WO1992003107A1 - Self-supporting woven vascular graft - Google Patents
Self-supporting woven vascular graft Download PDFInfo
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- WO1992003107A1 WO1992003107A1 PCT/US1991/005907 US9105907W WO9203107A1 WO 1992003107 A1 WO1992003107 A1 WO 1992003107A1 US 9105907 W US9105907 W US 9105907W WO 9203107 A1 WO9203107 A1 WO 9203107A1
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- yarn
- vascular graft
- woven
- multifilament
- graft
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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
-
- D—TEXTILES; PAPER
- D03—WEAVING
- D03D—WOVEN FABRICS; METHODS OF WEAVING; LOOMS
- D03D3/00—Woven fabrics characterised by their shape
- D03D3/02—Tubular fabrics
-
- D—TEXTILES; PAPER
- D03—WEAVING
- D03D—WOVEN FABRICS; METHODS OF WEAVING; LOOMS
- D03D15/00—Woven fabrics characterised by the material, structure or properties of the fibres, filaments, yarns, threads or other warp or weft elements used
- D03D15/20—Woven fabrics characterised by the material, structure or properties of the fibres, filaments, yarns, threads or other warp or weft elements used characterised by the material of the fibres or filaments constituting the yarns or threads
- D03D15/283—Woven fabrics characterised by the material, structure or properties of the fibres, filaments, yarns, threads or other warp or weft elements used characterised by the material of the fibres or filaments constituting the yarns or threads synthetic polymer-based, e.g. polyamide or polyester fibres
-
- D—TEXTILES; PAPER
- D03—WEAVING
- D03D—WOVEN FABRICS; METHODS OF WEAVING; LOOMS
- D03D15/00—Woven fabrics characterised by the material, structure or properties of the fibres, filaments, yarns, threads or other warp or weft elements used
- D03D15/40—Woven fabrics characterised by the material, structure or properties of the fibres, filaments, yarns, threads or other warp or weft elements used characterised by the structure of the yarns or threads
- D03D15/41—Woven fabrics characterised by the material, structure or properties of the fibres, filaments, yarns, threads or other warp or weft elements used characterised by the structure of the yarns or threads with specific twist
-
- D—TEXTILES; PAPER
- D03—WEAVING
- D03D—WOVEN FABRICS; METHODS OF WEAVING; LOOMS
- D03D15/00—Woven fabrics characterised by the material, structure or properties of the fibres, filaments, yarns, threads or other warp or weft elements used
- D03D15/40—Woven fabrics characterised by the material, structure or properties of the fibres, filaments, yarns, threads or other warp or weft elements used characterised by the structure of the yarns or threads
- D03D15/44—Woven fabrics characterised by the material, structure or properties of the fibres, filaments, yarns, threads or other warp or weft elements used characterised by the structure of the yarns or threads with specific cross-section or surface shape
- D03D15/46—Flat yarns, e.g. tapes or films
-
- D—TEXTILES; PAPER
- D03—WEAVING
- D03D—WOVEN FABRICS; METHODS OF WEAVING; LOOMS
- D03D15/00—Woven fabrics characterised by the material, structure or properties of the fibres, filaments, yarns, threads or other warp or weft elements used
- D03D15/40—Woven fabrics characterised by the material, structure or properties of the fibres, filaments, yarns, threads or other warp or weft elements used characterised by the structure of the yarns or threads
- D03D15/49—Woven fabrics characterised by the material, structure or properties of the fibres, filaments, yarns, threads or other warp or weft elements used characterised by the structure of the yarns or threads textured; curled; crimped
-
- D—TEXTILES; PAPER
- D03—WEAVING
- D03D—WOVEN FABRICS; METHODS OF WEAVING; LOOMS
- D03D15/00—Woven fabrics characterised by the material, structure or properties of the fibres, filaments, yarns, threads or other warp or weft elements used
- D03D15/50—Woven fabrics characterised by the material, structure or properties of the fibres, filaments, yarns, threads or other warp or weft elements used characterised by the properties of the yarns or threads
- D03D15/56—Woven fabrics characterised by the material, structure or properties of the fibres, filaments, yarns, threads or other warp or weft elements used characterised by the properties of the yarns or threads elastic
-
- D—TEXTILES; PAPER
- D03—WEAVING
- D03D—WOVEN FABRICS; METHODS OF WEAVING; LOOMS
- D03D15/00—Woven fabrics characterised by the material, structure or properties of the fibres, filaments, yarns, threads or other warp or weft elements used
- D03D15/50—Woven fabrics characterised by the material, structure or properties of the fibres, filaments, yarns, threads or other warp or weft elements used characterised by the properties of the yarns or threads
- D03D15/573—Tensile strength
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- D—TEXTILES; PAPER
- D03—WEAVING
- D03D—WOVEN FABRICS; METHODS OF WEAVING; LOOMS
- D03D27/00—Woven pile fabrics
-
- 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
- A61F2002/065—Y-shaped blood vessels
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- D—TEXTILES; PAPER
- D10—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B2321/00—Fibres made from polymers obtained by reactions only involving carbon-to-carbon unsaturated bonds
- D10B2321/04—Fibres made from polymers obtained by reactions only involving carbon-to-carbon unsaturated bonds polymers of halogenated hydrocarbons
- D10B2321/042—Fibres made from polymers obtained by reactions only involving carbon-to-carbon unsaturated bonds polymers of halogenated hydrocarbons polymers of fluorinated hydrocarbons, e.g. polytetrafluoroethene [PTFE]
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- D—TEXTILES; PAPER
- D10—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B2331/00—Fibres made from polymers obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds, e.g. polycondensation products
- D10B2331/04—Fibres made from polymers obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds, e.g. polycondensation products polyesters, e.g. polyethylene terephthalate [PET]
-
- D—TEXTILES; PAPER
- D10—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B2331/00—Fibres made from polymers obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds, e.g. polycondensation products
- D10B2331/10—Fibres made from polymers obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds, e.g. polycondensation products polyurethanes
-
- D—TEXTILES; PAPER
- D10—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B2401/00—Physical properties
- D10B2401/04—Heat-responsive characteristics
- D10B2401/041—Heat-responsive characteristics thermoplastic; thermosetting
-
- D—TEXTILES; PAPER
- D10—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B2401/00—Physical properties
- D10B2401/06—Load-responsive characteristics
- D10B2401/061—Load-responsive characteristics elastic
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- D—TEXTILES; PAPER
- D10—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B2401/00—Physical properties
- D10B2401/06—Load-responsive characteristics
- D10B2401/062—Load-responsive characteristics stiff, shape retention
-
- D—TEXTILES; PAPER
- D10—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B—INDEXING SCHEME ASSOCIATED WITH SUBLASSES OF SECTION D, RELATING TO TEXTILES
- D10B2509/00—Medical; Hygiene
- D10B2509/06—Vascular grafts; stents
Definitions
- This invention relates to synthetic vascular grafts, and more particularly to synthetic woven vascular grafts including a stiffening component to provide a non-crimped self- supporting graft.
- vascular grafts of synthetic materials are widely used for the replacement of segments of human blood vessels.
- Synthetic vascular grafts have taken a wide variety of configurations and are formed of a wide variety of materials.
- the accepted and successful vascular graft implants are those formed from a biologically compatible material in tubular form which retain an open lumen to permit blood to flow normally through the graft after implantation.
- the biologically compatible materials include thermoplastic materials such as polyester, polytetrafluoroethylene (PTFE) , silicone and polyurethanes.
- the most widely used are polyester fibers and PTFE.
- the polyester fibers usually Dacron, may be knit or woven and may be of a monofilament, multifilament or staple yarn, or combination of each.
- Synthetic fabric vascular grafts may be of a woven, knitted with or without a velour construction.
- a synthetic vascular graft having a warp-knit construction is disclosed by William J. Liebig in U.S. Patent No. 3,945,052.
- Another graft having a warp knit double-velour construction is described by Liebig and German Rodriguez in U.S. Patent No. 4,047,252.
- William J. Liebig and Dennis Cummings describe a synthetic woven double-velour graft in U.S. Patent No. 4,517,687; the velour loops being formed of warp yarns which are texturized preshrunk multifilament yarns.
- U.S. Patent No. 4,892,539 issued to Durmus Koch describes a synthetic fabric woven graft with a single velour on the outer surface.
- the graft is described as woven from multifilament polyester yarns, specifically described as texturized, with the single outer velour formed of filling yarns with each velour loop extending outside a plurality of warp yarns.
- the grafts are compacted by a method such as disclosed in U.S. Patents No. 3,853,462 to Ray E. Smith and No. 3,986,828 to Harmon Hoffman and Jacob Tolsma also assigned to the same assignee as this application. Compaction results in shrinking of the yarns and generally reduces the overall porosity of the fabric substrate.
- These tubular grafts after compacting generally have a diameter from about 6 mm to 40 mm.
- the degree of protection afforded by irregular corrugation varies over the lengths of the tube and can fall below the required level of protection at specific regions.
- the warp-knit and woven grafts described above in U.S. Patent No. 3,945,052, No. 4,047,252 and 4,517,687 are circularly crimped.
- the graft in U.S. Patent No. 4,892,539 is crimped in a spiral fashion. Crimped or corrugated walls can disrupt blood flow and create areas of thick tissue buildup, due to the profile.
- S. Polansky in U.S. Patent No. 3,304,557 avoids crimping in vascular prothesis by forming a tube with repeating reinforcing ring sections.
- a vascular surgeon depends upon several factors. Among the factors included is the particular location of the implantation. This also dictates the size of the graft in order to maintain a sufficiently large or small lumen to accommodate normal blood flow in the region of implantation. The ultimate strength requirements and blood pressure in the location of implantation also affect the selection. Generally, the woven grafts provide greater strength and reduced porosity, but are generally considered to be more difficult to handle and suture. Velours are often preferred because the velour surfaces facilitate growth of tissue into the loops extending from the surface of the velour fabric. The knitted grafts are generally softer and more easily sutured, but are generally more porous. Depending on the location of the implant and heparinization condition of the patient, synthetic fabric grafts generally must be preclotted with the patients blood before implantation. Preclotting may not be essential with a woven graft, but is generally recommended nonetheless.
- Tubular grafts of smaller diameter for example, 6 mm and below are often utilized in peripheral regions of the body and appendages.
- Today, the most successful in this respect are grafts of PTFE of the material disclosed by Robert W. Gore in U.S. Patents Nos. 4,187,390 and No. 3,953,566. These grafts are formed by extrusion of the PTFE material. While accepted for use in small diameter applications, PTFE grafts often require surgical replacement within relatively short periods of time compared to the larger diameter fabric vascular grafts described above.
- a woven synthetic vascular grafts having improved kink resistance including a stiffening component in the filling yarn.
- the stiffening component of the filling yarn provides radial burst strength, dimensional stability and radial rigidity with resiliency to maintain the lumen of the tubular structure open and provide the necessary burst strength properties.
- the graft may also include low modulus elastomeric warp yarns.
- a plurality of elastomeric and multifilament warp yarns are woven in tubular form with a filling yarn of stiffer monofilament and multifilament yarn which have been twisted together.
- the elastomeric warp yarns provide longitudinal compliance (stretch) which aids in bending flexibility.
- the graft surfaces may be smooth or as a single or as a double velour.
- the inner surface is provided with a fine, low profile woven surface to promote smooth, thin pseudointima formation.
- the loops on the exterior surface are formed of multifilament warp yarns which provide the necessary texture cover for tissue adhesion and ingrowth.
- the multifilament warp yarns and the multifilament component of the filling yarns control blood porosity.
