|Publication number||US3272204 A|
|Publication date||Sep 13, 1966|
|Filing date||Sep 22, 1965|
|Priority date||Sep 22, 1965|
|Publication number||US 3272204 A, US 3272204A, US-A-3272204, US3272204 A, US3272204A|
|Inventors||Artandi Charles, Bechtol Lavon Dee|
|Original Assignee||Ethicon Inc|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (12), Referenced by (313), Classifications (15)|
|External Links: USPTO, USPTO Assignment, Espacenet|
Sept 13, 1966 .2 c. ARTANDI ETAL 3,272,204
ABSORBABLE COLLAGEN PROSTHETIC IMPLANT WITH NON-ABSORBABLE REINFORCING STRAND-S Original Filed March 1, 1961 2 Sheets-Sheet 1 INVENTORS. (Iv m2 E5 /4 P74/VD/ Ara/v 052-" (554W 704.
ATTO R N EY pt. 13, 1966 c. ARTANDI ETAL 3,272,204
ABSORBABLE COLLAGEN PROSTHETIC IMPLANT WITH NON-ABSORBABLE REINFORCING STRANDS Original Filed March 1, 1961 2 Sheets-Sheet 2 INVENTOR'S. (7 4/6455 4/? r4/v0/ Zmgo /v 0E6 550/;
ATTORNEY United States Patent 3,272,204 ABSDRISABLE CDLLAGEN PRGSTHETIC IM- PLANT WITH NON-ABSOABLIE REIN- FORQTNG STRANDS Charles Artandi, Highiand Park, N..I., and Lavon Dee Bechtel, Indianapolis, Ind., assignors to Ethicon, Inc., a corporation of New Jersey Continuation of application Ser. No. 92,620, Mar. 1, 1961. This application Sept. 22, 1965, Ser. No. 495,010 Claims. (Cl. 128334) This application is a continuation of copending application Serial No. 92,620, filed March 1, 1961, now abandoned.
The present invention relates to reinforced collagen prostheses adapted to be placed permanently in the human body, and to a method of making the same. More particularly, this invention relates to collagen articles that are reinforced with non-absorbable fabrics.
In the surgical repair of hernias, tantalum gauze and inert fabrics have found considerable use, particularly in older patients who are recognized to have a reduced ability to rebuild tissue at the point of surgery. Tantalum gauze, however, has the undesirable property of work hardening and may curl up within the body, causing discomfort. Inert fabric prostheses have the disadvantage that they do not becomea part of the body tissues. Such inserts frequently remain surrounded by a pool of sera after the healing process. A suitable prostheses for strengthening the repair should be non-toxic, flexible and porous. The ideal prostheses should retain its strength permanently in intimate contact with body fluids and should be readily accepted and incorporated into the tissue. Porosity is an important characteristic of such a prosthesis to avoid the formation of fluid pockets and to promote the growth through the fabric of repair tissue.
The present invention has for its principal object the provision of flexible films and tubes constructed of collagen and reinforced with an open mesh, non-absorbable fabric that is compatible with the human body.
A further object of the invention is the provision of such flexible tubes that are not subject to kinking or collapsing in any desired diameter or length suitable for use with human arteries or veins.
Another object is the manufacture of prostheses having a structure which promotes the growth of body tissue into and through the prostheses during the healing process.
It has now been discovered that an improved prostheses can be constructed using as a framework or support a non-absorbable plastic material, knitted, woven or braided to have a wide mesh, thus permitting easy invasion by the host into the interstices between the non-absorbable fibers. In the improved prostheses of the present invention, the interstices between the non-absor-bable fibers are initially filled and rendered blood tight by collagen fibrils. The collagen fibrils have considerable tensile strength, are non-antigenic, are slowly absorbed and permit satisfactory in-growth of fibroblasts and endothelial cells, resulting in attachment of the prosthesis to the host tissues. Since collagen is the type of connective tissue normally laid down by the body during the healing process, there is no appreciable decrease in the strength of the prosthesis during the period that the collagen fibrils are being replaced.
The invention will appear more clearly from the following detailed description when taken in connection with the accompanying drawings, showing by way of example, a preferred embodiment of the inventive idea. Referring now to the drawings:
FIGURE 1 is a view of a reinforced collagen film. In this view, the surface collagen films have been forcibly ice pulled away from the n-on-absorbable fabric to illustrate the laminated construction.
FIG. 2 is a greatly enlarged view of the non-absorbable fabric that forms the reinforcing central element of the structure illustrated by FIG. 1.
FIG. 3 is a view of a fabric mesh tube reinforced with a plastic helix.
FIG. 3a is a view in section of a fabric mesh tube reinformed with a plastic helix on the line 3a-3a of FIG. 3.
FIG. 3b is a large scale fragmentary sectional view of FIG. 3 showing a method of supporting a fabric tube in accordance with a feature of the instant invention.
FIG. 4 is a view, partially in section, of a fabric mesh tube reinforced with plastic rings and coated with collagen fibrils.
FIG. 5 is a view, partially in section, of a reinforced molded collagen tube.
The non-absorbable fabric that is used to reinforce the collagen prostheses of the present invention may be knit, woven, crocheted or braided in the desired shape of any synthetic or natural fibers that are compatible with the human body. Examples of suitable materials are Vinyon-N, a resin manufactured by the Carbide and Carbon Corporation by copolymerizing vinyl chloride and acrylonitrile; nylon, a polyamide resin made by polymerization of the hexamethylene diamine salt of adipic acid; Orlon, a synthetic fiber made by the E. I. du Pont de Nemours & Go, from polyacrylonitrile; Dacron, a synthetic fiber made by the E. I. du Pont de Nemours & Go, from terephthalic acid and ethylene glycol; Teflon, a tetrafluoroethylene polymer manufactured by the E. I. du Pont de Nemours & 00.; cotton and silk. Dacron and T efion are particularly preferred because both have displayed excellent retention of tensile strength over long periods of time and both are essentially inert. Teflon being slightly more inert and slightly stronger than Dacron.
The non-absorbable fabrics may be knitted, crocheted, woven or braided in the shape of the desired prosthesis as a film, tube, Y-tube, et-c. Optionally, a film of the fabric may be rolled or cut and sewed with suitable thread to form the desired shape. The fabric may be further strengthened by plastic rings as illustrated in FIG. 4. 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 either side of the fabric framework and form a unitary structure that resists delamination.
After the fabric framework has been constructed in the desired shape, it is 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.
The improved prostheses of the present invention may also be manufactured by an alternate process consisting of knitting, weaving, crocheting or braiding together an inert non-absorbable thread or yarn with collagen yarn or collagen multifilament. A suitable fabric can be woven with warp yarns of Dacron or Teflon and filling yarns of collagen. The preparation of a collagen multifilament suitable for such use is described in United States patent application Serial No. 768,969, filed October 22, 1958, abandoned in favor of continuing appli cation Serial No. 102,533, filed April 12, 1961, now Patent No. 3,114,372.
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 control the rate at which the collagen will be absorbed.
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 n the examples, but is limited solely by the description in this specification and the appended claims. Throughout the specification and the examples which follow, all quantities are expressed in parts by weight.
EXAMPLE I The deep flexor tendon of cattle is cleaned of fat, superficial non-collagenous protein and other extraneous matter and is Sliced on an electric meat-slicing machine (rotary knife) in the frozen condition. The tendon sections are sliced perpendicularly to their longitudinal axis to a thickness of about 11 mils. An aliquot sample of the tendon slices is analyzed; the dry solids amounts to The sliced tendon is next treated with an enzyme solution to dissolve elastin. The enzyme solution is 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 is immersed in this solution which is stored at room temperature overnight. Then 2.25 parts of 30% hydrogen peroxide is added to destroy any residual ficin.
To this mixture of tendon slices in about 750 parts of water is added an additional 2244 parts of water and 5.87 parts of cyanoacetic acid. The swelling solution is cooled to below 25 C. This mixture is stirred in a dispersion kettle at about 60 r.p.m. The remaining steps in the proceSs are carried out at temperatures below about 25 C. and the temperature of the collagen dispersion is not allowed to exceed this temperature.
Stirring is continued for about 3 hours, during which time the individual collagen slices are swollen. The dispersion is then homogenized by repeated passes through series-connected jets having orifices of 50 mils and 40 mils respectively. The dispersion is then forced through a leaf filter containing three screens of #316 stainless steel. These screens are separated by Aa-inch spacers and decrease in mesh size so that the dispersion first passes a 14- mil screen, then a 9-mil screen, and finally a 4-mil screen. The dispersion of swollen solvated collagen fibrils so obtained analyzes 1.09% solids and has a pH of 2.52.
The above collagen dispersion (300 grams) is poured into a stainless-steel tray measuring x 9" x 1 /2" and smoothed out. A Dacron tulle is placed flat on the surface of the collagen dispersion and covered with another 300 grams of collagen dispersion. The tray is frozen in a sub-zero cabinet at C. overnight. The frozen sandwich is then removed from the tray and immersed in a circulating bath containing 5 liters of 99% isopropanol and milliliters of concentrated ammonium hydroxide at room temperature. After approximately four hours, the isopropanol solution is replaced with 5 liters of a fresh solution and the dehydration is continued overnight at room temperature. The isopropanol solution containing the water extracted is removed and a third bath of 99% isopropanol is used in the further dehydration of the collagen. The third bath is replaced in turn with a fourth bath of 99% isopropanol containing 0.4% formaldehyde, the dehydrating time amounting to 6 to 8 hours in both the third and fourth baths. At this time, the collagen fibrils are practically free of water and the Dacron-collagen film may be squeezed repeatedly between rubber rollers and air-dried in an oven at C. overnight without damage.
