US20040098097A1 - Methods and apparatus for conformably sealing prostheses within body lumens - Google Patents
Methods and apparatus for conformably sealing prostheses within body lumens Download PDFInfo
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- US20040098097A1 US20040098097A1 US10/712,376 US71237603A US2004098097A1 US 20040098097 A1 US20040098097 A1 US 20040098097A1 US 71237603 A US71237603 A US 71237603A US 2004098097 A1 US2004098097 A1 US 2004098097A1
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- sealing layer
- prosthesis
- tubular
- body lumen
- tubular prosthesis
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
- A61F2/06—Blood vessels
- A61F2/07—Stent-grafts
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/848—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents having means for fixation to the vessel wall, e.g. barbs
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/89—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure the wire-like elements comprising two or more adjacent rings flexibly connected by separate members
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/94—Stents retaining their form, i.e. not being deformable, after placement in the predetermined place
- A61F2/945—Stents retaining their form, i.e. not being deformable, after placement in the predetermined place hardenable, e.g. stents formed in situ
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
- A61F2/06—Blood vessels
- A61F2/07—Stent-grafts
- A61F2002/072—Encapsulated stents, e.g. wire or whole stent embedded in lining
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
- A61F2/06—Blood vessels
- A61F2/07—Stent-grafts
- A61F2002/075—Stent-grafts the stent being loosely attached to the graft material, e.g. by stitching
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
- A61F2/06—Blood vessels
- A61F2/07—Stent-grafts
- A61F2002/077—Stent-grafts having means to fill the space between stent-graft and aneurysm wall, e.g. a sleeve
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2002/30001—Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
- A61F2002/30316—The prosthesis having different structural features at different locations within the same prosthesis; Connections between prosthetic parts; Special structural features of bone or joint prostheses not otherwise provided for
- A61F2002/30535—Special structural features of bone or joint prostheses not otherwise provided for
- A61F2002/30581—Special structural features of bone or joint prostheses not otherwise provided for having a pocket filled with fluid, e.g. liquid
- A61F2002/30583—Special structural features of bone or joint prostheses not otherwise provided for having a pocket filled with fluid, e.g. liquid filled with hardenable fluid, e.g. curable in-situ
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/848—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents having means for fixation to the vessel wall, e.g. barbs
- A61F2002/8483—Barbs
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2210/00—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2210/0085—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof hardenable in situ, e.g. epoxy resins
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2220/00—Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2220/0025—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
- A61F2220/0058—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements soldered or brazed or welded
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2230/0002—Two-dimensional shapes, e.g. cross-sections
- A61F2230/0028—Shapes in the form of latin or greek characters
- A61F2230/0054—V-shaped
Definitions
- the present invention relates generally to methods and apparatus for the endoluminal placement of tubular prostheses, such as grafts, stents, and other structures. More particularly, the present invention relates to the implantation of luminal prostheses in a sealing layer within a body lumen.
- Vascular aneurysms are the result of abnormal dilation of a blood vessel, usually resulting from disease and/or genetic predisposition which can weaken the arterial wall and allow it to expand. While aneurysms can occur in any blood vessel, most occur in the aorta and peripheral arteries, with the majority of aortic aneurysms occurring in the abdominal aorta, usually beginning below the renal arteries and often extending distally into one or both of the iliac arteries.
- Aortic aneurysms are most commonly treated in open surgical procedures where the diseased vessel segment is bypassed and repaired with an artificial vascular graft. While considered to be an effective surgical technique, particularly considering the alternative of a usually fatal ruptured abdominal aortic aneurysm, conventional vascular graft surgery suffers from a number of disadvantages.
- the surgical procedure is complex and requires experienced surgeons and well-equipped surgical facilities. Even with the best surgeons and equipment, however, the patients being treated frequently are elderly and weakened from cardiovascular and other diseases, reducing the number of eligible patients.
- conventional aneurysm repair surgery performed prior to rupture has a relatively high mortality rate, usually from 2% to 10%. Morbidity related to the conventional surgery includes myocardial infarction, renal failure, impotence, paralysis, and other conditions. Additionally, even with successful surgery, recovery can take several weeks and often requires a lengthy hospital stay.
- endovascular graft placement procedures for the treatment of aneurysms have been proposed.
- endovascular procedures will deliver a radially compressed graft intravascularly to the aneurysm.
- the graft is then expanded in situ, either by releasing a self-expanding graft or by internally expanding a malleable graft (e.g. using a balloon catheter) to protect the aneurysm.
- the vascular graft will comprise both a frame and a liner, where the frame provides the necessary mechanical support and the liner provides the necessary blood barrier.
- FIGS. 1 - 3 the problem of blood flow leakage past a graft structure 10 implanted within the region of an aneurysm A in a blood vessel BV is illustrated. While the graft 10 may be adequately anchored on each side of the aneurysm A, as illustrated in FIG. 1, over time the inner surface of the blood vessel lumen can partially separate from the outer surface of the graft 10 , as illustrated in FIGS. 2 and 3. Such separations S can allow bypass blood flow into the region of the aneurysm A.
- intraluminal prostheses and methods for their implantation which can overcome at least some of the difficulties described above.
- intraluminal prostheses and methods for their implantation which would provide a generally fluid tight seal circumscribing at least one end of the prosthesis, and preferably both ends or the entire length of the prosthesis, to prevent bypass blood or other fluid flow into the interstitial region between the inner wall of the body lumen and the outer surface of the prosthesis.
- such improved prostheses and methods for their implantation would provide for sealing of the prosthesis which would resist separating from the intraluminal wall in order to prevent such bypass flow in a long-term or permanent fashion after implantation of the prosthesis.
- a tubular prosthesis having an annular cavity for receiving a plastic material to enlarge and anchor the prosthesis within a blood vessel is described in U.S. Pat. No. 5,156,620.
- a tubular prosthesis having inflatable cuffs on each end is described in U.S. Pat. No. 3,991,767.
- a tubular prosthesis having everted cuffs for receiving sutures is described in U.S. Pat. No. 4,728,328.
- a tubular stent having hook-like projections over its outer surface is described in U.S. Pat. No. 5,167,614.
- a tubular stent having a plurality of self-locking fingers extending outward from its outer surface is described in U.S. Pat. No. 5,344,426.
- a fluid delivery catheter comprising concentric lumens in a balloon structure is described in U.S. Pat. No. 5,295,962.
- a vascular prosthesis comprising two porous concentrically associated tubes with a helical spring enclosed therebetween is disclosed in U.S. Pat. No. 4,130,904.
- a vascular prosthesis comprising a multilaminar tubular member is disclosed in U.S. Pat. No. 5,354,329.
- Microporous materials suitable for the fabrication of prosthetic devices are described in U.S. Pat. Nos. 3,890,107 and 5,348,788.
- the present invention provides methods and apparatus for the transluminal positioning of tubular prostheses at a target location within a body lumen.
- the tubular prostheses are suitable for a wide variety of therapeutic uses, including stenting of the ureter, urethra, biliary tract, and the like.
- the devices and methods will also find use in the creation of temporary or long-term lumens, such as the formation of fistulas.
- the present invention will find its greatest use, however, in the placement of endovascular grafts into blood vessels for the treatment of abdominal and other aneurysms, vascular stenoses, and the like.
- a tubular prosthesis is delivered to the target site within the body lumen in a radially compressed configuration and is expanded in situ at the target location so that an exterior surface of the prosthesis engages an inner wall of the body lumen over an interface region therebetween.
- Radial expansion of the prosthesis may be effected in any conventional manner, including the use of a balloon catheter for expanding malleable prostheses, the release of compressed, self-expanding prostheses from suitable delivery catheters, and the like.
- the present invention particularly provides for expansion of the prostheses into a sealing layer which is disposed in or over at least a portion of the interface region.
- the sealing layer may be disposed within substantially the entire interface region, or may be disposed over one or more discrete, circumferential bands within the interface region.
- the sealing layer will be disposed at least at each end of the tubular prosthesis in order to provide a barrier against the bypass leakage of fluid into portions of the interface region therebetween.
- the sealing layer will occupy substantially the entire interface region.
- the sealing layer may be composed of virtually any material which is biocompatable and capable of conforming to the interface region between the outer wall of the tubular prosthesis and the inner wall of the body lumen.
- Exemplary materials include gels, foams, adhesives, biological polymers, compliant sleeves, sponges, porous matrices and meshes, and the like.
- the materials are initially present on the prosthesis or delivered in a fluid or semi-solid state to the interface region, and thereafter cured or hardened to achieve the final, desired geometry.
- the sealing layer may be composed of materials which expand in situ in order to fully conform to the geometry of the interface region, e.g. including materials such as hydrophilic gels, hydrophilic foams, and the like.
- An exemplary material for the sealing layer comprises a microporous mesh, particularly composed of silicone rubber and similar materials.
- the sealing layer may be initially formed or disposed over at least a portion of the exterior surface of the tubular prosthesis prior to in situ expansion.
- the tubular prosthesis will usually be pre-coated or covered with the material of the sealing layer prior to introduction of the prosthesis to the body lumen.
- the material of the sealing layer may be introduced in an initial step prior to introduction of the tubular prosthesis.
- a fluid delivery catheter will be employed to apply the sealing layer material in a fluid or semi-solid state over at least a portion of the interface region.
- the fluid delivery catheter is removed, and a prosthesis delivery catheter is then introduced to the target location.
- the prosthesis carried by the catheter may then be expanded in situ so that it engages and conforms to the material of the sealing layer.
- Apparatus according to the present invention includes tubular prostheses comprising an expansible tubular frame having a sealing layer formed at least partially over an exterior surface thereof.
- the sealing layer may be formed of any of the materials described above.
- the apparatus according to the present invention further includes a fluid delivery catheter comprising a catheter body having a proximal end and a distal end.
- An outer balloon and an inner balloon are disposed on the catheter near its distal end.
- the outer balloon is positioned over the inner balloon and includes a plurality of fluid delivery ports formed over its surface.
- the outer balloon is connected to a first lumen within the catheter body and can receive a fluid or semi-solid sealing material therethrough.
- the inner balloon is connected to a second lumen within the catheter body and can receive an expansion medium therethrough.
- the sealing material By first filling the outer balloon with the fluid or semi-solid sealing material, and thereafter expanding the inner balloon within the outer balloon, the sealing material is extruded outwardly through the fluid delivery ports in an annuler layer over the inner surface of the luminal wall.
- the prosthesis may then be delivered to the body lumen and expanded so that it becomes embedded in the layer of sealing material.
- the sealing material hardens, optionally with the application of energy conforming to the exterior of the prosthesis and providing a substantially permanent anchor and barrier to the bypass of body fluid.
- FIGS. 1 - 3 illustrate prior art implantation of a vascular prosthesis.
- FIG. 4 is a cross-sectional view of a vascular prosthesis embedded in a sealing layer in the region of an aneurysm according to the present invention.
- FIG. 5 is a cross-sectional view taken along line 5 - 5 of FIG. 4.
- FIG. 6 is a cross-sectional view taken along line 6 - 6 of FIG. 4.
- FIG. 7 illustrates a tubular prosthesis constructed in accordance with the principles of the present invention, in a radially compressed configuration.
- FIG. 8 illustrates the tubular prosthesis of FIG. 7 in a radially expanded configuration.
- FIG. 9 illustrates a bifurcated prosthesis constructed in accordance with the principles of the present invention.
- FIG. 10 illustrates a fluid delivery catheter intended for the intraluminal delivery of a sealing material for use in the methods of the present invention.
- FIGS. 11 A- 11 F illustrate a particular embodiment of the method of the present invention employing an initial sealing material delivery step followed by a separate prosthesis implantation step.
- FIG. 12 illustrates a first embodiment of a sealing sleeve intended for implantation at the bifurcation of the abdominal aorta into the left and right iliac arteries.
- FIG. 13 is an alternate embodiment of a sealing sleeve for implantation at the bifurcation of the abdominal aorta into the right and left iliac arteries.
- FIG. 14 illustrates the implantation of a vascular graft between a pair of sealing sleeves to treat an abdominal aortic aneurysm.
- FIG. 15 illustrates an alternative anchoring of the vascular graft of FIG. 14 with a sealing sleeve which extends into the renal arteries.
- FIG. 16 illustrates use of the vascular prosthesis of the present invention for sealing at each end of a previously implanted prosthesis.
- FIG. 17 illustrates an alternative embodiment of the sealing prosthesis of the present invention.
- FIG. 18 illustrates one end of a tubular prosthesis having a plurality of resilient tines which support a fabric sealing layer circumferentially thereabout.
- FIG. 19 is a detailed section view taken along line 19 - 19 in FIG. 18.
- the present invention provides methods and apparatus for the implantation of tubular prostheses in body lumens.
- the present invention will find use in the placement of any type of graft or stent in a wide variety of body lumens, including blood vessels, the ureter, the urethra, the biliary tract, and the like.
- the methods and devices will also find use in the creation of temporary or long-term lumens, such as the formation of fistulas.
- the preferred use of the present invention is for the percutaneous placement of endovascular grafts and stents for the treatment of diseases of the vasculature, particularly aneurysms, stenoses, and the like.
- Tubular prostheses will comprise a tubular body having a radially compressed configuration and a radially expanded configuration.
- the tubular prosthesis is introduced to a target size within the body lumen with the tubular body in its radially compressed configuration. After proper placement at the target location, the tubular body will be radially expanded, either by releasing the body to permit self-expansion or by applying a force to the body to cause radial expansion, as described in more detail below.
- the tubular body of the prosthesis will typically have a length in the range from about 30 mm to 500 mm, usually from 80 mm to 200 mm, with an expanded diameter in the range from 2 mm to 45 mm, usually being in the range from 5 mm to 25 mm, and a compressed diameter in the range from 1 mm to 9 mm, usually from 3.5 mm to 7 mm. These dimensions are particularly suitable for graft structures intended for treating vascular aneurysms.
- the tubular body of the prosthesis can have any configuration normally employed for such medical prostheses, including sleeves, lattices, counter-wound helices, braids, slotted tubes, and the like.
- the tubular body may be linear (i.e., in the form of a single cylindrical tube with a first end, a second end, and a lumen therebetween), or branched (i.e., in the form of a “Y” with a first end, a pair of branched, second ends, and lumens therebetween, such as those typically used for aortic aneurysms extending from the abdominal aorta into the iliac arteries), or in any other configuration used for vascular and other luminal prostheses now or in the future.
- the tubular body of the prosthesis can be composed of a wide variety of biologically compatible materials, including metals, organic polymers, and combinations thereof.
- the materials can further be selected or modified to provide a variety of secondary characteristics, such as shape memory, drug delivery, bioabsorbability, radiopaqueness, and the like.
- the tubular body will be composed of two or more different materials in order to provide desired characteristics to the body.
- Such different materials can be incorporated in a variety of ways. For example, different interwoven helices, braids, or other elements can be composed of different materials.
- the interwoven elements can themselves be composed of two or more materials, particularly when the flat ribbons are composed of multiple individual filaments. Additionally, different materials can be laminated over within the body of the tubular prosthesis to provide for desired properties. Preferred materials of construction include tantalum, titanium, nickel-titanium alloy (Nitinol®), polyester (e.g. polyethylene terephthalate), and polytetrafluoroethylene (PTFE).
- the present invention particularly provides for a sealing layer to be disposed over a tubular prosthesis body which has been implanted in the patient's body lumen.
- the sealing layer will provide for an essentially fluid-tight seal over at least one circumferential band disposed in an interface region between the exterior surface of the tubular prosthesis body and an inner wall of the body lumen.
- the sealing layer will fill or cover substantially the entire interface region, but such complete coverage will not always be necessary.
- the sealing layer will usually serve in addition to anchor the prosthesis body in the patient's body lumen.
- the sealing layer may immediately, or over time, assume a generally a solid (although preferably compliant) configuration which both blocks fluid flow (e.g. prevents incursion of fluid into an aneurysm which is being treated with a vascular prosthesis) and which also firmly anchors the prosthesis at the target location.
- an adhesive may be placed over at least a portion of the interface between the sealing layer and the interior of the blood vessel wall.
- the sealing layer which is eventually formed will have a thickness sufficient to provide both the occlusion and anchoring functions described above.
- the thickness of the sealing layer will generally be between about 0.5 mm to 5 mm, usually from 1 mm to 3 mm, depending on the nature of both the sealing layer material and the tubular prosthesis body. For example, gels and foams will typically be thicker than will be adhesives, as described in more detail below.
