be to provide a twist mechanism for the distal end of the handle, rather than a second linear actuator 806. This twist mechanism would be provided with a slot that allows the same movement as the third tube 104, mandrel lever control 1000, insertion sizing 1103 and second tube 108 as second linear actuator 806.
[00113] Once lockout release has been achieved, the safety rope lock 803 is then twisted to remove it from the first linear actuator 802 and pulled until the safety rope 110 is freed from the delivery system. A rescue cord 10 is attached to the lock retrieval cord 803 at one end. Recovery cord 110 can be constructed of any material with suitable mechanical properties such as Kevlar®, flexible metal wire, polymers and the like. In some embodiments, the recovery strand 110 is an ePTFE fiber. Retrieval cord lock 803 can be configured in a variety of shapes and sizes. Possible retrieval cord locks can be designed to provide a slot in the 802 linear actuator, through which the retrieval passes. In some configurations, the retrieval cord is secured by passing the cable through a slot or hole in the hand shift wheel shaft disposed on the 802 linear actuator and tightened by twisting the hand shift wheel. An alternative configuration would be to provide a slip lock that attaches to the recoil cord between the lock and the 802 linear actuator using friction. In some embodiments, the retrieval cord is clamped between teeth formed in the lock retrieval cord, as shown in Figure 11.
[00114] Suitable materials for construction of retrieval lanyard latch 803 are similar to those used for construction of casing 810 and other handle components. As mentioned above, the lock retrieval cord 803 has, in some embodiments, teeth or protrusions corresponding to the notches on linear actuator 802 for the purpose of gripping lifeline 110. Lock retrieval cord 803 can be configured on a variety of shapes, to allow retrieval 1 cable out of 10 to be protected. In some embodiments, openings are included through the retrieval lock cord 803 to allow a retrieval cord 10 to be threaded therethrough and knotted. After twisting the lock cord 803, the retrieval cord 110 is pulled until the retrieval cord 110 is removed from the delivery system.
[00115] Prior to step four described in Figure 9C, the sealing device 100 can be retrieved as described in the flowchart illustrated in Figure 9D. The safety rope lock 803 can be fitted to the first linear actuator 802. This serves to lock the safety rope 110 in place. The doctor then moves the first linear actuator 802 to the right edge of groove 812. The first linear actuator 802 moves in 812 groove to the right by pressing spring 1100, while the mandrel control lever 1000 rotates on the sliding rod 1102 to the right. to handle. Although in some embodiments the sliding rod 1102 has a round cross-section, those skilled in the art will recognize that a variety of cross-sectional shapes (e.g., square or triangular) would be acceptable. A sliding rod 102 may also be configured in the form of a crown spring 1400 as shown in Figures 14A and B. The spring may be inserted into a slot 1402 via the linear actuator to allow forward and backward translation of the linear actuator. An alternative embodiment of a spring 100 may be a spring molded as an integral part of the first linear actuator 1500 802, as illustrated by Figure 15. Another embodiment of the spring 1100 is shown in Figure 16. In this configuration, the spring 1600 is connected to housing 810 and pushes the first linear actuator 802 into key positions. As indicated above, one skilled in the art will recognize materials suitable for use as a spring or molding. The first linear actuator 802 is free from distal notch 1104 and the second tube 108 is prevented from moving. The first linear actuator is moved proximally by the clinician causing the first tube 102 to displace proximally. This movement translates the proximal end of the proximal sealing device 100 into elongating the device 100 and allowing it to be pulled into the third tube 104
[00116] EXAMPLES
[00117] Without intending to limit the scope of the invention, the following examples illustrate how various embodiments of the invention can be made and/or used.
[00118] Example 1
[00119] A sealing device similar to Figure 1 was produced using the following components and assembly processes.
[00120] An expanded polytetrafluoroethylene material was obtained with the following properties: Bubble point Methanol 1 psi Mass / area 2.2 grams / square meter Maximum Longitudinal Load 1.6 kg / cm Thickness 0.0003 inches Resistance to longitudinal matrix tension of 92000 psi
[00121] The following test methods and equipment were used to determine the aforementioned properties: Methanol bubble point was measured using a custom built machine with a 1 inch diameter foot, a ramp rate of 0.2 psi/second and a liquid methanol medium. Length and width of material were measured using a metal ruler. Mass/area was measured using a scale (Model GF-400 Top Loader Balance, ANG, San Jose CA.) with a 36 x 5 cm sample. Maximum longitudinal load was measured using a materials testing machine (Model 5564, Instron, Grove City, PA) equipped with a 10 kg load cell. The gauge length was 1 cm and the cross head speed was 25mm/minute. Width of sample was 1 inch. Longitudinal tensile test measurements were taken along the length of the material. Thickness was measured using a thickness gauge (Mitutoyo Digital Indicator 547-400) with a foot diameter of % inch. The longitudinal matrix tensile strengths (MTS) were calculated using the following equation: Density was calculated using the formula, density = mass / volume. Matrix Tensile Strength = (amih ss) * (The FTFE) where: p PnE » 2.2 grams / eeCF Max Loa Widtb) Ttocknessp saaagk = (Area Mass) / Huckness.
[00122] An expanded polytetrafluoroethylene with a thin layer of FEP (fluorinated propylene ethene) material was obtained with the following properties: Mass / area of 36.1 grams / square meter Maximum Load, Longitudinal 12.6 kg / cm Maximum Load, 0.3 kg / cm thickness 0.0012 inches
[00123] The following test methods and equipment were used to determine the properties mentioned above: The material was weighed using a precision analytical balance (model GF-400 superior from Equilíbrio loader, ANG, San Jose CA.) With a sample area of 36 x 1 inch sample. Length and width of material were measured using a metal ruler. Material thickness was measured using a digital thickness gauge (Mitutoyo Digital Indicator 547-400), with a foot diameter of % inch. Maximum shear load was measured using a materials testing machine (Model 5564, Instron, Grove City, PA) equipped with a 10 kg load cell. The sample width was 1 cm, the measurement length was 1 cm and the crosshead speed was 25mm/minute. Maximum longitudinal load was measured using a materials testing machine (Model 5564, Instron, Grove City, PA) equipped with a 200 kg load cell. The sample width was 1 cm, the measurement length was 1 cm and the crosshead speed was 25mm/minute. Longitudinal tensile test measurements were taken in the material length direction and transverse tensile test measurements were taken in the direction orthogonal to the length direction.
[00124] A distal hole was formed by first obtaining a 10% length of platinum filled nitinol wire (Fort Wayne Metals, Fort Wayne, IN.) designed with a diameter of about 0.23 mm. This wire was marked "first wire". The free end of the first wire was bent back on itself to create an open circuit and the open circuit was inserted into the button. The button was then inserted into the keyed center pin. The button has been shaped to have an opening through the center to accommodate the keyed center pin and has features that allow it to be secure in the winding jig. The central pin of the keyway (major shaft approx. 0.51 mm and minor shaft approx. 0.25 mm and a length approx 10.16 mm) was then inserted into the center of a winding jig. The keyed center pin was fabricated from high strength steel (Super Cobalt HSS Tool Bit, MSC #56424278, Seco Fagersta). The steel was tempered per manufacturer's instructions at 1475 °C for one hour. The winding jig and knob were manufactured in-house from corrosion resistant tool steel.
[00125] A second length of the same type of drawn filled nitinol wire was obtained and identified as "fifth wire". The first, fifth and an additional three strands were straightened by attaching weights to the ends of the strands. The first strand and fifth strand were then wound around the free end of the first strand for one full revolution. The three additional strands were introduced to the winding mounting device and all five strands wound around the free end of the first strand from a height of about 1.98 mm.
[00126] A distal disc was then formed by separating the five wires and securing them in radial grooves around the circumferential edge of the winding jig. A radius was formed with the dimensions of 15 mm. Each wire formed a petal of the distal disc. The radius of curvature of the petals has been maximized in order to minimize the sharp bending angles in the handle.
[00127] A center eyelet was formed by bundling the wires together and winding them around the free end of the first screen and the keyed center pin to a height of about 1.98 mm. The wires were then separated and fixed in radial grooves around the peripheral edge of the winding arm creating a proximal disc with a radius of 15 mm.
[00128] A proximal eyelet was again formed by grouping the five threads and wrapping them around the free end of the first mesh and the central pin with key to a height of about 1.98 mm. The five wires were then separated and fixed by placing a stainless steel plate on top of the wires and locking the plate with screws. The free end of the first wound wire was then rotated around a stainless steel pin with a diameter of about 3.18 millimeters and fixed similarly to the other five wires.
[00129] The jig with sealing device was then removed from the stabilization equipment and placed in an oven (BLUEM SPX Electric Forced Air Convection Oven) and the wires were thermally defined as known in the art. The device and the jig were then extinguished by water. The shielded wires were released from the clamp plate and the device was cooled and removed from the jig and keyed center pin. The device was then placed on a piece of flattened PEEK (polyether ether ketone) and trimmed by hand to the outer diameter of the distal eyelet. The locking loop was cut by hand to a point just beyond a full turn and pulled through the proximal and central eyelets.
[00130] The device was pushed from the PEEK mandrel into a stainless steel process key mandrel with an oval cross section. The mandrel was produced from stainless steel wire (Ft. Wayne Metals, Fort Wayne, IN) with an oval cross section to have a 45° clockwise twist between the proximal hole and the central hole and one second of 45° clockwise between the central orifice twist and the distal orifice.
[00131] The process mandrel and device were then placed in a stabilization facility, which was placed in a FEP powder coating machine (C-30, Electrostatic Technology, Inc., Bradford, NC) and processed until fully coated. Excess FEP powder was removed from the device. The FEP was aspirated from the lockout circuit, the chuck and bumper process. The process mandrel and device were taken from the stabilizer luminaire, placed inside an oven and baked to adjust the FEP coating as commonly known in the art.
[00132] A hollow core film mandrel (35.99mm OD 76.2cm long in stainless steel) was obtained. Expanded polytetrafluoroethylene material with a slit width of 22.22 mm was obtained and loaded into a spiral wrapping machine. The machine was manufactured in-house to wrap PTFE (polytetrafluoroethylene) material in any desired angle, tension and rhythm. The mandrel was loaded onto the packaging machine and the material was wrapped three times around the perimeter of the hollow mandrel core. The material was then wound around the mandrel at an angle of about 8°C for the life of the mandrel. The wrapping direction has been reversed and the material is rolled at the same angle. The third and fourth layers were wrapped in the same way with plywood seams. The mandrel was removed from the packaging machine, inserted into an oven and baked at 370 °C for 45 minutes. The rolled mandrel was removed from the oven and allowed to cool to room temperature. The resulting PTFE tube was removed from the mandrel.
[00133] The PTFE tube was then cut to approximately 140mm and hand extended to a desired length of 155mm. The PTFE tube was then leaned against the frame. The PTFE tube was then compressed against the central hole and then compressed against the proximal and distal eyelets.
[00134] An expanded polytetrafluoroethylene with a thin layer of FEP (fluorinated Ethylene Propylene) material was then wrapped four times around the grommets starting with the center hole. The wrapped eyelets were nailed in place of a soldering iron. The PTFE tube was then heat set for 3 minutes at 320°C and adjusted to the greatest number of outer points of the proximal and distal eyelets. The device was removed from the mandrel.