- the filling yarn is a monofilament yarn twisted with a multifilament yarn to provide required strength and reduce porosity.
- the self-supporting woven grafts prepared in accordance with the invention are particularly well suited to 2-6 mm diameter peripheral vascular prosthesis, but are suitable for larger dimensions up to about 40 mm as well. Kink resistance is provided without the necessity to crimp the vascular graft.
- Another object of the invention is to provide a self- supporting woven synthetic vascular graft which resists kinking without the need to crimp the graft.
- a further object of the invention is to provide a woven synthetic fabric vascular graft which is suitable for peripheral use in small diameters of 6 mm or less.
- Still another object of the invention is to provide a small diameter woven synthetic fabric vascular graft which resists kinking and provides a desirable amount of longitudinal stretch without crimping.
- Still a further object of the invention is to provide a self-supporting woven synthetic fabric vascular graft which includes an outer velour surface to promote tissue ingrowth.
- Yet another object of the invention is to provide a self-supporting woven synthetic vascular graft having a fine, low profile woven surface to promote smooth, thin pseudointima formation.
- Yet a further object of the invention is to provide a self-supporting woven synthetic fabric single-velour vascular graft having improved kink resistance without crimping.
- Another object of the invention is to provide a method of preparing an improved self-supporting woven synthetic fabric vascular graft in accordance with the invention.
- the invention accordingly comprises the several steps and the relation of one or more of such steps with respect to each of the others, the apparatus embodying features of construction, combination and arrangement of parts which are adapted to effect such steps, and the product which possesses the characteristics, properties, and relation of constituents (components) , all as exemplified in the detailed disclosure hereinafter set forth, and the scope of the invention will be indicated in the claims.
- FIG. 1 is a weaving diagram of a woven synthetic fabric vascular graft prepared in accordance with a preferred embodiment of the invention
- FIG. 2 is a cross-sectional view in schematic in the warp direction of a finished graft section showing the interlacing ends of filling yarn of a graft fabric having the weave pattern of FIG. 1;
- FIG. 3 is a perspective view of a tubular woven single-velour vascular graft prepared in accordance with the invention.
- FIG. 4 is a perspective view of a bifurcated woven single-velour vascular graft prepared in accordance with the invention.
- the woven tubular synthetic vascular grafts prepared in accordance with the invention are applicable to a wide range of diameters, including the small 2 to 6 mm diameter range suitable for peripheral use as well as dimensions up to about 40 mm. Accordingly, the grafts woven having inside diameters which range from about 2 to about 40 mm and are self-supporting and resist kinking without being crimped.
- the stiffening component in the filling yarns may be a textile material, such as a monofilament yarn. Selection will vary depending on the desired characteristic of the tubular graft. However, the stiffening component must be sufficiently stiff to impart dimensional stability and radial rigidity to the tube without crimping.
- the stiffening component should have the following minimum physical properties:
- E is the initial modulus of elasticity
- I is the moment of inertia.
- the diameter can vary depending on desired characteristics, but will typically be in the range of about 2 to 10 mils.
- the woven graft has a diameter less than about 6 mm. In another preferred embodiment the woven graft has an exterior surface with loops and a smooth interior surface.
- the grafts are self- supporting and resistant to kinking without crimping the fabric surface.
- the grafts possess longitudinal elasticity imparted by including a plurality of thermoplastic low modulus elastomeric yarns as a component of the warp yarns.
- Elastomeric Yarns have properties which exhibit high stretch, low modulus, and good elastic recovery. Typical properties for yarns suitable for use would be:
- the resin can either be thermoplastic or thermoset, but should possess good biocompatibility.
- the remaining yarns utilized are those which are compatible biologically. Such yarns include polyethylene terephthalate, polyurethane, polytetrafluoroethylene and silicone. Preferably, the majority of the yarn utilized in the woven graft is polyethylene terephthalate, such as Dacron available from du Pont. The remaining component is the elastomeric yarn which may be present in amounts ranging from about 2 to 20 percent by weight.
- the graft substrate is formed by weaving a plurality of warp yarns including elastomeric yarn and multifilament yarn with filling yarns of stiffer monofilament yarn and multifilament yarn which have been twisted together prior to weaving.
- the stiffer monofilament component of the filling yarn provides mechanical strength, dimensional stability and radial rigidity with resiliency which maintains an open lumen for normal blood flow and provides the necessary burst strength.
- the elastomeric warp yarn component provides longitudinal compliance which aids in bending flexibility.
- the monofilament polyester utilized as a stiffening component in the Examples which follow is a 5 mil polyethylene terephthalate yarn.
- the yarn has the following physical properties:
- Diameter .005 inch (5 mils or 0.127 mm)
- the multifilament warp yarns and multifilament component of the filling yarns provide the necessary texture and cover for tissue adhesion and ingrowth on the outer surface and assist in controlling porosity of the graft.
- the velour loops are of multifilament warp yarns on the outer surface only.
- the inner surface has a fine, low profile which promotes smooth, thin pseudointima formation.
- the particular selection of elastomeric and multifilament warp yarns together with the stiffer combined monofilament and multifilament filling yarns provide a graft having improved kink resistance over a wide range of diameters. Thus, smaller bending radii can be achieved without occluding.
- the external velour surface promotes tissue ingrowth.
- FIG. 1 illustrates the weaving pattern of a woven vascular graft substrate 11 prepared in accordance with a preferred embodiment of the invention.
- Substrate 11 is woven from a plurality of warp ends 12 and filling yarn 13.
- FIG. 2 is a schematic illustration at substrate 11 in cross-section with a smooth interior surface 14 and a velour exterior surface 16 having loops 17 of multifilament warp yarns 19 which stand away from the surface of the graft.
- warp yarns 12 include alternating ground warp ends of a first multifilament yarn 18 and, a low modulus elastomeric monofilament yarn 19.
- multifilament yarn 18 is a one ply seventy denier untexturized preshrunk (flat) polyethylene terephthalate (Dacron) yarn (1/70/54) with a 5z twist (one ply/70 denier 54 filaments) .
- Elastomeric yarn 19 is a 140 denier polyurethane (Lycra Spandex) or an S-E-B-S (styrene- ethylene-butylene-styrene block copoly er) .
- multifilament ground warp yarn 18 Two ends of multifilament ground warp yarn 18 alternate with one end of ground warp elastomeric yarn 19.
- the loop or pile component 19 of warp yarns 12 is a multifilament warp yarn 21 which alternates with each end of warp ground yarns 18 and 19.
- multifilament yarn 21 is an texturized unshrunk 2/40/27 (two ply/40 denier (27 filament) with a 1.55 twist) polyethylene terephthalate (Dacron) yarn.
- Filling yarn 13 is a combined yarn of a monofilament yarn component 22 twisted together with a multifilament yarn component 23 to form filling yarn 13.
- monofilament yarn 12 is a 5 mil polyethylene terephthalate monofilament yarn twisted with multifilament yarn component 23 which is a texturized preshrunk yarn 2/40/27 (1.5s). This is the same yarn as texturized preshrunk warp direction yarn 21.
- the components are twisted 1.5 turns per inch in the "S".
- Elastomeric component 19 of warp yarns 12 may be formed of any one of the biologically compatible materials having a low modulus of elasticity as noted above.
- the modulus of elasticity is typically less than 1 gram per denier with an elongation to break greater than 100 percent.
- the elastic component may be a polyester, polyurethane, silicone or other compatible copolymers such as a styrene-ethylene- butylene-styrene block copolymer known as a C-Flex resin available from Concept Polymers.
- the elastomeric component is present in substrate 11 in an amount between about 2-20 percent by weight.
- elastomeric component 19 is present in an amount about 5 to 10 percent by weight.
- the styrene- ethylene-butylene-styrene block copolymer monofilament yarn is 5 mil C-Flex.
- An alternative preferred yarn suitable for elastomeric component 19 is a Lycra polyurethane yarn of 140 denier.
- FIG. 3 is a perspective view of a tubular graft 31 prepared in accordance with the invention.
- Graft 31 has a smooth inner surface 32 and external raised fabric velour surface 33 having a multiplicity of outwardly extending loops 34.
- FIG. 4 illustrates a bifurcated graft 41 having a main body segment 42 and two legs 43 and 44. Legs 43 and 44 are joined to main body 42 at a crotch 46 which is generally reinforced by a row of stitches 47 to maintain as tight an initial porosity of the graft as possible.
- Graft 41 has a smooth interior surface 48 and an external surface 49 having loops 51.
- loops 34 and 51 of grafts 31 and 41 are formed from multifilament warp pile yarns.
- the pile yarns are texturized unshrunk polyester yarns 21.
- grafts 31 and 41 are scoured and washed in a hot water and detergent bath which results in about 10 to 30 percent longitudinal shrinkage.
- the washed tubes are cut to desired lengths and heatset in a convection oven on straight aluminum mandrels at about 175 ⁇ C for about 15 minutes to one hour.
- the grafts can also be heat set in a non-straight condition to create shaped grafts, such as an aortic arch, which will not have to be bent or shaped by the surgeon during implantation.
- tubular woven vascular grafts 31 and 41 prepared in accordance with the invention are not crimped in order to maintain an open lumen. This is due to inclusion of the relatively stiffer monofilament component 22 in filling yarns 13 and elastomeric component 19 in warp yarns 12.
- Tubular grafts were woven with the following yarns on the pattern of FIG. 1.
- Warp float weave for loop or pile surface
- Crowfoot (floats on outside surfaces. See FIG. 2) alternates every other end (See FIG. 1)
- Dacron 56 Polyester & 5 mil C-Flex alternating 2 ends of Dacron 56 Polyester and 1 end of C-Flex.
- Warp Float 2/40/27 Texturized Unshrunk Dacron 56
- a 140 Denier Lycra Spandex monofilament yarn is utilized as the elastomeric component 19 in the same pattern as substrate 11.
- Tubular vascular grafts having an identical weaving pattern as shown in FIG. 1 are formed with the following specifications:
- Warp float weave for loop or pile surface crowfoot (floats on outside surface, See FIG. 2) weave alternates on every other end (See FIG. 1)
- YARN CONSTRUCTION Warp Ground: 1/70/54 (5z) untexturized unshrunk Dacron 56 polyester and 140 Denier Lycra monofilament, alternating 2 ends of polyester and 1 end of Lycra.
- Warp Float 2/40/27 (1.5s) - Dacron 56 Texturized Preshrunk Polyester.
- the velour for both grafts was formed by weaving every other end in a crowfoot pattern, which allows the warp yarn to float over three picks and under one pick. The remaining adjacent ends form a plain weave. Every third warp end in the lattice structure is Lycra or C-Flex, which in total means that one in six warp ends is elastomeric yarn. The elastomeric yarn causes the fabric to retract in length which raises the floats of the warp weaving in a crowfoot pattern to form loops.
- Example 2 After weaving, the self-supporting woven single velour graft material of Example 2 was scoured and dried and then rinsed to remove trace chemicals and dried again. Scouring shrank or relaxed the graft tubing about 20.5%. The relaxation which occurs contributes to the ultimate longitudinal stretch.
- the tubing was pressed along the tubing edges to remove the crease line formed during weaving.
- the tubing was then cut to 36 cm lengths and heatset by sliding them onto straight aluminum mandrels at the cut length and placed into a convection oven at 121 ⁇ C for 20 minutes.
- the porosity of the grafts was measured using a Wesolowski permeability tester. Six specimens were tested at two locations. The paired values were added together and reported as a single value. The grafts were tested both relaxed and stretched using a 4 lb weight. The results were as follows:
- the average burst strength of the graft was determined by measuring six graft samples on an Instron Tensile Tester and was 509 ⁇ 58psi.
