US3688317A - Vascular prosthetic - Google Patents

Vascular prosthetic Download PDF

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US3688317A
US3688317A US66710A US3688317DA US3688317A US 3688317 A US3688317 A US 3688317A US 66710 A US66710 A US 66710A US 3688317D A US3688317D A US 3688317DA US 3688317 A US3688317 A US 3688317A
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anticoagulant
heparin
prosthetic
layer
vascular
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US66710A
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Leonard D Kurtz
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Sutures Inc
MTG Divestitures LLC
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Sutures Inc
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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
    • 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
    • A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A61L27/54—Biologically active materials, e.g. therapeutic substances
    • 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
    • A61L33/00—Antithrombogenic treatment of surgical articles, e.g. sutures, catheters, prostheses, or of articles for the manipulation or conditioning of blood; Materials for such treatment
    • A61L33/0005—Use of materials characterised by their function or physical properties
    • A61L33/0011—Anticoagulant, e.g. heparin, platelet aggregation inhibitor, fibrinolytic agent, other than enzymes, attached to the substrate
    • 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
    • A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/20—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices containing or releasing organic materials
    • A61L2300/204—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices containing or releasing organic materials with nitrogen-containing functional groups, e.g. aminoxides, nitriles, guanidines
    • A61L2300/208—Quaternary ammonium compounds
    • 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
    • A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/20—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices containing or releasing organic materials
    • A61L2300/23—Carbohydrates
    • A61L2300/236—Glycosaminoglycans, e.g. heparin, hyaluronic acid, chondroitin
    • 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
    • A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/40—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a specific therapeutic activity or mode of action
    • A61L2300/404—Biocides, antimicrobial agents, antiseptic agents
    • 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
    • A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/40—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a specific therapeutic activity or mode of action
    • A61L2300/42—Anti-thrombotic agents, anticoagulants, anti-platelet agents
    • 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
    • A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/40—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a specific therapeutic activity or mode of action
    • A61L2300/432—Inhibitors, antagonists
    • 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
    • A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
    • A61L2300/60—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a special physical form
    • A61L2300/606—Coatings
    • A61L2300/608—Coatings having two or more layers
    • A61L2300/61—Coatings having two or more layers containing two or more active agents in different layers

