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EP0000949A1 - Prothèses cardiaques et vasculaires et procédé pour leur fabrication - Google Patents

Prothèses cardiaques et vasculaires et procédé pour leur fabrication Download PDF

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Publication number
EP0000949A1
EP0000949A1 EP78100752A EP78100752A EP0000949A1 EP 0000949 A1 EP0000949 A1 EP 0000949A1 EP 78100752 A EP78100752 A EP 78100752A EP 78100752 A EP78100752 A EP 78100752A EP 0000949 A1 EP0000949 A1 EP 0000949A1
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EP
European Patent Office
Prior art keywords
prosthesis
dacron
surface material
protein
graft
Prior art date
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Granted
Application number
EP78100752A
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German (de)
English (en)
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EP0000949B1 (fr
Inventor
Philip Nicholas Sawyer
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Individual
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Publication date
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Publication of EP0000949A1 publication Critical patent/EP0000949A1/fr
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Classifications

    • 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
    • A61F2/0077—Special surfaces of prostheses, e.g. for improving ingrowth
    • 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
    • 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
    • A61L27/28—Materials for coating prostheses
    • A61L27/34—Macromolecular materials
    • 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
    • A61L27/507—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials for artificial 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
    • 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

Definitions

  • This invention relates to cardiac and vascular prostheses and methods of making the same and materials therefor.
  • the Dacron graft is considered to be the most successful cloth type graft. (Sawyer, P. N. et al. Vascular Graft Symposium, Current Status and Future Trends. NIH (1976)).
  • vascular graft must: (i) have an appropriate porosity (10,000-20,000 ml of water/square cm/minute) Sawyer, P. N., Wu, K. T., Wesolowski, S. A. Brattain, W. and Boddy, P. J. An Aid in the Selection of Vascular Prosthesis Proc. Natl. Acad. Sci., U.S.A., 53:1965), (ii) be blood compatible, (iii) possess tensile strength and (iv) be easy to handle with respect to sewing characteristics (Sawyer, P. N. and Srinivasan, S. New Approaches in the Selections of Materials Compatible with Bluod. Artificial Heart Prog.Conf.Proc.Chapter 2,1969).
  • Dacron vascular grafts have been altered, in accordance with the invention, by coating them and filling their interstitial spaces with a variety of agents, in a variety of ways, to produce grafts with superior anti- thrombogenic characteristics.
  • the techniques utilized include: (1) copolymerization of proteins to the Dacron with glutaraldehyde and subsequent negative charging, (2) aluminization of the grafts,
  • a prosthesis suitable for implantation in a bloody environment comprising a surface material adapted for exhibiting a regular and periodic surface charge characteristic in said bloody environment, and prostheses means supporting said surface material and adapted to perform a prosthetic function in this environment.
  • the surface material may be aluminum. In accordance with another embodiment, the surface material may be albumin. In accordance with still other embodiments, the surface material may be agar or acrylamide.
  • the prosthetic means is of a material normally incapable of crosslinking to said surface material.
  • the surface charge is preferably equivalent to approximately one electron per thousand square Angstroms in a regular three-dimensional pattern.
  • a method for preparing a prosthesis for functioning in a bloody environment with minimal thrombogenicity comprises depositing on the surface of the prostheses a material adapted for exhibiting a regular and periodic thrombosis resistant surface charge in the bloody environment.
  • a synthetic material may be adapted for use as a prosthetic material which is adapted to function in a bloody environment. This may be achieved, for example, by metallizing the material at the surface thereof.
  • the metallizing may take place by the vapor depositing of aluminum on the surface.
  • the aluminum may be sprayed in an aerosol on the surface.
  • the prosthesis may be, for example, of woven Dacron. Thereupon may be deposited a surface material in the form of albumin, combined with gelatin. The thusly coated prosthesis may, for example, thereafter be treated with glutaraldehyde.