- a woven single velour graft woven with Lycra Spandex [WSV (Lycra) ] was tested for the force required to pull a suture from the end of the graft.
- WSV Lycra Spandex
- One 2-0 Dexon suture was inserted through the graft 3 mm from the edge.
- the graft was mounted in the bottom pneumatic grip of the Instron Tensile Tester and the suture in the top grip.
- the tensile tester was activated to cause the suture to be torn from the graft.
- the graft exhibited a suture pullout of 7.50 ⁇ .3 kg for a cut edge and 7.661.21 kg for cauterized specimens.
- the graft wall thickness and pile height was determined using SEM analysis.
- the average overall wall thickness was 0.80 mm with a pile height of 0.48 mm.
- the longitudinal compliance is a relative measurement of the ability of the graft to elongate at a given force and is expressed as the percent elongation per kilogram force.
- the longitudinal compliance was measured on an Instron Tensile Tester using pneumatic grips as follows.
- the Instron was set to the following settings: Full Scale Load: 2 kg Crosshead Speed: 10 in/min Chart Speed: 10 in/min
- Load Cycling Limits 0.1 kg to 1.0 kg The specimens were mounted in the grips with a preload tension of 0.04 kg. The specimens were cycled between 0.1 and 1.0 kg for a total of 50 cycles. On the 50th cycle, the strip chart recorder was activated to record the event. After the last cycle, the crosshead was returned to the 0.1 kg force and stopped. The extension indicated on the digital readout was recorded. This value was added to the original gauge length of 3 inches to arrive at the effective gauge length for calculating the percent elongation and compliance. The average longitudinal compliance was 23.4 %/kg.
- the relative kink resistance was measured in a dry, non-pressurized condition. This was a quick test to see if the graft could be bent longitudinally without kinking. If or when it did kink, to what extent, as determined by the inside radius of curvature.
- grafts prepared in accordance with the invention are considered kink resistant, since they are flexible longitudinally and can be looped or bent to a significant degree.
- rigid or non-longitudinally compliant grafts or tubular structures will kink immediately upon the application of sufficient stress to deform the structure about their longitudinal axis.
- Radial compression of the graft was measured to determine the crush resistance of the graft.
- Four specimens between 15 and 20 cm in length were individually mounted into an Instron Tensile Tester with a flat plate compression apparatus, which measured 4 inches in diameter. The specimens were mounted into the compression apparatus so that the ends of the grafts extended beyond the ends of the plates. The gap between the upper and lower plates was reduced so that they came into contact with the specimens and exerted a preloaded force of .02 kg. The distance between the plates was measured with a Vernier to the nearest 0.5 mm, which is the initial gap. The crosshead travel was started at a rate of 0.5 inches/min and stopped when the grafts were completely compressed.
- the strip charts generated were analyzed by measuring the slope of the curves to determine the compression moduli.
- the compression modulus is calculated by the following formula:
- the modulus values can be normalized by multiplying them by the inside diameters of the graft.
- the resulting units are grams - millimeter diameter per centimeter length.
- the self-supporting WSV (Lycra) grafts exhibited a radial compression of 28501182 g-mm/cm.
- the radial compression is an important property in contributing to the ability of a graft to resist kinking when deformed. If the radial compression is high with respect to longitudinal compliance or stiffness, then kink resistance is achieved. If radial compression is low, the wall of the graft is more flexible and consequently kinks more readily.
- Graft substrate 11 in FIG. 1 includes every third ground warp end of elastomeric component 19 resulting in one in six warp ends being elastomeric component 19.
- Elastomeric component 19 causes substrate 11 to retract in length which raises the floats of the warp yarns to form loops in a crowfoot pattern to form loops 17.
- Filling yarn 13 includes texturized preshrunk polyester, but may be either texturized or untexturized depending on the shrinkage characteristics desired. The only requirement is that these yarns be multifilament to assist in reducing porosity of the graft and facilitating tissue adhesion and ingrowth after implantation.
- the stiff monofilament component of filling yarn 13 provides radial burst strength, dimensional stability and radial rigidity with resiliency to maintain an open lumen for normal blood flow and provide the necessary burst strength of the graft.
- the characteristics and properties of the graft woven in accordance with the invention can be varied as desired by selection and combination of the starting warp and filling yarns and the weaving pattern.
- the warp ground yarns are multifilament untexturized unshrunk (or flat) polyester, but could be texturized or untexturized preshrunk or unshrunk, or elastomeric yarns.
- the preferred loop yarn is a multifilament texturized polyester yarn, but could also be untexturized, preshrunk or unshrunk. The sole limiting feature is that there be sufficient multifilament yarns considering the desired end results.
- the filling yarn is a composite monofilament twisted with a multifilament component of texturized preshrunk yarn.
Abstract
Description
Claims
Priority Applications (5)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
CA002090435A CA2090435C (en) | 1990-08-28 | 1991-08-27 | Self-supporting woven vascular graft |
EP91915550A EP0546021B1 (en) | 1990-08-28 | 1991-08-27 | Self-supporting woven vascular graft |
AU84379/91A AU659097B2 (en) | 1990-08-28 | 1991-08-27 | Self-supporting woven vascular graft |
DE69114505T DE69114505T2 (en) | 1990-08-28 | 1991-08-27 | SELF-SUPPORTING WOVEN VESSEL TRANSPLANT. |
GR960400158T GR3018760T3 (en) | 1990-08-28 | 1996-01-24 | Self-supporting woven vascular graft. |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US57393290A | 1990-08-28 | 1990-08-28 | |
US573,932 | 1990-08-28 |
Publications (1)
Publication Number | Publication Date |
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WO1992003107A1 true WO1992003107A1 (en) | 1992-03-05 |
Family
ID=24293977
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US1991/005907 WO1992003107A1 (en) | 1990-08-28 | 1991-08-27 | Self-supporting woven vascular graft |
Country Status (12)
Country | Link |
---|---|
US (4) | US5385580A (en) |
EP (1) | EP0546021B1 (en) |
JP (1) | JP2779456B2 (en) |
AT (1) | ATE129882T1 (en) |
AU (1) | AU659097B2 (en) |
CA (1) | CA2090435C (en) |
DE (1) | DE69114505T2 (en) |
DK (1) | DK0546021T3 (en) |
ES (1) | ES2081490T3 (en) |
GR (1) | GR3018760T3 (en) |
IL (1) | IL99326A (en) |
WO (1) | WO1992003107A1 (en) |
Cited By (18)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP0582232A1 (en) * | 1992-08-06 | 1994-02-09 | SORIN BIOMEDICA CARDIO S.p.A. | A process for the manufacture of textile prostheses, for example vascular prostheses, and prostheses obtainable by this process |
WO1996021404A1 (en) * | 1995-01-14 | 1996-07-18 | Prograft, Medical, Inc. | Kink-resistant stent-graft |
WO1997013475A1 (en) * | 1995-10-11 | 1997-04-17 | Schneider (Usa) Inc. | Braided composite prosthesis |
WO1998016173A1 (en) * | 1996-10-11 | 1998-04-23 | C.R. Bard, Inc. | Vascular graft fabric |
WO2000067681A1 (en) * | 1999-05-06 | 2000-11-16 | Koyfman, Ilya | Fabric for use in prosthetics |
WO2001060426A1 (en) * | 2000-02-16 | 2001-08-23 | Viktoria Kantsevitcha | Arterial prosthesis |
WO2002028314A2 (en) * | 2000-10-03 | 2002-04-11 | Scimed Life Systems, Inc. | High profile fabric graft for arteriovenous access |
DE10125712A1 (en) * | 2001-05-21 | 2002-11-28 | Aesculap Ag & Co Kg | Surgical implant, useful particularly for vascular prostheses, comprises woven fabric that is self-sealing when impregnated with blood that then coagulates |
EP1326556A2 (en) * | 2000-10-10 | 2003-07-16 | Prodesco Inc. | Bifurcated fabric sleeve stent graft with junction region strengthening elements |
US6863696B2 (en) | 2000-02-16 | 2005-03-08 | Viktoria Kantsevitcha | Vascular prosthesis |
US7244227B2 (en) | 2003-03-10 | 2007-07-17 | Ams Research Corporation | Implantable penile prosthesis pump |
US7250026B2 (en) | 2003-10-02 | 2007-07-31 | Ams Research Corporation | Implantable penile prosthesis pump |
EP1943983A1 (en) * | 1998-11-30 | 2008-07-16 | Imperial College of Science, Technology and Medicine | Stents for blood vessels |
DE102007063267A1 (en) * | 2007-12-17 | 2009-06-18 | Aesculap Ag | Woven textile vascular prosthesis for forming branch of end-to-side anastomosis, has tubular section comprising hopper, and prosthesis wall in region of concave curve, where wall is weaved thicker than in region with original web connection |
DE102007063265A1 (en) * | 2007-12-17 | 2009-06-18 | Aesculap Ag | Woven textile vascular prosthesis |
WO2009085281A1 (en) * | 2007-12-27 | 2009-07-09 | Cook Incorporated | Implantable device |
US7637861B2 (en) | 2004-12-17 | 2009-12-29 | Ams Research Corporation | Implantable penile prosthesis pump |
US8911350B2 (en) | 2007-10-23 | 2014-12-16 | Ams Research Corporation | Malleable prosthesis with enhanced concealability |
Families Citing this family (298)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5693083A (en) * | 1983-12-09 | 1997-12-02 | Endovascular Technologies, Inc. | Thoracic graft and delivery catheter |
US6344053B1 (en) | 1993-12-22 | 2002-02-05 | Medtronic Ave, Inc. | Endovascular support device and method |
DK0546021T3 (en) * | 1990-08-28 | 1996-03-18 | Meadox Medicals Inc | Self-supporting woven blood vessel graft |