Definitions

  • 1; 128/334 R layer does not contain an anticoagulamand may Com tain an anticoagulant inhibitor or antagonist to permit [56] References cued clot formation adjacent the outer layer to thus prevent UNITED STATES PATENTS exsanguination- 3,105,492 10/1963 Jeckel ..128/334 R 6 Claims, 1 Drawing Figure mfiefiiasw 5 m2 INVENTOR LEONARD D. KURTZ ATTORNEYS BACKGROUND OF THE INVENTION
  • the present invention relates to prosthetic devices, vascular implants and the like for surgical use in the repair and replacement of vessels and tracts in human and animal bodies.
  • vascular prosthetic grafts are employed in various sizes and in all parts of the vascular system, and comprise straight or variously branched tubes of flexible, porous construction or fabrication from fibers or strands run together or interlaced in an interstitial or mesh structure.
  • the vascular prosthetic grafts here concerned desirably are non-toxic and non-allergenic; non-deteriorating upon implantation for prolonged periods; and capable of deforming without collapsing and twisting without kinking. Desirably also the porosity of the grafts on implantation is low enough to permit the implantation without pre-cloting.
  • the body heals by fibrosis; that is, the organisms reaction to the implantation of the foreign body is to attempt to completely encapsulate the graft with fibrous or scar tissue, forming both an outer layer or capsule of fibrous tissue and an inner capsule of fibrous tissue within the lumen of the graft.
  • the healing process is initiated withing hours of implantation by the deposit of a thin fibrous layer or mat on the inside of the graft in contact with the blood stream.
  • the fibrous mat then organized more slowly, within a period of days to weeks, into a layer of mature scar tissue.
  • the origin of the fibroblasts forming the inner layer or capsule is considered to be migration or growth from the outer capsule through the mesh or interstices of the graft.
  • the fibrous inner layer then, is dependent for its blood supply and integrity on interstitial tissue ingrowth, and a principal factor limiting the biological fate of the graft is the case with which the fibrous tissue may grow through the implant wall.
  • vascular prosthetic comprising a porous, multilayered tubular fabric comprising a first tubular fabric layer containing an anticoagulant and a second tubular fabric layer surrounding said first fabric layer, said second layer being free of anticoagulant.
  • the drawing is a perspective view, partially cut away, of a vascular prosthetic according to the present invention.
  • a vascular prosthetic according to the present invention comprises a porous, multilayered tubular fabric 1 comprising a first tubular fabric layer 2 and a second tubular fabric layer surrounding the first tubular fabric layer. A portion of second layer 3 is cut away in the drawing to reveal first layer 2.
  • the multilayered prosthetic is conveniently made by inserting one vascular prosthetic within another and stitching the two together.
  • One or both of the prosthetics may be crimped and each is of conventional construction such as woven or knitted.
  • the composite prosthetic may be in the form shown in US. Pat. No. 3,105,492, herein incorporated by reference.
  • the graft may be fabricated from fibers of synthetic resins useful in prosthetics such as polyesters such as polyethylene terephthalate, polyamides such as nylon 66, acrylics and modacrylics such as Orlon, and polyhalogenated hydrocarbons such as Teflon, or from mixtures of these fibers with one another or with animal derivative fibers such as disclosed in US. Pat. No. 3,316,557, herein incorporated by reference.
  • each layer of the prosthetic, as well as the composite prosthetic is conventional in configuration, the porosity, size and other structural features being selected as desired for a given use according to known considerations.
  • a first fabric layer of the implant is provided with an anticoagulant and a second fabric layer of the implant surrounds the first.