- the sealing layer may be composed of a wide variety of materials, usually being in the form of a gel, foam, sponge, adhesive, biological polymer, compliant sleeve, microporous mesh, or the like.
- the material may initially be in a fluid (liquid) or semi-solid state, where the material may be at least partially hardened after introduction to the target location within the body lumen and in situ expansion of the tubular prosthesis body.
- the sealing layer material may be hydrophilic, particularly being in the form of a hydrophilic gel or foam, so that it may absorb body fluids to enhance occlusion of the interface region.
- Such hydrophilic materials are often highly compliant and conformable and are particularly suitable for conforming to changes in the shape of the luminal wall which may occur over time.
- the sealing layer may also be in the form of a resilient or elastomeric sleeve which partially or fully occupies the interface region.
- the elastomeric sleeve can be a tubular member, such as an extruded elastomer, which is placed over the tubular prosthesis body before expansion.
- the sleeve could be a self-expanding mechanical assembly formed from a compliant fabric or other material, with internal springs or other mechanisms for providing the desired resilience and thickness.
- Suitable gel materials include hydrogels, particularly acrylates and acrylamides, such as polyacrylamide, polyhydroxyethyl methacrylate, and the like. These materials, which will typically be applied to the exterior surface of the tubular body of the prosthesis prior to expansion, may be formulated to provide for both surface adhesion and swellability. These materials may be applied either in circumferential rings at either single or multiple ends of the tubular graft structure, or to cover substantially the entire outer surface of the tubular prosthesis body.
- Hydrophilic sealing cuffs which absorb water and expand to seal about the periphery of the prosthesis body can be fabricated in a number of ways.
- a water permeable membrane can be made from a woven or knitted material composed of polyester, polyethylene, or polyethyleneterephthalate (PTFE).
- PTFE polyethyleneterephthalate
- a suitable woven PTFE is available under the tradename GORTEX®.
- a hydrogel can be placed inside the water permeable membrane. Suitable hydrogels include polyethylene glycol (PEG)/poly-hydroxyethyl methacrylate (pHEMA), commercially available under the tradename HYDRON®
- Suitable foams include polyurethanes (e.g. open cell polyurethanes), silicones, and the like. Such foams will generally be applied prior to implantation of the tubular prosthesis body, typically using a fluid delivery catheter as described in more detail below.
- Suitable adhesives include acrylates, epoxies (including two-part curable epoxies), fibrin-based adhesives, and other specialized adhesives.
- An exemplary adhesive is a crystalline polymer which changes from a non-tacky crystalline state to an adhesive gel state when the temperature is raised from room temperature to body temperature. Such material is available under the trade name Intillemer® adhesive, available from Landec Corp.
- Suitable biological polymers include proteins, such as collagen, fibrin, fibrinogen, elastin, and the like, which can be either formed over the tubular prosthesis body prior to implantation, or delivered to the target site in the body lumen prior to delivery of the tubular prosthesis body.
- proteins include fibrin-based glues which include both a fibrinogen component and a thrombin component to produce fibrin.
- An exemplary material for the compliant sleeve is microporous silicone rubber, such as that described in U.S. Pat. Nos. 3,890,107 and 5,348,788, the full disclosures of which are incorporated herein by reference.
- Such materials may be molded or machined into sleeves which are disposed between the exterior of the prosthesis and the interior of the lumenal wall.
- the sleeves may be pre-loaded over the tubular prosthesis (i.e., prior to delivery and in situ expansion of the combined prosthesis and sleeve) or may be delivered to and implanted at the target location in the body lumen prior to delivery and in situ expansion of the prosthesis.
- the prosthesis 10 includes a tubular prosthesis body 12 , which is illustrated as a linear, cylindrical prosthesis.
- the prosthesis body 12 is implanted within a sealing layer 14 which conforms to the exterior surface of the prosthesis body 12 and which substantially fills and occludes the annular interface region between the outer surface of the prosthesis body 12 and the inner wall of the blood vessel lumen at each end of the aneurysm A, as best seen in the cross-sectional views of FIGS. 5 and 6.
- the sealing layer 14 may have been applied within the blood vessel lumen prior to implantation of the tubular prosthesis body 12 , or may have been introduced over the exterior of the prosthesis body prior to implantation.
- a prosthesis 20 comprises a tubular prosthesis body 22 (which may be self-expanding or malleable, as generally described above) having a sealing layer 24 formed over its exterior surface.
- the sealing layer 24 may have any of the forms described above, and will be formed over the prosthesis body 22 prior to implantation.
- the sealing layer 24 will be configured to radially expand together with the prosthesis body 22 (optionally by application of an internal expansion force, e.g. applied from an internal balloon catheter), as illustrated in FIG. 8. After radial expansion, the sealing layer 24 will still be sufficiently resilient and conformable to provide for the occlusion of the interface region between the prosthesis and the inner wall of the body lumen.
- FIG. 9 An exemplary branched prosthesis having a “Y”-configuration and constructed in accordance with the principles of the present invention is illustrated in FIG. 9.
- the prosthesis body 32 may be of conventional construction, but includes a circumferential band of sealing material at each of the ends thereof.
- the prosthesis could also have a cross or “X”-configuration where bands of sealing material are provided at one or more of the four branches (not illustrated).
- Catheter 40 designed to deliver fluid or semi-solid phase sealants to interior of a body lumen will be described.
- Catheter 40 includes catheter body 42 having a distal end 44 and a proximal end 46 .
- An outer balloon 48 and inner balloon 50 are coaxially mounted near the distal end 44 of the catheter body 42 .
- the outer balloon 48 is connected through a lumen in body 42 to a first port 52 in proximal housing 54 to receive the fluid or semi-solid phase sealant.
- the inner balloon 50 is connected through a second lumen in catheter body 42 to receive inflation medium through a second port 56 in the proximal hub 54 .
- a fluid or semi-solid sealant may first be delivered to the interior of outer balloon 48 over the inner balloon 50 .
- the sealant may be expelled outward through a plurality of fluid delivery ports 58 disposed substantially uniformly over the outer cylindrical surface of the outer balloon 58 .
- the outer balloon 58 will be formed from a non-compliant material, such as polyethyleneterphthalate.
- the inner balloon 50 is preferably formed from an elastomeric material, such as silicone rubber latex rubber, or polyurethane.
- the catheter body 42 is configured to be introduced over a movable guidewire, including guidewire port 60 extending therethrough.
- fluid delivery catheter 40 is introduced to a region of an aneurysm A in blood vessel BV over a guidewire GW, as illustrated in FIG. 11A.
- the outer balloon 48 is then at least partially filled with a fluid or semi-solid sealant S, as illustrated in FIG. 11B.
- the inner balloon 50 is then expanded to expel the sealant through the ports 58 into the region of aneurysm A, as illustrated in FIG. 11C.
- the catheter 40 After sufficient sealant S has been introduced to the interface region along the inner surface of the blood vessel wall, the catheter 40 will be withdrawn, leaving the sealant S in place, as illustrated in FIG. 11D.
- a graft delivery catheter 60 may then be introduced to the blood vessel BV so that a tubular prosthesis body 62 is positioned within the sealant S, as illustrated in FIG. 11E.
- the prosthesis body 62 As illustrated in FIG. 11E, the prosthesis body 62 is malleable and expanded by an internal balloon 64 . It will be appreciated, however, that the prosthesis body 62 could be in the form of a self-expanding (resilient) tube which is released from radial constraint by a different delivery catheter.
- prosthesis body 62 After the prosthesis body 62 is expanded and/or released, it will compress radially outwardly against the sealant material S to compress and conform the sealant into the interface region, as illustrated in FIG. 11F. Sealant material may then at least partially harden (optionally by applying energy to cure the material) to provide both for occlusion of the interface region (to prevent bypass flow of blood into the aneurysm A) and also to anchor the prosthesis body 62 in place.
- a sealing layer in the form of a bifurcated tube 100 includes a trunk segment 102 and a pair of leg segments 104 and 106 .
- the sleeve 100 will be composed of a resilient, preferably “spongy” material which can be introduced into the base of the abdominal aorta so that the legs 104 and 106 into the right and left iliac arteries, respectively.
- each of the trunk 102 and right and left legs 104 and 106 will comprise structure, such as a self-expanding spring 108 , which will radially expand the sleeve at each of its openings so that the sleeve will self-anchor in the aorta and iliac arteries.
- FIG. 13 shows an alternative 120 which is generally similar to the sleeve 100 , expect that self-expanding tubular elements 122 , 124 , and 126 , are provided in the trunk 128 , leg 130 , and leg 132 respectively.
- These self-expanding tubes are generally similar to the tubular prosthesis structures described previously and provide the necessary mechanical support to anchor the sleeve 120 at the bifurcation of the abdominal aorta into the iliac arteries.
- the sleeve 120 will not itself form the necessary vascular graft over the aneurysm, but rather will form a resilient anchor at the base of the aorta for subsequent implantation of a separate vascular graft, as described in below in connection with FIGS. 14 and 15.
- the preferred material for the sleeves 100 and 120 will be micro porous silicone rubber, as described above.
- the sleeve 100 or 120 can be implanted at the base of an abdominal aortic aneurysm AAA so that the trunk portion 102 or 128 extends into the aorta and the leg portions 104 or 130 and 106 or 132 extend into the right iliac RI and left iliac LI, respectively.
- An upper sleeve anchor 140 will be implanted above the aneurysm AAA and below the renal arteries RA.
- the sleeve 140 will be composed of a similar resilient material, preferably silicone rubber, and will usually be self-expanding so that it can be initially placed at the desired location.
- a vascular prosthesis P which may be any self-expanding or expandable vascular graft as described previously, may then be implanted between the upper sleeve 140 and base sleeve 100 or 120 .
- a simple, linear prosthesis can be used to treat an aortic aneurysm AAA.
- additional prosthesis (not shown) could be implanted in each of the legs 104 / 130 and 106 / 132 of the sleeve in order the further anchor the sleeve and provide desired support within the iliac arteries.
- a sleeve 150 (FIG. 15) could be provided having side branches 152 and 154 which extend into the renal arteries RA. Such a sleeve would be particularly desirable for aneurysms which extend upwardly and approach the renal arteries.
- the tubular prostheses of the present invention will also find use in sealing at one or more ends of a previously implanted prosthesis as shown in FIG. 16.
- a prosthesis 200 (which may be a conventional graft or stent or may itself be a “sealing” prosthesis according to the present invention) is initially implanted in an aneurysm A. Over time, the length of the aneurysm may increase, creating paths at one or both ends for blood to bypass the prosthesis into the aneurysm. This situation may be corrected by implanting additional sealing prosthesis 202 which are constructed in accordance with any of the designs described herein. The prostheses 202 will be disposed inside each end of the initial or central prosthesis 200 into the adjacent lumen of the blood vessel.
- the prostheses 202 are shown to include body 204 and sealing layer 206 , and the sealing layer is able to conform to the end transition between the prosthesis 200 and the blood vessel wall, providing an effective seal against blood bypass and a further anchor of the prosthesis 200 in place. While particularly useful for post-placement sealing, the method of introducing the sealing prostheses into one or more ends of a primary graft would also be useful at the time the primary graft is first introduced.
- a prosthesis 250 comprises a tubular body 252 and an inner liner 254 .
- the tubular body comprises a plurality of spring-like fingers 256 which support an outer liner 258 radially outward.
- the inner liner 254 and outer liner 258 may be composed of the same or different materials, typically being polyester, polytetrafluoroethylene (PTFE), polyurethane, non-woven fabric, polymeric sheet material or the like.
- PTFE polytetrafluoroethylene
- the spring-like fingers will allow the outer liner 258 to conform to the inner wall of the blood vessel to provide sealing as described generally above.
- FIGS. 18 and 19 show yet another alternative construction for a sealing layer according to the present invention.
- the sealing layer comprises a fabric or membrane layer 300 which opens conically about an end 302 of a prosthesis 304 .
- the layer 300 is shown to be supported by a plurality of tines 306 which are connected to the end of the prosthesis 304 .
- the tines 306 are formed integrally as part of a metallic framework 310 of the prosthesis, but it will be appreciated that the tines could be welded or otherwise attached to the framework.
- a fabric liner 316 is shown to be folded from the interior of the prosthesis back into and over a V-shaped cavity 318 defined by the tines 306 .
- the layer 300 upon deployment in a blood vessel, the layer 300 will engage and conform to the interior surface of the vessel and the layer will seal the end of the prosthesis 304 to inhibit by-pass blood flow. It will be further appreciated that the sealing layer 300 could be formed in a variety of other specific designs, including an unsupported or partially supported fabric or membrane which is held open to seal against the blood vessel wall by the blood flow itself which applies pressure within the cavity 318 .
Abstract
A tubular prosthesis is implanted at a target location within a body lumen by transluminally placing and embedding an expansible prosthesis body within a sealing layer. The sealing layer occludes at least a circumferential band within an interface region between the prosthesis body and the inner wall of the body lumen, thus providing for blockage of body lumen flow past the prosthesis. The sealing layer may be introduced prior to or simultaneously with the prosthesis body. A tubular prosthesis may be implanted in blood vessels, particularly to protect aneurysms.
Description
- The present application is a divisional of, and claims the benefit under 35 U.S.C. § 120 of, U.S. application Ser. No. 09/008,686, filed Jan. 16, 1998, which is a divisional of U.S. application Ser. No. 08/525,989, filed Sep. 8, 1995 that issued as U.S. Pat. No. 5,769,882. The disclosure of each of these related applications is incorporated by reference in its entirety herein.
- 1. Field of the Invention
- The present invention relates generally to methods and apparatus for the endoluminal placement of tubular prostheses, such as grafts, stents, and other structures. More particularly, the present invention relates to the implantation of luminal prostheses in a sealing layer within a body lumen.
- Vascular aneurysms are the result of abnormal dilation of a blood vessel, usually resulting from disease and/or genetic predisposition which can weaken the arterial wall and allow it to expand. While aneurysms can occur in any blood vessel, most occur in the aorta and peripheral arteries, with the majority of aortic aneurysms occurring in the abdominal aorta, usually beginning below the renal arteries and often extending distally into one or both of the iliac arteries.
- Aortic aneurysms are most commonly treated in open surgical procedures where the diseased vessel segment is bypassed and repaired with an artificial vascular graft. While considered to be an effective surgical technique, particularly considering the alternative of a usually fatal ruptured abdominal aortic aneurysm, conventional vascular graft surgery suffers from a number of disadvantages. The surgical procedure is complex and requires experienced surgeons and well-equipped surgical facilities. Even with the best surgeons and equipment, however, the patients being treated frequently are elderly and weakened from cardiovascular and other diseases, reducing the number of eligible patients. Even for eligible patients, conventional aneurysm repair surgery performed prior to rupture has a relatively high mortality rate, usually from 2% to 10%. Morbidity related to the conventional surgery includes myocardial infarction, renal failure, impotence, paralysis, and other conditions. Additionally, even with successful surgery, recovery can take several weeks and often requires a lengthy hospital stay.
- In order to overcome some or all of these drawbacks, endovascular graft placement procedures for the treatment of aneurysms have been proposed. Generally, such endovascular procedures will deliver a radially compressed graft intravascularly to the aneurysm. The graft is then expanded in situ, either by releasing a self-expanding graft or by internally expanding a malleable graft (e.g. using a balloon catheter) to protect the aneurysm. Usually, the vascular graft will comprise both a frame and a liner, where the frame provides the necessary mechanical support and the liner provides the necessary blood barrier.
- While highly promising, the endovascular placement of vascular grafts is problematic in several respects. In contrast to surgically implanted grafts, which are sutured in place, endovascularly placed grafts can be difficult to anchor and position. Reliance on the outward spring-force of a self-expanding graft is not always sufficient. Malleable grafts, in contrast, may be easier to initially anchor but may be less able to expand and contract with the blood vessel during the continuous pulse of the patient. While the use of hooks or barbs for anchoring grafts into the blood vessel wall has been proposed, such devices can be traumatic and can loosen from the blood vessel wall over time. As the anchoring of the vascular prosthesis loosens over time, blood can begin to bypass the graft and flow into the region between the graft and the blood vessel wall. Such misdirected blood flow into the aneurysm can again expose the patient to risk of aneurysm rupture and its consequences. Additionally, heretofore, it has been difficult to radially reinforce both self-expanding and malleable graft structures to help in maintaining the structures within the blood vessel.
