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  1. Recherche avancée dans les brevets
Numéro de publicationUS3425418 A
Type de publicationOctroi
Date de publication4 févr. 1969
Date de dépôt15 avr. 1964
Date de priorité15 juin 1963
Autre référence de publicationDE1491218A1, DE1491218B2, DE1491218C3
Numéro de publicationUS 3425418 A, US 3425418A, US-A-3425418, US3425418 A, US3425418A
InventeursMilos Chvapil, Milan Krajicek, Miloslav Adam
Cessionnaire d'origineSpofa Vereinigte Pharma Werke
Exporter la citationBiBTeX, EndNote, RefMan
Liens externes: USPTO, Cession USPTO, Espacenet
Artificial blood vessels and method of preparing the same
US 3425418 A
Résumé  disponible en
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Revendications  disponible en
Description  (Le texte OCR peut contenir des erreurs.)

Feb. 4, 1969 M. CHVAPIL ET AL 3,425,413

ARTIFICIAL BLOOD VESSELS AND METHOD OF PREPARING THE SAME Filed April 15, 1964 United States Patent 1962, 5,644/62 U.S. Cl. 128-334 5 Claims Int. Cl. A6111 17/04; A61f l /24; A61] 17/00 ABSTRACT OF THE DISCLOSURE An artificial blood vessel includes a tanned collagen tube strong enough to be self-supporting, and impregnated with an anti-coagulant which is covered with open mesh fabric secured to the tanned collagen by an outer wall portion of collagen in the native chemical state thin enough not to close the pores in the fabric.

This application is a continuation-in-part of our copending application Ser. No. 330,221, filed on Dec. 10, 1963, and now abandoned.

This invention relates to vascular grafts, that is, to artificial blood vessels, and to a method of preparing the same.

As described in more detail in a paper published by us and on our behalf in the Journal of Surgical Research (vol. 3, No. 7, pages 358 to 368, Sept. 1963), a vascular graft should be non-toxic, flexible, and porous. It should retain its strength permanently in intimate contact with body fluids, and should be readily accepted and incorporated into the surrounding tissue. The graft or prosthesis, moreover, should not unfavorably affect the flow of blood therethrough.

In the surgical repair of blood vessels and body ducts, inert fabrics have found considerable use. The known inert fabric prostheses, however, do not become parts of the body tissues. They frequently remain surrounded by a pool of serum after the healing process is terminated. We have found that the relatively low porosity of the known prostheses accounts for the observed formation of fluid pockets, and prevents the growth of repair tissue through the fabric grafts.

The porosity of a fabric may be characterized by the volume of Water in milliliters per minute that will pass through one square centimeter of the fabric under a pressure differential of 120 millimeters mercury and this definition of porosity is being employed in this specification and the appended claims. The vascular fabric prostheses that have found use in surgery heretofore have a porosity of less than 2,000 milliliters per minute.

It has now been discovered that healing will be greatly improved and the growth of repair tissue through the fabric promoted if the porosity of the fabric is much greater, that is, in the range of 10,000 to about 22,000 milliliters per minute. A vascular graft of the invention thus includes a fabric of the desired porosity. Such a fabric is not in itself impervious to blood.

In the improved prostheses of the present invention, the porous, non-absorbable fabric framework is rendered bloodtight by a collagen film or tube bonded to one side of the fabric. The fabric is exposed to the surrounding tissue thus permitting ingrowth of fibroblasts and endothelial cells which results in the attachment of the prosthesis to the host tisues. The collagen has considera- 3,425,418 Patented Feb. 4, 1969 ble tensile strength, is non-antigenic, and is slowly absorbed at a rate which may be controlled by partial tanning so that there is no appreciable decrease in the strength of the vessel structure while the collagen is being replaced by new body tissue.

It has further been found that clotting of blood in vascular grafts of even very small internal diameter (three millimeters and less) can be prevented if the interior collagen surface of a vascular prosthesis of the invention contains an anti-coagulant such as heparin. The anticoagulant properties of natural blood vessels are ascribed to the presence of mucopolysaccharides, particularly chondroitin sulfate B and heparitin sulfate. We may therefore add these or other anticoagulants to the collagen structure as a whole, or we incorporate an anticoagulant only in the inner wall portion of the collagen tube to decrease the thrombotic effects of the graft. We have found that heparin is quickly adsorbed from aqueous solutions by a partly tanned collagen wall, and cannot readily be removed from the wall under ordinary physiological conditions. A collagen wall containing heparin has permanent anticoagulant properties.

