US3927422A - Prosthesis and method for making same - Google Patents

Prosthesis and method for making same Download PDF

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US3927422A
US3927422A US42406273A US3927422A US 3927422 A US3927422 A US 3927422A US 42406273 A US42406273 A US 42406273A US 3927422 A US3927422 A US 3927422A
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prosthesis
collagen
method
surface
vascular
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Philip Nicholas Sawyer
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Interface Biomedical Laboratories Corp
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    • 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
    • A61L33/0076Chemical modification of the substrate
    • A61L33/0082Chemical modification of the substrate by reacting with an organic compound other than heparin

Abstract

A tubular collagen vascular graft prosthesis is subjected to treatment so that its intimal surface has an increased net negative surface charge which prevents thrombosis. Treatment with succinic anhydride is shown as one way of accomplishing this. Valve grafts are likewise treated.

Description

Umted States Patent 11 1 [111 3,

Sawyer 5] Dec. 23, 1975 54 ISROSTHESIS AND METHOD FOR MAKING OTHER PUBLICATIONS Means et a1 Chem. Modification of Proteins" Hold- Inventori Philip Nicholas Sawyer, 603 Third en-Day, Inc. S.F., Califor. pp. 144-148, 74-83.

Brooklyn. NY. 11215 Sawyer et al. Trans. ASAIO, v61. x11, 1966 pp. 22 Filed: Dec. 12, 1973 18344 PP N05 424,062 Primary Examiner-Dalton L. Truluck Attorney, Agent, or FirmRoberts & Cohen [52] U.S. Cl. 3/1; 128/334 R 51 1111. C1 A61F 01/24 [57] ABSTRACT [58] Field of Search 3/1,D1G 1; 128/334 R, A tubular collagen vascular graft prosthesis is sub- 128/335, 335.5; 161/178, 226; 117/95 jected to treatment so that its intimal surface has an increased net negative surface charge which prevents References Cited thrombosis. Treatment with succinic anhydride is UNITED STATES PATENTS shown as one way of accomplishing this. Valve grafts 2,900,644 8/1959 Rosenberg et al. 3/1 are hkewlse treated 3,609,768 10/1971 Ayres 128/334 R X 13 Claims, 3 Drawing Figures U.S. Patant Dec. 23, 1975 3,927,422

UPSTREAM EL E 677F005 DOWNSTREAM ELECTRODE ELfCTEODE PROSTHESIS AND METHOD FOR MAKING SAME BACKGROUND Aside from the publications and articles to be mentioned hereafter, pertinent material will be found in the following:

Wesolowski, S. A.: The healing of vascular prostheses. Surgery 57:319, 1965.

Wesolowski, S. A., Fries, C. C., Domingo, R. T., Fox L. M., and Sawyer, P. N.: Fate of simple and compound arterial prostheses: Experimental and human observations. In: Fundamentals of Vascular Grafting. McGraw- Hill, New York, 1963, pp. 252-268.

Wesolowski, S. A., Hennigar, G. R., Fox, L. M., Fries, C. C., and Sauvage, L. R.: Factors contributing to long term failure in human vascular prosthetic grafts. Presented at Symposium on Late Results of Arterial Reconstruction. International Cardiovascular Society Meeting, Rome, September 1963. J. Cardiov. Surg. :44 1964.

Sawyer, P. N., and Pate, J. W.: A study of electrical potential differences across the normal aorta and aortic grafts of dogs. Research Report NM 007081, 10.06. Naval Medical Research Institute, Bethesda, Md., 1953.

Sawyer, P. N., and Pate, J. W.: Bioelectric phenomena as etiologic factors in intravascular thrombosis. Amer. J. Physiol. 1751103, 1953.

Williams, R. D., and Carey, L. C.: Studies in the production of standard venous thrombosis. Ann. Surg. 149:381, 1959.

Schwartz, S. 1., and Robinson, J. W.: Prevention of thrombosis with the use of a negative electric current. Surg. Forum 12:46, 1961.

Sadd, J. R., Koepke, D. E., Daggett, R. L., Zarnsdorff, W. C., Young, W. P., and Gott, V. L.: Relative ability of different conductive surfaces to repel clot formation on intravascular prostheses. Surg. Forum 12:252, 1961.

Means, G. E., and Feeney, R. E.: Chemical Modification of Proteins. Holden-Day, lnc., San Francisco, Calif. 1971, pp. 144-148.

SUMMARY OF INVENTION It is an object of the invention to provide an improved method for preparing a collagen vascular graft prosthesis.

Still another object of the invention is to provide an improved vascular graft prosthetic device which is less susceptible to thrombosis and the like.

Still another object of the invention is to provide an improved tubular vascular graft, the intimal surface of which cannot be recognized by blood platelets for purposes of accumulation. I

The above and other objects of the invention are achieved by the provision of a method in accordance with the invention which comprises modifying the intimal surface of a'vascular graft prosthesis by increasing the net negative" surface chargeof the intimal surface thereof. g I

Preferably the prosthesis will be of collagen and the intimal surface thereof will be treated by a succinylacollagen surface be covered.

tion reaction in order that thefree amino groups of the Preferably the starting material of the graft will'be a collagen prepared from a ficin digested bovine carotid artery material also known as a dialdehyde' starch tanned collagen,

As will be'shown, the graft is generally provided in the form of a collagen tube one end of which is closed and inserted into a fluid such as ethanol with a liquid chemical reactant being inserted into'the lumen of the tube to increase the negative surface charge of the intimal surface thereof. The reactant may preferably be, as will be shown hereinafter, succinic anhydride in a basic solution.

More particularly a Nal-lCO buffer solution is inserted into the lumen in sequential additions of approximately 10 ml. aliquots to which about 0.1 gm. of crystals of succinic anhydride are respectively added.

The above and other objects and features of the invention will become apparent from the detailed description which follows hereinbelow.

Before, however, the detailed description of the invention is presented, there is next given a further brief summary as to how the study leading to the instant invention was undertaken.

Collagen vascular prostheses prepared by enzymatically digesting bovine carotid arteries with ficin was obtained. Segments of these vascular prostheses were modified chemically to alter their intimal surface electrochemical configuration and, more particularly, for producing a net positive surface charge, negative surface charge, or neutral surface charge. These modified vascular grafts, together with segments of the unmodified collagen vascular prostheses were implanted into the carotid arteries, external jugular veins, femoral arteries and femoral veins of mongrel dogs for periods of 1 minute, 15 minutes, 30 minutes and 2 hours. The grafts were then removed and examined macroscopically for the presence and degree of thrombotic occlusion. These same prostheses were further analyzed using a scanning electron microscope in an attempt to determine the precisenature of the occluding thrombi. It was found that by increasing the net negative surface charge density on the intimal surface of these vascular prostheses, thrombotic occlusion could be substantially averted, while creating a more positive prosthesesblood interface potential greatly accelerated the thrombotic events.