The product so obtained is illustrated in FIGURE 1. The collagen fibrils of the surface coatings 11 and 12 extend through the openings 13 in the fabric 14 and make it difficult to separate the collagen layer from the fabric.
4 EXAMPLE II A collagen dispersion is prepared according to the general procedure described in Example I above from 391 parts of sliced beef leg tendon and 17,110 parts of distilled Water containing 7.3 parts of glacial acetic acid. This dispersion contains 0.8% solids and is placed in trays and reinforced by immersing a Teflon fabric in the dispersion so that the fabric is suspended about halfway between the sur-face of the dispersion and the bottom of the tray. The contents of each tray is frozen and transferred in the frozen condition to a wire mesh frame. The frozen mass from each tray is dehydrated and coagulated by immersing in a circulating bath containing 60,000 parts of 99% isopropanol, 300 parts of concentrated ammonium hydroxide and 240 parts of formaldehyde (37% solution) at room temperature for approximately 8 hours. The circulating isopropanol bath is then replaced with a freshly constituted bath and the dehydration is continued overnight. This second bath is replaced with a third bath containing 99% isopropanol at room temperature and the dehydration is continued for 8 to 16 hours after which a fourth bath consisting of 99% isopropanol is substituted for the third bath. After dehydration for 8 to 16 hours in the fourth bath, the collagen coated Teflon fabric is compressed at about 128 pounds per square inch pressure and air-dried at C. overnight.
EXAMPLE III Example II above was repeated, substituting for the 7.3 parts of glacial acetic acid employed in that example 59.5 parts of cyanoacetic acid. The resulting prosthesis is sterilized by electron beam irradiation and may be used by the surgeon for hernia repair.
EXAMPLE IV A collagen dispersion is prepared according to the general procedure described in Example I above from 216 parts of sliced beef leg tendon and 9,780 parts of distilled water containing 50 parts of malonic acid. This dispersion contains 0.8% solids and is used to coat both sides of a Teflon net fabric as described in Example I. The Teflon-collagen composition is frozen and transferred in the frozen condition to a wire mesh frame. The frozen mass is dehydrated and coagulated by immersing in a circulating bath containing 45,000 parts of 99% isopropanol and 1330 parts of concentrated ammonium hydroxide at room temperature for approximately 8 hours. The freshly constituted bath and the dehydration is continued overnight. This second bath is replaced with a third bath containing 99% isopropanol at room temperature and the dehydration is continued for 8 to 16 hours after which a fourth bath consisting of 99% isopropanol is substituted for the third bath. After dehydration in the fourth bath for 8 to 16 hours, the resulting product is air-dried at 50 C. overnight.
The film so obtained is tanned by immersing for 30 seconds 1n 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 hydrox- 1de and redried in an oven at 50 C. for 6 hours.
The film is 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 adusted to pH 2.7 with sodium hydroxide, and dried in an oven at 50 C. overnight.
EXAMPLE V A glass tube having an inside diameter of about /1 inch is fitted With a one-hole stopper of rubber through which a A -inch glass rod is placed so that the glass rod extends coaxially within the glass tube. Before placing the glass rod and rubber stopper in position, the glass rod is covered With a piece of rubber tubing and a cylindrical tube of open-mesh woven Dacron about inch in diameter is slipped over the glass rod and rubber tube.
The glass tube and glass rod are assembled in an upright position with the bottom of the Dacron fabric tube resting on the rubber stopper. A dispersion of swollen collagen fibrils (0.08% collagen in 0.05 N acetic acid) is 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 are coated with the collagen dispersion. This mold with the dispersion and fabric in place is then frozen in the vertical position for at least 4 hours at C.
The mold is then placed in a static coagulation bat-h consisting of 2 liters of isopropanol alcohol, cubic centimeters of concentrated ammonia (25%) and 10 cubic centimeters of formaldehyde (37% solution) at room temperature and the mold is maintained in the solution for 16 hours. The glass rod covered with the rubber tube and the formed collagen tube is then removed and placed in a dehydrating bath consisting of 2 liters of isopropanol alcohol. The collagen tube is left in this bath for an additional 16 hours to complete the dehydration.
After dehydration, the rubber tube with the collagen tube on it, is very carefully slid off the glass rod and the rubber tube is 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 is removed from the rubber tubing, it is plasticized in a bath consisting of 2 liters of 90% isopropanol alcohol (10% water) containing 5% glycerine. This plasticizing operation is optional. After 24 hours in the plasticizing bath, the collagen tube is supported on a glass rod and air-dried. The resulting product is illustrated in FIGURE 5.
EXAMPLE VI Tanned Dacron reinforced collagen films prepared by the method described in Example II above are rolled and sewed to form tubes about 1 centimeter in diameter and sterilized by irradiating with an electron beam. These tubes are used to replace segments of the abdominal aorta in mongrel dogs averaging 15 kilograms in weight. The animals were sacrificed at varying periods of time up to 8 months.
Grossly, the Dacron-collagen prothesis shows an orderly pattern of organization at varying periods of time following insertion of the graft. The prostheses are all 5 centimeters long, divided into two typesthick and thin,
according to the amount of impregnated collagen. N0 significant response difference can be detected in the two types. However, there is a significant difference, particularly in regard to initial hemorrhage, between the untreated collagen and the collagen that has been tanned. The following results are observed:
One week Gross specimen-The one-week specimens are contained in a fibrous envelope which is not in any Way adherent to the prosthesis. The interstices of the graft are still occlude-dby the impregnated collagen and the lumen is lined by a red, granular coagulum.
Microscopic section.Sections of the proximal portion show an artefactual separation of the Dacron prosthesis from the surrounding fibro-adipose tissue.
The fibre-adipose tissue shows active fibroplasia and a minimal inflammatory infiltrate, comprised of polymorphonuclear leukocytes, a few lymphocytes and some plasma cells. The prosthesis itself shows the open meshwork with the interstices filled by a series of haphazardlyarranged, tangled fibrils of bovine collagen with irregular interstices containing small numbers of erythrocytes. The surface of the prosthesis is covered by fibrin clot containing a few histiocytes, erythrocytes and neutrophils. There is no tongue-like extension of fibroplasia extending from the severed end of the aorta out into the graft, although there is a focal zone of reactive hyperplasia with capillaries and occasional inflammatory elements present at the anastomotic line. The lining consists of a thin fibrin layer, maximally 1 millimeter in thickness.
Two weeks Gross specimen.By two weeks, the fibrous envelope is partially adherent but may be readily dissected free by lysis of delicate fibrous and fibrinous bands. The wall of the prosthesis and the lining are similar to those of the one-week specimen.
Microscopic seclion.-The two-week specimen shows a lack of inflammatory reaction similar to the specimen at one week. The zone of fibrosis and fibroplasia in the fibro-adipose tissue adjoining the prosthesis is more mature, but as yet, there is no extension of fibroblasts into the prosthesis except at microscopic points. At the anastomosis, a well developed zone of fibroplasia extends across the anastomotic line onto the surface of the prosthesis and this tongue, in turn, is covered in part by endothelium. The prosthesis itself appears quite similar to the oneweek specimen. The impregnated collagen appears well retained. The lining surface of the prosthesis now appears to be more dense fibrin with enmeshed erythrocytes and is somewhat thinner than the fibrin lining of the oneweek specimen.
Three weeks Gross specimen.-At three weeks the fibrous envelope is more adherent than earlier, but still may be separated by forceful dissection. The lining is smoother and averages approximately one millimeter in thickness.
Microscopic section-The peripheral enveloping zone of fibrosis is wider than previously and there is extension of fibroblasts into the interstices of the prosthesis at numerous points. Foreign body reaction to the Dacron of the prosthesis is present but still remains minimal. The inflammatory reaction is largely composed of histiocytes containing hemosiderin, plasma cells and lymphocytes. A mural fibrin thrombus is present and is focally organiZed, particularly at the anastomotic line. This organization is part of the tongue of advancing fibroblasts.
Four weeks Gross specimen.-The four-week specimen is finely swedged to the fibrous envelope. A thin semi-transparent membrane covers the anastomotic lines.
Microscopic section.A dense, surrounding fibrous envelope of mature collagenous connective tissue stains bright green in a Masson trichrome stain. The prosthesis adheres densely to this envelope and there are irregular extensions of this material into the interstitial areas of the prosthesis, most particularly between the Dacron meshwork. The interstices of the bovine collagen are now partially filled with green-staining collagenous connective tissue from the host. Inflammatory reaction is meager. The lining of the prosthesis consists of a zone of fibrous tissue apparently covered by endothelium that ranges in thickness from about 1 millimeter to less than 0.1 millimeter, being thinnest in its more central extent. This lining is continuous with the lining of the dogs aorta.
Five weeks Gross specimen-The five-week specimen is essentially the same as the four-week specimen.
Microscopic secti0n.-The appearance is substantially the same as that of the four-week specimen, although there is slightly less of the bovine collagen remaining and more of green-staining collagen contributed by the host, particularly at the anastomosis.
Two-and-a-half months Gross specimen-The organization is almost complete. The fibrous envelope is firmly adherent and the lumen is lined by a thin, well-defined, smooth, semi-transparent grayish membrane.
Microscopic section-There is notable progress of the fibrous tissue ingrowth into the prosthesis. Only an occasional, longitudinally, oriented wavy thread of the original prosthetic impregnation remains.
