|Número de publicación||US3272204 A|
|Tipo de publicación||Concesión|
|Fecha de publicación||13 Sep 1966|
|Fecha de presentación||22 Sep 1965|
|Fecha de prioridad||22 Sep 1965|
|Número de publicación||US 3272204 A, US 3272204A, US-A-3272204, US3272204 A, US3272204A|
|Inventores||Artandi Charles, Bechtol Lavon Dee|
|Cesionario original||Ethicon Inc|
|Exportar cita||BiBTeX, EndNote, RefMan|
|Citas de patentes (12), Citada por (348), Clasificaciones (15)|
|Enlaces externos: USPTO, Cesión de USPTO, 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
|Patente citada||Fecha de presentación||Fecha de publicación||Solicitante||Título|
|US2072302 *||3 Mar 1932||2 Mar 1937||Chemische Forschungs Gmbh||Polymerized vinyl alcohol articles and processes of making same|
|US2127903 *||5 May 1936||23 Ago 1938||Davis & Geck Inc||Tube for surgical purposes and method of preparing and using the same|
|US2453056 *||12 Mar 1947||2 Nov 1948||Edwin Zack William||Surgical anastomosis apparatus and method|
|US2637321 *||27 Sep 1951||5 May 1953||American Cyanamid Co||Shaped article and method of producing it|
|US2671444 *||8 Dic 1951||9 Mar 1954||Pease Jr Benjamin F||Nonmetallic mesh surgical insert for hernia repair|
|US2731788 *||8 Oct 1949||24 Ene 1956||Cluett||Composite thread.|
|US2827359 *||22 Mar 1954||18 Mar 1958||Rohm & Haas||Process for stabilization of protein textiles with 4-vinyl pyridine copolymers and products produced therefrom|
|US2845959 *||26 Mar 1956||5 Ago 1958||Sidebotham John B||Bifurcated textile tubes and method of weaving the same|
|US2920000 *||22 Oct 1958||5 Ene 1960||Ethicon Inc Ethicon Inc||Removable valve Collagen article and the manufacture thereof|
|US2934447 *||22 Oct 1957||26 Abr 1960||United Shoe Machinery Corp||Collagen fiber masses and methods of making the same|
|US3011527 *||23 May 1957||5 Dic 1961||Rhodiaceta||Prosthesis consisting of textile materials|
|US3014024 *||19 Mar 1958||19 Dic 1961||Johnson & Johnson||Collagen film|
|Patente citante||Fecha de presentación||Fecha de publicación||Solicitante||Título|
|US3366440 *||3 Nov 1964||30 Ene 1968||Ethicon Inc||Process for manufacturing a collagen fabric-film laminate|
|US3400719 *||9 Jun 1964||10 Sep 1968||Albert O.L.J. Eckhart Buddecke||Plastic graft material and method of making same|
|US3408659 *||21 Jul 1965||5 Nov 1968||Thiele Heinrich||Artificial blood vessels and process of making same|
|US3425418 *||15 Abr 1964||4 Feb 1969||Spofa Vereinigte Pharma Werke||Artificial blood vessels and method of preparing the same|
|US3452366 *||21 Jun 1966||1 Jul 1969||Avco Corp||Percutaneous conduit and connector|
|US3463158 *||9 Ene 1967||26 Ago 1969||American Cyanamid Co||Polyglycolic acid prosthetic devices|
|US3479670 *||19 Oct 1966||25 Nov 1969||Ethicon Inc||Tubular prosthetic implant having helical thermoplastic wrapping therearound|
|US3491760 *||6 Jul 1966||27 Ene 1970||Braun Intern Gmbh B||Wound coverings|
|US3514791 *||25 Jul 1967||2 Jun 1970||Charles H Sparks||Tissue grafts|
|US3625198 *||9 May 1969||7 Dic 1971||Charles H Sparks||Die and holder for implanting in a living body to grow tissue grafts|
|US3862452 *||21 Jun 1971||28 Ene 1975||Ceskoslovenska Akademie Ved||Hydrogel substitutes for tubular somatic organs|
|US3918099 *||29 May 1974||11 Nov 1975||Fettback Helmut||Artificial organ or part or section thereof for implanation into the human body and method of producing the same|
|US4086665 *||16 Dic 1976||2 May 1978||Thermo Electron Corporation||Artificial blood conduit|
|US4130904 *||6 Jun 1977||26 Dic 1978||Thermo Electron Corporation||Prosthetic blood conduit|
|US4182339 *||17 May 1978||8 Ene 1980||Hardy Thomas G Jr||Anastomotic device and method|
|US4229838 *||3 Jul 1978||28 Oct 1980||Sumitomo Electric Industries, Ltd.||Vascular prosthesis having a composite structure|
|US4329743 *||27 Abr 1979||18 May 1982||College Of Medicine And Dentistry Of New Jersey||Bio-absorbable composite tissue scaffold|
|US4338926 *||21 Nov 1980||13 Jul 1982||Howmedica, Inc.||Bone fracture prosthesis with controlled stiffness|
|US4361552 *||26 Sep 1980||30 Nov 1982||Board Of Regents, The University Of Texas System||Wound dressing|
|US4365357 *||25 Abr 1980||28 Dic 1982||Merck Patent Gesellschaft Mit Beschrankter Haftung||Surgical materials suitable for use with bone cements|
|US4411027 *||23 Feb 1982||25 Oct 1983||University Of Medicine And Dentistry Of New Jersey||Bio-absorbable composite tissue scaffold|
|US4441215 *||23 Feb 1983||10 Abr 1984||Kaster Robert L||Vascular graft|
|US4457028 *||14 Oct 1982||3 Jul 1984||Merck Patent Gesellschaft Mit Beschrankter Haftung||Surgical materials suitable for use with bone cements|
|US4501263 *||31 Mar 1982||26 Feb 1985||Harbuck Stanley C||Method for reducing hypertension of a liver|
|US4512038 *||6 Abr 1981||23 Abr 1985||University Of Medicine And Dentistry Of New Jersey||Bio-absorbable composite tissue scaffold|
|US4550447 *||3 Ago 1983||5 Nov 1985||Shiley Incorporated||Vascular graft prosthesis|
|US4647416 *||26 Abr 1985||3 Mar 1987||Shiley Incorporated||Method of preparing a vascular graft prosthesis|