Segments of these vascular protheses were again implanted into the vascular system of mongrel dogs and in vivo arterial and venous streaming potential measurements were carried out. The polarity of the streaming potential reflects the interfacial potential between the vascular prosthesis and the blood flowing through the graft with a positive streaming potential at the downstream electrode indicating a net negative surface charge density on the intimal surface of the graft with respect to the blood elements. The arterial and venous in vivo streaming potentials obtained from the negatively altered collagen vascular prostheses were uniformly positive in polarity, while those streaming po- 'tentials obtained from the positively modified grafts were uniformly negative. The streaming potentials obtained from those grafts altered chemically to neutralize the intimal surface charges at physiological pH were also found to be positive in polarity but of a lesser magnitude: than the negatively altered grafts. The unmodified ficin digested bovine carotid arteries had streaming potentials of a slightly negative polarity. These streaming potential measurements served to check the chemical modification procedures and assure that the electrical alteration of surface charge density occurred as predicted.

BRIEF DESCRIPTION OF DRAWING FIG. I diagrammatically illustrates apparatus for practicing the invention;

the primary step in haemostasis. Nature New Biology 23415 (I971 Barber, A. J. and Jamieson, G. A.: Platelet collagen adhesion characterization of collagen glucosyltransferase of plasma membanes of human blood platelets. Biochim. Biophys. Acta 2522533 (1971)). The reaction involves the enzymatic coupling of glucose to galaetosyl residues attached to hydroxylysine side chains incorporated into the collagen peptides. The glucose is supplied by platelets as uridinedi- FIG. 2 diagrammatically illustrates a technique for phosphoglucose (UDPG) according to the following:

Q-aminO group of hydroxylysine H OH H2 Galaetose R R H o UDPG Glucosyltransferase UDP H N 2 CH OH R: Collagen H o ca oa R N R.

Glucose H measuring streaming potential in accordance with the invention; and

FIG. 3 diagrammatically illustrates a portion of FIG. 2 on enlarged scale.

DETAILED DESCRIPTION Platelet aggregation activity of collagen in vitro has been shown to require the structural integrity of the 6-hydroxymethyl group of galactose and the e-amino groups of lysine and hydroxylysineon the collagen molecule. It has been postulated that the substrate specificity of the platelet glucosyltransferase is responsible for these observed platelet aggregation dependent phenomena (Chesney, C., Harper, E., and Coleman, R.

W.: Critical role of the carbohydrate side chains of collagen in platelet aggregation. HIEG 72-43 (I972); Wilner, G. D., Nossel, H. L., and LeRoy, E. C.: Aggregation of platelets by collagen. J; Clin. Invest. 4722616 (I968) The use of modified bovine arterial heterografts as vascular prostheses has previously been reported and their physical and behavioral characteristics as arterial grafts have been discussed in detail. In the present studies it was found that increasing the electronegativity of the inner surface of the prosthesis significantly contributed to afavorable graft performance.

Some of the above is discussed in the following:

Bothwell, J. W., Lord, G. H., Rosenberg, N., Burrowes, C. B., Wesolowski, S. A., and Sawyer, P. N.: Modified arterial heterografts: relationship of processing techniques to interface characteristics. In: Biophysical Mechanisms in Vascular Homeostasis and Intravascular Thrombosis, P. N. Sawyer, Ed. Appleton-Century-Crofts, New York, 1965, pp. 306-313; Rosenberg, N., Henderson, J., Douglas, J. F., Lord, G. H., and Gaughran, E. R. L.: Use of arterial implants prepared by enzymatic modification of arterial heterografts. II. Physical properties of the elastica and collagen components of the arterial wall. Arch. Surg. 74:89 (1957); Rosenberg, N., Henderson, J., Lord, G. H., and Bothwell, J. W.: Use of enzyme treated heterografts as segmental arterial substitutes. V. Influence of processing factors on strength and invasion by host. Arch. Surg. 85:192 (1962); Rosenberg, N., Henderson, J., Lord, G. H., and Bothwell, J. W.: An arterial prosthesis of heterologous vascular origin. JAMA 1872741 (1964); R- senberg, N., Henderson, J., Lord, G. H., and Bothwell, J. W.: Collagen arterial prosthesis of heterologous vascular origin: physical properties and behavior as an arterial graft. In: Biophysical Mechanisms in Vascular Homeostasis and Intravascular Thrombosis, P. N. Sawyer, Ed. Appleton-Century-Crofts, New York, I965, pp. 314-321.

Succinylation of solubilized collagen has been demonstrated to result in an approximately 95% conversion of e-amino groups to free carboxyl groups (Gustavson, K. H.: Akiv. For Kemi I7: 541 (1961)). Furthermore, it has been shown that blockage of the free amino groups of collagen by deamination, N-aeetylation or treatment with dinitroflurobenzene results in a greater than 90% reduction in platelet aggregating activity in vitro.

Investigation has now been conducted in order to elucidate the antiplatelet and antithrombogenic activity of chemically modified collagen by the in vivo evaluation of ficin digested bovine arterial heterograft vascular prostheses implanted into the vascular system of mongrel dogs.

For the chemical modification of ficin digested bovine carotid arteries, the apparatus devised for the chemical modification of ficin digested bovine carotid arteries is as appears in FIG. 1. It includes a receptacle 10 having an open mouth 12 through which extends the shaft 14 of an electric stirrer 16. A glass stopcock I8 is arranged in the lower end of a ficin digested bovine carotid artery which is immersed, for example, in ethanol.

In order to increase the net positive surface charge density on the intimal surface of the collagen vascular prostheses a carbodiimide-promoted amide formation reaction was employed to convert the major source of net negative charges (free carboxyl groups of aspartic and glutamic acid) to amide moieties. The procedure involves treatment of the protein with excess EDC (l-ethyl-3,3 -dim ethylaminopro pylcarbodiimide HCI) and an amine (NH CI) in the presence of a high concentration of a denaturant (urea). This reaction (Means, GE, and Feeney, R.E.: Chemical Modification of Proteins. Holden-Day, Inc., San Francisco, Calif, 1971, pp. l44l48) has been used for the near quantitative conversion of protein carboxyl groups to amides for determining numbers of carboxyl groups in proteins (Hoare, D. G. and Koshland, D. E.: J. Biol. Chem. 242:2447 v( 1967)). The chemical reaction proceeds at room temperature as follows:

wherein:

R CH CH 100 ml of reaction solution at room temperature containing 0.5 M EDC (7.75 gm/IOO ml), 7.5 M urea (45 gm/IOO ml), and 5.0 M NH CI (26.75 gm/l00 ml) in triple distilled water were prepared (adjusted to pH5) and added into the lumen of the vascular prosthesis in 10 ml aliquots with the implant suspended in 40% ethanol as shown in FIG. 1. The reaction solution was changed every hour with the last aliquot remaining within the lumen overnight. At the conclusion of the 24 hour reaction period the vascular prosthesis was removed from the modification apparatus and placed in a pan of sterile saline where the long tubes were cut into segments of 3.5 cm for implantation studies or 10.0cm lengths for streaming potential measurements.