Eight months Gross specimen.The prosthesis is solidly united to the fibrous envelope. In cross section, the entire thickness of the prosthetic wall is slightly less than 2 millimeters. The lumen is covered by a smooth, glistening, grayish membrane that appears continuous with the intima of the host artery.
Microscopic section.The prosthesis is completely organized by mature collagen that fills all of the interstices and has replaced all of the original bovine collagen fibrils except for a rare remaining fibril. The luminal aspect of the prosthesis is smooth and is continuous with the dogs aorta. There is virtually no inflammatory reaction. The Dacron material of the prosethetic meshwork appears embedded in a continuous, rather uniform collagen mass. Externally, the prosthesis blends with the adjoining fibroadipose tissue.
EXAMPLE VII A Teflon fabric 14 is rolled to form a cylinder'as indicated in FIGURE 3 and the fabric is sewed with Dacron thread 15 to a surrounding Teflon helix 16 as illustrated in FIGURE 3. The supporting helix prevents the fabric tube from kinking or collapsing. This structure is covered with collagen fibrils on both sides by the procedure outlined in Example V. The resulting tube resists fraying at the ends and is adapted for use in grafts that traverse the inguinal fold or the popliteal space.
EXAMPLE VIII A Dacron fabric 14 is sewed to form a cylinder as indicated in FIGURE 4 and the fabric is sewed with Dacron thread 15 to spaced surrounding Teflon rings 17 as illustrated in FIGURE 4. The supporting rings 17 serve the same function as the helix 16 in FIGURE 3 and prevents the fabric tube from kinking or collapsing. This structure is covered by collagen fibrils on both sides by the procedure outlined in Example V. The resulting article after electron beam sterilization is adapted for use in clinical vascular surgery. The finished tube is quite flexible and may be flexed repeatedly without collapsing.
EXAMPLE IX A collagen dispersion (0.86% solids) is extruded into a circulating acetone dehydrating bath through a stainless steel spinnerette drilled with 192 openings arranged in concentric circles. Each opening in the spinnerette is approximately 18 mils in diameter and each opening has a taper from this diameter at a point 34 mils from the spinnerette surface to a inch opening at the bottom surface of the spinnerette. The multifilament that emerges from the acetone dehydrating bath is wrapped 1 /2 times around a godet and passes to a false twister. Warm air is circulated to dry out the multifilament as it contacts the false twister which is rotated at about 200 r.p.m. Under these conditions, the individual filaments that make up the multifilament do not bond together. The multifilament, which consists of 192 individual collagen threads, may be collected directly on a takeup spool.
The collagen multifilament so obtained may be woven together with non-absorbable multifilament or yarn such as Dacron yarn to form fabrics and tubes that are useful in surgery. It is desirable that the collagen multifilament be tanned by methods well-known in the art to increase the strength and in vivo digestion time of the collagen. The collagen multifilament may be tanned prior to or after weaving. If the collagen multifilament is tanned prior to weaving, a collagen strand may conveniently be formed by twisting the collagen multifilament and drying under tension. Under these conditions, the individual filaments cohere to form a strand which may be woven into a fabric or tube with non-absorbable threads or yarn.
While the invention has been described in detail according to the preferred method of carrying out the process and yielding the products, it will be obvious to those skilled in the art, after understanding the invention, that changes and modifications may be made (without departing from the spirit or scope of the invention) and it is intended in the appended claims to cover such changes and modifications.
What is claimed is: 1. A method of manufacturing surgical prostheses which comprises the steps of:
impregnating a non-absorbable fabric with an aqueous acid dispersion of swollen collagen fibrils; freezing the aqueous acid dispersion of swollen collagen fibrils; immersing the frozen mass in a water-miscible organic solvent containing sufficient base to neutralize the acid present in said dispersion; removing the resulting structure from the organic solvent; and, drying the resulting structure. 2. A method of manufacturing surgical prostheses which comprises the steps of:
knitting an open mesh tube; impregnating this tube with an aqueous acid dispersion of collagen fibrils, whereby said collagen fibrils fill the interstices of the tube; freezing the aqueous acid dispersion of collagen fibrils; immersing the frozen mass in acetone containing suflicient ammonium hydroxide to neutralize the acid present in said dispersion, whereby the collagen fibrils are dehydrated and coagulated; removing the structure so obtained from the acetone;
and, drying. 3. A surgical prosthesis comprising: an open mesh non-absorbable fabric, manufactured of material selected from the group consisting of polyethylene terephthalate and tetra fluoroethylene polymer, and impregnated with a body absor-bable substance consisting of collagen fibrils, whereby the prosthesis is rendered bloodtight. 4. -A surgical prosthesis comprising: an open mesh non-absorbable tulle, manufactured of material selected from the group consisting of polyethylene terephthalate and tetrafluoroethylene polymer, the interstices of which are filled with a body absorbable substance consisting of collagen fibrils, whereby the prosthesis is rendered bloodtight. 5. A surgical prosthesis comprising: an open mesh non-absorbable cylindrical tube, manufactured of material selected from the group consisting of polyethylene terephthalate and tetrafluoroethylene polymer, and coated on at least one side with a body absorbable substance consisting of collagen fibrils, whereby the prosthesis is rendered bloodtight.
A surgical prosthesis comprising:
a knit open mesh non-absorba'ble cylindrical tube, manufactured of material selected from the group consisting of polyethylene terephthalate and tetrafluoroethylene polymer, and coated on at least one side with a body absorbable substance consisting of collagen fibrils, whereby the prosthesis is rendered bloodtight.
7. A surgical prosthesis comprising:
a woven open mesh non-absorbable cylindrical tube, manufactured of material selected from the group consisting of polyethylene terephthalate and tetrafluoroethylene polymer, and coated on both sides with a body absorbable substance consisting of collagen fibrils, whereby the prosthesis is rendered bloodtight.
'8. A surgical prosthesis comprising:
a non-absorbable tulle, manufactured of material selected from the group consisting of polyethylene t r phthalate and tetrafluoroethylene polymer, and
shaped to form a cylindrical tube; a plurality of reinforcing non-absonbable rings manufactured of tet rafiuoroethylene polymer surrounding and spaced along the axis of said tube; said tube being encapsulated in a matrix of collagen fibrils.
9. A surgical prosthesis comprising:
a non-absorbable fabric, manufactured of material selected from the group consisting of polyethylene terephthalate and tetraifluoroethylene polymer fabrics, and shaped to form a cylindrical tube; a nylon helix coiled around said tube; the tube and surrounding helix being coated with collagen fibrils.
10. A surgical prosthesis comprising a bloodtight knitted fabric consisting of a non absorbable yarn selected from the group consisting of polyethylene terephthalate, tetrafluoroethylene polymer yarn and mixtures thereof; and a body absonbable extruded multifilament consisting of collagen fibrils, the interstices between the non-absorbable yarn of the fabric being sufficiently large to permit easy invasion by the host tissue during the healing process.
1 1. A surgical prosthesis comprising a bloodtight fabric woven with filling yarns of non-absorbable threads selected from the group consisting of polyethylene terephthalate and tetrafluoroethylene polymer threads; and Warp yarns of body absorbable extruded strands consisting of collagen fibrils, the non-absorbable threads of the fabric being separated sufficiently from each other to permit easy invasion by the host tissue during the healing process.
12. A surgical prosthesis comprising a bloodtight fabric woven with tfilling yarns of non-absorbable threads selected from the group consisting of polyethylene terephthalate and tetrafluoroethy-lene polymer threads; and Warp yarns of a body absorbable extruded multifilamen-t consisting of collagen fibrils, the interstices between the nonabsorbable threads of the fabric being sufficiently lange to permit easy invasion by the host tissue during the healing process.
1 3. A surgical prosthesis comprising a bloodtight woven fabric consisting of a non-absorbable yarn selected from the group consisting of polyethylene terephthalate, tetrafiuoroethylene polymer yarn and mixtures thereof; and a body absorbable extruded multifilament consisting of collagen fibrils, the interstices between the non-absorb able yarn of the fabric being sufliciently large to permit easy invasion by the host tissue during the healing process.
14. A surgical prosthesis comprising a bloodtight braided fabric consisting of a non-absorbable yarn selected from the group consisting of polyethylene terephthalate, tetrafiuoroethylene polymer yarn and mixtures thereof; and a body absorbable extruded multifilament consisting of collagen fibrils, the interstices between the non-absorbable yarn of the fabric being sufficiently large to permit easy invasion by the host tissue during the healing process.
15. A surgical prosthesis comprising a bloodtight crocheted fabric consisting of a non-absorbable yarn selected from the group consisting of polyethylene terephthalate, tetrafluoroethy lene polymer yarn and mixtures thereof; and a body absonbable extruded multifilament consisting of collagen fibrils, the interstices between the non-a-bsorbable yarn of the fabric being sufficiently large to permit easy invasion by the host tissue during the healing process.
References Cited by the Examiner UNITED STATES PATENTS 2,072,302 3/ 1937 Hermann et al 12'8-335 .5 2,127,903 8/ 1938 =Bowen 128-334 2,453,056 11/1948 Zack 128-334 2,667,321 5/1953 Cresswell 128- 3355 2,671,444 3/ 1954 Pease 128-455 X 2,731,788 1/1956 Donaldson 2 8-7 6 2,827,359 3/1958 Kine et al 28-80 X 2,845,959 8/1958 Sidebotham 31 X 2,920,000 1/ 1960 Hochstadt et al. 260- 123] X 2,934,447 4/1960 Highbenger et al. 106-155 3,011,527 1 2/ 1961 Corbiere 1 393-87 3,014,024 12/ 1961 Lieberman et al. 260-l23.7
OTHER REFERENCES Progress in Synthetic Graft Development, Surgery, vol.