|US4662884 *||25 Abr 1984||5 May 1987||University Of Utah Research Foundation||Prostheses and methods for promoting nerve regeneration|
|US4670286 *||26 Dic 1985||2 Jun 1987||Allied Corporation||Method of forming prosthetic devices|
|US4778467 *||10 Jul 1986||18 Oct 1988||The University Of Utah||Prostheses and methods for promoting nerve regeneration and for inhibiting the formation of neuromas|
|US4787391 *||11 Ago 1987||29 Nov 1988||Elefteriades John A||Anastomotic marking device and related method|
|US4842575 *||5 Ago 1988||27 Jun 1989||Meadox Medicals, Inc.||Method for forming impregnated synthetic vascular grafts|
|US4865031 *||3 Oct 1988||12 Sep 1989||Keeffe Paul J O||Fabric and method of use for treatment of scars|
|US4871365 *||24 Dic 1986||3 Oct 1989||American Cyanamid Company||Partially absorbable prosthetic tubular article having an external support|
|US4915893 *||15 Jul 1983||10 Abr 1990||Medtronic, Inc.||Method of preparing polyester filament material|
|US4997440 *||10 Ago 1990||5 Mar 1991||American Cyanamid Company||Vascular graft with absorbable and nonabsorbable components|
|US5098779 *||25 Jun 1990||24 Mar 1992||W. L. Gore & Associates, Inc.||Carvable implant material|
|US5108424 *||28 Ene 1991||28 Abr 1992||Meadox Medicals, Inc.||Collagen-impregnated dacron graft|
|US5110852 *||27 Oct 1988||5 May 1992||Rijksuniversiteit Te Groningen||Filament material polylactide mixtures|
|US5141522 *||21 Ene 1992||25 Ago 1992||American Cyanamid Company||Composite material having absorbable and non-absorbable components for use with mammalian tissue|
|US5147374 *||5 Dic 1991||15 Sep 1992||Alfredo Fernandez||Prosthetic mesh patch for hernia repair|
|US5178630 *||26 May 1992||12 Ene 1993||Meadox Medicals, Inc.||Ravel-resistant, self-supporting woven graft|
|US5197977 *||30 Abr 1992||30 Mar 1993||Meadox Medicals, Inc.||Drug delivery collagen-impregnated synthetic vascular graft|
|US5201745 *||15 Ago 1991||13 Abr 1993||Imedex||Visceral surgery patch|
|US5207670 *||9 Dic 1991||4 May 1993||Rare Earth Medical, Inc.||Photoreactive suturing of biological materials|
|US5282823 *||19 Mar 1992||1 Feb 1994||Medtronic, Inc.||Intravascular radially expandable stent|
|US5282846 *||29 Abr 1992||1 Feb 1994||Meadox Medicals, Inc.||Ravel-resistant, self-supporting woven vascular graft|
|US5282848 *||19 Abr 1993||1 Feb 1994||Meadox Medicals, Inc.||Self-supporting woven vascular graft|
|US5282860 *||8 Oct 1992||1 Feb 1994||Olympus Optical Co., Ltd.||Stent tube for medical use|
|US5326355 *||24 Ago 1992||5 Jul 1994||American Cyanamid Company||Composite material having absorbable and nonabsorbable components for use with mammalian tissue|
|US5383925 *||14 Sep 1992||24 Ene 1995||Meadox Medicals, Inc.||Three-dimensional braided soft tissue prosthesis|
|US5385156 *||27 Ago 1993||31 Ene 1995||Rose Health Care Systems||Diagnostic and treatment method for cardiac rupture and apparatus for performing the same|
|US5385580 *||21 Sep 1992||31 Ene 1995||Meadox Medicals, Inc.||Self-supporting woven vascular graft|
|US5423849 *||15 Ene 1993||13 Jun 1995||Target Therapeutics, Inc.||Vasoocclusion device containing radiopaque fibers|
|US5443496 *||15 Oct 1993||22 Ago 1995||Medtronic, Inc.||Intravascular radially expandable stent|
|US5458636 *||20 Jul 1994||17 Oct 1995||U.S. Biomaterials Corporation||Prosthetic device for repair and replacement of fibrous connective tissue|
|US5487858 *||31 Ene 1994||30 Ene 1996||Meadox Medicals, Inc.||Process of making self-supporting woven vascular graft|
|US5496364 *||31 Ene 1994||5 Mar 1996||Meadox Medicals, Inc.||Self-supporting woven vascular graft|
|US5509931 *||28 Ene 1994||23 Abr 1996||Meadox Medicals, Inc.||Ravel-resistant self-supporting woven vascular graft|
|US5540677 *||24 Oct 1994||30 Jul 1996||Rare Earth Medical, Inc.||Endoscopic systems for photoreactive suturing of biological materials|
|US5542594 *||6 Oct 1993||6 Ago 1996||United States Surgical Corporation||Surgical stapling apparatus with biocompatible surgical fabric|
|US5562725 *||14 Sep 1992||8 Oct 1996||Meadox Medicals Inc.||Radially self-expanding implantable intraluminal device|
|US5562946 *||2 Nov 1994||8 Oct 1996||Tissue Engineering, Inc.||Apparatus and method for spinning and processing collagen fiber|
|US5569239 *||18 Ago 1994||29 Oct 1996||Rare Earth Medical, Inc.||Photoreactive suturing of biological materials|
|US5628788 *||7 Nov 1995||13 May 1997||Corvita Corporation||Self-expanding endoluminal stent-graft|
|US5651174 *||27 Abr 1995||29 Jul 1997||Medtronic, Inc.||Intravascular radially expandable stent|
|US5665114 *||12 Ago 1994||9 Sep 1997||Meadox Medicals, Inc.||Tubular expanded polytetrafluoroethylene implantable prostheses|
|US5693085 *||26 Abr 1995||2 Dic 1997||Scimed Life Systems, Inc.||Stent with collagen|
|US5697969 *||20 Sep 1995||16 Dic 1997||Meadox Medicals, Inc.||Vascular prosthesis and method of implanting|
|US5700269 *||13 Nov 1995||23 Dic 1997||Corvita Corporation||Endoluminal prosthesis deployment device for use with prostheses of variable length and having retraction ability|
