CA2229315C - Medical device having a constricted region for occluding fluid flow in a body lumen - Google Patents
Medical device having a constricted region for occluding fluid flow in a body lumen Download PDFInfo
- Publication number
- CA2229315C CA2229315C CA002229315A CA2229315A CA2229315C CA 2229315 C CA2229315 C CA 2229315C CA 002229315 A CA002229315 A CA 002229315A CA 2229315 A CA2229315 A CA 2229315A CA 2229315 C CA2229315 C CA 2229315C
- Authority
- CA
- Canada
- Prior art keywords
- support structure
- membrane
- fluid flow
- medical device
- tubular
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Fee Related
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/12—Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
- A61B17/12022—Occluding by internal devices, e.g. balloons or releasable wires
- A61B17/12099—Occluding by internal devices, e.g. balloons or releasable wires characterised by the location of the occluder
- A61B17/12109—Occluding by internal devices, e.g. balloons or releasable wires characterised by the location of the occluder in a blood vessel
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/12—Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
- A61B17/12022—Occluding by internal devices, e.g. balloons or releasable wires
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/12—Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
- A61B17/12022—Occluding by internal devices, e.g. balloons or releasable wires
- A61B17/12131—Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device
- A61B17/12168—Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device having a mesh structure
- A61B17/12172—Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device having a mesh structure having a pre-set deployed three-dimensional shape
Abstract
The present invention is an occlusion device (10) adapted for implantation into a fluid flow-supporting body lumen. The occlusion device (10) comprises a flexible support structure (13) and a flexible fluid flow-occluding membrane (20) that is positioned concentric with the flexible support structure (13). The support structure (13) is formed from a plurality of interwoven filaments (16) that form an axially flexible and radially compressible structure that, in its expanded state, engages the lumen. The membrane (20) generally includes a constricted region (24) and constriction means, such as a mechanical seal (28), for closing the membrane (20) at one end. The membrane (20) is formed from a plurality of filaments (26), and in one embodiment, the membrane filaments (26) are tightly interbraided with the structure filaments (16) to form the occlusion device (10). Alternatively, the membrane (20) is separately fabricated of interwoven filaments, and is positioned either within the support structure or without the structure so as to surround the support structure.
Description
PC9544 CA 0222931~ 1998-02-10 MEDICAL DEVICE HAVING A CONSTRICTED REGION FOR
OCCLUDING FLUID FLOW IN A BODY LUMEN
BACKGROUND OF THE INVENTION
Field of the Invention S The present invention relates generally to implantable, radially expandable medical devices for occluding fluid flow in a body lumen. In particular, the present invention is an occlusion device having an interwoven support structure and fluid flow-occluding membrane.
Description of the Related Art Medical devices adapted for implantation in body lumens that support fluid flow are well known and commercially available. One such device is the self-expandable stent of the type disclosed in the Wallsten U.S.
Patent No. 4,655,771, which is expressly incorporated herein by reference in its entirety. Self-expanding stents can be used to treat vascular stenosis and to maintain openings in the urinary, biliary, esophageal, tracheal and bronchial tracts of a patient. Self-expanding stents of the type shown in the Wallsten patent are formed from a number of resilient filaments that are helically wound and interwoven to form a porous lattice. The stents assume a substantially tubular form in their unloaded or expanded state when they are not subjected to external forces. When subjected to inwardly-directed radial forces, the stents are forced into a reduced-radius and extended length form, known as the loaded or colllpressed state. A delivery device, such as a catheter, that retains the stent in its compressed state is used to deliver the stent to a treatment site through a lumen in a patient's body. After the stent is positioned at the treatment site, the delivery device is actuated to release the stent, thereby allowing the stent to self-expand and engage the body lumen. The delivery device is then detached from the stent and removed from the body.
CA 0222931~ 1998-02-10 Another type of' implantable device is a vena cava filter.
Vena cava filters are implanted in the vena cava that lead to a patient's heart in order to trap emboli in the fluid flow that would otherwise be carried into the heart and lungs. Vena cava filters can include a structure similar to the self-expanding stents described above, but act as a filter that traps large particles and emboli in the flow while allowing the remaining fluid flow to pass through the device.
It is sometimes desirable, however, to completely occlude a body lumen or stop fluid flow to a lumen that has been bypassed. By way of example, occlusion can be used to control internal bleeding, bypass a lumen, relieve the pressure created by an aneurysm in a lumen, or stop the flow of fluid to a tumor in a lumen. Because of their generally porous nature and substantially tubular expanded form, self-expanding stents are typically not used to occlude a fluid flow within a body lumen. Similarly, vena cava filters are specifically designed to filter and trap only emboli while allowing the remaining fluid flow in a lumen to pass through the filter, and thus are not typically used to occlude a lumen.
Implantable medical devices have been designed, however, to occlude fluid flow in a body lumen. One such device is a balloon that is carried to a treatment site by a catheter or other similar instrument. When positioned at the treatment site~ the balloon is filled with a fluid, such as a polymerized resin, thereby occluding the fluid flow in the body lumen.
Another type of implantable occlusion device is a wire coil that is first linearly stretched and then positioned at a treatment site in the body lumen. Devices of this type are generally disclosed in the Ritchart et al. U.S. Patent 4,994,069 and the Phelps et al. U.S. Patent 5,522,822. The coil is delivered to a treatment site by a catheter. Upon being released from the catheter the coil assumes a randomly shaped mass that substantially fills CA 0222931~ 1998-02-10 the lumen. The coil can also be coated with fibers or a braided fibrous element to promote clotting of the fluid flow at the treatment site.
A continuing need exists, however, for implantable medical devices that will effectively occlude fluid flow in a body lumen. Occlusion devices exhibiting a relatively high degree of biocompatibility, that are efficient to manufacture, and that can be deployed using known techniques would be especially desirable.
SUMMARY OF THE INVENTION
The present invention is an improved medical device adapted for implantation into a body lumen. The device includes a support structure and a flexible fluid flow-occluding member. In one embodiment, the flexible fluid-flow occluding member is an interwoven membrane. At least a portion of the support structure is expandable from a reduced-diameter compressed state to a self-supporting and lumen-engaging expanded state.
The flexible fluid flow-occluding membrane has at least a first tubular end that is concentrically oriented culd circumferentially engaged with the support structure, and a constricted region. At least a portion of the membrane is expandable with the support structure from a reduced-diameter compressed state to an expanded state for occluding fluid flow through the body lumen when the support structure is in the lumen-engaging expanded state.
In a second embodiment, the support structure includes a plurality of elongate structural filaments that are interwoven. The support structure is radially self-expandable from a reduced-diameter colllpressed state to a self-supporting and lumen-engaging expanded state. The flexible fluid flow-occluding membrane includes polymeric filaments that are interbraided with the structural filaments. The membrane has a first tubular end that is co-extensive with at least a portion of the length of the support CA 0222931~ 1998-02-10 structure and a constricted region. The membrane is expandable with the support structure from a reduced-diameter compressed state to an expanded state for occluding fluid flow through the body lumen when the support structure is in the lumen-eng~gin,Q expanded state.
In a third embodiment of the present invention, the support structure includes a plurality of elongate structural filaments that are interwoven. The support structure is radially self-expandable from a reduced-diameter compressed state to a self-supporting and lumen-eng~ing expanded state. The flexible fluid flow-occluding membrane includes polymeric filaments that are interbraided with the structural filaments. The membrane has a first tubular end that is co-extensive with at least a portion of the length of the support structure and a constricted region. The membrane is expandable with the support structure from a reduced-diameter compressed state to an expanded state for occluding fluid flow through the body lumen when the support structure is in the lumen-engaging expanded state. The constricted region of the membrane extends from the tubular end beyond the end of the support structure.
In a fourth embodiment of the present invention, the medical device includes a radially self-expandable support structure, a flexible fluid flow-occluding membrane, and constriction means for constricting a portion of the support structure and the membrane for occluding fluid flow through the body lumen. The support structure has first and second opposite ends and includes a plurality of elongate structural filaments that are interwoven.
The support structure is expandable from a reduced-diameter compressed state to a self-supporting and lumen-eng~gin~ expanded state. The flexible fluid-flow occluding membrane includes polymeric filaments that are interwoven with the structural filaments. The membrane is coextensive with at least a portion of the length of the support structure.
CA 0222931~ 1998-02-10 In a fifth embodiment of the present invention, the medical device is comprised of a radially self-expandable support structure and a flexible fluid flow-occluding membrane. The support structure includes a plurality of elongated structural filaments that are interwoven. The support structure is expandable from a reduced-diameter compressed state to a self-supporting and lumen-engaging expanded state. The flexible fluid flow-occluding membrane has at least a first tubular end that is concentrically oriented and circumferentially engaged with the support structure and a constricted region. The membrane is expandable with the support structure from a reduced diameter compressed state to an expanded state for occluding fluid flow through the body lumen when the support structure is in the lumen-eng~ging expanded state.
BR~EF DESCRIPTION OF THE DR~WINGS
Figure 1 is a side view of an interbraided occlusion device in accordance with the present invention in its expanded state and implanted in a body lumen.
Figure 2 is a side view of the occlusion device shown in Figure 1 in its compressed state.
Figure 3 is a side view of a second embodiment of an interbraided occlusion device in accordance with the present invention.
Figure 4 is a side view of a third embodiment of an interbraided occlusion device in accordance with the present invention.
Figure 5 is a detailed side view of a portion of an interbraided occlusion device showing the interbraided filaments of the device.
Figures 6-8 schematically illustrate a process for manufacturing the interbraided occlusion devices shown in Figures 1-5.
CA 0222931~ 1998-02-10 Figure 9 is a side view of a sheath occlusion device in accordance with the present invention.
Figure 10 is a side view of the sheath occlusion device shown in Figure 9 with portions removed to show the membrane surrounding the support structure of the device.
Figure 11 is a side view of a second embodiment of a sheath occlusion device in accordance with the present invention.
Figure 12 is a side view of a third embodiment of a sheath occlusion device in accordance with the present invention.
Figure 13 is a side view of a fourth embodiment of a sheath occlusion device in accordance with the present invention.
Figure 14 is a detailed side view of a portion of the occlusion device shown in Figures 1 and 2 having a fusion seal.