US5282847A (en) * | 1991-02-28 | 1994-02-01 | Medtronic, Inc. | Prosthetic vascular grafts with a pleated structure |
BE1006440A3 (en) * | 1992-12-21 | 1994-08-30 | Dereume Jean Pierre Georges Em | Luminal endoprosthesis AND METHOD OF PREPARATION. |
US5913894A (en) * | 1994-12-05 | 1999-06-22 | Meadox Medicals, Inc. | Solid woven tubular prosthesis |
US5632772A (en) * | 1993-10-21 | 1997-05-27 | Corvita Corporation | Expandable supportive branched endoluminal grafts |
US5639278A (en) * | 1993-10-21 | 1997-06-17 | Corvita Corporation | Expandable supportive bifurcated endoluminal grafts |
US5723004A (en) * | 1993-10-21 | 1998-03-03 | Corvita Corporation | Expandable supportive endoluminal grafts |
US5855598A (en) * | 1993-10-21 | 1999-01-05 | Corvita Corporation | Expandable supportive branched endoluminal grafts |
US5629077A (en) * | 1994-06-27 | 1997-05-13 | Advanced Cardiovascular Systems, Inc. | Biodegradable mesh and film stent |
US5458636A (en) * | 1994-07-20 | 1995-10-17 | U.S. Biomaterials Corporation | Prosthetic device for repair and replacement of fibrous connective tissue |
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 |
CA2161712A1 (en) * | 1994-11-03 | 1996-05-04 | Ketan N. Shah | Silane modified elastomeric compositions and articles made therefrom |
US5800521A (en) * | 1994-11-09 | 1998-09-01 | Endotex Interventional Systems, Inc. | Prosthetic graft and method for aneurysm repair |
JP3611578B2 (en) * | 1994-11-09 | 2005-01-19 | エンドテックス インターベンショナル システムズ,インコーポレイテッド | Delivery catheter and graft for the treatment of aneurysms |
US5683449A (en) * | 1995-02-24 | 1997-11-04 | Marcade; Jean Paul | Modular bifurcated intraluminal grafts and methods for delivering and assembling same |
US6264684B1 (en) | 1995-03-10 | 2001-07-24 | Impra, Inc., A Subsidiary Of C.R. Bard, Inc. | Helically supported graft |
US6451047B2 (en) | 1995-03-10 | 2002-09-17 | Impra, Inc. | Encapsulated intraluminal stent-graft and methods of making same |
US6039755A (en) * | 1997-02-05 | 2000-03-21 | Impra, Inc., A Division Of C.R. Bard, Inc. | Radially expandable tubular polytetrafluoroethylene grafts and method of making same |
CA2215027C (en) * | 1995-03-10 | 2007-04-10 | Impra, Inc. | Endoluminal encapsulated stent and methods of manufacture and endoluminal delivery |
US6124523A (en) * | 1995-03-10 | 2000-09-26 | Impra, Inc. | Encapsulated stent |
US5605696A (en) * | 1995-03-30 | 1997-02-25 | Advanced Cardiovascular Systems, Inc. | Drug loaded polymeric material and method of manufacture |
US5591199A (en) * | 1995-06-07 | 1997-01-07 | Porter; Christopher H. | Curable fiber composite stent and delivery system |
DE69533289T2 (en) | 1995-08-24 | 2005-08-18 | Bard Peripheral Vascular, Inc., Tempe | ARRANGEMENT PROCESS OF A COVERED, ENDOLUMINARY STENT |
US5824037A (en) * | 1995-10-03 | 1998-10-20 | Medtronic, Inc. | Modular intraluminal prostheses construction and methods |
US6193745B1 (en) * | 1995-10-03 | 2001-02-27 | Medtronic, Inc. | Modular intraluminal prosteheses construction and methods |
US6287315B1 (en) | 1995-10-30 | 2001-09-11 | World Medical Manufacturing Corporation | Apparatus for delivering an endoluminal prosthesis |
US5591195A (en) | 1995-10-30 | 1997-01-07 | Taheri; Syde | Apparatus and method for engrafting a blood vessel |
AU1413797A (en) | 1995-12-14 | 1997-07-03 | 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 |
WO1997025002A1 (en) | 1996-01-05 | 1997-07-17 | Medtronic, Inc. | Expansible endoluminal prostheses |
US5843158A (en) * | 1996-01-05 | 1998-12-01 | Medtronic, Inc. | Limited expansion endoluminal prostheses and methods for their use |
US5800514A (en) * | 1996-05-24 | 1998-09-01 | Meadox Medicals, Inc. | Shaped woven tubular soft-tissue prostheses and methods of manufacturing |
US6451044B1 (en) | 1996-09-20 | 2002-09-17 | Board Of Regents, The University Of Texas System | Method and apparatus for heating inflammed tissue |
US5976178A (en) * | 1996-11-07 | 1999-11-02 | Vascular Science Inc. | Medical grafting methods |
US5941908A (en) * | 1997-04-23 | 1999-08-24 | Vascular Science, Inc. | Artificial medical graft with a releasable retainer |
US6120432A (en) * | 1997-04-23 | 2000-09-19 | Vascular Science Inc. | Medical grafting methods and apparatus |
US6036702A (en) * | 1997-04-23 | 2000-03-14 | Vascular Science Inc. | Medical grafting connectors and fasteners |
US6352561B1 (en) | 1996-12-23 | 2002-03-05 | W. L. Gore & Associates | Implant deployment apparatus |
US6551350B1 (en) | 1996-12-23 | 2003-04-22 | Gore Enterprise Holdings, Inc. | Kink resistant bifurcated prosthesis |
SE9700384D0 (en) * | 1997-02-04 | 1997-02-04 | Biacore Ab | Analytical method and apparatus |
US7192450B2 (en) | 2003-05-21 | 2007-03-20 | Dexcom, Inc. | Porous membranes for use with implantable devices |
US6741877B1 (en) * | 1997-03-04 | 2004-05-25 | Dexcom, Inc. | Device and method for determining analyte levels |
US7657297B2 (en) | 2004-05-03 | 2010-02-02 | Dexcom, Inc. | Implantable analyte sensor |
US8527026B2 (en) | 1997-03-04 | 2013-09-03 | Dexcom, Inc. | Device and method for determining analyte levels |
US7899511B2 (en) | 2004-07-13 | 2011-03-01 | Dexcom, Inc. | Low oxygen in vivo analyte sensor |
US6862465B2 (en) | 1997-03-04 | 2005-03-01 | Dexcom, Inc. | Device and method for determining analyte levels |
US6001067A (en) * | 1997-03-04 | 1999-12-14 | Shults; Mark C. | Device and method for determining analyte levels |
US20050033132A1 (en) * | 1997-03-04 | 2005-02-10 | Shults Mark C. | Analyte measuring device |
US9155496B2 (en) | 1997-03-04 | 2015-10-13 | Dexcom, Inc. | Low oxygen in vivo analyte sensor |
US8172897B2 (en) * | 1997-04-15 | 2012-05-08 | Advanced Cardiovascular Systems, Inc. | Polymer and metal composite implantable medical devices |
US10028851B2 (en) * | 1997-04-15 | 2018-07-24 | Advanced Cardiovascular Systems, Inc. | Coatings for controlling erosion of a substrate of an implantable medical device |
US6240616B1 (en) * | 1997-04-15 | 2001-06-05 | Advanced Cardiovascular Systems, Inc. | Method of manufacturing a medicated porous metal prosthesis |
US20020087046A1 (en) * | 1997-04-23 | 2002-07-04 | St. Jude Medical Cardiovascular Group, Inc. | Medical grafting methods and apparatus |
US6776792B1 (en) * | 1997-04-24 | 2004-08-17 | Advanced Cardiovascular Systems Inc. | Coated endovascular stent |
CA2235911C (en) * | 1997-05-27 | 2003-07-29 | Schneider (Usa) Inc. | Stent and stent-graft for treating branched vessels |
US6070589A (en) | 1997-08-01 | 2000-06-06 | Teramed, Inc. | Methods for deploying bypass graft stents |
US6187033B1 (en) * | 1997-09-04 | 2001-02-13 | Meadox Medicals, Inc. | Aortic arch prosthetic graft |
US6371982B2 (en) | 1997-10-09 | 2002-04-16 | St. Jude Medical Cardiovascular Group, Inc. | Graft structures with compliance gradients |
US6048362A (en) * | 1998-01-12 | 2000-04-11 | St. Jude Medical Cardiovascular Group, Inc. | Fluoroscopically-visible flexible graft structures |
US6015432A (en) * | 1998-02-25 | 2000-01-18 | Cordis Corporation | Wire reinforced vascular prosthesis |
US6235054B1 (en) | 1998-02-27 | 2001-05-22 | St. Jude Medical Cardiovascular Group, Inc. | Grafts with suture connectors |
US8974386B2 (en) | 1998-04-30 | 2015-03-10 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US8480580B2 (en) | 1998-04-30 | 2013-07-09 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US9066695B2 (en) | 1998-04-30 | 2015-06-30 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US6175752B1 (en) | 1998-04-30 | 2001-01-16 | Therasense, Inc. | Analyte monitoring device and methods of use |
US8688188B2 (en) | 1998-04-30 | 2014-04-01 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US6949816B2 (en) | 2003-04-21 | 2005-09-27 | Motorola, Inc. | Semiconductor component having first surface area for electrically coupling to a semiconductor chip and second surface area for electrically coupling to a substrate, and method of manufacturing same |
US8346337B2 (en) | 1998-04-30 | 2013-01-01 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US8465425B2 (en) | 1998-04-30 | 2013-06-18 | Abbott Diabetes Care Inc. | Analyte monitoring device and methods of use |
US6159239A (en) * | 1998-08-14 | 2000-12-12 | Prodesco, Inc. | Woven stent/graft structure |
US6475222B1 (en) * | 1998-11-06 | 2002-11-05 | St. Jude Medical Atg, Inc. | Minimally invasive revascularization apparatus and methods |
US6398803B1 (en) | 1999-02-02 | 2002-06-04 | Impra, Inc., A Subsidiary Of C.R. Bard, Inc. | Partial encapsulation of stents |
WO2000053104A1 (en) * | 1999-03-09 | 2000-09-14 | St. Jude Medical Cardiovascular Group, Inc. | Medical grafting methods and apparatus |
FR2797279B1 (en) * | 1999-08-02 | 2002-03-29 | Fed Mogul Systems Prot Group | TEXTILE SOUND PROTECTION SHEATH |
US6790228B2 (en) * | 1999-12-23 | 2004-09-14 | Advanced Cardiovascular Systems, Inc. | Coating for implantable devices and a method of forming the same |
US6344052B1 (en) | 1999-09-27 | 2002-02-05 | World Medical Manufacturing Corporation | Tubular graft with monofilament fibers |
US7947069B2 (en) * | 1999-11-24 | 2011-05-24 | University Of Washington | Medical devices comprising small fiber biomaterials, and methods of use |
US6251136B1 (en) | 1999-12-08 | 2001-06-26 | Advanced Cardiovascular Systems, Inc. | Method of layering a three-coated stent using pharmacological and polymeric agents |
US6702849B1 (en) | 1999-12-13 | 2004-03-09 | Advanced Cardiovascular Systems, Inc. | Method of processing open-celled microcellular polymeric foams with controlled porosity for use as vascular grafts and stent covers |
US8109994B2 (en) | 2003-01-10 | 2012-02-07 | Abbott Cardiovascular Systems, Inc. | Biodegradable drug delivery material for stent |
US6527801B1 (en) * | 2000-04-13 | 2003-03-04 | Advanced Cardiovascular Systems, Inc. | Biodegradable drug delivery material for stent |
US7875283B2 (en) * | 2000-04-13 | 2011-01-25 | Advanced Cardiovascular Systems, Inc. | Biodegradable polymers for use with implantable medical devices |