[00135] Example 2
[00136] A sealing device similar to Figure 6 was manufactured using the following components and assembly processes.
[00137] Expanded and expanded polytetrafluoroethylene with a thin layer of FEP (fluorinated propene ethene) materials similar to that described in Example 1 were obtained.
[00138] A distal hole was formed by first obtaining a 10% length of platinum filled nitinol wire (Fort Wayne Metals, Fort Wayne, IN.) designed with a diameter of about 0.23 mm. This wire was marked "first wire". The free end of the first wire was bent back on itself to create an open circuit and the open circuit was inserted into the button. The button was then inserted into the keyed center pin. The button has been shaped to have an opening through the center to accommodate the keyed center pin and has features that allow it to be secure in the winding jig. The center pin of the keyway (major shaft about 5.79mm and a minor shaft about 0.25mm and a length of about 10.16mm) was inserted into the center of a winding jig. The keyed center pin was fabricated from high strength steel (Super Cobalt HSS Tool Bit, MSC #56424278, Seco Fagersta). The winding jig and knob were manufactured in-house from corrosion resistant tool steel.
[00139] A second length of the same type of drawn filled nitinol wire was obtained and identified as "fifth wire". The first, fifth and an additional three strands were straightened by attaching weights to the ends of the strands. The first strand and fifth strand were then wound around the free end of the first strand for one full revolution. The three additional strands were introduced to the winding mounting device and all five strands wound around the free end of the first strand from a height of about 1.98 mm.
[00140] A device was then formed by separating the five wires and securing them in radial grooves around the circumferential edge of the winding jig. A radius was formed with the dimensions of 15 mm. Each wire made a complete revolution around the winding jig.
[00141] A proximal eyelet was formed by grouping five strands and wrapping them around the free end of the first mesh and the keyed central pin to a height of about 1,981mm. The five wires were then separated and fixed by placing a stainless steel plate on top of the wires and locking the plate with screws. The free end of the first wound wire was then rotated around a stainless steel pin with a diameter of about 3.18 millimeters and fixed similarly to the other five wires.
[00142] The jig with sealing device was removed from the stabilization equipment and placed in an oven (Blue M electric SPX forced air convection oven), in which the wires were partially thermally set as known in the art. The device and the jig were then extinguished by water. The shielded wires were released from the clamp plate and then the device was cooled and removed from the jig and keyed center pin. The locking loop was cut by hand to a point just beyond a full turn and pulled through the proximal and central eyelets.
[00143] The device was pushed from the PEEK mandrel to a stainless steel transfer mandrel by keyway with an oval cross section. The mandrel was produced from flattened stainless steel wire (Ft. Wayne Metals, Fort Wayne, IN) with an oval cross-section. The device was then partially removed from one end of the transfer chuck. The removed end of the device was twisted about 180" clockwise and repositioned over the transfer chuck. The transfer device and the chuck were placed in an oven (Blue M SPX Electric Forced Air Convection Oven) in which the wires were thermally shaping defined as known in the arts.
[00144] The mandrel and transfer device were then placed in a stabilization facility, which was placed in a FEP powder coating machine (C-30, Electrostatic Technology, Inc., Bradford, NC) and processed until fully coated. Excess FEP powder was removed. FEP dust was aspirated from the lock circuit, chuck and bumper process. The mandrel and transfer device were then removed from the stabilizer attachment, placed into an oven and baked to adjust the FEP coating as commonly known in the art.
[00145] A hollow core film mandrel (35.99mm OD 76.2cm long in stainless steel) was obtained. An ePTFE material with a slit width of 22.24mm was obtained and loaded into a spiral wrapping machine. The machine was manufactured in-house to wrap ePTFE film in any desired angle, tension and rhythm. The mandrel was loaded into the wrapping machine and the film was wrapped three times around the perimeter of the hollow mandrel core. The ePTFE material is then wound around the mandrel at an angle of about 8°C for the life of the mandrel. The wrapping direction has been reversed and the material is rolled at the same angle. The third and fourth layers were wrapped in the same way with plywood seams. The mandrel was removed from the packaging machine, inserted into an oven and baked at 370 °C for 45 minutes. The rolled mandrel was removed from the oven and allowed to cool to room temperature. The resulting ePTFE tube was removed from the mandrel.
[00146] The ePTFE tube was then cut to approximately 140mm and hand extended to a desired length of 155mm. The ePTFE tube was then stopped in the frame. The ePTFE tube was then compressed against the proximal and distal grommets. An ePTFE with a thin layer of FEP (fluorinated ethylene-propylene) material was then wrapped four times around the grommets. The wrapped eyelets were nailed in place of a soldering iron. The ePTFE tube would then heat set for 3 minutes at 320°C and adjusted to the greatest number of outer points of the proximal and distal eyelets. The device was then removed from the mandrel.
[00147] Example 3
[00148] A mounting handle similar to figure 8 was fabricated using the following components and mounting processes.
[00149] Components for the cable assembly were manufactured using an injection molding process. The parts were manufactured by Contour Plastics (Baldwin, WI) using Lustran ® 348. This material was suitable for use in medical devices, and has a advertised breaking strength of 48.2 MPa and a modulus of elasticity of 2.62 GPa. Nine parts were manufactured using this injection process and Lustran ® 348. Parts included in the second linear actuator, seal retainer flush, a first linear actuator, safety rope lock, chuck control lever, left body housing, sizing insert, right body housing, and an unlocking actuator.
[00150] Other materials needed for assembling the handle were purchased items. A catheter tube formed with a configuration above procedure commonly known in the arts was ordered (Teleflex Medical, Jaffrey, NH) with an ID of 0.048mm and an outer diameter of 0.33mm and a platinum iridium marking band placed close together. from the end of the distal tip. The main body of the catheter tube was Pebax ® 7233 tube with PTFE coating and stainless steel braid (65 PPI) and the most distal 20.32 mm of the catheter tube was composed of Pebax ® 6333 (0.027 mm inner diameter and an outer diameter 0.033mm) and a bend at the distal end (39.98mm radius). A guidewire port formed by a laser was placed at the proximal end of the marker band catheter tube. A flushing gasket or u-cup type gasket made of silicone (depth 22.99mm, taper ID 2.89mm to 1.85mm, tapered diameter 6.71mm to 7.75mm) was obtained from the Apple Rubber from Lancaster, NY. A flush port (Medical Merit, South Jordan, UT) with an approximately six-inch flexible pvc (polyvinyl chloride) tube with a 3.18mm OD female luer connector was obtained. A cyanoacrylate quick set adhesive was provided from home stock. Stainless steel hypotubes were ordered from Small Parts, Inc. (1.45 mm outer diameter, 1.30 mm diameter, length 30.48 cm.). Slider rods (PTFE coated stainless steel hypotubes, 3.18mm OD, 1 0.65mm ID, length 33.02cm) were purchased from Applied Plastics. Control Springs (PTFE coated stainless steel sheet springs, thickness 0.10mm, shortest flange length 5.33mm, longest flange length 10.11mm, total length 15.88mm) were ordered from Incodema of Ithaca, NY .
[00151] The rest of the components were supplied from in-house stock or manufactured in-house. All triple lumen tubes were manufactured from Pebax ® 7233 with 20% barium sulfate. Both triple lumen tubes had an OD (outer diameter) of 0.25 mm. A triple lumen tube had lumens rotated with two IDs (internal diameters) of 0.035 mm and an ID of 0.15 mm. A triple lumen tube had a lumen with an oval cross section with two IDs of 0.036mm and an ID of 0.127 x 0.07mm. Stainless steel chucks coated with PTFE (polytetrafluoroethylene) processes were manufactured in-house. A process mandrel had a transverse shape, which transitioned back (OD of 0.16mm) or ovals (OD of 0.14 x 0.07mm). PTFE covered stainless steel wire was obtained from home in stock (OD 0.03mm). Standard luer fittings were obtained from house in stock. A PEEK (Polyether) second tube extrusion was obtained from house stock with an oval cross section of 1.27 x 0.69mm OD
[00152] A first tube was made as follows. A triple extruded tube lumen with round lumens was obtained. Another lumen of the triple extruded tube was obtained with a lumen having an oval cross section. A stainless steel processing mandrel was also obtained with a transverse shape, which goes from round (OD 1 0.52mm) to oval (OD 1 0.39 x 0.81mm). Both extruded tubes were loaded onto the mandrel, with the mandrel being inserted through the larger lumen in both tubes. Two small PTFE covered stainless steel wires were inserted through the smaller lumens of both extruded tubes. The mandrel and tubes were placed on an RF (radio frequency) die (2.51 mm in diameter, 4.45 mm in length, fabricated from D2 tool steel). The junction of the two types of catheters was positioned in the center of the RF mold. The RF matrix and mandrel were placed in the middle of an RF coil in an RF welding machine (Hot Shot I, Ameritherm Inc., Scottsville, NY) and welded as commonly known in the art. When the components had lowed ref, pressure was applied to each end of the extruded pipes to fuse the pipe joint. The matrix was then sprayed with compressed air to cool the mold and to set the Pebax®. The extruded tube and die were removed from the RF machine and the extruded tube was removed from the mold. The mandrel and process wires were removed from the lumens of the extruded tube.
[00153] A lubricious coating can be applied to the second tube. A silicone mold release spray (Nix Stix X-9032A, Dwight Products, Inc., Lyndhurst NJ) can be sprayed onto the distal 30 cm of the second tube and allowed to dry at room temperature in a fume hood.
[00154] The third tube sub-assembly was done in the following manner. A catheter tube was split in two with a razor blade about 6.35 centimeters from the proximal end of the catheter tube. One male and one female in-line luer connector (Qosina, Edgewood, NY) was obtained and drilled to an ID of 3.45 mm. UV (ultra-violet) cured adhesive (Loctite 3041) was applied to the bisected ends of the catheter tube and the perforated luer fittings were attached. The adhesive was cured per manufacturer's instructions and the luer fittings were screwed on.
[00155] The second linear actuator sub-assembly was made as follows. The second linear actuator, port flush, gasket retainer flush and silicone flush gasket were obtained. The flush gasket was inserted into the back of the second linear actuator, with the U-part of the flush gasket facing distally. The flush gasket retainer was mounted from above inside the second linear actuator. Cyanoacrylate glue was applied around the seal retainer to hold the retaining gasket in place. The flush port was placed into an opening in the second linear actuator and an adhesive UV cure was applied and cured according to the manufacturer's instructions.
[00156] A first tube was obtained and cyanoacrylate was applied to the outer surface of the rotated ID section of the catheter in a band 2.54 cm from the end. The catheter was then inserted into the distal end of the control shuttle until the catheter was flush with the back of the control shuttle. The catheter was oriented so that the two small lumens were horizontal and in the upper portion of the lumen round. The recovery cable lock has been snapped into the control transport.
[00157] The second tube sub-assembly was manufactured in the following manner. A four inch diameter piece of 0.033mm diameter nitinol wire was inserted into the second extrusion tube. The second extrusion tube with wire insertion was inserted into a hypotube. The distal end of the hypotube was bent from the side three times.
