CA2148670C - Vascular graft impregnated with a heparin-containing collagen sealant - Google Patents

Vascular graft impregnated with a heparin-containing collagen sealant Download PDF

Info

Publication number
CA2148670C
CA2148670C CA002148670A CA2148670A CA2148670C CA 2148670 C CA2148670 C CA 2148670C CA 002148670 A CA002148670 A CA 002148670A CA 2148670 A CA2148670 A CA 2148670A CA 2148670 C CA2148670 C CA 2148670C
Authority
CA
Canada
Prior art keywords
collagen
heparin
dispersion
synthetic
prosthesis
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Expired - Fee Related
Application number
CA002148670A
Other languages
French (fr)
Other versions
CA2148670A1 (en
Inventor
Kevin Weadock
David J. Lentz
Jack Tant
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Maquet Cardiovascular LLC
Original Assignee
Meadox Medicals Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Meadox Medicals Inc filed Critical Meadox Medicals Inc
Publication of CA2148670A1 publication Critical patent/CA2148670A1/en
Application granted granted Critical
Publication of CA2148670C publication Critical patent/CA2148670C/en
Anticipated expiration legal-status Critical
Expired - Fee Related legal-status Critical Current

Links

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS 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
    • A61L33/00Antithrombogenic treatment of surgical articles, e.g. sutures, catheters, prostheses, or of articles for the manipulation or conditioning of blood; Materials for such treatment
    • A61L33/0005Use of materials characterised by their function or physical properties
    • A61L33/0011Anticoagulant, e.g. heparin, platelet aggregation inhibitor, fibrinolytic agent, other than enzymes, attached to the substrate
    • A61L33/0029Anticoagulant, e.g. heparin, platelet aggregation inhibitor, fibrinolytic agent, other than enzymes, attached to the substrate using an intermediate layer of polymer
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS 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
    • A61L27/00Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/14Macromolecular materials
    • A61L27/22Polypeptides or derivatives thereof, e.g. degradation products
    • A61L27/24Collagen
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS 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
    • A61L27/00Materials for grafts or prostheses or for coating grafts or prostheses
    • A61L27/28Materials for coating prostheses
    • A61L27/34Macromolecular materials
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61LMETHODS 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
    • A61L33/00Antithrombogenic treatment of surgical articles, e.g. sutures, catheters, prostheses, or of articles for the manipulation or conditioning of blood; Materials for such treatment
    • A61L33/0005Use of materials characterised by their function or physical properties
    • A61L33/0011Anticoagulant, e.g. heparin, platelet aggregation inhibitor, fibrinolytic agent, other than enzymes, attached to the substrate
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10STECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10S623/00Prosthesis, i.e. artificial body members, parts thereof, or aids and accessories therefor
    • Y10S623/92Method or apparatus for preparing or treating prosthetic
    • Y10S623/921Blood vessel

Abstract

A heparin-collagen dispersion is provided for impregnating a vascular prosthesis with heparin and collagen. The dispersion is prepared at an alkaline pH to allow the addition of heparin without causing the agglutination of collagen from the dispersion. The impregnation of collagen and heparin within the prosthesis effectively prevents blood loss and thrombus formation after implantation of the prosthesis.

Description

PATENT
VASCULAR GRAFT IMPREGNATED WITH
A HEPARIN-CONTAINING COLLAGEN SEALANT
BACKGROUND OF THE INVENTION

The present invention relates to vascular prostheses, and more particularly relates to vascular grafts impregnated with a heparin-containing collagen sealant.

Vascular prostheses, commonly referred to as grafts, are typically used as soft tissue prostheses to replace damaged or diseased portions of blood vessels. During a surgical procedure, a damaged or diseased blood vessel portion may be removed and replaced with a vascular prosthesis. Complications, however, may occur as a result of the implanted prosthesis because of the body's natural tendency to reject foreign matter. More particularly, thrombosis or blood clotting within or upon the prosthesis may occur.

Precautions must be taken to minimize thrombosis and assure the patency of an implanted vascular prosthesis.
Ideally, antithrombogenic properties should be imparted to the prosthesis. In addition to antithrombogenic properties, a vascular graft or prosthesis must be flexible and pliable to ensure that the prosthesis bends and flexes with the normal contours of the body into which it is transplanted. Without such flexibility, normal healing and acceptance by the body of the graft may not occur.

Vascular grafts or prostheses must also be porous to promote an ingrowth of tissue within or upon the vascular graft. More particularly, the exterior surface of the vascular prosthesis should include pores large enough to facilitate the entry of connective tissue and connective tissue cells such as fibroblasts, i.e., the ingrowth of the perigraft tissue. Generally, the larger the pore size, the better the ingrowth of the tissue into the wall from the perigraft tissue.

The interior surface should include pores that are not so large as to allow leakage of blood into surrounding tissues but large enough to promote tissue ingrowth.
Blood leakage into surrounding tissues increases the likelihood of infection. The more porous the vascular graft substrate, the greater the tendency to hemorrhage during and after implantation.

Much effort has gone into hemostatic control, i.e., reducing the initial high rate of blood seepage into surrounding tissue from highly porous vascular graft substrates during and immediately after surgery. U.S.
Patents No. 3,805,301 and 4,047,242, assigned to the assignee of the subject application, disclose synthetic vascular grafts that are sufficiently porous to permit tissue ingrowth and allow firm attachment of a neointimal lining in the graft.

The vascular grafts disclosed within the 3,805,301 and 4,047,242 patents, however require a general procedure for implantation which includes the step of pre-clotting.
During pre-clotting, the graft is immersed in the blood of the patient ex-vivo and allowed to stand for a period of time sufficient for clotting the porous substrate.
Without the preclotting, excessive bleeding would occur when blood begins to flow into the vascular graft.

Emersion within a patients blood to pre-clot a graft, however, leaves the graft lumen highly thrombogenic due to the presence of a high concentration of thrombin on the intraluminal surface of the vascular graft. As the blood passes the thrombin buildup, the thrombin attracts platelets, forming a thrombus or blood clot that may detract from the graft's patency.