|US5716660 *||31 May 1995||10 Feb 1998||Meadox Medicals, Inc.||Tubular polytetrafluoroethylene implantable prostheses|
|US5725522 *||7 Jun 1995||10 Mar 1998||Rare Earth Medical, Inc.||Laser suturing of biological materials|
|US5741332 *||19 Oct 1995||21 Abr 1998||Meadox Medicals, Inc.||Three-dimensional braided soft tissue prosthesis|
|US5741333 *||3 Abr 1996||21 Abr 1998||Corvita Corporation||Self-expanding stent for a medical device to be introduced into a cavity of a body|
|US5800541 *||8 Ene 1997||1 Sep 1998||Collagen Corporation||Collagen-synthetic polymer matrices prepared using a multiple step reaction|
|US5824034 *||5 Jun 1995||20 Oct 1998||Meadox Medicals, Inc.||Method for repositioning a radially self-expanding implantable intraluminal device|
|US5849037 *||3 Abr 1996||15 Dic 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 *||18 Oct 1996||22 Dic 1998||Meadox Medicals, Inc.||Vascular graft with a heparin-containing collagen sealant|
|US5851290 *||22 May 1996||22 Dic 1998||Tissue Engineering, Inc.||Apparatus for spinning and processing collagen fiber|
|US5908427 *||30 May 1997||1 Jun 1999||United States Surgical Corporation||Surgical stapling apparatus and method|
|US5911942 *||2 Nov 1995||15 Jun 1999||Tissue Engineering, Inc.||Method for spinning and processing collagen fiber|
|US5913894 *||20 Oct 1995||22 Jun 1999||Meadox Medicals, Inc.||Solid woven tubular prosthesis|
|US5964774 *||12 Sep 1997||12 Oct 1999||United States Surgical Corporation||Surgical stapling apparatus and method with surgical fabric|
|US5968091 *||26 Nov 1997||19 Oct 1999||Corvita Corp.||Stents and stent grafts having enhanced hoop strength and methods of making the same|
|US5972007 *||31 Oct 1997||26 Oct 1999||Ethicon Endo-Surgery, Inc.||Energy-base method applied to prosthetics for repairing tissue defects|
|US6042592 *||4 Ago 1997||28 Mar 2000||Meadox Medicals, Inc.||Thin soft tissue support mesh|
|US6045560 *||17 Jun 1996||4 Abr 2000||United States Surgical Corporation||Surgical stapling apparatus with biocompatible surgical fabric|
|US6090137 *||5 Feb 1999||18 Jul 2000||Meadox Medicals, Inc.||Solid woven tubular prosthesis methods|
|US6090996 *||4 Ago 1997||18 Jul 2000||Collagen Matrix, Inc.||Implant matrix|
|US6120539 *||1 May 1997||19 Sep 2000||C. R. Bard Inc.||Prosthetic repair fabric|
|US6162247 *||21 Dic 1998||19 Dic 2000||Meadox Medicals, Inc.||Vascular graft impregnated with a heparin-containing collagen sealant|
|US6177609 *||10 Mar 1997||23 Ene 2001||Meadox Medicals, Inc.||Self-aggregating protein compositions and use as sealants|
|US6197296||29 Mar 1994||6 Mar 2001||National Heart Research Fund||Tissue equivalents|
|US6228111||27 Sep 1996||8 May 2001||Bionx Implants Oy||Biodegradable implant manufactured of polymer-based material and a method for manufacturing the same|
|US6237460||30 Abr 1998||29 May 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||31 Mar 1999||26 Jun 2001||Ethicon Endo-Surgery, Inc.||Combined radio frequency and ultrasonic surgical device|
|US6257241||31 Mar 1999||10 Jul 2001||Ethicon Endo-Surgery, Inc.||Method for repairing tissue defects using ultrasonic radio frequency energy|
|US6258124||10 May 1999||10 Jul 2001||C. R. Bard, Inc.||Prosthetic repair fabric|
|US6270530||9 Jun 2000||7 Ago 2001||C.R. Bard, Inc.||Prosthetic repair fabric|
|US6273897||29 Feb 2000||14 Ago 2001||Ethicon, Inc.||Surgical bettress and surgical stapling apparatus|
|US6287344||31 Mar 1999||11 Sep 2001||Ethicon Endo-Surgery, Inc.||Method for repairing tissue defects using an ultrasonic device|
|US6296645||9 Abr 1999||2 Oct 2001||Depuy Orthopaedics, Inc.||Intramedullary nail with non-metal spacers|
|US6325810||30 Jun 1999||4 Dic 2001||Ethicon, Inc.||Foam buttress for stapling apparatus|
|US6334872 *||7 Jul 1997||1 Ene 2002||Organogenesis Inc.||Method for treating diseased or damaged organs|
|US6348065||24 Jul 1998||19 Feb 2002||Scimed Life Systems, Inc.||Longitudinally flexible expandable stent|
|US6350277||15 Ene 1999||26 Feb 2002||Scimed Life Systems, Inc.||Stents with temporary retaining bands|
|US6368347 *||23 Abr 1999||9 Abr 2002||Sulzer Vascutek Ltd.||Expanded polytetrafluoroethylene vascular graft with coating|
|US6375662||23 Nov 1999||23 Abr 2002||Scimed Life Systems, Inc.||Thin soft tissue surgical support mesh|
|US6391052||29 Oct 1997||21 May 2002||Scimed Life Systems, Inc.||Stent with collagen|
|US6416486||31 Mar 1999||9 Jul 2002||Ethicon Endo-Surgery, Inc.||Ultrasonic surgical device having an embedding surface and a coagulating surface|
|US6488705||18 Sep 2001||3 Dic 2002||Meadox Medicals, Inc.||Radially self-expanding implantable intraluminal device|
|US6497650||28 Jul 2000||24 Dic 2002||C. R. Bard, Inc.||Hernia prosthesis|
|US6524345||22 Oct 1997||25 Feb 2003||Bionx Implants Oy||Surgical implant|
|US6572650||4 Jun 1999||3 Jun 2003||Organogenesis Inc.||Bioengineered vascular graft support prostheses|
|US6652595||9 Ene 1998||25 Nov 2003||Davol Inc.||Method of repairing inguinal hernias|