  • the anticoagulant is preferably heparin and is provided in the first layer by impregnation of the fibers making up the layer or by impregnation of the layer prior to assembling the composite prosthetic.
  • a tubular fabric prosthetic of crimped woven Dacron is immersed into a 5 percent aqueous solution of sodium heparin for a few minutes and the thus-impregnated implant is dried providing about 0.5 percent by weight of heparin in the prosthetic.
  • the impregnated prosthetic is then inserted inside a second tubular prosthetic fabric having an inside diameter slightly larger than the outside diameter of the impregnated prosthetic.
  • the second prosthetic is preferably woven more loosely than the first.
  • An implant constructed in the foregoing manner is utilized in surgery in the usual manner.
  • the presence of heparin anticoagulant in the inner layer minimizes the risk of clotting within the implant.
  • the outer layer is free of anticoagulant and permits the formation of clots outside the inner layer thus minimizing the likelihood of exsanguination due to the presence of heparin in the prosthetic.
  • the second layer may be relatively large in thickness relative to the first layer thus providing greater capacity to absorb the anticoagulant.
  • the second layer may comprise a material which inhibits the effect of the anticoagulant.
  • the inhibitor may be the fabric material itself or a material added thereto such as an anticoagulant antagonist or inhibitor.
  • Heparin anticoagulant is an organic acid which will react with a base.
  • the fabric may comprise a basic material, such as silk or other protenaceous fiber, which will chemically combine with heparin thus effectively inhibiting the effect of heparin on clotting in the second fabric layer.
  • the second fabric may be coated or impregnated with a basic salt, such as a quaternary ammonium germicide, for example benzethonium chloride, which will react chemically with heparin to form a highly insoluble material having very little anticoagulating effect.
  • the second fabric may be coated or impregnated with a heparin antagonist such as a protamine or protamine zinc or with an antifibrinolytic agent such as epsilon amino caproic acid.
  • heparin inhibitors which may be provided in the second fabric include Acridine Blue, Polybrene, and Toluidine Blue.
  • the amount of anticoagulant is, in general, less than that which would give the normal dosage of anticoagulant if released.
  • the amount of anticoagulant is not more than one-tenth that amount.
  • the conventional dosage of heparin anticoagulant is about 50 mg i.v. Therefore, the maximum amount of heparin anticoagulant in a prosthetic would generally be about 50 mgm., preferably about 5 mgm.
  • the amount thereof will, in general, be at least an amount sufficient to inhibit a substantial amount of the anticoagulant in the first layer.
  • the amount of inhibitor is at least sufficient to react with a substantial amount, preferably a major proportion of the anticoagulant present in the prosthetic.
  • the maximum amount of the inhibitor is preferably about five times the amount theoretically needed to inhibit all of the anticoagulant, and more preferably, about twice that amount.
  • the preferred prosthetic has two layers as shown, additional fabric layers may be added. However, at least the inner layer will be heparinized in accordance with the invention and at least one outer layer, preferably the outermost layer, will be free of heparin according to the present invention.
  • a vascular prosthetic comprising a porous, multilayered tubular fabric comprising a first tubular fabric layer containing an anticoagulant and a second tubular fabric layer surrounding said first fabric layer, said second layer being free of anticoagulant and containing an inhibitor for said anticoagulant.
  • a vascular prosthetic according to claim 3 wherein said heparin inhibitor is selected from the group consisting of epsilon amino caprioc acid, protamine, protamine zinc, acridine blue, polybrene and toludine blue.