Other attempts to limit hemorrhaging from implanted grafts during and immediately after surgery include impregnating the vascular graft substrate with gelatinous material, such as that described in U.S. Patent No.
4,747,848. The impregnated graft is then crosslinked by chemically modifying amino groups of the gelatinous molecules so that they will chemically bond to one another. The crosslinked, impregnated graft provides a sealed structure which prevents or controls bleeding.
Subsequent to implantation, the gelatinous material is degraded by hydrolysis, slowly increasing the porosity over time and allowing tissue ingrowth to occur.

Collagen is also well known as an agent which is effectively used to impregnate the pores of synthetic grafts in an effort to limit bleeding upon implantation.
Collagen is an insoluble fibrous protein that occurs naturally in vertebrates as the chief constituent of connective tissue fibrils. The patency of grafts impregnated with collagen is high. Collagen impregnated within grafts is gradually biodegraded by the body, uncovering pores present in the graft substrate structure to allow for tissue ingrowth and healing. Collagen coatings, however, are known to attract thrombin agents which form thrombosis or blood clots on surfaces treated with collagen. This can potentially lead to occlusion within transplanted grafts, the problem being especially acute in blood vessels having diameters of 10 mm or less.

U.S. Patent No. 5,197,977, assigned to the assignee of the present invention, discloses a collagen-impregnated vascular graft which is effective in preventing blood leakage and which also does not require additional processing such as preclotting prior to use. The collagen-impregnation also slowly degrades in the body to enable host tissue ingrowth.

The collagen source with which the vascular graft is impregnated is a fibrous dispersion of high purity. The dispersion may also act as a reservoir for the sustained release of drug materials, such as anti-bacterial agents, 5 anti-thrombogenetic agents and anti-viral agents, in an attempt to minimize bacterial infection and thrombosis subsequent to implantation.

Heparin is a chemical agent that prevents the clotting of blood, i.e., an anticoagulant. Conventional techniques for preparing collagen-heparin dispersions typically result in the precipitation of collagen from the collagen dispersion upon the addition of heparin in sufficient quantity to effectively prevent thrombosis upon grafts impregnated thereby. To prepare a graft with collagen using conventional methods therefore allows for only small quantities of heparin to be added to the sealant.

It is therefore an object of the present invention to provide a collagen-heparin dispersion which overcomes the aforementioned problems of the prior art, and method for forming the same.

It'is another object of the present invention to provide a collagen-heparin dispersion in ratios of collagen to heparin such that thrombogenic events are minimized resulting from the implantation of a graft treated with the dispersion.

It is still another object of the present invention to provide a synthetic vascular graft which does not require pre-clotting with a patient's blood prior to implantation, and method for forming the same.

It is another object of the present invention to provide a collagen and heparin impregnated synthetic vascular graft that is coated with heparin to prevent thrombus formation and inhibit smooth muscle cell anastomotic hyperplasia after implantation, and method of forming the same.

It is yet another object of the present invention to provide a collagen and heparin impregnated synthetic vascular prosthesis which minimizes blood loss after implantation, and method for forming the same.

It is still another object of the present invention to provide a collagen and heparin impregnated synthetic vascular prosthesis that promotes cell ingrowth and enhances the rate and degree of healing within a patient's body after implantation, and method for forming the same.

It is still a further object of the present invention to provide a collagen and heparin impregnated vascular prosthesis that releases heparin at a sustained or controlled rate when implanted into a patient's body, and method for forming the same.

Still other objects and advantages of the invention will in part be obvious and will in part be apparent from the detailed description of the invention that follows.
SiJMMARY OF THE INVENTION

The present invention includes a method of sealing a synthetic vascular prothesis to prevent thrombus formation. The method includes the steps of providing a stable collagen-heparin dispersion and applying the same to the synthetic vascular prosthesis to effectuate sealing and impart anti-thrombogenic properties thereto.
Application of the stable collagen-heparin dispersion may be by coating or impregnating the prosthesis with the dispersion. The method particularly focuses on preparing a stable collagen-heparin dispersion at alkaline pH, preferably within a range of from about 9 to about 11, and, most preferably, at a pH of approximately 10. The collagen may be crosslinked by chemical or physical techniques subsequent to application to the synthetic vascular prosthesis.

The present invention also provides a synthetic vascular prosthesis comprised of a flexible, porous, tubular substrate having an intraluminal and an extraluminal surface and fabricated from any conventional stitch structure, such as a knit, weave or braid. Double or single velours may also be employed. At, a minimum, the intraluminal surface is coated or impregnated with a stable collagen-heparin dispersion prepared with an alkaline dispersion of collagen and heparin, although all surfaces may be contacted with the dispersion. The ratio of collagen to heparin may be greater than or equal to one as a result of the alkaline collagen-heparin dispersion of this invention. The substrate may be a three-dimensional braid, a knit, a weave or a velour structure.

Also included is a collagen-heparin impregnated vascular prosthesis with a synthetic tubular substrate having an extraluminal and an intraluminal surface, prepared by the process of this invention. The process from which the vascular prosthesis is derived includes providing a stable alkaline dispersion of collagen and heparin and applying the dispersion to at least the intraluminal surface of the tubular substrate thereby providing an improved antithrombogenic seal to the vascular prosthesis.

The stable alkaline dispersion allows for more heparin and more collagen in solution, resulting in an improved ability to effectively coat and impregnate interstitial spaces within the textile material comprising 21486'70 the vascular prosthesis. The resulting vascular prothesis produced by the process of this invention, may minimize thrombus formation and smooth muscle cell hyperplasia on the intraluminal surface of the vascular prothesis after implantation.

BRIEF DESCRIPTION OF THE DRAWINGS

Figure 1 is a partial cut away side perspective view of a' vascular graft made in accordance with present invention; and Figure 2 is a partial cut away side perspective view of a branched vascular graft of the type illustrated in Figure 1.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT

A vascular graft 20 constructed in accordance with the method of present invention is shown in Figure 1. For purposes of describing the present invention, the terms "graft", "prosthesis" and "vascular graft" are interchangeably used in describing the methods apparatus and structures referred to herein. Vascular graft 20 includes a porous, tubular substrate portion 22 preferably formed of a synthetic material such as polyethylene terephthalate (commonly marketed under the trademark DACRON ) .