Figure 15 is a detailed side view of a portion of the occlusion device shown in Figures 1 and 2 having a suture.
DETAILED DESCNPTION OF THE PREFERRED
EMBODIMENTS
A first embodiment of an occlusion device 10 in accordance with the present invention is shown in Figures 1 and 2. Occlusion device 10 is substantially tubular, axially flexible, and radially compressible over at least a portion of the device, and is adapted to be implanted in a body lumen 6 that can support a fluid flow 8. As shown in Figure 2, occlusion device 10 can be compressed in part or over the entire length of the device to a reduced-diameter state by subjecting the device to radially directed forces.
CA 0222931~ 1998-02-10 When the entire length of occlusion device 10 is in this compressed state, the device can be inserted into body lumen 6 using conventional techniques and tools such as an insertion catheter (not shown). When released from the insertion catheter, the radial forces are removed from occlusion device 10, and it expands to the enlarged-diameter state shown in Figure 1. When in this expanded state, occlusion device 10 engages body lumen 6, thereby anchoring the device in the lumen.
Occlusion device 10 is shown having an upstream end 11 that is open to accept fluid flow 8 into the device and a downstream end 12 that is closed to occlude the flow. Those skilled in the art, however, will recognize that occlusion device 10 can be reversed in fluid flow 8 so that the closed end of the device is the upstream end 11 while the open end of the device is the downstream end 12.
Occlusion device 10 is generally comprised of a support structure 13 and a fluid flow-occluding membrane 20. In the embodiment shown, support structure 13 is substantially tubular, axially flexible, and radially compressible over at least a portion of the structure, and has a first tubular end 14. Support structure 13 can be comprised of two sets of oppositely-directed elongate filaments 16 that are helically wound and interwoven to form a support structure 13 that is self-expandable. The sets of filaments 16 are interwoven in an over and under configuration, and intersect to form an open mesh construction. The first set of filaments 16 have a common direction of winding, are parallel and axially displaced relative to each other, and cross a second set of filaments 16 that are also parallel and axially displaced relative to each other, but have an opposite direction of winding.
Figure 6 shows a method for manufacturing a support structure 13 wherein two structural filaments 32a and 32b, one from each ' . CA 0222931~ 1998-02-10 set of oppositely directed filaments, are wound about a mandrel 60 and supported by respective bobbins 62 and 64. While just filaments 32a and 32b are illustrated as a matter of convenience, it is to be appreciated that allof the structural filaments are wound about the mandrel and maintained S together for shaping. The filaments are age-hardened within a furnace 66 in a vacuum or a protective atmosphere. Temperatures in furnace 66 range between about 350-1000~ C., with the specific temperature depending upon the material used for the structural filaments. Filaments 32a and 32b overlie one another to form multiple intersections, one of which is indicated at 68.
Bobbins, including 62 and 64, are set to tension their respective filaments during age-hardening. The appropriate duration for age-hardening varies with materials and dimensions, but can range from as brief as 30 seconds, to about S hours.
After age-hardening, the structural filaments are allowed to cool, whereupon each filament retains the helical shape as its nominal shape. In the context of elastic materials, "nominal shape" refers to the shape in a relaxed state, i.e. when under no external stress. The age-hardened filaments are highly resilient, i.e. deformable under external stress, but elastically return to the nominal shape when free of the external stress.
In this manner, support structure 13 can be radially compressed into a reduced-radius, extended-length configuration suitable for delivery to a treatment site in body lumen 6. When released from this compressed state, support structure 13 will self-expand, thereby c~ucin~ occlusion device 10 to engage body lumen 6.
Fluid flow-occluding membrane 20 has a first tubular end 22 that is concentrically oriented and circumferentially engages support structure 13. Membrane 20 further includes at least one constricted region 24 that operates to occlude fluid flow 8 in lumen 6, and membrane 20 is CA 0222931~ 1998-02-10 expandable along with support structure 13 from the compressed state to the expanded state of the occlusion device 10. Membrane 20 can be closed at constricted region 24 by any of a number of constriction techniques, such as mechanical seal 28, in order to occlude fluid flow. Those skilled in the art will recognize that other constriction techniques, such as a sealing member, a fusion seal 28, or a suture 28', can also be used.
In the embodiment shown in Figures 1 and 2, membrane 20 includes a plurality of polymeric filaments 26 that, as shown in greater detail in Figure 5, are interbraided with support structure filaments 16 in forming occlusion device 10. Figures 7 and 8 schematically illustrate a method for interbraiding membrane filaments with structural filaments. Figure 7 shows a braiding apparatus 70 including a cylindrical carrier assembly 72 including several annular arrays of bobbins, two of the bobbins being indicated at 80a and 80b. The apparatus further includes a mandrel 78, centered within the cylindrical assembly and movable longitudinally relative to the assembly as indicated by the arrow.
Figure 8 illustrates part of a carrier assembly 72 in greater detail, to reveal five annular arrays or sets of carrier bobbins indicated at 80, 82, 84, 86, and 88. The sets are coaxial and axially spaced apart, each including forty-eight bobbins, twenty-four bobbins for respective clockwise and counterclockwise windings about mandrel 78. While those skilled in the art are acquainted with the use of braiding machinery, it is emph~.~i7ed here that braiding apparatus 70 is configured as described in detail in the commonly assigned P. Thompson U.S. Patent Applications, Serial Nos.
08/640,091 and 08/640,062 entitled "Three-Dimensional Braided Covered Stent" and entitled "Braided Composite Prosthesis," both of which are expressly incorporated herein by reference in their entirety. Suitable CA 0222931~ 1998-02-10 braiding machinery is available from Albany International Research Company of Mansfield, Massachusetts.
Support structure filaments 16 and membrane filaments 26 can be tightly interwoven so that membrane 20 is generally non-porous in order to occlude fluid flow. Membrane filaments 26 can also be formed from a thrombogenic material in order to promote clotting of fluid flow 8 and thereby occlude the fluid flow. The resulting structure will preferably have a porosity of less than 5,000 ml/cm21min at 120 mmHg. More preferred are porosities of between about 100 and 3,000 ml/cm21min, and even more preferably, between about 300 and 2,000 mllcm21min at 120 mmHg.
In the interbraided occlusion device 10 shown in Figures 1 and 2, first tubular end 14 of support structure 12 extends beyond first tubular end 22 of membrane 20, and the constricted region 24 of membrane 20 extends beyond a second tubular end 15 of support structure 13. The individual membrane fibers 26 of membrane 20 are drawn together in the constricted region 24 and sealed together with mechanical seal 28.
Figure 3 shows a second embodiment of an interbraided occlusion device 110 in its expanded state. Features of occlusion device 110 that correspond to features of occlusion device 10 shown in Figures 1 and 2 and described above are designated with corresponding reference numbers that are preceded by the prefix "1." In this embodiment, support structure filaments 116 and membrane filaments 126 are inle~ aided throughout the entire length of occlusion device 110. Mechanical seal 128 compresses both support structure 113 and membrane 120 at the constricted region 124, thereby closing occlusion device 110 and occluding fluid flow through the device.
CA 0222931~ 1998-02-10 Figure 4 shows a third embodiment of an interbraided occlusion device 210 in its expanded state. Features of occlusion device 210 that correspond to features of occlusion device 10 shown in Figures 1 and 2 and described above are designated with corresponding reference numbers that are preceded by the prefix "2." Support structure 213 includes first and second tubular ends 214 and 215, respectively, and fluid flow-occluding membrane 220 includes first and second tubular ends 222 and 223, respectively. In this embodiment, support structure filaments 216 and membrane filaments 226 are interbraided throughout the entire length of occlusion device 210, and the respective first and second ends of structure 213 and membrane 220 are thus concentric and substantially coextensive.
Mechanical seal 228 is positioned between the first and second tubular ends of the occlusion device 210, and constricts both the support structure 213 and the membrane 220 in order to occlude fluid flow in a body lumen.
Support structure 213 and membrane 220 radially expand in the areas adjacent mechanical seal 228 to form first and second constricted regions 224 and 225.
Figures 9 and 10 show a sheath occlusion device 310 in accordance with the present invention. Sheath occlusion device 310 is comprised of support structure 313 and a separately fabricated fluid flow-occluding membrane 320. Support structure 313 can be comprised of a plurality of interbraided elongate filaments 316, and can be m~nllf~ctured using the method for manufacturing support structure 13 described above and shown in Figure 6. Membrane 320 circumferentially engages support structure 313, and in the embodiment shown in Figure 9, membrane 320 is positioned within support structure 313. In this manner, support structure 313 acts as a "sheath" that covers membrane 320. Alternatively, as in the embodiment shown in Figure 10, membrane 320 can encompass support structure 313, thereby acting as a sheath that covers structure 313.
CA 0222931~ 1998-02-10 Membrane 320 can be formed from a plurality of filaments 326 that are either tightly interwoven to occlude fluid flow, or are thrombogenic in order to promote clotting of the fluid flow, and thereby occlude the flow. Alternatively, membrane 320 can be formed from a sheet of flexible material that is substantially non-porous, is thrombogenic, or is covered with a non-porous coating in order to occlude fluid flow.
The sheath occlusion device 310 shown in Figures 9 and 10 includes a first tubular end 314 of support structure 313 and a first tubular end 322 of membrane 320 that are concentric and substantially coextensive, and support structure 313 extends the entire length of membrane 320.
Membrane 320 and support stmcture 313 of occlusion device 310 are separately fabricated, and membrane 320 engages stnucture 313 using conventional techniques, such as adhesive or thread stitching. Mechanical seal 328 closes the support structure 313 and membrane 320 at the constricted region 324, thereby occluding fluid flow.
Figure 11 shows a second embodiment of a sheath occlusion device 410 in accordance with the present invention. Features of occlusion device 410 that correspond to features of occlusion device 310 shown in Figures 9 and 10 and described above are designated with "400" series reference numbers as opposed to the "300" series used in Figures 9 and 10.
Sheath occlusion device 410 includes a support stnucture 413 and membrane 420 that are separately fabricated, and a first tubular end 414 of support structure 413 extends beyond a first tubular end 422 of membrane 420. Support structure 413 thus acts as a sheath that surrounds a portion of membrane 420. A constricted region 424 of membrane 420 extends beyond a second tubular end 415 of support structure 413, and is closed at constricted region 424 with mechanical seal 428.