While the present invention is not limited to any particular theory of action, it is believed that heparin and other anticoagulants are reversibly bound to the collagen through polar groups present in the anticoagulants and in the collagen, and that the anticoagulant is slowly released into the bloodstream over a period of days as the collagen is absorbed by the body. Thus, the probability of clotting is sharply reduced during the first few days after the implantation of the graft when the patient is most susceptible to this danger, and an open lumen is maintained during the deposition and organization of the fibrin lining surrounding the graft.

Added mucopolysaccharides also increase the hydropliilic properties of the collagen, and they improve the physicochemical stability of the collagen by the presumed link between the mucopolysaccharides and the collagen molecules. The hydrophilic properties of the absorbable tube are also greatly enhanced by the admixture of glycerin which ensures elasticity of the tube even after tanning.

The artificial blood vessels of the inveniton may be sterilized by radiation or by chemical means in a known manner. They may be stored over extended periods without loss of their desirable properties. Small amounts of antibiotics added to the collagen during the preparation of the vessel and contained in the adsorbable walls thereof further ensure safe storage and have the expected beneficial results after implantation.

An outer wall portion of the collagen layer adjacent the fabric layer is preferably kept untanned, that is, in the native chemical state and amorphous. The untanned outer wall portion is adhered to the fabric layer, but does not obstruct access from the outside to the pores of the fabric.

Fabrics well suited for the vascular grafts of the invention include those made from polyester fibers such as polyethylene terephthalate which are sold under the registered trademarks Dacron and Terylene. Polytetrafluoroethylene fibers, such as those 'known under the trademark Teflon also may be employed, but are less resilient and are not so conveniently fabricated as the polyester fabrics. The polytetrafluoroethylene fabrics, however, have superior healing properties and produce thinner, more compact capsules.

The non-absorbable fabric that reinforces the collagen may be prepared in tubular form by braiding, weaving, or knitting. Braided grafts lack dimensional stability and are not widely used, whereas, both woven and knitted grafts have been used clinically. Woven grafts must be tightly constructed or fraying and tfiber slippage become problems at implantation. -It is for this reason that woven grafts have comparatively low porosities. Knitting permits variations in the tightness or porosity without commensurate penalties in fray or slip qualities, and is the preferred method of construction.

Other features and many of the attendant advantages of this invention will be readily appreciated as the same becomes better understood by reference to the following detailed description when considered in connection with the accompanying drawing in which:

FIG. 1 is a perspective view of an extruded collagen tube;

FIG. 2 is a perspective view of a non-absorbable fabric tube;

FIG. 3 is a greatly enlarged view of the nonabsorbable knitted fabric that forms the reinforcing structure illustrated by FIG. 2;

FIG. 4 is a greatly enlarged view of a section of a vascular prosthesis constructed in accordance with the present invention;

FIG. 5 is a fragment of FIG. 4, enlarged; and

FIG. 6 is a view along the line 6-6 of FIG. 5.

Referring now to FIGS. 1, 2, and 4, a vascular graft may be constructed in accordance with the present invention by slipping a collagen tube inside of a fabric tube. The collagen tube is softened by soaking in water or a dilute aqueous acid solution and is then expanded against the external fabric tube. A convenient way to accomplish this is to increase the pressure of the air within the tube, and thereby force the collagen into contact with the inner wall of the fabric. In so doing the collagen is forced against the fabric and into the interstices between the non-absorbable fibers. The structure is then air-dried whereby the inner collagen tube is stabilized in the form illustrated in FIGS. 4, 5, and 6.

The non-absorbable fabrics may be knitted, crocheted, woven, or braided in the shape of the desired prosthesis, as a film, tube, Y-tube, etc. While the drawings illustrate a tubular structure suitable for use as a vascular graft, it will be understood that other shapes in which collagen is bonded to one side of a non-absorbable fabric characterized by a porosity not less than 10,000 milliliters per minute and not substantially more than 22,000 milliliters per minute offer similar advantages.

It will be understood that the collagen present in the prostheses of the present invention may be treated with tanning agents such as formaldehyde, pyrogallol, chromium, etc., by methods well known in the art to obtain increased strength, and to control the rate at which the collagen will be absorbed.

A combination fabric-collagen vascular graft may also be manufactured by constructing the tubular fabric framework of Dacron or Teflon to the desired diameter. The fabric framework is then coated on both sides with a collagen mass obtained by swelling collagen fibrils in an aqueous acid solution. The swollen collagen fibrils are then frozen in position and deswollen by dehydration in an organic solvent. Finally the collagen that lines the interior wall of the composite tube is treated with heparin.