US6783793B1 (en) * | 2000-10-26 | 2004-08-31 | Advanced Cardiovascular Systems, Inc. | Selective coating of medical devices |
AU2002230522B2 (en) | 2000-11-15 | 2004-06-03 | Atex Technologies , Inc. | Soft-tissue tubular prostheses with seamed transitions |
US6560471B1 (en) | 2001-01-02 | 2003-05-06 | Therasense, Inc. | Analyte monitoring device and methods of use |
US6955686B2 (en) * | 2001-03-01 | 2005-10-18 | Cordis Corporation | Flexible stent |
US7041468B2 (en) | 2001-04-02 | 2006-05-09 | Therasense, Inc. | Blood glucose tracking apparatus and methods |
US6565659B1 (en) * | 2001-06-28 | 2003-05-20 | Advanced Cardiovascular Systems, Inc. | Stent mounting assembly and a method of using the same to coat a stent |
US6702857B2 (en) | 2001-07-27 | 2004-03-09 | Dexcom, Inc. | Membrane for use with implantable devices |
US20030032874A1 (en) * | 2001-07-27 | 2003-02-13 | Dexcom, Inc. | Sensor head for use with implantable devices |
US7989018B2 (en) * | 2001-09-17 | 2011-08-02 | Advanced Cardiovascular Systems, Inc. | Fluid treatment of a polymeric coating on an implantable medical device |
US7285304B1 (en) | 2003-06-25 | 2007-10-23 | Advanced Cardiovascular Systems, Inc. | Fluid treatment of a polymeric coating on an implantable medical device |
US6863683B2 (en) * | 2001-09-19 | 2005-03-08 | Abbott Laboratoris Vascular Entities Limited | Cold-molding process for loading a stent onto a stent delivery system |
US7147661B2 (en) | 2001-12-20 | 2006-12-12 | Boston Scientific Santa Rosa Corp. | Radially expandable stent |
US9282925B2 (en) * | 2002-02-12 | 2016-03-15 | Dexcom, Inc. | Systems and methods for replacing signal artifacts in a glucose sensor data stream |
US8010174B2 (en) | 2003-08-22 | 2011-08-30 | Dexcom, Inc. | Systems and methods for replacing signal artifacts in a glucose sensor data stream |
US8858434B2 (en) * | 2004-07-13 | 2014-10-14 | Dexcom, Inc. | Transcutaneous analyte sensor |
US8260393B2 (en) | 2003-07-25 | 2012-09-04 | Dexcom, Inc. | Systems and methods for replacing signal data artifacts in a glucose sensor data stream |
US9247901B2 (en) | 2003-08-22 | 2016-02-02 | Dexcom, Inc. | Systems and methods for replacing signal artifacts in a glucose sensor data stream |
US7613491B2 (en) * | 2002-05-22 | 2009-11-03 | Dexcom, Inc. | Silicone based membranes for use in implantable glucose sensors |
US8364229B2 (en) | 2003-07-25 | 2013-01-29 | Dexcom, Inc. | Analyte sensors having a signal-to-noise ratio substantially unaffected by non-constant noise |
US7063721B2 (en) * | 2002-03-20 | 2006-06-20 | Terumo Kabushiki Kaisha | Woven tubing for stent type blood vascular prosthesis and stent type blood vascular prosthesis using the tubing |
US20030187498A1 (en) * | 2002-03-28 | 2003-10-02 | Medtronic Ave, Inc. | Chamfered stent strut and method of making same |
US7226978B2 (en) * | 2002-05-22 | 2007-06-05 | Dexcom, Inc. | Techniques to improve polyurethane membranes for implantable glucose sensors |
US20060258761A1 (en) * | 2002-05-22 | 2006-11-16 | Robert Boock | Silicone based membranes for use in implantable glucose sensors |
US6805706B2 (en) * | 2002-08-15 | 2004-10-19 | Gmp Cardiac Care, Inc. | Stent-graft with rails |
US20060271168A1 (en) * | 2002-10-30 | 2006-11-30 | Klaus Kleine | Degradable medical device |
WO2004045474A1 (en) * | 2002-11-15 | 2004-06-03 | Gmp Cardiac Care, Inc. | Rail stent |
US7758881B2 (en) * | 2004-06-30 | 2010-07-20 | Advanced Cardiovascular Systems, Inc. | Anti-proliferative and anti-inflammatory agent combination for treatment of vascular disorders with an implantable medical device |
US8435550B2 (en) | 2002-12-16 | 2013-05-07 | Abbot Cardiovascular Systems Inc. | Anti-proliferative and anti-inflammatory agent combination for treatment of vascular disorders with an implantable medical device |
US7134999B2 (en) * | 2003-04-04 | 2006-11-14 | Dexcom, Inc. | Optimized sensor geometry for an implantable glucose sensor |
US7875293B2 (en) * | 2003-05-21 | 2011-01-25 | Dexcom, Inc. | Biointerface membranes incorporating bioactive agents |
US7186789B2 (en) * | 2003-06-11 | 2007-03-06 | Advanced Cardiovascular Systems, Inc. | Bioabsorbable, biobeneficial polyester polymers for use in drug eluting stent coatings |
US20050003142A1 (en) * | 2003-07-03 | 2005-01-06 | Williamson Curtis Brian | Pile fabric, and heat modified fiber and related manufacturing process |
WO2005010518A1 (en) * | 2003-07-23 | 2005-02-03 | Dexcom, Inc. | Rolled electrode array and its method for manufacture |
WO2005012871A2 (en) * | 2003-07-25 | 2005-02-10 | Dexcom, Inc. | Increasing bias for oxygen production in an electrode system |
US9763609B2 (en) | 2003-07-25 | 2017-09-19 | Dexcom, Inc. | Analyte sensors having a signal-to-noise ratio substantially unaffected by non-constant noise |
US7761130B2 (en) * | 2003-07-25 | 2010-07-20 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US8423113B2 (en) | 2003-07-25 | 2013-04-16 | Dexcom, Inc. | Systems and methods for processing sensor data |
WO2005012873A2 (en) | 2003-07-25 | 2005-02-10 | Dexcom, Inc. | Electrode systems for electrochemical sensors |
US20070208245A1 (en) * | 2003-08-01 | 2007-09-06 | Brauker James H | Transcutaneous analyte sensor |
US7986986B2 (en) | 2003-08-01 | 2011-07-26 | Dexcom, Inc. | System and methods for processing analyte sensor data |
US8060173B2 (en) | 2003-08-01 | 2011-11-15 | Dexcom, Inc. | System and methods for processing analyte sensor data |
US8160669B2 (en) | 2003-08-01 | 2012-04-17 | Dexcom, Inc. | Transcutaneous analyte sensor |
US7774145B2 (en) | 2003-08-01 | 2010-08-10 | Dexcom, Inc. | Transcutaneous analyte sensor |
US7494465B2 (en) * | 2004-07-13 | 2009-02-24 | Dexcom, Inc. | Transcutaneous analyte sensor |
US7591801B2 (en) | 2004-02-26 | 2009-09-22 | Dexcom, Inc. | Integrated delivery device for continuous glucose sensor |
US8788006B2 (en) * | 2003-08-01 | 2014-07-22 | Dexcom, Inc. | System and methods for processing analyte sensor data |
US8886273B2 (en) * | 2003-08-01 | 2014-11-11 | Dexcom, Inc. | Analyte sensor |
US9135402B2 (en) | 2007-12-17 | 2015-09-15 | Dexcom, Inc. | Systems and methods for processing sensor data |
US8275437B2 (en) * | 2003-08-01 | 2012-09-25 | Dexcom, Inc. | Transcutaneous analyte sensor |
US20190357827A1 (en) | 2003-08-01 | 2019-11-28 | Dexcom, Inc. | Analyte sensor |
US8369919B2 (en) * | 2003-08-01 | 2013-02-05 | Dexcom, Inc. | Systems and methods for processing sensor data |
US8845536B2 (en) * | 2003-08-01 | 2014-09-30 | Dexcom, Inc. | Transcutaneous analyte sensor |
US8761856B2 (en) | 2003-08-01 | 2014-06-24 | Dexcom, Inc. | System and methods for processing analyte sensor data |
US8233959B2 (en) * | 2003-08-22 | 2012-07-31 | Dexcom, Inc. | Systems and methods for processing analyte sensor data |
US20140121989A1 (en) | 2003-08-22 | 2014-05-01 | Dexcom, Inc. | Systems and methods for processing analyte sensor data |
US7920906B2 (en) | 2005-03-10 | 2011-04-05 | Dexcom, Inc. | System and methods for processing analyte sensor data for sensor calibration |
US7198675B2 (en) * | 2003-09-30 | 2007-04-03 | Advanced Cardiovascular Systems | Stent mandrel fixture and method for selectively coating surfaces of a stent |
US7189255B2 (en) * | 2003-10-28 | 2007-03-13 | Cordis Corporation | Prosthesis support ring assembly |
US20050090607A1 (en) * | 2003-10-28 | 2005-04-28 | Dexcom, Inc. | Silicone composition for biocompatible membrane |
US8615282B2 (en) | 2004-07-13 | 2013-12-24 | Dexcom, Inc. | Analyte sensor |
US9247900B2 (en) | 2004-07-13 | 2016-02-02 | Dexcom, Inc. | Analyte sensor |
WO2005051170A2 (en) | 2003-11-19 | 2005-06-09 | Dexcom, Inc. | Integrated receiver for continuous analyte sensor |
DE602004029092D1 (en) * | 2003-12-05 | 2010-10-21 | Dexcom Inc | CALIBRATION METHODS FOR A CONTINUOUSLY WORKING ANALYTIC SENSOR |
US8364231B2 (en) | 2006-10-04 | 2013-01-29 | Dexcom, Inc. | Analyte sensor |
US8423114B2 (en) * | 2006-10-04 | 2013-04-16 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US11633133B2 (en) | 2003-12-05 | 2023-04-25 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US8287453B2 (en) | 2003-12-05 | 2012-10-16 | Dexcom, Inc. | Analyte sensor |
US8532730B2 (en) | 2006-10-04 | 2013-09-10 | Dexcom, Inc. | Analyte sensor |
EP2329763B1 (en) * | 2003-12-09 | 2017-06-21 | DexCom, Inc. | Signal processing for continuous analyte sensor |
US7637868B2 (en) * | 2004-01-12 | 2009-12-29 | Dexcom, Inc. | Composite material for implantable device |
US20050182451A1 (en) * | 2004-01-12 | 2005-08-18 | Adam Griffin | Implantable device with improved radio frequency capabilities |
WO2005079257A2 (en) * | 2004-02-12 | 2005-09-01 | Dexcom, Inc. | Biointerface with macro- and micro- architecture |
US8808228B2 (en) * | 2004-02-26 | 2014-08-19 | Dexcom, Inc. | Integrated medicament delivery device for use with continuous analyte sensor |
US20050214339A1 (en) * | 2004-03-29 | 2005-09-29 | Yiwen Tang | Biologically degradable compositions for medical applications |
US20050288481A1 (en) * | 2004-04-30 | 2005-12-29 | Desnoyer Jessica R | Design of poly(ester amides) for the control of agent-release from polymeric compositions |
US8277713B2 (en) * | 2004-05-03 | 2012-10-02 | Dexcom, Inc. | Implantable analyte sensor |
US8792955B2 (en) | 2004-05-03 | 2014-07-29 | Dexcom, Inc. | Transcutaneous analyte sensor |
US20050245799A1 (en) * | 2004-05-03 | 2005-11-03 | Dexcom, Inc. | Implantable analyte sensor |
US20050288775A1 (en) * | 2004-06-24 | 2005-12-29 | Scimed Life Systems, Inc. | Metallic fibers reinforced textile prosthesis |
US8568469B1 (en) | 2004-06-28 | 2013-10-29 | Advanced Cardiovascular Systems, Inc. | Stent locking element and a method of securing a stent on a delivery system |
US8241554B1 (en) | 2004-06-29 | 2012-08-14 | Advanced Cardiovascular Systems, Inc. | Method of forming a stent pattern on a tube |
US20060015020A1 (en) * | 2004-07-06 | 2006-01-19 | Dexcom, Inc. | Systems and methods for manufacture of an analyte-measuring device including a membrane system |