45, No. 2, pp. 298 309, February 1959.
RICHARD A. GAUDET, Primary Examiner.
D. L. TRULUOK, Assistant Examiner.
UNITED STATES PATENT OFFICE CERTIFICATE OF CORRECTION Patent No. 3,272,204 September 13, 1966 Charles Artandi et a1.
ppears in the above numbered pat- It is hereby certified that error a aid Letters Patent should read as ent requiring correction and that the s corrected below.
Column 4 line 46, after. "The" insert circulating isopropanol bath is then replaced with a Signed and sealed this 1st day of August 1967.
EDWARD J. BRENNER Commissioner of Patents Edward M. Fletcher, Jr. Attesting Officer
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US2072302 *||Mar 3, 1932||Mar 2, 1937||Chemische Forschungs Gmbh||Polymerized vinyl alcohol articles and processes of making same|
|US2127903 *||May 5, 1936||Aug 23, 1938||Davis & Geck Inc||Tube for surgical purposes and method of preparing and using the same|
|US2453056 *||Mar 12, 1947||Nov 2, 1948||Edwin Zack William||Surgical anastomosis apparatus and method|
|US2637321 *||Sep 27, 1951||May 5, 1953||American Cyanamid Co||Shaped article and method of producing it|
|US2671444 *||Dec 8, 1951||Mar 9, 1954||Pease Jr Benjamin F||Nonmetallic mesh surgical insert for hernia repair|
|US2731788 *||Oct 8, 1949||Jan 24, 1956||Cluett||Composite thread.|
|US2827359 *||Mar 22, 1954||Mar 18, 1958||Rohm & Haas||Process for stabilization of protein textiles with 4-vinyl pyridine copolymers and products produced therefrom|
|US2845959 *||Mar 26, 1956||Aug 5, 1958||Sidebotham John B||Bifurcated textile tubes and method of weaving the same|
|US2920000 *||Oct 22, 1958||Jan 5, 1960||Ethicon Inc Ethicon Inc||Removable valve Collagen article and the manufacture thereof|
|US2934447 *||Oct 22, 1957||Apr 26, 1960||United Shoe Machinery Corp||Collagen fiber masses and methods of making the same|
|US3011527 *||May 23, 1957||Dec 5, 1961||Rhodiaceta||Prosthesis consisting of textile materials|
|US3014024 *||Mar 19, 1958||Dec 19, 1961||Johnson & Johnson||Collagen film|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US3366440 *||Nov 3, 1964||Jan 30, 1968||Ethicon Inc||Process for manufacturing a collagen fabric-film laminate|
|US3400719 *||Jun 9, 1964||Sep 10, 1968||Albert O.L.J. Eckhart Buddecke||Plastic graft material and method of making same|
|US3408659 *||Jul 21, 1965||Nov 5, 1968||Thiele Heinrich||Artificial blood vessels and process of making same|
|US3425418 *||Apr 15, 1964||Feb 4, 1969||Spofa Vereinigte Pharma Werke||Artificial blood vessels and method of preparing the same|
|US3452366 *||Jun 21, 1966||Jul 1, 1969||Avco Corp||Percutaneous conduit and connector|
|US3463158 *||Jan 9, 1967||Aug 26, 1969||American Cyanamid Co||Polyglycolic acid prosthetic devices|
|US3479670 *||Oct 19, 1966||Nov 25, 1969||Ethicon Inc||Tubular prosthetic implant having helical thermoplastic wrapping therearound|
|US3491760 *||Jul 6, 1966||Jan 27, 1970||Braun Intern Gmbh B||Wound coverings|
|US3514791 *||Jul 25, 1967||Jun 2, 1970||Charles H Sparks||Tissue grafts|
|US3625198 *||May 9, 1969||Dec 7, 1971||Charles H Sparks||Die and holder for implanting in a living body to grow tissue grafts|
|US3862452 *||Jun 21, 1971||Jan 28, 1975||Ceskoslovenska Akademie Ved||Hydrogel substitutes for tubular somatic organs|
|US3918099 *||May 29, 1974||Nov 11, 1975||Fettback Helmut||Artificial organ or part or section thereof for implanation into the human body and method of producing the same|
|US4086665 *||Dec 16, 1976||May 2, 1978||Thermo Electron Corporation||Artificial blood conduit|
|US4130904 *||Jun 6, 1977||Dec 26, 1978||Thermo Electron Corporation||Prosthetic blood conduit|
|US4182339 *||May 17, 1978||Jan 8, 1980||Hardy Thomas G Jr||Anastomotic device and method|
|US4229838 *||Jul 3, 1978||Oct 28, 1980||Sumitomo Electric Industries, Ltd.||Vascular prosthesis having a composite structure|
|US4329743 *||Apr 27, 1979||May 18, 1982||College Of Medicine And Dentistry Of New Jersey||Bio-absorbable composite tissue scaffold|
|US4338926 *||Nov 21, 1980||Jul 13, 1982||Howmedica, Inc.||Bone fracture prosthesis with controlled stiffness|
|US4361552 *||Sep 26, 1980||Nov 30, 1982||Board Of Regents, The University Of Texas System||Wound dressing|
|US4365357 *||Apr 25, 1980||Dec 28, 1982||Merck Patent Gesellschaft Mit Beschrankter Haftung||Surgical materials suitable for use with bone cements|
|US4411027 *||Feb 23, 1982||Oct 25, 1983||University Of Medicine And Dentistry Of New Jersey||Bio-absorbable composite tissue scaffold|
|US4441215 *||Feb 23, 1983||Apr 10, 1984||Kaster Robert L||Vascular graft|
|US4457028 *||Oct 14, 1982||Jul 3, 1984||Merck Patent Gesellschaft Mit Beschrankter Haftung||Surgical materials suitable for use with bone cements|
|US4501263 *||Mar 31, 1982||Feb 26, 1985||Harbuck Stanley C||Method for reducing hypertension of a liver|
|US4512038 *||Apr 6, 1981||Apr 23, 1985||University Of Medicine And Dentistry Of New Jersey||Bio-absorbable composite tissue scaffold|
|US4550447 *||Aug 3, 1983||Nov 5, 1985||Shiley Incorporated||Vascular graft prosthesis|
|US4647416 *||Apr 26, 1985||Mar 3, 1987||Shiley Incorporated||Method of preparing a vascular graft prosthesis|
|US4662884 *||Apr 25, 1984||May 5, 1987||University Of Utah Research Foundation||Prostheses and methods for promoting nerve regeneration|
|US4670286 *||Dec 26, 1985||Jun 2, 1987||Allied Corporation||Method of forming prosthetic devices|
|US4778467 *||Jul 10, 1986||Oct 18, 1988||The University Of Utah||Prostheses and methods for promoting nerve regeneration and for inhibiting the formation of neuromas|
|US4787391 *||Aug 11, 1987||Nov 29, 1988||Elefteriades John A||Anastomotic marking device and related method|
|US4842575 *||Aug 5, 1988||Jun 27, 1989||Meadox Medicals, Inc.||Method for forming impregnated synthetic vascular grafts|
|US4865031 *||Oct 3, 1988||Sep 12, 1989||Keeffe Paul J O||Fabric and method of use for treatment of scars|
|US4871365 *||Dec 24, 1986||Oct 3, 1989||American Cyanamid Company||Partially absorbable prosthetic tubular article having an external support|
|US4915893 *||Jul 15, 1983||Apr 10, 1990||Medtronic, Inc.||Method of preparing polyester filament material|
|US4997440 *||Aug 10, 1990||Mar 5, 1991||American Cyanamid Company||Vascular graft with absorbable and nonabsorbable components|
|US5098779 *||Jun 25, 1990||Mar 24, 1992||W. L. Gore & Associates, Inc.||Carvable implant material|
|US5108424 *||Jan 28, 1991||Apr 28, 1992||Meadox Medicals, Inc.||Collagen-impregnated dacron graft|
|US5110852 *||Oct 27, 1988||May 5, 1992||Rijksuniversiteit Te Groningen||Filament material polylactide mixtures|
|US5141522 *||Jan 21, 1992||Aug 25, 1992||American Cyanamid Company||Composite material having absorbable and non-absorbable components for use with mammalian tissue|
|US5147374 *||Dec 5, 1991||Sep 15, 1992||Alfredo Fernandez||Prosthetic mesh patch for hernia repair|
|US5178630 *||May 26, 1992||Jan 12, 1993||Meadox Medicals, Inc.||Ravel-resistant, self-supporting woven graft|
|US5197977 *||Apr 30, 1992||Mar 30, 1993||Meadox Medicals, Inc.||Drug delivery collagen-impregnated synthetic vascular graft|
|US5201745 *||Aug 15, 1991||Apr 13, 1993||Imedex||Visceral surgery patch|
|US5207670 *||Dec 9, 1991||May 4, 1993||Rare Earth Medical, Inc.||Photoreactive suturing of biological materials|
|US5282823 *||Mar 19, 1992||Feb 1, 1994||Medtronic, Inc.||Intravascular radially expandable stent|
|US5282846 *||Apr 29, 1992||Feb 1, 1994||Meadox Medicals, Inc.||Ravel-resistant, self-supporting woven vascular graft|