In this type of construction, it is important that the mesh of the non-absorbable fabric be sufficiently open to permit the collagen fibrils to extend into and through the interstices of the fabric. These collagen fibrils that pass through the fabric cohere to the collagen fibrils on the other side of the fabric framework and form a unitary structure that resists delamination. It is preferred that only the interior wall of the graft be treated with heparin as the ingrowth of fibroblasts and endothelial cells appears retarded by the presence of heparin on the exterior surface of the graft.

The improved prostheses of the present invention may also be constructed by weaving, knitting, Crocheting, or braiding together an inert non-absorbable thread or yarn with collagen yarn or collagen multifilament. Again the interior surface of this tubular structure is treated with heparin.

In applying heparin t0 the interior collagen wall an aqueous solution containing from 0.25% to 1% heparin may be used. The contact time of this solution with the collagen should be sufiicient to permit the heparin to penetrate about 70% of the distance through the wall of the tube. For the reasons indicated above it is preferred that there be no heparin on the exterior wall of the tube.

The present invention is more fully described and exemplified in the following examples. It is to be understood, however, that our invention is not to be limited to any specific form of materials or conditions set forth in the examples, but is limited solely by the appended claims. Throughout the examples which follow, all quantities are expressed in parts by weight.

Example I A rigid, self-supporting collagen tube having an internal diameter of about 10 millimeters and a wall thickness of about 1 millimeter was extruded by the procedure described in the Becker Patent No. 2,246,236, using a plastic collagen mass containing about 30% collagen by weight. The extruding mechanism was that described in the Becker Patent No. 2,115,607 and resulted in orientation of the collagen fibers to give excellent strength characteristics.

The tube so obtained was placed within a woven Dacron tube having a porosity of 22,000 milliliters per minute and the assembly was immersed in water until the collagen became plastic. One end of the prosthesis was then closed and sufiicient air pressure was applied to the other end of the prosthesis to force the collagen against the inner wall of the fabric. The fabric-collagen tube was then airdried in an oven at 45 C. overnight without damage. The product so obtained is illustrated in FIGS. 4, 5, and 6.

One end of the collagen-Dacron prosthesis was again closed and the tube was filled with an aqueous solution containing 1.0% of heparin. The heparin used, standardized by the sheep plasma coagulation method, was found to contain 100 units of anticoagulant activity per milligram of dry material. After the heparin solution had penetrated about three-fourths of the distance through the wall of the collagen tube, the prosthesis was emptied of the heparin solution and air-dried overnight.

The collagen-Dacron prosthesis was next tanned by immersing it for 30 seconds in a solution of 0.4 part of pyrogallol, 0.1 part .tetrasodium ethylenediamine tetraacetic acid, and 99.5 parts of water adjusted to pH 8.3 with ammonium hydroxide. It was then re-dried in an oven at 50 C. for 6 hours.

The prosthesis was next immersed for 30 seconds in a solution of chromium (III) sulfate comprising 0.8 part of chromium as chromic oxide, 0.5 part of lactic acid 0.24 part of formaldehyde, and 98.46 parts of water, adjusted to pH 2.7 with sodium hydroxide. The prosthesis was again dried in an oven at 50 C. overnight. The finished prosthesis was sterilized by irradiation.

Example II Fresh steer hides were washed with cold water at 13 C. or less in a rotating drum for 10 to 24 hours. After washing, the hides were defleshed with a scraping machine, and the hair and epidermis were cut off with a horizontal band knife. This preliminary cleaning was accomplished with standard tannery equipment.

The remaining hair and poorly cleaned sections were cut off by hand and compositions were prepared from five hides. The hide composites were then cut into /2 to 4 square inch sections and reduced to pulp by three passes through a meat grinder, each pass being a finer grind. The first and second passes were through 18 and 8 millimeter holes, respectively. The final grind was through holes 1.5 millimeters in diameter. Special care was taken during the grinding process to keep the pulp below C. This was done by adding crushed ice to the hide sections as they were fed to the grinder.

The ground pulp was next diluted with tap waterat 16 C. to give a smooth slurry containing dry solids. To this slurry was then added lactic acid, and the mixture was kneaded to form a homogeneous mass of swollen collagen fibers. The mixture so obtained contained about 25% by weight hide solids.

.The collagen mass was extruded as described in Example I to form a collagen tube having a diameter of about 8 millimeters and a wall thickness of about 0.4 millimeter.

This extruded tube was placed within a Teflon fabric tube of the type illustrated in FIG. 2, characterized by a porosity of 10,000 milliliters, and expanded against the interior wall of the fabric as described in Example I.