US8565848B2 (en) * | 2004-07-13 | 2013-10-22 | Dexcom, Inc. | Transcutaneous analyte sensor |
US8452368B2 (en) | 2004-07-13 | 2013-05-28 | Dexcom, Inc. | Transcutaneous analyte sensor |
US20060270922A1 (en) * | 2004-07-13 | 2006-11-30 | Brauker James H | Analyte sensor |
US7783333B2 (en) * | 2004-07-13 | 2010-08-24 | Dexcom, Inc. | Transcutaneous medical device with variable stiffness |
US8747879B2 (en) * | 2006-04-28 | 2014-06-10 | Advanced Cardiovascular Systems, Inc. | Method of fabricating an implantable medical device to reduce chance of late inflammatory response |
US8747878B2 (en) | 2006-04-28 | 2014-06-10 | Advanced Cardiovascular Systems, Inc. | Method of fabricating an implantable medical device by controlling crystalline structure |
US7731890B2 (en) * | 2006-06-15 | 2010-06-08 | Advanced Cardiovascular Systems, Inc. | Methods of fabricating stents with enhanced fracture toughness |
US20060020330A1 (en) * | 2004-07-26 | 2006-01-26 | Bin Huang | Method of fabricating an implantable medical device with biaxially oriented polymers |
US8778256B1 (en) | 2004-09-30 | 2014-07-15 | Advanced Cardiovascular Systems, Inc. | Deformation of a polymer tube in the fabrication of a medical article |
US7971333B2 (en) * | 2006-05-30 | 2011-07-05 | Advanced Cardiovascular Systems, Inc. | Manufacturing process for polymetric stents |
US20060041102A1 (en) * | 2004-08-23 | 2006-02-23 | Advanced Cardiovascular Systems, Inc. | Implantable devices comprising biologically absorbable polymers having constant rate of degradation and methods for fabricating the same |
US9283099B2 (en) * | 2004-08-25 | 2016-03-15 | Advanced Cardiovascular Systems, Inc. | Stent-catheter assembly with a releasable connection for stent retention |
US7229471B2 (en) * | 2004-09-10 | 2007-06-12 | Advanced Cardiovascular Systems, Inc. | Compositions containing fast-leaching plasticizers for improved performance of medical devices |
US8043553B1 (en) | 2004-09-30 | 2011-10-25 | Advanced Cardiovascular Systems, Inc. | Controlled deformation of a polymer tube with a restraining surface in fabricating a medical article |
US7875233B2 (en) | 2004-09-30 | 2011-01-25 | Advanced Cardiovascular Systems, Inc. | Method of fabricating a biaxially oriented implantable medical device |
US8173062B1 (en) | 2004-09-30 | 2012-05-08 | Advanced Cardiovascular Systems, Inc. | Controlled deformation of a polymer tube in fabricating a medical article |
US7833568B2 (en) * | 2005-02-02 | 2010-11-16 | Vartest Labs Inc. | Method of determining the cuticle scale height of fibers |
US20090076360A1 (en) | 2007-09-13 | 2009-03-19 | Dexcom, Inc. | Transcutaneous analyte sensor |
US8133178B2 (en) | 2006-02-22 | 2012-03-13 | Dexcom, Inc. | Analyte sensor |
US20060216431A1 (en) * | 2005-03-28 | 2006-09-28 | Kerrigan Cameron K | Electrostatic abluminal coating of a stent crimped on a balloon catheter |
US20060224226A1 (en) * | 2005-03-31 | 2006-10-05 | Bin Huang | In-vivo radial orientation of a polymeric implantable medical device |
US7381048B2 (en) * | 2005-04-12 | 2008-06-03 | Advanced Cardiovascular Systems, Inc. | Stents with profiles for gripping a balloon catheter and molds for fabricating stents |
US8060174B2 (en) | 2005-04-15 | 2011-11-15 | Dexcom, Inc. | Analyte sensing biointerface |
US7291166B2 (en) * | 2005-05-18 | 2007-11-06 | Advanced Cardiovascular Systems, Inc. | Polymeric stent patterns |
US7622070B2 (en) * | 2005-06-20 | 2009-11-24 | Advanced Cardiovascular Systems, Inc. | Method of manufacturing an implantable polymeric medical device |
US20060292690A1 (en) * | 2005-06-22 | 2006-12-28 | Cesco Bioengineering Co., Ltd. | Method of making cell growth surface |
US7658880B2 (en) * | 2005-07-29 | 2010-02-09 | Advanced Cardiovascular Systems, Inc. | Polymeric stent polishing method and apparatus |
US7297758B2 (en) * | 2005-08-02 | 2007-11-20 | Advanced Cardiovascular Systems, Inc. | Method for extending shelf-life of constructs of semi-crystallizable polymers |
US20070038290A1 (en) * | 2005-08-15 | 2007-02-15 | Bin Huang | Fiber reinforced composite stents |
US7476245B2 (en) * | 2005-08-16 | 2009-01-13 | Advanced Cardiovascular Systems, Inc. | Polymeric stent patterns |
US9248034B2 (en) * | 2005-08-23 | 2016-02-02 | Advanced Cardiovascular Systems, Inc. | Controlled disintegrating implantable medical devices |
US20070045255A1 (en) * | 2005-08-23 | 2007-03-01 | Klaus Kleine | Laser induced plasma machining with an optimized process gas |
US20070045252A1 (en) * | 2005-08-23 | 2007-03-01 | Klaus Kleine | Laser induced plasma machining with a process gas |
US7867547B2 (en) | 2005-12-19 | 2011-01-11 | Advanced Cardiovascular Systems, Inc. | Selectively coating luminal surfaces of stents |
US20070148251A1 (en) * | 2005-12-22 | 2007-06-28 | Hossainy Syed F A | Nanoparticle releasing medical devices |
US20070151961A1 (en) * | 2006-01-03 | 2007-07-05 | Klaus Kleine | Fabrication of an implantable medical device with a modified laser beam |
US20070156230A1 (en) | 2006-01-04 | 2007-07-05 | Dugan Stephen R | Stents with radiopaque markers |
US7951185B1 (en) | 2006-01-06 | 2011-05-31 | Advanced Cardiovascular Systems, Inc. | Delivery of a stent at an elevated temperature |
US9757061B2 (en) | 2006-01-17 | 2017-09-12 | Dexcom, Inc. | Low oxygen in vivo analyte sensor |
US20070179219A1 (en) * | 2006-01-31 | 2007-08-02 | Bin Huang | Method of fabricating an implantable medical device using gel extrusion and charge induced orientation |
US7964210B2 (en) * | 2006-03-31 | 2011-06-21 | Abbott Cardiovascular Systems Inc. | Degradable polymeric implantable medical devices with a continuous phase and discrete phase |
US20070254012A1 (en) * | 2006-04-28 | 2007-11-01 | Ludwig Florian N | Controlled degradation and drug release in stents |
US8069814B2 (en) | 2006-05-04 | 2011-12-06 | Advanced Cardiovascular Systems, Inc. | Stent support devices |
US7785514B2 (en) * | 2006-05-18 | 2010-08-31 | Mccarthy Peter T | Snorkels, flexible tubes, mouthpieces and methods |
US7761968B2 (en) * | 2006-05-25 | 2010-07-27 | Advanced Cardiovascular Systems, Inc. | Method of crimping a polymeric stent |
US20130325105A1 (en) | 2006-05-26 | 2013-12-05 | Abbott Cardiovascular Systems Inc. | Stents With Radiopaque Markers |
US7951194B2 (en) | 2006-05-26 | 2011-05-31 | Abbott Cardiovascular Sysetms Inc. | Bioabsorbable stent with radiopaque coating |
US8343530B2 (en) * | 2006-05-30 | 2013-01-01 | Abbott Cardiovascular Systems Inc. | Polymer-and polymer blend-bioceramic composite implantable medical devices |
US7842737B2 (en) | 2006-09-29 | 2010-11-30 | Abbott Cardiovascular Systems Inc. | Polymer blend-bioceramic composite implantable medical devices |
US20070282434A1 (en) * | 2006-05-30 | 2007-12-06 | Yunbing Wang | Copolymer-bioceramic composite implantable medical devices |
US7959940B2 (en) * | 2006-05-30 | 2011-06-14 | Advanced Cardiovascular Systems, Inc. | Polymer-bioceramic composite implantable medical devices |
US20080058916A1 (en) * | 2006-05-31 | 2008-03-06 | Bin Huang | Method of fabricating polymeric self-expandable stent |
US8034287B2 (en) * | 2006-06-01 | 2011-10-11 | Abbott Cardiovascular Systems Inc. | Radiation sterilization of medical devices |
US8486135B2 (en) | 2006-06-01 | 2013-07-16 | Abbott Cardiovascular Systems Inc. | Implantable medical devices fabricated from branched polymers |
US20070281073A1 (en) * | 2006-06-01 | 2007-12-06 | Gale David C | Enhanced adhesion of drug delivery coatings on stents |
US20070282433A1 (en) * | 2006-06-01 | 2007-12-06 | Limon Timothy A | Stent with retention protrusions formed during crimping |
US20080124372A1 (en) * | 2006-06-06 | 2008-05-29 | Hossainy Syed F A | Morphology profiles for control of agent release rates from polymer matrices |
WO2007143225A2 (en) | 2006-06-07 | 2007-12-13 | Abbott Diabetes Care, Inc. | Analyte monitoring system and method |
US20070286941A1 (en) * | 2006-06-13 | 2007-12-13 | Bin Huang | Surface treatment of a polymeric stent |
US8603530B2 (en) | 2006-06-14 | 2013-12-10 | Abbott Cardiovascular Systems Inc. | Nanoshell therapy |
US8048448B2 (en) * | 2006-06-15 | 2011-11-01 | Abbott Cardiovascular Systems Inc. | Nanoshells for drug delivery |
US8535372B1 (en) | 2006-06-16 | 2013-09-17 | Abbott Cardiovascular Systems Inc. | Bioabsorbable stent with prohealing layer |
US8333000B2 (en) | 2006-06-19 | 2012-12-18 | Advanced Cardiovascular Systems, Inc. | Methods for improving stent retention on a balloon catheter |
US20070290412A1 (en) * | 2006-06-19 | 2007-12-20 | John Capek | Fabricating a stent with selected properties in the radial and axial directions |
US8017237B2 (en) * | 2006-06-23 | 2011-09-13 | Abbott Cardiovascular Systems, Inc. | Nanoshells on polymers |
US9072820B2 (en) * | 2006-06-26 | 2015-07-07 | Advanced Cardiovascular Systems, Inc. | Polymer composite stent with polymer particles |
US8128688B2 (en) * | 2006-06-27 | 2012-03-06 | Abbott Cardiovascular Systems Inc. | Carbon coating on an implantable device |
US20070299511A1 (en) * | 2006-06-27 | 2007-12-27 | Gale David C | Thin stent coating |
US7794776B1 (en) | 2006-06-29 | 2010-09-14 | Abbott Cardiovascular Systems Inc. | Modification of polymer stents with radiation |
US7740791B2 (en) * | 2006-06-30 | 2010-06-22 | Advanced Cardiovascular Systems, Inc. | Method of fabricating a stent with features by blow molding |
US7823263B2 (en) | 2006-07-11 | 2010-11-02 | Abbott Cardiovascular Systems Inc. | Method of removing stent islands from a stent |
US7757543B2 (en) | 2006-07-13 | 2010-07-20 | Advanced Cardiovascular Systems, Inc. | Radio frequency identification monitoring of stents |
US7998404B2 (en) * | 2006-07-13 | 2011-08-16 | Advanced Cardiovascular Systems, Inc. | Reduced temperature sterilization of stents |
US20080014244A1 (en) * | 2006-07-13 | 2008-01-17 | Gale David C | Implantable medical devices and coatings therefor comprising physically crosslinked block copolymers |