- Referring to Prior Art FIGS.1-3, the problem of blood flow leakage past a
graft structure 10 implanted within the region of an aneurysm A in a blood vessel BV is illustrated. While thegraft 10 may be adequately anchored on each side of the aneurysm A, as illustrated in FIG. 1, over time the inner surface of the blood vessel lumen can partially separate from the outer surface of thegraft 10, as illustrated in FIGS. 2 and 3. Such separations S can allow bypass blood flow into the region of the aneurysm A. - For these reasons, it would be desirable to provide improved luminal prostheses and methods for their implantation which can overcome at least some of the difficulties described above. In particular, it would be desirable to provide intraluminal prostheses and methods for their implantation which would provide a generally fluid tight seal circumscribing at least one end of the prosthesis, and preferably both ends or the entire length of the prosthesis, to prevent bypass blood or other fluid flow into the interstitial region between the inner wall of the body lumen and the outer surface of the prosthesis. In particular, it would be desirable if such improved prostheses and methods for their implantation would provide for sealing of the prosthesis which would resist separating from the intraluminal wall in order to prevent such bypass flow in a long-term or permanent fashion after implantation of the prosthesis. In some cases, it will be desirable to provide methods which permit such sealing implantation when using otherwise conventional prosthesis structures, such as vascular stents and grafts. In other cases, it will be desirable to provide improved prosthesis structures which incorporate features which provide for such sealing implantation when implanted using methods according to present invention.
- 2. Description of the Background Art
- The delivery of polymerizable fluids to body tissues for a variety of purposes, including “paving” of vascular lumens, has been proposed. See, for example, PCT Publications WO 94/24962 and WO 94/21324, and U.S. Pat. No. 5,092,841. Luminal prostheses which are delivered in a compliant state and hardened in situ by exposure to heat, radiation, or other polymerization-initiating event are described in U.S. Pat. Nos. 5,344,444; 5,334,201; and 5,100,429; EP 521573; and de Vries et al., “Instant Tubular Prosthesis: A Totally New Concept,”International Congress VII Endovascular Interventions, Phoenix, Ariz., February 1994. A fabric prosthesis which is secured to an inner vascular wall by a contact adhesive, such as cyanoacrylate, is described in U.S. Pat. No. 4,577,631. The use of autologous fibrin glue for sealing porous, fabric grafts prior to open surgical implantation is described in Kjaergard and Weis-Fogh (1994) Card. Surg. 2:45-46. A tubular prosthesis having an annular cavity for receiving a plastic material to enlarge and anchor the prosthesis within a blood vessel is described in U.S. Pat. No. 5,156,620. A tubular prosthesis having inflatable cuffs on each end is described in U.S. Pat. No. 3,991,767. A tubular prosthesis having everted cuffs for receiving sutures is described in U.S. Pat. No. 4,728,328. A tubular stent having hook-like projections over its outer surface is described in U.S. Pat. No. 5,167,614. A tubular stent having a plurality of self-locking fingers extending outward from its outer surface is described in U.S. Pat. No. 5,344,426. A fluid delivery catheter comprising concentric lumens in a balloon structure is described in U.S. Pat. No. 5,295,962. A vascular prosthesis comprising two porous concentrically associated tubes with a helical spring enclosed therebetween is disclosed in U.S. Pat. No. 4,130,904. A vascular prosthesis comprising a multilaminar tubular member is disclosed in U.S. Pat. No. 5,354,329. Microporous materials suitable for the fabrication of prosthetic devices are described in U.S. Pat. Nos. 3,890,107 and 5,348,788.
- The present invention provides methods and apparatus for the transluminal positioning of tubular prostheses at a target location within a body lumen. The tubular prostheses are suitable for a wide variety of therapeutic uses, including stenting of the ureter, urethra, biliary tract, and the like. The devices and methods will also find use in the creation of temporary or long-term lumens, such as the formation of fistulas. The present invention will find its greatest use, however, in the placement of endovascular grafts into blood vessels for the treatment of abdominal and other aneurysms, vascular stenoses, and the like.
- According to the method of the present invention, a tubular prosthesis is delivered to the target site within the body lumen in a radially compressed configuration and is expanded in situ at the target location so that an exterior surface of the prosthesis engages an inner wall of the body lumen over an interface region therebetween. Radial expansion of the prosthesis may be effected in any conventional manner, including the use of a balloon catheter for expanding malleable prostheses, the release of compressed, self-expanding prostheses from suitable delivery catheters, and the like. The present invention particularly provides for expansion of the prostheses into a sealing layer which is disposed in or over at least a portion of the interface region.
- The sealing layer may be disposed within substantially the entire interface region, or may be disposed over one or more discrete, circumferential bands within the interface region. Usually, the sealing layer will be disposed at least at each end of the tubular prosthesis in order to provide a barrier against the bypass leakage of fluid into portions of the interface region therebetween. Preferably, the sealing layer will occupy substantially the entire interface region.
- The sealing layer may be composed of virtually any material which is biocompatable and capable of conforming to the interface region between the outer wall of the tubular prosthesis and the inner wall of the body lumen. Exemplary materials include gels, foams, adhesives, biological polymers, compliant sleeves, sponges, porous matrices and meshes, and the like. In some cases, the materials are initially present on the prosthesis or delivered in a fluid or semi-solid state to the interface region, and thereafter cured or hardened to achieve the final, desired geometry. Additionally, the sealing layer may be composed of materials which expand in situ in order to fully conform to the geometry of the interface region, e.g. including materials such as hydrophilic gels, hydrophilic foams, and the like. An exemplary material for the sealing layer comprises a microporous mesh, particularly composed of silicone rubber and similar materials.
- In a first particular aspect of the present invention, the sealing layer may be initially formed or disposed over at least a portion of the exterior surface of the tubular prosthesis prior to in situ expansion. In such cases, the tubular prosthesis will usually be pre-coated or covered with the material of the sealing layer prior to introduction of the prosthesis to the body lumen.
- In a second particular aspect of the method of the present invention, the material of the sealing layer may be introduced in an initial step prior to introduction of the tubular prosthesis. Usually, a fluid delivery catheter will be employed to apply the sealing layer material in a fluid or semi-solid state over at least a portion of the interface region. The fluid delivery catheter is removed, and a prosthesis delivery catheter is then introduced to the target location. The prosthesis carried by the catheter may then be expanded in situ so that it engages and conforms to the material of the sealing layer.
- Apparatus according to the present invention includes tubular prostheses comprising an expansible tubular frame having a sealing layer formed at least partially over an exterior surface thereof. The sealing layer may be formed of any of the materials described above.
- The apparatus according to the present invention further includes a fluid delivery catheter comprising a catheter body having a proximal end and a distal end. An outer balloon and an inner balloon are disposed on the catheter near its distal end. The outer balloon is positioned over the inner balloon and includes a plurality of fluid delivery ports formed over its surface. The outer balloon is connected to a first lumen within the catheter body and can receive a fluid or semi-solid sealing material therethrough. The inner balloon is connected to a second lumen within the catheter body and can receive an expansion medium therethrough. By first filling the outer balloon with the fluid or semi-solid sealing material, and thereafter expanding the inner balloon within the outer balloon, the sealing material is extruded outwardly through the fluid delivery ports in an annuler layer over the inner surface of the luminal wall. The prosthesis may then be delivered to the body lumen and expanded so that it becomes embedded in the layer of sealing material. The sealing material hardens, optionally with the application of energy conforming to the exterior of the prosthesis and providing a substantially permanent anchor and barrier to the bypass of body fluid.
- FIGS.1-3 illustrate prior art implantation of a vascular prosthesis.
- FIG. 4 is a cross-sectional view of a vascular prosthesis embedded in a sealing layer in the region of an aneurysm according to the present invention.
- FIG. 5 is a cross-sectional view taken along line5-5 of FIG. 4.
- FIG. 6 is a cross-sectional view taken along line6-6 of FIG. 4.
- FIG. 7 illustrates a tubular prosthesis constructed in accordance with the principles of the present invention, in a radially compressed configuration.
- FIG. 8 illustrates the tubular prosthesis of FIG. 7 in a radially expanded configuration.
- FIG. 9 illustrates a bifurcated prosthesis constructed in accordance with the principles of the present invention.
- FIG. 10 illustrates a fluid delivery catheter intended for the intraluminal delivery of a sealing material for use in the methods of the present invention.
- FIGS.11A-11F illustrate a particular embodiment of the method of the present invention employing an initial sealing material delivery step followed by a separate prosthesis implantation step.
- FIG. 12 illustrates a first embodiment of a sealing sleeve intended for implantation at the bifurcation of the abdominal aorta into the left and right iliac arteries.
- FIG. 13 is an alternate embodiment of a sealing sleeve for implantation at the bifurcation of the abdominal aorta into the right and left iliac arteries.
- FIG. 14 illustrates the implantation of a vascular graft between a pair of sealing sleeves to treat an abdominal aortic aneurysm.
- FIG. 15 illustrates an alternative anchoring of the vascular graft of FIG. 14 with a sealing sleeve which extends into the renal arteries.
- FIG. 16 illustrates use of the vascular prosthesis of the present invention for sealing at each end of a previously implanted prosthesis.
- FIG. 17 illustrates an alternative embodiment of the sealing prosthesis of the present invention.
- FIG. 18 illustrates one end of a tubular prosthesis having a plurality of resilient tines which support a fabric sealing layer circumferentially thereabout.
- FIG. 19 is a detailed section view taken along line19-19 in FIG. 18.
- The present invention provides methods and apparatus for the implantation of tubular prostheses in body lumens. The present invention will find use in the placement of any type of graft or stent in a wide variety of body lumens, including blood vessels, the ureter, the urethra, the biliary tract, and the like. The methods and devices will also find use in the creation of temporary or long-term lumens, such as the formation of fistulas. The preferred use of the present invention, however, is for the percutaneous placement of endovascular grafts and stents for the treatment of diseases of the vasculature, particularly aneurysms, stenoses, and the like.
- Tubular prostheses according to the present invention will comprise a tubular body having a radially compressed configuration and a radially expanded configuration. The tubular prosthesis is introduced to a target size within the body lumen with the tubular body in its radially compressed configuration. After proper placement at the target location, the tubular body will be radially expanded, either by releasing the body to permit self-expansion or by applying a force to the body to cause radial expansion, as described in more detail below.
- The tubular body of the prosthesis will typically have a length in the range from about 30 mm to 500 mm, usually from 80 mm to 200 mm, with an expanded diameter in the range from 2 mm to 45 mm, usually being in the range from 5 mm to 25 mm, and a compressed diameter in the range from 1 mm to 9 mm, usually from 3.5 mm to 7 mm. These dimensions are particularly suitable for graft structures intended for treating vascular aneurysms.
- The tubular body of the prosthesis can have any configuration normally employed for such medical prostheses, including sleeves, lattices, counter-wound helices, braids, slotted tubes, and the like. The tubular body may be linear (i.e., in the form of a single cylindrical tube with a first end, a second end, and a lumen therebetween), or branched (i.e., in the form of a “Y” with a first end, a pair of branched, second ends, and lumens therebetween, such as those typically used for aortic aneurysms extending from the abdominal aorta into the iliac arteries), or in any other configuration used for vascular and other luminal prostheses now or in the future.
- Configurations suitable for use as the tubular body component of the tubular prostheses of the present invention are well described in the patent and medical literature. See, for example, U.S. Pat. Nos. 5,219,355; 5,211,658; 5,104,399; 5,078,726; 4,820,298; 4,787,899; 4,617,932; 4,562,596; 4,577,631; and 4,140,126, the full disclosures of which are incorporated herein by reference. Preferred constructions for the tubular body of the present invention are described in copending application Ser. No. 08/255,681, filed on Jun. 8, 1994, and Ser. No. 08/414,995, filed on Mar. 31, 1995 that issued as U.S. Pat. No. 5,709,713, the full disclosures of which are incorporated herein by reference.
- The tubular body of the prosthesis can be composed of a wide variety of biologically compatible materials, including metals, organic polymers, and combinations thereof. The materials can further be selected or modified to provide a variety of secondary characteristics, such as shape memory, drug delivery, bioabsorbability, radiopaqueness, and the like. Frequently, the tubular body will be composed of two or more different materials in order to provide desired characteristics to the body. For example, it may be desirable to fabricate the tubular body both from organic polymers, which can provide flexibility and impermeability, and from metallic elements which can provide self-expansion, resilience, and structural integrity. Such different materials can be incorporated in a variety of ways. For example, different interwoven helices, braids, or other elements can be composed of different materials. Alternatively or additionally, the interwoven elements can themselves be composed of two or more materials, particularly when the flat ribbons are composed of multiple individual filaments. Additionally, different materials can be laminated over within the body of the tubular prosthesis to provide for desired properties. Preferred materials of construction include tantalum, titanium, nickel-titanium alloy (Nitinol®), polyester (e.g. polyethylene terephthalate), and polytetrafluoroethylene (PTFE).
- The present invention particularly provides for a sealing layer to be disposed over a tubular prosthesis body which has been implanted in the patient's body lumen. The sealing layer will provide for an essentially fluid-tight seal over at least one circumferential band disposed in an interface region between the exterior surface of the tubular prosthesis body and an inner wall of the body lumen. Often, the sealing layer will fill or cover substantially the entire interface region, but such complete coverage will not always be necessary. Sometimes, it will be sufficient to form only a single band of the sealing layer material at one or both ends of a linear prosthesis body, or at one, two, or three ends of a bifurcated prosthesis body.
- In addition to at least partially occluding the interface region between the tubular prosthesis body and the body lumen, the sealing layer will usually serve in addition to anchor the prosthesis body in the patient's body lumen. Thus, the sealing layer may immediately, or over time, assume a generally a solid (although preferably compliant) configuration which both blocks fluid flow (e.g. prevents incursion of fluid into an aneurysm which is being treated with a vascular prosthesis) and which also firmly anchors the prosthesis at the target location. Optionally, an adhesive may be placed over at least a portion of the interface between the sealing layer and the interior of the blood vessel wall.
- The sealing layer which is eventually formed will have a thickness sufficient to provide both the occlusion and anchoring functions described above. The thickness of the sealing layer will generally be between about 0.5 mm to 5 mm, usually from 1 mm to 3 mm, depending on the nature of both the sealing layer material and the tubular prosthesis body. For example, gels and foams will typically be thicker than will be adhesives, as described in more detail below.
- The sealing layer may be composed of a wide variety of materials, usually being in the form of a gel, foam, sponge, adhesive, biological polymer, compliant sleeve, microporous mesh, or the like. The material may initially be in a fluid (liquid) or semi-solid state, where the material may be at least partially hardened after introduction to the target location within the body lumen and in situ expansion of the tubular prosthesis body. Additionally, the sealing layer material may be hydrophilic, particularly being in the form of a hydrophilic gel or foam, so that it may absorb body fluids to enhance occlusion of the interface region. Such hydrophilic materials are often highly compliant and conformable and are particularly suitable for conforming to changes in the shape of the luminal wall which may occur over time. In contrast to the fluid and semi-solid materials, the sealing layer may also be in the form of a resilient or elastomeric sleeve which partially or fully occupies the interface region. The elastomeric sleeve can be a tubular member, such as an extruded elastomer, which is placed over the tubular prosthesis body before expansion. Alternatively, the sleeve could be a self-expanding mechanical assembly formed from a compliant fabric or other material, with internal springs or other mechanisms for providing the desired resilience and thickness.
- Suitable gel materials include hydrogels, particularly acrylates and acrylamides, such as polyacrylamide, polyhydroxyethyl methacrylate, and the like. These materials, which will typically be applied to the exterior surface of the tubular body of the prosthesis prior to expansion, may be formulated to provide for both surface adhesion and swellability. These materials may be applied either in circumferential rings at either single or multiple ends of the tubular graft structure, or to cover substantially the entire outer surface of the tubular prosthesis body.
- Hydrophilic sealing cuffs which absorb water and expand to seal about the periphery of the prosthesis body can be fabricated in a number of ways. For example, a water permeable membrane can be made from a woven or knitted material composed of polyester, polyethylene, or polyethyleneterephthalate (PTFE). A suitable woven PTFE is available under the tradename GORTEX®. A hydrogel can be placed inside the water permeable membrane. Suitable hydrogels include polyethylene glycol (PEG)/poly-hydroxyethyl methacrylate (pHEMA), commercially available under the tradename HYDRON®
- Suitable foams include polyurethanes (e.g. open cell polyurethanes), silicones, and the like. Such foams will generally be applied prior to implantation of the tubular prosthesis body, typically using a fluid delivery catheter as described in more detail below.