The vascular prosthesis so formed was tanned by immersing it in an aqueous solution containing 2% trimethylolmelamine (Solarpret), and dried in an oven at 45 C. overnight. It was further treated with heparin as in Example 1.

Example III The deep flexor tendon of cattle was cleaned of fat, superficial non-collagenous protein and other extraneous. matter and was sliced on an electric meat-slicing rna'chine (rotary knife) in the frozen condition. The tendon sections were sliced perpendicularly to their longitudinal axis to a thickness of about 11 mils. An aliquot sample of the tendon slices Was analyzed; the dry solids amounted to 36.97%.

The sliced tendon was next treated with an enzyme solution to dissolve elastin. This enzyme solution was prepared by dissolving 0.15 part of ficin and 3.75 parts of ethylene diamine tetrasodium tetraacetate in 750 parts of water. Seventy-five parts of the sliced tendon was immersed in this solution which was stored at room temperature overnight. Then 2.25 parts of hydrogen peroxide were added to destroy any residual ficin.

To this mixture of tendon slices in about 750 parts of water were added an additional 2244 parts of water and 5.87 parts of cyanoacetic acid. The swelling solution was cooled to below 25 C. This mixture was stirred in a dis.- persion kettle at about 60 rpm. The remaining steps in the process were carried out at a temperature below about 25 C. and the temperature of the collagen dispersion was not allowed to exceed this temperature.

Stirring was continued for about 3 hours, during which time the individual collagen slices were swollen. The dispersion was homogenized by repeated passes through series-connected jets having orifices of 50 mils and mils respectively. The dispersion was then forced through a leaf filter containing three screens of #316 stainless steel. These screens were separated by A;-inch spacers and decreased in mesh size so that the dispersion first passed a l44mil screen, then a 9-mil screen, and finally a 4-mil screen. The dispersion of swollen solvated collagen fibrils so obtained analyzed 1.09% solids and had a pH of 2.52.

A glass tube having an inside diameter of about A- inch was fitted with a one-hole stopper of rubber through which a i -inch :glas rod was placed so that the glass rod extended coaxially within the glass tube. Before placing the glass rod and rubber stopper in position, the glass rod was covered with a piece of rubber tubing, and a cylindrical tube of open-mesh woven Dacron about inch in diameter was slipped over the glass rod and rubber tube. The glass tube and glass rod were assembled in an upright position with the bottom of the Dacron fabric tube resting on the rubber stopper. The dispersion of swollen collagen fibrils, prepared as described above, was poured into the glass tube while maintaining the fabric tube in a coaxial position and equally spaced between the rubber tube and glass tube so that both sides of the fabric were coated with the collagen dispersion. This mold with the dispersion and fabric in place was frozen in the vertical position for at least 4 hours at -20 C.

'The mold was then placed in a static coagulation bath consisting of 2 liters of isopropanol, 30 cubic centimeters of concentrated ammonia (25 and 10 cubic centimeters of formaldehyde (37% solution) at room temperature, and the mold was maintained in the solution for 16 hours. The glass rod covered with the rubber tube and the formed collagen tube were then removed and placed in a dehydrating bath consisting of 2 liters of isoproponal. The collagen tube was left in this bath for an additional 16 hours to complete the dehydration.

After dehydration, the rubber tube with the collagen tube on it was very carefully slid from the glass rod, and the rubber tube was removed from the interior of the collagen tube by pulling on both ends of the rubber tube, thereby stretching the rubber tube and reducing its diameter. After the collagen tube was removed from the rubber tubing, it was plasticized in a bath consisting of 2 liters of isopropanol (10% water) containing 5% glycerine. This plasticizing operation is optional. After 24 hours in the plasticizing bath, the collagen tube was supported on a glass rod and air-dried.

One end of the collagen-Dacron prosthesis so obtained was closed and the tube was filled with an aqueous solution containing 0.25% heparin. When the heparin solution had penetrated three-fourths of the way through the collagen-Dacron tube, the tube was emptied and airdried.

Example IV Hide sections of beef cattle were comrn'inuted and homogenized together with a dilute solution of sodium hydroxide for 24 hours, 60 milliliters 1/100 N NaOH being added per grams of the hide material. The homogenized mass was left standing in a refrigerator for 24 hours at a temperature between 0 and 4 C. whereupon it congealed into a soft gel.

During homogenizing, there were added 0.5 percent hyaluronic acid (a mucopolysaccharide), 3 percent glycerin, and 1 gram chlorotetracyclin per 100 grams of hide material.