Generally, the porosity of the DACRON substrate ranges from about 2000 to 3000 ml/min-cm2 (purified water at 120 mm Hg). Tubular substrate portion 22 is not limited, however, to DACRON. Tubular substrate portion 22 may be formed of any porous bio-compatible, filamentary synthetic material known to those skilled in the art which permits tissue ingrowth and is capable of maintaining an open, intraluminal passageway for the flow of blood after implantation.

Tubular substrate portion 22 may take on various forms.
For example, tubular substrate portion 22 may be formed with an inner and outer velour surface such as the prostheses described in commonly owned U.S. Patents No.
4,047,252 and 4,842,575.

For example, U.S. Patent No. 4,047,452 discloses a double-velour synthetic vascular graft produced by a warp-knitting machine using a double needle bar. The trellis of the graft is made from a yarn with counts from 30 to 150 denier, preferably singly ply. Loops project from the trellis both on the inner and outer surfaces of the graft to provide for more effective ingrowth of tissue without impeding the flow of blood through the tubular body.
The knit fabric is compacted to decrease the size of pore openings and therefore the porosity of the fabric.
Thereafter, the graft is clumped to impart uniform, regular, circular corrugations to provide uniform strength over the entire graft surface of the graft tubing and to minimize kinking and the propensity of the fabric to collapse.

U.S. Patent No. 4,842,575 discloses a synthetic collagen-impregnated vascular graft which may be bifurcated. The grafts typically employ a DACRON warp knit fabric of varying diameter and porosity.

Figure 1 shows an intraluminal surface 24 of tubular substrate portion 22 that is impregnated with and sealed by an application of the collagen-heparin dispersion of the present invention. The collagen-heparin coating imparts both hemostatic and anti-thrombogenic properties to a surface 26 of vascular graft 20. Bleeding is minimized, therefore, during and immediately after surgery. In addition, thrombin formation and accompanying stenosis are minimized within the vascular graft.

Collagen is a well known hemostatic agent used for coating porous, vascular synthetic grafts. Collagen applied thereby prevents blood seepage into surrounding tissue during and immediately after surgery. In addition to preventing blood loss, collagen is readily accepted by the body and may promote cell ingrowth and enhance the rate and degree of healing.

Methods for adhering collagen to a porous graft substrate typically include applying a collagen dispersion to the substrate, allowing it to dry and repeating the process. Collagen dispersions are typically made by blending insoluble collagen (approximately 1-2% by weight) in a dispersion at acidic pH (a pH in a range of 2 to 4).
The dispersion is typically injected via syringe into the lumen of a graft and massaged manually to cover the entire inner surface area with the collagen slurry.
Excess collagen slurry is removed through one of the open ends of the graft. Coating and drying steps are repeated several times to provide sufficient treatment.

A collagen coated and/or impregnated prosthesis, however, tends to absorb or accept fibrinogen on its blood contacting surfaces, forming a fibrin matrix thereon.
Growing fibrin strands within a fibrin matrix forms a thrombus or clot. Typically, an anticoagulant such as heparin is administered prior to the insertion of the graft to prevent clotting and consequential occlusion.

Collagen may also be utilized as a vehicle for the controlled release of pharmacological agents such as antibiotics and growth factors, as well as heparin. To accomplish this, the active (e.g., heparin) is provided in 214$6'7Q

a collagen matrix which is coated on or impregnated within the graft. As the collagen biodegrades, the active is released and becomes bioavailable on the coated surface.
Because of the conventional requirements for creating and performing a collagen-pharmaceutical coating, the amount of pharmaceuticals which can be dispersed within the coating has been limited.

Heparin has been used as an anti-coagulant for many years. Heparin is known to prevent thrombus build-up on an intraluminal surface to which it has been coated or bonded, such as intraluminal surface 24 of vascular graft 20.

After implantation of a vascular prosthesis with a collagen-heparin coating 26, heparin is released at a controlled rate thereby reducing the incidence of thrombosis or intraluminal surface 24. Collagen-heparin coating 26, by minimizing thrombosis and therefore stenosis within the prosthesis lumen enables production of vascular prosthesis with diameters that are smaller than diameters of previously available grafts, i.e., less than 10mm (for implantation).

However, adding sufficient quantity of heparin to a conventional collagen dispersion (at the acidic pH) results in a collagen-heparin interaction which induces precipitation of the collagen from the dispersive phase.
The result is that less collagen is available for application to the prosthetic substrate.

This interaction is believed to be the result of the negatively charged heparin molecule ionically interacting with the positively charged collagen molecules. However, this ionic interaction occurs regardless of whether the event proceeds above or below the isoelectric point of collagen.

The isoelectric point of limed, insoluble collagen, a pH of about 4, is that pH value at which the collagen molecules do not move in an electric field. Typically, precipitation of a colloid from suspension will occur above or below the colloid's isoelectric point; that is, with a change in pH in either the positive or negative direction.

The result of the ionic interaction is that water is forced from the collagen molecule causing a significant increase in the viscosity of the precipitate. This renders impregnation of the vascular prothesis extremely difficult. Vascular grafts coated or impregnated with a collagen-heparin dispersion prepared in a conventional manner must accordingly make due with a minimum of heparin to prevent the coagulation of the coating dispersion.
That is, the conventional ratio of collagen to heparin was required to be many times greater than one in order to have sufficient collagen for sealing, yet, prostheses having such sealant compositions lacked sufficient heparin to be antithrombogenic.

The present invention overcomes the problems associated with the combination of collagen and antithrombogenic effective amount of heparin in dispersion. The present invention provides a unique method of preparing the collagen-heparin dispersion which avoids the precipitation of collagen that is typical of the prior art with the addition of substantial amounts of heparin.

The collagen dispersion of this invention is formed at an alkaline pH to provide a vehicle for adding proportionally large amounts of heparin without inducing collagen precipitation. At conventional pH, either the ratio of collagen to heparin would need be extremely high to prevent viscosity increase, or the concentration of collagen and heparin needed to be extremely low, minimizing the effectiveness of collagen as a sealant.
The biological properties of the heparin and collagen are not significantly altered at alkaline pH. Although a pH
of about 10 is preferred, large amounts of heparin may be added to a collagen solution within a range of 9 to 11 without causing the collagen to precipitate out. The present invention preferably contemplates, however, dispersions with a ratio of heparin to collagen ranging between about 1:100 to 1:1.