- Suitable adhesives include acrylates, epoxies (including two-part curable epoxies), fibrin-based adhesives, and other specialized adhesives. An exemplary adhesive is a crystalline polymer which changes from a non-tacky crystalline state to an adhesive gel state when the temperature is raised from room temperature to body temperature. Such material is available under the trade name Intillemer® adhesive, available from Landec Corp.
- Suitable biological polymers include proteins, such as collagen, fibrin, fibrinogen, elastin, and the like, which can be either formed over the tubular prosthesis body prior to implantation, or delivered to the target site in the body lumen prior to delivery of the tubular prosthesis body. Specific examples of the proteins include fibrin-based glues which include both a fibrinogen component and a thrombin component to produce fibrin.
- An exemplary material for the compliant sleeve is microporous silicone rubber, such as that described in U.S. Pat. Nos. 3,890,107 and 5,348,788, the full disclosures of which are incorporated herein by reference. Such materials may be molded or machined into sleeves which are disposed between the exterior of the prosthesis and the interior of the lumenal wall. The sleeves may be pre-loaded over the tubular prosthesis (i.e., prior to delivery and in situ expansion of the combined prosthesis and sleeve) or may be delivered to and implanted at the target location in the body lumen prior to delivery and in situ expansion of the prosthesis.
- Referring now to FIGS.4-6, implantation of a
vascular prosthesis 10 within an aneurysm A in a blood vessel BV will be described. Theprosthesis 10 includes atubular prosthesis body 12, which is illustrated as a linear, cylindrical prosthesis. Theprosthesis body 12 is implanted within asealing layer 14 which conforms to the exterior surface of theprosthesis body 12 and which substantially fills and occludes the annular interface region between the outer surface of theprosthesis body 12 and the inner wall of the blood vessel lumen at each end of the aneurysm A, as best seen in the cross-sectional views of FIGS. 5 and 6. Thesealing layer 14 may have been applied within the blood vessel lumen prior to implantation of thetubular prosthesis body 12, or may have been introduced over the exterior of the prosthesis body prior to implantation. - Referring now to FIGS. 7 and 8, a
prosthesis 20 comprises a tubular prosthesis body 22 (which may be self-expanding or malleable, as generally described above) having asealing layer 24 formed over its exterior surface. Thesealing layer 24 may have any of the forms described above, and will be formed over theprosthesis body 22 prior to implantation. Thus, thesealing layer 24 will be configured to radially expand together with the prosthesis body 22 (optionally by application of an internal expansion force, e.g. applied from an internal balloon catheter), as illustrated in FIG. 8. After radial expansion, thesealing layer 24 will still be sufficiently resilient and conformable to provide for the occlusion of the interface region between the prosthesis and the inner wall of the body lumen. - An exemplary branched prosthesis having a “Y”-configuration and constructed in accordance with the principles of the present invention is illustrated in FIG. 9. The
prosthesis body 32 may be of conventional construction, but includes a circumferential band of sealing material at each of the ends thereof. The prosthesis could also have a cross or “X”-configuration where bands of sealing material are provided at one or more of the four branches (not illustrated). - Referring now to FIG. 10, a
catheter 40 designed to deliver fluid or semi-solid phase sealants to interior of a body lumen will be described.Catheter 40 includescatheter body 42 having adistal end 44 and aproximal end 46. Anouter balloon 48 andinner balloon 50 are coaxially mounted near thedistal end 44 of thecatheter body 42. Theouter balloon 48 is connected through a lumen inbody 42 to afirst port 52 inproximal housing 54 to receive the fluid or semi-solid phase sealant. Theinner balloon 50 is connected through a second lumen incatheter body 42 to receive inflation medium through asecond port 56 in theproximal hub 54. In this way, a fluid or semi-solid sealant may first be delivered to the interior ofouter balloon 48 over theinner balloon 50. By then inflating theinner balloon 50, the sealant may be expelled outward through a plurality offluid delivery ports 58 disposed substantially uniformly over the outer cylindrical surface of theouter balloon 58. Preferably, theouter balloon 58 will be formed from a non-compliant material, such as polyethyleneterphthalate. Theinner balloon 50 is preferably formed from an elastomeric material, such as silicone rubber latex rubber, or polyurethane. Thecatheter body 42 is configured to be introduced over a movable guidewire, includingguidewire port 60 extending therethrough. - Referring now to FIGS.11A-11F, a method for delivering a vascular prosthesis according to the present invention will be described. Initially,
fluid delivery catheter 40 is introduced to a region of an aneurysm A in blood vessel BV over a guidewire GW, as illustrated in FIG. 11A. Theouter balloon 48 is then at least partially filled with a fluid or semi-solid sealant S, as illustrated in FIG. 11B. Theinner balloon 50 is then expanded to expel the sealant through theports 58 into the region of aneurysm A, as illustrated in FIG. 11C. - After sufficient sealant S has been introduced to the interface region along the inner surface of the blood vessel wall, the
catheter 40 will be withdrawn, leaving the sealant S in place, as illustrated in FIG. 11D. Agraft delivery catheter 60 may then be introduced to the blood vessel BV so that atubular prosthesis body 62 is positioned within the sealant S, as illustrated in FIG. 11E. As illustrated in FIG. 11E, theprosthesis body 62 is malleable and expanded by aninternal balloon 64. It will be appreciated, however, that theprosthesis body 62 could be in the form of a self-expanding (resilient) tube which is released from radial constraint by a different delivery catheter. Other delivery techniques, such as axial contraction to cause radial expansion of the prosthesis, are also known and could be employed with the present invention. In any case, after theprosthesis body 62 is expanded and/or released, it will compress radially outwardly against the sealant material S to compress and conform the sealant into the interface region, as illustrated in FIG. 11F. Sealant material may then at least partially harden (optionally by applying energy to cure the material) to provide both for occlusion of the interface region (to prevent bypass flow of blood into the aneurysm A) and also to anchor theprosthesis body 62 in place. - Referring now to FIG. 12, a sealing layer in the form of a
bifurcated tube 100 includes atrunk segment 102 and a pair ofleg segments sleeve 100 will be composed of a resilient, preferably “spongy” material which can be introduced into the base of the abdominal aorta so that thelegs trunk 102 and right and leftlegs spring 108, which will radially expand the sleeve at each of its openings so that the sleeve will self-anchor in the aorta and iliac arteries. FIG. 13 shows an alternative 120 which is generally similar to thesleeve 100, expect that self-expandingtubular elements leg 130, andleg 132 respectively. These self-expanding tubes are generally similar to the tubular prosthesis structures described previously and provide the necessary mechanical support to anchor thesleeve 120 at the bifurcation of the abdominal aorta into the iliac arteries. Thesleeve 120, however, will not itself form the necessary vascular graft over the aneurysm, but rather will form a resilient anchor at the base of the aorta for subsequent implantation of a separate vascular graft, as described in below in connection with FIGS. 14 and 15. The preferred material for thesleeves - Referring now to FIG. 14, the
sleeve trunk portion 102 or 128 extends into the aorta and theleg portions upper sleeve anchor 140 will be implanted above the aneurysm AAA and below the renal arteries RA. Thesleeve 140 will be composed of a similar resilient material, preferably silicone rubber, and will usually be self-expanding so that it can be initially placed at the desired location. A vascular prosthesis P which may be any self-expanding or expandable vascular graft as described previously, may then be implanted between theupper sleeve 140 andbase sleeve legs 104/130 and 106/132 of the sleeve in order the further anchor the sleeve and provide desired support within the iliac arteries. - As an alternative to the
upper sleeve 140, a sleeve 150 (FIG. 15) could be provided havingside branches - The tubular prostheses of the present invention will also find use in sealing at one or more ends of a previously implanted prosthesis as shown in FIG. 16. There, a prosthesis200 (which may be a conventional graft or stent or may itself be a “sealing” prosthesis according to the present invention) is initially implanted in an aneurysm A. Over time, the length of the aneurysm may increase, creating paths at one or both ends for blood to bypass the prosthesis into the aneurysm. This situation may be corrected by implanting
additional sealing prosthesis 202 which are constructed in accordance with any of the designs described herein. Theprostheses 202 will be disposed inside each end of the initial orcentral prosthesis 200 into the adjacent lumen of the blood vessel. Theprostheses 202 are shown to includebody 204 and sealinglayer 206, and the sealing layer is able to conform to the end transition between theprosthesis 200 and the blood vessel wall, providing an effective seal against blood bypass and a further anchor of theprosthesis 200 in place. While particularly useful for post-placement sealing, the method of introducing the sealing prostheses into one or more ends of a primary graft would also be useful at the time the primary graft is first introduced. - An alternative sealing layer construction is shown in FIG. 17. A
prosthesis 250 comprises atubular body 252 and aninner liner 254. The tubular body comprises a plurality of spring-like fingers 256 which support anouter liner 258 radially outward. Theinner liner 254 and outer liner 258-may be composed of the same or different materials, typically being polyester, polytetrafluoroethylene (PTFE), polyurethane, non-woven fabric, polymeric sheet material or the like. Generally the liners should present a barrier to blood flow therethrough. The spring-like fingers will allow theouter liner 258 to conform to the inner wall of the blood vessel to provide sealing as described generally above. - FIGS. 18 and 19 show yet another alternative construction for a sealing layer according to the present invention. The sealing layer comprises a fabric or
membrane layer 300 which opens conically about anend 302 of aprosthesis 304. Thelayer 300 is shown to be supported by a plurality oftines 306 which are connected to the end of theprosthesis 304. As illustrated, thetines 306 are formed integrally as part of ametallic framework 310 of the prosthesis, but it will be appreciated that the tines could be welded or otherwise attached to the framework. In the embodiment of FIGS. 17 and 18, afabric liner 316 is shown to be folded from the interior of the prosthesis back into and over a V-shapedcavity 318 defined by thetines 306. It will be appreciated that, upon deployment in a blood vessel, thelayer 300 will engage and conform to the interior surface of the vessel and the layer will seal the end of theprosthesis 304 to inhibit by-pass blood flow. It will be further appreciated that thesealing layer 300 could be formed in a variety of other specific designs, including an unsupported or partially supported fabric or membrane which is held open to seal against the blood vessel wall by the blood flow itself which applies pressure within thecavity 318. - Although the foregoing invention has been described in some detail by way of illustration and example, for purposes of clarity of understanding, it will be obvious that certain changes and modifications may be practiced within the scope of the appended claims.
Claims (31)
1. In a method for implanting a tubular prosthesis in a body lumen of the type wherein the tubular prosthesis is expanded in situ so that an exterior surface of the prosthesis engages an inner wall of the body lumen over an interface region, the improvement comprising expanding the tubular prosthesis, in a sealing layer disposed in at least a portion of the interface region.
2. A method as in claim 1 , wherein the tubular prosthesis has at least a first end, a second end, and a lumen therebetween, and wherein the sealing layer is disposed over at least one circumferential band within the interface region.
3. A method as in claim 2 , wherein the sealing layer is disposed within substantially the entire interface region.
4. A method as in claim 1 , wherein the tubular prosthesis has a first end and a pair of branched second ends with lumens therebetween, and wherein the sealing layer is disposed over at least a circumferential band within the interface region near the first end.
5. A method as in claim 4 , wherein the sealing layer is disposed over substantially the entire interface region.
6. A method as in claim 1 , wherein the sealing layer is selected from the group consisting of gels, foams, sponges, adhesives, biological polymers, microporous meshes, and a self-expanding mechanical assembly.
7. A method as in claim 6 , wherein the sealing layer is a microporous silicone rubber mesh.
8. A method as in claim 1 , wherein the sealing layer is disposed over at least a portion of the exterior surface of the tubular prosthesis prior to in situ expansion.
9. A method as in claim 1 , wherein the improvement further comprises introducing the sealing layer within the body lumen prior to in situ expansion of the tubular prosthesis.
10. A method for implanting a tubular prosthesis in a body lumen, said method comprising:
introducing a sealing layer over an interface region along an interior wall of the body lumen; and
expanding a tubular prosthesis within the body lumen so that the sealing layer provides a seal between an exterior surface of the tubular prosthesis and the interior wall of the body lumen.
11. A method as in claim 10 , wherein the sealing layer introducing step comprises transluminally positioning a distal end of a catheter at the interface region within the body lumen and applying a fluid phase sealing material from the distal end of the catheter over said interface region.
12. A method as in claim 11 , wherein the fluid phase sealing material is selected from the group consisting of gels, foams, adhesives, and biological polymers.
13. A method as in claim 10 , wherein the tubular prosthesis expanding step comprises transluminally positioning a distal end of a catheter near the sealing layer within the body lumen and releasing a radially constrained, self-expanding prosthesis within said sealing layer.
14. A method as in claim 10 , wherein the tubular prosthesis expanding step comprises transluminally positioning a distal end of a catheter near the sealing layer within the body lumen and inflating a balloon on the catheter to expand an at least partially malleable prosthesis within said sealing layer.
15. An improved tubular prosthesis of the type including an expansible tubular frame, wherein the improvement comprises a sealing layer formed over at least a portion of the exterior surface of the tubular frame, said sealing layer being expansible together with the tubular frame and capable of forming a liquid-resistant barrier over an annular exterior segment of the frame after expansion when implanted in a body lumen.
16. An improved tubular prosthesis as in claim 15 , wherein the expansible tubular frame is at least partly resilient so that it can be released from radial constraint to assume a large diameter configuration.
17. An improved tubular prosthesis as in claim 15 , wherein the expansible tubular frame is at least partly malleable so that it can be radially expanded by application of an internal expansion force.
18. An improved tubular prosthesis as in claim 15 , wherein the sealing layer is selected from the group consisting of gels, foams, adhesives biological polymers, sponges, compliant sleeves, microporous meshes, and a self-expanding mechanical assembly.
19. An improved tubular prosthesis as in claim 18 , wherein the sealing layer is a microporous silicone rubber mesh.
20. An improved tubular prosthesis as in claim 15 , wherein the sealing layer is disposed over at least a circumferential band of the exterior surface of the tubular frame.
21. An improved tubular prosthesis as in claim 20 , wherein the sealing layer is disposed over substantially the entire exterior surface.
22. A fluid delivery catheter, said catheter comprising:
a catheter body having a proximal and a distal end, and at least two lumens extending therebetween;
an outer balloon disposed near the distal end of the catheter body and having fluid delivery ports formed therein, said outer balloon being connected to receive a fluid from a first of the lumens; and
an inner balloon disposed on the catheter body within the outer balloon and connected to receive an inflation medium from a second of the lumens, wherein expansion of the inner balloon will expel fluid within the outer balloon outwardly through the delivery ports.
23. A fluid delivery catheter as in claim 22 , wherein the outer balloon is non-compliant and the inner balloon is elastic.
24. A fluid delivery catheter as in claim 23 , wherein the outer balloon has a generally cylindrical profile when expanded and wherein the delivery ports are substantially uniformly distributed over an outer cylindrical wall thereof.
25. A, fluid delivery catheter as in claim 22 , wherein the fluid delivery ports have sufficient flow resistance to inhibit fluid flow in the absence of internal pressure provided by the inner balloon.
26. A method for delivering a fluid to an inner wall of a body lumen, said method comprising:
positioning an outer balloon at a target site within the body lumen;
at least partially filling the outer balloon with a fluid material to be delivered; and
inflating an inner balloon within the outer balloon to expel the fluid material through fluid delivery ports formed in the outer balloon.
27. A method as in claim 26 , wherein the body lumen is a blood vessel and the target site is a location which is to receive a tubular prosthesis.
28. A method as in claim 27 , wherein the site is proximate an aneurysm.
29. A method as in claim 26 , wherein the outer balloon is filled with a material selected from the group consisting of gels, foams, adhesives, and biological polymers.
30. A method as in claim 29 , wherein the outer balloon is filled sufficient to engage its outer surface against an interior wall of the body lumen without substantial loss of fluid material through the delivery ports prior to expansion of the inner balloon.
31. A method as in claim 30 , wherein the inner balloon is elastic and is inflated sufficiently to conform to the inner wall of the outer balloon to expel substantially all fluid through the delivery ports.