The distal end of the first tube was threaded through the top of the mandrel control lever and through the top of the opening in the distal end of the mandrel control lever. The distal end of the second tube was threaded onto the proximal end of the control catheter. The second tube was pushed into the first tube, until about 4 cm of hypotube protruded from the end of the control catheter. A cyanoacrylate adhesive was applied to the proximal end of the hypotube for approximately a 12.7mm section. This section was inserted into the top of the opening at the proximal end of the mandrel control lever until flush with the back of the mandrel control lever. The distal end of the first tube was then threaded onto the proximal end of the second linear actuator. The second linear actuator was moved to the back more position on the control catheter.
[00159] The sizing insert was then mounted on a left bodywork. The sizing insert has been oriented so that the groove on the sizing insert fits over the ridge on the left shell. The catheter sub-assembly was placed within the housing on the left of the body so that the mandrel control lever fits into the sizing insert and the second linear actuator fits into the groove at the distal end of the left body housing. A sliding rod was inserted through the openings in the sizing insert part, the mandrel control lever, control spool and the second linear actuator. The sliding rod was made to rest on two brackets on the left body. The control spring was inserted into the right bodywork so that it would fit into the opposite teeth. The right body was then placed over the body shield to the left and the two were photographed together. Two screws (# 4-24 x V inside in Pan Head thread form) were inserted into the available openings in the left bodywork and tightened. The unlocking actuator was snapped into place on the right tab of the second linear actuator with a drop of cyanoacrylate glue to ensure it stayed on.
[00160] The second linear actuator, shuttle control, and the mandrel control lever have been transferred to their forward most positions. The second linear actuator was pulled back and then returned to its forward position. The distal end of the first tube was cut by hand, with a razor blade, to 1.27 mm, measured from the tip of the third tube. The sizing insert was pushed forward. The second tube was cut by hand using a razor blade to a length of about 0.76 mm, measured from the most distal end of the control catheter. An approximately 4-inch long piece of nitinol wire (0.30 mm in diameter) was obtained. A cyanoacrylate adhesive was applied to the end of the second tube with an elongated applicator tip. Nitinol wire was inserted into the tip of the locking device and another piece of wire was used to insert the nitinol wire of about 2 mm into the second tube. The cyanoacrylate adhesive was allowed to cure.
[00161] The second linear actuator was pulled back and a slot was punched out of the control catheter. The groove had a width that is approximately the same width as the minor axis of the oval of the catheter lumen. A shaver was used to trim the groove to a final length of about 19.05 mm. The second linear actuator and gluing insert were then moved to a forward position.
[00162] A rope of approximately 3.05 m in length (PTFE fiber with an OD 0.25 mm) and a nitinol 1 wire 0.52 m (0.15 mm in outer diameter) were obtained. The nitinol wire was inserted into one of the 0.04mm lumens in the first tube and pushed through until it came out onto the handle. Tweezers were used to grip the wire and pull it out of the groove in the handle. About 76.2 millimeters of wires were made to protrude from the distal end of the control catheter. A loop was formed in the wire, inserting the loose end into the same lumen at the distal end of the control catheter. About 76.2 millimeters of safety rope was then introduced through the resulting circuit. The nitinol wire was pulled through the catheter until the retrieval cord protruded onto the identifier.
[00163] A sealing device was obtained. A needle of a type commonly used for sewing was threaded with the retrieval cord and the needle was inserted through the PTFE bag opposite the locking loop and through the lumen of the proximal hole of the sealing device. The nitinol wire was then threaded into the remaining unoccupied 0.04mm lumen of the first tube with the end of the wire loop pointing distally. The needle was removed from the retrieval cord and the cable was threaded through the loop of the nitinol wire. The retrieval cord was then pulled through the catheter in the manner described above.
[00164] The control bus was retracted approximately 12.7 mm. The second tube was then threaded through the grommets of the device. Tweezers were used to catch the retrieval cord and pull it to the outside of the handle. A loop was formed on a small diameter portion of the nitinol wire. The circuit was inserted through an opening in the distal portion of the control transport service start. The safety rope was introduced through this loop and pulled through the opening in the distal portion of the control bus. The lock retrieval cord was removed from transport to control and a free end of the retrieval cord was inserted through the opening in the lock retrieval cord from the bottom. Four more hand knots were tied to the cord. The excess cable was cut by hand and the safety rope lock was returned to the control bus.
[00165] The remaining free retrieval cable was pulled until all slack was gone. The remaining free end of the retrieval cord was inserted into an opening in the front of the upper part of the control wheel. The safety rope was pulled until taught and the safety rope lock was snapped shut. The cable was cut by hand to about 20.32 centimeters.
[00166] The second tube was burned by obtaining a soldering iron with a sharp tip and heating it to about 500°F. The iron tip was inserted into the second tube until a surge was created that was about 1, 39mm in diameter. The lockout circuit over the device has cooled down.
[00167] Example 4
[00168] A length of 0.23mm diameter wire of nitinol (Fort Wayne Metals, Fort Wayne, IN.) was obtained. The specific length of the yarn has not been measured, it is just necessary for the yarn to be long enough to bend through the feed holes described in the following paragraph. The wire was obtained from having been electro polished.
[00169] A base template 8 as described in fig. 17 was obtained. The base template was fixed to a lathe pin bushing and center 22 was inserted into the center of the pin hole 24 enough to fit it securely. A knot was tied at one end of a length of one length of nitinol wire and the untied end was fed through a 10 wire feed hole. Two additional lengths of nitinol wire were bent in half and the free ends were Feed through four remnant holes 12, 14, 16, 18. Weights 20 were attached to the free ends of the five wires to hold the cables tensioned and in place.
[00170] The other end of the center pin 22 was located within the center hole 28 of the tail stock support 26, which was thrown into the tail stock, where the closed face 30 of the tail stock support 26 faced the base jig 8. The base jig 8 and tail support stock 26 were positioned about 5 cm apart. A wire guide 34 was used to prevent the wires from crossing. The base jig 8 was positioned so that the wire feed holes 10, 12, 14, 16, 18 were oriented vertically above the center of the pin 22 and the wires were positioned on the rear side of the center pin 22. wires were wrapped twice around the center and left 22 pin to hang parallel with the wire feed holes.
[00171] The 36 petal template hole has been rotated 720°. The petal jig 38 was inserted into the petal jig hole 36. Without going through the wires, the wires were wrapped clockwise around the petal jig 38 past the drop pin 39 and around the circumference of the drop pin 39. The wires were wrapped around the outer circumference of the petal jig 38 to bring the wire between the petal jig 38 and the center pin 22. They were then wrapped around the center pin 22 twice.
[00172] The wires were placed under anchor plate 11. The anchor plate 11 was secured with Allen head screws 14. The wires were cut on the side of the anchor plate 11, weight 20.
[00173] With the weights 20, tail support material 26, and wire guide 34 removed, the assembly was placed in a convection oven set at 475°C for 14 minutes. The assembly was removed from the oven and quenched in water. Templates were disassembled and the item removed.
[00174] The wire ends were cut with the eyelets and the petals were fanned in the same direction as the helical winding, such that each petal was oriented at 72° relative to the adjacent petal.
[00175] The article was powder coated with powdered FEP (obtained from home stock) in the following manner. A hollow steel mandrel of 2 mm outside diameter was obtained of sufficient length to hold the article and has remaining length to extend to the commercial mixer. The mandrel was inserted into the central hole of the article. One end of the mandrel was grounded. A commercial blender (Variable Speed Lab Blender Waring, Torrington, CT) was obtained and an amount of powdered FEP was added, leaving the tips of the blender blades exposed. The article and mandrel were suspended in the center of the blender, the lid was replaced and the blender was turned on to the highest level of about 5 seconds. The article and mandrel were removed, the mandrel was used to perform a more uniform powder coating, the powder coating was aspirated from the mandrel and the article and mandrel were then hung inside a convection oven set to 320°C for 3 minutes. The article and mandrel were removed from the oven, allowed to cool, and excess FEP was removed from the article, the mandrel removed.
[00176] In a separate process a closed-loop lock 43 (illustrated in Fig. 18A) was manufactured. Locking loop 43 was inserted through hypotube 45 (smaller than eyelet ID) with looped end 47 of locking loop 43 straightened. The hypotube 45 was inserted through the distal end grommets until the locking loop grommet 49 is situated above the distal port 608 of the device. The hypotube has been removed.
[00177] A crimping chuck 41 (shown in Fig. 18B and 18C) was inserted into the article through the grommets with the locking loop 43 along the outer length of the chuck 41. The article was extended in length on the chuck holding the proximal eyelets and center with tweezers. The eyelets were fixed in place, positioning them beyond the mandrel ribs.
[00178] Then, a porous ePTFE film having the following properties was obtained: Bubble point Methanol 0.7 psi Mass / area 2.43 grams / square meter Longitudinal matrix tensile strength 96000 psi Strength Matrix tension in the orthogonal direction of 1433 psi Maximum longitudinal load of 10.6 kg / inch Thickness 0.00889 mm
[00179] The methanol bubble point is measured using a custom built machine with a 1 inch diameter foot, a ramp rate of 0.2 psi/second and a liquid methanol medium. Length and width of material are measured using a metal ruler. Mass/area is measured using a scale (Model GF-400 Top Loader Balance, ANG, San Jose CA.) With a 36 x 5 cm sample. Maximum longitudinal load is measured using a materials testing machine (Model 5564, Instron, Grove City, PA) equipped with a 10 kg load cell. The indicator length is 2.54cm and the cross head speed is 25mm/minute. Width of the sample is 2.54cm. Longitudinal tensile test measurements are taken in the material length direction. Thickness is measured using a thickness gauge (Mitutoyo Digital Indicator 547-400) with a foot diameter of % inch. The longitudinal matrix tensile strengths (MTS) are calculated using the following equation: Density is calculated using the formula, density = mass / volume, as described in an earlier example.
[00180] A 30mm film tube is constructed from ePTFE material as follows. For a 25 mm diameter device, a film with a slit width of about 0.905 centimeters 1 is wound onto a 30 mm OD mandrel. The amount of film overlap is not critical, but no edge overlap is unacceptable. The film tube is then removed from the mandrel and stretched to make the tube identification to be about 25mm. The film tube was slid over the top of the article and tensioned using ePTFE film, the ends of the tube were clamped around the center of the device, then the grommets.
[00181] Another porous ePTFE film, which has a FEP layer, was obtained having the following properties: Mass / area of 36.1 grams / square meter Maximum Load, Longitudinal 12.6 kg / cm Maximum Load, transverse of 0.3 kg / cm Thickness of 0.030 mm
[00182] The test methods for the above tests are described above. The FEP thickness in the film is about 62.5%. FEP Thickness (%) is calculated as the ratio of FEP thickness to film thickness. The reported value represents the average measurements of five samples. FEP thickness and film thickness is measured from scanning electron microscopy images of cross-sections of the laminated ePTFE/FEP material in the following manner. Magnification is chosen to allow viewing of the full thickness of the film. Five lines perpendicular to the horizontal edge of the image are drawn randomly across the full thickness of the film. Thickness is determined by measuring the thickness of the FEP and the thickness of the film.