|US6669706||18 Dic 2001||30 Dic 2003||Scimed Life Systems, Inc.||Thin soft tissue surgical support mesh|
|US6709436||22 May 2000||23 Mar 2004||Depuy Orthopaedics, Inc.||Non-metal spacers for intramedullary nail|
|US6726664 *||6 Ago 2001||27 Abr 2004||Optonol Ltd.||Flow control device, introducer and method of implanting|
|US6770088||18 May 2000||3 Ago 2004||Scimed Life Systems, Inc.||Intravascular stent|
|US6783529||19 Oct 2001||31 Ago 2004||Depuy Orthopaedics, Inc.||Non-metal inserts for bone support assembly|
|US6786908||2 Ago 2001||7 Sep 2004||Depuy Orthopaedics, Inc.||Bone fracture support implant with non-metal spacers|
|US6790213||7 Ene 2002||14 Sep 2004||C.R. Bard, Inc.||Implantable prosthesis|
|US6808527||25 Mar 2002||26 Oct 2004||Depuy Orthopaedics, Inc.||Intramedullary nail with snap-in window insert|
|US6818014||3 Ago 1995||16 Nov 2004||Scimed Life Systems, Inc.||Longitudinally flexible expandable stent|
|US6827743 *||25 Feb 2002||7 Dic 2004||Sdgi Holdings, Inc.||Woven orthopedic implants|
|US6846323||15 May 2003||25 Ene 2005||Advanced Cardiovascular Systems, Inc.||Intravascular stent|
|US6890351 *||7 Sep 2001||10 May 2005||Organogenesis Inc.||Method for treating diseased or damaged organs|
|US6913619||11 Jul 2002||5 Jul 2005||Boston Scientific Scimed, Inc.||Longitudinally flexible expandable stent|
|US6929659||25 Feb 2002||16 Ago 2005||Scimed Life Systems, Inc.||Method of preventing the dislodgment of a stent-graft|
|US6962603||22 Jun 2000||8 Nov 2005||Boston Scientific Scimed, Inc.||Longitudinally flexible expandable stent|
|US6976952||25 Abr 2000||20 Dic 2005||Vascutek Limited||Expanded polytetrafluoroethylene vascular graft with coating|
|US6981986||20 Sep 2000||3 Ene 2006||Boston Scientific Scimed, Inc.||Longitudinally flexible expandable stent|
|US6986735||3 Mar 2003||17 Ene 2006||Organogenesis Inc.||Method of making a bioremodelable vascular graft prosthesis|
|US7022132||26 Feb 2002||4 Abr 2006||Boston Scientific Scimed, Inc.||Stents with temporary retaining bands|
|US7041131||11 Abr 2003||9 May 2006||Organogenesis, Inc.||Bioengineered vascular graft support prostheses|
|US7044982||27 Ago 2001||16 May 2006||Michael Milbocker||Surgical repair of tissue defects|
|US7060103||28 Feb 2003||13 Jun 2006||Organogenesis Inc.||Tissue repair fabric|
|US7081130||16 Abr 2002||25 Jul 2006||Boston Scientific Scimed, Inc.||Intravascular Stent|
|US7121999||3 Mar 2003||17 Oct 2006||Organogenesis Inc.||Method of preparing layered graft prostheses|
|US7156804||2 Dic 2002||2 Ene 2007||Davol, Inc.||Hernia prosthesis|
|US7160333||5 Sep 2003||9 Ene 2007||Depuy Orthopaedics, Inc.||Reinforced small intestinal submucosa|
|US7163563||15 Jul 2002||16 Ene 2007||Depuy Products, Inc.||Unitary surgical device and method|
|US7201917||15 Jul 2002||10 Abr 2007||Depuy Products, Inc.||Porous delivery scaffold and method|
|US7204848||20 Nov 1998||17 Abr 2007||Boston Scientific Scimed, Inc.||Longitudinally flexible expandable stent|
|US7214242||3 Mar 2003||8 May 2007||Organogenesis, Inc.||Bioengineered tubular graft prostheses|
|US7326241||9 Ago 2001||5 Feb 2008||Boston Scientific Scimed, Inc.||Intravascular stent|
|US7341601||28 Jul 2004||11 Mar 2008||Warsaw Orthopedic, Inc.||Woven orthopedic implants|
|US7354627||22 Dic 2004||8 Abr 2008||Depuy Products, Inc.||Method for organizing the assembly of collagen fibers and compositions formed therefrom|
|US7404819||14 Sep 2000||29 Jul 2008||C.R. Bard, Inc.||Implantable prosthesis|
|US7410488||18 Feb 2005||12 Ago 2008||Smith & Nephew, Inc.||Hindfoot nail|
|US7468210||10 Dic 2003||23 Dic 2008||Biosurface Engineering Technologies, Inc.||Cross-linked heparin coatings and methods|
|US7481816||27 Oct 2003||27 Ene 2009||Optonol Ltd.||Intraocular implant, delivery device, and method of implantation|
|US7513865||20 Dic 2005||7 Abr 2009||Boston Scientific Scimed, Inc.||Flattened tubular mesh sling and related methods|
|US7513866||29 Oct 2004||7 Abr 2009||Depuy Products, Inc.||Intestine processing device and associated method|
|US7569233||20 Abr 2005||4 Ago 2009||Depuy Products, Inc.||Hybrid biologic-synthetic bioabsorbable scaffolds|
|US7585319 *||27 Sep 2004||8 Sep 2009||Maquet Cardiovascular, Llc||Self-aggregating protein compositions and use as sealants|
|US7595062||28 Jul 2005||29 Sep 2009||Depuy Products, Inc.||Joint resurfacing orthopaedic implant and associated method|
|US7614258||19 Oct 2006||10 Nov 2009||C.R. Bard, Inc.||Prosthetic repair fabric|
|US7655009||30 Nov 2004||2 Feb 2010||Smith & Nephew, Inc.||Humeral nail|
|US7670310||7 Dic 2007||2 Mar 2010||Optonol Ltd||Flow regulating implants|
|US7682392||30 Oct 2002||23 Mar 2010||Depuy Spine, Inc.||Regenerative implants for stabilizing the spine and devices for attachment of said implants|
|US7700563||19 Ago 2003||20 Abr 2010||Biosurface Engineering Technologies, Inc.||Synthetic heparin-binding factor analogs|
|US7766956||26 Nov 2003||3 Ago 2010||Boston Scientific Scimed, Inc.||Intravascular stent and assembly|
|US7799089||10 Oct 2006||21 Sep 2010||Depuy Orthopaedics, Inc.||Reinforced small intestinal submucosa|