|US5282848 *||Apr 19, 1993||Feb 1, 1994||Meadox Medicals, Inc.||Self-supporting woven vascular graft|
|US5282860 *||Oct 8, 1992||Feb 1, 1994||Olympus Optical Co., Ltd.||Stent tube for medical use|
|US5326355 *||Aug 24, 1992||Jul 5, 1994||American Cyanamid Company||Composite material having absorbable and nonabsorbable components for use with mammalian tissue|
|US5383925 *||Sep 14, 1992||Jan 24, 1995||Meadox Medicals, Inc.||Three-dimensional braided soft tissue prosthesis|
|US5385156 *||Aug 27, 1993||Jan 31, 1995||Rose Health Care Systems||Diagnostic and treatment method for cardiac rupture and apparatus for performing the same|
|US5385580 *||Sep 21, 1992||Jan 31, 1995||Meadox Medicals, Inc.||Self-supporting woven vascular graft|
|US5423849 *||Jan 15, 1993||Jun 13, 1995||Target Therapeutics, Inc.||Vasoocclusion device containing radiopaque fibers|
|US5443496 *||Oct 15, 1993||Aug 22, 1995||Medtronic, Inc.||Intravascular radially expandable stent|
|US5458636 *||Jul 20, 1994||Oct 17, 1995||U.S. Biomaterials Corporation||Prosthetic device for repair and replacement of fibrous connective tissue|
|US5487858 *||Jan 31, 1994||Jan 30, 1996||Meadox Medicals, Inc.||Process of making self-supporting woven vascular graft|
|US5496364 *||Jan 31, 1994||Mar 5, 1996||Meadox Medicals, Inc.||Self-supporting woven vascular graft|
|US5509931 *||Jan 28, 1994||Apr 23, 1996||Meadox Medicals, Inc.||Ravel-resistant self-supporting woven vascular graft|
|US5540677 *||Oct 24, 1994||Jul 30, 1996||Rare Earth Medical, Inc.||Endoscopic systems for photoreactive suturing of biological materials|
|US5542594 *||Oct 6, 1993||Aug 6, 1996||United States Surgical Corporation||Surgical stapling apparatus with biocompatible surgical fabric|
|US5562725 *||Sep 14, 1992||Oct 8, 1996||Meadox Medicals Inc.||Radially self-expanding implantable intraluminal device|
|US5562946 *||Nov 2, 1994||Oct 8, 1996||Tissue Engineering, Inc.||Apparatus and method for spinning and processing collagen fiber|
|US5569239 *||Aug 18, 1994||Oct 29, 1996||Rare Earth Medical, Inc.||Photoreactive suturing of biological materials|
|US5628788 *||Nov 7, 1995||May 13, 1997||Corvita Corporation||Self-expanding endoluminal stent-graft|
|US5651174 *||Apr 27, 1995||Jul 29, 1997||Medtronic, Inc.||Intravascular radially expandable stent|
|US5665114 *||Aug 12, 1994||Sep 9, 1997||Meadox Medicals, Inc.||Tubular expanded polytetrafluoroethylene implantable prostheses|
|US5693085 *||Apr 26, 1995||Dec 2, 1997||Scimed Life Systems, Inc.||Stent with collagen|
|US5697969 *||Sep 20, 1995||Dec 16, 1997||Meadox Medicals, Inc.||Vascular prosthesis and method of implanting|
|US5700269 *||Nov 13, 1995||Dec 23, 1997||Corvita Corporation||Endoluminal prosthesis deployment device for use with prostheses of variable length and having retraction ability|
|US5716660 *||May 31, 1995||Feb 10, 1998||Meadox Medicals, Inc.||Tubular polytetrafluoroethylene implantable prostheses|
|US5725522 *||Jun 7, 1995||Mar 10, 1998||Rare Earth Medical, Inc.||Laser suturing of biological materials|
|US5741332 *||Oct 19, 1995||Apr 21, 1998||Meadox Medicals, Inc.||Three-dimensional braided soft tissue prosthesis|
|US5741333 *||Apr 3, 1996||Apr 21, 1998||Corvita Corporation||Self-expanding stent for a medical device to be introduced into a cavity of a body|
|US5800541 *||Jan 8, 1997||Sep 1, 1998||Collagen Corporation||Collagen-synthetic polymer matrices prepared using a multiple step reaction|
|US5824034 *||Jun 5, 1995||Oct 20, 1998||Meadox Medicals, Inc.||Method for repositioning a radially self-expanding implantable intraluminal device|
|US5849037 *||Apr 3, 1996||Dec 15, 1998||Corvita Corporation||Self-expanding stent for a medical device to be introduced into a cavity of a body, and method for its preparation|
|US5851230 *||Oct 18, 1996||Dec 22, 1998||Meadox Medicals, Inc.||Vascular graft with a heparin-containing collagen sealant|
|US5851290 *||May 22, 1996||Dec 22, 1998||Tissue Engineering, Inc.||Apparatus for spinning and processing collagen fiber|
|US5908427 *||May 30, 1997||Jun 1, 1999||United States Surgical Corporation||Surgical stapling apparatus and method|
|US5911942 *||Nov 2, 1995||Jun 15, 1999||Tissue Engineering, Inc.||Method for spinning and processing collagen fiber|
|US5913894 *||Oct 20, 1995||Jun 22, 1999||Meadox Medicals, Inc.||Solid woven tubular prosthesis|
|US5964774 *||Sep 12, 1997||Oct 12, 1999||United States Surgical Corporation||Surgical stapling apparatus and method with surgical fabric|
|US5968091 *||Nov 26, 1997||Oct 19, 1999||Corvita Corp.||Stents and stent grafts having enhanced hoop strength and methods of making the same|
|US5972007 *||Oct 31, 1997||Oct 26, 1999||Ethicon Endo-Surgery, Inc.||Energy-base method applied to prosthetics for repairing tissue defects|
|US6042592 *||Aug 4, 1997||Mar 28, 2000||Meadox Medicals, Inc.||Thin soft tissue support mesh|
|US6045560 *||Jun 17, 1996||Apr 4, 2000||United States Surgical Corporation||Surgical stapling apparatus with biocompatible surgical fabric|
|US6090137 *||Feb 5, 1999||Jul 18, 2000||Meadox Medicals, Inc.||Solid woven tubular prosthesis methods|
|US6090996 *||Aug 4, 1997||Jul 18, 2000||Collagen Matrix, Inc.||Implant matrix|
|US6120539 *||May 1, 1997||Sep 19, 2000||C. R. Bard Inc.||Prosthetic repair fabric|
|US6162247 *||Dec 21, 1998||Dec 19, 2000||Meadox Medicals, Inc.||Vascular graft impregnated with a heparin-containing collagen sealant|
|US6177609 *||Mar 10, 1997||Jan 23, 2001||Meadox Medicals, Inc.||Self-aggregating protein compositions and use as sealants|
|US6197296||Mar 29, 1994||Mar 6, 2001||National Heart Research Fund||Tissue equivalents|
|US6228111||Sep 27, 1996||May 8, 2001||Bionx Implants Oy||Biodegradable implant manufactured of polymer-based material and a method for manufacturing the same|
|US6237460||Apr 30, 1998||May 29, 2001||Corvita Corporation||Method for preparation of a self-expanding stent for a medical device to be introduced into a cavity of a body|
|US6251110||Mar 31, 1999||Jun 26, 2001||Ethicon Endo-Surgery, Inc.||Combined radio frequency and ultrasonic surgical device|
|US6257241||Mar 31, 1999||Jul 10, 2001||Ethicon Endo-Surgery, Inc.||Method for repairing tissue defects using ultrasonic radio frequency energy|
|US6258124||May 10, 1999||Jul 10, 2001||C. R. Bard, Inc.||Prosthetic repair fabric|
|US6270530||Jun 9, 2000||Aug 7, 2001||C.R. Bard, Inc.||Prosthetic repair fabric|
|US6273897||Feb 29, 2000||Aug 14, 2001||Ethicon, Inc.||Surgical bettress and surgical stapling apparatus|
|US6287344||Mar 31, 1999||Sep 11, 2001||Ethicon Endo-Surgery, Inc.||Method for repairing tissue defects using an ultrasonic device|
|US6296645||Apr 9, 1999||Oct 2, 2001||Depuy Orthopaedics, Inc.||Intramedullary nail with non-metal spacers|
|US6325810||Jun 30, 1999||Dec 4, 2001||Ethicon, Inc.||Foam buttress for stapling apparatus|
|US6334872 *||Jul 7, 1997||Jan 1, 2002||Organogenesis Inc.||Method for treating diseased or damaged organs|
|US6348065||Jul 24, 1998||Feb 19, 2002||Scimed Life Systems, Inc.||Longitudinally flexible expandable stent|
|US6350277||Jan 15, 1999||Feb 26, 2002||Scimed Life Systems, Inc.||Stents with temporary retaining bands|
|US6368347 *||Apr 23, 1999||Apr 9, 2002||Sulzer Vascutek Ltd.||Expanded polytetrafluoroethylene vascular graft with coating|
|US6375662||Nov 23, 1999||Apr 23, 2002||Scimed Life Systems, Inc.||Thin soft tissue surgical support mesh|
|US6391052||Oct 29, 1997||May 21, 2002||Scimed Life Systems, Inc.||Stent with collagen|
|US6416486||Mar 31, 1999||Jul 9, 2002||Ethicon Endo-Surgery, Inc.||Ultrasonic surgical device having an embedding surface and a coagulating surface|