The gel was extruded in the manner described in Example I to form a tube of 9 millimeter external diameter and a wall thickness of 0.5 millimeter. Air was simultaneously blown into the axial cavity of the extruded tube at a pressure which was controlled between 40 and 150 mm. water column to prevent collapse of the extrudate.

The extruded tube was dried to constant temperature at ordinary room temperature (15 to 25 C.) in a gentle stream of air. A very thin layer of amorphous unmodified collagen was applied to the dry outer surface by spraying from a gun, and a loosely knit tube of smooth, noncrimped Terylene was slipped over the tube in contact with the freshly deposited collagen layer.

The fabric, of conventional weft knit construction, had a permeability to water of 18,000 ml./cm. /min. at mm. Hg. It was elastically stretchable about 15% longitudinally as well as transversely. While some of its threads were adhered to the collagen tube by the freshly deposited collagen layer, the porosity of the fabric was virtually unatfected by its engagement with the resorbable material.

The tube was filled with an aqueous 1% solution of 2,4,6-trimethoxytriazine, a commercial tanning agent commonly sold under the name Solapret. The tanning solution was removed after ten minutes, and the tube was washed out with water to remove residual unreacted tanning agent. The treatment was then repeated with aqueous 1% heparin solution which was left in contact with the inner wall of the tube for five minutes. The hepar'in penetrated about A of the collagen wall. The tube was emptied and air-dried overnight.

The completed artificial blood vessel was sealed in a glass ampoule and was sterilized by exposure over five hours to gamma radiation of 2x10 roentgen.

The method outlined above may be modified in many respects without departing from the spirit and scope of this invention. It is not necessary fully to dry the collagen tube prior to covering the same with fabric. Actually, it is possible to encase a freshly extruded wet collagen tube in a tubular fabric envelope, and to adhere the fabric to the collagenous material by expanding the tube under internal air pressure. The pressure has to be carefully matched to the mechanical strength of the collagen tube to avoid embedding the fabric material in collagen to an extent which would make the pores of the fabric unavailable or not readily available. The use of a sprayed or brushed outer coating of unmodified collagen may be dispensed with in such a case, but it may also be omitted where a fabric layer is applied to dried collagen, and high mechanical strength of the vascular graft is not required.

The composition of the collagen tube may be varied as to the minor admixtures. Hyaluronie acid thus may be replaced by other mucopolysaccharides or mixtures thereof, such as those derived in a conventional manner from the corpus vitreum or cartilage of beef cattle. The mucopolysaccharides have distinctly noticeable effects on the stability of the gel when present in amounts of as little as 0.5 percent. We have not observed further desirable changes when more than 3 percent of the mucopolysaccharides were added to those naturally present in the collagen material after processing.

Glycerin is beneficial in amounts of at least 0.5 percent, and may be increased to five percent with corresponding improvement of elasticity and plasticity of the collagenous material, even when partially tanned.

The effects and dosages of antibiotics are well known from the literature on the use of implants of a similar nature. Merely by Way of example, it may be stated that suitable antibiotics include chlortetracycline in amounts of 1 to 5 grams per 100 grams of the collagen mass. 0.5 to 5 grams neomycin, or 10,000 to 50,000 units bacitracin. The quantitative limits indicated are not critical nor is this list complete.

While it is critically important that the resorption and swelling rates of the collagen be reduced by hardening, the hardening reagent and the hardening method may be freely chosen from the tanners art. Synthetic tanning agents are preferred because of the very close reproducibility of their results, but we have successfully employed natural tanning extracts of Chinese gallnu'ts, oak, pine, quebracho, sumach, mimosa, and valonia.

Many other modifications and variations of the present invention are possible in the light of the above teachings. It is therefore to be understood that, within the scope of the appended claims, the invention may be practiced otherwise than as specifically described.

This application is a continuation-in-part of our copending application Ser. No. 330,221 filed on Dec. 10, 1963.

We claim:

1. An artificial blood vessel of tubular laminar structure comprising, in combination:

(a) an exposed outer tubular layer of a physiologically inert fabric resistant to resorption by body fluids,

(1) said outer layer having a permeability to water of not less than 10,000 milliliters per square centimeter per minute at a pressure differential of millimeters mercury column; and

(b) a tubular composite layer essentially consisting of two laminae of collagen,

(1) one of said laminae of collagen being tanned and constituting an inner and self-supporting Wall of said vessel,

(2) said inner wall containing an amount of an anti-coagulant effective to prevent coagulation of blood in contact with said inner wall, and

(3) the other of said collagen laminae being essentially in the native chemical state and being bonded to said outer layer, said outer layer and said other lamina constituting an outer wall of said vessel.