Priority Applications (1)
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US10/712,376 US20040098097A1 (en) | 1995-09-08 | 2003-11-14 | Methods and apparatus for conformably sealing prostheses within body lumens |
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Application Number | Priority Date | Filing Date | Title |
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US08/525,989 US5769882A (en) | 1995-09-08 | 1995-09-08 | Methods and apparatus for conformably sealing prostheses within body lumens |
US09/008,686 US6656214B1 (en) | 1995-09-08 | 1998-01-16 | Methods and apparatus for conformably sealing prostheses within body lumens |
US10/712,376 US20040098097A1 (en) | 1995-09-08 | 2003-11-14 | Methods and apparatus for conformably sealing prostheses within body lumens |
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US09/008,686 Division US6656214B1 (en) | 1995-09-08 | 1998-01-16 | Methods and apparatus for conformably sealing prostheses within body lumens |
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US10/712,376 Abandoned US20040098097A1 (en) | 1995-09-08 | 2003-11-14 | Methods and apparatus for conformably sealing prostheses within body lumens |
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US09/008,686 Expired - Lifetime US6656214B1 (en) | 1995-09-08 | 1998-01-16 | Methods and apparatus for conformably sealing prostheses within body lumens |
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Cited By (10)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20060282111A1 (en) * | 2005-06-09 | 2006-12-14 | Baylor College Of Medicine | Segmented Embolectomy Catheter |
US20070219620A1 (en) * | 2004-04-12 | 2007-09-20 | Cook Incorporated | Stent Graft Repair Device |
US20070244544A1 (en) * | 2006-04-14 | 2007-10-18 | Medtronic Vascular, Inc. | Seal for Enhanced Stented Valve Fixation |
WO2009102439A1 (en) * | 2008-02-11 | 2009-08-20 | William Cook Europe Aps | Prosthesis coupling device and method |
WO2011005840A3 (en) * | 2009-07-07 | 2011-06-03 | Med Institute, Inc. | Hydrogel enhanced medical devices |
US20120310328A1 (en) * | 2011-05-31 | 2012-12-06 | Edwards Lifesciences Corporation | System and method for treating valve insufficiency or vessel dilatation |
US20130018414A1 (en) * | 2004-01-30 | 2013-01-17 | W.L. Gore & Associates | Devices, Systems and Methods for Closure of Cardiac Openings |
US8425548B2 (en) | 2010-07-01 | 2013-04-23 | Aneaclose LLC | Occluding member expansion and then stent expansion for aneurysm treatment |
CN106214287A (en) * | 2016-08-24 | 2016-12-14 | 杨威 | Dissection of aorta operation overlay film frame, conveyer device and using method |
CN109475402A (en) * | 2016-06-21 | 2019-03-15 | 美敦力瓦斯科尔勒公司 | The vascular endoprostheses of coating for aneurysm treatment |
Families Citing this family (340)
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 |
US6331188B1 (en) | 1994-08-31 | 2001-12-18 | Gore Enterprise Holdings, Inc. | Exterior supported self-expanding stent-graft |
US6015429A (en) | 1994-09-08 | 2000-01-18 | Gore Enterprise Holdings, Inc. | Procedures for introducing stents and stent-grafts |
US5769882A (en) * | 1995-09-08 | 1998-06-23 | Medtronic, Inc. | Methods and apparatus for conformably sealing prostheses within body lumens |
US6287315B1 (en) | 1995-10-30 | 2001-09-11 | World Medical Manufacturing Corporation | Apparatus for delivering an endoluminal prosthesis |
EP0866677A4 (en) | 1995-12-14 | 1999-10-27 | Prograft Medical Inc | Stent-graft deployment apparatus and method |
US6042605A (en) | 1995-12-14 | 2000-03-28 | Gore Enterprose Holdings, Inc. | Kink resistant stent-graft |
DE69732794T2 (en) | 1996-01-05 | 2006-04-06 | Medtronic, Inc., Minneapolis | EXPANDABLE ENDOLUMINARY PROSTHESIS |
US6010529A (en) * | 1996-12-03 | 2000-01-04 | Atrium Medical Corporation | Expandable shielded vessel support |
US5925074A (en) * | 1996-12-03 | 1999-07-20 | Atrium Medical Corporation | Vascular endoprosthesis and method |
US6015431A (en) * | 1996-12-23 | 2000-01-18 | Prograft Medical, Inc. | Endolumenal stent-graft with leak-resistant seal |
US6551350B1 (en) | 1996-12-23 | 2003-04-22 | Gore Enterprise Holdings, Inc. | Kink resistant bifurcated prosthesis |
US6352561B1 (en) | 1996-12-23 | 2002-03-05 | W. L. Gore & Associates | Implant deployment apparatus |
US5957974A (en) * | 1997-01-23 | 1999-09-28 | Schneider (Usa) Inc | Stent graft with braided polymeric sleeve |
ATE275888T1 (en) | 1997-01-29 | 2004-10-15 | Endovascular Tech Inc | MODULAR STENT FABRIC WITH BELL-SHAPED EXTENDED END |
WO1998041167A1 (en) * | 1997-03-14 | 1998-09-24 | Harry Bernard Joseph Spoelstra | Arrangement for the endovascular repair of a blood vessel section |
GR970100134A (en) * | 1997-04-10 | 1998-12-31 | Bifurcated inravascular implant for the intravascular treatment of aneurysms of the abdominal aorta and implanting technique | |
CA2235911C (en) * | 1997-05-27 | 2003-07-29 | Schneider (Usa) Inc. | Stent and stent-graft for treating branched vessels |
US5906641A (en) * | 1997-05-27 | 1999-05-25 | Schneider (Usa) Inc | Bifurcated stent graft |
US5957940A (en) * | 1997-06-30 | 1999-09-28 | Eva Corporation | Fasteners for use in the surgical repair of aneurysms |
US6070589A (en) | 1997-08-01 | 2000-06-06 | Teramed, Inc. | Methods for deploying bypass graft stents |
US5984965A (en) * | 1997-08-28 | 1999-11-16 | Urosurge, Inc. | Anti-reflux reinforced stent |
US5968090A (en) * | 1997-09-08 | 1999-10-19 | United States Surgical Corp. | Endovascular graft and method |
US6511468B1 (en) | 1997-10-17 | 2003-01-28 | Micro Therapeutics, Inc. | Device and method for controlling injection of liquid embolic composition |
WO1999026559A1 (en) * | 1997-11-25 | 1999-06-03 | Triad Vascular Systems, Inc. | Layered endovascular graft |
FR2773057B1 (en) | 1997-12-29 | 2001-01-05 | Braun Celsa Sa | MEDICAL ASSEMBLY FOR TREATING A DISEASE OF AN ANATOMICAL CONDUIT |
EP0961598B1 (en) | 1997-12-16 | 2004-09-08 | B. Braun Celsa | Medical device for the treatment of a diseased anatomical duct |
US6146414A (en) * | 1997-12-19 | 2000-11-14 | Gelman; Martin L. | Medical graft and construction of the same |
US6626919B1 (en) | 1997-12-29 | 2003-09-30 | Lee L. Swanstrom | Method and apparatus for attaching or locking an implant to an anatomic vessel or hollow organ wall |
US6395018B1 (en) | 1998-02-09 | 2002-05-28 | Wilfrido R. Castaneda | Endovascular graft and process for bridging a defect in a main vessel near one of more branch vessels |
US6395019B2 (en) | 1998-02-09 | 2002-05-28 | Trivascular, Inc. | Endovascular graft |
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 |
JP2002510524A (en) * | 1998-04-02 | 2002-04-09 | サルヴィアック・リミテッド | Implant having a support structure and a transition material comprising a porous plastic material |
US6669707B1 (en) | 1998-07-21 | 2003-12-30 | Lee L. Swanstrom | Method and apparatus for attaching or locking an implant to an anatomic vessel or hollow organ wall |
US6340368B1 (en) | 1998-10-23 | 2002-01-22 | Medtronic Inc. | Implantable device with radiopaque ends |
FR2773058B1 (en) | 1998-11-24 | 2001-11-02 | Braun Celsa Sa | MEANS FOR ATTACHING AN IMPLANT TO AN ANATOMICAL CONDUIT AND MEDICAL ASSEMBLY FOR TREATING A CONDITION OF THIS CONDUIT |
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 |
WO2000044309A2 (en) | 1999-02-01 | 2000-08-03 | Board Of Regents, The University Of Texas System | Woven bifurcated and trifurcated stents and methods for making the same |
US6361557B1 (en) | 1999-02-05 | 2002-03-26 | Medtronic Ave, Inc. | Staplebutton radiopaque marker |
US6261316B1 (en) | 1999-03-11 | 2001-07-17 | Endologix, Inc. | Single puncture bifurcation graft deployment system |
US6620192B1 (en) * | 1999-03-16 | 2003-09-16 | Advanced Cardiovascular Systems, Inc. | Multilayer stent |
US6709465B2 (en) | 1999-03-18 | 2004-03-23 | Fossa Medical, Inc. | Radially expanding ureteral device |
US7214229B2 (en) | 1999-03-18 | 2007-05-08 | Fossa Medical, Inc. | Radially expanding stents |
US6312457B1 (en) * | 1999-04-01 | 2001-11-06 | Boston Scientific Corporation | Intraluminal lining |
US6309367B1 (en) * | 1999-07-23 | 2001-10-30 | Neurovasx, Inc. | Aneurysm shield |
US6312421B1 (en) | 1999-07-23 | 2001-11-06 | Neurovasx, Inc. | Aneurysm embolization material and device |
US6312462B1 (en) | 1999-09-22 | 2001-11-06 | Impra, Inc. | Prosthesis for abdominal aortic aneurysm repair |
US6383171B1 (en) * | 1999-10-12 | 2002-05-07 | Allan Will | Methods and devices for protecting a passageway in a body when advancing devices through the passageway |
CA2397980C (en) | 2000-03-03 | 2009-08-04 | Cook Incorporated | Endovascular device having a stent |
US7220276B1 (en) * | 2000-03-06 | 2007-05-22 | Surmodics, Inc. | Endovascular graft coatings |
US6929658B1 (en) | 2000-03-09 | 2005-08-16 | Design & Performance-Cyprus Limited | Stent with cover connectors |
EP1267748B1 (en) * | 2000-03-09 | 2006-06-28 | Design & Performance - Cyprus Limited | Stent with cover connectors |
US6772026B2 (en) * | 2000-04-05 | 2004-08-03 | Therics, Inc. | System and method for rapidly customizing design, manufacture and/or selection of biomedical devices |
US6454799B1 (en) | 2000-04-06 | 2002-09-24 | Edwards Lifesciences Corporation | Minimally-invasive heart valves and methods of use |
US20020049490A1 (en) | 2000-04-11 | 2002-04-25 | Pollock David T. | Single-piece endoprosthesis with high expansion ratios |
US6517573B1 (en) | 2000-04-11 | 2003-02-11 | Endovascular Technologies, Inc. | Hook for attaching to a corporeal lumen and method of manufacturing |
US6729356B1 (en) | 2000-04-27 | 2004-05-04 | Endovascular Technologies, Inc. | Endovascular graft for providing a seal with vasculature |
US6942691B1 (en) * | 2000-04-27 | 2005-09-13 | Timothy A. M. Chuter | Modular bifurcated graft for endovascular aneurysm repair |
US20030114918A1 (en) * | 2000-04-28 | 2003-06-19 | Garrison Michi E. | Stent graft assembly and method |
US6658288B1 (en) | 2000-05-05 | 2003-12-02 | Endovascular Technologies, Inc. | Apparatus and method for aiding thrombosis through the application of electric potential |
JP2004506469A (en) | 2000-08-18 | 2004-03-04 | アトリテック, インコーポレイテッド | Expandable implantable device for filtering blood flow from the atrial appendage |
US7229472B2 (en) * | 2000-11-16 | 2007-06-12 | Cordis Corporation | Thoracic aneurysm repair prosthesis and system |
US6942692B2 (en) * | 2000-11-16 | 2005-09-13 | Cordis Corporation | Supra-renal prosthesis and renal artery bypass |
EP1258230A3 (en) | 2001-03-29 | 2003-12-10 | CardioSafe Ltd | Balloon catheter device |
ITTO20010465A1 (en) * | 2001-05-18 | 2002-11-18 | Sorin Biomedica Cardio Spa | MODIFYING STRUCTURE ELEMENT FOR INSTALLATION DEVICES, RELATED INSTALLATION DEVICE AND CONSTRUCTION PROCEDURE. |
KR20020094074A (en) * | 2001-06-07 | 2002-12-18 | (주)에이치비메디컬스 | Implantation tube in the body |
GB0114918D0 (en) | 2001-06-19 | 2001-08-08 | Vortex Innovation Ltd | Devices for repairing aneurysms |
US6994722B2 (en) | 2001-07-03 | 2006-02-07 | Scimed Life Systems, Inc. | Implant having improved fixation to a body lumen and method for implanting the same |
US20030014075A1 (en) * | 2001-07-16 | 2003-01-16 | Microvention, Inc. | Methods, materials and apparatus for deterring or preventing endoleaks following endovascular graft implanation |
US8715312B2 (en) | 2001-07-20 | 2014-05-06 | Microvention, Inc. | Aneurysm treatment device and method of use |
US7572288B2 (en) * | 2001-07-20 | 2009-08-11 | Microvention, Inc. | Aneurysm treatment device and method of use |
US8252040B2 (en) * | 2001-07-20 | 2012-08-28 | Microvention, Inc. | Aneurysm treatment device and method of use |
GB0121980D0 (en) | 2001-09-11 | 2001-10-31 | Cathnet Science Holding As | Expandable stent |
DE10148185B4 (en) | 2001-09-28 | 2005-08-11 | Alveolus, Inc. | Instrument for implanting vascular prostheses |
US7033389B2 (en) * | 2001-10-16 | 2006-04-25 | Scimed Life Systems, Inc. | Tubular prosthesis for external agent delivery |
GR1004173B (en) * | 2001-10-31 | 2003-02-26 | Μεντισπες Ιατροφαρμακευτικων Ειδων Ανωνυμη Εμπορικη Και Βιομηχανικη Εταιρεια Α.Ε.Β.Ε. | Metallic stent with arms for the fixation and implantation of biological grafts |
US20060292206A1 (en) | 2001-11-26 | 2006-12-28 | Kim Steven W | Devices and methods for treatment of vascular aneurysms |
US20030135266A1 (en) | 2001-12-03 | 2003-07-17 | Xtent, Inc. | Apparatus and methods for delivery of multiple distributed stents |
US7137993B2 (en) | 2001-12-03 | 2006-11-21 | Xtent, Inc. | Apparatus and methods for delivery of multiple distributed stents |
US8080048B2 (en) | 2001-12-03 | 2011-12-20 | Xtent, Inc. | Stent delivery for bifurcated vessels |
US7892273B2 (en) | 2001-12-03 | 2011-02-22 | Xtent, Inc. | Custom length stent apparatus |
US7147656B2 (en) | 2001-12-03 | 2006-12-12 | Xtent, Inc. | Apparatus and methods for delivery of braided prostheses |
US7270668B2 (en) | 2001-12-03 | 2007-09-18 | Xtent, Inc. | Apparatus and methods for delivering coiled prostheses |
US7351255B2 (en) * | 2001-12-03 | 2008-04-01 | Xtent, Inc. | Stent delivery apparatus and method |
US7182779B2 (en) * | 2001-12-03 | 2007-02-27 | Xtent, Inc. | Apparatus and methods for positioning prostheses for deployment from a catheter |
US7294146B2 (en) * | 2001-12-03 | 2007-11-13 | Xtent, Inc. | Apparatus and methods for delivery of variable length stents |
US20040186551A1 (en) | 2003-01-17 | 2004-09-23 | Xtent, Inc. | Multiple independent nested stent structures and methods for their preparation and deployment |
US7309350B2 (en) * | 2001-12-03 | 2007-12-18 | Xtent, Inc. | Apparatus and methods for deployment of vascular prostheses |
US7147661B2 (en) * | 2001-12-20 | 2006-12-12 | Boston Scientific Santa Rosa Corp. | Radially expandable stent |
AUPR969201A0 (en) * | 2001-12-20 | 2002-01-24 | White, Geoffrey H. | A device for use in intraluminal grafting |
US6676624B2 (en) * | 2001-12-20 | 2004-01-13 | Scimed Life Systems, Inc. | Drainage devices and methods |