[00183] The 2mm wide strip of this ePTFE FEP-coated film, with the FEP side down, was wrapped four times around the tight parts and heated with a soldering iron to join the film layers together.
[00184] The mandrel and article were placed inside a convection oven set to 320°C for 3 minutes and then removed and allowed to cool. Excess ePTFE material was trimmed and the article removed from the mandrel.
[00185] Example 5
[00186] An article was constructed in the same way as in example 1 with the following exceptions:
[00187] Instead of using petal jig 38, self centering petal jig 39 (Fig. 19) was used in which jig 39 was placed over center pin 22 and tail support stock 26 was introduced before winding the first hoop. After wrapping the first self centering petal grommet jig 39 was inserted into the petal jig hole 36. The wire was wrapped around the perimeter of petal jig 39 to form petals and wrapping was continued around the center of the pin 22 to create a second hole . A final, fully extended article of this example is shown in Figures 20A and B.
[00188] Example 6
[00189] An additional article 32 shown in fig. 21 was constructed using two intermediate articles (i.e., not powder coated) (one inside and one outside) of example 5, in which, the intermediate articles were wrapped in opposite directions. In addition, the inner intermediate article was manufactured in such a way that the grommets of the inner intermediate article would fit inside the grommets of the outer intermediate article. Prior to FEP coating, the interior and exterior intermediate articles were nested using the following method:
[00190] In order to achieve nesting of the two intermediate articles, the distal eyelets and the proximal eyelets must be nested. Inner intermediate article was positioned at the end of a straight circular mandrel. An outer intermediate article hole was positioned over an inner intermediate article hole and the two intermediate articles were repositioned to the other end of the mandrel. The remaining eyelet of the outer intermediate article was placed over the remaining hole of the inner intermediate article. They were arranged so that the overlapping wires were evenly spaced (about 72" apart), thus creating a frame. The frame was later FEP coated and covered with an ePTFE bag in order to create the final article.
[00191] Example 7
[00192] With the following exceptions, an article similar to the one described in example 1 has been created: A similar template 50 illustrated in fig. 22B as previously described in example 1 was obtained. The petal 52 and waist 54 jigs jigs were positioned as shown in Figure 22B. The wire winding process is shown in the wire path 56 shown in Figure 22B, where the wire starts at anchor points 57 and ends at the pin eye 58 (not shown) which is inserted into the hole 59 of the grommet pin. The wire is wound around 720° around the eye pin, at the beginning of the wrapping device and at the end of the wrapping device. The final, fully extended article 51 of this example is shown in Figure 22A.
[00193] Example 8
[00194] An additional article (Figures 23A and 23B) was constructed using two intermediate (i.e. not powder coated) articles (one inside and one outside) from example 7, in which, the intermediate articles were wrapped in opposite directions . In addition, the inner intermediate article was manufactured in such a way that the grommets of the inner intermediate article would fit inside the grommets of the outer intermediate article.
[00195] Prior to FEP coating, the interior and exterior intermediate articles were nested using the following method:
[00196] In order to achieve nesting of the two intermediate articles, the distal eyelets and the proximal eyelets were nested. Inner intermediate article was positioned at the end of a straight circular mandrel. An outer intermediate article hole was positioned over an inner intermediate article hole and the two intermediate articles were repositioned to the other end of the mandrel. The remaining eyelet of the outer intermediate article was placed over the remaining hole of the inner intermediate article. They were arranged so that the overlapping strands were evenly spaced (about 72° apart), thus creating a frame. The framework was later FEP coated and covered with an ePTFE bag in order to create the final article.
[00197] Example 9
[00198] yarn was obtained as described in the previous examples. A locking loop base jig 60 (Fig. 24A) with center pin 22 was placed on custom stand as a fabrication aid. The knob component 62 configured in such a way that the inner lumen is not round but is keyed so as not to rotate on a central pin has been obtained. The wire was formed into a loop shape and the loop was inserted through the lumen of the button 62. The button with wire mesh was threaded onto the central pin 22, with the mesh facing away from the center pin as the mating portion of the inner lumen of the button component. The mating part of the button component 62 was situated to the right of the base template of the locking loop 60. A wire was chosen and bent towards the constructor, then wrapped 360° around the button component 62, then wrapped around center pin 22 for a minimum of four revolutions and tied after the fourth revolution. The wire wraps should be spaced about 1 mm apart. Circuit forming tool 64 (Fig. 24B) was inserted into locking snare base jig 200 against center pin 22. The free wire was wound about 370° from axis 66 of snare forming tool 64 then wrapped around pin 68, that the loop forming tool 64 is anchored to the locking loop template base 60. The base template 60 and loop forming tool 64 were removed from the holder and placed in an oven. The entire set was heated in an oven as described above for 14 min. at 475°C. The locking loop was removed from the jig 60 and forming clip tool 64 and the excess wire was trimmed.
[00199] Example 10
[00200] The following embodiments teach a heat assembly for the device described in Example 7, prior to application of the cap, hereinafter called the table of Example 7.
[00201] The frame of Example 7 was placed on a mandrel of about 2 mm. The mandrel 72 was bent on both sides if the article so as to secure it from moving. The frame was then placed over the tubular cylinder 70 depicted in Figure 25A such that the outer perimeter of the frame rested on the upper edge of the cylinder 70. Plug 74 was then placed over the frame and cylinder 70 as shown in Figure 25B and secured. in place via setscrew 76. The entire assembly was then placed in a forced air circulation oven set at 475°C for 14 minutes. The assembly was removed from the oven and quenched in room temperature water. Structure 78 was further powder coated FEP as described in Example 2.
[00202] Example 11
[00203] The following embodiments teach an anchoring device for the device described in Example 10.
[00204] (a) an anchoring member 80 as shown in Figure 26A was created by the method as is generally shown in Figure 26B. Thread 82 of each of the petals was cut at location 84, thus eliminating the remaining 86 of the loop length, resulting in anchor 80. Anchor component 80 was affixed to the molding side 78, as is generally shown in Figure 26C . The anchor spokes 82 were aligned with the wires of the structure 78. A tape made of ePTFE film with a thin layer of FEP was wrapped around the wires 82 and the wires of the structure 78, 88 and then heated to bond. wires together as shown in Figure 27.
[00205] The article was powder coated with powdered FEP as described above. Frame 78 was covered as described above, after which wires 82 were individually manipulated to protrude through sealing member 106, as shown in Figure 28.
[00206] (b) In another embodiment, the anchoring component 80 of Example 11(a) has been further modified as follows. Jig 90 and washer 92, as shown in Figures 29A and 29B, respectively, were obtained. Anchor member 80 was inserted grommets into template 90 such that grommet 80 was located within bore 91 and wires 82 were located within slots 95 of template 90. Washer 92 was placed on top of anchor member 80 to hold it in place and washer 92, was fixed with screw 323 in hole 94, as shown in Figures 29A-29C, which caused the wire points 82 to orient towards the face of the washer.
[00207] (c) In another embodiment, the anchoring member 80 (. Shown in Fig. 30) is manufactured as follows:
[00208] A length of about 1 meter of 10% platinum filled nitinol wire (Fort Wayne Metals, Fort Wayne, IN.) designed with a diameter of about 0.23 millimeters is obtained. The specific length of the yarn is not measured, it is just necessary for the yarn to be long enough to complete the winding pattern as described in the following paragraph. The yarn is obtained having been electropolished. Nitinol Electropolishing wire confers certain well-known properties, such as spontaneously forming a layer of titanium dioxide on the surface, selectively reducing the amount of nickel on the wire surface, and removing some of the stresses in the wire by improving, thus, fatigue.
[00209] A base template 8 as described in fig. 17 is obtained. One end of a length of wire about 0.5 meters long is knotted and the unknotted end is fed through a 10 wire feed hole. Two additional lengths of wire (about 1 meter each ) are folded in half and the free ends are fed through the remaining four feed holes 12, 14, 16, 18, with the wire entering the funnel-shaped opening holes 19 (not shown) with the small feed holes at the bottom of the opening 19. The wires then exit through holes 10, 12, 14, 16 and 18 in the flat end surface of the jig 8. weights 20 are attached to the free ends of the five wires to hold the cables tensioned and in place . The base template is attached to a lathe pin bushing and center 22 is inserted into the center of the pin hole 24 enough to fit it securely.
[00210] The other end of the center pin 22 is located within the center hole 28 of the tail stock support 26, which is thrown into the tail stock, wherein the closed face 30 of the tail stock support 26 faces the base jig 8. 8 base jig and 26 stock support tail are positioned about 5 cm apart. A wire guide 34 is used to prevent the wires from crossing. The base jig 8 is positioned such that the wire feed holes 10, 12, 14, 16, 18 are oriented vertically above the center of the pin 22 and the wires are positioned on the rear side of the center pin 22.
[00211] The 36 petal template hole is rotated 720°. The petal jig 38 is inserted into the petal jig hole 36. Without going through the wires, the wires are placed on top of the petal jig 38. The base jig 8 is rotated 360° to create the device petals. The base jig 8 is rotated another 720", with the wires placed on top of the center pin 22.
[00212] With the weights 20, the tail support material 26, and the wire guide 34 removed, the assembly is placed in a convection oven set at 475°C for 14 minutes. The set is removed from the oven and has been tempered in water. Templates are disassembled and the item is removed. The ends of the wires are cut to the grommets and the anchor loops are spread in the same direction as the helical winding, so that each anchor loop is oriented 72" offset relative to the adjacent anchor loops. The anchor loops are pressed in the center by hand and heat set again as described earlier.
[00213] (d) In another embodiment, the fastening components are manufactured by stapling lengths of about 2 cm of straight wire nrtinol 71. A tape made of ePTFE film with a thin layer of FEP is wrapped around 88 the 71 wires and the structure wires 78 and then heated to connect the wires together as shown in Figure 31.
[00214] Example 12 A device as previously described in Example 10 with anchors as described in example 11(d) is fabricated by connecting the anchors at various locations along the frame wires 78.
[00215] In addition to being directed to the teachings described above and claimed below, devices and/or methods that possess different combinations of the features described above and claimed below are contemplated. As such, the description is also directed to other devices and/or methods that have any other possible combination of the dependent features claimed below.
[00216] Numerous features and advantages have been presented in the above description, including several alternatives, along with details of the structure and function of the devices and/or methods. The disclosure is intended as illustrative only and as such is not intended to be exhaustive. It will be apparent to those skilled in the art that various modifications can be made, in particular with regard to structure, materials, elements, components, shape, size and arrangement of parts, including combinations within the principles of the invention, to the fullest extent indicated by broad, general meaning of the terms in which the appended claims are expressed. Insofar as these various modifications do not depart from the spirit and scope of the appended claims, they are intended to be covered therein.