  • the material deposited on the prosthesis may be , for example, of the general category of proteins and may be applied preferably in, for example, about a 3 % solution.
  • a thusly coated prosthesis may be further treated with a succinic acid compound.
  • the material may be applied by immersing the prosthesis in a slurry of agar.
  • the prosthesis may be immersed in a solution of acrylamide.
  • the invention relates to the provision of a prosthesis having the capability of fuctioning in a bloody environment.
  • the prosthesis may be of varying types but it can be for example, a vascular prosthesis consisting of a tube adapted to function as a connection for bypass or a valve functioning to operate in the cardiac environment.
  • the invention is based in general on having the prosthesis exhibit a regular and periodic negative surface charge characteristic in the preferred case approximating one electron per thousand square Angstroms of surface in a regular threedimensional pattern. Under certain circumstances, the regular and periodic surface charge may be positive.
  • a surface material will generally be employed to exhibit the above-noted characteristic.
  • the present invention is concerned with hybrid prostheses which are prostheses consisting of a basic material forming a prosthesis so that it is capable of performing the desired function and a surface material which exhibits the aforenoted charge.
  • an adaptive material may be provided to offer architectural continuity and cross-link the surface material and the supporting material by being adapted to cross-link itself respectively to each of these materials.
  • the invention offers, for example, copolymerization for a form of protein deposition, metallizing, agar application in the form of a uniform coating and the application of, for example, acrylamide.
  • the invention offers further selective processing of certain of the above materials by treatment with succinic acid or the like or, for example, by treatment with glutaraldehyde.
  • Copolymerization (a method of protein deposition) Fraction V Albumin (purified bovine or other mammalia albumin) purchased from Sigma Corporation, St. Louis, Mo.,USA was dissolved (1, 3, 5 and 10 grams in 100 ml. of water) to produce several solutions of 1 % - 10 % with distilled and deionized water Gelatin (cutaneous), purchased from Baker Corporation * , was dissolved at room temperature in water, producing solutions ranging in concentration (1, 3, 5 and 10 grams in 100 ml of water) from 1 % - 10%.
  • Fraction V Albumin purified bovine or other mammalia albumin
  • a Microknit® knitted or woven vascular prosthesis possessing 18 ridge to the inch (50 interstices per inch) was cut into 10 cm. segmen (collapsed length) and cleaned in distilled and deionized water. It is then immersed in 10-20 % (preferably 20%) qlutaraldehyde (purchased from Electron Microscope Science Corporation of Fort Washington Penna., USA) with distilled and deionized water (40 ml of 50 % glutaraldehyde in 60 ml of water) and was allowed to stand for three hours.
  • the graft materials were then immersed in the appropriate protein (albumin, gelatin, collagen or the like) solution until thin (1 to 2,000 microns) coats of polymerized protein surrounded the Dacron tube. They were then suspended in air at room temperature and rinsed with water at room temperature for a minimum of 2 minutes. Care was taken to rinse the lumen of the grafts with water.
  • the graft-protein "hybrid" prostheses were then reintroduced into fresh (20%) glutaraldehyde (40 ml of 50 % glutaraldehyde in 60 ml of water) for 5-15 minutes. The process was repeated several times (three to ten times) until thin (1 to 2000 microns), uniformly coated grafts with their interstitial spaces filled were produced.
  • grafts and varying concentrations of proteins were utilized to determine optimal reaction condition. They included 3 and 6 mm. I.D. (2-20 mm is the range), 18 and 32 ridges/inch (10-32 ridges would be the range), and 1, 3, 5 and 10 % protein solutions. It was found that the grafts possessing 18 ridges/inch (half crimp) were the optimal type of graft to modify, as they possessed the best surface configuration to provide for an even deposition of protein. The grafts having 32 ridges/inch (full crimp) had to be stretched on a glass rod of the same I.D. as the grafts in order to coat them properly.
  • the protein copolymerized hybrid grafts were further modified to enhance their net negative surface charge.
  • the end terminal amino acid residues were covalently coupled to succinic acid under acetylation reaction conditions (see Pat. No. 3,927,422).
  • the grafts were rinsed thoroughly with distilled deionized water, and placed into a 10 % (8-10 % range) sodium bicarbonate buffer at a pH 8.5 (8.2-8.7 range) (8-10 grains in 100 ml of water).