|US6488705||Sep 18, 2001||Dec 3, 2002||Meadox Medicals, Inc.||Radially self-expanding implantable intraluminal device|
|US6497650||Jul 28, 2000||Dec 24, 2002||C. R. Bard, Inc.||Hernia prosthesis|
|US6524345||Oct 22, 1997||Feb 25, 2003||Bionx Implants Oy||Surgical implant|
|US6572650||Jun 4, 1999||Jun 3, 2003||Organogenesis Inc.||Bioengineered vascular graft support prostheses|
|US6652595||Jan 9, 1998||Nov 25, 2003||Davol Inc.||Method of repairing inguinal hernias|
|US6669706||Dec 18, 2001||Dec 30, 2003||Scimed Life Systems, Inc.||Thin soft tissue surgical support mesh|
|US6709436||May 22, 2000||Mar 23, 2004||Depuy Orthopaedics, Inc.||Non-metal spacers for intramedullary nail|
|US6726664 *||Aug 6, 2001||Apr 27, 2004||Optonol Ltd.||Flow control device, introducer and method of implanting|
|US6770088||May 18, 2000||Aug 3, 2004||Scimed Life Systems, Inc.||Intravascular stent|
|US6783529||Oct 19, 2001||Aug 31, 2004||Depuy Orthopaedics, Inc.||Non-metal inserts for bone support assembly|
|US6786908||Aug 2, 2001||Sep 7, 2004||Depuy Orthopaedics, Inc.||Bone fracture support implant with non-metal spacers|
|US6790213||Jan 7, 2002||Sep 14, 2004||C.R. Bard, Inc.||Implantable prosthesis|
|US6808527||Mar 25, 2002||Oct 26, 2004||Depuy Orthopaedics, Inc.||Intramedullary nail with snap-in window insert|
|US6818014||Aug 3, 1995||Nov 16, 2004||Scimed Life Systems, Inc.||Longitudinally flexible expandable stent|
|US6827743 *||Feb 25, 2002||Dec 7, 2004||Sdgi Holdings, Inc.||Woven orthopedic implants|
|US6846323||May 15, 2003||Jan 25, 2005||Advanced Cardiovascular Systems, Inc.||Intravascular stent|
|US6890351 *||Sep 7, 2001||May 10, 2005||Organogenesis Inc.||Method for treating diseased or damaged organs|
|US6913619||Jul 11, 2002||Jul 5, 2005||Boston Scientific Scimed, Inc.||Longitudinally flexible expandable stent|
|US6929659||Feb 25, 2002||Aug 16, 2005||Scimed Life Systems, Inc.||Method of preventing the dislodgment of a stent-graft|
|US6962603||Jun 22, 2000||Nov 8, 2005||Boston Scientific Scimed, Inc.||Longitudinally flexible expandable stent|
|US6976952||Apr 25, 2000||Dec 20, 2005||Vascutek Limited||Expanded polytetrafluoroethylene vascular graft with coating|
|US6981986||Sep 20, 2000||Jan 3, 2006||Boston Scientific Scimed, Inc.||Longitudinally flexible expandable stent|
|US6986735||Mar 3, 2003||Jan 17, 2006||Organogenesis Inc.||Method of making a bioremodelable vascular graft prosthesis|
|US7022132||Feb 26, 2002||Apr 4, 2006||Boston Scientific Scimed, Inc.||Stents with temporary retaining bands|
|US7041131||Apr 11, 2003||May 9, 2006||Organogenesis, Inc.||Bioengineered vascular graft support prostheses|
|US7044982||Aug 27, 2001||May 16, 2006||Michael Milbocker||Surgical repair of tissue defects|
|US7060103||Feb 28, 2003||Jun 13, 2006||Organogenesis Inc.||Tissue repair fabric|
|US7081130||Apr 16, 2002||Jul 25, 2006||Boston Scientific Scimed, Inc.||Intravascular Stent|
|US7121999||Mar 3, 2003||Oct 17, 2006||Organogenesis Inc.||Method of preparing layered graft prostheses|
|US7156804||Dec 2, 2002||Jan 2, 2007||Davol, Inc.||Hernia prosthesis|
|US7160333||Sep 5, 2003||Jan 9, 2007||Depuy Orthopaedics, Inc.||Reinforced small intestinal submucosa|
|US7163563||Jul 15, 2002||Jan 16, 2007||Depuy Products, Inc.||Unitary surgical device and method|
|US7201917||Jul 15, 2002||Apr 10, 2007||Depuy Products, Inc.||Porous delivery scaffold and method|
|US7204848||Nov 20, 1998||Apr 17, 2007||Boston Scientific Scimed, Inc.||Longitudinally flexible expandable stent|
|US7214242||Mar 3, 2003||May 8, 2007||Organogenesis, Inc.||Bioengineered tubular graft prostheses|
|US7326241||Aug 9, 2001||Feb 5, 2008||Boston Scientific Scimed, Inc.||Intravascular stent|
|US7341601||Jul 28, 2004||Mar 11, 2008||Warsaw Orthopedic, Inc.||Woven orthopedic implants|
|US7354627||Dec 22, 2004||Apr 8, 2008||Depuy Products, Inc.||Method for organizing the assembly of collagen fibers and compositions formed therefrom|
|US7404819||Sep 14, 2000||Jul 29, 2008||C.R. Bard, Inc.||Implantable prosthesis|
|US7410488||Feb 18, 2005||Aug 12, 2008||Smith & Nephew, Inc.||Hindfoot nail|
|US7468210||Dec 10, 2003||Dec 23, 2008||Biosurface Engineering Technologies, Inc.||Cross-linked heparin coatings and methods|
|US7481816||Oct 27, 2003||Jan 27, 2009||Optonol Ltd.||Intraocular implant, delivery device, and method of implantation|
|US7513865||Dec 20, 2005||Apr 7, 2009||Boston Scientific Scimed, Inc.||Flattened tubular mesh sling and related methods|
|US7513866||Oct 29, 2004||Apr 7, 2009||Depuy Products, Inc.||Intestine processing device and associated method|
|US7569233||Apr 20, 2005||Aug 4, 2009||Depuy Products, Inc.||Hybrid biologic-synthetic bioabsorbable scaffolds|
|US7585319 *||Sep 27, 2004||Sep 8, 2009||Maquet Cardiovascular, Llc||Self-aggregating protein compositions and use as sealants|
|US7595062||Jul 28, 2005||Sep 29, 2009||Depuy Products, Inc.||Joint resurfacing orthopaedic implant and associated method|
|US7614258||Oct 19, 2006||Nov 10, 2009||C.R. Bard, Inc.||Prosthetic repair fabric|
|US7655009||Nov 30, 2004||Feb 2, 2010||Smith & Nephew, Inc.||Humeral nail|
|US7670310||Dec 7, 2007||Mar 2, 2010||Optonol Ltd||Flow regulating implants|
|US7682392||Oct 30, 2002||Mar 23, 2010||Depuy Spine, Inc.||Regenerative implants for stabilizing the spine and devices for attachment of said implants|
|US7700563||Aug 19, 2003||Apr 20, 2010||Biosurface Engineering Technologies, Inc.||Synthetic heparin-binding factor analogs|
|US7766956||Nov 26, 2003||Aug 3, 2010||Boston Scientific Scimed, Inc.||Intravascular stent and assembly|
|US7799089||Oct 10, 2006||Sep 21, 2010||Depuy Orthopaedics, Inc.||Reinforced small intestinal submucosa|
|US7815562||Aug 11, 2005||Oct 19, 2010||Boston Scientific Scimed, Inc.||Tubular implantable sling and related delivery systems, methods and devices|
|US7819918 *||Dec 29, 2003||Oct 26, 2010||Depuy Products, Inc.||Implantable tissue repair device|
|US7820172||Jun 1, 2007||Oct 26, 2010||Biosurface Engineering Technologies, Inc.||Laminin-derived multi-domain peptides|
|US7824420||May 26, 2004||Nov 2, 2010||C.R. Bard, Inc.||Implantable prosthesis|
|US7824701||Feb 25, 2003||Nov 2, 2010||Ethicon, Inc.||Biocompatible scaffold for ligament or tendon repair|
|US7862531||Jun 25, 2004||Jan 4, 2011||Optonol Ltd.||Flow regulating implants|
|US7871440||Dec 11, 2006||Jan 18, 2011||Depuy Products, Inc.||Unitary surgical device and method|
|US7875296||Nov 29, 2007||Jan 25, 2011||Depuy Mitek, Inc.||Conformable tissue repair implant capable of injection delivery|
|US7900484||Nov 5, 2009||Mar 8, 2011||C.R. Bard, Inc.||Prosthetic repair fabric|
|US7901461||Dec 5, 2003||Mar 8, 2011||Ethicon, Inc.||Viable tissue repair implants and methods of use|
|US7909886||Mar 24, 2006||Mar 22, 2011||Organogenesis, Inc.||Tissue repair fabric|
|US7914808 *||Jul 15, 2002||Mar 29, 2011||Depuy Products, Inc.||Hybrid biologic/synthetic porous extracellular matrix scaffolds|
|US7927619||Apr 26, 2006||Apr 19, 2011||Promethean Surgical Devices Llc||In situ bulking composition|
|US7981862||Jun 22, 2007||Jul 19, 2011||Biosurface Engineering Technologies, Inc.||Composition comprising BMP-2 amplifier/co-activator for enhancement of osteogenesis|
|US7988717||Nov 10, 2003||Aug 2, 2011||Boston Scientific Scimed, Inc.||Longitudinally flexible expandable stent|
|US7988720||Jul 20, 2007||Aug 2, 2011||Boston Scientific Scimed, Inc.||Longitudinally flexible expandable stent|
|US8012205 *||Jul 15, 2002||Sep 6, 2011||Depuy Products, Inc.||Cartilage repair and regeneration device|