- CA 0222931~ 1998-02-10 Figure 12 shows a third embodiment of a sheath occlusion device 510. Features of occlusion device 510 that correspond to features of occlusion device 310 shown in Figures 9 and 10 and described above are designated with "500" series reference numbers as opposed to the "300"
series used in Figures 9 and 10. Sheath occlusion device 510 includes a support structure 513 and membrane 520 that are separately fabricated.
First tubular ends 514 and 522 of support structure 513 and membrane 520, respectively, are concentric and substantially coextensive, as are second tubular ends 515 and 523 of the structure and the membrane. Mechanical seal 528 is positioned between the first and second ends of the device, and engages both support structure 513 and membrane 520 at the conskicted region 524. Due to the self-expanding nature of support structure 513, the areas adjacent mechanical seal 528 expand, thereby creating a second constricted region 525. While occlusion device 510 is shown with membrane 520 positioned within support structure 513, those skilled in the art will recognize that membrane 520 can alternatively surround support structure 513 without departing from the spirit and scope of the invention.
Figure 13 shows a fourth embodiment of a sheath occlusion device 610. Features of occlusion device 610 that correspond to features of occlusion device 310 shown in Figures 9 and 10 and described above are designated with "600" series reference numbers as opposed to the "300"
series used in Figures 9 and 10 A separately fabricated membrane 620 is positioned within and engages support structure 613. In this embodiment, mechanical seal 628 is also positioned within support structure 613, and thus closes only membrane 620 at the constricted region 624. Because membrane 620 engages support structure 613, membrane 620 expands in the areas adjacent mechanical seal 628, thereby creating a second constricted region 625.
CA 0222931~ 1998-02-10 The elongate filaments of the support structures described above can be formed from a metal or other resilient material, including Elgiloy~ alloy (available from Carpenter Technology Corporation of Reading, Pennsylvania), Phynox~ alloy (available from Metal Imphy of Imphy, France), 316 stainless steel and MP35N alloy (both of which are available from Carpenter Technology Corporation and Latrobe Steel Company of Latrobe, Pennsylvania), and superelastic Nitinol nickel-titanium alloy (available from Shape Memory Applications of Santa Clara, California).
The fluid flow-occluding membranes of the present invention described above generally have a high degree of compliance, which may or may not include elasticity. These membranes can be formed from a plurality of filaments that are either tightly woven to occlude fluid flow, or are thrombogenic to promote clotting of the fluid flow, and thereby occlude the flow. Suitable materials for the plurality of filaments include polyethylene and polyethylene terephthalate. One suitable high molecular weight polyethylene that can be used for the filaments is sold under the brand name "Spectra". Alternatively, these membranes can be formed from a sheet of flexible material that is non-porous, is thrombogenic, or is covered with a non-porous coating to occlude fluid flow. Suitable materials for a sheet of flexible material used to form the membranes include silicone, polyurethane, polycarbonate urethane, polytetrafluoroethylene, or expanded polytetrafluoroethylene.
The occlusion device described above has many advantages.
The device exhibits a relatively high degree of biocompatibility. The support structure securely engages the device in a body lumen while the membrane effectively occludes fluid flow in the lumen. In addition, the occlusion device can be deployed using conventional insertion techniques CA 0222931~ 1998-02-10 and tools, such as an insertion catheter. The present invention is also efficient to manufacture.
Although the present invention has been described with reference to preferred embodiments, those skilled in the art will recognize that changes can be made in form and detail without departing from the spirit and scope of the invention.
OCCLUDING FLUID FLOW IN A BODY LUMEN
BACKGROUND OF THE INVENTION
Field of the Invention S The present invention relates generally to implantable, radially expandable medical devices for occluding fluid flow in a body lumen. In particular, the present invention is an occlusion device having an interwoven support structure and fluid flow-occluding membrane.
Description of the Related Art Medical devices adapted for implantation in body lumens that support fluid flow are well known and commercially available. One such device is the self-expandable stent of the type disclosed in the Wallsten U.S.
Patent No. 4,655,771, which is expressly incorporated herein by reference in its entirety. Self-expanding stents can be used to treat vascular stenosis and to maintain openings in the urinary, biliary, esophageal, tracheal and bronchial tracts of a patient. Self-expanding stents of the type shown in the Wallsten patent are formed from a number of resilient filaments that are helically wound and interwoven to form a porous lattice. The stents assume a substantially tubular form in their unloaded or expanded state when they are not subjected to external forces. When subjected to inwardly-directed radial forces, the stents are forced into a reduced-radius and extended length form, known as the loaded or colllpressed state. A delivery device, such as a catheter, that retains the stent in its compressed state is used to deliver the stent to a treatment site through a lumen in a patient's body. After the stent is positioned at the treatment site, the delivery device is actuated to release the stent, thereby allowing the stent to self-expand and engage the body lumen. The delivery device is then detached from the stent and removed from the body.
CA 0222931~ 1998-02-10 Another type of' implantable device is a vena cava filter.
Vena cava filters are implanted in the vena cava that lead to a patient's heart in order to trap emboli in the fluid flow that would otherwise be carried into the heart and lungs. Vena cava filters can include a structure similar to the self-expanding stents described above, but act as a filter that traps large particles and emboli in the flow while allowing the remaining fluid flow to pass through the device.
It is sometimes desirable, however, to completely occlude a body lumen or stop fluid flow to a lumen that has been bypassed. By way of example, occlusion can be used to control internal bleeding, bypass a lumen, relieve the pressure created by an aneurysm in a lumen, or stop the flow of fluid to a tumor in a lumen. Because of their generally porous nature and substantially tubular expanded form, self-expanding stents are typically not used to occlude a fluid flow within a body lumen. Similarly, vena cava filters are specifically designed to filter and trap only emboli while allowing the remaining fluid flow in a lumen to pass through the filter, and thus are not typically used to occlude a lumen.
Implantable medical devices have been designed, however, to occlude fluid flow in a body lumen. One such device is a balloon that is carried to a treatment site by a catheter or other similar instrument. When positioned at the treatment site~ the balloon is filled with a fluid, such as a polymerized resin, thereby occluding the fluid flow in the body lumen.
Another type of implantable occlusion device is a wire coil that is first linearly stretched and then positioned at a treatment site in the body lumen. Devices of this type are generally disclosed in the Ritchart et al. U.S. Patent 4,994,069 and the Phelps et al. U.S. Patent 5,522,822. The coil is delivered to a treatment site by a catheter. Upon being released from the catheter the coil assumes a randomly shaped mass that substantially fills CA 0222931~ 1998-02-10 the lumen. The coil can also be coated with fibers or a braided fibrous element to promote clotting of the fluid flow at the treatment site.
A continuing need exists, however, for implantable medical devices that will effectively occlude fluid flow in a body lumen. Occlusion devices exhibiting a relatively high degree of biocompatibility, that are efficient to manufacture, and that can be deployed using known techniques would be especially desirable.
SUMMARY OF THE INVENTION
The present invention is an improved medical device adapted for implantation into a body lumen. The device includes a support structure and a flexible fluid flow-occluding member. In one embodiment, the flexible fluid-flow occluding member is an interwoven membrane. At least a portion of the support structure is expandable from a reduced-diameter compressed state to a self-supporting and lumen-engaging expanded state.
The flexible fluid flow-occluding membrane has at least a first tubular end that is concentrically oriented culd circumferentially engaged with the support structure, and a constricted region. At least a portion of the membrane is expandable with the support structure from a reduced-diameter compressed state to an expanded state for occluding fluid flow through the body lumen when the support structure is in the lumen-engaging expanded state.
In a second embodiment, the support structure includes a plurality of elongate structural filaments that are interwoven. The support structure is radially self-expandable from a reduced-diameter colllpressed state to a self-supporting and lumen-engaging expanded state. The flexible fluid flow-occluding membrane includes polymeric filaments that are interbraided with the structural filaments. The membrane has a first tubular end that is co-extensive with at least a portion of the length of the support CA 0222931~ 1998-02-10 structure and a constricted region. The membrane is expandable with the support structure from a reduced-diameter compressed state to an expanded state for occluding fluid flow through the body lumen when the support structure is in the lumen-eng~gin,Q expanded state.
In a third embodiment of the present invention, the support structure includes a plurality of elongate structural filaments that are interwoven. The support structure is radially self-expandable from a reduced-diameter compressed state to a self-supporting and lumen-eng~ing expanded state. The flexible fluid flow-occluding membrane includes polymeric filaments that are interbraided with the structural filaments. The membrane has a first tubular end that is co-extensive with at least a portion of the length of the support structure and a constricted region. The membrane is expandable with the support structure from a reduced-diameter compressed state to an expanded state for occluding fluid flow through the body lumen when the support structure is in the lumen-engaging expanded state. The constricted region of the membrane extends from the tubular end beyond the end of the support structure.
In a fourth embodiment of the present invention, the medical device includes a radially self-expandable support structure, a flexible fluid flow-occluding membrane, and constriction means for constricting a portion of the support structure and the membrane for occluding fluid flow through the body lumen. The support structure has first and second opposite ends and includes a plurality of elongate structural filaments that are interwoven.
The support structure is expandable from a reduced-diameter compressed state to a self-supporting and lumen-eng~gin~ expanded state. The flexible fluid-flow occluding membrane includes polymeric filaments that are interwoven with the structural filaments. The membrane is coextensive with at least a portion of the length of the support structure.
CA 0222931~ 1998-02-10 In a fifth embodiment of the present invention, the medical device is comprised of a radially self-expandable support structure and a flexible fluid flow-occluding membrane. The support structure includes a plurality of elongated structural filaments that are interwoven. The support structure is expandable from a reduced-diameter compressed state to a self-supporting and lumen-engaging expanded state. The flexible fluid flow-occluding membrane has at least a first tubular end that is concentrically oriented and circumferentially engaged with the support structure and a constricted region. The membrane is expandable with the support structure from a reduced diameter compressed state to an expanded state for occluding fluid flow through the body lumen when the support structure is in the lumen-eng~ging expanded state.