AU2003234651B2 (en) * | 2002-05-28 | 2005-10-06 | The Cleveland Clinic Foundation | Minimally invasive treatment system for aortic aneurysms |
US20030225439A1 (en) * | 2002-05-31 | 2003-12-04 | Cook Alonzo D. | Implantable product with improved aqueous interface characteristics and method for making and using same |
US7044962B2 (en) * | 2002-06-25 | 2006-05-16 | Scimed Life Systems, Inc. | Implantable prosthesis with displaceable skirt |
DE10233085B4 (en) | 2002-07-19 | 2014-02-20 | Dendron Gmbh | Stent with guide wire |
US8425549B2 (en) | 2002-07-23 | 2013-04-23 | Reverse Medical Corporation | Systems and methods for removing obstructive matter from body lumens and treating vascular defects |
AU2003272682C1 (en) | 2002-09-20 | 2009-07-16 | Nellix, Inc. | Stent-graft with positioning anchor |
US20040098096A1 (en) * | 2002-10-22 | 2004-05-20 | The University Of Miami | Endograft device to inhibit endoleak and migration |
US20040093056A1 (en) | 2002-10-26 | 2004-05-13 | Johnson Lianw M. | Medical appliance delivery apparatus and method of use |
US7959671B2 (en) | 2002-11-05 | 2011-06-14 | Merit Medical Systems, Inc. | Differential covering and coating methods |
US7637942B2 (en) | 2002-11-05 | 2009-12-29 | Merit Medical Systems, Inc. | Coated stent with geometry determinated functionality and method of making the same |
US7875068B2 (en) | 2002-11-05 | 2011-01-25 | Merit Medical Systems, Inc. | Removable biliary stent |
US7481821B2 (en) * | 2002-11-12 | 2009-01-27 | Thomas J. Fogarty | Embolization device and a method of using the same |
US20080208160A9 (en) * | 2003-01-10 | 2008-08-28 | Mawad Michel E | Microcatheter including swellable tip |
US20040260382A1 (en) | 2003-02-12 | 2004-12-23 | Fogarty Thomas J. | Intravascular implants and methods of using the same |
US7220274B1 (en) | 2003-03-21 | 2007-05-22 | Quinn Stephen F | Intravascular stent grafts and methods for deploying the same |
US7637934B2 (en) | 2003-03-31 | 2009-12-29 | Merit Medical Systems, Inc. | Medical appliance optical delivery and deployment apparatus and method |
US7452374B2 (en) * | 2003-04-24 | 2008-11-18 | Maquet Cardiovascular, Llc | AV grafts with rapid post-operative self-sealing capabilities |
US7604660B2 (en) | 2003-05-01 | 2009-10-20 | Merit Medical Systems, Inc. | Bifurcated medical appliance delivery apparatus and method |
US7241308B2 (en) | 2003-06-09 | 2007-07-10 | Xtent, Inc. | Stent deployment systems and methods |
US7247986B2 (en) * | 2003-06-10 | 2007-07-24 | Samsung Sdi. Co., Ltd. | Organic electro luminescent display and method for fabricating the same |
US20050010138A1 (en) * | 2003-07-11 | 2005-01-13 | Mangiardi Eric K. | Lumen-measuring devices and method |
US9861346B2 (en) | 2003-07-14 | 2018-01-09 | W. L. Gore & Associates, Inc. | Patent foramen ovale (PFO) closure device with linearly elongating petals |
US20050015140A1 (en) * | 2003-07-14 | 2005-01-20 | Debeer Nicholas | Encapsulation device and methods of use |
US20050015110A1 (en) * | 2003-07-18 | 2005-01-20 | Fogarty Thomas J. | Embolization device and a method of using the same |
US7757691B2 (en) * | 2003-08-07 | 2010-07-20 | Merit Medical Systems, Inc. | Therapeutic medical appliance delivery and method of use |
US8721710B2 (en) * | 2003-08-11 | 2014-05-13 | Hdh Medical Ltd. | Anastomosis system and method |
US20050075713A1 (en) * | 2003-10-06 | 2005-04-07 | Brian Biancucci | Minimally invasive valve replacement system |
AU2004279458B2 (en) * | 2003-10-10 | 2009-12-10 | Cook Incorporated | Fenestrated stent grafts |
US7553324B2 (en) * | 2003-10-14 | 2009-06-30 | Xtent, Inc. | Fixed stent delivery devices and methods |
US7192440B2 (en) * | 2003-10-15 | 2007-03-20 | Xtent, Inc. | Implantable stent delivery devices and methods |
US7403966B2 (en) * | 2003-12-08 | 2008-07-22 | Freescale Semiconductor, Inc. | Hardware for performing an arithmetic function |
US20080109057A1 (en) * | 2003-12-10 | 2008-05-08 | Calabria Marie F | Multiple point detacher system |
US20070104752A1 (en) * | 2003-12-10 | 2007-05-10 | Lee Jeffrey A | Aneurysm embolization material and device |
JP4464972B2 (en) * | 2003-12-17 | 2010-05-19 | クック・インコーポレイテッド | Interconnected leg extensions for endoluminal prostheses |
US7381219B2 (en) | 2003-12-23 | 2008-06-03 | Sadra Medical, Inc. | Low profile heart valve and delivery system |
US20120041550A1 (en) | 2003-12-23 | 2012-02-16 | Sadra Medical, Inc. | Methods and Apparatus for Endovascular Heart Valve Replacement Comprising Tissue Grasping Elements |
US11278398B2 (en) | 2003-12-23 | 2022-03-22 | Boston Scientific Scimed, Inc. | Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements |
US7326236B2 (en) | 2003-12-23 | 2008-02-05 | Xtent, Inc. | Devices and methods for controlling and indicating the length of an interventional element |
US8828078B2 (en) | 2003-12-23 | 2014-09-09 | Sadra Medical, Inc. | Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements |
US8343213B2 (en) | 2003-12-23 | 2013-01-01 | Sadra Medical, Inc. | Leaflet engagement elements and methods for use thereof |
US8840663B2 (en) | 2003-12-23 | 2014-09-23 | Sadra Medical, Inc. | Repositionable heart valve method |
US7988724B2 (en) | 2003-12-23 | 2011-08-02 | Sadra Medical, Inc. | Systems and methods for delivering a medical implant |
US7323006B2 (en) | 2004-03-30 | 2008-01-29 | Xtent, Inc. | Rapid exchange interventional devices and methods |
US7674284B2 (en) | 2004-03-31 | 2010-03-09 | Cook Incorporated | Endoluminal graft |
US20050288766A1 (en) * | 2004-06-28 | 2005-12-29 | Xtent, Inc. | Devices and methods for controlling expandable prostheses during deployment |
US8317859B2 (en) | 2004-06-28 | 2012-11-27 | J.W. Medical Systems Ltd. | Devices and methods for controlling expandable prostheses during deployment |
WO2006012567A2 (en) * | 2004-07-22 | 2006-02-02 | Nellix, Inc. | Methods and systems for endovascular aneurysm treatment |
US8048145B2 (en) * | 2004-07-22 | 2011-11-01 | Endologix, Inc. | Graft systems having filling structures supported by scaffolds and methods for their use |
US7887579B2 (en) | 2004-09-29 | 2011-02-15 | Merit Medical Systems, Inc. | Active stent |
US20070179600A1 (en) * | 2004-10-04 | 2007-08-02 | Gil Vardi | Stent graft including expandable cuff |
US20060074481A1 (en) * | 2004-10-04 | 2006-04-06 | Gil Vardi | Graft including expandable cuff |
KR100614654B1 (en) * | 2005-01-04 | 2006-08-22 | 삼성전자주식회사 | RF transmitter for efficiently compensating output power variation due to temperature and process |
DE102005003632A1 (en) | 2005-01-20 | 2006-08-17 | Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. | Catheter for the transvascular implantation of heart valve prostheses |
US7766959B2 (en) | 2005-03-25 | 2010-08-03 | Scimed Life Systems, Inc. | Variable length endovascular graft prosthesis adapted to prevent endoleaks |
US20060222596A1 (en) | 2005-04-01 | 2006-10-05 | Trivascular, Inc. | Non-degradable, low swelling, water soluble radiopaque hydrogel polymer |
US7402168B2 (en) * | 2005-04-11 | 2008-07-22 | Xtent, Inc. | Custom-length stent delivery system with independently operable expansion elements |
US20060233990A1 (en) | 2005-04-13 | 2006-10-19 | Trivascular, Inc. | PTFE layers and methods of manufacturing |
US20060233991A1 (en) | 2005-04-13 | 2006-10-19 | Trivascular, Inc. | PTFE layers and methods of manufacturing |
EP1874231B1 (en) | 2005-04-28 | 2016-01-06 | Endologix, Inc. | Graft systems having filling structures supported by scaffolds |
US20060247760A1 (en) * | 2005-04-29 | 2006-11-02 | Medtronic Vascular, Inc. | Methods and apparatus for treatment of aneurysms adjacent branch arteries |
US7731654B2 (en) | 2005-05-13 | 2010-06-08 | Merit Medical Systems, Inc. | Delivery device with viewing window and associated method |
US7955372B2 (en) * | 2005-06-01 | 2011-06-07 | Board Of Trustees Of The Leland Stanford Junior University | Endoluminal delivery system |
US7938851B2 (en) | 2005-06-08 | 2011-05-10 | Xtent, Inc. | Devices and methods for operating and controlling interventional apparatus |
US7320702B2 (en) | 2005-06-08 | 2008-01-22 | Xtent, Inc. | Apparatus and methods for deployment of multiple custom-length prostheses (III) |
AU2006269419A1 (en) | 2005-07-07 | 2007-01-18 | Nellix, Inc. | Systems and methods for endovascular aneurysm treatment |
JP5203192B2 (en) | 2005-07-27 | 2013-06-05 | クック メディカル テクノロジーズ エルエルシー | Stent / graft device and method for placement in open surgery |
US7569071B2 (en) | 2005-09-21 | 2009-08-04 | Boston Scientific Scimed, Inc. | Venous valve, system, and method with sinus pocket |
US8690957B2 (en) | 2005-12-21 | 2014-04-08 | Warsaw Orthopedic, Inc. | Bone graft composition, method and implant |
US20070213813A1 (en) | 2005-12-22 | 2007-09-13 | Symetis Sa | Stent-valves for valve replacement and associated methods and systems for surgery |
US8900287B2 (en) * | 2006-01-13 | 2014-12-02 | Aga Medical Corporation | Intravascular deliverable stent for reinforcement of abdominal aortic aneurysm |
CA2646885A1 (en) | 2006-03-20 | 2007-09-27 | Xtent, Inc. | Apparatus and methods for deployment of linked prosthetic segments |
US7481836B2 (en) * | 2006-03-30 | 2009-01-27 | Medtronic Vascular, Inc. | Prosthesis with coupling zone and methods |
US9308105B2 (en) * | 2006-04-19 | 2016-04-12 | Cook Medical Technologies Llc | Delivery device for an endoluminal prosthesis |
US7790273B2 (en) * | 2006-05-24 | 2010-09-07 | Nellix, Inc. | Material for creating multi-layered films and methods for making the same |
US7872068B2 (en) * | 2006-05-30 | 2011-01-18 | Incept Llc | Materials formable in situ within a medical device |
US20070296125A1 (en) * | 2006-06-22 | 2007-12-27 | Joel Colburn | Thin cuff for use with medical tubing and method and apparatus for making the same |
US8434487B2 (en) | 2006-06-22 | 2013-05-07 | Covidien Lp | Endotracheal cuff and technique for using the same |
US8196584B2 (en) | 2006-06-22 | 2012-06-12 | Nellcor Puritan Bennett Llc | Endotracheal cuff and technique for using the same |
GB0616738D0 (en) * | 2006-08-23 | 2006-10-04 | Evexar Medical Ltd | Improvements in and relating to medical devices |
US20080053454A1 (en) * | 2006-09-01 | 2008-03-06 | Nellcor Puritan Bennett Incorporated | Endotracheal tube including a partially inverted cuff collar |
US8684175B2 (en) | 2006-09-22 | 2014-04-01 | Covidien Lp | Method for shipping and protecting an endotracheal tube with an inflated cuff |
US8807136B2 (en) * | 2006-09-29 | 2014-08-19 | Covidien Lp | Self-sizing adjustable endotracheal tube |
US20080078399A1 (en) | 2006-09-29 | 2008-04-03 | O'neil Michael P | Self-sizing adjustable endotracheal tube |
US20080078401A1 (en) * | 2006-09-29 | 2008-04-03 | Nellcor Puritan Bennett Incorporated | Self-sizing adjustable endotracheal tube |
US7950393B2 (en) * | 2006-09-29 | 2011-05-31 | Nellcor Puritan Bennett Llc | Endotracheal cuff and technique for using the same |
US8307830B2 (en) | 2006-09-29 | 2012-11-13 | Nellcor Puritan Bennett Llc | Endotracheal cuff and technique for using the same |
US20080078405A1 (en) * | 2006-09-29 | 2008-04-03 | Crumback Gary L | Self-sizing adjustable endotracheal tube |
CN103767810B (en) | 2006-10-22 | 2016-06-15 | Idev科技公司 | From the manufacturing process of extendable bracket |
KR101659197B1 (en) | 2006-10-22 | 2016-09-22 | 이데브 테크놀로지스, 아이엔씨. | Devices and methods for stent advancement |
US20080269774A1 (en) | 2006-10-26 | 2008-10-30 | Chestnut Medical Technologies, Inc. | Intracorporeal Grasping Device |
US20080188923A1 (en) * | 2007-02-01 | 2008-08-07 | Jack Fa-De Chu | Endovascular devices to protect aneurysmal wall |
US20080199510A1 (en) | 2007-02-20 | 2008-08-21 | Xtent, Inc. | Thermo-mechanically controlled implants and methods of use |
US20080210243A1 (en) * | 2007-03-02 | 2008-09-04 | Jessica Clayton | Endotracheal cuff and technique for using the same |
US20080215034A1 (en) * | 2007-03-02 | 2008-09-04 | Jessica Clayton | Endotracheal cuff and technique for using the same |
EP2142142B1 (en) | 2007-03-05 | 2017-02-08 | Endospan Ltd | Multi-component expandable supportive bifurcated endoluminal grafts and methods for using same |
US20080228259A1 (en) * | 2007-03-16 | 2008-09-18 | Jack Fa-De Chu | Endovascular devices and methods to protect aneurysmal wall |
US8486132B2 (en) | 2007-03-22 | 2013-07-16 | J.W. Medical Systems Ltd. | Devices and methods for controlling expandable prostheses during deployment |
US20080294237A1 (en) * | 2007-04-04 | 2008-11-27 | Jack Fa-De Chu | Inflatable devices and methods to protect aneurysmal wall |
US9005242B2 (en) | 2007-04-05 | 2015-04-14 | W.L. Gore & Associates, Inc. | Septal closure device with centering mechanism |
US7896915B2 (en) | 2007-04-13 | 2011-03-01 | Jenavalve Technology, Inc. | Medical device for treating a heart valve insufficiency |
JP5734650B2 (en) | 2007-06-25 | 2015-06-17 | マイクロベンション インコーポレイテッド | Self-expanding prosthesis |
EP3492043A3 (en) | 2007-08-21 | 2019-09-04 | Symetis SA | A replacement valve |
US8066755B2 (en) | 2007-09-26 | 2011-11-29 | Trivascular, Inc. | System and method of pivoted stent deployment |
US8226701B2 (en) | 2007-09-26 | 2012-07-24 | Trivascular, Inc. | Stent and delivery system for deployment thereof |
EP4309627A2 (en) | 2007-09-26 | 2024-01-24 | St. Jude Medical, LLC | Collapsible prosthetic heart valves |
US8663309B2 (en) | 2007-09-26 | 2014-03-04 | Trivascular, Inc. | Asymmetric stent apparatus and method |
US9532868B2 (en) | 2007-09-28 | 2017-01-03 | St. Jude Medical, Inc. | Collapsible-expandable prosthetic heart valves with structures for clamping native tissue |
AU2008308474B2 (en) | 2007-10-04 | 2014-07-24 | Trivascular, Inc. | Modular vascular graft for low profile percutaneous delivery |
US8088140B2 (en) | 2008-05-19 | 2012-01-03 | Mindframe, Inc. | Blood flow restorative and embolus removal methods |
US11337714B2 (en) | 2007-10-17 | 2022-05-24 | Covidien Lp | Restoring blood flow and clot removal during acute ischemic stroke |
CA2703665C (en) | 2007-10-25 | 2016-05-10 | Symetis Sa | Stents, valved-stents and methods and systems for delivery thereof |
