US3317924A - Vascular prostheses - Google Patents

Vascular prostheses Download PDF

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US3317924A
US3317924A US283528A US28352863A US3317924A US 3317924 A US3317924 A US 3317924A US 283528 A US283528 A US 283528A US 28352863 A US28352863 A US 28352863A US 3317924 A US3317924 A US 3317924A
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article
porosity
layer
filament
fiber
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US283528A
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Veen Harry H Le
Leonard D Kurtz
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/14—Macromolecular materials
    • 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

Definitions

  • this invention relates to vascular prosthetics having a pre-determined porosity.
  • Prosthetics are known and are commonly manufactured from Dacron (proprietary name for polyethylene terephthalate) or Teflon (proprietary name for polytetrafiuoroethylene) fibers. Such articles are available in essentially four types of construction:
  • the knitted type is highly resistant to fraying on the cut edges.
  • greater care must be taken in handling cut edges and each suture placed well back from the cut edge.
  • a seamless knitted graft the most widely used, as the more open weave allows the blood to penetrate the interstices of the fabric, permits subsequent ingrowth of fibrous tissue to produce firm attachment of the new intima lining on the inner surface.
  • Seamless woven grafts are relatively non-porous and their use is indicated in certain conditions where the clotting mechanism has been temporarily altered by heparinization. From the above it is noted that the seamless knitted grafts are undoubtedly preferred under all the usual conditions and that porosity of the graft is important.
  • this invention essentially comprises Winding a fiber on a form of suitable configuration so that the fibers overlap, and fusing the fibers where they are in contact.
  • the wind ing operation controls porosity and the fusing step forms the wound fibers into an integral article.
  • a fiber for example of Dacron, having a suitable diameter
  • the diameter of the mandrel will determine the inside diameter of the finished article and will depend on the size of the vessel to be repaired.
  • the fiber can be wound back and forth along the mandrel in a number of winding patterns, and the number of turns per unit length plus the thickness of the wound material will determine the porosity.
  • the closeness of turns is easily regulated by ordinary apparatus, such as a universal winder of the type usually found in textile mills.
  • the wound fabric is then fused by means of adhesion between the crossed threads to form an integral article.
  • Various adhesives can be used for this purpose and the Versamids (proprietary name for a series of. polyamide resins produced by the condensation of polycarboxylic acids with polyamines) are one suitable type of adhesive.
  • the fusing step when the foregoing polyamide resin-is employed, can be accomplished by simply curing the heat-setting adhesive.
  • Ultrasonic techniques may also be employed to fuse the fiber.
  • Polyethylene terephthalate is known to be sealable by this technique. See Ultrasonic Splicing of Polyethylene Terephthalate Fibers, by F. P. Alles, appearing in 3,317,924 Patented May 9, 1967 the Journal of the Society of Motion Picture and Television Engineers.
  • the mandrel is part of a universal winder and is supported in a chuck driven by an electric motor.
  • a fiber feeding device is mounted in a carriage movable parallel to the axis of the mandrel.
  • a variable speed and reversible electric motor drives the carriage and feeding device. By varying the speeds of the electric motors, an infinite variety of winding patterns can be achieved.
  • a brush roller coating device is also mounted on the carriage and is adapted to apply a thin coating of a Versamid resin adhesive (Versamid 400) to the Dacron fiber.
  • Adhesive is not applied to the fiber until a layer of fiber has been first wound on the mandrel to prevent the fiber from sticking to the mandrel. While the mandrel is turning, the carriage is caused to traverse the length of the mandrel .several times. The fibers of each layer overlap underlying layers and form a porous hollow tube. For a given number of turns per inch and a given number of layers (which establishes wall thickness) the porosity of the resultant article can be readily determined by experimentation. Once a suitable value is obtained, the process parameters of turns per inch and wall thickness are established. An article having that porosity can thereafter be rapidly fabricated.