  • the grafts were allowed to equilibrate with the buffer (5-30 minutes at 17-27°C) then ground solid succinic anhydride was added in 5 mg portions (range 2-5 grams) to the buffer such that the final succinate solution concentration would be 1 M, (range: 1 to 5 molar) (2 to 8 micromoles of succinate per gram of protein).
  • the reaction was sufficiently vigorous to perfuse the lumen of the grafts.
  • Several aliquots range: 3 to 5) of the solid anhydride were added directly into the lumens of the grafts which were then placed into the buffer.
  • the grafts were retested on a Zarb hydrostatic testing apparatus to ascertain structural integrity of copolymerization.
  • the grafts were recoated if necessary and then stored and sterilized in 10 % (range 3 - 10 %) glutaraldehyde.
  • Acrylamide was prepared in accordance with the method of Davis et al. A solution which would yield 7 % (range: 5 to 8 %) gel was utilized. The graft was immersed into solution and was allowed to polymerize. The graft was removed, washed with distilled deionized water and stored in 40 % ETOH and water.
  • a 20 ml solution of 28,0 g of acrylamide (Bio-Rad Labs of Richmond, Ca.) and .735 g of bis-acrylamide (Bio-Rad Labs of Richmond, Ca.) were added to a 20 ml solution containing 1 N. HC1, 48.0ml/100 ml., 36.3 g/100 ml of TRIS (Bio-Rad Inc. of ) and 0.723 ml of TEMED/100 ml.
  • a segment ot graft material was added to the acrylamide solution and allowed to equilibrate for one hour (1/2-1 hours at room temperature). At that time, a 40 ml solution of ammonium persulfate, 1 mg/ml, (Bio-Rad Labs of Richmond, Ca.) was added to the acrylamide-bis-acrylamide solution in order to polymerize the solution. The solution was allowed to gel at room temperature for 1/2 hour (range: 10-40 minutes). During this time interval, the graft was removed and reintroduced into the gelling medium 10 (range: 10 to 20) times. The graft was removed after the solution began to gel but before a solidified gel could form.
  • the graft was then placed into a new test tube, and the acrylamide which had coated the Dacron fibers was allowed to gel. After the acrylamide polymerized, the graft was perfused with water at room temperature for 1 hour (range: 1/2 to 1 hour).
  • a 3 % agar-water mixture (Difco Labs, Detroit,Mich. USA) was made and heated to 100°C until a uniform (aggregate free) slurry was evident.
  • the graft material washed three to ten times in distilled and deionized water, was immersed in the agar slurry until it was uniformly coated (100-2,000 microns). It was then kept at 4°C (range: 4-10°C) until the agar congealed.
  • the graft was removed, washed and stored in 40 % ethanol-H 2 0 until used.
  • Two techniques of coating a Dacron prosthesis with aluminum were utilized. They were: (1) vapor deposition and (2) hot plasma spray technique.
  • Vapor deposition was accomplished in vacuum at 10 -5 Torr.
  • the aluminium vapor was forced through a small opening ( .25 to 20 mm) in a heat shield and deposited on a Dagron graft in a thin, uniform coat of 1/2 to 10 microns.
  • This technique proved to be the best technique for coating Dacron tubular material with aluminum as it provides a vapor which coats the graft completely with localized over concentration.
  • Aluminium powder is heated to its melting points and is then sprayed by a pressurized aerosol-like container. This is repeated until a thin coating (1/2 to 10 microns) of aluminum is observed on the Dacron.
  • Implantation studies were divided into chronic and short term evaluation of hybrid graft materials.
  • Three and four mm hybrid grafts were sutured (implanted) into the carotid and femoral arteries of dogs for periods ranging from 1 second to 2 months. (1 second, 2 hours, 1 week, 1 month, 2 months).
  • the hybrid grafts were removed from their sterile solutions and placed into a sterilized 500 ml beaker and sequential washed with 250 ml of sterile saline 20 x. The grafts were then placed into a sterile stainless steel bin containing 1.5 liters of sterile saline, until placed in a sterile field and implanted.
  • the end pieces Prior to implantation, the end pieces were cut to provide an even surface for anastomosis and samples for controls, culturing and SEM studies to determine efficiency of coating and fuction.
  • End-to-end anastomosis was carried out using a running Carrell suture with 4-0 cardiovascular Dacron or other material. Precise anastomosis was carried out in all cases.
  • Percent patency has been determined using a semiquantative scale. This has been determined by taking the cross sectional view of a graft and dividing it into equal
  • the graft-hybrid materials were analyzed using (1) scanning electron microscopy (SEM), (2) light microscopy and (3) histological staining. Patency was determined using the aforementioned semi-quantitative technique.