The ratio of heparin to collagen by weight can be raised to 1 or greater if prepared according to the present invention without effecting the viscosity of the dispersion significantly, since the precipitation phenomenon and resultant loss of water does not occur. As a result, the interstitial spaces of a synthetic or textile type vascular prothesis are readily impregnated with the collagen-heparin dispersion with a significantly increased amount of heparin than those of the prior art.

Because of the increased heparin content in the collagen-heparin coating, a vascular prosthesis impregnated by the method of this invention such as that shown in vascular prosthesis 20, possesses enhanced antithrombogenic properties on its surface. Further, the improved healing response of the impregnated vascular prothesis inhibits smooth muscle anastomotic hyperplasia, i.e., an abnormal build up of smooth muscle cells at the surgical connection. Such results provide for a graft with a prolonged patency.

The following example is set forth to illustrate the method of preparing the collagen-heparin dispersion of the invention and applying it to a vascular graft. The examples are set forth for the purpose for illustration and are not intended in a limiting sense.

A 1.44% collagen slurry was prepared at a pH of 3.47 at 25 C. Four (4) drops/100 ml of 10M NaOh was added to raise the pH of the collagen slurry to 10.5. 50 grams of the collagen slurry was transferred to a 1000m1 volumetric flask. An amount of 0.72 g of heparin was added to the collagen slurry. No change in the state of the slurry occurred when this quantity of heparin was added to form a collagen-heparin dispersion.

The experiment was repeated varying the pH of the collagen prior to the addition of heparin, that is, the addition of .72 g of heparin to a 50 g portion of 1.441 collagen slurry. The pH was varied to find an operable range of solution in which a sufficient antithrombogenic amount of heparin may be added without inducing collagen precipitable.

When the pH was dropped to 10.0 by the addition of NaOh, there was no collagen precipitation upon the addition of .72 g of heparin. When the pH was reduced to merely 6.4, there was a 50% percipitation. When the pH
was further reduced to 4.50, there was a 90%
percipitation.

The collagen-heparin dispersion i.e., 50 grams of 1.44% collagen slurry in which 0.72 g of heparin has been added was then applied to a bifurcated vascular graft 30 (Fig. 2) thereby impregnating and coating the graft.

Figure 2 shows a bifurcated vascular graft 30 impregnated with a collagen-heparin coating 38 of the present invention. Bifurcated vascular graft 30 comprises a main porous, synthetic tubular substrate 32 including bifurcated portions 34 formed from a biologically compatible filamentary material. The graft may be constructed in any manner known to those skilled in the art for providing a porous vascular prosthesis which permits tissue ingrowth and maintains an open lumen for the flow of blood.

5 An inner surface 36 of porous, synthetic tubular substrate 32, including bifurcated portions 34, is impregnated with the collagen-heparin dispersion of the present invention. Collagen-heparin coating 38 is formed thereon. The impregnated vascular graft 30 showed a low 10 incidence of bleeding as well as an increased absorbance of heparin. After implantation, the grafts are expected to display a lower incidence of thrombotic events occurring on either the coated surfaces 36 of tubular substrate portions 32 and bifurcated portions 34.

15 The specific embodiments of the vascular graft impregnated with a collagen-heparin sealant identified in this disclosure are not limited thereto and may be varied without materially effecting the anti-thrombogenic property of a vascular graft fabricated according to the invention. The invention accordingly is not limited to any precise embodiment disclosed and various other changes and modifications may be effected therein by one skill of the art without departing from the scope or spirit of the invention.

Claims (25)

1. ~A method of sealing a synthetic vascular prosthesis with a collagen-heparin composition, comprising the steps of:
preparing a stable collagen-heparin dispersion at alkaline pH within a range from about 9 to about 11, wherein said dispersion is maintained within a pH range of from about 9 to about 11; and applying said dispersion to said prosthesis to effectuate sealing and impart enhanced antithrombogenic properties thereto.
2. ~A method as defined by claim 1, wherein said prosthesis is impregnated with said dispersion.
3. ~A method as defined by claim 1, wherein said prosthesis is coated with said dispersion.
4. ~A method as defined by claim 1, wherein the collagen-heparin dispersion is prepared at a pH within a range of from about 9 to about 11.
5. ~A method as defined by claim 1, wherein the collagen-heparin dispersion is prepared at a pH of about 10.
6. ~A method as defined by claim 1, wherein the collagen-heparin dispersion has a ratio of heparin to collagen within a range of about 1:100 to about 1:1.
7. ~A method as defined by Claim 1, wherein the collagen-heparin dispersion applied to said prosthesis is crosslinked.
8. ~A synthetic vascular prosthesis comprising:
a flexible, porous, tubular substrate having an intraluminal and an extraluminal surface, wherein a least said intraluminal surface is treated with an alkaline collagen-heparin sealant prepared with an alkaline dispersion of collagen and heparin wherein said dispersion is maintained within a pH range of between about 9 to about 11.
9. ~A synthetic vascular prosthesis as defined by Claim 8, wherein said dispersion is formed with a ratio of heparin to collagen within a range of about 1:100 to about 1:1.
10. ~A synthetic vascular prosthesis as defined by claim 8, wherein said substrate is a three-dimensional braided structure.
11. ~A synthetic vascular prosthesis as defined by claim 8, wherein said substrate is a polyethylene terephthalate.
12. ~A synthetic vascular prosthesis as defined by claim 8, wherein said substrate is knitted.
13. ~A synthetic vascular prosthesis as defined by claim 8, wherein said substrate is woven.
14. ~A synthetic vascular prosthesis as defined by claim 8, wherein said substrate is braided.
15. ~A synthetic vascular prosthesis as defined by claim 8, wherein said intraluminal and extraluminal surfaces contain a velour structure.
16. ~A synthetic vascular prosthesis as defined by claim 8, wherein the collagen applied to said prosthesis is crosslinked.
17. ~A collagen-heparin impregnated vascular prosthesis comprising a synthetic tubular substrate with an extraluminal and an intraluminal surface, prepared by a process comprising the steps of:
preparing a stable collagen-heparin dispersion at alkaline pH within a range from about 9 to about 11, wherein said dispersion is maintained within a pH range of from about 9 to about 11; and applying said dispersion to at least said intraluminal surface of said tubular substrate to provide an improved antithrombogenic seal to said prosthesis.
18. ~A synthetic collagen-heparin impregnated vascular prosthesis as defined by claim 17, wherein said process includes applying said dispersion to at least the intraluminal surface of a three-dimensional braided substrate.
19. ~A synthetic collagen-heparin impregnated vascular prosthesis as defined by claim 17, wherein said process includes applying said dispersion to at least the intraluminal surface of a knitted substrate.
20. ~A synthetic collagen-heparin impregnated vascular prosthesis as defined by claim 17, wherein said process includes applying said dispersion to at least the intraluminal surface of a woven substrate.
21. ~A synthetic collagen-heparin impregnated vascular prosthesis as defined by claim 17, wherein said process includes supplying said dispersion in a ratio of collagen to heparin of not less than one.
22. ~A synthetic collagen-heparin impregnated vascular prosthesis as defined by claim 17, wherein said process includes crosslinking said collagen after it is applied to said prosthesis.
23. ~A synthetic collagen-heparin impregnated vascular prosthesis as defined by claim 17, wherein said process includes providing said dispersion in a pH
with a range of about 9 to about 11.
24. ~A synthetic collagen-heparin impregnated vascular prosthesis as defined by claim 17, wherein said process includes providing said dispersion at pH of about 10.
25. ~A method of preparing a stable collagen-heparin dispersion for treating implantable synthetic prostheses, comprising the steps of:
mixing collagen and water to prepare a collagen dispersion in which the percentage of collagen is 2% by weight;
adding sodium hydroxide in sufficient amounts to said dispersion to raise the pH to an alkaline pH
level within a pH range of about 9 to 11 to avoid collagen precipitation; and adding heparin to said dispersion in an amount in a ratio of heparin to collagen of from about 1:100 to about 1.1.
CA002148670A 1994-08-12 1995-05-04 Vascular graft impregnated with a heparin-containing collagen sealant Expired - Fee Related CA2148670C (en)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US28979294A 1994-08-12 1994-08-12
US08/289,792 1994-08-12