In order to increase the net negative surface charge density on the intimal surface of the collagen vascular prostheses acylation of the free amino groups (especially those of lysine and hydroxylysine) of the protein with succinic anhydride in a solution more basic than a PH of 7.0 was carried out. This reaction not only covers the major source of free positive charges, but also converts them into anionic residues (Means, G. E., and Feeney, R. B: Chemical Modification of Proteins. Holden-Day, Inc., San Francisco, Calif, I971, pp. 74,75). The chemical reaction proceeds as follows:

I! u Protein-NH-C -CH CH C--O A basic solution of ml of ethanol and 25 ml of I M NaHCO buffer solution was prepared and added into the lumen of the vascular prosthesis in 10 ml aliquots over a 5 hour period with the implant suspended in 40% ethanol as shown in FIG. I. To each of these ml aliquots of basic solution were added crystals of succinic anhydride. 1.0 gm of succinic anhydride was equally divided among the 10 aliquots. At the conclusion of the reaction period, the vascular prosthesis was removed from the modification apparatus and placed in a pan of sterile saline where the long tubes were cut into segments of 3.5 cm for implantation studies or 10.0 cm lengths for streaming potential measurements.

In order to neutralize the electrical surface charges on the intimal surface of the collagen vascular prostheses, a carbodiimide promoted internal amide formation reaction was employed to link together the free carboxyl and amino groups of adjacent peptide chains. Such a reaction removed the major sources of electronegativity (carboxyl groups) and electropositivity (free amino groups). The chemical reaction proceeds as follows:

vein was ligated with 3-0 silk and divided near its entrance. The external jugular vein was then dissected free of its fascial attachments down to where it disappears behind the posterior border of the sternocleidomastoid muscle where another loose ligature of umbilical tape was secured. All small perforating branches of the external jugular vein were ligated with 3-0 silk and divided close to their entrance. The anterior border of the sternocleidomastoid muscle was retracted posteriorly to expose the dissection of the fascia and fibroare olar tissue layers that overlie the carotid sheath. The carotid sheath was incised and, after identification of the vagus nerve, a loose ligature of umbilical tape was made to encircle the carotid artery at the level of the third tracheal ring. The incision in the carotid sheath was continued cephalad to the bifurcation of the common carotid artery (or the superior thyroid artery) where another loose ligature of umbilical tape was Protein-CO H,,NProtein 0.5 M EDC ProteinCNHProtein A 100 ml solution of 0.5 M EDC (7.75 gm/lOO ml) in triple distilled water was prepared and added into the lumen of the vascular prosthesis in 10 ml aliquots with the implant suspended in 40% ethanol as shown in FIG. 1. The reaction solution was changed every hour with the last aliquot remaining within the lumen overnight. At the conclusion of the 24 hour reaction period, the vascular prosthesis was removed from the modification apparatus and placed in a pan of sterile saline where the long tubes were cut into segments of 3.5 cm for implantation studies or 10.0 cm lengths for streaming potential measurements.

As a starting material in the above, there was employed, for example, dialdehyde starch tanned collagen vascular prostheses including dialdehyde starch tanned bovine collagen vascular heterografts which were commercially available and obtained from Johnson & Johnson, New Brunswick, New Jersey.

Surgical implantation of modified collagen vascular prostheses involved carotid artery and jugular vein implantation. Mongrel dogs weighing between 10 and 28 Kg (ave. 18.6 Kg) were anesthetized with Nembutal (Sodium Pentabarbital), 0.5 cc/Kg, by intravenous injection. The animals were placed on the operating table in the supine position and an oblique cervical incision, paralleling the anterior border of the sternocleidomastoid muscle was made. The platysma muscle layer was incised along with the anterior layer of the deep cervical fascia and after achieving hemostasis these structures were retracted posteriorly to reveal the external jugular vein. At the angle of the mandible, the posterior auricular vein, the common facial vein and the retromandibular vein were identified and a mobilized segment of each was encircled with a loose ligature of umbilical tape. The posterior external jugular secured.

Implantation of the respective modified collagen vascular prosthesis was carried out as follows: Booties were constructed of 2 cm segments of heavy rubber tubing and placed around the free ends of the loose ligatures of umbilical tape. These booties were then drawn down the ligatures to prevent flow in the respective vessel and held in place with Kelly clamps. Two transverse incisions approximately 2.5 cm apart were made in the respective blood vessel with a pair of fine curved Metzenbaum scissors. The vascular prostheses (3.5 cm in length for macroscopic studies and SEM evaluation and 10.0 cm lengths for streaming potential measurements), mounted over hydrochloric acidcleaned stainless steel cannulas (1.5 cm in length) doubly ligatured with 3-0 silk were implanted via their free cannula ends into the rents in the vessel and secured in place with two ligatures of 3-0 silk. The two anastomoses thus prepared, the connecting piece of blood vessel was severed thus permitting the graft to lie flat in its fascial bed. The Kelly clamps were then removed relieving tension from the booties over the umbilical tapes (distal to blood flow removed first) and allowing blood to flow through the vascular prosthesis. The vascular grafts were left in place for the specified periods of time with the wound covered with saline-soaked gauze pads.

The internal diameters of the blood vessels and the prostheses were calculated by measuring the external diameters of the vessels and implants with blood flowing through the system with a micrometer and substracting two wall thicknesses from these diameters. The discrepancies between the internal diameters of recipient and prosthetic blood vessels are found in Table l.

TABLE I DISCREPANCY BETWEEN INTERNAL DIAMETER OF REClPlENT AND PROSTHETIC BLOOD VESSELS 9 10 TABLE l-continued DISCREPANCY BETWEEN INTERNAL DIAMETER OF RECIPIENT AND PROSTHETIC BLOOD VESSELS *I.D. of Recipient *LD. of Prosthetic Change in Vessel Vessel (mm) Vessel (mm) Internal Diameter 4 l 6 Y= 4.6 T= 9.4 T= 4.8