|US7815562||11 Ago 2005||19 Oct 2010||Boston Scientific Scimed, Inc.||Tubular implantable sling and related delivery systems, methods and devices|
|US7819918 *||29 Dic 2003||26 Oct 2010||Depuy Products, Inc.||Implantable tissue repair device|
|US7820172||1 Jun 2007||26 Oct 2010||Biosurface Engineering Technologies, Inc.||Laminin-derived multi-domain peptides|
|US7824420||26 May 2004||2 Nov 2010||C.R. Bard, Inc.||Implantable prosthesis|
|US7824701||25 Feb 2003||2 Nov 2010||Ethicon, Inc.||Biocompatible scaffold for ligament or tendon repair|
|US7862531||25 Jun 2004||4 Ene 2011||Optonol Ltd.||Flow regulating implants|
|US7871440||11 Dic 2006||18 Ene 2011||Depuy Products, Inc.||Unitary surgical device and method|
|US7875296||29 Nov 2007||25 Ene 2011||Depuy Mitek, Inc.||Conformable tissue repair implant capable of injection delivery|
|US7900484||5 Nov 2009||8 Mar 2011||C.R. Bard, Inc.||Prosthetic repair fabric|
|US7901461||5 Dic 2003||8 Mar 2011||Ethicon, Inc.||Viable tissue repair implants and methods of use|
|US7909886||24 Mar 2006||22 Mar 2011||Organogenesis, Inc.||Tissue repair fabric|
|US7914808 *||15 Jul 2002||29 Mar 2011||Depuy Products, Inc.||Hybrid biologic/synthetic porous extracellular matrix scaffolds|
|US7927619||26 Abr 2006||19 Abr 2011||Promethean Surgical Devices Llc||In situ bulking composition|
|US7981862||22 Jun 2007||19 Jul 2011||Biosurface Engineering Technologies, Inc.||Composition comprising BMP-2 amplifier/co-activator for enhancement of osteogenesis|
|US7988717||10 Nov 2003||2 Ago 2011||Boston Scientific Scimed, Inc.||Longitudinally flexible expandable stent|
|US7988720||20 Jul 2007||2 Ago 2011||Boston Scientific Scimed, Inc.||Longitudinally flexible expandable stent|
|US8012205 *||15 Jul 2002||6 Sep 2011||Depuy Products, Inc.||Cartilage repair and regeneration device|
|US8016867||28 Oct 2004||13 Sep 2011||Depuy Mitek, Inc.||Graft fixation device and method|
|US8021414||25 Jul 2002||20 Sep 2011||Boston Scientific Scimed, Inc.||Intravascular stent|
|US8025896||15 Jul 2002||27 Sep 2011||Depuy Products, Inc.||Porous extracellular matrix scaffold and method|
|US8034016||7 Dic 2007||11 Oct 2011||Optonol, Ltd.||Flow regulating implants and methods of implanting|
|US8070792||28 Mar 2002||6 Dic 2011||Boston Scientific Scimed, Inc.||Stent|
|US8092529||15 Jul 2002||10 Ene 2012||Depuy Products, Inc.||Meniscus regeneration device|
|US8101570||24 May 2010||24 Ene 2012||Biosurface Engineering Technologies, Inc.||Single branch heparin-binding growth factor analogs|
|US8109896||11 Feb 2008||7 Feb 2012||Optonol Ltd.||Devices and methods for opening fluid passageways|
|US8114146||15 Mar 2004||14 Feb 2012||Boston Scientific Scimed, Inc.||Longitudinally flexible expandable stent|
|US8137686||20 Abr 2004||20 Mar 2012||Depuy Mitek, Inc.||Nonwoven tissue scaffold|
|US8137702||29 Dic 2010||20 Mar 2012||Depuy Mitek, Inc.||Conformable tissue repair implant capable of injection delivery|
|US8142489||5 Sep 2008||27 Mar 2012||Boston Scientific Scimed, Inc.||Flexible and expandable stent|
|US8163717||6 Oct 2009||24 Abr 2012||Biosurface Engineering Technologies, Inc.||Dual chain synthetic heparin-binding growth factor analogs|
|US8182545||10 Jul 2008||22 May 2012||C.R. Bard, Inc.||Implantable prosthesis|
|US8192763||23 Jul 2008||5 Jun 2012||Cook Biotech Incorporated||Processed ECM materials with enhanced component profiles|
|US8221780||29 Jun 2006||17 Jul 2012||Depuy Mitek, Inc.||Nonwoven tissue scaffold|
|US8226715||30 Jun 2003||24 Jul 2012||Depuy Mitek, Inc.||Scaffold for connective tissue repair|
|US8227411||23 Feb 2006||24 Jul 2012||BioSurface Engineering Technologies, Incle||FGF growth factor analogs|
|US8231930 *||4 Ago 2009||31 Jul 2012||Maquet Cardiovascular, Llc||Self-aggregating protein compositions and use as sealants|
|US8282542||24 Feb 2009||9 Oct 2012||Boston Scientific Scimed, Inc.||Flattened tubular mesh sling and related methods|
|US8313454||26 Mar 2010||20 Nov 2012||Optonol Ltd.||Fluid drainage device, delivery device, and associated methods of use and manufacture|
|US8337537||15 Jul 2002||25 Dic 2012||Depuy Products, Inc.||Device from naturally occurring biologically derived materials|
|US8348992||21 Ago 2001||8 Ene 2013||Boston Scientific Scimed, Inc.||Longitudinally flexible expandable stent|
|US8366787||14 Jun 2002||5 Feb 2013||Depuy Products, Inc.||Hybrid biologic-synthetic bioabsorbable scaffolds|
|US8449561||15 Feb 2007||28 May 2013||Depuy Mitek, Llc||Graft fixation device combination|
|US8449597||21 Nov 2011||28 May 2013||Boston Scientific Scimed, Inc.||Longitudinally flexible expandable stent|
|US8486086||7 Nov 2011||16 Jul 2013||Optonol, Ltd||Flow regulating implant, method of manufacture, and delivery device|
|US8496970||27 Feb 2012||30 Jul 2013||Depuy Mitek, Llc||Conformable tissue repair implant capable of injection delivery|
|US8541372||3 Ene 2011||24 Sep 2013||Cook Biotech Incorporated||Isolated extracellular matrix material including subserous fascia|