US7794495B2 (en) * | 2006-07-17 | 2010-09-14 | Advanced Cardiovascular Systems, Inc. | Controlled degradation of stents |
US7886419B2 (en) * | 2006-07-18 | 2011-02-15 | Advanced Cardiovascular Systems, Inc. | Stent crimping apparatus and method |
US20080091262A1 (en) * | 2006-10-17 | 2008-04-17 | Gale David C | Drug delivery after biodegradation of the stent scaffolding |
US8016879B2 (en) * | 2006-08-01 | 2011-09-13 | Abbott Cardiovascular Systems Inc. | Drug delivery after biodegradation of the stent scaffolding |
US9173733B1 (en) | 2006-08-21 | 2015-11-03 | Abbott Cardiovascular Systems Inc. | Tracheobronchial implantable medical device and methods of use |
KR100770440B1 (en) * | 2006-08-29 | 2007-10-26 | 삼성전기주식회사 | Nitride semiconductor light emitting device |
US7923022B2 (en) * | 2006-09-13 | 2011-04-12 | Advanced Cardiovascular Systems, Inc. | Degradable polymeric implantable medical devices with continuous phase and discrete phase |
US7831287B2 (en) * | 2006-10-04 | 2010-11-09 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US8099849B2 (en) | 2006-12-13 | 2012-01-24 | Abbott Cardiovascular Systems Inc. | Optimizing fracture toughness of polymeric stent |
US8388679B2 (en) | 2007-01-19 | 2013-03-05 | Maquet Cardiovascular Llc | Single continuous piece prosthetic tubular aortic conduit and method for manufacturing the same |
ES2554533T3 (en) * | 2007-03-02 | 2015-12-21 | Atex Technologies, Inc. | Textile medical device with a conical transition and manufacturing method |
US8177834B2 (en) * | 2007-03-12 | 2012-05-15 | Cook Medical Technologies Llc | Woven fabric with shape memory element strands |
US20080243228A1 (en) * | 2007-03-28 | 2008-10-02 | Yunbing Wang | Implantable medical devices fabricated from block copolymers |
US8262723B2 (en) | 2007-04-09 | 2012-09-11 | Abbott Cardiovascular Systems Inc. | Implantable medical devices fabricated from polymer blends with star-block copolymers |
US20200037874A1 (en) | 2007-05-18 | 2020-02-06 | Dexcom, Inc. | Analyte sensors having a signal-to-noise ratio substantially unaffected by non-constant noise |
US7829008B2 (en) * | 2007-05-30 | 2010-11-09 | Abbott Cardiovascular Systems Inc. | Fabricating a stent from a blow molded tube |
US7959857B2 (en) * | 2007-06-01 | 2011-06-14 | Abbott Cardiovascular Systems Inc. | Radiation sterilization of medical devices |
US8293260B2 (en) * | 2007-06-05 | 2012-10-23 | Abbott Cardiovascular Systems Inc. | Elastomeric copolymer coatings containing poly (tetramethyl carbonate) for implantable medical devices |
US20080306582A1 (en) * | 2007-06-05 | 2008-12-11 | Yunbing Wang | Implantable medical devices with elastomeric copolymer coatings |
US8202528B2 (en) * | 2007-06-05 | 2012-06-19 | Abbott Cardiovascular Systems Inc. | Implantable medical devices with elastomeric block copolymer coatings |
US20080306444A1 (en) | 2007-06-08 | 2008-12-11 | Dexcom, Inc. | Integrated medicament delivery device for use with continuous analyte sensor |
US8425591B1 (en) | 2007-06-11 | 2013-04-23 | Abbott Cardiovascular Systems Inc. | Methods of forming polymer-bioceramic composite medical devices with bioceramic particles |
US8048441B2 (en) | 2007-06-25 | 2011-11-01 | Abbott Cardiovascular Systems, Inc. | Nanobead releasing medical devices |
US7901452B2 (en) * | 2007-06-27 | 2011-03-08 | Abbott Cardiovascular Systems Inc. | Method to fabricate a stent having selected morphology to reduce restenosis |
US7955381B1 (en) | 2007-06-29 | 2011-06-07 | Advanced Cardiovascular Systems, Inc. | Polymer-bioceramic composite implantable medical device with different types of bioceramic particles |
EP4159114B1 (en) | 2007-10-09 | 2024-04-10 | DexCom, Inc. | Integrated insulin delivery system with continuous glucose sensor |
US8417312B2 (en) | 2007-10-25 | 2013-04-09 | Dexcom, Inc. | Systems and methods for processing sensor data |
US8290559B2 (en) | 2007-12-17 | 2012-10-16 | Dexcom, Inc. | Systems and methods for processing sensor data |
US8834552B2 (en) * | 2007-12-27 | 2014-09-16 | Cook Medical Technologies Llc | Stent graft having floating yarns |
US8123817B2 (en) * | 2007-12-28 | 2012-02-28 | Boston Scientific Scimed, Inc. | Meshes of variable construction |
EP2252196A4 (en) * | 2008-02-21 | 2013-05-15 | Dexcom Inc | Systems and methods for processing, transmitting and displaying sensor data |
US8196279B2 (en) * | 2008-02-27 | 2012-06-12 | C. R. Bard, Inc. | Stent-graft covering process |
US8396528B2 (en) | 2008-03-25 | 2013-03-12 | Dexcom, Inc. | Analyte sensor |
EP3795987B1 (en) | 2008-09-19 | 2023-10-25 | Dexcom, Inc. | Particle-containing membrane and particulate electrode for analyte sensors |
US20100228337A1 (en) * | 2009-03-04 | 2010-09-09 | Abbott Laboratories Vascular Enterprises Limited | Mirror image stent and method of use |
US9446194B2 (en) | 2009-03-27 | 2016-09-20 | Dexcom, Inc. | Methods and systems for promoting glucose management |
WO2010141553A1 (en) | 2009-06-02 | 2010-12-09 | Surmodics, Inc. | SILANE-FUNCTIONALIZED HYDROPHOBIC a(1→4)GLUCOPYRANOSE POLYMERS AND POLYMERIC MATRICES FOR IMPLANTATION OR INJECTION |
US9628890B2 (en) | 2009-06-10 | 2017-04-18 | Apple Inc. | Electronic device accessories formed from intertwined fibers |
EP2482863A1 (en) | 2009-09-30 | 2012-08-08 | SurModics, Inc. | Hydrophobic polysaccharides with silyl ether linkages having enhanced degradation and medical articles made therefrom |
US8808353B2 (en) | 2010-01-30 | 2014-08-19 | Abbott Cardiovascular Systems Inc. | Crush recoverable polymer scaffolds having a low crossing profile |
US8568471B2 (en) | 2010-01-30 | 2013-10-29 | Abbott Cardiovascular Systems Inc. | Crush recoverable polymer scaffolds |
US8696738B2 (en) | 2010-05-20 | 2014-04-15 | Maquet Cardiovascular Llc | Composite prosthesis with external polymeric support structure and methods of manufacturing the same |
US8696741B2 (en) | 2010-12-23 | 2014-04-15 | Maquet Cardiovascular Llc | Woven prosthesis and method for manufacturing the same |
JP6141827B2 (en) | 2011-04-15 | 2017-06-07 | デックスコム・インコーポレーテッド | Method of operating a system for measuring an analyte and sensor system configured to implement the method |
US8726483B2 (en) | 2011-07-29 | 2014-05-20 | Abbott Cardiovascular Systems Inc. | Methods for uniform crimping and deployment of a polymer scaffold |
US9833597B2 (en) | 2014-05-12 | 2017-12-05 | Cook Medical Technologies Llc | Textile balloon catheters |
US9999527B2 (en) | 2015-02-11 | 2018-06-19 | Abbott Cardiovascular Systems Inc. | Scaffolds having radiopaque markers |
CA2985599A1 (en) * | 2015-05-27 | 2016-12-01 | Toray Industries, Inc. | Tubular woven construct |
US9700443B2 (en) | 2015-06-12 | 2017-07-11 | Abbott Cardiovascular Systems Inc. | Methods for attaching a radiopaque marker to a scaffold |
US10213326B2 (en) | 2015-08-19 | 2019-02-26 | Cook Medical Technologies Llc | Stent graft with fenestration |
US11008676B2 (en) * | 2015-12-16 | 2021-05-18 | Edwards Lifesciences Corporation | Textured woven fabric for use in implantable bioprostheses |
US11331022B2 (en) | 2017-10-24 | 2022-05-17 | Dexcom, Inc. | Pre-connected analyte sensors |
AU2018354120A1 (en) | 2017-10-24 | 2020-04-23 | Dexcom, Inc. | Pre-connected analyte sensors |
US10575973B2 (en) | 2018-04-11 | 2020-03-03 | Abbott Cardiovascular Systems Inc. | Intravascular stent having high fatigue performance |
WO2019208262A1 (en) | 2018-04-26 | 2019-10-31 | 東レ株式会社 | Tubular fabric and base material for medical use using same |
EP4097281A1 (en) * | 2020-03-18 | 2022-12-07 | Edwards Lifesciences Corporation | Textiles, implantable medical devices using such textiles, and processes for making the same |
US11324583B1 (en) | 2021-07-06 | 2022-05-10 | Archo Medical LTDA | Multi-lumen stent-graft and related surgical methods |
Citations (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
GB820014A (en) | 1956-12-21 | 1959-09-16 | Davenport Ltd P | Improvements in woven tubular fabrics |
US3272204A (en) | 1965-09-22 | 1966-09-13 | Ethicon Inc | Absorbable collagen prosthetic implant with non-absorbable reinforcing strands |
US3304557A (en) | 1965-09-28 | 1967-02-21 | Ethicon Inc | Surgical prosthesis |
US3479670A (en) | 1966-10-19 | 1969-11-25 | Ethicon Inc | Tubular prosthetic implant having helical thermoplastic wrapping therearound |
US3953566A (en) | 1970-05-21 | 1976-04-27 | W. L. Gore & Associates, Inc. | Process for producing porous products |
WO1983003752A1 (en) * | 1982-04-30 | 1983-11-10 | Wallsten Hans Ivar | A prosthesis comprising an expansible or contractile tubular body |
EP0122744A1 (en) * | 1983-04-04 | 1984-10-24 | Pfizer Hospital Products Group, Inc. | Triaxially-braided fabric prosthesis |
US4517687A (en) * | 1982-09-15 | 1985-05-21 | Meadox Medicals, Inc. | Synthetic woven double-velour graft |
Family Cites Families (27)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
GB770678A (en) * | 1953-07-02 | 1957-03-20 | Bay Statf Abrasive Products Co | Durable open mesh fabric and process of making same |
US2836181A (en) * | 1955-01-17 | 1958-05-27 | Chemstrand Corp | Flexible nylon tube and method for preparing same |
US3096560A (en) * | 1958-11-21 | 1963-07-09 | William J Liebig | Process for synthetic vascular implants |
NL301060A (en) * | 1962-11-30 | 1900-01-01 | ||
GB1033605A (en) * | 1963-11-25 | 1966-06-22 | Ici Ltd | Woven fabrics |
US3878565A (en) * | 1971-07-14 | 1975-04-22 | Providence Hospital | Vascular prosthesis with external pile surface |
US3853462A (en) * | 1972-02-23 | 1974-12-10 | Meadox Medicals Inc | Compaction of polyester fabric materials |
US3945052A (en) * | 1972-05-01 | 1976-03-23 | Meadox Medicals, Inc. | Synthetic vascular graft and method for manufacturing the same |
US3986828A (en) * | 1974-03-05 | 1976-10-19 | Meadox Medicals, Inc. | Polymer fabric compacting process |
US4192020A (en) * | 1975-05-07 | 1980-03-11 | Washington University | Heart valve prosthesis |