Jugular 8 10 2 Vein 7 9 2 8 IO 2 8 10 2 8 10 2 Y= 7.8 x'= 9.8 T= 2.0

Femoral 4 10 6 Artery 5 9 4 4 I0 6 5 8 3 4 IO 6 Y= 4.4 T= 9.4 Y= 5.0

Femoral 7 3 Vein 7 8 l 7 9 2 8 10 2 7 l0 3 T= 7.2 Tf= 9.4 Y= 2.2

*LD. Internal Diameter For femoral artery and femoral vein implantation, an incision overlying the femoral triangle was extended caudad over the medial aspect of the thigh to the level of the knee joint. The superficial femoral fascia was dissected free from its loose attachment to the underlying femoral sheath revealing the femoral artery and vein lying within the sheath at the fossa ovalis. The femoral vessels were dissected free of their sheath and the branches of the femoral artery (superficial circumflex iliac artery, external pudendal artery, medial femoral circumflexartery and lateral femoral circumflex artery) were identified, ligated with 3-0 silk and divided close to their origin. A loose ligature of umbilical tape was encircled about the origin of the femoral artery. The rostral branches of the femoral vein were likewise identified, ligated with 3-0 silk and divided near their entrance and the femoral vein was also encircled with a loose ligature of umbilical tape. The sartorius muscle was retracted laterally and the adductor Iongus muscle retracted medially with a pair of self-retaining retractors thus exposing the descending genicular artery and vein. Blunt dissection was carefully continued deep to the descending genicular vessels to expose the caudad continuation of the femoral artery and vein. Small perforating vessels and muscular branches were ligated with 3-0 silk and divided close to their origin or en- For streaming potential measurements, a pair of silversilver chloride electrodes 22 and 24 (FIGS. 2 and 3) were placed into the lumen 26 of the vascular prosthesis 27 through the center of two purse-strings 28 and 30 of 5-0 Dacron sewn into its superficial surface and separated by a distance equivalent to at least 10' radii. Electrodes were attached via conventional shielded leads to a Kiethley electrometer 32 (Sawyer, P. N., Himmelfarb, E., Lustrin, 1., and Ziskind, H.: Measurement of streaming potentials of mammalian blood vessels, aorta, and vena cava, in vivo. Biophys. J. 6: 641 (1966)).

For removal, fixation and macroscopic observation, at the conclusion of the respective time periods, the blood vessels upstream and downstream from both the arterial and venous implants were doubly crossclamped with straight Kelly clamps and divided between the two clamps. Bothv prostheses (arterial and venous) filled with blood and occluded at both ends with the Kelly clamps were immediately removed and placed into a 10% formalin solution. While remaining under the fluid level of the formalin, the Kelly clamps were removed along with the stainless steel cannulas and the 3-0 silk Iigatures and the vascular implants were placed in appropriately labeled tubes containing 10% formalin. The degree of thrombotic occlusion was graded on a scale of O to 4+ by three independent observers in a single-blind manner. The averages of the three graded values for each vessel and time period appear in Table 2.

TABLE 2 MACROSCOPIC OBSERVATION OF MODIFIED COLLAGEN VASCULAR PROSTHESES IMPLANTATION* TABLE 2-continued MACROSCOPIC OBSERVATION OF MODIFIED COLLAGEN VASCULAR PROSTHESES IMPLANTATION* I Blood Dialdehydc Time Vessel Unmodified Positive Negative Neutral Starch Tanned 2 hrs R] V 3 4+ l+ 3+ 3+ prosthetic vascular lumen. All scaled observations were carried out single-blind.

(LFA Left Femoral Artery; LFV Left Femoral Vein; LCA Left Carotid Artery; LIV Left .lugular Vein; RFA Right Femoral Artery; RFV Right Femoral Vein; RCA Right Carotid Artery;

RJV Right jugular Vein) The degree of thrombotic occlusion of the variously modified ficin digested bovine vascular hetcrografts is seen in Table 2 above. The unmodified arterial and venous heterografts did not initially thrombose when exposed to the blood elements. As the implantation time increased, however, it can be noted that both the arterial and to a greater extent the venous vascular prostheses became thrombotically occluded. A similar sequence of events was found to occur with the neutrally modified collagen prostheses and the dialdehyde starch tanned vessels. In the latter case, the thrombotic events proceeded at a slower pace.

The chemical procedure carried out in order to cause an increase in the-net positive surface charge density on the intimal surface of the vascular heterografts resulted in an acceleration of the thrombotic events. It can be noted from Table 2 that the more contact of the blood elements with the prosthetic vascular surface resulted in significant occlusion of the vessel lumen (more marked in the slower flowing venous implant). Total thrombotic occlusion occurred in the venous implant immediately and wasnoted within 15 minutes in the arterial grafts.

The negative modification reaction carried out on the collagen tubes resulted in a most favorable performance of these implants. It can be seen from Table 2 that the thrombotic events occurring on the intimal surface of the vascular prostheses were significantly prolonged. A macroscopically clean intimal surface was achieved on both the arterial and venous grafts for up to I5 minutes of blood flow. After 2 hours of contact with the flowing blood elements onlyjunctional thrombi at the stainless steel cannula-prosthesis interface was noted.

The results of the in vivo arterial and venous streaming potential measurements of modified collagen vascular prosthcsesimplantations appear in Table 3.

TABLE 3 IN VIVO STREAMING POTENTIAL MEASUREMENTS OF TABLE 3 continued IN VIVO STREAMING POTENTIAL MEASUREMENTS OF MODIFIED COLLAGEN VASCULAR PROSTHESES VASCULAR ARTERIAL VENOUS STREAMING STREAMING PROSTHESIS POTENTIAL (mv) POTENTIAL (mv) Neutral Ficin +0.3 +0.1 Digested +0.2 +0.2 +0.2 +0.l

T= +0.23 Y= +0. I 3

Unmodified 0.2 0.l Ficin Digested The polarity of the streaming potential reflects the interfacial potential between the vascular prosthesis elements. An even greater magnitude of negative streaming potential (positive interfacial potential) was noted with the arterial and venous heterografts chemically modified to increase the positive surface charge density (0.7 mv-arterial; 0.4 mv-venous).

Collagen vascular heterografts chemically modified to neutralize the electrical surface charges on the prosthetic intimal wall produced arterial and venous streaming potentials on the order of +0.23 and +0.13 mv, respectively. These collagen vascular implants chemically altered so as to increase the negative surface charge density gavc positive streaming potential measurements of greater magnitude (+0.6 mv-arterial; +0.4 mv-venous). These latter values indicate that a significant negative interfacial potential was in fact produced on the intimal surface of the vascular grafts by the chemical modification procedure.

An ideal vascular prosthesis would possess the recoil characteristics of an intact elastica plus the strength of a collagen backbone. The strength of this collagen backbone to withstand many months of repetitive pulsatilc arterial pressures and function as a prosthetic vascular hetcrograft has been documented (Rosenberg, N., Henderson, 1., Lord, G. H., and Bothwell, .l. W.: Collagen arterial prosthesis of hetcrologous vascular origin: physical properties and behavior as an arterial graft. In: Biophysical Mechanisms in Vascular Homeostasis and Intravascular Thrombosis, P. N. Sawyer, Ed. Appleton-Century-Crofts, New York 1965, pp. 314-321 )..Furthermore, many of the desirable features of a vascular prosthesis (Wesolowski, S. A., Fries, C. C., and Sawyer, P. N.: Some desirable physical charae teristics of prosthetic vascular grafts. In: Biophysical Mechanisms in Vascular Homeostasis and Intravascular Thrombosis, P. N. Sawyer, Ed. Appleton-Century- Crofts, New York 1965, pp. 322336) are present in ficin digested bovine carotid artery preparations. Enzyme treatment removes the parenchymal elements subject to necrosis and thus prevents the associated inflammatory reaction which impairs the integrity of the graft wall and predisposes to intimal thrombosis. It further produces a degree of porosity of the prosthetic vascular wall which favors the orderly invasion by host connective tissue and due to the relative absence of inflammatory reaction, favors early endothelialization as well.