Publications (2)

Publication Number Publication Date
CA2148670A1 CA2148670A1 (en) 1996-02-13
CA2148670C true CA2148670C (en) 2008-05-13

Family

ID=23113122

Family Applications (1)

Application Number Title Priority Date Filing Date
CA002148670A Expired - Fee Related CA2148670C (en) 1994-08-12 1995-05-04 Vascular graft impregnated with a heparin-containing collagen sealant

Country Status (7)

Country Link
US (2) US5851230A (en)
EP (1) EP0698396B1 (en)
JP (1) JP3504389B2 (en)
AU (1) AU700584C (en)
CA (1) CA2148670C (en)
DE (1) DE69524501T2 (en)
FI (1) FI952217A (en)

Families Citing this family (67)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6334872B1 (en) * 1994-02-18 2002-01-01 Organogenesis Inc. Method for treating diseased or damaged organs
AU700584C (en) * 1994-08-12 2002-03-28 Meadox Medicals, Inc. Vascular graft impregnated with a heparin-containing collagen sealant
US20020095218A1 (en) 1996-03-12 2002-07-18 Carr Robert M. Tissue repair fabric
GB9616272D0 (en) * 1996-08-02 1996-09-11 Vascutek Ltd Expansible woven fabric
US7241309B2 (en) 1999-04-15 2007-07-10 Scimed Life Systems, Inc. Self-aggregating protein compositions and use as sealants
US6177609B1 (en) 1997-03-10 2001-01-23 Meadox Medicals, Inc. Self-aggregating protein compositions and use as sealants
FI974321A0 (en) * 1997-11-25 1997-11-25 Jenny Ja Antti Wihurin Rahasto Multiple heparinglycosaminoglycans and proteoglycans are used
US20020099438A1 (en) 1998-04-15 2002-07-25 Furst Joseph G. Irradiated stent coating
EP1083843A4 (en) 1998-06-05 2005-06-08 Organogenesis Inc Bioengineered vascular graft support prostheses
AU754838B2 (en) 1998-06-05 2002-11-28 Organogenesis Inc. Bioengineered flat sheet graft prostheses
WO1999062425A2 (en) 1998-06-05 1999-12-09 Organogenesis Inc. Bioengineered vascular graft prostheses
EP1082057B1 (en) 1998-06-05 2009-02-25 Organogenesis Inc. Bioengineered tubular graft prostheses
US6312457B1 (en) 1999-04-01 2001-11-06 Boston Scientific Corporation Intraluminal lining
US6355063B1 (en) 2000-01-20 2002-03-12 Impra, Inc. Expanded PTFE drug delivery graft
US20070055367A1 (en) * 2000-03-15 2007-03-08 Orbus Medical Technologies, Inc. Medical device with coating that promotes endothelial cell adherence and differentiation
US20030229393A1 (en) * 2001-03-15 2003-12-11 Kutryk Michael J. B. Medical device with coating that promotes cell adherence and differentiation
EP1263484B1 (en) 2000-03-15 2007-05-16 OrbusNeich Medical, Inc. Coating which promotes endothelial cell adherence
US8088060B2 (en) 2000-03-15 2012-01-03 Orbusneich Medical, Inc. Progenitor endothelial cell capturing with a drug eluting implantable medical device
US8460367B2 (en) 2000-03-15 2013-06-11 Orbusneich Medical, Inc. Progenitor endothelial cell capturing with a drug eluting implantable medical device
US9522217B2 (en) 2000-03-15 2016-12-20 Orbusneich Medical, Inc. Medical device with coating for capturing genetically-altered cells and methods for using same
CA2777791A1 (en) * 2000-09-18 2002-03-21 Organogenesis Inc. Methods for treating a patient using a bioengineered flat sheet graft prostheses
AU2002230770A1 (en) * 2000-10-31 2002-05-15 Prodesco, Inc. Graft having region for biological seal formation
US6641607B1 (en) 2000-12-29 2003-11-04 Advanced Cardiovascular Systems, Inc. Double tube stent
CN1492759A (en) 2001-01-16 2004-04-28 Ѫ�������������ι�˾ Device and method for preventing or treating failure of hemodialysis vascular access and other vascular grafts
WO2002077336A1 (en) * 2001-03-26 2002-10-03 University College London Methods for forming hardened tubes and sheets
US7029838B2 (en) * 2001-03-30 2006-04-18 Arizona Board Of Regents On Behalf Of The University Of Arizona Prevascularized contructs for implantation to provide blood perfusion
US7226611B2 (en) * 2001-04-02 2007-06-05 Yaizu Suisankagaku Industry Co., Ltd. Glycosaminoglycan/collagen complexes and use thereof
US7682669B1 (en) 2001-07-30 2010-03-23 Advanced Cardiovascular Systems, Inc. Methods for covalently immobilizing anti-thrombogenic material into a coating on a medical device
US7022135B2 (en) * 2001-08-17 2006-04-04 Medtronic, Inc. Film with highly porous vascular graft prostheses
US8740973B2 (en) 2001-10-26 2014-06-03 Icon Medical Corp. Polymer biodegradable medical device
US9539121B2 (en) * 2002-02-07 2017-01-10 Dsm Ip Assets B.V. Apparatus and methods for conduits and materials
US8016881B2 (en) * 2002-07-31 2011-09-13 Icon Interventional Systems, Inc. Sutures and surgical staples for anastamoses, wound closures, and surgical closures