权利要求:
Claims (31)
[0001]
1. A medical device comprising: a plurality of elongated members disposed to define a structure of the medical device, the structure includes a proximal eyelet near a first longitudinal end of the device, a distal eyelet near a second longitudinal end of the device, a proximal bulb, and a distal bulb, wherein the proximal bulb and distal bulb are each located between the first eyelet and the second eyelet, and wherein the distal bulb includes a plurality of petals; and a sealing member covering at least a portion of the structure of the medical device, characterized in that it comprises at least one anchor (500) attached to at least one of the petals of the distal bulb, wherein the at least one anchor (500) includes a first leg (501) and a second leg (502), wherein at least a portion of the first leg is oriented parallel to a portion of the second leg, and wherein the first leg and second leg converge to a bent end (503) at least one anchor.
[0002]
The medical device of claim 1, characterized in that each petal of the plurality of petals includes at least one anchor (500).
[0003]
The medical device of claim 1, characterized in that at least one petal of the plurality of petals includes at least two anchors (500).
[0004]
Medical device according to claim 1, characterized in that at least one petal of the plurality of petals is free of an anchor (500).
[0005]
The medical device of claim 1, characterized in that each petal of the plurality of petals includes at least one anchor (500).
[0006]
The medical device of claim 1, characterized in that the at least one anchor (500) is covered by the sealing member.
[0007]
Medical device according to claim 1, characterized in that the sealing element comprises polytetrafluoroethylene.
[0008]
Medical device according to claim 1, characterized in that at least one anchor (500) is freed from the cover by the sealing member.
[0009]
The medical device of claim 1, characterized in that at least one anchor (500) is adapted to atraumatically contact body tissue at the site of an implant.
[0010]
10. Medical device according to claim 1, characterized in that the distal eyelet extends from the distal bulb.
[0011]
Medical device according to claim 1, characterized in that at least a portion of the distal bulb is concave with respect to the distal eyelet.
[0012]
A medical device according to claim 1, characterized in that the medical device is adapted to occlude a left atrial appendage.
[0013]
The medical device of claim 1, characterized in that the first leg (501) and the second leg (502) each comprise first and second portions.
[0014]
The medical device of claim 13, characterized in that the first portion of the first leg (501) and the first portion of the second leg (502) are of the same length and are parallel to each other.
[0015]
The medical device of claim 14, characterized in that second portions of the first and second legs (501, 502) diverge laterally from the respective first portions and converge at the bent end to define an opening (504) of at least , an anchor (500).
[0016]
The medical device of claim 15, characterized in that the opening (504) has an oval shape.
[0017]
The medical device of claim 15, characterized in that the opening (504) has a rectangular shape.
[0018]
The medical device of claim 15, characterized in that the opening (504) is circular in shape.
[0019]
The medical device of claim 15, characterized in that at least one anchor (500) has a hockey stick configuration, and wherein the first portion of the first and second legs (501, 502) corresponds to an axis of a hockey stick and the second portion of the first and second legs corresponds to a hockey stick blade.
[0020]
The medical device of claim 15, characterized in that the first portion of the first leg (501) and the second portion of the first leg define an angle (A) in the range of 45 degrees to 135 degrees.
[0021]
The medical device of claim 15, characterized in that the first portion of the first leg (501) and the second portion of the first leg define an angle in the range of 75 degrees to 155 degrees.
[0022]
The medical device of claim 15, characterized in that the first portion of the first leg (501) and the second portion of the first leg define an angle of 90 degrees.
[0023]
The medical device of claim 1, characterized in that at least a portion of the first and second legs (501, 502) are not parallel to each other.
[0024]
24. A medical device comprising: a plurality of wires (602); a proximal grommet (610) formed by proximal end portions of the plurality of wires (602); a distal grommet (608) formed by distal end portions of the plurality of wires (602); a proximal disk comprising a plurality of proximal petals formed by the proximal portions of a plurality of wires (602); and a distal disk comprising a plurality of distal petals formed by the proximal portions of a plurality of wires (602), characterized by comprising a waist portion (614) disposed between the proximal disk and the distal disk formed by central portions of the plurality of wires (602).
[0025]
25. The medical device of claim 24, characterized in that each of the plurality of wires (602) includes a reniform shape.
[0026]
26. Medical device according to claim 24, characterized in that it further comprises a sealing element fixed to the plurality of wires (602), the sealing element and the proximal disc form a proximal occlusion element, and the element seal and the distal disc form a distal occluding element.
[0027]
27. The medical device of claim 24, wherein the plurality of wires (602) forms an hourglass shape in an elongated configuration.
[0028]
28. The medical device of claim 24, characterized in that the waist portion (614) includes an internal open area (53).
[0029]
29. The medical device of claim 24, characterized in that the plurality of proximal petals includes overlapping zones, and the plurality of distal petals includes overlapping zones.
[0030]
30. The medical device of claim 24, characterized in that the waist portion forms a reniform shape with an open inner area (53) when the medical device is in an implanted configuration.
[0031]
31. The medical device of claim 30, characterized in that the plurality of wires (52) form a wire structure (61) that includes an inner peripheral edge (54) and an outer peripheral edge (55), and the outer peripheral edge (55) is shown as the outermost edge of the wire structure (51), and the inner peripheral edge (54) is an innermost edge of the open inner area (53) of the reniform shape in an implanted configuration. .