  • the Wound fiber is gently heated to cure the resin while still on the mandrel.
  • Curing agents known in the art as suitable catalysts for this reaction may be employed to facilitate the process.
  • a convenient method of heating the article is to employ a steam jacketed mandrel. Hot water or steam circulated through the mandrel efficiently sets the resin.
  • Other heating apparatus, such as heat lamps, may be used.
  • the resin may be applied by other means such as roller coating or dip coating.
  • a method of fabricating a vascular prosthetic article of pre-deterniined porosity comprising winding a nonabsorbable fiber filament suitable for vascular prosthetic use onto a form in a first direction to provide a first helically wound layer of filament on said form, winding said filament in a second opposite direction to provide a second helical layer of filament disposed over said first layer to thereby form a plurality of points of intersection of said filament and to increase the thickness of the wall of the hollow article so formed while at the same time reducing the porosity of said wall, continuing said winding by repeating winding in alternating opposite directions a pre-determined number of times to provide an article of pre-determined wall porosity which porosity renders said article suitable for prosthetic use, and fusing the fiber filaments together at said points of intersection to provide an integral vascular prosthetic article.
  • a method of fabricating a vascular prosthetic article of pre-determined porosity comprising winding a nonabsorbable fiber filament suitable for vascular prosthetic use onto a rotating cylindrical form to provide a first helically wound layer of said fiber on said form, continuing said winding by providing a second helically wound layer over and of opposite hand with respect to said first layer to form a plurality of points of intersection between filaments of said first and second layers and to increase the thickness of the wall of the hollow cylindrical article so formed while simultaneously reducing the porosity of said wall, continuing said winding by providing a pre-determined number of further helically wound layers over said second layer each further layer having a hand opposite to that of the underlying layer to provide a vascular prosthetic article of pre-determined porosity which porosity renders said article suitable for vascular prosthetic use, the fiber of said second and following layers being coated prior to winding with a heat setting adhesive, and heating said vascular prosthetic article to cure set adhesive and to fuse said fiber at said points of intersection to form an integral
  • a vascular prosthetic comprising a hollow tubular article having a wall comprising a plurality of layers of a fiber filament suitable for vascular prosthetic use and wound in the form of a helix, each helical layer being of opposite hand such that a plurality of points of intersection of fibers is present between each helical layer, .said article having a pre-determined porosity suitable for vascu- References Cited by the Examiner UNITED STATES PATENTS 2,127,903 8/1938 Bowen 3l 2,609,320 9/1952 Modigliani l56-174 3,105,492 10/1963 Jeckel l28334 3,105,786 10/1963 Anderson 156-l73 3,106,940 10/1963 Young l38l25 3,108,357 10/1963 Lieb-ig 128334 X FOREIGN PATENTS 874,543 8/ 1961 Great Britain.

Description

United States Patent 0,
3,317,924 VASCULAR PROSTHESES Harry H. Le Veen, 85-35 Midland Parkway, Jamaica, N.Y. 11432, and Leonard D. Kurtz, 46 Woodmere Blvd., Woodmere, N.Y. 11598 No Drawing. Filed May 27., 1963, Ser. N 283,528 6 Claims. (Cl. 3-1) This invention relates to prosthetic articles.
More particularly, this invention relates to vascular prosthetics having a pre-determined porosity.
Prosthetics are known and are commonly manufactured from Dacron (proprietary name for polyethylene terephthalate) or Teflon (proprietary name for polytetrafiuoroethylene) fibers. Such articles are available in essentially four types of construction:
(1) Seamless knitted arterial grafts;
(2) Seamless woven arterial grafts;
(3) Seamless knitted bifurcations; and
(4) Seamless Woven bifurcations.