BR~EF DESCRIPTION OF THE DR~WINGS
Figure 1 is a side view of an interbraided occlusion device in accordance with the present invention in its expanded state and implanted in a body lumen.
Figure 2 is a side view of the occlusion device shown in Figure 1 in its compressed state.
Figure 3 is a side view of a second embodiment of an interbraided occlusion device in accordance with the present invention.
Figure 4 is a side view of a third embodiment of an interbraided occlusion device in accordance with the present invention.
Figure 5 is a detailed side view of a portion of an interbraided occlusion device showing the interbraided filaments of the device.
Figures 6-8 schematically illustrate a process for manufacturing the interbraided occlusion devices shown in Figures 1-5.
CA 0222931~ 1998-02-10 Figure 9 is a side view of a sheath occlusion device in accordance with the present invention.
Figure 10 is a side view of the sheath occlusion device shown in Figure 9 with portions removed to show the membrane surrounding the support structure of the device.
Figure 11 is a side view of a second embodiment of a sheath occlusion device in accordance with the present invention.
Figure 12 is a side view of a third embodiment of a sheath occlusion device in accordance with the present invention.
Figure 13 is a side view of a fourth embodiment of a sheath occlusion device in accordance with the present invention.
Figure 14 is a detailed side view of a portion of the occlusion device shown in Figures 1 and 2 having a fusion seal.
Figure 15 is a detailed side view of a portion of the occlusion device shown in Figures 1 and 2 having a suture.
DETAILED DESCNPTION OF THE PREFERRED
EMBODIMENTS
A first embodiment of an occlusion device 10 in accordance with the present invention is shown in Figures 1 and 2. Occlusion device 10 is substantially tubular, axially flexible, and radially compressible over at least a portion of the device, and is adapted to be implanted in a body lumen 6 that can support a fluid flow 8. As shown in Figure 2, occlusion device 10 can be compressed in part or over the entire length of the device to a reduced-diameter state by subjecting the device to radially directed forces.
CA 0222931~ 1998-02-10 When the entire length of occlusion device 10 is in this compressed state, the device can be inserted into body lumen 6 using conventional techniques and tools such as an insertion catheter (not shown). When released from the insertion catheter, the radial forces are removed from occlusion device 10, and it expands to the enlarged-diameter state shown in Figure 1. When in this expanded state, occlusion device 10 engages body lumen 6, thereby anchoring the device in the lumen.
Occlusion device 10 is shown having an upstream end 11 that is open to accept fluid flow 8 into the device and a downstream end 12 that is closed to occlude the flow. Those skilled in the art, however, will recognize that occlusion device 10 can be reversed in fluid flow 8 so that the closed end of the device is the upstream end 11 while the open end of the device is the downstream end 12.
Occlusion device 10 is generally comprised of a support structure 13 and a fluid flow-occluding membrane 20. In the embodiment shown, support structure 13 is substantially tubular, axially flexible, and radially compressible over at least a portion of the structure, and has a first tubular end 14. Support structure 13 can be comprised of two sets of oppositely-directed elongate filaments 16 that are helically wound and interwoven to form a support structure 13 that is self-expandable. The sets of filaments 16 are interwoven in an over and under configuration, and intersect to form an open mesh construction. The first set of filaments 16 have a common direction of winding, are parallel and axially displaced relative to each other, and cross a second set of filaments 16 that are also parallel and axially displaced relative to each other, but have an opposite direction of winding.
Figure 6 shows a method for manufacturing a support structure 13 wherein two structural filaments 32a and 32b, one from each ' . CA 0222931~ 1998-02-10 set of oppositely directed filaments, are wound about a mandrel 60 and supported by respective bobbins 62 and 64. While just filaments 32a and 32b are illustrated as a matter of convenience, it is to be appreciated that allof the structural filaments are wound about the mandrel and maintained S together for shaping. The filaments are age-hardened within a furnace 66 in a vacuum or a protective atmosphere. Temperatures in furnace 66 range between about 350-1000~ C., with the specific temperature depending upon the material used for the structural filaments. Filaments 32a and 32b overlie one another to form multiple intersections, one of which is indicated at 68.
Bobbins, including 62 and 64, are set to tension their respective filaments during age-hardening. The appropriate duration for age-hardening varies with materials and dimensions, but can range from as brief as 30 seconds, to about S hours.
After age-hardening, the structural filaments are allowed to cool, whereupon each filament retains the helical shape as its nominal shape. In the context of elastic materials, "nominal shape" refers to the shape in a relaxed state, i.e. when under no external stress. The age-hardened filaments are highly resilient, i.e. deformable under external stress, but elastically return to the nominal shape when free of the external stress.
In this manner, support structure 13 can be radially compressed into a reduced-radius, extended-length configuration suitable for delivery to a treatment site in body lumen 6. When released from this compressed state, support structure 13 will self-expand, thereby c~ucin~ occlusion device 10 to engage body lumen 6.
Fluid flow-occluding membrane 20 has a first tubular end 22 that is concentrically oriented and circumferentially engages support structure 13. Membrane 20 further includes at least one constricted region 24 that operates to occlude fluid flow 8 in lumen 6, and membrane 20 is CA 0222931~ 1998-02-10 expandable along with support structure 13 from the compressed state to the expanded state of the occlusion device 10. Membrane 20 can be closed at constricted region 24 by any of a number of constriction techniques, such as mechanical seal 28, in order to occlude fluid flow. Those skilled in the art will recognize that other constriction techniques, such as a sealing member, a fusion seal 28, or a suture 28', can also be used.
In the embodiment shown in Figures 1 and 2, membrane 20 includes a plurality of polymeric filaments 26 that, as shown in greater detail in Figure 5, are interbraided with support structure filaments 16 in forming occlusion device 10. Figures 7 and 8 schematically illustrate a method for interbraiding membrane filaments with structural filaments. Figure 7 shows a braiding apparatus 70 including a cylindrical carrier assembly 72 including several annular arrays of bobbins, two of the bobbins being indicated at 80a and 80b. The apparatus further includes a mandrel 78, centered within the cylindrical assembly and movable longitudinally relative to the assembly as indicated by the arrow.
Figure 8 illustrates part of a carrier assembly 72 in greater detail, to reveal five annular arrays or sets of carrier bobbins indicated at 80, 82, 84, 86, and 88. The sets are coaxial and axially spaced apart, each including forty-eight bobbins, twenty-four bobbins for respective clockwise and counterclockwise windings about mandrel 78. While those skilled in the art are acquainted with the use of braiding machinery, it is emph~.~i7ed here that braiding apparatus 70 is configured as described in detail in the commonly assigned P. Thompson U.S. Patent Applications, Serial Nos.
08/640,091 and 08/640,062 entitled "Three-Dimensional Braided Covered Stent" and entitled "Braided Composite Prosthesis," both of which are expressly incorporated herein by reference in their entirety. Suitable CA 0222931~ 1998-02-10 braiding machinery is available from Albany International Research Company of Mansfield, Massachusetts.
Support structure filaments 16 and membrane filaments 26 can be tightly interwoven so that membrane 20 is generally non-porous in order to occlude fluid flow. Membrane filaments 26 can also be formed from a thrombogenic material in order to promote clotting of fluid flow 8 and thereby occlude the fluid flow. The resulting structure will preferably have a porosity of less than 5,000 ml/cm21min at 120 mmHg. More preferred are porosities of between about 100 and 3,000 ml/cm21min, and even more preferably, between about 300 and 2,000 mllcm21min at 120 mmHg.
In the interbraided occlusion device 10 shown in Figures 1 and 2, first tubular end 14 of support structure 12 extends beyond first tubular end 22 of membrane 20, and the constricted region 24 of membrane 20 extends beyond a second tubular end 15 of support structure 13. The individual membrane fibers 26 of membrane 20 are drawn together in the constricted region 24 and sealed together with mechanical seal 28.
Figure 3 shows a second embodiment of an interbraided occlusion device 110 in its expanded state. Features of occlusion device 110 that correspond to features of occlusion device 10 shown in Figures 1 and 2 and described above are designated with corresponding reference numbers that are preceded by the prefix "1." In this embodiment, support structure filaments 116 and membrane filaments 126 are inle~ aided throughout the entire length of occlusion device 110. Mechanical seal 128 compresses both support structure 113 and membrane 120 at the constricted region 124, thereby closing occlusion device 110 and occluding fluid flow through the device.
CA 0222931~ 1998-02-10 Figure 4 shows a third embodiment of an interbraided occlusion device 210 in its expanded state. Features of occlusion device 210 that correspond to features of occlusion device 10 shown in Figures 1 and 2 and described above are designated with corresponding reference numbers that are preceded by the prefix "2." Support structure 213 includes first and second tubular ends 214 and 215, respectively, and fluid flow-occluding membrane 220 includes first and second tubular ends 222 and 223, respectively. In this embodiment, support structure filaments 216 and membrane filaments 226 are interbraided throughout the entire length of occlusion device 210, and the respective first and second ends of structure 213 and membrane 220 are thus concentric and substantially coextensive.
Mechanical seal 228 is positioned between the first and second tubular ends of the occlusion device 210, and constricts both the support structure 213 and the membrane 220 in order to occlude fluid flow in a body lumen.
Support structure 213 and membrane 220 radially expand in the areas adjacent mechanical seal 228 to form first and second constricted regions 224 and 225.
Figures 9 and 10 show a sheath occlusion device 310 in accordance with the present invention. Sheath occlusion device 310 is comprised of support structure 313 and a separately fabricated fluid flow-occluding membrane 320. Support structure 313 can be comprised of a plurality of interbraided elongate filaments 316, and can be m~nllf~ctured using the method for manufacturing support structure 13 described above and shown in Figure 6. Membrane 320 circumferentially engages support structure 313, and in the embodiment shown in Figure 9, membrane 320 is positioned within support structure 313. In this manner, support structure 313 acts as a "sheath" that covers membrane 320. Alternatively, as in the embodiment shown in Figure 10, membrane 320 can encompass support structure 313, thereby acting as a sheath that covers structure 313.