  • the SEM's were used to detect (1) efficiency of hybridization (to determine structural flaws in the coatings) and (2) to determine visible evidence of the type of blood prostheses interfacial reactions.
  • H&E Hemotoxylan and Eosin
  • Elastic VG stain Van Geisen
  • Table 1 Relates the type of hybridization, time of implantation and percent patency. Column 1 is the type of "coating" and subsequent negative charging. The next 4 colums are the time parameters at which they were analyzed. The numbers represent the % of patency. A check indicates that the graft is still functioning in-vivo. A - indicates that that parameter was not measured. The last column is the type of Dacron support used with that particular modification.
  • FIG. l(a) shows scanning electron micrographs of a polymerized protein, namely, of an albumin Dacron hybrid graft. This series of photographs demonstrates the homo- genicity of a protein on Dacron surface.
  • Fig. l(B) shows scanning electron micrographs of a protein-gelatin Dacron hybrid graft. The photographs show a homogeneous surface prior to and after exposure of the surface to blood for 1 second.
  • Fig. 2(A) shows scanning electron micrographs of a gelatin-Dacron hybrid graft. These photographs reveal minor cracking of the polymerized surface at high (lOKx) magnification.
  • Fig. 2(B) shows scanning electron micrographs of a gelatin-Dacron hybrid graft. Following polymerization of the hybrid, the surface was chemically treated (succinylating) to produce a net negative surface charge. These micrographs indicate that the negative surface at 1 second, 2 hours and 1 month is far less reactive than the unmodified hybrid surface.
  • the unmodified surface has a dense amount of cellular protein deposition thereon, while the negatively charged surface attracts fewer cellular aggregates.
  • the patency rate for the negatively charged grafts was approximately 90 % as opposed to 60 % for the unmodified surface at 2 hours.
  • Fig. 3(A) shows the smooth structure of an agar coated Microknit ⁇ Dacron graft and Fig. 3(B) shows implantation results of a protein-gelatin Dacron hybrid graft.
  • the SEM photographs reveal that the protein-gelatin negatively charged hybrid is less reactive at 1 second, 2 hours and 1 month than the unmodified graft. Many erythrocytes entrapped in a protein matrix can be seen in the unmodified surface while the negatively charged surface possesses few red cells and no visible platelets. Patency rates for the negatively charged grafts was approximately 90 % as opposed to 70 % for the unmodified grafts at 2 hours.
  • F ig. 4 shows scanning electron micrographs of an aluminum coated Dacron hybrid graft. Following implantation, the graft was examined. Little protein deposition could be seen. A layer of cells which appear to be erythrocytes and monocytes bound to fibrinogin seem to be sparsely coating the surface. The metallic coating may be toxic to cellular elements, as the monocytes are atypical. The patency rate in all cases was 100 %.
  • Fig. 5 shows scanning electron micrographs of an agar coated-Dacron hybrid. Implantation results indicate a reactive surface with cellular and protein deposition. Patentcy rates were 80 % at 1 second and 40 % at 2 hours.
  • Fig. 6(A) shows an aluminum coated Dacron prosthesis exposed to blood for 1 second.
  • the fibrils are virtually free of cellular elements with the exception of a very few erythrocytes and leukocytes with a few visible platelets attached as well.
  • the single large cell appears to be a toxic neutrophile.
  • the remainder of the photograph displays proteinated aluminum substrate.
  • the cells are smaller and appear to be crenating.
  • Fig. 6(B) shows further magnifications at 1 K X and these reveal a few crenating cells with a very thin layer of protein attached to the aluminized Dacron fabric. These cells are completely gone by 1 month, the fabric being joined by what appears to be a thin amorphous layer of protein. This may be proteinated aluminum.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Veterinary Medicine (AREA)
  • Public Health (AREA)
  • General Health & Medical Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Epidemiology (AREA)
  • Transplantation (AREA)
  • Medicinal Chemistry (AREA)
  • Dermatology (AREA)
  • Chemical & Material Sciences (AREA)
  • Vascular Medicine (AREA)
  • Hematology (AREA)
  • Surgery (AREA)
  • Cardiology (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Materials For Medical Uses (AREA)
  • Prostheses (AREA)
  • External Artificial Organs (AREA)
EP78100752A 1977-08-26 1978-08-25 Prothèses cardiaques et vasculaires et procédé pour leur fabrication Expired EP0000949B1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US05/827,952 US4167045A (en) 1977-08-26 1977-08-26 Cardiac and vascular prostheses
US827952 1977-08-26