Abstract

A vascular prosthetic comprising a multilayered tubular fabric contains an anticoagulant on an inner layer to reduce the likelihood of clot formation. An outer layer does not contain an anticoagulant and may contain an anticoagulant inhibitor or antagonist to permit clot formation adjacent the outer layer to thus prevent exsanguination.

Description

United States Patent Kurtz Sept. 5, 1972 [54] VASCULAR PROSTHETIC 3,425,418 2/1969 Chvapil et al. ..128/334 R [72] Inventor: Leonard D. Kurtz, Woodmere, N.Y.
Primary ExammerR1chard A. Gaudet [73] Assigneez Sutures Inc., Coventry, Conn. Assistant Examine, Rona1d L Frinks [22] Filed: Aug 5 7 Att0rneyLarson, Taylor and Hinds [21] Appl. No.: 66,710 57 ABSTRACT A vascular prosthetic comprising a multilayered tubu- 3/DIG' lar fabric contains an anticoagulant on an inner layer I! to reduce the of clot formation- An outer [58] Field of Search ..3/l, DIG. 1; 128/334 R layer does not contain an anticoagulamand may Com tain an anticoagulant inhibitor or antagonist to permit [56] References cued clot formation adjacent the outer layer to thus prevent UNITED STATES PATENTS exsanguination- 3,105,492 10/1963 Jeckel ..128/334 R 6 Claims, 1 Drawing Figure mfiefiiasw 5 m2 INVENTOR LEONARD D. KURTZ ATTORNEYS BACKGROUND OF THE INVENTION The present invention relates to prosthetic devices, vascular implants and the like for surgical use in the repair and replacement of vessels and tracts in human and animal bodies.
In the practice of vascular surgery, such defects in he vascular system as aneurysms or occlusions are corrected by the technique of suture anastomosis, by which the area or segment of pathology is excised or resected, and replaced by a prosthetic device, or graft, which is implanted, or sutured in. The vascular prosthetic grafts are employed in various sizes and in all parts of the vascular system, and comprise straight or variously branched tubes of flexible, porous construction or fabrication from fibers or strands run together or interlaced in an interstitial or mesh structure.
The vascular prosthetic grafts here concerned desirably are non-toxic and non-allergenic; non-deteriorating upon implantation for prolonged periods; and capable of deforming without collapsing and twisting without kinking. Desirably also the porosity of the grafts on implantation is low enough to permit the implantation without pre-cloting.
The body heals by fibrosis; that is, the organisms reaction to the implantation of the foreign body is to attempt to completely encapsulate the graft with fibrous or scar tissue, forming both an outer layer or capsule of fibrous tissue and an inner capsule of fibrous tissue within the lumen of the graft. The healing process is initiated withing hours of implantation by the deposit of a thin fibrous layer or mat on the inside of the graft in contact with the blood stream. The fibrous mat then organized more slowly, within a period of days to weeks, into a layer of mature scar tissue. The origin of the fibroblasts forming the inner layer or capsule is considered to be migration or growth from the outer capsule through the mesh or interstices of the graft. The fibrous inner layer, then, is dependent for its blood supply and integrity on interstitial tissue ingrowth, and a principal factor limiting the biological fate of the graft is the case with which the fibrous tissue may grow through the implant wall.
It has been proposed to heparinize the prosthetic to reduce the likelihood of clot formation within the lumen of the graft. The use of an anticoagulant, however, inhibits the formation of clots not only in the graft lumen but throughout the implant itself as well which may result in exsanguination. This adverse result may be minimized by reducing porosity, but this has the adverse effect of interfering with the normal healing process as described above. Alternatively, a reduced amount of heparin may be utilized but this results in increased likelihood of clot formation in the graft lumen. Furthermore, in both of these cases, the anticoagulant affects clotting to substantially the same extend throughout the implant.
It is an object of the present invention to provide a vascular prosthetic which includes an anticoagulant but which is free from the disadvantages mentioned above.
BRIEF SUMMARY OF THE PRESENT INVENTION of the Present Invention The foregoing and other objects are achieved according to the present invention by providing a vascular prosthetic comprising a porous, multilayered tubular fabric comprising a first tubular fabric layer containing an anticoagulant and a second tubular fabric layer surrounding said first fabric layer, said second layer being free of anticoagulant.
DESCRIPTION OF PREFERRED EMBODIMENTS There'follows a detailed description of a preferred embodiment of the invention, together with accompanying drawings. However, it is to be understood that the detailed description and accompanying drawings are provided solely for the purpose of illustrating a preferred embodiment and that the invention is capable of numerous modifications and variations apparent to those skilled in the art without departing from the spirit and scope of the invention.
The drawing is a perspective view, partially cut away, of a vascular prosthetic according to the present invention.