Of the foregoing, the knitted type is highly resistant to fraying on the cut edges. In the woven type greater care must be taken in handling cut edges and each suture placed well back from the cut edge. A seamless knitted graft, the most widely used, as the more open weave allows the blood to penetrate the interstices of the fabric, permits subsequent ingrowth of fibrous tissue to produce firm attachment of the new intima lining on the inner surface. Seamless woven grafts are relatively non-porous and their use is indicated in certain conditions where the clotting mechanism has been temporarily altered by heparinization. From the above it is noted that the seamless knitted grafts are undoubtedly preferred under all the usual conditions and that porosity of the graft is important.
It is an object of this invention to provide prosthetics of pre-determined porosity and a simple method of manufacturing the same.
It is a further object of the invention to provide a vascular prosthetic of the foregoing characteristics and made from fibers well known to be suitable for such articles.
The foregoing objects are achieved by this invention which essentially comprises Winding a fiber on a form of suitable configuration so that the fibers overlap, and fusing the fibers where they are in contact. The wind ing operation controls porosity and the fusing step forms the wound fibers into an integral article.
To fabricate a vascular prosthetic according to this invention, a fiber, for example of Dacron, having a suitable diameter, is wound on a mandrel. The diameter of the mandrel will determine the inside diameter of the finished article and will depend on the size of the vessel to be repaired. The fiber can be wound back and forth along the mandrel in a number of winding patterns, and the number of turns per unit length plus the thickness of the wound material will determine the porosity. The closeness of turns is easily regulated by ordinary apparatus, such as a universal winder of the type usually found in textile mills.
The wound fabric is then fused by means of adhesion between the crossed threads to form an integral article. Various adhesives can be used for this purpose and the Versamids (proprietary name for a series of. polyamide resins produced by the condensation of polycarboxylic acids with polyamines) are one suitable type of adhesive. The fusing step, when the foregoing polyamide resin-is employed, can be accomplished by simply curing the heat-setting adhesive.
Ultrasonic techniques may also be employed to fuse the fiber. Polyethylene terephthalate is known to be sealable by this technique. See Ultrasonic Splicing of Polyethylene Terephthalate Fibers, by F. P. Alles, appearing in 3,317,924 Patented May 9, 1967 the Journal of the Society of Motion Picture and Television Engineers.
The following example illustrates a preferred embodiment of carrying out the invention, but it is to be understood that this example is given by way of illustration and not limitation.
Example Dacron fiber w-as wound from a bobbin onto a mandrel having a diameter of approximately 0.20". The mandrel is part of a universal winder and is supported in a chuck driven by an electric motor. A fiber feeding device is mounted in a carriage movable parallel to the axis of the mandrel. A variable speed and reversible electric motor drives the carriage and feeding device. By varying the speeds of the electric motors, an infinite variety of winding patterns can be achieved. A brush roller coating device is also mounted on the carriage and is adapted to apply a thin coating of a Versamid resin adhesive (Versamid 400) to the Dacron fiber. Adhesive is not applied to the fiber until a layer of fiber has been first wound on the mandrel to prevent the fiber from sticking to the mandrel. While the mandrel is turning, the carriage is caused to traverse the length of the mandrel .several times. The fibers of each layer overlap underlying layers and form a porous hollow tube. For a given number of turns per inch and a given number of layers (which establishes wall thickness) the porosity of the resultant article can be readily determined by experimentation. Once a suitable value is obtained, the process parameters of turns per inch and wall thickness are established. An article having that porosity can thereafter be rapidly fabricated.
To set the resin and thereby render the article integral, the Wound fiber is gently heated to cure the resin while still on the mandrel. Curing agents known in the art as suitable catalysts for this reaction may be employed to facilitate the process. A convenient method of heating the article is to employ a steam jacketed mandrel. Hot water or steam circulated through the mandrel efficiently sets the resin. Other heating apparatus, such as heat lamps, may be used.
Rather than employ a brush-coating technique, the resin may be applied by other means such as roller coating or dip coating.
The process lends itself to mass production techniques and can employ the usual type of winding equipment. For this reason, no expensive or unusual equipment is necessary.