US7550004B2 (en) * 2002-08-20 2009-06-23 Cook Biotech Incorporated Endoluminal device with extracellular matrix material and methods
US6649514B1 (en) * 2002-09-06 2003-11-18 Lattice Semiconductor Corporation EEPROM device having improved data retention and process for fabricating the device
IL152030A0 (en) * 2002-09-30 2003-05-29 Nvr Labs Ltd Neural & Vascular Cohesive biopolymers comprising sulfated polysaccharides and fibrillar proteins and use thereof for tissue repair
US7060684B1 (en) 2002-12-16 2006-06-13 Quijano Rodolfo C Device for treating diabetes and methods thereof
WO2004112864A2 (en) 2003-06-19 2004-12-29 Vascular Therapies Llc Medical devices and methods for regulating the tissue response to vascular closure devices
US7211108B2 (en) 2004-01-23 2007-05-01 Icon Medical Corp. Vascular grafts with amphiphilic block copolymer coatings
US20050196571A1 (en) * 2004-03-03 2005-09-08 Penny John H.Iii Air freshener
EP2946666B1 (en) 2004-04-30 2017-11-15 OrbusNeich Medical, Inc. Medical device with coating for capturing genetically-altered cells and methods of using same
US8313524B2 (en) 2004-08-31 2012-11-20 C. R. Bard, Inc. Self-sealing PTFE graft with kink resistance
WO2006044904A2 (en) * 2004-10-15 2006-04-27 Vanderbilt University Nano- and micro-scale engineering of polymeric scaffolds for vascular tissue engineering
US8029563B2 (en) 2004-11-29 2011-10-04 Gore Enterprise Holdings, Inc. Implantable devices with reduced needle puncture site leakage
WO2006110197A2 (en) 2005-03-03 2006-10-19 Icon Medical Corp. Polymer biodegradable medical device
US9107899B2 (en) 2005-03-03 2015-08-18 Icon Medical Corporation Metal alloys for medical devices
US7540995B2 (en) 2005-03-03 2009-06-02 Icon Medical Corp. Process for forming an improved metal alloy stent
US9788821B2 (en) * 2005-04-29 2017-10-17 Cook Biotech Incorporated Physically modified extracellular matrix materials and uses thereof
US20060257355A1 (en) * 2005-05-10 2006-11-16 Abiomed, Inc. Impregnated polymer compositions and devices using them
JP5127120B2 (en) * 2005-05-13 2013-01-23 独立行政法人国立循環器病研究センター Connective tissue-forming substrate and method for producing connective tissue using the same
WO2007001472A2 (en) 2005-06-17 2007-01-04 C. R. Bard, Inc. Vascular graft with kink resistance after clamping
CA2618776A1 (en) * 2005-08-10 2007-02-22 Martin S. Dieck Anti-restenotic therapeutic device
EP1945138A4 (en) * 2005-11-09 2010-02-10 Bard Inc C R Grafts and stent grafts having a radiopaque marker
FR2892939B1 (en) * 2005-11-10 2010-01-22 Groupement Coeur Artificiel Total Carpentier Matra Carmat COMPOSITE HEMOCOMPATIBLE MATERIAL AND METHOD FOR OBTAINING THE SAME
US20070225795A1 (en) * 2006-03-24 2007-09-27 Juan Granada Composite vascular prosthesis
US7572625B2 (en) * 2006-05-18 2009-08-11 Boston Scientific Scimed, Inc. Medical devices coated with drug carrier macromolecules
WO2008063780A2 (en) * 2006-10-12 2008-05-29 C.R. Bard Inc. Vascular grafts with multiple channels and methods for making
US8388679B2 (en) 2007-01-19 2013-03-05 Maquet Cardiovascular Llc Single continuous piece prosthetic tubular aortic conduit and method for manufacturing the same
BRPI0914304A2 (en) * 2008-06-20 2015-10-13 Cook Biotech Inc compressible / expandable graft medical products, and methods for applying haemostasis
US8398916B2 (en) 2010-03-04 2013-03-19 Icon Medical Corp. Method for forming a tubular medical device
US8696741B2 (en) 2010-12-23 2014-04-15 Maquet Cardiovascular Llc Woven prosthesis and method for manufacturing the same
PL231639B1 (en) 2012-04-17 2019-03-29 Politechnika Lodzka Medical material for the reconstruction of blood vessels, a method for producing the medical material and medical material applied to the reconstruction of blood vessels
US9814560B2 (en) 2013-12-05 2017-11-14 W. L. Gore & Associates, Inc. Tapered implantable device and methods for making such devices
CN106535826A (en) 2014-06-24 2017-03-22 怡康医疗股份有限公司 Improved metal alloys for medical devices
CA2985477C (en) 2015-06-05 2020-03-10 W.L. Gore & Associates, Inc. A low bleed implantable prosthesis with a taper
WO2017151548A1 (en) 2016-03-04 2017-09-08 Mirus Llc Stent device for spinal fusion
GB201717885D0 (en) 2017-10-31 2017-12-13 Hothouse Medical Ltd Prothesis and method of manufacture
US11027046B2 (en) 2017-10-31 2021-06-08 Hothouse Medical Limited Textile products having selectively applied sealant or coating and method of manufacture