With reference to the drawings, a vascular prosthetic according to the present invention comprises a porous, multilayered tubular fabric 1 comprising a first tubular fabric layer 2 and a second tubular fabric layer surrounding the first tubular fabric layer. A portion of second layer 3 is cut away in the drawing to reveal first layer 2. The multilayered prosthetic is conveniently made by inserting one vascular prosthetic within another and stitching the two together. One or both of the prosthetics may be crimped and each is of conventional construction such as woven or knitted. The composite prosthetic may be in the form shown in US. Pat. No. 3,105,492, herein incorporated by reference. The graft may be fabricated from fibers of synthetic resins useful in prosthetics such as polyesters such as polyethylene terephthalate, polyamides such as nylon 66, acrylics and modacrylics such as Orlon, and polyhalogenated hydrocarbons such as Teflon, or from mixtures of these fibers with one another or with animal derivative fibers such as disclosed in US. Pat. No. 3,316,557, herein incorporated by reference. Thus, each layer of the prosthetic, as well as the composite prosthetic, is conventional in configuration, the porosity, size and other structural features being selected as desired for a given use according to known considerations.
In accordance with the present invention, a first fabric layer of the implant is provided with an anticoagulant and a second fabric layer of the implant surrounds the first. The anticoagulant is preferably heparin and is provided in the first layer by impregnation of the fibers making up the layer or by impregnation of the layer prior to assembling the composite prosthetic. In a preferred embodiment, a tubular fabric prosthetic of crimped woven Dacron is immersed into a 5 percent aqueous solution of sodium heparin for a few minutes and the thus-impregnated implant is dried providing about 0.5 percent by weight of heparin in the prosthetic.
The impregnated prosthetic is then inserted inside a second tubular prosthetic fabric having an inside diameter slightly larger than the outside diameter of the impregnated prosthetic. The second prosthetic is preferably woven more loosely than the first.
An implant constructed in the foregoing manner is utilized in surgery in the usual manner. The presence of heparin anticoagulant in the inner layer minimizes the risk of clotting within the implant. The outer layer, however, is free of anticoagulant and permits the formation of clots outside the inner layer thus minimizing the likelihood of exsanguination due to the presence of heparin in the prosthetic.
The inhibiting effect of the outer layer on the anticoagulant can be enhanced according to the invention in several ways. First, the second layer may be relatively large in thickness relative to the first layer thus providing greater capacity to absorb the anticoagulant. Alternatively, the second layer may comprise a material which inhibits the effect of the anticoagulant. The inhibitor may be the fabric material itself or a material added thereto such as an anticoagulant antagonist or inhibitor.
Heparin anticoagulant is an organic acid which will react with a base. The fabric may comprise a basic material, such as silk or other protenaceous fiber, which will chemically combine with heparin thus effectively inhibiting the effect of heparin on clotting in the second fabric layer.
Where a material is added to the second fabric layer as an inhibiting agent, that material may simply react chemically with the anticoagulant to form a reaction product having no effect on clotting. For example, the second fabric may be coated or impregnated with a basic salt, such as a quaternary ammonium germicide, for example benzethonium chloride, which will react chemically with heparin to form a highly insoluble material having very little anticoagulating effect. Alternatively, the second fabric may be coated or impregnated with a heparin antagonist such as a protamine or protamine zinc or with an antifibrinolytic agent such as epsilon amino caproic acid. Other heparin inhibitors which may be provided in the second fabric include Acridine Blue, Polybrene, and Toluidine Blue.
The amount of anticoagulant is, in general, less than that which would give the normal dosage of anticoagulant if released. Preferably, the amount of anticoagulant is not more than one-tenth that amount. Thus, the conventional dosage of heparin anticoagulant is about 50 mg i.v. Therefore, the maximum amount of heparin anticoagulant in a prosthetic would generally be about 50 mgm., preferably about 5 mgm. Where a heparin antagonist or inhibitor is utilized in the second fabric layer, the amount thereof will, in general, be at least an amount sufficient to inhibit a substantial amount of the anticoagulant in the first layer. For example, where anticoagulant inhibition is achieved by chemical reaction, the amount of inhibitor is at least sufficient to react with a substantial amount, preferably a major proportion of the anticoagulant present in the prosthetic. The maximum amount of the inhibitor is preferably about five times the amount theoretically needed to inhibit all of the anticoagulant, and more preferably, about twice that amount.
While the preferred prosthetic has two layers as shown, additional fabric layers may be added. However, at least the inner layer will be heparinized in accordance with the invention and at least one outer layer, preferably the outermost layer, will be free of heparin according to the present invention.
What is claimed is: 1. A vascular prosthetic comprising a porous, multilayered tubular fabric comprising a first tubular fabric layer containing an anticoagulant and a second tubular fabric layer surrounding said first fabric layer, said second layer being free of anticoagulant and containing an inhibitor for said anticoagulant.
2. A vascular prosthetic according to claim 1 wherein said anticoagulant comprises heparin.
3. A vascular prosthetic according to claim 2 wherein said inhibitor comprises a heparin inhibitor.
4. A vascular prosthetic according to claim 3 wherein said heparin inhibitor is selected from the group consisting of epsilon amino caprioc acid, protamine, protamine zinc, acridine blue, polybrene and toludine blue.
5. A vascular prosthetic according to claim 3 wherein said heparin inhibitor comprises a basic salt capable of reacting with heparin to form an insoluble salt with heparin.
6. A vascular prosthetic according to claim 5 wherein said basic salt comprises a quaternary ammonium salt germicide.