2. A vessel as set forth in claim 1, wherein said other lamina of collagen is of a thickness sufiicient to adhere said fabric to said inner wall Without closing the pores of the fabric.

3. A vessel as set forth in claim 1, wherein said anticoagulant includes a mucopolysaccharide admixed to said collagen.

4. A vessel as set forth in claim 1, wherein said inner Wall further includes glycerin admixed to said collagen.

5. A vessel as set forth in claim 1, wherein said inner Wall further includes an antibiotic admixed to said collagen.

References Cited UNITED STATES PATENTS 3,106,483 10/1963 Kline et al 1l762.2 3,108,357 10/1963 Liebig 128-334 X 3,272,204- 10/1966 Artandi et al 128334 FOREIGN PATENTS 591,509 8/1947 Great Britain.

DALTON L. TRULUCK, Primal Examiner.

US. Cl. X.R.

Citations de brevets
Brevet cité Date de dépôt Date de publication Déposant Titre
US3106483 *27 juil. 19618 oct. 1963Us Catheter & Instr CorpSynthetic blood vessel grafts
US3108357 *20 juin 196229 oct. 1963William J LiebigCompound absorbable prosthetic implants, fabrics and yarns therefor
US3272204 *22 sept. 196513 sept. 1966Ethicon IncAbsorbable collagen prosthetic implant with non-absorbable reinforcing strands
GB591509A * Titre non disponible
Référencé par
Brevet citant Date de dépôt Date de publication Déposant Titre
US3526005 *29 juin 19671 sept. 1970Gulf General Atomic IncMethod of preparing an intravascular defect by implanting a pyrolytic carbon coated prosthesis
US3688317 *25 août 19705 sept. 1972Sutures IncVascular prosthetic
US3710400 *30 août 197116 janv. 1973C SparksGraft member grown in a living body
US3710777 *23 déc. 197016 janv. 1973C SparksMethod and apparatus for growing graft tubes in place
US3908657 *15 janv. 197330 sept. 1975Univ Johns HopkinsSystem for continuous withdrawal of blood
US3974526 *23 janv. 197517 août 1976Dardik Irving IVascular prostheses and process for producing the same
US4008717 *5 mars 197622 févr. 1977The Johns Hopkins UniversitySystem for continuous withdrawal and analysis of blood
US4229838 *3 juil. 197828 oct. 1980Sumitomo Electric Industries, Ltd.Vascular prosthesis having a composite structure
US4319363 *23 mai 197916 mars 1982Vettivetpillai KetharanathanVascular prostheses
US4321711 *12 oct. 197930 mars 1982Sumitomo Electric Industries, Ltd.Vascular prosthesis
US4416028 *4 juin 198022 nov. 1983Ingvar ErikssonBlood vessel prosthesis
US4442133 *22 févr. 198210 avr. 1984Greco Ralph SAntibiotic bonding of vascular prostheses and other implants
US4539716 *8 mai 198110 sept. 1985Massachusetts Institute Of TechnologyFabrication of living blood vessels and glandular tissues
US4546500 *26 févr. 198215 oct. 1985Massachusetts Institute Of TechnologyFabrication of living blood vessels and glandular tissues
US4629458 *26 févr. 198516 déc. 1986Cordis CorporationReinforcing structure for cardiovascular graft
US4670286 *26 déc. 19852 juin 1987Allied CorporationMethod of forming prosthetic devices
US4695281 *25 mars 198322 sept. 1987Koken Co., Ltd.Medical material
US4743251 *5 mars 198510 mai 1988Henry BocqueeVein prothesis and method for producing same
US4744792 *22 janv. 198517 mai 1988Richards Medical CompanyMiddle ear ventilating tube
US4822361 *24 déc. 198618 avr. 1989Sumitomo Electric Industries, Ltd.Tubular prosthesis having a composite structure
US4834746 *17 mars 198630 mai 1989Kanegafuchi Kagaku Kogyo Kabushiki KaishaArtificial vessel and process for preparing the same
US4842575 *5 août 198827 juin 1989Meadox Medicals, Inc.Method for forming impregnated synthetic vascular grafts
US4915893 *15 juil. 198310 avr. 1990Medtronic, Inc.Method of preparing polyester filament material
US4927410 *18 nov. 198822 mai 1990University Of South FloridaMethod for fabricating prosthesis material
US4997440 *10 août 19905 mars 1991American Cyanamid CompanyVascular graft with absorbable and nonabsorbable components
US5037377 *21 août 19866 août 1991Medtronic, Inc.Means for improving biocompatibility of implants, particularly of vascular grafts