We claim:
1. A method of fabricating a vascular prosthetic article of pre-deterniined porosity comprising winding a nonabsorbable fiber filament suitable for vascular prosthetic use onto a form in a first direction to provide a first helically wound layer of filament on said form, winding said filament in a second opposite direction to provide a second helical layer of filament disposed over said first layer to thereby form a plurality of points of intersection of said filament and to increase the thickness of the wall of the hollow article so formed while at the same time reducing the porosity of said wall, continuing said winding by repeating winding in alternating opposite directions a pre-determined number of times to provide an article of pre-determined wall porosity which porosity renders said article suitable for prosthetic use, and fusing the fiber filaments together at said points of intersection to provide an integral vascular prosthetic article.
2. A method of fabricating a vascular prosthetic article of pre-determined porosity comprising winding a nonabsorbable fiber filament suitable for vascular prosthetic use onto a rotating cylindrical form to provide a first helically wound layer of said fiber on said form, continuing said winding by providing a second helically wound layer over and of opposite hand with respect to said first layer to form a plurality of points of intersection between filaments of said first and second layers and to increase the thickness of the wall of the hollow cylindrical article so formed while simultaneously reducing the porosity of said wall, continuing said winding by providing a pre-determined number of further helically wound layers over said second layer each further layer having a hand opposite to that of the underlying layer to provide a vascular prosthetic article of pre-determined porosity which porosity renders said article suitable for vascular prosthetic use, the fiber of said second and following layers being coated prior to winding with a heat setting adhesive, and heating said vascular prosthetic article to cure set adhesive and to fuse said fiber at said points of intersection to form an integral vascular prosthetic article.
3. A method according to claim 2 wherein said fiber is polyethylene terephthalate and said adhesive is a polyamide resin.
4. A vascular prosthetic comprising a hollow tubular article having a wall comprising a plurality of layers of a fiber filament suitable for vascular prosthetic use and wound in the form of a helix, each helical layer being of opposite hand such that a plurality of points of intersection of fibers is present between each helical layer, .said article having a pre-determined porosity suitable for vascu- References Cited by the Examiner UNITED STATES PATENTS 2,127,903 8/1938 Bowen 3l 2,609,320 9/1952 Modigliani l56-174 3,105,492 10/1963 Jeckel l28334 3,105,786 10/1963 Anderson 156-l73 3,106,940 10/1963 Young l38l25 3,108,357 10/1963 Lieb-ig 128334 X FOREIGN PATENTS 874,543 8/ 1961 Great Britain.
RICHARD A. GAUDET, Primary Examiner.
ROBERT E. MORGAN, Examiner.
D. L. TRULUCK, Assistant Examiner.

Claims (2)

1. A METHOD OF FABRICATING A VASCULAR PROSTHETIC ARTICLE OF PRE-DETERMINED POROSITY COMPRISING WINDING A NONABSORBABLE FIBER FILAMENT SUITABLE FOR VASCULAR PROSTHETIC USE ONTO A FORM IN A FIRST DIRECTION TO PROVIDE A FIRST HELICALLY WOUND LAYER OF FILAMENT ON SAID FORM, WINDING SAID FILAMENT IN A SECOND OPPOSITE DIRECTION TO PROVIDE A SECOND HELICAL LAYER OF FILAMENT DISPOSED OVER SAID FIRST LAYER TO THEREBY FORM A PLURALITY OF POINTS OF INTERSECTION OF SAID FILAMENT AND TO INCREASE THE THICKNESS OF THE WALL OF THE HOLLOW ARTICLE SO FORMED WHILE AT THE SAME TIME REDUCING THE POROSITY OF SAID WALL, CONTINUING SAID WINDING BY REPEATING WINDING IN ALTERNATING OPPOSITE DIRECTIONS A PRE-DETERMINED NUMBER OF TIMES TO PROVIDE AN ARTICLE OF PRE-DETERMINED WALL POROSITY WHICH POROSITY RENDERS SAID ARTICLE SUITABLE FOR PROSTHETIC USE, AND FUSING THE FIBER FILAMENTS TOGETHER AT SAID POINTS OF INTERSECTION TO PROVIDE AN INTEGRAL VASCULAR PROSTHETIC ARTICLE.