US20090112237A1 (en) * | 2007-10-26 | 2009-04-30 | Cook Critical Care Incorporated | Vascular conduit and delivery system for open surgical placement |
US8083789B2 (en) | 2007-11-16 | 2011-12-27 | Trivascular, Inc. | Securement assembly and method for expandable endovascular device |
US8328861B2 (en) | 2007-11-16 | 2012-12-11 | Trivascular, Inc. | Delivery system and method for bifurcated graft |
US8486131B2 (en) | 2007-12-15 | 2013-07-16 | Endospan Ltd. | Extra-vascular wrapping for treating aneurysmatic aorta in conjunction with endovascular stent-graft and methods thereof |
US8750978B2 (en) * | 2007-12-31 | 2014-06-10 | Covidien Lp | System and sensor for early detection of shock or perfusion failure and technique for using the same |
US7862538B2 (en) * | 2008-02-04 | 2011-01-04 | Incept Llc | Surgical delivery system for medical sealant |
AU2009217354B2 (en) | 2008-02-22 | 2013-10-10 | Covidien Lp | Methods and apparatus for flow restoration |
ES2903231T3 (en) | 2008-02-26 | 2022-03-31 | Jenavalve Tech Inc | Stent for positioning and anchoring a valve prosthesis at an implantation site in a patient's heart |
US9044318B2 (en) | 2008-02-26 | 2015-06-02 | Jenavalve Technology Gmbh | Stent for the positioning and anchoring of a valvular prosthesis |
US20090227976A1 (en) * | 2008-03-05 | 2009-09-10 | Calabria Marie F | Multiple biocompatible polymeric strand aneurysm embolization system and method |
US9101503B2 (en) | 2008-03-06 | 2015-08-11 | J.W. Medical Systems Ltd. | Apparatus having variable strut length and methods of use |
US20130165967A1 (en) | 2008-03-07 | 2013-06-27 | W.L. Gore & Associates, Inc. | Heart occlusion devices |
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 |
US8974487B2 (en) * | 2008-05-01 | 2015-03-10 | Aneuclose Llc | Aneurysm occlusion device |
US10028747B2 (en) | 2008-05-01 | 2018-07-24 | Aneuclose Llc | Coils with a series of proximally-and-distally-connected loops for occluding a cerebral aneurysm |
US10716573B2 (en) | 2008-05-01 | 2020-07-21 | Aneuclose | Janjua aneurysm net with a resilient neck-bridging portion for occluding a cerebral aneurysm |
EP3005959B1 (en) * | 2008-05-15 | 2019-04-03 | Cook Medical Technologies LLC | Systems for accessing a bodily opening |
EP2299933A4 (en) * | 2008-06-04 | 2015-07-29 | Endologix Inc | Docking apparatus and methods of use |
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 |
EP4119097A1 (en) | 2008-06-06 | 2023-01-18 | Edwards Lifesciences Corporation | Low profile transcatheter heart valve |
JP5379852B2 (en) | 2008-07-15 | 2013-12-25 | セント ジュード メディカル インコーポレイテッド | Collapsible and re-expandable prosthetic heart valve cuff design and complementary technology application |
DE202008009604U1 (en) * | 2008-07-17 | 2008-11-27 | Sahl, Harald, Dr. | Membrane implant for the treatment of cerebral artery aneurysms |
WO2010022180A1 (en) | 2008-08-19 | 2010-02-25 | Micro Therapeutics, Inc. | Detachable tip microcatheter |
US11298252B2 (en) | 2008-09-25 | 2022-04-12 | Advanced Bifurcation Systems Inc. | Stent alignment during treatment of a bifurcation |
US8821562B2 (en) | 2008-09-25 | 2014-09-02 | Advanced Bifurcation Systems, Inc. | Partially crimped stent |
EP2344068B1 (en) | 2008-09-25 | 2022-10-19 | Advanced Bifurcation Systems Inc. | Partially crimped stent |
US8828071B2 (en) | 2008-09-25 | 2014-09-09 | Advanced Bifurcation Systems, Inc. | Methods and systems for ostial stenting of a bifurcation |
JP5607639B2 (en) | 2008-10-10 | 2014-10-15 | サドラ メディカル インコーポレイテッド | Medical devices and systems |
US20100131002A1 (en) * | 2008-11-24 | 2010-05-27 | Connor Robert A | Stent with a net layer to embolize and aneurysm |
KR20110102422A (en) * | 2008-12-10 | 2011-09-16 | 마이크로벤션, 인코포레이티드 | Microcatheter |
WO2010093873A2 (en) | 2009-02-12 | 2010-08-19 | Incept, Llc | Drug delivery through hydrogel plugs |
US10772717B2 (en) | 2009-05-01 | 2020-09-15 | Endologix, Inc. | Percutaneous method and device to treat dissections |
US9579103B2 (en) | 2009-05-01 | 2017-02-28 | Endologix, Inc. | Percutaneous method and device to treat dissections |
US8590534B2 (en) | 2009-06-22 | 2013-11-26 | Covidien Lp | Cuff for use with medical tubing and method and apparatus for making the same |
US20120029556A1 (en) | 2009-06-22 | 2012-02-02 | Masters Steven J | Sealing device and delivery system |
US8956389B2 (en) | 2009-06-22 | 2015-02-17 | W. L. Gore & Associates, Inc. | Sealing device and delivery system |
CA3009244C (en) | 2009-06-23 | 2020-04-28 | Endospan Ltd. | Vascular prostheses for treating aneurysms |
CA2767596C (en) | 2009-07-09 | 2015-11-24 | Endospan Ltd. | Apparatus for closure of a lumen and methods of using the same |
WO2011017123A2 (en) | 2009-07-27 | 2011-02-10 | Endologix, Inc. | Stent graft |
CA2778944C (en) | 2009-11-02 | 2019-08-20 | Symetis Sa | Aortic bioprosthesis and systems for delivery thereof |
US9358140B1 (en) | 2009-11-18 | 2016-06-07 | Aneuclose Llc | Stent with outer member to embolize an aneurysm |
EP3735937A1 (en) | 2009-11-30 | 2020-11-11 | Endospan Ltd. | Multi-component stent-graft system for implantation in a blood vessel with multiple branches |
WO2011070576A1 (en) | 2009-12-08 | 2011-06-16 | Endospan Ltd. | Endovascular stent-graft system with fenestrated and crossing stent-grafts |
US20110276078A1 (en) | 2009-12-30 | 2011-11-10 | Nellix, Inc. | Filling structure for a graft system and methods of use |
CA2785953C (en) | 2009-12-31 | 2016-02-16 | Endospan Ltd. | Endovascular flow direction indicator |
US8906057B2 (en) * | 2010-01-04 | 2014-12-09 | Aneuclose Llc | Aneurysm embolization by rotational accumulation of mass |
US20110184509A1 (en) * | 2010-01-27 | 2011-07-28 | Abbott Laboratories | Dual sheath assembly and method of use |
US9468517B2 (en) | 2010-02-08 | 2016-10-18 | Endospan Ltd. | Thermal energy application for prevention and management of endoleaks in stent-grafts |
US20110208292A1 (en) * | 2010-02-19 | 2011-08-25 | Abbott Laboratories | Hinged sheath assembly and method of use |
CA2794078A1 (en) | 2010-03-24 | 2011-09-29 | Advanced Bifurcation Systems, Inc. | Stent alignment during treatment of a bifurcation |
EP2549952A4 (en) | 2010-03-24 | 2017-01-04 | Advanced Bifurcation Systems, Inc. | System and methods for treating a bifurcation |
CA2794064A1 (en) | 2010-03-24 | 2011-09-29 | Advanced Bifurcation Systems, Inc. | Methods and systems for treating a bifurcation with provisional side branch stenting |
JP2013526388A (en) | 2010-05-25 | 2013-06-24 | イエナバルブ テクノロジー インク | Artificial heart valve, and transcatheter delivery prosthesis comprising an artificial heart valve and a stent |
US9023095B2 (en) | 2010-05-27 | 2015-05-05 | Idev Technologies, Inc. | Stent delivery system with pusher assembly |
EP2613737B2 (en) | 2010-09-10 | 2023-03-15 | Symetis SA | Valve replacement devices, delivery device for a valve replacement device and method of production of a valve replacement device |
US8961501B2 (en) | 2010-09-17 | 2015-02-24 | Incept, Llc | Method for applying flowable hydrogels to a cornea |
US9039749B2 (en) | 2010-10-01 | 2015-05-26 | Covidien Lp | Methods and apparatuses for flow restoration and implanting members in the human body |
EP2627395B1 (en) * | 2010-10-11 | 2017-12-06 | Peter S. Dardi | Hydrogel jacketed stents |
US8676319B2 (en) | 2010-10-29 | 2014-03-18 | Medtronic, Inc. | Implantable medical device with compressible fixation member |
WO2012068298A1 (en) | 2010-11-17 | 2012-05-24 | Endologix, Inc. | Devices and methods to treat vascular dissections |
WO2012071626A1 (en) * | 2010-12-01 | 2012-06-07 | Daniel Eduard Kleiner | Device for use in endoluminal vacuum therapy |
US8801768B2 (en) | 2011-01-21 | 2014-08-12 | Endologix, Inc. | Graft systems having semi-permeable filling structures and methods for their use |
US9526638B2 (en) | 2011-02-03 | 2016-12-27 | Endospan Ltd. | Implantable medical devices constructed of shape memory material |
CA2826760A1 (en) | 2011-02-08 | 2012-08-16 | Advanced Bifurcation Systems, Inc. | Multi-stent and multi-balloon apparatus for treating bifurcations and methods of use |
EP3449879B1 (en) | 2011-02-08 | 2020-09-23 | Advanced Bifurcation Systems Inc. | System for treating a bifurcation with a fully crimped stent |
WO2012111006A1 (en) | 2011-02-17 | 2012-08-23 | Endospan Ltd. | Vascular bands and delivery systems therefor |
US9884172B2 (en) | 2011-02-25 | 2018-02-06 | Microvention, Inc. | Reinforced balloon catheter |
US9486341B2 (en) | 2011-03-02 | 2016-11-08 | Endospan Ltd. | Reduced-strain extra-vascular ring for treating aortic aneurysm |
US9415195B2 (en) | 2011-04-06 | 2016-08-16 | Engologix, Inc. | Method and system for treating aneurysms |
EP2520251A1 (en) | 2011-05-05 | 2012-11-07 | Symetis SA | Method and Apparatus for Compressing Stent-Valves |
CA2835427A1 (en) | 2011-05-11 | 2012-11-15 | Microvention, Inc. | Device for occluding a lumen |
US9138232B2 (en) | 2011-05-24 | 2015-09-22 | Aneuclose Llc | Aneurysm occlusion by rotational dispensation of mass |
US8574287B2 (en) | 2011-06-14 | 2013-11-05 | Endospan Ltd. | Stents incorporating a plurality of strain-distribution locations |
ES2568377T3 (en) | 2011-06-21 | 2016-04-28 | Endospan Ltd | Endovascular system with circumferentially overlapping stents |
EP2729095B1 (en) | 2011-07-07 | 2016-10-26 | Endospan Ltd. | Stent fixation with reduced plastic deformation |
US9770232B2 (en) | 2011-08-12 | 2017-09-26 | W. L. Gore & Associates, Inc. | Heart occlusion devices |
US9839510B2 (en) | 2011-08-28 | 2017-12-12 | Endospan Ltd. | Stent-grafts with post-deployment variable radial displacement |
US9216076B2 (en) | 2011-09-09 | 2015-12-22 | Endoluminal Sciences Pty. Ltd. | Means for controlled sealing of endovascular devices |
CN105232187A (en) * | 2011-09-09 | 2016-01-13 | 安多拉米诺科学公司 | Means for controlled sealing of endovascular devices |
US9427339B2 (en) | 2011-10-30 | 2016-08-30 | Endospan Ltd. | Triple-collar stent-graft |
US9597204B2 (en) | 2011-12-04 | 2017-03-21 | Endospan Ltd. | Branched stent-graft system |
US9006359B2 (en) | 2011-12-14 | 2015-04-14 | Semprus Biosciences Corporation | Imbibing process for contact lens surface modification |
EP2790744A4 (en) | 2011-12-14 | 2015-06-24 | Semprus Biosciences Corp | Surface modification for dialysis catheters |
EP2791214A4 (en) | 2011-12-14 | 2015-11-04 | Semprus Biosciences Corp | Redox processes for contact lens modification |
MX2014007204A (en) | 2011-12-14 | 2015-04-14 | Semprus Biosciences Corp | Multistep uv process to create surface modified contact lenses. |
MX2014007202A (en) | 2011-12-14 | 2015-03-09 | Semprus Biosciences Corp | Surface modified contact lenses. |
JP2015502437A (en) | 2011-12-14 | 2015-01-22 | センプラス・バイオサイエンシーズ・コーポレイションSemprus Biosciences Corp. | Silicone hydrogel contact lenses modified with lanthanides or transition metal oxidants |
US20130274873A1 (en) | 2012-03-22 | 2013-10-17 | Symetis Sa | Transcatheter Stent-Valves and Methods, Systems and Devices for Addressing Para-Valve Leakage |
US11207176B2 (en) | 2012-03-22 | 2021-12-28 | Boston Scientific Scimed, Inc. | Transcatheter stent-valves and methods, systems and devices for addressing para-valve leakage |
US20130261660A1 (en) * | 2012-04-03 | 2013-10-03 | Warsaw Orthopedic, Inc. | Medical devices and methods for inserting an adhesive membrane |
US8992595B2 (en) | 2012-04-04 | 2015-03-31 | Trivascular, Inc. | Durable stent graft with tapered struts and stable delivery methods and devices |
US9498363B2 (en) | 2012-04-06 | 2016-11-22 | Trivascular, Inc. | Delivery catheter for endovascular device |
WO2013171730A1 (en) | 2012-05-15 | 2013-11-21 | Endospan Ltd. | Stent-graft with fixation elements that are radially confined for delivery |
JP6230166B2 (en) * | 2012-06-03 | 2017-11-15 | ダニエル・エデュアード・クレイナー | Intraluminal negative pressure therapy device |
US9883941B2 (en) | 2012-06-19 | 2018-02-06 | Boston Scientific Scimed, Inc. | Replacement heart valve |
US10124087B2 (en) | 2012-06-19 | 2018-11-13 | Covidien Lp | Detachable coupling for catheter |
WO2014108895A2 (en) | 2013-01-08 | 2014-07-17 | Endospan Ltd. | Minimization of stent-graft migration during implantation |
US10828019B2 (en) | 2013-01-18 | 2020-11-10 | W.L. Gore & Associates, Inc. | Sealing device and delivery system |
EP2967830B1 (en) | 2013-03-11 | 2017-11-01 | Endospan Ltd. | Multi-component stent-graft system for aortic dissections |
US20140350668A1 (en) | 2013-03-13 | 2014-11-27 | Symetis Sa | Prosthesis Seals and Methods for Sealing an Expandable Prosthesis |
US10201638B2 (en) | 2013-03-14 | 2019-02-12 | Endologix, Inc. | Systems and methods for forming materials in situ within a medical device |
WO2015020676A1 (en) * | 2013-08-08 | 2015-02-12 | Boston Scientific Scimed, Inc. | Dissolvable or degradable adhesive polymer to prevent stent migration |
JP6563394B2 (en) | 2013-08-30 | 2019-08-21 | イェーナヴァルヴ テクノロジー インコーポレイテッド | Radially foldable frame for an artificial valve and method for manufacturing the frame |
US10076399B2 (en) | 2013-09-13 | 2018-09-18 | Covidien Lp | Endovascular device engagement |
WO2015055652A1 (en) | 2013-10-14 | 2015-04-23 | Symetis Sa | Prosthesis seal |
US9913715B2 (en) | 2013-11-06 | 2018-03-13 | St. Jude Medical, Cardiology Division, Inc. | Paravalvular leak sealing mechanism |
WO2015075708A1 (en) | 2013-11-19 | 2015-05-28 | Endospan Ltd. | Stent system with radial-expansion locking |
CA2945515C (en) * | 2014-04-10 | 2019-08-13 | C.R. Bard, Inc. | Ureteral stents |
US10154904B2 (en) | 2014-04-28 | 2018-12-18 | Edwards Lifesciences Corporation | Intravascular introducer devices |
US10195025B2 (en) | 2014-05-12 | 2019-02-05 | Edwards Lifesciences Corporation | Prosthetic heart valve |
US9808230B2 (en) | 2014-06-06 | 2017-11-07 | W. L. Gore & Associates, Inc. | Sealing device and delivery system |
US10959826B2 (en) | 2014-10-16 | 2021-03-30 | Cook Medical Technology LLC | Support structure for scalloped grafts |
WO2016098113A1 (en) | 2014-12-18 | 2016-06-23 | Endospan Ltd. | Endovascular stent-graft with fatigue-resistant lateral tube |