CA 0222931~ 1998-02-10 Membrane 320 can be formed from a plurality of filaments 326 that are either tightly interwoven to occlude fluid flow, or are thrombogenic in order to promote clotting of the fluid flow, and thereby occlude the flow. Alternatively, membrane 320 can be formed from a sheet of flexible material that is substantially non-porous, is thrombogenic, or is covered with a non-porous coating in order to occlude fluid flow.
The sheath occlusion device 310 shown in Figures 9 and 10 includes a first tubular end 314 of support structure 313 and a first tubular end 322 of membrane 320 that are concentric and substantially coextensive, and support structure 313 extends the entire length of membrane 320.
Membrane 320 and support stmcture 313 of occlusion device 310 are separately fabricated, and membrane 320 engages stnucture 313 using conventional techniques, such as adhesive or thread stitching. Mechanical seal 328 closes the support structure 313 and membrane 320 at the constricted region 324, thereby occluding fluid flow.
Figure 11 shows a second embodiment of a sheath occlusion device 410 in accordance with the present invention. Features of occlusion device 410 that correspond to features of occlusion device 310 shown in Figures 9 and 10 and described above are designated with "400" series reference numbers as opposed to the "300" series used in Figures 9 and 10.
Sheath occlusion device 410 includes a support stnucture 413 and membrane 420 that are separately fabricated, and a first tubular end 414 of support structure 413 extends beyond a first tubular end 422 of membrane 420. Support structure 413 thus acts as a sheath that surrounds a portion of membrane 420. A constricted region 424 of membrane 420 extends beyond a second tubular end 415 of support structure 413, and is closed at constricted region 424 with mechanical seal 428.
- CA 0222931~ 1998-02-10 Figure 12 shows a third embodiment of a sheath occlusion device 510. Features of occlusion device 510 that correspond to features of occlusion device 310 shown in Figures 9 and 10 and described above are designated with "500" series reference numbers as opposed to the "300"
series used in Figures 9 and 10. Sheath occlusion device 510 includes a support structure 513 and membrane 520 that are separately fabricated.
First tubular ends 514 and 522 of support structure 513 and membrane 520, respectively, are concentric and substantially coextensive, as are second tubular ends 515 and 523 of the structure and the membrane. Mechanical seal 528 is positioned between the first and second ends of the device, and engages both support structure 513 and membrane 520 at the conskicted region 524. Due to the self-expanding nature of support structure 513, the areas adjacent mechanical seal 528 expand, thereby creating a second constricted region 525. While occlusion device 510 is shown with membrane 520 positioned within support structure 513, those skilled in the art will recognize that membrane 520 can alternatively surround support structure 513 without departing from the spirit and scope of the invention.
Figure 13 shows a fourth embodiment of a sheath occlusion device 610. Features of occlusion device 610 that correspond to features of occlusion device 310 shown in Figures 9 and 10 and described above are designated with "600" series reference numbers as opposed to the "300"
series used in Figures 9 and 10 A separately fabricated membrane 620 is positioned within and engages support structure 613. In this embodiment, mechanical seal 628 is also positioned within support structure 613, and thus closes only membrane 620 at the constricted region 624. Because membrane 620 engages support structure 613, membrane 620 expands in the areas adjacent mechanical seal 628, thereby creating a second constricted region 625.
CA 0222931~ 1998-02-10 The elongate filaments of the support structures described above can be formed from a metal or other resilient material, including Elgiloy~ alloy (available from Carpenter Technology Corporation of Reading, Pennsylvania), Phynox~ alloy (available from Metal Imphy of Imphy, France), 316 stainless steel and MP35N alloy (both of which are available from Carpenter Technology Corporation and Latrobe Steel Company of Latrobe, Pennsylvania), and superelastic Nitinol nickel-titanium alloy (available from Shape Memory Applications of Santa Clara, California).
The fluid flow-occluding membranes of the present invention described above generally have a high degree of compliance, which may or may not include elasticity. These membranes can be formed from a plurality of filaments that are either tightly woven to occlude fluid flow, or are thrombogenic to promote clotting of the fluid flow, and thereby occlude the flow. Suitable materials for the plurality of filaments include polyethylene and polyethylene terephthalate. One suitable high molecular weight polyethylene that can be used for the filaments is sold under the brand name "Spectra". Alternatively, these membranes can be formed from a sheet of flexible material that is non-porous, is thrombogenic, or is covered with a non-porous coating to occlude fluid flow. Suitable materials for a sheet of flexible material used to form the membranes include silicone, polyurethane, polycarbonate urethane, polytetrafluoroethylene, or expanded polytetrafluoroethylene.
The occlusion device described above has many advantages.
The device exhibits a relatively high degree of biocompatibility. The support structure securely engages the device in a body lumen while the membrane effectively occludes fluid flow in the lumen. In addition, the occlusion device can be deployed using conventional insertion techniques CA 0222931~ 1998-02-10 and tools, such as an insertion catheter. The present invention is also efficient to manufacture.
Although the present invention has been described with reference to preferred embodiments, those skilled in the art will recognize that changes can be made in form and detail without departing from the spirit and scope of the invention.
Claims (17)
1. A medical device (10) adapted for implantation into a body lumen having a tubular interior surface, including:
a support structure (13) of which at least a tubular portion is expandable from a reduced-diameter compressed state to a self-supporting and lumen-engaging expanded state, the tubular portion for engaging the tubular interior surface of the lumen in the expanded state; and;
a flexible, interwoven fluid flow-occluding membrane (20) having at least a first tubular end (22) concentrically oriented and circumferentially engaged with the tubular portion of the support structure, and a constricted region (24), the membrane having a porosity of greater than 0 ml/cm2/min, and at least a portion of the membrane (20) being expandable with the support structure (13) from a reduced-diameter compressed state to an expanded state for occluding fluid flow through the body lumen when the support structure (13) is in the lumen-engaging expanded state.
a support structure (13) of which at least a tubular portion is expandable from a reduced-diameter compressed state to a self-supporting and lumen-engaging expanded state, the tubular portion for engaging the tubular interior surface of the lumen in the expanded state; and;
a flexible, interwoven fluid flow-occluding membrane (20) having at least a first tubular end (22) concentrically oriented and circumferentially engaged with the tubular portion of the support structure, and a constricted region (24), the membrane having a porosity of greater than 0 ml/cm2/min, and at least a portion of the membrane (20) being expandable with the support structure (13) from a reduced-diameter compressed state to an expanded state for occluding fluid flow through the body lumen when the support structure (13) is in the lumen-engaging expanded state.
2. The medical device (10) of claim 1 wherein the flow-occluding membrane (20) further includes a second tubular end opposite the constricted region (24) from the first tubular end (22), the second tubular end concentrically oriented and circumferentially engaged with the support structure.
3. The medical device (610) of claim 2 wherein the flow-occluding membrane (620) is a tubular member and the device further includes constriction means (628) for closing the tubular member at the constricted region (624) within the support structure (613) and enabling portions of the support structure (613) adjacent to the constricted region (624) to expand.
4. The medical device (210) of claim 2 wherein the fluid flow-occluding membrane (220) is a tubular member and the device further includes constriction means (228) for closing the tubular member and the support structure (213) at the constricted region (224).
5. The medical device (110) of claim 1 wherein the fluid flow-occluding membrane (120) is a tubular member having at least a portion including the first end (122) that is coextensive with at least a portion of thelength of the support structure (113) and the device further includes constriction means (128) for closing the tubular member and the support structure at the constricted region (124).
6. The medical device (10) of claim 1 wherein the fluid flow-occluding membrane (20) is a tubular member having at least a first portion including the first tubular end (22) that is coextensive with at least a portionof the length of the support structure (13), and a second portion including the constricted region (24) that is capable of extending beyond an end of the support structure (13).
7. The medical device (10) of claim 1 wherein:
the support structure (13) includes a metal structure, and the flow-occluding membrane (20) is formed of polymeric material.
the support structure (13) includes a metal structure, and the flow-occluding membrane (20) is formed of polymeric material.
8. The medical device (10) of claim 1 wherein:
the support structure (13) is radially compressible and self-expandable structure including one or more elongate filaments (16), and the flow-occluding membrane (20) is formed of polymeric material.
the support structure (13) is radially compressible and self-expandable structure including one or more elongate filaments (16), and the flow-occluding membrane (20) is formed of polymeric material.
9. A medical device (10) adapted for implantation into a body lumen having a tubular interior surface, including:
a radially self-expandable support structure (13) including a plurality of elongate structural filaments (16) that are interwoven, the support structure (13) expandable from a reduced-diameter compressed state to a self-supporting and lumen-engaging expanded state, the support structure (13) having a tubular portion for engaging the tubular interior surface of the lumen in the expanded state; and a flexible fluid flow-occluding membrane (20) including polymeric filaments (26) interwoven with the structural filaments (16) and having at least a first tubular end (22) coextensive with at least a portion of the length of the support structure (13), and a constricted region (24), the membrane (20) expandable with the support structure (13) from a reduced-diameter compressed state to an expanded state for occluding fluid flow through the body lumen when the support structure (13) is in the lumen-engaging expanded state.
a radially self-expandable support structure (13) including a plurality of elongate structural filaments (16) that are interwoven, the support structure (13) expandable from a reduced-diameter compressed state to a self-supporting and lumen-engaging expanded state, the support structure (13) having a tubular portion for engaging the tubular interior surface of the lumen in the expanded state; and a flexible fluid flow-occluding membrane (20) including polymeric filaments (26) interwoven with the structural filaments (16) and having at least a first tubular end (22) coextensive with at least a portion of the length of the support structure (13), and a constricted region (24), the membrane (20) expandable with the support structure (13) from a reduced-diameter compressed state to an expanded state for occluding fluid flow through the body lumen when the support structure (13) is in the lumen-engaging expanded state.
10. The medical device (10) of claim 9 wherein:
the support structure (13) includes first and second opposite ends (14, 15); and the constricted region (24) of flow-occluding membrane (20) extends beyond the second end (15) of the support structure (13).
the support structure (13) includes first and second opposite ends (14, 15); and the constricted region (24) of flow-occluding membrane (20) extends beyond the second end (15) of the support structure (13).