4. A VASCULAR PROSTHETIC COMPRISING A HOLLOW TUBULAR ARTICLE HAVING A WALL COMPRISING A PLURALITY OF LAYERS OF A FIBER FILAMENT SUITABLE FOR VASCULAR PROSTHETIC USE AND WOUND IN THE FORM OF A HELIX, EACH HELICAL LAYER BEING OF OPPOSITE HAND SUCH THAT A PLURALITY OF POINTS OF INTERSECTION OF FIBERS IS PRESENT BETWEEN EACH HELICAL LAYER, SAID ARTICLE HAVING A PRE-DETERMINED POROSITY SUITABLE FOR VASCULAR PROSTHETIC USE AND BEING ESTABLISHED BY THE NUMBER OF HELICAL LAYERS CONSTITUTING SAID WALL, AND THE FIBER OF EACH LAYER BEING FUSED TO EACH ADJACENT LAYER ONLY AT SAID POINTS OF INTERSECTION.
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Cited By (42)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3479670A (en) * 1966-10-19 1969-11-25 Ethicon Inc Tubular prosthetic implant having helical thermoplastic wrapping therearound
US3490975A (en) * 1965-10-18 1970-01-20 Univ Of Birmingham The Method of making an artificial artery of wound silicone rubber thread
US3571815A (en) * 1968-09-19 1971-03-23 John V Somyk Suture ring for heart valve
WO1982001647A1 (en) * 1980-11-17 1982-05-27 Robert L Kaster Vascular graft
FR2522696A1 (en) * 1982-03-05 1983-09-09 Ontario Research Foundation Porous nonwoven tubular implantable prod. - made by winding extruded biocompatible material onto mandrel with simultaneous fibre to fibre bonding of overlying fibres
US4441215A (en) * 1980-11-17 1984-04-10 Kaster Robert L Vascular graft
US4469101A (en) * 1980-10-23 1984-09-04 Battelle Memorial Institute Suture device
US4662884A (en) * 1984-04-25 1987-05-05 University Of Utah Research Foundation Prostheses and methods for promoting nerve regeneration
US4712553A (en) * 1985-05-30 1987-12-15 Cordis Corporation Sutures having a porous surface
US4778467A (en) * 1984-04-25 1988-10-18 The University Of Utah Prostheses and methods for promoting nerve regeneration and for inhibiting the formation of neuromas
US4832025A (en) * 1987-07-30 1989-05-23 American Cyanamid Company Thermoplastic surgical suture with a melt fused length
US4880002A (en) * 1985-05-30 1989-11-14 Corvita Corporation Stretchable porous sutures
US4915893A (en) * 1982-07-16 1990-04-10 Medtronic, Inc. Method of preparing polyester filament material
US5110852A (en) * 1982-07-16 1992-05-05 Rijksuniversiteit Te Groningen Filament material polylactide mixtures
US5383925A (en) * 1992-09-14 1995-01-24 Meadox Medicals, Inc. Three-dimensional braided soft tissue prosthesis
US5562725A (en) * 1992-09-14 1996-10-08 Meadox Medicals Inc. Radially self-expanding implantable intraluminal device
US5628788A (en) * 1995-11-07 1997-05-13 Corvita Corporation Self-expanding endoluminal stent-graft
US5697969A (en) * 1991-03-25 1997-12-16 Meadox Medicals, Inc. Vascular prosthesis and method of implanting
US5700269A (en) * 1995-06-06 1997-12-23 Corvita Corporation Endoluminal prosthesis deployment device for use with prostheses of variable length and having retraction ability
US5726422A (en) * 1996-05-10 1998-03-10 Ethicon, Inc. Apparatus with moving clamp for making surgical sutures, and method for using same
US5741333A (en) * 1995-04-12 1998-04-21 Corvita Corporation Self-expanding stent for a medical device to be introduced into a cavity of a body