类似技术:

---

公开号 | 公开日 | 专利标题

---

BR112014011156B1|2021-06-01|MEDICAL DEVICE

---

US20210007725A1|2021-01-14|Sealing device and delivery system

---

EP2945548B1|2019-05-01|Sealing device

---

US20170007222A1|2017-01-12|Sealing device and delivery system

---

JP6470316B2|2019-02-13|Sealing device and delivery system

---

CA3053118C|2022-02-15|Sealing device and delivery system

同族专利:

---

公开号 | 公开日

---

AU2012336058A1|2014-05-01|

---

JP6480494B2|2019-03-13|

---

EP2775930B1|2017-10-18|

---

EP2775930A1|2014-09-17|

---

CN104039241B|2017-07-07|

---

KR102118755B1|2020-06-03|

---

HK1202040A1|2015-09-18|

---

CN104039241A|2014-09-10|

---

JP2015500676A|2015-01-08|

---

WO2013070554A1|2013-05-16|

---

US9381006B2|2016-07-05|

---

CN107157527A|2017-09-15|

---

BR112014011156A2|2017-05-09|

---

JP6208678B2|2017-10-04|

---

EP3292825A1|2018-03-14|

---

US20120143242A1|2012-06-07|

---

KR20140090666A|2014-07-17|

---

CA2854184C|2017-08-15|

---

JP2017131678A|2017-08-03|

---

RU2014123311A|2015-12-20|

---

CN107157527B|2020-10-30|

---

CA2854184A1|2013-05-16|

---

HK1250567A1|2018-12-28|

引用文献:

---

公开号 | 申请日 | 公开日 | 申请人 | 专利标题

---

---

DK151404C|1984-05-23|1988-07-18|Cook Europ Aps William|FULLY FILTER FOR IMPLANTATION IN A PATIENT'S BLOOD|

---

US4917089A|1988-08-29|1990-04-17|Sideris Eleftherios B|Buttoned device for the transvenous occlusion of intracardiac defects|

---

WO1991015155A1|1990-04-02|1991-10-17|Kanji Inoue|Device for closing shunt opening by nonoperative method|

---

JPH0613686Y2|1990-06-08|1994-04-13|加藤発条株式会社|Blood vessel obturator|

---

US5108420A|1991-02-01|1992-04-28|Temple University|Aperture occlusion device|

---

EP0545091B1|1991-11-05|1999-07-07|The Children's Medical Center Corporation|Occluder for repair of cardiac and vascular defects|

---

DE69226841T2|1991-11-05|1999-05-20|Childrens Medical Center|Occlusion device for repairing heart and vascular defects|

---

DK168419B1|1991-11-25|1994-03-28|Cook Inc A Cook Group Company|Abdominal wall support device and apparatus for insertion thereof|

---

DE69324239T2|1992-01-21|1999-11-04|Univ Minnesota|SEPTUAL DAMAGE CLOSURE DEVICE|

---

US5486193A|1992-01-22|1996-01-23|C. R. Bard, Inc.|System for the percutaneous transluminal front-end loading delivery of a prosthetic occluder|

---

US6497709B1|1992-03-31|2002-12-24|Boston Scientific Corporation|Metal medical device|

---

JPH07505316A|1992-03-31|1995-06-15|

---

US6346074B1|1993-02-22|2002-02-12|Heartport, Inc.|Devices for less invasive intracardiac interventions|

---

US6123715A|1994-07-08|2000-09-26|Amplatz; Curtis|Method of forming medical devices; intravascular occlusion devices|

---

US6168622B1|1996-01-24|2001-01-02|Microvena Corporation|Method and apparatus for occluding aneurysms|

---

JPH10504738A|1994-07-08|1998-05-12|マイクロベナコーポレイション|Medical device forming method and vascular embolization device|

---

US5725552A|1994-07-08|1998-03-10|Aga Medical Corporation|Percutaneous catheter directed intravascular occlusion devices|

---

US6171329B1|1994-12-19|2001-01-09|Gore Enterprise Holdings, Inc.|Self-expanding defect closure device and method of making and using|

---

US5634936A|1995-02-06|1997-06-03|Scimed Life Systems, Inc.|Device for closing a septal defect|

---

DE19604817C2|1996-02-09|2003-06-12|Pfm Prod Fuer Die Med Ag|Device for closing defect openings in the human or animal body|