11. The medical device (110) of claim 9 wherein:
the support structure (113) includes first and second opposite ends (114, 115); and the constricted region (124) includes constriction means (128) for constricting a portion of the support structure (113) and the membrane (120).
the support structure (113) includes first and second opposite ends (114, 115); and the constricted region (124) includes constriction means (128) for constricting a portion of the support structure (113) and the membrane (120).
12. The medical device (210) of claim 11 wherein the constriction means (228) is located between the first and second opposite ends (214, 215) of the support structure (213).
13. The medical device (110) of claim 11 wherein the constriction means (128) is located on the first end of the support structure (113).
14. A medical device (310) adapted for implantation into a body lumen having a tubular interior surface, including:
a radially self-expandable support structure (313) including a plurality of elongated structural filaments (316) that are interwoven, the support structure (313) expandable from a reduced-diameter compressed state to a self-supporting and lumen-engaging expanded state, the support structure (313) having a tubular portion for engaging the tubular interior surface of the lumen in the expanded state; and a flexible fluid flow-occluding membrane (320) having at least a first tubular end (322) concentrically oriented and circumferentially engaged with the support structure (313), and a constricted region (324), the membrane (320) being expandable with the support structure (313) from a reduced diameter compressed state to an expanded state for occluding fluid flow through the body lumen when the support structure (313) is in the lumen-engaging expanded state.
a radially self-expandable support structure (313) including a plurality of elongated structural filaments (316) that are interwoven, the support structure (313) expandable from a reduced-diameter compressed state to a self-supporting and lumen-engaging expanded state, the support structure (313) having a tubular portion for engaging the tubular interior surface of the lumen in the expanded state; and a flexible fluid flow-occluding membrane (320) having at least a first tubular end (322) concentrically oriented and circumferentially engaged with the support structure (313), and a constricted region (324), the membrane (320) being expandable with the support structure (313) from a reduced diameter compressed state to an expanded state for occluding fluid flow through the body lumen when the support structure (313) is in the lumen-engaging expanded state.
15. The medical device (310) of claim 14, wherein the fluid flow-occluding membrane (320) further comprises a second portion including the constricted region (324) that is capable of extending beyond a second end of the support structure (313).
16. The medical device (610) of claim 14 wherein the fluid flow-occluding membrane (620) is positioned within the support structure (613), the device further including constriction means (628) for closing the fluid-flowoccluding membrane (620) within the support structure (613).
17. The medical device (310) of claim 14 further including constriction means (328) for closing the support structure (313) and membrane (320) at the constricted region (324).
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US08/797,983 US5919224A (en) | 1997-02-12 | 1997-02-12 | Medical device having a constricted region for occluding fluid flow in a body lumen |
| US08/797,983 | 1997-02-12 |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2229315A1 CA2229315A1 (en) | 1998-08-12 |
| CA2229315C true CA2229315C (en) | 2000-09-05 |
Family
ID=25172247
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002229315A Expired - Fee Related CA2229315C (en) | 1997-02-12 | 1998-02-10 | Medical device having a constricted region for occluding fluid flow in a body lumen |
Country Status (5)
| Country | Link |
|---|---|
| US (2) | US5919224A (en) |
| EP (1) | EP0864301B1 (en) |
| JP (1) | JPH10225458A (en) |
| CA (1) | CA2229315C (en) |
| DE (1) | DE69829430T2 (en) |
Families Citing this family (133)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6039749A (en) | 1994-02-10 | 2000-03-21 | Endovascular Systems, Inc. | Method and apparatus for deploying non-circular stents and graftstent complexes |
| GB2324729B (en) * | 1997-04-30 | 2002-01-02 | Bradford Hospitals Nhs Trust | Lung treatment device |
| US6258120B1 (en) | 1997-12-23 | 2001-07-10 | Embol-X, Inc. | Implantable cerebral protection device and methods of use |
| US6070589A (en) | 1997-08-01 | 2000-06-06 | Teramed, Inc. | Methods for deploying bypass graft stents |
| GB9716497D0 (en) * | 1997-08-05 | 1997-10-08 | Bridport Gundry Plc | Occlusion device |
| US6656215B1 (en) | 2000-11-16 | 2003-12-02 | Cordis Corporation | Stent graft having an improved means for attaching a stent to a graft |
| US6290731B1 (en) | 1998-03-30 | 2001-09-18 | Cordis Corporation | Aortic graft having a precursor gasket for repairing an abdominal aortic aneurysm |
| US7004962B2 (en) * | 1998-07-27 | 2006-02-28 | Schneider (Usa), Inc. | Neuroaneurysm occlusion and delivery device and method of using same |
| US6634364B2 (en) | 2000-12-15 | 2003-10-21 | Cardiac Pacemakers, Inc. | Method of deploying a ventricular lead containing a hemostasis mechanism |
| US6240321B1 (en) | 1998-08-12 | 2001-05-29 | Cardiac Pacemakers, Inc. | Expandable seal for use with medical device and system |
| US7314477B1 (en) | 1998-09-25 | 2008-01-01 | C.R. Bard Inc. | Removable embolus blood clot filter and filter delivery unit |
| US7018401B1 (en) | 1999-02-01 | 2006-03-28 | Board Of Regents, The University Of Texas System | Woven intravascular devices and methods for making the same and apparatus for delivery of the same |
| US6428558B1 (en) | 1999-03-10 | 2002-08-06 | Cordis Corporation | Aneurysm embolization device |
| US8428747B2 (en) * | 1999-04-05 | 2013-04-23 | The Spectranetics Corp. | Lead locking device and method |
| US20040236396A1 (en) * | 1999-04-05 | 2004-11-25 | Coe Michael Sean | Lead locking device and method |
| US7195641B2 (en) | 1999-11-19 | 2007-03-27 | Advanced Bio Prosthetic Surfaces, Ltd. | Valvular prostheses having metal or pseudometallic construction and methods of manufacture |
| US6458153B1 (en) * | 1999-12-31 | 2002-10-01 | Abps Venture One, Ltd. | Endoluminal cardiac and venous valve prostheses and methods of manufacture and delivery thereof |
| US6361546B1 (en) * | 2000-01-13 | 2002-03-26 | Endotex Interventional Systems, Inc. | Deployable recoverable vascular filter and methods for use |
| US6468303B1 (en) | 2000-03-27 | 2002-10-22 | Aga Medical Corporation | Retrievable self expanding shunt |
| GB0011053D0 (en) | 2000-05-09 | 2000-06-28 | Hudson John O | Medical device and use thereof |
| WO2001093782A1 (en) * | 2000-06-08 | 2001-12-13 | Frantzen John J | Radially expandable stent featuring covering tip primarily for bifurcated artery aneurysms |
| US6584362B1 (en) * | 2000-08-30 | 2003-06-24 | Cardiac Pacemakers, Inc. | Leads for pacing and/or sensing the heart from within the coronary veins |
| US6695833B1 (en) * | 2000-09-27 | 2004-02-24 | Nellix, Inc. | Vascular stent-graft apparatus and forming method |
| GB0030794D0 (en) * | 2000-12-16 | 2001-01-31 | Hudson John O | Medical device and use thereof |
| US20020128680A1 (en) * | 2001-01-25 | 2002-09-12 | Pavlovic Jennifer L. | Distal protection device with electrospun polymer fiber matrix |
| US7798147B2 (en) * | 2001-03-02 | 2010-09-21 | Pulmonx Corporation | Bronchial flow control devices with membrane seal |
| US20030100945A1 (en) * | 2001-11-23 | 2003-05-29 | Mindguard Ltd. | Implantable intraluminal device and method of using same in treating aneurysms |
| US20030050648A1 (en) | 2001-09-11 | 2003-03-13 | Spiration, Inc. | Removable lung reduction devices, systems, and methods |
| CA2462509A1 (en) | 2001-10-04 | 2003-04-10 | Neovasc Medical Ltd. | Flow reducing implant |
| US6592594B2 (en) * | 2001-10-25 | 2003-07-15 | Spiration, Inc. | Bronchial obstruction device deployment system and method |
| US9204956B2 (en) | 2002-02-20 | 2015-12-08 | C. R. Bard, Inc. | IVC filter with translating hooks |
| US6929637B2 (en) * | 2002-02-21 | 2005-08-16 | Spiration, Inc. | Device and method for intra-bronchial provision of a therapeutic agent |
| US20030216769A1 (en) | 2002-05-17 | 2003-11-20 | Dillard David H. | Removable anchored lung volume reduction devices and methods |
| US20030181922A1 (en) | 2002-03-20 | 2003-09-25 | Spiration, Inc. | Removable anchored lung volume reduction devices and methods |
| US6752828B2 (en) | 2002-04-03 | 2004-06-22 | Scimed Life Systems, Inc. | Artificial valve |
| US7887575B2 (en) * | 2002-05-22 | 2011-02-15 | Boston Scientific Scimed, Inc. | Stent with segmented graft |
| AU2003256798A1 (en) * | 2002-07-26 | 2004-02-16 | Emphasys Medical, Inc. | Bronchial flow control devices with membrane seal |