Early thrombosis after insertion of these grafts can be inhibited by increasing the negative surface charge density on their intimal surfaces. The above results substantiate the importance of the negative intimal surface charge density in preventing early thrombotic occlusion of collagen heterograft vascular prostheses. Chemical modification designed to increase the negative surface charge density on the inner wall of ficin treated bovine arterial heterografts was found to prevent luminal occlusion by mural thrombosis significantly. Chemical modification by a earbodiimide-promoted amide formation reaction designed to increase the positive surface charge density on the intimal surface was found to greatly accelerate the thrombotic events (Table 2).

The polarity of the arterial and venous streaming potentials measured through the lumens of these vascular prostheses served to check the chemical modification procedures and assure that the electrical alteration of surface charge density occurred with the predicted polarity. It can be seen from Table 3 that the arterial and venous streaming potentials measured through the lumens of those grafts modified to increase the intimal surface electronegativity were uniformly positive in polarity, while those grafts designed to present a positively charged surface to the flowing blood elements produced streaming potentials with a negative polarity. Thus the chemical modification procedures were effective in modulating the polarity of the interfacial potential between the luminal surface of the vascular prosthesis and the blood elements flowing within.

Ficin digested bovine carotid artery vascular heterografts were also implanted into the vascular system of mongrel dogs in their unmodified state and in a chemically altered condition designed to neutralize the electrical surface charges on the graft. It can be seen from Table 2 that both of these implants were inferior in their performance when compared with the negatively modified surface, but superior to the more positively charged graft.

The streaming potential measurements obtained from the unmodified ficin digested collagen grafts indicate that their interfacial polarity is slightly positive while that of the neutrally modified implants is slightly negative, (Table 3). It can be seen from these results that the'chemical procedure designed to neutralize the slightly positive surface charge on the ficin digested surfaces (unmodified) actually overshot electrical neutrality and produced a surface with a slight excess negative charge. Even though the excess charges on the surfaces of these two vascular prostheses were opposite in polarity, their funtioning as vascular grafting material as judged macroscopically was comparable. This apparent lack of difference in performance between the two can probably be accounted for on the basis of their relatively small surface charge density (as compared with the positively and negatively modified vascular prostheses see Table 3).

A further type of ficin digested bovine vascular heterograft was also evaluated. This dialdehyde starch tanned prosthesis has previously been reported to perform well in long term (3 years) studies (Bothwell, J. W., Lord, G. H., Rosenberg, N., Burrowes, C. B., Wesolowski, S. A. and Sawyer, P. N.: Modified arterial heterografts: relationship of processing techniques to interface characteristics. In: Biophysical Mechanisms in Vascular Homeostasis and Intravascular Thrombosis, P. N. Sawyer, Ed. Appleton-Century-Crofts, New York, 1965 pp. 306-313). It can be seen from Table 2 that this grafting material was markedly inferior to the negatively modified collagen prostheses but comparable to the unmodified and neutrally altered collagens. The streaming potential measurements obtained from these implants were quite ambiguous. The arterial streaming potentials were uniformly positive in polarity, indicating that the prosthesis presents a slightly negative surface to the flowing blood. The venous streaming potentials, however, were not consistent, two of the three measurements indicating that the graft actually presents a slightly positive surface to the bloodstream.

The critical role of platelets in intravascular thrombosis has been well documented in the following:

Mitchell, J. R. A.: Chapter XVI Platelets and Thrombosis, Sci. Basis Med. Ann. Rev. 266288 (1968);

Hampton, J. R.: The study of platelet behavior and its relation to thrombosis. J. Atheroscler. Res. 7:729 (1967);

Mustard, J. F., Packham, M. A. Rowsell, H. C., and Jorgensen, L.: The role of platelets in thrombosis and aterosclerosis. Thromb. Diath. Haemorrh. Suppl. 231261 (1967).

It is believed by some that the initial event leading to the formation of an intravascular mural thrombus is the unmasking of subintimal collagen and its subsequent recognition by circulating platelets with the latters resulting adhesion and aggregation (this view is not universally accepted). It is known, however, that collagen is capable of initiating platelet adhesion to itself and that this adhesion can result in platelet aggregation. The precise biochemical mechanism by which platelets recognize collagen and subsequently adhere to it has been shown to involve the formation of a complex between incomplete carbohydrate side chains in collagen and glueosyltransferase present on the outer surface of platelets (see FIG. 1). The reaction involves the enzymatic coupling of glucose (supplied by the platelets as uridinediphosphoglucose) to galactosyl residues attached to hydroxylysine side chains incorporated into the collagen peptides.

The reaction employed to increase the net negative surface charge density on the intimal surface of the collagen vascular prostheses was a succinylation reaction designed to cover the free amino groups of the protein. Succinylation'of solubilized collagen has been demonstrated to result in an approximately 95% con version of epsilon amino groups to free carboxyl groups (Gustavson, K. H.: Akiv. for Kemi 17:541 (1961)). This reaction was observed to result in the production of a vascular prosthesis which when implanted into the vascular system of mongrel dogs resulted in the least amount of platelet deposition and subsequent throm botic occlusion. It can be seen from the above biochemical data that this succinylation reaction which covered the epsilon amino groups of the protein sufficiently altered the substrate of platelet glucosyltransferase such that the specificity of this enzyme no longer recognized the heterograft collagen as such. Without platelet recognition there could be no adhesion to the prosthetic intimal surface and thus no thrombotic occlusion.

Furthermore, it has been shown that blocking the free carboxyl groups of collagen results in increased platelet aggregation activity in vitro. This has been postulated to result from the potentiation of the effects of the free epsilon amino groups (Wilner, G. D., Nossel, H. L., and LeRoy, E. C.: Aggregation of platelets by collagen. J. Clin. Invest. 4712616 (1968)). The results obtained in this study with the reaction designed to increase the net positive surface charge density on the intimal surface of the collagen vascular prosthesis by amidation of the free carboxyl groups is entirely consistent with these in vitro studies. The positive modification reaction resulted in the rapid and total thrombotic occlusion of these vascular heterografts when implanted into the vascular system of mongrel dogs.

A negative intimal surface charge density results in a favorable vascular heterograft performance by preventing early thrombotic occlusion of the prosthesis lumen. A simple chemical modification procedure is given by which the intimal surface of ficin digested bovine carotid arteries can be prepared with this added electronegativity.