Publications (2)

Publication Number Publication Date
EP0000949A1 true EP0000949A1 (fr) 1979-03-07
EP0000949B1 EP0000949B1 (fr) 1983-05-18

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EP78100752A Expired EP0000949B1 (fr) 1977-08-26 1978-08-25 Prothèses cardiaques et vasculaires et procédé pour leur fabrication

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US (1) US4167045A (fr)
EP (1) EP0000949B1 (fr)
JP (1) JPS5463588A (fr)
CA (1) CA1122353A (fr)
DE (1) DE2862259D1 (fr)

Cited By (14)

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Publication number Priority date Publication date Assignee Title
EP0124659A1 (fr) * 1983-04-13 1984-11-14 Koken Co. Ltd. Matériau médical
FR2572654A1 (fr) * 1984-11-08 1986-05-09 Mitsubishi Monsanto Chem Materiel medical en poly(chlorure de vinyle) souple et comportant un revetement de gelatine reticulee, et procede de fabrication de ce materiel
GB2203342A (en) * 1987-04-07 1988-10-19 Julian Garth Ellis Radio-opaque tracer for surgical implants
US4842575A (en) * 1984-01-30 1989-06-27 Meadox Medicals, Inc. Method for forming impregnated synthetic vascular grafts
US5073171A (en) * 1989-01-12 1991-12-17 Eaton John W Biocompatible materials comprising albumin-binding dyes
US5108424A (en) * 1984-01-30 1992-04-28 Meadox Medicals, Inc. Collagen-impregnated dacron graft
EP0311305B1 (fr) * 1987-10-02 1992-09-09 Koken Company Limited Vaisseau sanguin artificiel
EP0183365B1 (fr) * 1984-11-30 1992-12-30 Vascutek Limited Greffe vasculaire
US5197977A (en) * 1984-01-30 1993-03-30 Meadox Medicals, Inc. Drug delivery collagen-impregnated synthetic vascular graft
EP0542880A4 (en) * 1990-07-27 1993-07-28 Lawrence Samuel Bass Tissue bonding and sealing composition and method of using the same
WO1996040302A1 (fr) * 1995-06-07 1996-12-19 W.L. Gore & Associates, Inc. Prothese-tissu souple bioabsorbable comblant un espace
US5716660A (en) * 1994-08-12 1998-02-10 Meadox Medicals, Inc. Tubular polytetrafluoroethylene implantable prostheses
US5851230A (en) * 1994-08-12 1998-12-22 Meadox Medicals, Inc. Vascular graft with a heparin-containing collagen sealant
EP1267749B2 (fr) † 2000-03-20 2017-07-26 Vactronix Scientific, Inc. Dispositifs d'implantation endoluminale et procede de production correspondant

Families Citing this family (37)