Family Cites Families (66)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3106483A (en) * 1961-07-27 1963-10-08 Us Catheter & Instr Corp Synthetic blood vessel grafts
DE1494939B2 (en) * 1963-06-11 1972-03-02 Buddecke, Eckhart, Prof Dr , 4400 Munster Implantation material for prostheses for the replacement of arteries and other pathways and hollow organs containing body juices and processes for the production thereof
CH472219A (en) * 1963-06-15 1969-05-15 Spofa Vereinigte Pharma Werke Highly porous collagen tissue blood vessel prosthesis and method for producing the same
US3272204A (en) * 1965-09-22 1966-09-13 Ethicon Inc Absorbable collagen prosthetic implant with non-absorbable reinforcing strands
US3479670A (en) * 1966-10-19 1969-11-25 Ethicon Inc Tubular prosthetic implant having helical thermoplastic wrapping therearound
DE1766340A1 (en) * 1967-05-19 1971-07-01 Vyzk Ustav Pletarzsky Textile collagen prosthesis
FR2029155A5 (en) * 1969-01-15 1970-10-16 Mo Med I Prosthetic vessels of high biological - permeability
CA962021A (en) * 1970-05-21 1975-02-04 Robert W. Gore Porous products and process therefor
JPS494559B1 (en) * 1970-08-06 1974-02-01
US3688317A (en) * 1970-08-25 1972-09-05 Sutures Inc Vascular prosthetic
DE2119004A1 (en) * 1971-04-20 1972-10-26 Friess, Alfred, 8802 Wieseth Paint roller
US3805301A (en) * 1972-07-28 1974-04-23 Meadox Medicals Inc Tubular grafts having indicia thereon
US4164524A (en) * 1974-05-31 1979-08-14 Ward Charles A Treatment of blood containing vessels
US3928653A (en) * 1975-02-05 1975-12-23 Tee Pak Inc Collagen slurry containing partial fatty acid esters of glycerin
US4281669A (en) * 1975-05-09 1981-08-04 Macgregor David C Pacemaker electrode with porous system
US4280954A (en) * 1975-07-15 1981-07-28 Massachusetts Institute Of Technology Crosslinked collagen-mucopolysaccharide composite materials
GB1515963A (en) * 1975-07-15 1978-06-28 Massachusetts Inst Technology Crosslinked collagen-mucopolysaccharide composite materials
DE2601289C3 (en) * 1976-01-15 1978-07-13 B. Braun Melsungen Ag, 3508 Melsungen Method for sealing synthetic velor vascular prostheses
US4047252A (en) * 1976-01-29 1977-09-13 Meadox Medicals, Inc. Double-velour synthetic vascular graft
DE7618150U1 (en) * 1976-06-08 1976-10-07 Hucke, Hans, Pratteln (Schweiz) FLOW ELEMENT
GB1538810A (en) * 1976-08-10 1979-01-24 Sumitomo Electric Industries Hydrophilic porous fluorocarbon structures and process for their production
GB1537448A (en) * 1976-08-20 1978-12-29 Sumitomo Electric Industries Vascular prostheses and process for production thereof
US4349467A (en) * 1977-01-31 1982-09-14 Williams Joel L Nonthrombogenic articles and method of preparation
JPS5413694A (en) * 1977-07-01 1979-02-01 Sumitomo Electric Industries Composite blood vessel prosthesis and method of producing same
US4167045A (en) * 1977-08-26 1979-09-11 Interface Biomedical Laboratories Corp. Cardiac and vascular prostheses
DE2843963A1 (en) * 1978-10-09 1980-04-24 Merck Patent Gmbh BODY-RESORBABLE SHAPED MATERIAL BASED ON COLLAGEN AND THEIR USE IN MEDICINE
US4219520A (en) * 1978-08-30 1980-08-26 Medical Evaluation Devices And Instruments Corp. Method of making thrombo-resistant non-thrombogenic objects formed from a uniform mixture of a particulate resin and colloidal graphite
CA1147109A (en) * 1978-11-30 1983-05-31 Hiroshi Mano Porous structure of polytetrafluoroethylene and process for production thereof
US4713070A (en) * 1978-11-30 1987-12-15 Sumitom Electric Industries, Ltd. Porous structure of polytetrafluoroethylene and process for production thereof
US4254180A (en) * 1979-01-02 1981-03-03 Medical Evaluation Devices & Instruments Corp. Thrombo-resistant non-thrombogenic objects formed from resin-graphite mixtures
US4416028A (en) * 1981-01-22 1983-11-22 Ingvar Eriksson Blood vessel prosthesis
US4409172A (en) * 1981-02-13 1983-10-11 Thoratec Laboratories Corporation Device and method for fabricating multi-layer tubing using a freely suspended mandrel
US4546500A (en) * 1981-05-08 1985-10-15 Massachusetts Institute Of Technology Fabrication of living blood vessels and glandular tissues
EP0085077A1 (en) * 1981-08-05 1983-08-10 Service First International Limited Temperature controlling or detecting device
EP0107711A4 (en) * 1982-04-19 1985-10-24 Massachusetts Inst Technology A multilayer bioreplaceable blood vessel prosthesis.
EP0130401B1 (en) * 1983-06-06 1989-05-17 Kanegafuchi Kagaku Kogyo Kabushiki Kaisha Artificial vessel and process for preparing the same
US5034265A (en) * 1983-08-01 1991-07-23 Washington Research Foundation Plasma gas discharge treatment for improving the compatibility of biomaterials
US4842575A (en) * 1984-01-30 1989-06-27 Meadox Medicals, Inc. Method for forming impregnated synthetic vascular grafts
US5197977A (en) * 1984-01-30 1993-03-30 Meadox Medicals, Inc. Drug delivery collagen-impregnated synthetic vascular graft
US5108424A (en) * 1984-01-30 1992-04-28 Meadox Medicals, Inc. Collagen-impregnated dacron graft
FR2559666B1 (en) * 1984-02-21 1986-08-08 Tech Cuir Centre PROCESS FOR THE MANUFACTURE OF COLLAGEN TUBES, ESPECIALLY LOW-DIAMETER TUBES, AND APPLICATION OF THE TUBES OBTAINED IN THE FIELD OF VASCULAR PROSTHESES AND NERVOUS SUTURES
US4837024A (en) * 1984-02-24 1989-06-06 The Regents Of The University Of California Compositions, articles and mehtod for improving wound healing
US4837285A (en) * 1984-03-27 1989-06-06 Medimatrix Collagen matrix beads for soft tissue repair
US5037377A (en) * 1984-11-28 1991-08-06 Medtronic, Inc. Means for improving biocompatibility of implants, particularly of vascular grafts
GB8430265D0 (en) * 1984-11-30 1985-01-09 Vascutek Ltd Vascular graft
JPS6229532A (en) * 1985-07-31 1987-02-07 Koken:Kk Antithrombogenetic medical material and production thereof
US5061281A (en) * 1985-12-17 1991-10-29 Allied-Signal Inc. Bioresorbable polymers and implantation devices thereof
CA1292597C (en) * 1985-12-24 1991-12-03 Koichi Okita Tubular prothesis having a composite structure
DE3608158A1 (en) * 1986-03-12 1987-09-17 Braun Melsungen Ag VESSELED PROSTHESIS IMPREGNATED WITH CROSSLINED GELATINE AND METHOD FOR THE PRODUCTION THEREOF
US4911713A (en) * 1986-03-26 1990-03-27 Sauvage Lester R Method of making vascular prosthesis by perfusion
ES2004281A6 (en) * 1986-04-04 1988-12-16 Univ Jefferson Method of treating a synthetic naturally occurring surface with a collagen laminate to support microvascular endothelial cell growth, and the surface itself
EP0241838B1 (en) * 1986-04-07 1992-04-15 Agency Of Industrial Science And Technology Antithrombogenic material
EP0246638A3 (en) * 1986-05-23 1989-03-15 Cordis Corporation Biologically modified synthetic grafts
CH670759A5 (en) * 1986-06-02 1989-07-14 Sulzer Ag
US5061276A (en) * 1987-04-28 1991-10-29 Baxter International Inc. Multi-layered poly(tetrafluoroethylene)/elastomer materials useful for in vivo implantation
US4842275A (en) * 1988-04-21 1989-06-27 Yury Tsatskin Method for conducting a competition
US5024671A (en) * 1988-09-19 1991-06-18 Baxter International Inc. Microporous vascular graft
US4973609A (en) * 1988-11-17 1990-11-27 Memron, Inc. Porous fluoropolymer alloy and process of manufacture
JP2814574B2 (en) * 1989-06-15 1998-10-22 住友電気工業株式会社 Polytetrafluoroethylene porous body and method for producing the same
US5141522A (en) * 1990-02-06 1992-08-25 American Cyanamid Company Composite material having absorbable and non-absorbable components for use with mammalian tissue
US5148222A (en) * 1990-08-22 1992-09-15 Spectrum Sciences B.V. Liquid developer system
US5178630A (en) * 1990-08-28 1993-01-12 Meadox Medicals, Inc. Ravel-resistant, self-supporting woven graft
US5118524A (en) * 1990-09-14 1992-06-02 The Toronto Hospital Vascular biomaterial
US5120833A (en) * 1991-03-15 1992-06-09 Alexander Kaplan Method of producing grafts
US5192310A (en) * 1991-09-16 1993-03-09 Atrium Medical Corporation Self-sealing implantable vascular graft
AU700584C (en) * 1994-08-12 2002-03-28 Meadox Medicals, Inc. Vascular graft impregnated with a heparin-containing collagen sealant