US5108424 *28 janv. 199128 avr. 1992Meadox Medicals, Inc.Collagen-impregnated dacron graft
US5110852 *27 oct. 19885 mai 1992Rijksuniversiteit Te GroningenFilament material polylactide mixtures
US5192311 *13 août 19909 mars 1993Angeion CorporationMedical implant and method of making
US5197977 *30 avr. 199230 mars 1993Meadox Medicals, Inc.Drug delivery collagen-impregnated synthetic vascular graft
US5256418 *6 avr. 199026 oct. 1993Organogenesis, Inc.Collagen constructs
US5413597 *15 avr. 19939 mai 1995Krajicek; MilanThree-layer vascular prostheses
US5480423 *20 mai 19932 janv. 1996Boston Scientific CorporationProsthesis delivery
US5716660 *31 mai 199510 févr. 1998Meadox Medicals, Inc.Tubular polytetrafluoroethylene implantable prostheses
US5800519 *4 nov. 19961 sept. 1998Kopin CorporationTubular medical prosthesis for use in a body lumen
US5824058 *21 juil. 199720 oct. 1998Boston Scientific CorporationProsthesis delivery
US5851230 *18 oct. 199622 déc. 1998Meadox Medicals, Inc.Vascular graft with a heparin-containing collagen sealant
US5928279 *3 juil. 199627 juil. 1999Baxter International Inc.Stented, radially expandable, tubular PTFE grafts
US5986168 *12 sept. 199716 nov. 1999Nicem, Ltd.Prosthesis containing bioabsorbable materials insolubilized without chemical reagents and method of making the same
US6013099 *29 avr. 199811 janv. 2000Medtronic, Inc.Medical device for delivering a water-insoluble therapeutic salt or substance
US6106454 *17 juin 199722 août 2000Medtronic, Inc.Medical device for delivering localized radiation
US6162247 *21 déc. 199819 déc. 2000Meadox Medicals, Inc.Vascular graft impregnated with a heparin-containing collagen sealant
US617760910 mars 199723 janv. 2001Meadox Medicals, Inc.Self-aggregating protein compositions and use as sealants
US620353617 juin 199720 mars 2001Medtronic, Inc.Medical device for delivering a therapeutic substance and method therefor
US625113220 oct. 199826 juin 2001Boston Scientific CorporationProsthesis delivery
US629963915 avr. 19999 oct. 2001Meadox Medicals, Inc.Self-aggregating protein compositions and use as sealants
US639105229 oct. 199721 mai 2002Scimed Life Systems, Inc.Stent with collagen
US639914412 févr. 20014 juin 2002Medtronic Inc.Medical device for delivering a therapeutic substance and method therefor
US641969426 août 199816 juil. 2002Scimed Life Systems, Inc.Medical prosthesis
US643613524 oct. 197420 août 2002David GoldfarbProsthetic vascular graft
US665621229 déc. 20002 déc. 2003Scimed Life Systems, Inc.Prosthesis delivery
US673012026 janv. 20014 mai 2004Medtronic, Inc.Medical device for delivering a therapeutic substance and method therefor
US678692016 oct. 20017 sept. 2004Edwards Lifesciences CorporationRadially expandable stented tubular PTFE grafts
US699794920 mai 200214 févr. 2006Medtronic, Inc.Medical device for delivering a therapeutic agent and method of preparation
US711229317 déc. 200126 sept. 2006Nicast Ltd.Method and apparatus for manufacturing polymer fiber shells via electrospinning
US711522017 déc. 20013 oct. 2006Nicast Ltd.Vascular prosthesis and method for production thereof
US72413098 juin 200110 juil. 2007Scimed Life Systems, Inc.Self-aggregating protein compositions and use as sealants
US724411619 mars 200217 juil. 2007Nicast Ltd.Apparatus for improving mechanical characteristics of nonwoven materials
US724427214 févr. 200517 juil. 2007Nicast Ltd.Vascular prosthesis and method for production thereof
US727627119 mars 20022 oct. 2007Nicast Ltd.Polymer fiber tubular structure having kinking resistance
US741969630 nov. 20052 sept. 2008Medtronic, Inc.Medical devices for delivering a therapeutic agent and method of preparation
US758531927 sept. 20048 sept. 2009Maquet Cardiovascular, LlcSelf-aggregating protein compositions and use as sealants
US779421919 mars 200214 sept. 2010Nicast Ltd.Portable electrospinning device
US779449022 juin 200414 sept. 2010Boston Scientific Scimed, Inc.Implantable medical devices with antimicrobial and biodegradable matrices