In addition to the above, the invention provides a new kind of prosthesis consisting of a ficin digested artery modified with anionic dialdehyde starch. This prosthesis will be tanned and will have had negative charges incorporated into it in one step. Thus the resulting product will be strengthened as by dialdehydestarch tanning and will have an excess of negative charge so as to make a better non-thrombogenic surface. The dialdehyde-starch derivative needed is the 6-carboxy-methyl derivative l (i- CH COO This material is either available or can be made. It is available as a product called Water Soluble Anionic Polymeric Dialdehyde" known as DASOL A available from Miles Laboratories, Inc, which is of interest as a tanner and suitable charge carrier.

As a dification of an existing prosthesis to introduce negative charge, a ficin digested dialdehyde starch modified artery can be further modified with succinic anhydride to introduce negative charges. The reaction of dialdehyde starch may occur mainly with the 6- amino groups oflysine under conditions of tanning (pH 8.8). Some reaction occurs with the guanidino groups of arginine as it is known that this group reacts with neighboring dicarboxyl groups which is one way of looking at dealdehyde-starch. Be that as it may, there may be sites which are still available for attack by suecinic anhydride. This will result in a tanned, negatively charged prosthesis.

Further, there is the exhaustive decationization of a succinic anhydride modified prosthesis. Succinic anhydride reacts mainly with the e-amino groups of lysine introducing a negatively charged carboxy propeonoyl moeity. Assuming all the lysine groups are blocked, positive charge sites exist on the arginine residues and on the histidine residues (some of the imidazole groups of histidine may have the positive charge removed at pH 7.4). Modification of the arginine residues can be effected by phenyl glyoxal which reacts under mild conditions with the positively charged guanidinum group and results in a neutral derivative. Histidine can be converted to a neutral derivative by reaction with diethyl pyrocarbonate to given an ethoxyformyl derivative on the imidazole ring.

The above techniques involve the negatively charged tanning of collagen for protection against intravascular thrombosis. It is appropriate to apply these techniques to other areas in the body when collagen prostheses and, in fact, heterograft materials are used which are taken from various species of animals and used in humans. The most significant of these prosthetic devices are homograph valves taken from one human and placed in another human and heterograft valves which conventionally are taken from pigs and inserted into the aortic valve area. These valves are known to have certain advantages in that their leaflets permit central flow. The basic problem with various aspects of their application has always been that, while they work satisfactorily in the aortic position, there has always been some question about their utility in the mitral valve area. The negatively charged tanning of these valves enhances their utility.

By way of further embodiment of the invention, a heterograft valve is removed under semi-sterile conditions from the porcine heart. lt is tanned using the negatively charged tanning techniques described above. The tanning procedure is effected using either succinic anhydride or dasol to produce a highly negatively charged collagen surface on the valve which makes the prosthesis more anticoagulent in character than it would be under conventional circumstances. The charge characteristic provides not only additional antithrombogenesis but also increases the life span of the implanted heterograft valve because of its resistance to fibrin deposition and destruction. The same also applies to homograph valves.

There will now be obvious to those skilled in the art many modifications and variations based on the above. These modifications and variations will not depart from the scope of the invention as defined by the following claims.

What is claimed is:

l. A method of improving the performance of a graft prosthesis comprising making the prosthesis of collagen 17 and increasing the negative surface charge of the intimal surface thereof by a succinylation reaction.

2. A method as claimed in claim 1 wherein the collagen is prepared from ficin digested bovine carotid artery material.

3. A method as claimed in claim 1 wherein the prosthesis is formed as a vascular prosthesis.

4. A method as claimed in claim 1 wherein the prosthesis is formed as a valve.

5. A prosthesis made as claimed in claim 1.

6. A method of improving the performance of a graft prosthesis comprising making the prosthesis of collagen, the prosthesis including protein with free amino groups, and increasing the net negative surface charge of the intimal surface thereof by covering the free amino group.

7. A method of improving the performance of a graft prosthesis comprising making the prosthesis of collagen and increasing the negative surface charge of the intimal surface thereof by the following chemical reaction Protein-NR "O 8. A method of improving the performance of a graft prosthesis comprising making the prosthesis of collagen and increasing the negative surface charge of the intimal surface thereof, said collagen being dialdehyde starch tanned collagen which is treated with succinic anhydride.

9. A method as claimed in claim 8 comprising further modifying said surface with phenylglyoxal.

10. A method as claimed in claim 8 comprising further modifying said surface with diethyl pyrocarbonate.

11. A method of improving the performance of a graft prosthesis comprising making the prosthesis of collagen, said graft being in the form of a collagen tube, comprising closing off an end of said tube, inserting said end into a fluid and inserting a liquid chemical succinylation reactant into the lumen of the tube to in crease the negative surface charge of the intimal surface thereof.

12. A method as claimed in claim 11 wherein the chemical reactant is succinic anhydride in a basic solunon.

13. A method as claimed in claim 12 wherein a NaH- CO buffer solution is inserted into the lumen in seu 7 rroeein-nu-c-cu cn -c-o' quential additions of approximately 10 ml. aliquots to which about 0.1 gm. of crystals of succinic anhydride were respectively added.

Claims (13)

1. A method of improving the performance of a graft prosthesis comprising making the prosthesis of collagen and increasing the negative surface charge of the intimal surface thereof by a succinylation reaction.
2. A method as claimed in claim 1 wherein the collagen is prepared from ficin digested bovine carotid artery material.
3. A method as claimed in claim 1 wherein the prosthesis is formed as a vascular prosthesis.
4. A method as claimed in claim 1 wherein the prosthesis is formed as a valve.
5. A prosthesis made as claimed in claim 1.
6. A method of improving the performance of a graft prosthesis comprising making the prosthesis of collagen, the prosthesis including protein with free amino groups, and increasing the net negative surface charge of the intimal surface thereof by covering the free amino group.
7. A method of improving the performance of a graft prosthesis comprising making the prosthesis of collagen and increasing the negative surface charge of the intimal surface thereof by thE following chemical reaction
8. A method of improving the performance of a graft prosthesis comprising making the prosthesis of collagen and increasing the negative surface charge of the intimal surface thereof, said collagen being dialdehyde starch tanned collagen which is treated with succinic anhydride.
9. A method as claimed in claim 8 comprising further modifying said surface with phenylglyoxal.
10. A method as claimed in claim 8 comprising further modifying said surface with diethyl pyrocarbonate.
11. A method of improving the performance of a graft prosthesis comprising making the prosthesis of collagen, said graft being in the form of a collagen tube, comprising closing off an end of said tube, inserting said end into a fluid and inserting a liquid chemical succinylation reactant into the lumen of the tube to increase the negative surface charge of the intimal surface thereof.
12. A method as claimed in claim 11 wherein the chemical reactant is succinic anhydride in a basic solution.
13. A method as claimed in claim 12 wherein a NaHCO3 buffer solution is inserted into the lumen in sequential additions of approximately 10 ml. aliquots to which about 0.1 gm. of crystals of succinic anhydride were respectively added.
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Cited By (40)