Claims (5)

  1. 2. A vascular prosthetic according to claim 1 wherein said anticoagulant comprises heparin.
  2. 3. A vascular prosthetic according to claim 2 wherein said inhibitor comprises a heparin inhibitor.
  3. 4. A vascular prosthetic according to claim 3 wherein said heparin inhibitor is selected from the group consisting of epsilon amino caprioc acid, protamine, protamine zinc, acridine blue, polybrene and toludine blue.
  4. 5. A vascular prosthetic according to claim 3 wherein said heparin inhibitor comprises a basic salt capable of reacting with heparin to form an insoluble salt with heparin.
  5. 6. A vascular prosthetic according to claim 5 wherein said basic salt comprises a quaternary ammonium salt germicide.
US66710A 1970-08-25 1970-08-25 Vascular prosthetic Expired - Lifetime US3688317A (en)

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CA (1) CA957802A (en)
DE (1) DE2129004B2 (en)
FR (1) FR2112890A5 (en)
GB (1) GB1317842A (en)

Cited By (52)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3908201A (en) * 1972-06-30 1975-09-30 Ici Ltd Prosthetics
US3908657A (en) * 1973-01-15 1975-09-30 Univ Johns Hopkins System for continuous withdrawal of blood
US3976081A (en) * 1974-04-10 1976-08-24 Abraham Lapidot Laminar middle ear vent tube assembly
US4042978A (en) * 1972-06-30 1977-08-23 Imperial Chemical Industries Limited Prosthetics
US4061134A (en) * 1975-10-28 1977-12-06 Samuels Peter B Arterial graft device
US4086665A (en) * 1976-12-16 1978-05-02 Thermo Electron Corporation Artificial blood conduit
US4130904A (en) * 1977-06-06 1978-12-26 Thermo Electron Corporation Prosthetic blood conduit
US4186448A (en) * 1976-04-16 1980-02-05 Brekke John H Device and method for treating and healing a newly created bone void
US4321711A (en) * 1978-10-18 1982-03-30 Sumitomo Electric Industries, Ltd. Vascular prosthesis
US4361552A (en) * 1980-09-26 1982-11-30 Board Of Regents, The University Of Texas System Wound dressing
US4652263A (en) * 1985-06-20 1987-03-24 Atrium Medical Corporation Elasticization of microporous woven tubes
US4814120A (en) * 1984-02-21 1989-03-21 Bioetica S.A. Process for the preparation of collagen tubes
US4870966A (en) * 1988-02-01 1989-10-03 American Cyanamid Company Bioabsorbable surgical device for treating nerve defects
US4871365A (en) * 1985-04-25 1989-10-03 American Cyanamid Company Partially absorbable prosthetic tubular article having an external support
US4986831A (en) * 1988-04-25 1991-01-22 Angeion Corporation Medical implant
US4990158A (en) * 1989-05-10 1991-02-05 United States Surgical Corporation Synthetic semiabsorbable tubular prosthesis
US4997440A (en) * 1985-04-25 1991-03-05 American Cyanamid Company Vascular graft with absorbable and nonabsorbable components
US5084065A (en) * 1989-07-10 1992-01-28 Corvita Corporation Reinforced graft assembly
US5147400A (en) * 1989-05-10 1992-09-15 United States Surgical Corporation Connective tissue prosthesis
US5217495A (en) * 1989-05-10 1993-06-08 United States Surgical Corporation Synthetic semiabsorbable composite yarn
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US20080275544A1 (en) * 1993-04-26 2008-11-06 Medtronic, Inc. Medical devices for delivering a therapeutic agent and method of preparation
US6997949B2 (en) 1993-04-26 2006-02-14 Medtronic, Inc. Medical device for delivering a therapeutic agent and method of preparation
US7811317B2 (en) 1993-04-26 2010-10-12 Medtronic, Inc. Medical devices for delivering a therapeutic agent and method of preparation
US5584877A (en) * 1993-06-25 1996-12-17 Sumitomo Electric Industries, Ltd. Antibacterial vascular prosthesis and surgical suture
US6045560A (en) * 1993-10-06 2000-04-04 United States Surgical Corporation Surgical stapling apparatus with biocompatible surgical fabric
US5908427A (en) * 1993-10-06 1999-06-01 United States Surgical Corporation Surgical stapling apparatus and method
US5964774A (en) * 1993-10-06 1999-10-12 United States Surgical Corporation Surgical stapling apparatus and method with surgical fabric
US5542594A (en) * 1993-10-06 1996-08-06 United States Surgical Corporation Surgical stapling apparatus with biocompatible surgical fabric
US5935594A (en) * 1993-10-28 1999-08-10 Thm Biomedical, Inc. Process and device for treating and healing a tissue deficiency
US5800510A (en) * 1993-12-02 1998-09-01 Meadox Medicals, Inc. Implantable tubular prosthesis
US6814753B2 (en) 1993-12-02 2004-11-09 Scimed Life Systems, Inc. Implantable tubular prosthesis