---

US5733294A|1996-02-28|1998-03-31|B. Braun Medical, Inc.|Self expanding cardiovascular occlusion device, method of using and method of making the same|

---

US5853422A|1996-03-22|1998-12-29|Scimed Life Systems, Inc.|Apparatus and method for closing a septal defect|

---

AT424767T|2000-11-07|2009-03-15|Carag Ag|APPARATUS FOR SEALING AN OPENING, FOR EXAMPLE, IN A WALL OF A HOLLOW OR TUBULAR ORGAN|

---

US6488706B1|1996-05-08|2002-12-03|Carag Ag|Device for plugging an opening such as in a wall of a hollow or tubular organ|

---

US5861003A|1996-10-23|1999-01-19|The Cleveland Clinic Foundation|Apparatus and method for occluding a defect or aperture within body surface|

---

US5879366A|1996-12-20|1999-03-09|W.L. Gore & Associates, Inc.|Self-expanding defect closure device and method of making and using|

---

US5782860A|1997-02-11|1998-07-21|Biointerventional Corporation|Closure device for percutaneous occlusion of puncture sites and tracts in the human body and method|

---

WO1999025280A1|1997-11-14|1999-05-27|Boston Scientific Limited|Multi-sheath delivery catheter|

---

US5944738A|1998-02-06|1999-08-31|Aga Medical Corporation|Percutaneous catheter directed constricting occlusion device|

---

US5925060A|1998-03-13|1999-07-20|B. Braun Celsa|Covered self-expanding vascular occlusion device|

---

US7044134B2|1999-11-08|2006-05-16|Ev3 Sunnyvale, Inc|Method of implanting a device in the left atrial appendage|

---

US6152144A|1998-11-06|2000-11-28|Appriva Medical, Inc.|Method and device for left atrial appendage occlusion|

---

US6994092B2|1999-11-08|2006-02-07|Ev3 Sunnyvale, Inc.|Device for containing embolic material in the LAA having a plurality of tissue retention structures|

---

CN2351104Y|1998-12-21|1999-12-01|李春江|Reticular atrial and ventricular septal defect occluding device|

---

US6368338B1|1999-03-05|2002-04-09|Board Of Regents, The University Of Texas|Occlusion method and apparatus|

---

US6656206B2|1999-05-13|2003-12-02|Cardia, Inc.|Occlusion device with non-thrombogenic properties|

---

US6712836B1|1999-05-13|2004-03-30|St. Jude Medical Atg, Inc.|Apparatus and methods for closing septal defects and occluding blood flow|

---

EP1210014A1|1999-09-07|2002-06-05|Microvena Corporation|Retrievable septal defect closure device|

---

US8083766B2|1999-09-13|2011-12-27|Rex Medical, Lp|Septal defect closure device|

---

US6551303B1|1999-10-27|2003-04-22|Atritech, Inc.|Barrier device for ostium of left atrial appendage|

---

DE10000137A1|2000-01-04|2001-07-12|Pfm Prod Fuer Die Med Ag|Implantate for closing defect apertures in human or animal bodies, bearing structure of which can be reversed from secondary to primary form by elastic force|

---

US6468303B1|2000-03-27|2002-10-22|Aga Medical Corporation|Retrievable self expanding shunt|

---

US6214029B1|2000-04-26|2001-04-10|Microvena Corporation|Septal defect occluder|

---

US20090069885A1|2004-05-14|2009-03-12|Rahdert David A|Devices, systems, and methods for reshaping a heart valve annulus|

---

US6623506B2|2001-06-18|2003-09-23|Rex Medical, L.P|Vein filter|

---

US20060052821A1|2001-09-06|2006-03-09|Ovalis, Inc.|Systems and methods for treating septal defects|

---

US20080015633A1|2001-09-06|2008-01-17|Ryan Abbott|Systems and Methods for Treating Septal Defects|

---

US20090054912A1|2001-09-06|2009-02-26|Heanue Taylor A|Systems and Methods for Treating Septal Defects|

---

RU2208400C2|2001-10-08|2003-07-20|Робак Анатолий Николаевич|Apparatus for application of compression circular anastomoses|

---

US6939352B2|2001-10-12|2005-09-06|Cordis Corporation|Handle deployment mechanism for medical device and method|

---

US6866669B2|2001-10-12|2005-03-15|Cordis Corporation|Locking handle deployment mechanism for medical device and method|

---

CN2524710Y|2001-12-27|2002-12-11|龚善石|New cardiac atrial septal defect blocking device|

---

CA2477220C|2002-03-14|2007-11-06|Jeffrey E. Yeung|Suture anchor and approximating device|

---

US6960189B2|2002-03-29|2005-11-01|Gore Enterprise Holdings|Proximal catheter assembly allowing for natural and suction-assisted aspiration|

---

US7431729B2|2002-06-05|2008-10-07|Nmt Medical, Inc.|Patent foramen ovale closure device with radial and circumferential support|

---

WO2004052213A1|2002-12-09|2004-06-24|Nmt Medical, Inc.|Septal closure devices|

---

DE10302447B4|2003-01-21|2007-12-06|pfm Produkte für die Medizin AG|Occlusion device, placement system, set of such a placement system and such occlusion device and method for producing an occlusion device|

---

US20040143294A1|2003-01-22|2004-07-22|Cardia, Inc.|Septal stabilization device|

---

US20040267306A1|2003-04-11|2004-12-30|Velocimed, L.L.C.|Closure devices, related delivery methods, and related methods of use|

---

US8372112B2|2003-04-11|2013-02-12|St. Jude Medical, Cardiology Division, Inc.|Closure devices, related delivery methods, and related methods of use|

---

US6913614B2|2003-05-08|2005-07-05|Cardia, Inc.|Delivery system with safety tether|

---

US7625364B2|2003-05-27|2009-12-01|Cardia, Inc.|Flexible center connection for occlusion device|

---

US9861346B2|2003-07-14|2018-01-09|W. L. Gore & Associates, Inc.|Patent foramen ovale closure device with linearly elongating petals|

---

US8480706B2|2003-07-14|2013-07-09|W.L. Gore & Associates, Inc.|Tubular patent foramen ovale closure device with catch system|

---

ES2428967T3|2003-07-14|2013-11-12|W.L. Gore & Associates, Inc.|Oval foramen tubular permeable closure device with retention system|

---

US7735493B2|2003-08-15|2010-06-15|Atritech, Inc.|System and method for delivering a left atrial appendage containment device|

---

US7192435B2|2003-09-18|2007-03-20|Cardia, Inc.|Self centering closure device for septal occlusion|

---

US7658748B2|2003-09-23|2010-02-09|Cardia, Inc.|Right retrieval mechanism|

---

US7967829B2|2003-10-09|2011-06-28|Boston Scientific Scimed, Inc.|Medical device delivery system|

---

US20050192627A1|2003-10-10|2005-09-01|Whisenant Brian K.|Patent foramen ovale closure devices, delivery apparatus and related methods and systems|

---

US20060106447A1|2004-01-26|2006-05-18|Nmt Medical, Inc.|Adjustable stiffness medical system|

---

JP4531774B2|2004-02-04|2010-08-25|カラクアーゲー|Implants for occluding passages in the body|

---

CA2558247A1|2004-03-03|2005-10-06|Nmt Medical, Inc.|Delivery/recovery system for septal occluder|

---

JP4589643B2|2004-03-17|2010-12-01|テルモ株式会社|In vivo tissue closure device|

---

US8398670B2|2004-03-19|2013-03-19|Aga Medical Corporation|Multi-layer braided structures for occluding vascular defects and for occluding fluid flow through portions of the vasculature of the body|

---

US8777974B2|2004-03-19|2014-07-15|Aga Medical Corporation|Multi-layer braided structures for occluding vascular defects|

---

ES2552086T5|2004-04-08|2020-03-25|Aga Medical Corp|Flanged occlusion devices|

---

US8361110B2|2004-04-26|2013-01-29|W.L. Gore & Associates, Inc.|Heart-shaped PFO closure device|

---

US7704268B2|2004-05-07|2010-04-27|Nmt Medical, Inc.|Closure device with hinges|

---

CN100413471C|2004-06-25|2008-08-27|深圳市先健科技股份有限公司|Latching of left auricular appendix and conveyor thereof|

---

US7905901B2|2004-11-29|2011-03-15|Cardia, Inc.|Self-centering occlusion device|

---

US7582104B2|2004-12-08|2009-09-01|Cardia, Inc.|Daisy design for occlusion device|

---

US9545300B2|2004-12-22|2017-01-17|W. L. Gore & Associates, Inc.|Filament-wound implantable devices|

---

US8277480B2|2005-03-18|2012-10-02|W.L. Gore & Associates, Inc.|Catch member for PFO occluder|

---

US20070185530A1|2005-09-01|2007-08-09|Chao Chin-Chen|Patent foramen ovale closure method|

---

KR101334502B1|2005-10-19|2013-12-05|펄사 배스큘러, 아이엔씨.|Method and systems for endovascularly clipping and repairing lumen and tissue defects|