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DE2720544A1 (en) * 1976-05-10 1977-12-08 Philip Nicholas Sawyer A method for controlling the thrombogenicity of an implant prosthesis, and the product thereby obtained
US4098571A (en) * 1975-09-02 1978-07-04 Kaneyasu Miyata Substitute blood vessel and a process for preparing the same
EP0000949A1 (en) * 1977-08-26 1979-03-07 Philip Nicholas Sawyer Cardiac and vascular prostheses and methods of making the same
EP0002931A1 (en) * 1977-12-21 1979-07-11 David Goldfarb Composition for use in making prosthetic vascular devices, and prosthetic devices made therefrom
WO1983000049A1 (en) * 1981-06-22 1983-01-06 American Hospital Supply Corp Low-pressure fixation of valvular tissue intended for implantation
EP0124659A1 (en) * 1983-04-13 1984-11-14 Koken Co. Ltd. Medical material
US4597762A (en) * 1980-11-13 1986-07-01 Heyl Chemisch-Pharmazeutische Fabrik Gmbh & Co Kg Collagen preparation
US4664658A (en) * 1984-11-08 1987-05-12 Mitsubishi Monsanto Chemical Company Medical material and process for its production
US4695281A (en) * 1983-03-25 1987-09-22 Koken Co., Ltd. Medical material
US4795458A (en) * 1987-07-02 1989-01-03 Regan Barrie F Stent for use following balloon angioplasty
US4814120A (en) * 1984-02-21 1989-03-21 Bioetica S.A. Process for the preparation of collagen tubes
US4979955A (en) * 1988-06-06 1990-12-25 Smith Robert M Power assisted prosthetic heart valve
WO1992014419A1 (en) * 1991-02-14 1992-09-03 Baxter International Inc. Pliable biological graft materials and their methods of manufacture
US5558875A (en) * 1994-06-06 1996-09-24 Wang; Su Method of preparing collagenous tissue
US5762600A (en) * 1994-04-29 1998-06-09 W. L. Gore & Associates, Inc. Blood contact surfaces employing natural subendothelial matrix and methods for making and using the same
US5824061A (en) * 1989-05-31 1998-10-20 Baxter International Inc. Vascular and venous valve implant prostheses
US5873906A (en) * 1994-09-08 1999-02-23 Gore Enterprise Holdings, Inc. Procedures for introducing stents and stent-grafts
US5876432A (en) * 1994-04-01 1999-03-02 Gore Enterprise Holdings, Inc. Self-expandable helical intravascular stent and stent-graft
US5925061A (en) * 1997-01-13 1999-07-20 Gore Enterprise Holdings, Inc. Low profile vascular stent
US6001123A (en) * 1994-04-01 1999-12-14 Gore Enterprise Holdings Inc. Folding self-expandable intravascular stent-graft
US6042605A (en) * 1995-12-14 2000-03-28 Gore Enterprose Holdings, Inc. Kink resistant stent-graft
US6210957B1 (en) 1994-07-29 2001-04-03 Edwards Lifescience Corporation Apparatuses for treating biological tissue to mitigate calcification
US6331188B1 (en) 1994-08-31 2001-12-18 Gore Enterprise Holdings, Inc. Exterior supported self-expanding stent-graft
US6352553B1 (en) 1995-12-14 2002-03-05 Gore Enterprise Holdings, Inc. Stent-graft deployment apparatus and method
US6352561B1 (en) 1996-12-23 2002-03-05 W. L. Gore & Associates Implant deployment apparatus
US20030072677A1 (en) * 2001-10-17 2003-04-17 Ralph Kafesjian Supercritical fluid extraction process for tissue preparation
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US20030226208A1 (en) * 1998-09-21 2003-12-11 Carpentier Alain F. Method for treatment of biological tissues to mitigate post-implantation calcification and thrombosis
US6866686B2 (en) 2000-01-28 2005-03-15 Cryolife, Inc. Tissue graft
US20050107872A1 (en) * 2003-11-17 2005-05-19 Mensah Eugene A. Implantable heart valve prosthetic devices having intrinsically conductive polymers
US20060217805A1 (en) * 2005-03-25 2006-09-28 Dove Jeffrey S Treatment of bioprosthetic tissues to mitigate post implantation calcification
USRE40570E1 (en) 1994-07-29 2008-11-11 Edwards Lifesciences Corporation Apparatuses and methods for treating biological tissue to mitigate calcification
WO2012177671A1 (en) * 2011-06-20 2012-12-27 D4 Brands, Llc Duty belt buckle
US8632608B2 (en) 2002-01-03 2014-01-21 Edwards Lifesciences Corporation Treatment of bioprosthetic tissues to mitigate post implantation calcification
US8846390B2 (en) 2010-03-23 2014-09-30 Edwards Lifesciences Corporation Methods of conditioning sheet bioprosthetic tissue
US8906601B2 (en) 2010-06-17 2014-12-09 Edwardss Lifesciences Corporation Methods for stabilizing a bioprosthetic tissue by chemical modification of antigenic carbohydrates
US9351829B2 (en) 2010-11-17 2016-05-31 Edwards Lifesciences Corporation Double cross-linkage process to enhance post-implantation bioprosthetic tissue durability
US9358107B2 (en) 2011-06-30 2016-06-07 Edwards Lifesciences Corporation Systems, dies, and methods for processing pericardial tissue
US9918832B2 (en) 2006-10-27 2018-03-20 Edwards Lifesciences Corporation Biological tissue for surgical implantation
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US4098571A (en) * 1975-09-02 1978-07-04 Kaneyasu Miyata Substitute blood vessel and a process for preparing the same
US4082507A (en) * 1976-05-10 1978-04-04 Sawyer Philip Nicholas Prosthesis and method for making the same
DE2720544A1 (en) * 1976-05-10 1977-12-08 Philip Nicholas Sawyer A method for controlling the thrombogenicity of an implant prosthesis, and the product thereby obtained
EP0000949A1 (en) * 1977-08-26 1979-03-07 Philip Nicholas Sawyer Cardiac and vascular prostheses and methods of making the same
US4167045A (en) * 1977-08-26 1979-09-11 Interface Biomedical Laboratories Corp. Cardiac and vascular prostheses
EP0002931A1 (en) * 1977-12-21 1979-07-11 David Goldfarb Composition for use in making prosthetic vascular devices, and prosthetic devices made therefrom
US4597762A (en) * 1980-11-13 1986-07-01 Heyl Chemisch-Pharmazeutische Fabrik Gmbh & Co Kg Collagen preparation
WO1983000049A1 (en) * 1981-06-22 1983-01-06 American Hospital Supply Corp Low-pressure fixation of valvular tissue intended for implantation
US4372743A (en) * 1981-06-22 1983-02-08 American Hospital Supply Corp. Low-pressure fixation of valvular tissue intended for implantation