Also Published As

Publication number Publication date
JP3504389B2 (en) 2004-03-08
US5851230A (en) 1998-12-22
JPH0866469A (en) 1996-03-12
DE69524501T2 (en) 2002-05-29
AU1772195A (en) 1996-02-22
DE69524501D1 (en) 2002-01-24
US6162247A (en) 2000-12-19
AU700584B2 (en) 1999-01-07
EP0698396B1 (en) 2001-12-12
CA2148670A1 (en) 1996-02-13
FI952217A (en) 1996-02-13
AU700584C (en) 2002-03-28
EP0698396A1 (en) 1996-02-28
FI952217A0 (en) 1995-05-08

Similar Documents

Publication Publication Date Title
CA2148670C (en) Vascular graft impregnated with a heparin-containing collagen sealant
EP0941131B1 (en) Improved bioresorbable sealants for porous vascular grafts
CA2147565C (en) Tubular polytetrafluoroethylene implantable prostheses
EP1173237B1 (en) Expanded polytetrafluoroethylene vascular graft with coating
Guidoin et al. Albumin coating of a knitted polyester arterial prosthesis: an alternative to preclotting
US5632776A (en) Implantation materials
EP0512122A1 (en) Implant material
CA2547559C (en) Blood-tight implantable textile material and method of making
NL8500239A (en) ARTIST OF ARTICLE DELIVERING MEDICINAL PRODUCT AND METHOD OF MANUFACTURE THEREOF
JPH0636818B2 (en) Collagen synthetic vascular graft tissue
EP0246638A2 (en) Biologically modified synthetic grafts
AU737348B2 (en) Vascular graft impregnated with a heparin-containing collagen sealant
EP0941739A1 (en) Porous coated artificial implant material and corresponding preparation process
JPH04187154A (en) Artificial blood vessel and patch
AU724790B2 (en) Tubular polytetrafluoroethylene implantable prostheses
Lee et al. Blood leak-proof porous vascular grafts

Legal Events

Date Code Title Description
EEER Examination request
MKLA Lapsed

Effective date: 20130506