|US8016867||Oct 28, 2004||Sep 13, 2011||Depuy Mitek, Inc.||Graft fixation device and method|
|US8021414||Jul 25, 2002||Sep 20, 2011||Boston Scientific Scimed, Inc.||Intravascular stent|
|US8025896||Jul 15, 2002||Sep 27, 2011||Depuy Products, Inc.||Porous extracellular matrix scaffold and method|
|US8034016||Dec 7, 2007||Oct 11, 2011||Optonol, Ltd.||Flow regulating implants and methods of implanting|
|US8070792||Mar 28, 2002||Dec 6, 2011||Boston Scientific Scimed, Inc.||Stent|
|US8092529||Jul 15, 2002||Jan 10, 2012||Depuy Products, Inc.||Meniscus regeneration device|
|US8101570||May 24, 2010||Jan 24, 2012||Biosurface Engineering Technologies, Inc.||Single branch heparin-binding growth factor analogs|
|US8109896||Feb 11, 2008||Feb 7, 2012||Optonol Ltd.||Devices and methods for opening fluid passageways|
|US8114146||Mar 15, 2004||Feb 14, 2012||Boston Scientific Scimed, Inc.||Longitudinally flexible expandable stent|
|US8137686||Apr 20, 2004||Mar 20, 2012||Depuy Mitek, Inc.||Nonwoven tissue scaffold|
|US8137702||Dec 29, 2010||Mar 20, 2012||Depuy Mitek, Inc.||Conformable tissue repair implant capable of injection delivery|
|US8142489||Sep 5, 2008||Mar 27, 2012||Boston Scientific Scimed, Inc.||Flexible and expandable stent|
|US8163717||Oct 6, 2009||Apr 24, 2012||Biosurface Engineering Technologies, Inc.||Dual chain synthetic heparin-binding growth factor analogs|
|US8182545||Jul 10, 2008||May 22, 2012||C.R. Bard, Inc.||Implantable prosthesis|
|US8192763||Jul 23, 2008||Jun 5, 2012||Cook Biotech Incorporated||Processed ECM materials with enhanced component profiles|
|US8221780||Jun 29, 2006||Jul 17, 2012||Depuy Mitek, Inc.||Nonwoven tissue scaffold|
|US8226715||Jul 24, 2012||Depuy Mitek, Inc.||Scaffold for connective tissue repair|
|US8227411||Feb 23, 2006||Jul 24, 2012||BioSurface Engineering Technologies, Incle||FGF growth factor analogs|
|US8231930 *||Aug 4, 2009||Jul 31, 2012||Maquet Cardiovascular, Llc||Self-aggregating protein compositions and use as sealants|
|US8282542||Feb 24, 2009||Oct 9, 2012||Boston Scientific Scimed, Inc.||Flattened tubular mesh sling and related methods|
|US8313454||Mar 26, 2010||Nov 20, 2012||Optonol Ltd.||Fluid drainage device, delivery device, and associated methods of use and manufacture|
|US8337537||Jul 15, 2002||Dec 25, 2012||Depuy Products, Inc.||Device from naturally occurring biologically derived materials|
|US8348992||Aug 21, 2001||Jan 8, 2013||Boston Scientific Scimed, Inc.||Longitudinally flexible expandable stent|
|US8366787||Jun 14, 2002||Feb 5, 2013||Depuy Products, Inc.||Hybrid biologic-synthetic bioabsorbable scaffolds|
|US8449561||Feb 15, 2007||May 28, 2013||Depuy Mitek, Llc||Graft fixation device combination|
|US8449597||Nov 21, 2011||May 28, 2013||Boston Scientific Scimed, Inc.||Longitudinally flexible expandable stent|
|US8486086||Nov 7, 2011||Jul 16, 2013||Optonol, Ltd||Flow regulating implant, method of manufacture, and delivery device|
|US8496970||Feb 27, 2012||Jul 30, 2013||Depuy Mitek, Llc||Conformable tissue repair implant capable of injection delivery|
|US8541372||Jan 3, 2011||Sep 24, 2013||Cook Biotech Incorporated||Isolated extracellular matrix material including subserous fascia|
|US8562665||Dec 17, 2002||Oct 22, 2013||Boston Scientific Scimed, Inc.||Tubular stent consists of chevron-shape expansion struts and contralaterally attached diagonal-connectors|
|US8591930||Apr 28, 2008||Nov 26, 2013||Cook Biotech Incorporated||Growth factor modified extracellular matrix material preparation and methods for preparation and use thereof|
|US8617206||Oct 4, 2010||Dec 31, 2013||Covidien Lp||Wound closure device|
|US8628464||Oct 2, 2012||Jan 14, 2014||Boston Scientific Scimed, Inc.||Flattened tubular mesh sling and related methods|
|US8637066||Sep 21, 2010||Jan 28, 2014||Depuy Mitek, Llc||Biocompatible scaffold for ligament or tendon repair|
|US8641775||Feb 1, 2011||Feb 4, 2014||Depuy Mitek, Llc||Viable tissue repair implants and methods of use|
|US8663086||Sep 28, 2010||Mar 4, 2014||Cook Biotech Incorporated||Medical reinforcement graft|
|US8663313||Sep 22, 2011||Mar 4, 2014||Boston Scientific Scimed, Inc.||Low strain high strength stent|
|US8691259||Nov 16, 2005||Apr 8, 2014||Depuy Mitek, Llc||Reinforced foam implants with enhanced integrity for soft tissue repair and regeneration|
|US8728147||Dec 20, 2011||May 20, 2014||Boston Scientific Limited||Longitudinally flexible expandable stent|
|US8790388||Mar 2, 2012||Jul 29, 2014||Boston Scientific Scimed, Inc.||Stent with reduced profile|
|US8795384||Jan 10, 2008||Aug 5, 2014||Cook Biotech Incorporated||Implantable devices useful for reinforcing a surgically created stoma|
|US8796212||Jul 19, 2011||Aug 5, 2014||Biosurface Engineering Technologies, Inc.||Composition and method for delivery of BMP-2 amplifier/co-activator for enhancement of osteogenesis|
|US8801773||Mar 26, 2012||Aug 12, 2014||Boston Scientific Scimed, Inc.||Flexible and expandable stent|
|US8895045||May 8, 2012||Nov 25, 2014||Depuy Mitek, Llc||Method of preparation of bioabsorbable porous reinforced tissue implants and implants thereof|
|US8956378||Feb 27, 2009||Feb 17, 2015||Cook Biotech Incorporated||Coated embolization device|
|US9044455||Jul 26, 2013||Jun 2, 2015||Cook Biotech Incorporated||Isolated extracellular matrix material including subserous fascia|
|US9072586||Oct 2, 2009||Jul 7, 2015||C.R. Bard, Inc.||Implantable prosthesis|
|US9078778||Sep 14, 2011||Jul 14, 2015||Boston Scientific Scimed, Inc.||Intravascular stent|
|US9173774||Sep 11, 2012||Nov 3, 2015||Optonol Ltd.||Fluid drainage device, delivery device, and associated methods of use and manufacture|
|US9180145||Oct 9, 2013||Nov 10, 2015||Mimedx Group, Inc.||Compositions and methods for recruiting and localizing stem cells|
|US9186053 *||Apr 11, 2013||Nov 17, 2015||Covidien Lp||Methods of using light to repair hernia defects|
|US20020049503 *||Aug 27, 2001||Apr 25, 2002||Michael Milbocker||Surgical repair of tissue defects|
|US20020095208 *||Mar 28, 2002||Jul 18, 2002||Scimed Life Systems, Inc.||Stent|
|US20020103542 *||Sep 18, 2001||Aug 1, 2002||Bilbo Patrick R.||Methods for treating a patient using a bioengineered flat sheet graft prostheses|
|US20020116049 *||Jan 9, 2002||Aug 22, 2002||Scimed Life Systems, Inc.||Stent|
|US20020123750 *||Feb 25, 2002||Sep 5, 2002||Lukas Eisermann||Woven orthopedic implants|
|US20030023316 *||Jun 14, 2002||Jan 30, 2003||Brown Laura Jean||Hybrid biologic-synthetic bioabsorable scaffolds|
|US20030033021 *||Jul 15, 2002||Feb 13, 2003||Plouhar Pamela Lynn||Cartilage repair and regeneration scaffold and method|
|US20030079329 *||Dec 9, 2002||May 1, 2003||Ira Yaron||Flow regulating implant, method of manufacture, and delivery device|
|US20030083736 *||Aug 3, 1995||May 1, 2003||Brian J. Brown||Longitudinally flexible expandable stent|
|US20030130747 *||Mar 3, 2003||Jul 10, 2003||Organogenesis, Inc.||Bioengineered flat sheet graft prostheses|
|US20030149472 *||Mar 7, 2003||Aug 7, 2003||Leonard Pinchuk||Modular endluminal stent-grafts and methods for their use|
|US20030158607 *||Feb 28, 2003||Aug 21, 2003||Carr Robert M.||Tissue repair fabric|
|US20030167088 *||Mar 3, 2003||Sep 4, 2003||Organogenesis, Inc.||Bioengineered vascular graft prostheses|
|US20030171824 *||Mar 3, 2003||Sep 11, 2003||Organogenesis, Inc.||Bioengineered tubular graft prostheses|
|US20030195618 *||Apr 11, 2003||Oct 16, 2003||Organogenesis, Inc.||Bioengineered vascular graft support prostheses|
|US20040059431 *||Sep 5, 2003||Mar 25, 2004||Plouhar Pamela L.||Reinforced small intestinal submucosa|