US4695281A (en) * 1983-03-25 1987-09-22 Koken Co., Ltd. Medical material
EP0124659A1 (en) * 1983-04-13 1984-11-14 Koken Co. Ltd. Medical material
US4814120A (en) * 1984-02-21 1989-03-21 Bioetica S.A. Process for the preparation of collagen tubes
US4664658A (en) * 1984-11-08 1987-05-12 Mitsubishi Monsanto Chemical Company Medical material and process for its production
US4795458A (en) * 1987-07-02 1989-01-03 Regan Barrie F Stent for use following balloon angioplasty
US4979955A (en) * 1988-06-06 1990-12-25 Smith Robert M Power assisted prosthetic heart valve
US5997573A (en) * 1989-05-31 1999-12-07 Baxter International, Inc. Stent devices and support/restrictor assemblies for use in conjunction with prosthetic vascular grafts
US5824061A (en) * 1989-05-31 1998-10-20 Baxter International Inc. Vascular and venous valve implant prostheses
WO1992014419A1 (en) * 1991-02-14 1992-09-03 Baxter International Inc. Pliable biological graft materials and their methods of manufacture
US6165210A (en) * 1994-04-01 2000-12-26 Gore Enterprise Holdings, Inc. Self-expandable helical intravascular stent and stent-graft
US6017362A (en) * 1994-04-01 2000-01-25 Gore Enterprise Holdings, Inc. Folding self-expandable intravascular stent
US5876432A (en) * 1994-04-01 1999-03-02 Gore Enterprise Holdings, Inc. Self-expandable helical intravascular stent and stent-graft
US6001123A (en) * 1994-04-01 1999-12-14 Gore Enterprise Holdings Inc. Folding self-expandable intravascular stent-graft
US5776182A (en) * 1994-04-29 1998-07-07 W. L. Gore & Associates, Inc. Blood contact surfaces employing natural subendothelial matrix and method for making and using the same
US5762600A (en) * 1994-04-29 1998-06-09 W. L. Gore & Associates, Inc. Blood contact surfaces employing natural subendothelial matrix and methods for making and using the same
US5558875A (en) * 1994-06-06 1996-09-24 Wang; Su Method of preparing collagenous tissue
US6210957B1 (en) 1994-07-29 2001-04-03 Edwards Lifescience Corporation Apparatuses for treating biological tissue to mitigate calcification
USRE40570E1 (en) 1994-07-29 2008-11-11 Edwards Lifesciences Corporation Apparatuses and methods for treating biological tissue to mitigate calcification
US8623065B2 (en) 1994-08-31 2014-01-07 W. L. Gore & Associates, Inc. Exterior supported self-expanding stent-graft
US6331188B1 (en) 1994-08-31 2001-12-18 Gore Enterprise Holdings, Inc. Exterior supported self-expanding stent-graft
US6517570B1 (en) 1994-08-31 2003-02-11 Gore Enterprise Holdings, Inc. Exterior supported self-expanding stent-graft
US6015429A (en) * 1994-09-08 2000-01-18 Gore Enterprise Holdings, Inc. Procedures for introducing stents and stent-grafts
US5919225A (en) * 1994-09-08 1999-07-06 Gore Enterprise Holdings, Inc. Procedures for introducing stents and stent-grafts
US5873906A (en) * 1994-09-08 1999-02-23 Gore Enterprise Holdings, Inc. Procedures for introducing stents and stent-grafts
US6613072B2 (en) 1994-09-08 2003-09-02 Gore Enterprise Holdings, Inc. Procedures for introducing stents and stent-grafts
US6520986B2 (en) 1995-12-14 2003-02-18 Gore Enterprise Holdings, Inc. Kink resistant stent-graft
US6042605A (en) * 1995-12-14 2000-03-28 Gore Enterprose Holdings, Inc. Kink resistant stent-graft
US6352553B1 (en) 1995-12-14 2002-03-05 Gore Enterprise Holdings, Inc. Stent-graft deployment apparatus and method
US8323328B2 (en) 1995-12-14 2012-12-04 W. L. Gore & Associates, Inc. Kink resistant stent-graft
US6361637B2 (en) 1995-12-14 2002-03-26 Gore Enterprise Holdings, Inc. Method of making a kink resistant stent-graft
US7682380B2 (en) 1996-12-23 2010-03-23 Gore Enterprise Holdings, Inc. Kink-resistant bifurcated prosthesis
US6551350B1 (en) 1996-12-23 2003-04-22 Gore Enterprise Holdings, Inc. Kink resistant bifurcated prosthesis
US6352561B1 (en) 1996-12-23 2002-03-05 W. L. Gore & Associates Implant deployment apparatus
US5925061A (en) * 1997-01-13 1999-07-20 Gore Enterprise Holdings, Inc. Low profile vascular stent
US20030226208A1 (en) * 1998-09-21 2003-12-11 Carpentier Alain F. Method for treatment of biological tissues to mitigate post-implantation calcification and thrombosis
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US8236241B2 (en) 1998-09-21 2012-08-07 Edwards Lifesciences Corporation Treating biological tissues to mitigate post-implantation calcification
US7763081B2 (en) 2000-01-28 2010-07-27 Cryolife, Inc. Tissue graft
US20050191281A1 (en) * 2000-01-28 2005-09-01 Cryolife, Inc. Tissue graft
US20100285587A1 (en) * 2000-01-28 2010-11-11 Cryolife, Inc. Tissue Graft
US6866686B2 (en) 2000-01-28 2005-03-15 Cryolife, Inc. Tissue graft
US20030072677A1 (en) * 2001-10-17 2003-04-17 Ralph Kafesjian Supercritical fluid extraction process for tissue preparation
US7008591B2 (en) 2001-10-17 2006-03-07 Edwards Lifesciences Corporation Supercritical fluid extraction process for tissue preparation
US8632608B2 (en) 2002-01-03 2014-01-21 Edwards Lifesciences Corporation Treatment of bioprosthetic tissues to mitigate post implantation calcification
US7740656B2 (en) 2003-11-17 2010-06-22 Medtronic, Inc. Implantable heart valve prosthetic devices having intrinsically conductive polymers
US20050107872A1 (en) * 2003-11-17 2005-05-19 Mensah Eugene A. Implantable heart valve prosthetic devices having intrinsically conductive polymers
US7579381B2 (en) 2005-03-25 2009-08-25 Edwards Lifesciences Corporation Treatment of bioprosthetic tissues to mitigate post implantation calcification
US20060217805A1 (en) * 2005-03-25 2006-09-28 Dove Jeffrey S Treatment of bioprosthetic tissues to mitigate post implantation calcification
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US8906601B2 (en) 2010-06-17 2014-12-09 Edwardss Lifesciences Corporation Methods for stabilizing a bioprosthetic tissue by chemical modification of antigenic carbohydrates
US9351829B2 (en) 2010-11-17 2016-05-31 Edwards Lifesciences Corporation Double cross-linkage process to enhance post-implantation bioprosthetic tissue durability
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