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Publication number Priority date Publication date Assignee Title
US4530974A (en) * 1981-03-19 1985-07-23 Board Of Regents, The University Of Texas System Nonthrombogenic articles having enhanced albumin affinity
SE446372B (sv) * 1983-02-03 1986-09-08 Medinvent Sa Blodkerlsprotes for anvendning som shunt mellan blodkerl
US4562596A (en) * 1984-04-25 1986-01-07 Elliot Kornberg Aortic graft, device and method for performing an intraluminal abdominal aortic aneurysm repair
JPS60227763A (ja) * 1984-04-27 1985-11-13 筏　義人 抗血栓性医用材料
US5037377A (en) * 1984-11-28 1991-08-06 Medtronic, Inc. Means for improving biocompatibility of implants, particularly of vascular grafts
US4629458A (en) * 1985-02-26 1986-12-16 Cordis Corporation Reinforcing structure for cardiovascular graft
DE3608158A1 (de) * 1986-03-12 1987-09-17 Braun Melsungen Ag Mit vernetzter gelatine impraegnierte gefaessprothese und verfahren zu ihrer herstellung
US4911713A (en) * 1986-03-26 1990-03-27 Sauvage Lester R Method of making vascular prosthesis by perfusion
CH670759A5 (fr) * 1986-06-02 1989-07-14 Sulzer Ag
US5447966A (en) * 1988-07-19 1995-09-05 United States Surgical Corporation Treating bioabsorbable surgical articles by coating with glycerine, polalkyleneoxide block copolymer and gelatin
US5464438A (en) * 1988-10-05 1995-11-07 Menaker; Gerald J. Gold coating means for limiting thromboses in implantable grafts
US5207706A (en) * 1988-10-05 1993-05-04 Menaker M D Gerald Method and means for gold-coating implantable intravascular devices
JPH02277886A (ja) * 1989-04-17 1990-11-14 Shigesaburo Mizushima ヒブロイン蛋白による合成繊維及び植物繊維の加工方法
JP2799596B2 (ja) * 1989-08-10 1998-09-17 株式会社ジェイ・エム・エス 生体埋植用具およびその製造法
US5118524A (en) * 1990-09-14 1992-06-02 The Toronto Hospital Vascular biomaterial
GB9026687D0 (en) * 1990-12-07 1991-01-23 Vascutek Ltd Process for providing a low-energy surface on a polymer
US5120833A (en) * 1991-03-15 1992-06-09 Alexander Kaplan Method of producing grafts
US5500013A (en) * 1991-10-04 1996-03-19 Scimed Life Systems, Inc. Biodegradable drug delivery vascular stent
US5584875A (en) * 1991-12-20 1996-12-17 C. R. Bard, Inc. Method for making vascular grafts
US5272074A (en) * 1992-04-23 1993-12-21 Mcmaster University Fibrin coated polymer surfaces
GEP20002074B (en) * 1992-05-19 2000-05-10 Westaim Tech Inc Ca Modified Material and Method for its Production
US5681575A (en) * 1992-05-19 1997-10-28 Westaim Technologies Inc. Anti-microbial coating for medical devices
CN1052915C (zh) * 1995-11-27 2000-05-31 中国医学科学院生物医学工程研究所 用于携载基因的蛋白质涂层医用载体及其制作方法
US6302909B1 (en) 1996-07-31 2001-10-16 St. Jude Medical, Inc. Calcification-resistant biomaterials
US6193749B1 (en) * 1996-02-05 2001-02-27 St. Jude Medical, Inc. Calcification-resistant biomaterials
US5851229A (en) * 1996-09-13 1998-12-22 Meadox Medicals, Inc. Bioresorbable sealants for porous vascular grafts
US5895419A (en) 1996-09-30 1999-04-20 St. Jude Medical, Inc. Coated prosthetic cardiac device
US6254635B1 (en) 1998-02-02 2001-07-03 St. Jude Medical, Inc. Calcification-resistant medical articles
CA2398547A1 (fr) * 2000-02-09 2001-08-16 Nikolai G. Sedelnikov Dispositifs implantables non thrombogenes
US6719987B2 (en) 2000-04-17 2004-04-13 Nucryst Pharmaceuticals Corp. Antimicrobial bioabsorbable materials
JP2003126125A (ja) * 2001-10-24 2003-05-07 Katsuko Sakai 人工血管及びその製造方法
US7740656B2 (en) * 2003-11-17 2010-06-22 Medtronic, Inc. Implantable heart valve prosthetic devices having intrinsically conductive polymers
US7329531B2 (en) * 2003-12-12 2008-02-12 Scimed Life Systems, Inc. Blood-tight implantable textile material and method of making
US7658975B2 (en) * 2003-12-12 2010-02-09 Intel Corporation Sealing porous dielectric materials
EP2161042A1 (fr) * 2004-01-29 2010-03-10 Smart Implant PLC Prothèse et procédé de fabrication d'une prothèse
WO2009111241A2 (fr) * 2008-02-29 2009-09-11 The Florida International University Board Of Trustees Prothèse de valvule cardiaque artificielle à plusieurs feuillets destinée à être mise en place par un cathéter, et système de mise en place intravasculaire pour une prothèse de valvule cardiaque destinée à être mise en place par un cathéter
DE102009037134A1 (de) 2009-07-31 2011-02-03 Aesculap Ag Tubuläres Implantat zum Ersatz von natürlichen Blutgefäßen