|US8562665||17 Dic 2002||22 Oct 2013||Boston Scientific Scimed, Inc.||Tubular stent consists of chevron-shape expansion struts and contralaterally attached diagonal-connectors|
|US8591930||28 Abr 2008||26 Nov 2013||Cook Biotech Incorporated||Growth factor modified extracellular matrix material preparation and methods for preparation and use thereof|
|US8617206||4 Oct 2010||31 Dic 2013||Covidien Lp||Wound closure device|
|US8628464||2 Oct 2012||14 Ene 2014||Boston Scientific Scimed, Inc.||Flattened tubular mesh sling and related methods|
|US8637066||21 Sep 2010||28 Ene 2014||Depuy Mitek, Llc||Biocompatible scaffold for ligament or tendon repair|
|US8641775||1 Feb 2011||4 Feb 2014||Depuy Mitek, Llc||Viable tissue repair implants and methods of use|
|US8663086||28 Sep 2010||4 Mar 2014||Cook Biotech Incorporated||Medical reinforcement graft|
|US8663313||22 Sep 2011||4 Mar 2014||Boston Scientific Scimed, Inc.||Low strain high strength stent|
|US8691259||16 Nov 2005||8 Abr 2014||Depuy Mitek, Llc||Reinforced foam implants with enhanced integrity for soft tissue repair and regeneration|
|US8728147||20 Dic 2011||20 May 2014||Boston Scientific Limited||Longitudinally flexible expandable stent|
|US8790388||2 Mar 2012||29 Jul 2014||Boston Scientific Scimed, Inc.||Stent with reduced profile|
|US8795384||10 Ene 2008||5 Ago 2014||Cook Biotech Incorporated||Implantable devices useful for reinforcing a surgically created stoma|
|US8796212||19 Jul 2011||5 Ago 2014||Biosurface Engineering Technologies, Inc.||Composition and method for delivery of BMP-2 amplifier/co-activator for enhancement of osteogenesis|
|US8801773||26 Mar 2012||12 Ago 2014||Boston Scientific Scimed, Inc.||Flexible and expandable stent|
|US8895045||8 May 2012||25 Nov 2014||Depuy Mitek, Llc||Method of preparation of bioabsorbable porous reinforced tissue implants and implants thereof|
|US8956378||27 Feb 2009||17 Feb 2015||Cook Biotech Incorporated||Coated embolization device|
|US9044455||26 Jul 2013||2 Jun 2015||Cook Biotech Incorporated||Isolated extracellular matrix material including subserous fascia|
|US9072586||2 Oct 2009||7 Jul 2015||C.R. Bard, Inc.||Implantable prosthesis|
|US9078778||14 Sep 2011||14 Jul 2015||Boston Scientific Scimed, Inc.||Intravascular stent|
|US9173774||11 Sep 2012||3 Nov 2015||Optonol Ltd.||Fluid drainage device, delivery device, and associated methods of use and manufacture|
|US9180145||9 Oct 2013||10 Nov 2015||Mimedx Group, Inc.||Compositions and methods for recruiting and localizing stem cells|
|US9186053 *||11 Abr 2013||17 Nov 2015||Covidien Lp||Methods of using light to repair hernia defects|
|US9211362||8 Jun 2012||15 Dic 2015||Depuy Mitek, Llc||Scaffold for connective tissue repair|
|US9308068 *||2 Dic 2008||12 Abr 2016||Sofradim Production||Implant for parastomal hernia|
|US9445883||27 Dic 2012||20 Sep 2016||Sofradim Production||Barbed prosthetic knit and hernia repair mesh made therefrom as well as process for making said prosthetic knit|
|US9445926||15 Ago 2008||20 Sep 2016||Boston Scientific Scimed, Inc.||Intravascular stent|
|US9468708 *||28 Oct 2010||18 Oct 2016||Biom'up||Composite matrix|
|US9499927||25 Sep 2013||22 Nov 2016||Sofradim Production||Method for producing a prosthesis for reinforcing the abdominal wall|
|US9511171||22 Nov 2010||6 Dic 2016||Depuy Mitek, Llc||Biocompatible scaffolds with tissue fragments|
|US9526603||1 Oct 2012||27 Dic 2016||Covidien Lp||Reversible stiffening of light weight mesh|
|US9554887||16 Mar 2012||31 Ene 2017||Sofradim Production||Prosthesis comprising a three-dimensional and openworked knit|
|US9622843||29 Jun 2012||18 Abr 2017||Sofradim Production||Umbilical hernia prosthesis|
|US9662355||17 Ene 2014||30 May 2017||Mimedx Group, Inc.||Methods for treating cardiac conditions|
|US9670258||18 Ago 2016||6 Jun 2017||Ferring B.V.||Positive modulator of bone morphogenic protein-2|
|US9750837||25 Sep 2013||5 Sep 2017||Sofradim Production||Haemostatic patch and method of preparation|
|US20020049503 *||27 Ago 2001||25 Abr 2002||Michael Milbocker||Surgical repair of tissue defects|
|US20020095208 *||28 Mar 2002||18 Jul 2002||Scimed Life Systems, Inc.||Stent|
|US20020103542 *||18 Sep 2001||1 Ago 2002||Bilbo Patrick R.||Methods for treating a patient using a bioengineered flat sheet graft prostheses|
|US20020116049 *||9 Ene 2002||22 Ago 2002||Scimed Life Systems, Inc.||Stent|
|US20020123750 *||25 Feb 2002||5 Sep 2002||Lukas Eisermann||Woven orthopedic implants|
|US20030023316 *||14 Jun 2002||30 Ene 2003||Brown Laura Jean||Hybrid biologic-synthetic bioabsorable scaffolds|
|US20030033021 *||15 Jul 2002||13 Feb 2003||Plouhar Pamela Lynn||Cartilage repair and regeneration scaffold and method|
|US20030079329 *||9 Dic 2002||1 May 2003||Ira Yaron||Flow regulating implant, method of manufacture, and delivery device|
|US20030083736 *||3 Ago 1995||1 May 2003||Brian J. Brown||Longitudinally flexible expandable stent|
|US20030130747 *||3 Mar 2003||10 Jul 2003||Organogenesis, Inc.||Bioengineered flat sheet graft prostheses|
|US20030149472 *||7 Mar 2003||7 Ago 2003||Leonard Pinchuk||Modular endluminal stent-grafts and methods for their use|