US781131730 oct. 200712 oct. 2010Medtronic, Inc.Medical devices for delivering a therapeutic agent and method of preparation
US802956329 nov. 20044 oct. 2011Gore Enterprise Holdings, Inc.Implantable devices with reduced needle puncture site leakage
US819248127 août 20105 juin 2012Boston Scientific Scimed, Inc.Implantable medical devices with anti-microbial and biodegradable matrices
US890608730 sept. 20119 déc. 2014W. L. Gore & Associates, Inc.Method of making implantable devices with reduced needle puncture site leakage
US20040030377 *17 déc. 200112 févr. 2004Alexander DubsonMedicated polymer-coated stent assembly
US20040054406 *17 déc. 200118 mars 2004Alexander DubsonVascular prosthesis and method for production thereof
US20040094873 *19 mars 200220 mai 2004Alexander DubsonPortable electrospinning device
US20040096532 *19 mars 200220 mai 2004Alexander DubsonPolymer fiber tubular structure having kinking resistance
US20040096533 *19 mars 200220 mai 2004Alexander DubsonMethod and apparatus of improving mechanical characteristics of nonwoven materials
US20040111150 *5 déc. 200310 juin 2004Medtronic Vascular, Inc.Medical device for delivering a therapeutic substance and method therefor
US20050085901 *27 sept. 200421 avr. 2005Dan CastroSelf-aggregating protein compostions and use as sealants
US20050283224 *22 juin 200422 déc. 2005Scimed Life Systems, Inc.Implantable medical devices with antimicrobial and biodegradable matrices
US20060085064 *30 nov. 200520 avr. 2006Medtronic, Inc.Medical devices for delivering a therapeutic agent and method of preparation
US20060118236 *29 nov. 20048 juin 2006House Wayne DImplantable devices with reduced needle puncture site leakage
US20070031607 *6 avr. 20068 févr. 2007Alexander DubsonMethod and apparatus for coating medical implants
US20080200975 *4 janv. 200521 août 2008Nicast Ltd.Vascular Prosthesis with Anastomotic Member
US20080275544 *30 oct. 20076 nov. 2008Medtronic, Inc.Medical devices for delivering a therapeutic agent and method of preparation
US20100324667 *27 août 201023 déc. 2010Boston Scientific Scimed, Inc.Implantable medical devices with anti-microbial and biodegradable matrices
US20100331947 *16 févr. 200630 déc. 2010Alon ShalevInflatable Medical Device
CN104027844A *4 avr. 201410 sept. 2014张志辉Novel method for coating artificial blood vessel with Astragalus polysaccharide
DE3503126A1 *30 janv. 19851 août 1985Meadox Medicals IncArzneimittel abgebender kollagenbeschichteter synthetischer gefaessersatz
DE3503127A1 *30 janv. 19851 août 1985Meadox Medicals IncKollagenbeschichteter synthetischer gefaessersatz
DE3546875C2 *30 janv. 19859 mai 1996Meadox Medicals IncSynthetic vascular grafts
WO1982003764A1 *5 mai 198211 nov. 1982Massachusetts Inst TechnologyFabrication of living blood vessels and glandular tissues
WO1984000540A1 *28 juil. 198316 févr. 1984Jolla Cancer Res FoundPolypeptide
WO1990005501A1 *17 nov. 198931 mai 1990University Of South FloridaMethod for fabricating prosthesis material
WO1993021860A1 *5 mai 199311 nov. 1993Intervascular, Inc.Non-thrombogenic vascular prosthesis
WO1998040112A1 *4 mars 199817 sept. 1998Meadox Medicals, Inc.Self-aggregating protein compositions and use as sealants
WO2006007214A1 *26 mai 200519 janv. 2006Boston Scientific Scimed, Inc.Composite vascular graft with antimicrobial and biodegradable matrices and an outer fabric layer
WO2014197768A1 *6 juin 201411 déc. 2014Baxter International Inc.Immobilization of an active agent on a substrate using compounds including trihydroxyphenyl groups
Classification aux États-Unis623/1.47
Classification internationaleA61L27/50, A61L33/00, A61L27/24, A61L27/54, A61L27/34, A61F2/06, A61F2/00
Classification coopérativeA61F2/062, A61L2300/406, A61L2300/236, A61L27/507, A61F2/06, A61L33/0011, A61L27/34, A61F2310/00365, A61L27/54, A61L2300/42, A61L27/24
Classification européenneA61L27/34, A61L27/24, A61F2/06, A61L27/50E, A61L27/54, A61F2/06B, A61L33/00H2