---

US8545530B2|2005-10-19|2013-10-01|Pulsar Vascular, Inc.|Implantable aneurysm closure systems and methods|

---

JP2009512521A|2005-10-24|2009-03-26|エヌエムティーメディカル，インコーポレイティッド|Radiopaque bioabsorbable occluder|

---

WO2007054116A1|2005-11-11|2007-05-18|Occlutech Gmbh|Occlusion instrument for closing a cardiac auricle and a method for producing such an occlusion instrument|

---

DE102006013770A1|2006-03-24|2007-09-27|Occlutech Gmbh|Occlusion instrument and method for its production|

---

CA2646825A1|2006-03-31|2007-10-11|Nmt Medical, Inc.|Adjustable length patent foramen ovale occluder and catch system|

---

EP2004068B1|2006-03-31|2018-08-15|W.L. Gore & Associates, Inc.|Deformable flap catch mechanism for occluder device|

---

DE102006036649A1|2006-04-27|2007-10-31|Biophan Europe Gmbh|Occluder for human or animal heart, has intermediate piece eccentrically connected with each closing body in edge area of bodies in closing condition, where occluder or its part forms electrical resonant oscillating circuit|

---

CN2904980Y|2006-05-11|2007-05-30|中国人民解放军第二军医大学|A left auricle occluding device|

---

CN200963203Y|2006-08-08|2007-10-24|深圳市先健科技股份有限公司|Blocking device for cardiac septal defect|

---

US20080039743A1|2006-08-09|2008-02-14|Coherex Medical, Inc.|Methods for determining characteristics of an internal tissue opening|

---

US20080077180A1|2006-09-26|2008-03-27|Nmt Medical, Inc.|Scaffold for tubular septal occluder device and techniques for attachment|

---

DE102006050385A1|2006-10-05|2008-04-10|pfm Produkte für die Medizin AG|Implantable mechanism for use in human and/or animal body for e.g. closing atrium septum defect, has partial piece that is folded back on another partial piece from primary form into secondary form of carrying structure|

---

CN200980690Y|2006-11-13|2007-11-28|王震|Multifunctional heart partition defect blocking device|

---

ES2353827T3|2006-11-20|2011-03-07|Septrx, Inc.|DEVICE FOR THE PREVENTION OF THE UNWANTED PASSAGE OF EMBOLS FROM A VENOUS BLOODY DEPOSIT TO AN ARTERIAL BLOODY DEPOSIT.|

---

DE602007009915D1|2006-11-20|2010-12-02|Septrx Inc|Device for preventing unwanted flow of emboli from the veins into the arteries|

---

US9005242B2|2007-04-05|2015-04-14|W.L. Gore & Associates, Inc.|Septal closure device with centering mechanism|

---

US8034061B2|2007-07-12|2011-10-11|Aga Medical Corporation|Percutaneous catheter directed intravascular occlusion devices|

---

CN201082203Y|2007-10-26|2008-07-09|先健科技有限公司|Heart defect occluder device|

---

US20090171386A1|2007-12-28|2009-07-02|Aga Medical Corporation|Percutaneous catheter directed intravascular occlusion devices|

---

US9743918B2|2008-01-18|2017-08-29|St. Jude Medical, Cardiology Division, Inc.|Percutaneous catheter directed intravascular occlusion device|

---

US9138213B2|2008-03-07|2015-09-22|W.L. Gore & Associates, Inc.|Heart occlusion devices|

---

US9119607B2|2008-03-07|2015-09-01|Gore Enterprise Holdings, Inc.|Heart occlusion devices|

---

RU84711U1|2008-10-30|2009-07-20|Государственное образовательное учреждение высшего профессионального образования "Белгородский государственный университет"|NOBILE CATHETER-DRAINAGE|

---

CN101773418B|2009-01-12|2011-12-07|赵菁|Cardiac ventricular septal defect closer|

---

EP2442728B1|2009-06-17|2018-07-25|Coherex Medical, Inc.|Medical device for modification of left atrial appendage|

---

US8956389B2|2009-06-22|2015-02-17|W. L. Gore & Associates, Inc.|Sealing device and delivery system|

---

US20120029556A1|2009-06-22|2012-02-02|Masters Steven J|Sealing device and delivery system|

---

JP5736378B2|2009-09-29|2015-06-17|カーディオキネティックス・インコーポレイテッドＣａｒｄｉｏｋｉｎｅｔｉｘ， Ｉｎｃ．|Endocardial device delivery system and system for reducing the effective volume of the ventricle|

---

US20110301630A1|2010-06-02|2011-12-08|Cook Incorporated|Occlusion device|

---

EP2524653A1|2011-05-17|2012-11-21|Carag AG|Occluder|

---

US10828019B2|2013-01-18|2020-11-10|W.L. Gore & Associates, Inc.|Sealing device and delivery system|US9005242B2|2007-04-05|2015-04-14|W.L. Gore & Associates, Inc.|Septal closure device with centering mechanism|

---

US20130165967A1|2008-03-07|2013-06-27|W.L. Gore & Associates, Inc.|Heart occlusion devices|

---

US20120083832A1|2009-06-03|2012-04-05|Symetis Sa|Closure device and methods and systems for using same|

---

US20120029556A1|2009-06-22|2012-02-02|Masters Steven J|Sealing device and delivery system|

---

US8956389B2|2009-06-22|2015-02-17|W. L. Gore & Associates, Inc.|Sealing device and delivery system|

---

US9744033B2|2011-04-01|2017-08-29|W.L. Gore & Associates, Inc.|Elastomeric leaflet for prosthetic heart valves|

---

US9770232B2|2011-08-12|2017-09-26|W. L. Gore & Associates, Inc.|Heart occlusion devices|

---

CN104039246A|2012-01-06|2014-09-10|因赛普特斯医学有限责任公司|Expandable occlusion devices and methods of use|

---

US10959715B2|2012-10-31|2021-03-30|W. L. Gore & Associates, Inc.|Devices and methods related to deposited support structures|

---

US10675012B2|2012-11-16|2020-06-09|W. L. Gore & Associates, Inc.|Joint assembly for medical devices|

---

US20140142610A1|2012-11-16|2014-05-22|W.L. Gore & Associates, Inc.|Space Filling Devices|

---

US10828019B2|2013-01-18|2020-11-10|W.L. Gore & Associates, Inc.|Sealing device and delivery system|

---

US10123805B2|2013-06-26|2018-11-13|W. L. Gore & Associates, Inc.|Space filling devices|

---

US20150005810A1|2013-06-26|2015-01-01|W. L. Gore & Associates, Inc.|Space filling devices|

---

WO2017185082A1|2016-04-23|2017-10-26|Nasser Rafiee|Devices and methods for closure of transvascular or transcameral access ports|

---

US9808230B2|2014-06-06|2017-11-07|W. L. Gore & Associates, Inc.|Sealing device and delivery system|

---

CN107889455B|2015-04-23|2021-09-03|得克萨斯农业及机械体系综合大学|Biocompatible biomedical occlusion devices|

---

EP3294150B1|2015-05-14|2021-12-15|W. L. Gore & Associates, Inc.|Devices for occlusion of an atrial appendage|

---

US10702384B2|2016-08-16|2020-07-07|Boston Scientific Scimed, Inc.|Heart valve regurgitation anchor and delivery tool|

---

CN113215721A|2016-10-14|2021-08-06|因赛普特斯医学有限责任公司|Knitting machine and method of use|

---

WO2018156962A1|2017-02-24|2018-08-30|Inceptus Medical LLC|Vascular occlusion devices and methods|

---

US11173023B2|2017-10-16|2021-11-16|W. L. Gore & Associates, Inc.|Medical devices and anchors therefor|

---

CN109124738B|2018-08-28|2021-02-09|浙江天松医疗器械股份有限公司|Puncture outfit casing pipe and use method of inner pipe and outer pipe thereof|

---

JP2020065810A|2018-10-25|2020-04-30|株式会社東海メディカルプロダクツ|Medical device|

---

CN111643145B|2020-06-28|2021-07-20|哈尔滨工业大学|Left auricle occluder and preparation method thereof|

法律状态:
2018-12-04| B06F| Objections, documents and/or translations needed after an examination request according [chapter 6.6 patent gazette]|

---

2019-11-19| B06U| Preliminary requirement: requests with searches performed by other patent offices: procedure suspended [chapter 6.21 patent gazette]|

---

2020-11-24| B06A| Patent application procedure suspended [chapter 6.1 patent gazette]|

---

2021-03-30| B09A| Decision: intention to grant [chapter 9.1 patent gazette]|

---

2021-06-01| 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 05/11/2012, OBSERVADAS AS CONDICOES LEGAIS. |

优先权:

---

申请号 | 申请日 | 专利标题

---

US13/291.914|2011-11-08|

---

US13/291,914|US9381006B2|2009-06-22|2011-11-08|Sealing device and delivery system|

---

PCT/US2012/063598|WO2013070554A1|2011-11-08|2012-11-05|Sealing device and delivery system|

---