WO2016126524A1 (en) | 2015-02-03 | 2016-08-11 | Boston Scientific Scimed, Inc. | Prosthetic heart valve having tubular seal |
US10426617B2 (en) | 2015-03-06 | 2019-10-01 | Boston Scientific Scimed, Inc. | Low profile valve locking mechanism and commissure assembly |
US10709555B2 (en) | 2015-05-01 | 2020-07-14 | Jenavalve Technology, Inc. | Device and method with reduced pacemaker rate in heart valve replacement |
US11129737B2 (en) | 2015-06-30 | 2021-09-28 | Endologix Llc | Locking assembly for coupling guidewire to delivery system |
US9974650B2 (en) | 2015-07-14 | 2018-05-22 | Edwards Lifesciences Corporation | Prosthetic heart valve |
JP7209541B2 (en) * | 2015-11-12 | 2023-01-20 | バイオステージ,インコーポレーテッド | Systems and methods for generation of gastrointestinal tissue |
US10179043B2 (en) | 2016-02-12 | 2019-01-15 | Edwards Lifesciences Corporation | Prosthetic heart valve having multi-level sealing member |
EP3454795B1 (en) | 2016-05-13 | 2023-01-11 | JenaValve Technology, Inc. | Heart valve prosthesis delivery system for delivery of heart valve prosthesis with introducer sheath and loading system |
US10201416B2 (en) | 2016-05-16 | 2019-02-12 | Boston Scientific Scimed, Inc. | Replacement heart valve implant with invertible leaflets |
US10813749B2 (en) | 2016-12-20 | 2020-10-27 | Edwards Lifesciences Corporation | Docking device made with 3D woven fabric |
JP7094965B2 (en) | 2017-01-27 | 2022-07-04 | イエナバルブ テクノロジー インク | Heart valve imitation |
EP3634311A1 (en) | 2017-06-08 | 2020-04-15 | Boston Scientific Scimed, Inc. | Heart valve implant commissure support structure |
WO2019028161A1 (en) | 2017-08-01 | 2019-02-07 | Boston Scientific Scimed, Inc. | Medical implant locking mechanism |
US10939996B2 (en) | 2017-08-16 | 2021-03-09 | Boston Scientific Scimed, Inc. | Replacement heart valve commissure assembly |
EP3740160A2 (en) | 2018-01-19 | 2020-11-25 | Boston Scientific Scimed Inc. | Inductance mode deployment sensors for transcatheter valve system |
WO2019144071A1 (en) | 2018-01-19 | 2019-07-25 | Boston Scientific Scimed, Inc. | Medical device delivery system with feedback loop |
EP3749252A1 (en) | 2018-02-07 | 2020-12-16 | Boston Scientific Scimed, Inc. | Medical device delivery system with alignment feature |
EP3758651B1 (en) | 2018-02-26 | 2022-12-07 | Boston Scientific Scimed, Inc. | Embedded radiopaque marker in adaptive seal |
CN112399836A (en) | 2018-05-15 | 2021-02-23 | 波士顿科学国际有限公司 | Replacement heart valve commissure assemblies |
US11241310B2 (en) | 2018-06-13 | 2022-02-08 | Boston Scientific Scimed, Inc. | Replacement heart valve delivery device |
WO2020123486A1 (en) | 2018-12-10 | 2020-06-18 | Boston Scientific Scimed, Inc. | Medical device delivery system including a resistance member |
JP2022525788A (en) | 2019-03-20 | 2022-05-19 | インキュベート メディカル テクノロジーズ、 エルエルシー | Aortic dissection implant |
US11439504B2 (en) | 2019-05-10 | 2022-09-13 | Boston Scientific Scimed, Inc. | Replacement heart valve with improved cusp washout and reduced loading |
EP3875057A1 (en) | 2020-03-04 | 2021-09-08 | Michel Marinus Petrus Johannes Reijnen | Catheter system for delivery of a filling body to an aneurysmal sac in a body lumen |
Citations (34)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3890107A (en) * | 1972-09-25 | 1975-06-17 | Research Corp | Materials useful for prosthetic devices and the like |
US3991767A (en) * | 1973-11-02 | 1976-11-16 | Cutter Laboratories, Inc. | Tubular unit with vessel engaging cuff structure |
US4130904A (en) * | 1977-06-06 | 1978-12-26 | Thermo Electron Corporation | Prosthetic blood conduit |
US4577631A (en) * | 1984-11-16 | 1986-03-25 | Kreamer Jeffry W | Aneurysm repair apparatus and method |
US4580568A (en) * | 1984-10-01 | 1986-04-08 | Cook, Incorporated | Percutaneous endovascular stent and method for insertion thereof |
US4728328A (en) * | 1984-10-19 | 1988-03-01 | Research Corporation | Cuffed tubular organic prostheses |
US5092841A (en) * | 1990-05-17 | 1992-03-03 | Wayne State University | Method for treating an arterial wall injured during angioplasty |
US5100429A (en) * | 1989-04-28 | 1992-03-31 | C. R. Bard, Inc. | Endovascular stent and delivery system |
US5156620A (en) * | 1991-02-04 | 1992-10-20 | Pigott John P | Intraluminal graft/stent and balloon catheter for insertion thereof |
US5167614A (en) * | 1991-10-29 | 1992-12-01 | Medical Engineering Corporation | Prostatic stent |
US5213580A (en) * | 1988-08-24 | 1993-05-25 | Endoluminal Therapeutics, Inc. | Biodegradable polymeric endoluminal sealing process |
US5295962A (en) * | 1992-04-29 | 1994-03-22 | Cardiovascular Dynamics, Inc. | Drug delivery and dilatation catheter |
US5330528A (en) * | 1989-12-01 | 1994-07-19 | British Technology Group Limited | Vascular surgical devices |
US5334201A (en) * | 1993-03-12 | 1994-08-02 | Cowan Kevin P | Permanent stent made of a cross linkable material |
US5344444A (en) * | 1991-07-03 | 1994-09-06 | Industrial Research B.V. | Expandable ring, cylinder or sleeve which can be made non-deformable |
US5344426A (en) * | 1990-04-25 | 1994-09-06 | Advanced Cardiovascular Systems, Inc. | Method and system for stent delivery |
US5348788A (en) * | 1991-01-30 | 1994-09-20 | Interpore Orthopaedics, Inc. | Mesh sheet with microscopic projections and holes |
US5354329A (en) * | 1992-04-17 | 1994-10-11 | Whalen Biomedical, Inc. | Vascular prosthesis having enhanced compatibility and compliance characteristics |
US5462704A (en) * | 1994-04-26 | 1995-10-31 | Industrial Technology Research Institute | Method for preparing a porous polyurethane vascular graft prosthesis |
US5489295A (en) * | 1991-04-11 | 1996-02-06 | Endovascular Technologies, Inc. | Endovascular graft having bifurcation and apparatus and method for deploying the same |
US5522880A (en) * | 1990-06-11 | 1996-06-04 | Barone; Hector D. | Method for repairing an abdominal aortic aneurysm |
US5522881A (en) * | 1994-06-28 | 1996-06-04 | Meadox Medicals, Inc. | Implantable tubular prosthesis having integral cuffs |
US5562727A (en) * | 1994-10-07 | 1996-10-08 | Aeroquip Corporation | Intraluminal graft and method for insertion thereof |
US5611775A (en) * | 1993-03-15 | 1997-03-18 | Advanced Cardiovascular Systems, Inc. | Method of delivery therapeutic or diagnostic liquid into tissue surrounding a body lumen |
US5618301A (en) * | 1993-10-07 | 1997-04-08 | Angiomed Ag | Reducing stent, device with reducing stent and use of a reducing stent |
US5628784A (en) * | 1994-01-18 | 1997-05-13 | Strecker; Ernst P. | Endoprosthesis that can be percutaneously implanted in the body of a patient |
US5674241A (en) * | 1995-02-22 | 1997-10-07 | Menlo Care, Inc. | Covered expanding mesh stent |
US5676696A (en) * | 1995-02-24 | 1997-10-14 | Intervascular, Inc. | Modular bifurcated intraluminal grafts and methods for delivering and assembling same |
US5683450A (en) * | 1994-02-09 | 1997-11-04 | Boston Scientific Technology, Inc. | Bifurcated endoluminal prosthesis |
US5693085A (en) * | 1994-04-29 | 1997-12-02 | Scimed Life Systems, Inc. | Stent with collagen |
US5693088A (en) * | 1993-11-08 | 1997-12-02 | Lazarus; Harrison M. | Intraluminal vascular graft |
US5749915A (en) * | 1988-08-24 | 1998-05-12 | Focal, Inc. | Polymeric endoluminal paving process |
US5769882A (en) * | 1995-09-08 | 1998-06-23 | Medtronic, Inc. | Methods and apparatus for conformably sealing prostheses within body lumens |
US5785679A (en) * | 1995-07-19 | 1998-07-28 | Endotex Interventional Systems, Inc. | Methods and apparatus for treating aneurysms and arterio-venous fistulas |
Family Cites Families (11)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
SE424045B (en) * | 1979-01-12 | 1982-06-28 | Tesi Ab | CATHETER |
US4636213A (en) * | 1985-01-24 | 1987-01-13 | Pakiam Anthony I | Implantable prosthesis |
US5628783A (en) * | 1991-04-11 | 1997-05-13 | Endovascular Technologies, Inc. | Bifurcated multicapsule intraluminal grafting system and method |
US5246452A (en) * | 1992-04-13 | 1993-09-21 | Impra, Inc. | Vascular graft with removable sheath |
ES2123135T3 (en) * | 1993-03-23 | 1999-01-01 | Focal Inc | APPARATUS AND METHOD FOR LOCAL APPLICATION OF POLYMERIC MATERIAL TO FABRIC. |
EP0696185B1 (en) * | 1993-04-28 | 1998-08-12 | Focal, Inc. | Apparatus, product and use related to intraluminal photothermoforming |
DE4418336A1 (en) * | 1994-05-26 | 1995-11-30 | Angiomed Ag | Stent for widening and holding open receptacles |
DK63894A (en) * | 1994-06-06 | 1996-01-08 | Meadox Medicals Inc | Stent catheter and method for making such a stent catheter |
JP3662255B2 (en) * | 1994-06-13 | 2005-06-22 | エンドームド・インコーポレーテッド | Expandable endovascular graft and method of placing the same |
CA2193983C (en) * | 1994-06-27 | 2005-07-26 | William M. Colone | Radially expandable polytetrafluoroethylene and expandable endovascular stents formed therewith |
US5823198A (en) | 1996-07-31 | 1998-10-20 | Micro Therapeutics, Inc. | Method and apparatus for intravasculer embolization |
-
1995
- 1995-09-08 US US08/525,989 patent/US5769882A/en not_active Expired - Lifetime
-
1996
- 1996-09-06 AU AU71547/96A patent/AU7154796A/en not_active Abandoned
- 1996-09-06 DE DE69633789T patent/DE69633789T2/en not_active Expired - Lifetime
- 1996-09-06 WO PCT/US1996/014281 patent/WO1997009008A1/en active IP Right Grant
- 1996-09-06 AT AT96932961T patent/ATE281129T1/en not_active IP Right Cessation
- 1996-09-06 EP EP96932961A patent/EP0857040B1/en not_active Expired - Lifetime
-
1998
- 1998-01-16 US US09/008,686 patent/US6656214B1/en not_active Expired - Lifetime
-
2003
- 2003-11-14 US US10/712,376 patent/US20040098097A1/en not_active Abandoned
Patent Citations (34)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3890107A (en) * | 1972-09-25 | 1975-06-17 | Research Corp | Materials useful for prosthetic devices and the like |
US3991767A (en) * | 1973-11-02 | 1976-11-16 | Cutter Laboratories, Inc. | Tubular unit with vessel engaging cuff structure |
US4130904A (en) * | 1977-06-06 | 1978-12-26 | Thermo Electron Corporation | Prosthetic blood conduit |
US4580568A (en) * | 1984-10-01 | 1986-04-08 | Cook, Incorporated | Percutaneous endovascular stent and method for insertion thereof |
US4728328A (en) * | 1984-10-19 | 1988-03-01 | Research Corporation | Cuffed tubular organic prostheses |
US4577631A (en) * | 1984-11-16 | 1986-03-25 | Kreamer Jeffry W | Aneurysm repair apparatus and method |
US5749915A (en) * | 1988-08-24 | 1998-05-12 | Focal, Inc. | Polymeric endoluminal paving process |
US5213580A (en) * | 1988-08-24 | 1993-05-25 | Endoluminal Therapeutics, Inc. | Biodegradable polymeric endoluminal sealing process |
US5100429A (en) * | 1989-04-28 | 1992-03-31 | C. R. Bard, Inc. | Endovascular stent and delivery system |
US5330528A (en) * | 1989-12-01 | 1994-07-19 | British Technology Group Limited | Vascular surgical devices |
US5344426A (en) * | 1990-04-25 | 1994-09-06 | Advanced Cardiovascular Systems, Inc. | Method and system for stent delivery |
US5092841A (en) * | 1990-05-17 | 1992-03-03 | Wayne State University | Method for treating an arterial wall injured during angioplasty |
US5522880A (en) * | 1990-06-11 | 1996-06-04 | Barone; Hector D. | Method for repairing an abdominal aortic aneurysm |
US5348788A (en) * | 1991-01-30 | 1994-09-20 | Interpore Orthopaedics, Inc. | Mesh sheet with microscopic projections and holes |
US5156620A (en) * | 1991-02-04 | 1992-10-20 | Pigott John P | Intraluminal graft/stent and balloon catheter for insertion thereof |
US5489295A (en) * | 1991-04-11 | 1996-02-06 | Endovascular Technologies, Inc. | Endovascular graft having bifurcation and apparatus and method for deploying the same |
US5344444A (en) * | 1991-07-03 | 1994-09-06 | Industrial Research B.V. | Expandable ring, cylinder or sleeve which can be made non-deformable |
US5167614A (en) * | 1991-10-29 | 1992-12-01 | Medical Engineering Corporation | Prostatic stent |
US5354329A (en) * | 1992-04-17 | 1994-10-11 | Whalen Biomedical, Inc. | Vascular prosthesis having enhanced compatibility and compliance characteristics |
US5295962A (en) * | 1992-04-29 | 1994-03-22 | Cardiovascular Dynamics, Inc. | Drug delivery and dilatation catheter |
US5334201A (en) * | 1993-03-12 | 1994-08-02 | Cowan Kevin P | Permanent stent made of a cross linkable material |
US5611775A (en) * | 1993-03-15 | 1997-03-18 | Advanced Cardiovascular Systems, Inc. | Method of delivery therapeutic or diagnostic liquid into tissue surrounding a body lumen |
US5618301A (en) * | 1993-10-07 | 1997-04-08 | Angiomed Ag | Reducing stent, device with reducing stent and use of a reducing stent |
US5693088A (en) * | 1993-11-08 | 1997-12-02 | Lazarus; Harrison M. | Intraluminal vascular graft |
US5628784A (en) * | 1994-01-18 | 1997-05-13 | Strecker; Ernst P. | Endoprosthesis that can be percutaneously implanted in the body of a patient |
US5683450A (en) * | 1994-02-09 | 1997-11-04 | Boston Scientific Technology, Inc. | Bifurcated endoluminal prosthesis |
US5462704A (en) * | 1994-04-26 | 1995-10-31 | Industrial Technology Research Institute | Method for preparing a porous polyurethane vascular graft prosthesis |
US5693085A (en) * | 1994-04-29 | 1997-12-02 | Scimed Life Systems, Inc. | Stent with collagen |
US5522881A (en) * | 1994-06-28 | 1996-06-04 | Meadox Medicals, Inc. | Implantable tubular prosthesis having integral cuffs |
US5562727A (en) * | 1994-10-07 | 1996-10-08 | Aeroquip Corporation | Intraluminal graft and method for insertion thereof |
US5674241A (en) * | 1995-02-22 | 1997-10-07 | Menlo Care, Inc. | Covered expanding mesh stent |
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Also Published As
Publication number | Publication date |
---|---|
DE69633789T2 (en) | 2005-11-10 |
WO1997009008A1 (en) | 1997-03-13 |
EP0857040A4 (en) | 1999-03-18 |
US5769882A (en) | 1998-06-23 |
US6656214B1 (en) | 2003-12-02 |
EP0857040A1 (en) | 1998-08-12 |
DE69633789D1 (en) | 2004-12-09 |
EP0857040B1 (en) | 2004-11-03 |
AU7154796A (en) | 1997-03-27 |
ATE281129T1 (en) | 2004-11-15 |
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