US5741332A (en) * 1995-01-23 1998-04-21 Meadox Medicals, Inc. Three-dimensional braided soft tissue prosthesis
US5792181A (en) * 1996-05-10 1998-08-11 Ethicon, Inc. Surgical suture having a thermally formed tip, and apparatus and method for making same
US5813303A (en) * 1996-05-10 1998-09-29 Ethicon, Inc. Apparatus for cutting a surgical suture at two locations
US5849037A (en) * 1995-04-12 1998-12-15 Corvita Corporation Self-expanding stent for a medical device to be introduced into a cavity of a body, and method for its preparation
US5855156A (en) * 1996-05-10 1999-01-05 Ethicon, Inc. Apparatus for cutting a surgical suture tip
US5891166A (en) * 1996-10-30 1999-04-06 Ethicon, Inc. Surgical suture having an ultrasonically formed tip, and apparatus and method for making same
US5913894A (en) * 1994-12-05 1999-06-22 Meadox Medicals, Inc. Solid woven tubular prosthesis
US5968091A (en) * 1996-03-26 1999-10-19 Corvita Corp. Stents and stent grafts having enhanced hoop strength and methods of making the same
US5975876A (en) * 1996-05-10 1999-11-02 Ethicon, Inc. Combined apparatus for heating and cutting a surgical suture tip
US6001121A (en) * 1998-04-14 1999-12-14 Ethicon, Inc. Surgical suture having a thermally formed tip, and apparatus and method for making same
US6035751A (en) * 1998-04-28 2000-03-14 Ethicon, Inc. Method for cutting a surgical suture at two locations
US6126676A (en) * 1996-10-30 2000-10-03 Ethicon, Inc. Surgical tipping apparatus
US20030149472A1 (en) * 1995-11-07 2003-08-07 Leonard Pinchuk Modular endluminal stent-grafts and methods for their use
US6730111B2 (en) 1996-10-30 2004-05-04 Semyon Shchervinsky Surgical tipping apparatus
US20040228411A1 (en) * 2003-05-12 2004-11-18 Sony Corporation Method and system for decoder clock control in presence of jitter
US20050033219A1 (en) * 2003-08-05 2005-02-10 Villafana Manuel A. Grafted network incorporating a multiple channel fluid flow connector
US20050033218A1 (en) * 2003-08-05 2005-02-10 Villafana Manuel A. Grafted network incorporating a multiple channel fluid flow connector
US20050228489A1 (en) * 2004-04-12 2005-10-13 Scimed Life Systems, Inc. Ultrasonic crimping of a varied diameter vascular graft
US7011643B2 (en) 2003-08-05 2006-03-14 Cabg Medical, Inc. Grafted network incorporating a multiple channel fluid flow connector
WO2009093954A1 (en) * 2008-01-21 2009-07-30 Artimplant Ab Fibre-based surgical implant and method of manufacture
US11957811B2 (en) 2008-01-21 2024-04-16 International Life Sciences, Llc Fiber-based surgical implant and method of manufacture

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US2127903A (en) * 1936-05-05 1938-08-23 Davis & Geck Inc Tube for surgical purposes and method of preparing and using the same
US2609320A (en) * 1947-05-29 1952-09-02 Johns Manville Method of making flexible unwoven fabric
GB874543A (en) * 1956-08-14 1961-08-10 Hoechst Ag Manufacture of flexible tubes
US3105786A (en) * 1960-05-05 1963-10-01 Smith Corp A O Method of forming a fiber-reinforced resinous spool
US3105492A (en) * 1958-10-01 1963-10-01 Us Catheter & Instr Corp Synthetic blood vessel grafts
US3106940A (en) * 1961-07-10 1963-10-15 Hercules Powder Co Ltd Manufacture of filament wound articles having reinforcement for openings formed therein