US4191218A (en) * | 1975-05-07 | 1980-03-04 | Albany International Corp. | Fabrics for heart valve and vascular prostheses and methods of fabricating same |
US4340091A (en) * | 1975-05-07 | 1982-07-20 | Albany International Corp. | Elastomeric sheet materials for heart valve and other prosthetic implants |
US4047252A (en) * | 1976-01-29 | 1977-09-13 | Meadox Medicals, Inc. | Double-velour synthetic vascular graft |
FR2364284A1 (en) * | 1976-09-10 | 1978-04-07 | Payen & Cie L | PROCESS FOR THE MANUFACTURE OF A RIGID SLITTED SHAFT AND SHOES THUS REALIZED |
JPS6037734B2 (en) * | 1978-10-12 | 1985-08-28 | 住友電気工業株式会社 | Tubular organ prosthesis material and its manufacturing method |
FR2522696B1 (en) * | 1982-03-05 | 1986-04-11 | Ontario Research Foundation | POROUS POLYMERIC MATERIAL OF TUBULAR FORM FOR USE IN PARTICULAR AS A VASCULAR PROSTHESIS AND METHOD FOR PRODUCING THE SAME |
US4530113A (en) * | 1983-05-20 | 1985-07-23 | Intervascular, Inc. | Vascular grafts with cross-weave patterns |
GB8422530D0 (en) * | 1984-09-06 | 1984-10-10 | Shirley Inst | Production of porous tubes |
US4652264A (en) * | 1985-04-25 | 1987-03-24 | American Cyanamid Company | Prosthetic tubular article |
US4632842A (en) * | 1985-06-20 | 1986-12-30 | Atrium Medical Corporation | Glow discharge process for producing implantable devices |
US4718907A (en) * | 1985-06-20 | 1988-01-12 | Atrium Medical Corporation | Vascular prosthesis having fluorinated coating with varying F/C ratio |
US4652263A (en) * | 1985-06-20 | 1987-03-24 | Atrium Medical Corporation | Elasticization of microporous woven tubes |
US4987665A (en) * | 1986-03-03 | 1991-01-29 | American Cyanamid Company | Prosthetic tubular article |
WO1987005796A1 (en) * | 1986-03-27 | 1987-10-08 | Advanced Vascular Technologies, Inc. | Vascular prostheses apparatus and method of manufacture |
JPH01156571A (en) * | 1987-12-08 | 1989-06-20 | Terumo Corp | Knitted fabric, its production, blood vessel repairing sheet composed of said knitted fabric and artificial blood vessel |
US4892539A (en) * | 1988-02-08 | 1990-01-09 | D-R Medical Systems, Inc. | Vascular graft |
DK0546021T3 (en) * | 1990-08-28 | 1996-03-18 | Meadox Medicals Inc | Self-supporting woven blood vessel graft |
-
1991
- 1991-08-27 DK DK91915550.7T patent/DK0546021T3/en active
- 1991-08-27 DE DE69114505T patent/DE69114505T2/en not_active Expired - Lifetime
- 1991-08-27 CA CA002090435A patent/CA2090435C/en not_active Expired - Lifetime
- 1991-08-27 JP JP3514852A patent/JP2779456B2/en not_active Expired - Fee Related
- 1991-08-27 AT AT91915550T patent/ATE129882T1/en active
- 1991-08-27 WO PCT/US1991/005907 patent/WO1992003107A1/en active IP Right Grant
- 1991-08-27 EP EP91915550A patent/EP0546021B1/en not_active Expired - Lifetime
- 1991-08-27 AU AU84379/91A patent/AU659097B2/en not_active Ceased
- 1991-08-27 ES ES91915550T patent/ES2081490T3/en not_active Expired - Lifetime
- 1991-08-28 IL IL9932691A patent/IL99326A/en not_active IP Right Cessation
-
1992
- 1992-09-21 US US07/949,176 patent/US5385580A/en not_active Expired - Lifetime
-
1993
- 1993-04-19 US US08/049,230 patent/US5282848A/en not_active Expired - Lifetime
-
1994
- 1994-01-31 US US08/189,305 patent/US5487858A/en not_active Expired - Lifetime
- 1994-01-31 US US08/189,310 patent/US5496364A/en not_active Expired - Lifetime
-
1996
- 1996-01-24 GR GR960400158T patent/GR3018760T3/en unknown
Patent Citations (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
GB820014A (en) | 1956-12-21 | 1959-09-16 | Davenport Ltd P | Improvements in woven tubular fabrics |
US3272204A (en) | 1965-09-22 | 1966-09-13 | Ethicon Inc | Absorbable collagen prosthetic implant with non-absorbable reinforcing strands |
US3304557A (en) | 1965-09-28 | 1967-02-21 | Ethicon Inc | Surgical prosthesis |
US3479670A (en) | 1966-10-19 | 1969-11-25 | Ethicon Inc | Tubular prosthetic implant having helical thermoplastic wrapping therearound |
US3953566A (en) | 1970-05-21 | 1976-04-27 | W. L. Gore & Associates, Inc. | Process for producing porous products |
US4187390A (en) | 1970-05-21 | 1980-02-05 | W. L. Gore & Associates, Inc. | Porous products and process therefor |
WO1983003752A1 (en) * | 1982-04-30 | 1983-11-10 | Wallsten Hans Ivar | A prosthesis comprising an expansible or contractile tubular body |
US4517687A (en) * | 1982-09-15 | 1985-05-21 | Meadox Medicals, Inc. | Synthetic woven double-velour graft |
EP0122744A1 (en) * | 1983-04-04 | 1984-10-24 | Pfizer Hospital Products Group, Inc. | Triaxially-braided fabric prosthesis |
Cited By (37)
Publication number | Priority date | Publication date | Assignee | Title |
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EP0582232A1 (en) * | 1992-08-06 | 1994-02-09 | SORIN BIOMEDICA CARDIO S.p.A. | A process for the manufacture of textile prostheses, for example vascular prostheses, and prostheses obtainable by this process |
US5611127A (en) * | 1992-08-06 | 1997-03-18 | Sorin Biomedica Cardio S.P.A. | Process for the manufacture of textile structures suitable for use in textile prostheses |
WO1996021404A1 (en) * | 1995-01-14 | 1996-07-18 | Prograft, Medical, Inc. | Kink-resistant stent-graft |
WO1997013475A1 (en) * | 1995-10-11 | 1997-04-17 | Schneider (Usa) Inc. | Braided composite prosthesis |
EP1281374A3 (en) * | 1995-10-11 | 2003-07-09 | Schneider (Usa) Inc. | Braided prosthesis |
WO1998016173A1 (en) * | 1996-10-11 | 1998-04-23 | C.R. Bard, Inc. | Vascular graft fabric |
US5824047A (en) * | 1996-10-11 | 1998-10-20 | C. R. Bard, Inc. | Vascular graft fabric |
EP2281530A1 (en) * | 1998-11-30 | 2011-02-09 | Veryan Medical Limited | Stents for blood vessels |
US8696735B2 (en) | 1998-11-30 | 2014-04-15 | Veryan Medical Limited | Stents for blood vessels |
US8066761B2 (en) | 1998-11-30 | 2011-11-29 | Veryan Medical Limited | Stenting method for blood vessels |
EP1943983A1 (en) * | 1998-11-30 | 2008-07-16 | Imperial College of Science, Technology and Medicine | Stents for blood vessels |
US6346492B1 (en) | 1999-05-06 | 2002-02-12 | American Medical Systems, Inc. | Fabric for use in prosthetics |
WO2000067681A1 (en) * | 1999-05-06 | 2000-11-16 | Koyfman, Ilya | Fabric for use in prosthetics |
US6733527B2 (en) | 1999-05-06 | 2004-05-11 | Ams Research Corporation | Method of controlling penile prosthetic expansion |
WO2001060426A1 (en) * | 2000-02-16 | 2001-08-23 | Viktoria Kantsevitcha | Arterial prosthesis |
US6863696B2 (en) | 2000-02-16 | 2005-03-08 | Viktoria Kantsevitcha | Vascular prosthesis |
US6709467B1 (en) | 2000-02-16 | 2004-03-23 | Viktoria Kantsevitcha | Arterial prosthesis |
WO2002028314A2 (en) * | 2000-10-03 | 2002-04-11 | Scimed Life Systems, Inc. | High profile fabric graft for arteriovenous access |
WO2002028314A3 (en) * | 2000-10-03 | 2003-01-09 | Scimed Life Systems Inc | High profile fabric graft for arteriovenous access |
US6547820B1 (en) | 2000-10-03 | 2003-04-15 | Scimed Life Systems, Inc. | High profile fabric graft for arteriovenous access |
EP1326556A4 (en) * | 2000-10-10 | 2004-09-01 | Prodesco | Bifurcated fabric sleeve stent graft with junction region strengthening elements |
EP1326556A2 (en) * | 2000-10-10 | 2003-07-16 | Prodesco Inc. | Bifurcated fabric sleeve stent graft with junction region strengthening elements |
US7530996B2 (en) | 2001-05-21 | 2009-05-12 | Aesculap Ag & Co. Kg | Surgical implant, method for the production and use thereof |
DE10125712A1 (en) * | 2001-05-21 | 2002-11-28 | Aesculap Ag & Co Kg | Surgical implant, useful particularly for vascular prostheses, comprises woven fabric that is self-sealing when impregnated with blood that then coagulates |
US8591572B2 (en) | 2001-05-21 | 2013-11-26 | Aesculap Ag | Surgical implant, method for the production and use thereof |
DE10125712B4 (en) * | 2001-05-21 | 2012-06-06 | Aesculap Ag | Implant for surgery |
US7244227B2 (en) | 2003-03-10 | 2007-07-17 | Ams Research Corporation | Implantable penile prosthesis pump |
US7250026B2 (en) | 2003-10-02 | 2007-07-31 | Ams Research Corporation | Implantable penile prosthesis pump |
US7914439B2 (en) | 2004-12-17 | 2011-03-29 | Ams Research Corporation | Implantable penile prosthesis pump |
US7637861B2 (en) | 2004-12-17 | 2009-12-29 | Ams Research Corporation | Implantable penile prosthesis pump |
US8911350B2 (en) | 2007-10-23 | 2014-12-16 | Ams Research Corporation | Malleable prosthesis with enhanced concealability |
US9517133B2 (en) | 2007-10-23 | 2016-12-13 | Boston Scientific Scimed, Inc. | Malleable prosthesis with enhanced concealability |
DE102007063267A1 (en) * | 2007-12-17 | 2009-06-18 | Aesculap Ag | Woven textile vascular prosthesis for forming branch of end-to-side anastomosis, has tubular section comprising hopper, and prosthesis wall in region of concave curve, where wall is weaved thicker than in region with original web connection |
EP2074960A1 (en) * | 2007-12-17 | 2009-07-01 | Aesculap AG | Webbed textile stent |
DE102007063265A1 (en) * | 2007-12-17 | 2009-06-18 | Aesculap Ag | Woven textile vascular prosthesis |
US8728151B2 (en) | 2007-12-17 | 2014-05-20 | Aesculap Ag | Woven textile vascular prosthesis |
WO2009085281A1 (en) * | 2007-12-27 | 2009-07-09 | Cook Incorporated | Implantable device |
Also Published As
Publication number | Publication date |
---|---|
US5385580A (en) | 1995-01-31 |
ATE129882T1 (en) | 1995-11-15 |
DE69114505T2 (en) | 1996-04-18 |
CA2090435A1 (en) | 1992-03-01 |
DE69114505D1 (en) | 1995-12-14 |
IL99326A0 (en) | 1992-07-15 |
ES2081490T3 (en) | 1996-03-16 |
AU659097B2 (en) | 1995-05-11 |
IL99326A (en) | 1995-07-31 |
JP2779456B2 (en) | 1998-07-23 |
US5282848A (en) | 1994-02-01 |
DK0546021T3 (en) | 1996-03-18 |
EP0546021B1 (en) | 1995-11-08 |
US5496364A (en) | 1996-03-05 |
JPH06500032A (en) | 1994-01-06 |
CA2090435C (en) | 2000-12-12 |
US5487858A (en) | 1996-01-30 |
EP0546021A1 (en) | 1993-06-16 |
AU8437991A (en) | 1992-03-17 |
GR3018760T3 (en) | 1996-04-30 |
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