|US20030158607 *||28 Feb 2003||21 Ago 2003||Carr Robert M.||Tissue repair fabric|
|US20030167088 *||3 Mar 2003||4 Sep 2003||Organogenesis, Inc.||Bioengineered vascular graft prostheses|
|US20030171824 *||3 Mar 2003||11 Sep 2003||Organogenesis, Inc.||Bioengineered tubular graft prostheses|
|US20030195618 *||11 Abr 2003||16 Oct 2003||Organogenesis, Inc.||Bioengineered vascular graft support prostheses|
|US20040059431 *||5 Sep 2003||25 Mar 2004||Plouhar Pamela L.||Reinforced small intestinal submucosa|
|US20040087505 *||19 Ago 2003||6 May 2004||Pena Louis A.||Synthetic heparin-binding factor analogs|
|US20040088048 *||27 Oct 2003||6 May 2004||Jacob Richter||Intraocular implant, delivery device, and method of implantation|
|US20040176834 *||15 Mar 2004||9 Sep 2004||Brown Brian J.||Longitudinally flexible expandable stent|
|US20040220574 *||15 Jul 2002||4 Nov 2004||Pelo Mark Joseph||Device from naturally occuring biologically derived materials|
|US20040230288 *||17 Abr 2002||18 Nov 2004||Rosenthal Arthur L.||Medical devices adapted for controlled in vivo structural change after implantation|
|US20050038520 *||11 Ago 2003||17 Feb 2005||Francois Binette||Method and apparatus for resurfacing an articular surface|
|US20050043733 *||28 Jul 2004||24 Feb 2005||Lukas Eisermann||Woven orthopedic implants|
|US20050085901 *||27 Sep 2004||21 Abr 2005||Dan Castro||Self-aggregating protein compostions and use as sealants|
|US20050125077 *||5 Dic 2003||9 Jun 2005||Harmon Alexander M.||Viable tissue repair implants and methods of use|
|US20050182484 *||12 Feb 2004||18 Ago 2005||Patel Umesh H.||Hybrid grafts|
|US20050192600 *||24 Feb 2005||1 Sep 2005||Enrico Nicolo||Inguinal hernia repair prosthetic|
|US20050232967||20 Abr 2004||20 Oct 2005||Kladakis Stephanie M||Nonwoven tissue scaffold|
|US20060034943 *||11 Oct 2005||16 Feb 2006||Technology Innovations Llc||Process for treating a biological organism|
|US20060100717 *||23 Nov 2005||11 May 2006||Organogenesis, Inc.||Bioengineered vascular graft prostheses|
|US20060147371 *||23 Feb 2005||6 Jul 2006||Tuszynski Jack A||Water-soluble compound|
|US20060198816 *||26 Abr 2006||7 Sep 2006||Milbocker Michael T||In situ bulking composition|
|US20060199764 *||23 Feb 2006||7 Sep 2006||Biosurface Engineering Technologies, Inc.||FGF growth factor analogs|
|US20070038017 *||11 Ago 2005||15 Feb 2007||Boston Scientific Scimed, Inc.||Tubular implantable sling and related delivery systems, methods and devices|
|US20070112360 *||15 Nov 2005||17 May 2007||Patrick De Deyne||Bioprosthetic device|
|US20070135906 *||5 Oct 2006||14 Jun 2007||Badylak Stephen F||Stent with collagen|
|US20070150059 *||22 Dic 2005||28 Jun 2007||Depuy Spine, Inc.||Methods and devices for intervertebral augmentation using injectable formulations and enclosures|
|US20070150063 *||22 Dic 2005||28 Jun 2007||Depuy Spine, Inc.||Devices for intervertebral augmentation and methods of controlling their delivery|
|US20070150064 *||22 Dic 2005||28 Jun 2007||Depuy Spine, Inc.||Methods and devices for intervertebral augmentation|
|US20080063622 *||22 Jun 2007||13 Mar 2008||Biosurface Engineering Technologies, Inc.||Composition and Method for Delivery of BMP-2 Amplifier/Co-Activator for Enhancement of Osteogenesis|
|US20080071385 *||29 Nov 2007||20 Mar 2008||Depuy Mitek, Inc.||Conformable tissue repair implant capable of injection delivery|
|US20080125691 *||7 Dic 2007||29 May 2008||Optonol Ltd.||Flow regulating implants|
|US20080160169 *||21 Dic 2007||3 Jul 2008||Zamora Paul O||Coating device and method for coating medical device with bioactive peptide|
|US20080166392 *||31 Ene 2008||10 Jul 2008||Zamora Paul O||Positive Modulator of Bone Morphogenic Protein-2|
|US20080167729 *||10 Ene 2008||10 Jul 2008||Nelson Christopher M||Implantable devices useful for reinforcing a surgically created stoma|
|US20080227696 *||21 Feb 2006||18 Sep 2008||Biosurface Engineering Technologies, Inc.||Single branch heparin-binding growth factor analogs|
|US20080286268 *||23 Jul 2008||20 Nov 2008||Johnson Chad E||Processed ecm materials with enhanced component profiles|
|US20080299171 *||28 Abr 2008||4 Dic 2008||Hiles Michael C||Growth factor modified extracellular matrix material and methods for preparation and use thereof|
|US20080319531 *||5 Sep 2008||25 Dic 2008||Boston Scientific Scimed, Inc.||Flexible and expandable stent|
|US20090036996 *||3 Ago 2007||5 Feb 2009||Roeber Peter J||Knit PTFE Articles and Mesh|
|US20090105753 *||26 Ago 2005||23 Abr 2009||Prodesco, Inc.||Sutures and methods of making the same|
|US20090112236 *||15 Oct 2008||30 Abr 2009||Tyco Healthcare Group Lp||Filament-Reinforced Composite Fiber|
|US20090142400 *||30 May 2008||4 Jun 2009||Hiles Michael C||Analgesic coated medical product|
|US20090156893 *||24 Feb 2009||18 Jun 2009||Boston Scientific Scimed, Inc.||Flattened tubular mesh sling and related methods|
|US20090187197 *||1 Ago 2008||23 Jul 2009||Roeber Peter J||Knit PTFE Articles and Mesh|
|US20090192528 *||29 Ene 2008||30 Jul 2009||Biomet Biologics, Inc.||Method and device for hernia repair|