| US8075585B2 (en) * | 2002-08-29 | 2011-12-13 | Stryker Corporation | Device and method for treatment of a vascular defect |
| AU2003272682C1 (en) | 2002-09-20 | 2009-07-16 | Nellix, Inc. | Stent-graft with positioning anchor |
| US7814912B2 (en) * | 2002-11-27 | 2010-10-19 | Pulmonx Corporation | Delivery methods and devices for implantable bronchial isolation devices |
| US7323001B2 (en) * | 2003-01-30 | 2008-01-29 | Ev3 Inc. | Embolic filters with controlled pore size |
| US7220271B2 (en) * | 2003-01-30 | 2007-05-22 | Ev3 Inc. | Embolic filters having multiple layers and controlled pore size |
| US20040153119A1 (en) * | 2003-01-30 | 2004-08-05 | Kusleika Richard S. | Embolic filters with a distal loop or no loop |
| US7100616B2 (en) * | 2003-04-08 | 2006-09-05 | Spiration, Inc. | Bronchoscopic lung volume reduction method |
| US20100196345A1 (en) * | 2003-04-27 | 2010-08-05 | Protalix | Production of high mannose proteins in plant culture |
| US7951557B2 (en) * | 2003-04-27 | 2011-05-31 | Protalix Ltd. | Human lysosomal proteins from plant cell culture |
| US7533671B2 (en) | 2003-08-08 | 2009-05-19 | Spiration, Inc. | Bronchoscopic repair of air leaks in a lung |
| US8333798B2 (en) | 2003-11-07 | 2012-12-18 | Merlin Md Pte Ltd. | Implantable medical devices with enhanced visibility, mechanical properties and biocompatability |
| US20050149109A1 (en) * | 2003-12-23 | 2005-07-07 | Wallace Michael P. | Expanding filler coil |
| JP4301935B2 (en) * | 2003-12-26 | 2009-07-22 | テルモ株式会社 | Device for retaining embolus member |
| KR101105218B1 (en) | 2004-01-09 | 2012-01-13 | 지.아이. 뷰 리미티드 | Pressure-propelled system for body lumen |
| WO2005094725A1 (en) | 2004-03-31 | 2005-10-13 | Merlin Md Pte Ltd | A method for treating aneurysms |
| US8500751B2 (en) | 2004-03-31 | 2013-08-06 | Merlin Md Pte Ltd | Medical device |
| US8715340B2 (en) | 2004-03-31 | 2014-05-06 | Merlin Md Pte Ltd. | Endovascular device with membrane |
| US8048145B2 (en) | 2004-07-22 | 2011-11-01 | Endologix, Inc. | Graft systems having filling structures supported by scaffolds and methods for their use |
| US7704267B2 (en) | 2004-08-04 | 2010-04-27 | C. R. Bard, Inc. | Non-entangling vena cava filter |
| US8517027B2 (en) * | 2004-09-03 | 2013-08-27 | Boston Scientific Scimed, Inc. | Reversible vessel seal |
| WO2006034153A2 (en) | 2004-09-17 | 2006-03-30 | Cordis Neurovascular, Inc. | Thin film metallic devices for plugging aneurysms or vessels |
| US8795315B2 (en) | 2004-10-06 | 2014-08-05 | Cook Medical Technologies Llc | Emboli capturing device having a coil and method for capturing emboli |
| US7794473B2 (en) | 2004-11-12 | 2010-09-14 | C.R. Bard, Inc. | Filter delivery system |
| US20060116713A1 (en) * | 2004-11-26 | 2006-06-01 | Ivan Sepetka | Aneurysm treatment devices and methods |
| US8267954B2 (en) | 2005-02-04 | 2012-09-18 | C. R. Bard, Inc. | Vascular filter with sensing capability |
| ES2380356T3 (en) | 2005-02-18 | 2012-05-10 | Tyco Healthcare Group Lp | Quick exchange catheter |
| US8221446B2 (en) | 2005-03-15 | 2012-07-17 | Cook Medical Technologies | Embolic protection device |
| US8945169B2 (en) | 2005-03-15 | 2015-02-03 | Cook Medical Technologies Llc | Embolic protection device |
| JP5102201B2 (en) | 2005-05-12 | 2012-12-19 | シー・アール・バード・インコーポレーテッド | Removable embolic clot filter |
| US7850708B2 (en) | 2005-06-20 | 2010-12-14 | Cook Incorporated | Embolic protection device having a reticulated body with staggered struts |
| US8109962B2 (en) | 2005-06-20 | 2012-02-07 | Cook Medical Technologies Llc | Retrievable device having a reticulation portion with staggered struts |
| AU2006269419A1 (en) | 2005-07-07 | 2007-01-18 | Nellix, Inc. | Systems and methods for endovascular aneurysm treatment |
| DE102005032308A1 (en) * | 2005-07-11 | 2007-01-18 | Campus Gmbh & Co. Kg | Endovascular implant for the occlusion of a blood vessel |
| US7771452B2 (en) | 2005-07-12 | 2010-08-10 | Cook Incorporated | Embolic protection device with a filter bag that disengages from a basket |
| US7766934B2 (en) | 2005-07-12 | 2010-08-03 | Cook Incorporated | Embolic protection device with an integral basket and bag |
| US8187298B2 (en) | 2005-08-04 | 2012-05-29 | Cook Medical Technologies Llc | Embolic protection device having inflatable frame |
| JP4851522B2 (en) | 2005-08-09 | 2012-01-11 | シー・アール・バード・インコーポレーテッド | Insertion type thrombus filter and delivery system |
| US8377092B2 (en) | 2005-09-16 | 2013-02-19 | Cook Medical Technologies Llc | Embolic protection device |
| US8632562B2 (en) | 2005-10-03 | 2014-01-21 | Cook Medical Technologies Llc | Embolic protection device |
| US8182508B2 (en) | 2005-10-04 | 2012-05-22 | Cook Medical Technologies Llc | Embolic protection device |
| US9265605B2 (en) * | 2005-10-14 | 2016-02-23 | Boston Scientific Scimed, Inc. | Bronchoscopic lung volume reduction valve |
| US8252017B2 (en) | 2005-10-18 | 2012-08-28 | Cook Medical Technologies Llc | Invertible filter for embolic protection |
| US8216269B2 (en) | 2005-11-02 | 2012-07-10 | Cook Medical Technologies Llc | Embolic protection device having reduced profile |
| US8152831B2 (en) | 2005-11-17 | 2012-04-10 | Cook Medical Technologies Llc | Foam embolic protection device |
| JP2009519731A (en) | 2005-11-18 | 2009-05-21 | シー・アール・バード・インコーポレイテツド | Vena cava filter with filament |
| US20090054966A1 (en) * | 2006-02-13 | 2009-02-26 | Merlin Md Pte Ltd. | Endovascular device with membrane |
| US8597341B2 (en) * | 2006-03-06 | 2013-12-03 | David Elmaleh | Intravascular device with netting system |
| DE602007001532D1 (en) * | 2006-03-20 | 2009-08-20 | Medical Device Works Nv Sa | DEVICE FOR DELIVERING MEDICAL TREATMENT |
| US7691151B2 (en) | 2006-03-31 | 2010-04-06 | Spiration, Inc. | Articulable Anchor |
| US10188496B2 (en) | 2006-05-02 | 2019-01-29 | C. R. Bard, Inc. | Vena cava filter formed from a sheet |
| DE102006023637A1 (en) * | 2006-05-18 | 2007-11-22 | Breathe Technologies, Inc., Freemont | Tracheostoma placeholder for use in trachea opening e.g. tracheostoma, has tubular support structure that is expandable from initial condition into support condition, where diameter of support structure is increased in support condition |
| US9326842B2 (en) | 2006-06-05 | 2016-05-03 | C. R . Bard, Inc. | Embolus blood clot filter utilizable with a single delivery system or a single retrieval system in one of a femoral or jugular access |
| EP2043551B1 (en) | 2006-07-19 | 2018-05-09 | Novate Medical Limited | A vascular filter |
| WO2008027293A2 (en) * | 2006-08-25 | 2008-03-06 | Emphasys Medical, Inc. | Bronchial isolation devices for placement in short lumens |
| US20080071307A1 (en) | 2006-09-19 | 2008-03-20 | Cook Incorporated | Apparatus and methods for in situ embolic protection |
| CN103767810B (en) | 2006-10-22 | 2016-06-15 | Idev科技公司 | From the manufacturing process of extendable bracket |
| US9901434B2 (en) | 2007-02-27 | 2018-02-27 | Cook Medical Technologies Llc | Embolic protection device including a Z-stent waist band |
| ES2660667T3 (en) * | 2007-05-07 | 2018-03-23 | Protalix Ltd. | Large-scale disposable bioreactor |
| US9138307B2 (en) | 2007-09-14 | 2015-09-22 | Cook Medical Technologies Llc | Expandable device for treatment of a stricture in a body vessel |
| US8419748B2 (en) | 2007-09-14 | 2013-04-16 | Cook Medical Technologies Llc | Helical thrombus removal device |
| US8252018B2 (en) | 2007-09-14 | 2012-08-28 | Cook Medical Technologies Llc | Helical embolic protection device |
| US20090088827A1 (en) * | 2007-10-02 | 2009-04-02 | Cardiac Pacemakers, Inc | Lead assembly providing sensing or stimulation of spaced-apart myocardial contact areas |
| US8043301B2 (en) * | 2007-10-12 | 2011-10-25 | Spiration, Inc. | Valve loader method, system, and apparatus |
| JP5570993B2 (en) * | 2007-10-12 | 2014-08-13 | スピレーション インコーポレイテッド | Valve loader methods, systems, and apparatus |
| US9259225B2 (en) * | 2008-02-19 | 2016-02-16 | St. Jude Medical, Cardiology Division, Inc. | Medical devices for treating a target site and associated method |
| AU2013273779B2 (en) * | 2008-02-19 | 2015-09-24 | St. Jude Medical, Cardiology Division, Inc. | Medical devices for treating a target site and associated method |
| US8764772B2 (en) * | 2008-02-21 | 2014-07-01 | Cook Medical Technologies Llc | Occlusion device |
| WO2009124247A2 (en) * | 2008-04-03 | 2009-10-08 | William Cook Europe Aps | Occlusion device |
| JP5663471B2 (en) | 2008-04-25 | 2015-02-04 | ネリックス・インコーポレーテッド | Stent / graft delivery system |
| JP2011522615A (en) | 2008-06-04 | 2011-08-04 | ネリックス・インコーポレーテッド | Sealing device and method of use |
| US8262692B2 (en) | 2008-09-05 | 2012-09-11 | Merlin Md Pte Ltd | Endovascular device |
| US8986338B2 (en) * | 2008-10-29 | 2015-03-24 | Cook Biotech Incorporated | Vascular plugs |
| US8388644B2 (en) | 2008-12-29 | 2013-03-05 | Cook Medical Technologies Llc | Embolic protection device and method of use |
| EP3505136A1 (en) | 2009-07-29 | 2019-07-03 | C.R. Bard Inc. | Tubular filter |