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US5911753A (en) * 1993-12-02 1999-06-15 Meadox Medicals, Inc. Implantable tubular prosthesis
US5476506A (en) * 1994-02-08 1995-12-19 Ethicon, Inc. Bi-directional crimped graft
US6391052B2 (en) 1994-04-29 2002-05-21 Scimed Life Systems, Inc. Stent with collagen
US5981825A (en) * 1994-05-13 1999-11-09 Thm Biomedical, Inc. Device and methods for in vivo culturing of diverse tissue cells
US6264701B1 (en) 1994-05-13 2001-07-24 Kensey Nash Corporation Device and methods for in vivo culturing of diverse tissue cells
USRE40404E1 (en) 1994-08-02 2008-06-24 Maquet Cardiovascular, Llp Thinly woven flexible graft
US5716660A (en) * 1994-08-12 1998-02-10 Meadox Medicals, Inc. Tubular polytetrafluoroethylene implantable prostheses
US6162247A (en) * 1994-08-12 2000-12-19 Meadox Medicals, Inc. Vascular graft impregnated with a heparin-containing collagen sealant
US5851230A (en) * 1994-08-12 1998-12-22 Meadox Medicals, Inc. Vascular graft with a heparin-containing collagen sealant
US20060159720A1 (en) * 1996-09-13 2006-07-20 Meadox Medicals, Inc. Bioresorbable sealants for porous vascular grafts
US6106454A (en) * 1997-06-17 2000-08-22 Medtronic, Inc. Medical device for delivering localized radiation
US20040111150A1 (en) * 1997-06-17 2004-06-10 Medtronic Vascular, Inc. Medical device for delivering a therapeutic substance and method therefor
US6203536B1 (en) 1997-06-17 2001-03-20 Medtronic, Inc. Medical device for delivering a therapeutic substance and method therefor
US6730120B2 (en) 1997-06-17 2004-05-04 Medtronic, Inc. Medical device for delivering a therapeutic substance and method therefor
US6013099A (en) * 1998-04-29 2000-01-11 Medtronic, Inc. Medical device for delivering a water-insoluble therapeutic salt or substance
US6399144B2 (en) 1998-04-29 2002-06-04 Medtronic Inc. Medical device for delivering a therapeutic substance and method therefor
US6325810B1 (en) 1999-06-30 2001-12-04 Ethicon, Inc. Foam buttress for stapling apparatus
US6273897B1 (en) 2000-02-29 2001-08-14 Ethicon, Inc. Surgical bettress and surgical stapling apparatus
US20070031607A1 (en) * 2000-12-19 2007-02-08 Alexander Dubson Method and apparatus for coating medical implants
US7115220B2 (en) 2000-12-19 2006-10-03 Nicast Ltd. Vascular prosthesis and method for production thereof
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US7276271B2 (en) 2000-12-19 2007-10-02 Nicast Ltd. Polymer fiber tubular structure having kinking resistance
US7112293B2 (en) 2000-12-19 2006-09-26 Nicast Ltd. Method and apparatus for manufacturing polymer fiber shells via electrospinning
US20040054406A1 (en) * 2000-12-19 2004-03-18 Alexander Dubson Vascular prosthesis and method for production thereof
US20040096533A1 (en) * 2000-12-19 2004-05-20 Alexander Dubson Method and apparatus of improving mechanical characteristics of nonwoven materials
US7794219B2 (en) 2001-03-20 2010-09-14 Nicast Ltd. Portable electrospinning device
US20040094873A1 (en) * 2001-03-20 2004-05-20 Alexander Dubson Portable electrospinning device
US8263170B2 (en) 2001-07-30 2012-09-11 Advanced Cardiovascular Systems, Inc. Methods for immobilizing anti-thrombogenic material onto a medical device or into a coating thereon
US20100173065A1 (en) * 2001-07-30 2010-07-08 Advanced Cardiovascular Systems, Inc. Methods For Immobilizing Anti-Thrombogenic Material Onto A Medical Device Or Into A Coating Thereon
US20040030377A1 (en) * 2001-10-19 2004-02-12 Alexander Dubson Medicated polymer-coated stent assembly
US20080200975A1 (en) * 2004-01-06 2008-08-21 Nicast Ltd. Vascular Prosthesis with Anastomotic Member
US9561309B2 (en) 2004-05-27 2017-02-07 Advanced Cardiovascular Systems, Inc. Antifouling heparin coatings
US20100331947A1 (en) * 2005-02-17 2010-12-30 Alon Shalev Inflatable Medical Device
US20100030321A1 (en) * 2008-07-29 2010-02-04 Aga Medical Corporation Medical device including corrugated braid and associated method
US8491649B2 (en) 2008-07-29 2013-07-23 Aga Medical Corporation Medical device including corrugated braid and associated method
US20120295871A1 (en) * 2011-05-19 2012-11-22 Oliva Eugene J Heparin-based compositions and methods for the inhibition of metastasis
US8912167B2 (en) * 2011-05-19 2014-12-16 Eugene J. Oliva Heparin-based compositions and methods for the inhibition of metastasis

Also Published As

Publication number Publication date
JPS5229118B1 (en) 1977-07-30
DE2129004B2 (en) 1972-12-28
FR2112890A5 (en) 1972-06-23
GB1317842A (en) 1973-05-23
DE2129004A1 (en) 1972-03-09
CA957802A (en) 1974-11-19

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