US3108357A (en) * 1962-06-20 1963-10-29 William J Liebig Compound absorbable prosthetic implants, fabrics and yarns therefor

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Publication number Priority date Publication date Assignee Title
US2127903A (en) * 1936-05-05 1938-08-23 Davis & Geck Inc Tube for surgical purposes and method of preparing and using the same
US2609320A (en) * 1947-05-29 1952-09-02 Johns Manville Method of making flexible unwoven fabric
GB874543A (en) * 1956-08-14 1961-08-10 Hoechst Ag Manufacture of flexible tubes
US3105492A (en) * 1958-10-01 1963-10-01 Us Catheter & Instr Corp Synthetic blood vessel grafts
US3105786A (en) * 1960-05-05 1963-10-01 Smith Corp A O Method of forming a fiber-reinforced resinous spool
US3106940A (en) * 1961-07-10 1963-10-15 Hercules Powder Co Ltd Manufacture of filament wound articles having reinforcement for openings formed therein
US3108357A (en) * 1962-06-20 1963-10-29 William J Liebig Compound absorbable prosthetic implants, fabrics and yarns therefor

Cited By (55)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3490975A (en) * 1965-10-18 1970-01-20 Univ Of Birmingham The Method of making an artificial artery of wound silicone rubber thread
US3479670A (en) * 1966-10-19 1969-11-25 Ethicon Inc Tubular prosthetic implant having helical thermoplastic wrapping therearound
US3571815A (en) * 1968-09-19 1971-03-23 John V Somyk Suture ring for heart valve
US4469101A (en) * 1980-10-23 1984-09-04 Battelle Memorial Institute Suture device
WO1982001647A1 (en) * 1980-11-17 1982-05-27 Robert L Kaster Vascular graft
US4441215A (en) * 1980-11-17 1984-04-10 Kaster Robert L Vascular graft
FR2522696A1 (en) * 1982-03-05 1983-09-09 Ontario Research Foundation Porous nonwoven tubular implantable prod. - made by winding extruded biocompatible material onto mandrel with simultaneous fibre to fibre bonding of overlying fibres
US4915893A (en) * 1982-07-16 1990-04-10 Medtronic, Inc. Method of preparing polyester filament material
US5110852A (en) * 1982-07-16 1992-05-05 Rijksuniversiteit Te Groningen Filament material polylactide mixtures
US4778467A (en) * 1984-04-25 1988-10-18 The University Of Utah Prostheses and methods for promoting nerve regeneration and for inhibiting the formation of neuromas
US4662884A (en) * 1984-04-25 1987-05-05 University Of Utah Research Foundation Prostheses and methods for promoting nerve regeneration
US4880002A (en) * 1985-05-30 1989-11-14 Corvita Corporation Stretchable porous sutures
US4712553A (en) * 1985-05-30 1987-12-15 Cordis Corporation Sutures having a porous surface
US4832025A (en) * 1987-07-30 1989-05-23 American Cyanamid Company Thermoplastic surgical suture with a melt fused length
US5697969A (en) * 1991-03-25 1997-12-16 Meadox Medicals, Inc. Vascular prosthesis and method of implanting
US5383925A (en) * 1992-09-14 1995-01-24 Meadox Medicals, Inc. Three-dimensional braided soft tissue prosthesis
US5562725A (en) * 1992-09-14 1996-10-08 Meadox Medicals Inc. Radially self-expanding implantable intraluminal device
US5824034A (en) * 1992-09-14 1998-10-20 Meadox Medicals, Inc. Method for repositioning a radially self-expanding implantable intraluminal device
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