|US20090204053 *||11 Feb 2008||13 Ago 2009||Optonol Ltd.||Devices and methods for opening fluid passageways|
|US20090270978 *||27 Feb 2009||29 Oct 2009||Virkler Joel A||Coated embolization device|
|US20090297692 *||4 Ago 2009||3 Dic 2009||Maquet Cardiovascular, Llc||Self-aggregating protein compositions and use as sealants|
|US20100015868 *||2 Jul 2009||21 Ene 2010||Philippe Gravagna||Reinforced composite implant|
|US20100174253 *||11 Jun 2008||8 Jul 2010||Convatec Technologies Inc.||Ostomy Appliance|
|US20100198236 *||2 Feb 2010||5 Ago 2010||Ralph Zipper||Surgical Meshes and Methods of Use|
|US20100203023 *||16 Abr 2010||12 Ago 2010||Johnson Chad E||Enhanced compositions containing cells and extracellular matrix materials|
|US20100274259 *||26 Mar 2010||28 Oct 2010||Optonol Ltd.||Fluid drainage device, delivery device, and associated methods of use and manufacture|
|US20100298218 *||24 May 2010||25 Nov 2010||Biosurface Engineering Technologies, Inc.||Single Branch Heparin-Binding Growth Factor Analogs|
|US20110077455 *||28 Sep 2010||31 Mar 2011||Mark Duncan||Medical reinforcement graft|
|US20110087271 *||4 Oct 2010||14 Abr 2011||Timothy Sargeant||Wound Closure Device|
|US20110087272 *||4 Oct 2010||14 Abr 2011||Timothy Sargeant||Wound Closure Device|
|US20110087273 *||4 Oct 2010||14 Abr 2011||Tyco Healthcare Group Lp||Wound Closure Device|
|US20110087274 *||4 Oct 2010||14 Abr 2011||Tyco Healtcare Group LP, New Haven, Ct||Wound Closure Device|
|US20110135700 *||31 Ene 2011||9 Jun 2011||Promethean Surgical Devices, Inc.||In situ bulking composition|
|US20110152196 *||3 Ene 2011||23 Jun 2011||Bhavin Shah||Isolated extracellular matrix material including subserous fascia|
|US20120253473 *||28 Oct 2010||4 Oct 2012||Biom'up||Composite matrix|
|US20130296657 *||11 Abr 2013||7 Nov 2013||Covidien Lp||Methods of using light to repair hernia defects|
|US20140067058 *||14 Ago 2013||6 Mar 2014||Mimedx Group, Inc.||Reinforced placental tissue grafts and methods of making and using the same|
|USRE44501||12 Ago 2010||17 Sep 2013||Smith & Nephew, Inc.||Hindfoot nail|
|USRE46008||13 Sep 2012||24 May 2016||Smith & Nephew, Inc.||Hindfoot nail|
|USRE46078||30 May 2012||26 Jul 2016||Smith & Nephew, Inc.||Hindfoot nail|
|CN102781490A *||28 Oct 2010||14 Nov 2012||比奥马普公司||Composite matrix|
|DE3503126A1 *||30 Ene 1985||1 Ago 1985||Meadox Medicals Inc||Arzneimittel abgebender kollagenbeschichteter synthetischer gefaessersatz|
|DE3503127A1 *||30 Ene 1985||1 Ago 1985||Meadox Medicals Inc||Kollagenbeschichteter synthetischer gefaessersatz|
|DE4128611A1 *||28 Ago 1991||5 Mar 1992||Meadox Medicals Inc||Ausfransfestes, selbsttragendes, gewobenes gefaessimplantat|
|DE4128611C3 *||28 Ago 1991||18 Abr 2002||Meadox Medicals Inc||Ausfransfestes, selbsttragendes, gewobenes Gefäßimplantat und Verfahren zu seiner Herstellung|
|EP0103005A1 *||16 Feb 1983||21 Mar 1984||SCHENCK, Robert R.||Method and apparatus for anastomosing blood vessels|
|EP0103005A4 *||16 Feb 1983||24 Oct 1985||Robert R Schenck||Method and apparatus for anastomosing blood vessels.|
|EP0129428A2 *||15 Jun 1984||27 Dic 1984||Robert Roy Schenk||Devices for joining anatomical structures|
|EP0129428A3 *||15 Jun 1984||15 Ene 1986||Robert Roy Schenk||Devices for joining anatomical structures|
|EP0466105A2 *||9 Jul 1991||15 Ene 1992||Corvita Corporation||Composite biosynthetic graft|
|EP0466105A3 *||9 Jul 1991||17 Mar 1993||Corvita Corporation||Composite biosynthetic graft|
|EP0587461A2 *||14 Jun 1993||16 Mar 1994||Terumo Kabushiki Kaisha||Artificial blood vessel|
|EP0587461A3 *||14 Jun 1993||18 May 1994||Terumo Corp||Artificial blood vessel|
|EP0943345A1 *||19 Nov 1997||22 Sep 1999||SHIMIZU, Yasuhiko||Artificial esophagus|
|EP0943345A4 *||19 Nov 1997||27 Dic 2000||Tapic Int Co Ltd||Artificial esophagus|
|WO1982001647A1 *||30 Oct 1981||27 May 1982||Robert L Kaster||Vascular graft|
|WO1983003536A1 *||18 Abr 1983||27 Oct 1983||Massachusetts Inst Technology||A multilayer bioreplaceable blood vessel prosthesis|
|WO1984000540A1 *||28 Jul 1983||16 Feb 1984||Jolla Cancer Res Found||Polypeptide|
|WO1992003107A1||27 Ago 1991||5 Mar 1992||Meadox Medicals, Inc.||Self-supporting woven vascular graft|
|WO1998018408A1||22 Oct 1997||7 May 1998||Bionix Implants Oy||Surgical implant|
|WO2001080918A1||25 Abr 2000||1 Nov 2001||Sulzer Vascutek Limited||Expanded polytetrafluoroethylene vascular graft with coating|
|WO2003034945A1 *||23 Oct 2002||1 May 2003||Katsuko Sakai||Artificial vessel and process for producing the same|
|WO2004093932A1 *||21 Abr 2004||4 Nov 2004||Verigen Ag||A seeded tear resistant scaffold|
|WO2011079976A1 *||28 Oct 2010||7 Jul 2011||Biom'up||Composite matrix|
|WO2017079659A1 *||4 Nov 2016||11 May 2017||Poly-Med, Inc.||Time dependent physiologic tissue scaffold|
|Clasificación de EE.UU.||606/151, 427/398.1, 139/387.00R, 427/338, 623/1.38, 606/229|
|Clasificación internacional||A61F2/04, A61L27/48, A61F2/06|
|Clasificación cooperativa||A61F2/06, A61L27/48, A61F2/04|
|Clasificación europea||A61L27/48, A61F2/06, A61F2/04|