| US20110144689A1 (en) * | 2009-12-15 | 2011-06-16 | Med Institute, Inc. | Occlusion Device |
| US20110276078A1 (en) | 2009-12-30 | 2011-11-10 | Nellix, Inc. | Filling structure for a graft system and methods of use |
| US8801768B2 (en) | 2011-01-21 | 2014-08-12 | Endologix, Inc. | Graft systems having semi-permeable filling structures and methods for their use |
| US9415195B2 (en) | 2011-04-06 | 2016-08-16 | Engologix, Inc. | Method and system for treating aneurysms |
| CA2835427A1 (en) * | 2011-05-11 | 2012-11-15 | Microvention, Inc. | Device for occluding a lumen |
| US8795241B2 (en) | 2011-05-13 | 2014-08-05 | Spiration, Inc. | Deployment catheter |
| ES2943709T3 (en) | 2012-04-06 | 2023-06-15 | Merlin Md Pte Ltd | Devices to treat an aneurysm |
| NZ701992A (en) | 2012-05-14 | 2016-03-31 | Bard Inc C R | Uniformly expandable stent |
| US9011481B2 (en) * | 2012-12-30 | 2015-04-21 | Cook Medical Technologies Llc | Vascular occlusion device having a jelly fish |
| USD723165S1 (en) | 2013-03-12 | 2015-02-24 | C. R. Bard, Inc. | Stent |
| US10201638B2 (en) | 2013-03-14 | 2019-02-12 | Endologix, Inc. | Systems and methods for forming materials in situ within a medical device |
| CN105899150B (en) | 2013-07-31 | 2018-07-27 | Neuvt 有限公司 | Method and apparatus for Endovascular Embolization |
| US10010328B2 (en) | 2013-07-31 | 2018-07-03 | NeuVT Limited | Endovascular occlusion device with hemodynamically enhanced sealing and anchoring |
| WO2015095538A1 (en) | 2013-12-20 | 2015-06-25 | Microvention, Inc. | Vascular occlusion |
| EP3197391A4 (en) * | 2014-09-26 | 2018-06-20 | Anaxiom Corporation | Removable vascular occlusion device |
| GB2534194B (en) * | 2015-01-16 | 2017-02-08 | Cook Medical Technologies Llc | Cone Expanding Collapsible Medical Device |
| US20170042551A1 (en) | 2015-08-13 | 2017-02-16 | The Brain Protection Company PTY LTD | Implantable damping devices for treating dementia and associated systems and methods of use |
| US11564692B2 (en) | 2018-11-01 | 2023-01-31 | Terumo Corporation | Occlusion systems |
| JP7403547B2 (en) | 2019-01-23 | 2023-12-22 | ニオバスク メディカル リミテッド | coated flow modifier |
| CN112057127B (en) * | 2020-08-14 | 2023-10-20 | 江立生 | Left auricle shutoff postoperative residual leakage shutoff system |
| WO2022132778A1 (en) * | 2020-12-14 | 2022-06-23 | Julason Richard D | Occluding medical devices and methods of use |
| CA3211889A1 (en) | 2021-03-12 | 2022-09-15 | Troy Thornton | Device and method for variable blood flow occlusion |
Family Cites Families (33)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US3868956A (en) * | 1972-06-05 | 1975-03-04 | Ralph J Alfidi | Vessel implantable appliance and method of implanting it |
| SE445884B (en) * | 1982-04-30 | 1986-07-28 | Medinvent Sa | DEVICE FOR IMPLANTATION OF A RODFORM PROTECTION |
| US4705517A (en) * | 1985-09-03 | 1987-11-10 | Becton, Dickinson And Company | Percutaneously deliverable intravascular occlusion prosthesis |
| US4710192A (en) * | 1985-12-30 | 1987-12-01 | Liotta Domingo S | Diaphragm and method for occlusion of the descending thoracic aorta |
| US4994069A (en) * | 1988-11-02 | 1991-02-19 | Target Therapeutics | Vaso-occlusion coil and method |
| EP0408245B1 (en) * | 1989-07-13 | 1994-03-02 | American Medical Systems, Inc. | Stent placement instrument |
| US5221261A (en) * | 1990-04-12 | 1993-06-22 | Schneider (Usa) Inc. | Radially expandable fixation member |
| US5108407A (en) * | 1990-06-08 | 1992-04-28 | Rush-Presbyterian St. Luke's Medical Center | Method and apparatus for placement of an embolic coil |
| US5229431A (en) * | 1990-06-15 | 1993-07-20 | Corvita Corporation | Crack-resistant polycarbonate urethane polymer prostheses and the like |
| US5108420A (en) * | 1991-02-01 | 1992-04-28 | Temple University | Aperture occlusion device |
| US5197978B1 (en) * | 1991-04-26 | 1996-05-28 | Advanced Coronary Tech | Removable heat-recoverable tissue supporting device |
| US5397351A (en) * | 1991-05-13 | 1995-03-14 | Pavcnik; Dusan | Prosthetic valve for percutaneous insertion |
| DE69229539T2 (en) * | 1991-11-05 | 2000-02-17 | Childrens Medical Center | Occlusion device for repairing heart and vascular defects |
| US5486193A (en) * | 1992-01-22 | 1996-01-23 | C. R. Bard, Inc. | System for the percutaneous transluminal front-end loading delivery of a prosthetic occluder |
| FR2689388B1 (en) * | 1992-04-07 | 1999-07-16 | Celsa Lg | PERFECTIONALLY RESORBABLE BLOOD FILTER. |
| DE9205797U1 (en) * | 1992-04-30 | 1992-06-17 | Schmitz-Rode, Thomas, Dipl.-Ing. Dr.Med. | |
| FR2694491B1 (en) * | 1992-08-07 | 1994-09-30 | Celsa Lg | Triangular tab filters. |
| US5382261A (en) * | 1992-09-01 | 1995-01-17 | Expandable Grafts Partnership | Method and apparatus for occluding vessels |
| US5527338A (en) * | 1992-09-02 | 1996-06-18 | Board Of Regents, The University Of Texas System | Intravascular device |
| US5382259A (en) * | 1992-10-26 | 1995-01-17 | Target Therapeutics, Inc. | Vasoocclusion coil with attached tubular woven or braided fibrous covering |
| US5423849A (en) * | 1993-01-15 | 1995-06-13 | Target Therapeutics, Inc. | Vasoocclusion device containing radiopaque fibers |
| WO1994024961A1 (en) * | 1993-04-23 | 1994-11-10 | Schneider (Usa) Inc. | Covered stent and stent delivery device |
| DE4334140C2 (en) * | 1993-10-07 | 1996-04-18 | Angiomed Ag | Stent and device with stent |
| US5573547A (en) * | 1993-10-19 | 1996-11-12 | Leveen; Harry H. | Brush fixation method for attachment of tissues and occlusion of blood vessels |
| EP0744977B1 (en) * | 1993-11-12 | 2003-03-26 | Micro Interventional Systems | Small diameter, high torque catheter |
| US5417708A (en) * | 1994-03-09 | 1995-05-23 | Cook Incorporated | Intravascular treatment system and percutaneous release mechanism therefor |
| EP0793457B2 (en) * | 1994-04-06 | 2006-04-12 | WILLIAM COOK EUROPE ApS | A medical article for implantation into the vascular system of a patient |
| US5634942A (en) * | 1994-04-21 | 1997-06-03 | B. Braun Celsa | Assembly comprising a blood filter for temporary or definitive use and a device for implanting it |
| US6123715A (en) * | 1994-07-08 | 2000-09-26 | Amplatz; Curtis | Method of forming medical devices; intravascular occlusion devices |
| JPH10504738A (en) * | 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 |
| US5709704A (en) * | 1994-11-30 | 1998-01-20 | Boston Scientific Corporation | Blood clot filtering |
| US5591195A (en) * | 1995-10-30 | 1997-01-07 | Taheri; Syde | Apparatus and method for engrafting a blood vessel |
| US5628788A (en) * | 1995-11-07 | 1997-05-13 | Corvita Corporation | Self-expanding endoluminal stent-graft |
-
1997
- 1997-02-12 US US08/797,983 patent/US5919224A/en not_active Expired - Lifetime
-
1998
- 1998-02-10 EP EP98200404A patent/EP0864301B1/en not_active Expired - Lifetime
- 1998-02-10 CA CA002229315A patent/CA2229315C/en not_active Expired - Fee Related
- 1998-02-10 DE DE69829430T patent/DE69829430T2/en not_active Expired - Lifetime
- 1998-02-10 JP JP2885698A patent/JPH10225458A/en active Pending
-
1999
- 1999-06-11 US US09/332,284 patent/US6193748B1/en not_active Expired - Lifetime
Also Published As
| Publication number | Publication date |
|---|---|
| EP0864301B1 (en) | 2005-03-23 |
| US5919224A (en) | 1999-07-06 |
| EP0864301A1 (en) | 1998-09-16 |
| JPH10225458A (en) | 1998-08-25 |
| US6193748B1 (en) | 2001-02-27 |
| CA2229315A1 (en) | 1998-08-12 |
| DE69829430T2 (en) | 2005-09-01 |
| DE69829430D1 (en) | 2005-04-28 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CA2229315C (en) | Medical device having a constricted region for occluding fluid flow in a body lumen | |
| CA1239755A (en) | Prosthesis comprising an expansible or contractile tubular body | |
| EP0812164B1 (en) | Endovascular stent with locking ring | |
| EP2751323B1 (en) | Method of forming a braided helical wire stent | |
| US5849037A (en) | Self-expanding stent for a medical device to be introduced into a cavity of a body, and method for its preparation | |
| JP4044192B2 (en) | Stent graft with knitted polymer sleeve | |
| US6488701B1 (en) | Stent-graft assembly with thin-walled graft component and method of manufacture | |
| US5741325A (en) | Self-expanding intraluminal composite prosthesis | |
| US6929659B2 (en) | Method of preventing the dislodgment of a stent-graft | |
| US6019786A (en) | Braided composite prosthesis | |
| US6689162B1 (en) | Braided composite prosthesis | |
| AU729170B2 (en) | Three-dimensional braided covered stent | |
| US20170296325A1 (en) | Stent-graft prosthesis and method of manufacture | |
| EP0938879A2 (en) | Stent-graft assembly and method of manufacture | |
| US20110106240A1 (en) | Large vessel stents and occluders | |
| WO2001052771A1 (en) | Stent-graft with helically arranged securement member | |
| EP1258229A1 (en) | Flexible and elastic vascular stents and grafts |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| EEER | Examination request | ||
| MKLA | Lapsed |