Citations (16)

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GB1008193A (en) * 1961-03-01 1965-10-27 Ethicon Inc Improvements in or relating to surgical implants
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US3276448A (en) * 1962-12-14 1966-10-04 Ethicon Inc Collagen coated fabric prosthesis
GB1064850A (en) * 1962-12-20 1967-04-12 Ethicon Inc Tubular body and process of making it
DE1494939A1 (de) * 1963-06-11 1969-06-04 Buddecke Dr Eckhart Implantationsmaterial und Verfahren zu seiner Herstellung
GB1097787A (en) * 1966-09-22 1968-01-03 Ethicon Inc Surgical prosthesis
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CH593676A5 (en) * 1975-12-16 1977-12-15 Intermedicat Gmbh Sealing of blood vessel implants of velour-coated fabric - by impregnating with organic colloidal solns. and drying
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EP0124659A1 (fr) * 1983-04-13 1984-11-14 Koken Co. Ltd. Matériau médical
US5108424A (en) * 1984-01-30 1992-04-28 Meadox Medicals, Inc. Collagen-impregnated dacron graft
US5197977A (en) * 1984-01-30 1993-03-30 Meadox Medicals, Inc. Drug delivery collagen-impregnated synthetic vascular graft
US4842575A (en) * 1984-01-30 1989-06-27 Meadox Medicals, Inc. Method for forming impregnated synthetic vascular grafts
FR2572654A1 (fr) * 1984-11-08 1986-05-09 Mitsubishi Monsanto Chem Materiel medical en poly(chlorure de vinyle) souple et comportant un revetement de gelatine reticulee, et procede de fabrication de ce materiel
EP0183365B1 (fr) * 1984-11-30 1992-12-30 Vascutek Limited Greffe vasculaire
GB2203342B (en) * 1987-04-07 1991-12-11 Julian Garth Ellis Radio-opaque tracer for surgical implants
GB2203342A (en) * 1987-04-07 1988-10-19 Julian Garth Ellis Radio-opaque tracer for surgical implants
EP0311305B1 (fr) * 1987-10-02 1992-09-09 Koken Company Limited Vaisseau sanguin artificiel
US5073171A (en) * 1989-01-12 1991-12-17 Eaton John W Biocompatible materials comprising albumin-binding dyes
EP0542880A4 (en) * 1990-07-27 1993-07-28 Lawrence Samuel Bass Tissue bonding and sealing composition and method of using the same
US5716660A (en) * 1994-08-12 1998-02-10 Meadox Medicals, Inc. Tubular polytetrafluoroethylene implantable prostheses
US5851230A (en) * 1994-08-12 1998-12-22 Meadox Medicals, Inc. Vascular graft with a heparin-containing collagen sealant
US6162247A (en) * 1994-08-12 2000-12-19 Meadox Medicals, Inc. Vascular graft impregnated with a heparin-containing collagen sealant
WO1996040302A1 (fr) * 1995-06-07 1996-12-19 W.L. Gore & Associates, Inc. Prothese-tissu souple bioabsorbable comblant un espace
EP1267749B2 (fr) † 2000-03-20 2017-07-26 Vactronix Scientific, Inc. Dispositifs d'implantation endoluminale et procede de production correspondant

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DE2862259D1 (en) 1983-07-07
US4167045A (en) 1979-09-11
JPS5463588A (en) 1979-05-22
CA1122353A (fr) 1982-04-27
JPH0137154B2 (fr) 1989-08-04
EP0000949B1 (fr) 1983-05-18

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