|US20040087505 *||Aug 19, 2003||May 6, 2004||Pena Louis A.||Synthetic heparin-binding factor analogs|
|US20040088048 *||Oct 27, 2003||May 6, 2004||Jacob Richter||Intraocular implant, delivery device, and method of implantation|
|US20040176834 *||Mar 15, 2004||Sep 9, 2004||Brown Brian J.||Longitudinally flexible expandable stent|
|US20040220574 *||Jul 15, 2002||Nov 4, 2004||Pelo Mark Joseph||Device from naturally occuring biologically derived materials|
|US20040230288 *||Apr 17, 2002||Nov 18, 2004||Rosenthal Arthur L.||Medical devices adapted for controlled in vivo structural change after implantation|
|US20050038520 *||Aug 11, 2003||Feb 17, 2005||Francois Binette||Method and apparatus for resurfacing an articular surface|
|US20050043733 *||Jul 28, 2004||Feb 24, 2005||Lukas Eisermann||Woven orthopedic implants|
|US20050085901 *||Sep 27, 2004||Apr 21, 2005||Dan Castro||Self-aggregating protein compostions and use as sealants|
|US20050125077 *||Dec 5, 2003||Jun 9, 2005||Harmon Alexander M.||Viable tissue repair implants and methods of use|
|US20050182484 *||Feb 12, 2004||Aug 18, 2005||Patel Umesh H.||Hybrid grafts|
|US20050192600 *||Feb 24, 2005||Sep 1, 2005||Enrico Nicolo||Inguinal hernia repair prosthetic|
|US20050232967||Apr 20, 2004||Oct 20, 2005||Kladakis Stephanie M||Nonwoven tissue scaffold|
|US20060034943 *||Oct 11, 2005||Feb 16, 2006||Technology Innovations Llc||Process for treating a biological organism|
|US20060100717 *||Nov 23, 2005||May 11, 2006||Organogenesis, Inc.||Bioengineered vascular graft prostheses|
|US20060147371 *||Feb 23, 2005||Jul 6, 2006||Tuszynski Jack A||Water-soluble compound|
|US20060198816 *||Apr 26, 2006||Sep 7, 2006||Milbocker Michael T||In situ bulking composition|
|US20060199764 *||Feb 23, 2006||Sep 7, 2006||Biosurface Engineering Technologies, Inc.||FGF growth factor analogs|
|US20070038017 *||Aug 11, 2005||Feb 15, 2007||Boston Scientific Scimed, Inc.||Tubular implantable sling and related delivery systems, methods and devices|
|US20070112360 *||Nov 15, 2005||May 17, 2007||Patrick De Deyne||Bioprosthetic device|
|US20070135906 *||Oct 5, 2006||Jun 14, 2007||Badylak Stephen F||Stent with collagen|
|US20070150059 *||Dec 22, 2005||Jun 28, 2007||Depuy Spine, Inc.||Methods and devices for intervertebral augmentation using injectable formulations and enclosures|
|US20070150063 *||Dec 22, 2005||Jun 28, 2007||Depuy Spine, Inc.||Devices for intervertebral augmentation and methods of controlling their delivery|
|US20070150064 *||Dec 22, 2005||Jun 28, 2007||Depuy Spine, Inc.||Methods and devices for intervertebral augmentation|
|US20080063622 *||Jun 22, 2007||Mar 13, 2008||Biosurface Engineering Technologies, Inc.||Composition and Method for Delivery of BMP-2 Amplifier/Co-Activator for Enhancement of Osteogenesis|
|US20080071385 *||Nov 29, 2007||Mar 20, 2008||Depuy Mitek, Inc.||Conformable tissue repair implant capable of injection delivery|
|US20080125691 *||Dec 7, 2007||May 29, 2008||Optonol Ltd.||Flow regulating implants|
|US20080160169 *||Dec 21, 2007||Jul 3, 2008||Zamora Paul O||Coating device and method for coating medical device with bioactive peptide|
|US20080166392 *||Jan 31, 2008||Jul 10, 2008||Zamora Paul O||Positive Modulator of Bone Morphogenic Protein-2|
|US20080167729 *||Jan 10, 2008||Jul 10, 2008||Nelson Christopher M||Implantable devices useful for reinforcing a surgically created stoma|
|US20080286268 *||Jul 23, 2008||Nov 20, 2008||Johnson Chad E||Processed ecm materials with enhanced component profiles|
|US20080299171 *||Apr 28, 2008||Dec 4, 2008||Hiles Michael C||Growth factor modified extracellular matrix material and methods for preparation and use thereof|
|US20080319531 *||Sep 5, 2008||Dec 25, 2008||Boston Scientific Scimed, Inc.||Flexible and expandable stent|
|US20090105753 *||Aug 26, 2005||Apr 23, 2009||Prodesco, Inc.||Sutures and methods of making the same|
|US20090112236 *||Oct 15, 2008||Apr 30, 2009||Tyco Healthcare Group Lp||Filament-Reinforced Composite Fiber|
|US20090142400 *||May 30, 2008||Jun 4, 2009||Hiles Michael C||Analgesic coated medical product|
|US20090156893 *||Feb 24, 2009||Jun 18, 2009||Boston Scientific Scimed, Inc.||Flattened tubular mesh sling and related methods|
|US20090187197 *||Aug 1, 2008||Jul 23, 2009||Roeber Peter J||Knit PTFE Articles and Mesh|
|US20090270978 *||Oct 29, 2009||Virkler Joel A||Coated embolization device|
|US20090297692 *||Dec 3, 2009||Maquet Cardiovascular, Llc||Self-aggregating protein compositions and use as sealants|
|US20100015868 *||Jan 21, 2010||Philippe Gravagna||Reinforced composite implant|
|US20100174253 *||Jun 11, 2008||Jul 8, 2010||Convatec Technologies Inc.||Ostomy Appliance|
|US20100274259 *||Mar 26, 2010||Oct 28, 2010||Optonol Ltd.||Fluid drainage device, delivery device, and associated methods of use and manufacture|
|US20100298218 *||May 24, 2010||Nov 25, 2010||Biosurface Engineering Technologies, Inc.||Single Branch Heparin-Binding Growth Factor Analogs|
|US20120253473 *||Oct 28, 2010||Oct 4, 2012||Biom'up||Composite matrix|
|US20130296657 *||Apr 11, 2013||Nov 7, 2013||Covidien Lp||Methods of using light to repair hernia defects|
|US20140067058 *||Aug 14, 2013||Mar 6, 2014||Mimedx Group, Inc.||Reinforced placental tissue grafts and methods of making and using the same|
|USRE44501||Aug 12, 2010||Sep 17, 2013||Smith & Nephew, Inc.||Hindfoot nail|
|DE3503126A1 *||Jan 30, 1985||Aug 1, 1985||Meadox Medicals Inc||Arzneimittel abgebender kollagenbeschichteter synthetischer gefaessersatz|
|DE3503127A1 *||Jan 30, 1985||Aug 1, 1985||Meadox Medicals Inc||Kollagenbeschichteter synthetischer gefaessersatz|
|DE4128611A1 *||Aug 28, 1991||Mar 5, 1992||Meadox Medicals Inc||Ausfransfestes, selbsttragendes, gewobenes gefaessimplantat|
|DE4128611C3 *||Aug 28, 1991||Apr 18, 2002||Meadox Medicals Inc||Ausfransfestes, selbsttragendes, gewobenes Gefäßimplantat und Verfahren zu seiner Herstellung|
|EP0103005A1 *||Feb 16, 1983||Mar 21, 1984||SCHENCK, Robert R.||Method and apparatus for anastomosing blood vessels|
|EP0129428A2 *||Jun 15, 1984||Dec 27, 1984||Robert Roy Schenk||Devices for joining anatomical structures|
|EP0466105A2 *||Jul 9, 1991||Jan 15, 1992||Corvita Corporation||Composite biosynthetic graft|
|EP0587461A2 *||Jun 14, 1993||Mar 16, 1994||Terumo Kabushiki Kaisha||Artificial blood vessel|
|EP0943345A1 *||Nov 19, 1997||Sep 22, 1999||SHIMIZU, Yasuhiko||Artificial esophagus|
|WO1982001647A1 *||Oct 30, 1981||May 27, 1982||Robert L Kaster||Vascular graft|
|WO1983003536A1 *||Apr 18, 1983||Oct 27, 1983||Massachusetts Inst Technology||A multilayer bioreplaceable blood vessel prosthesis|
|WO1984000540A1 *||Jul 28, 1983||Feb 16, 1984||Jolla Cancer Res Found||Polypeptide|
|WO1992003107A1||Aug 27, 1991||Mar 5, 1992||Meadox Medicals Inc||Self-supporting woven vascular graft|
|WO1998018408A1||Oct 22, 1997||May 7, 1998||Bionix Implants Oy||Surgical implant|
|WO2001080918A1||Apr 25, 2000||Nov 1, 2001||Karen Kelso||Expanded polytetrafluoroethylene vascular graft with coating|
|WO2003034945A1 *||Oct 23, 2002||May 1, 2003||Katsuko Sakai||Artificial vessel and process for producing the same|
|WO2004093932A1 *||Apr 21, 2004||Nov 4, 2004||Verigen Ag||A seeded tear resistant scaffold|
|WO2011079976A1 *||Oct 28, 2010||Jul 7, 2011||Biom'up||Composite matrix|
|U.S. Classification||606/151, 427/398.1, 139/387.00R, 427/338, 623/1.38, 606/229|
|International Classification||A61F2/04, A61L27/48, A61F2/06|
|Cooperative Classification||A61F2/06, A61L27/48, A61F2/04|
|European Classification||A61L27/48, A61F2/06, A61F2/04|