|Publication number||US3839743 A|
|Publication date||Oct 8, 1974|
|Filing date||Oct 15, 1973|
|Priority date||Apr 21, 1972|
|Publication number||US 3839743 A, US 3839743A, US-A-3839743, US3839743 A, US3839743A|
|Original Assignee||A Schwarcz|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (3), Referenced by (153), Classifications (19)|
|External Links: USPTO, USPTO Assignment, Espacenet|
United States'Patent [191 3/36; 128/214 R, 214 D, 334 R, 348, 349 R, 350 R, 335.5, 303; 117/124 R, 138.8 A,
Schwarcz 1 Oct. 8, 1974  METHOD FOR MAINTAINING THE  References Cited NORMAL INTEGRITY OF BLOOD UNITED STATES EN  Inventor: 'Andor Schwarcz, 2117 McClellan 3,633,578 l/l972 Roth,.... 3/1 X St., Schenectady, N Y, 12309 3,663,288 5/1972 Miller 117/138.8 A X 3,722,599 3/1973 Robertson 128/334'R  Filed: Oct. 15, 1973 [21,] Appl' 406,547 4 Primary Examiner-Richard A. Gaudet Related U.S.'Application Data 7 Assistant ExaminerRona1 d L. Frinks  Continuation-impart of Ser. No. 246,327, April 21,
I 1972, abandoned. ABSTRACT I 52 US. Cl 3/1, 3/1310. 1, 3/D1G. 2, Thromboresistam biomedical articles. are provided 3 3 3 3 23 214 R, 123 2 4 1), which are useful in the fields of sub'dermal surgical im- 128/348, 128/350 R, 117/124 E, plants, laboratory apparatus and b1ood containers. Y Y 1 17/1383 A These articles haveat least a thin surface coating of an 51 Int. Cl ..A61'f 1/ 24, A6lf 1/22, A61m 5/00 Organic polymeric material having fluoroalkyl side ["Sfi "FiFl'ibf SEiicHlI.'I.I.'..L..'. 3/"1, DIG 'I' DI G. 3, Chalns and Simple 9 slde F P 19 Claims, N0 Drawings METHOD FOR MAINTAI NING THE NORMAL INTEGRITY OF BLOOD This is a continuation-in-part of application Ser. No. 246,327, filed Apr. 21, 1972 and now abandoned.
BACKGROUND OF THE INVENTION 1. Field of the invention This invention relates to biomedical articles that resist the clotting of human blood and generally that of warm blooded animals. It describes the structure of these-articles and the various modes of their manufacture. One of such articles is a subdermal implant. Examples are subdermal prosthesis such as artificial blood vessels to correct atherosclerotic shrunken passage- 1 ways or to eliminate aneurisms in cardiac assist devices .and in artifical hearts and heart valves to replace or augment the function of the natural heart. Other subdermal prosthetic devices of this invention include reinforced and non reinforced sheetings, rubbers to reconstruct fractures, coronary arteries, denture soft liners, denture base materials, sponge subdermal implant materials, mammary prosthesis, testicular prosthesis, atoplasty prosthesis, rhinoplasty implants, scleral buckler drains, catheters for intravenous administration of flu ids for withdrawal of serial blood samples, for percuta' neous flow-guided cardia catheterization, continuous monitoring of blood glucose, intestinal decompression tubes, various catheters and thoriac drains. Other implanted articles of this invention include circulatory assist devices, tubes for blood transfusion, the implants of electrical devices and mechanical devices such as prosthetic valves and sutures. Other biomedical articles of this invention include thromboresistant surgical instru- 'rnents, laboratory apparatus used for blood handling and blood handling and blood containers for storage.
2. Description of the Prior Art One of the most striking property of blood is its tendency to undergo clotting, or thrombosis. This has been the major problem encountered in the use of subdennal prosthesis.
The detailed mechanisme of thrombosis is still not established. Its normal course involves a series of com-' plex reactions that, once initiated result in the formation of thrombosis. Two processes may occur:
1. The absorption of proteins leading to coagulation;
,thrombogenic and therefore require the use by the patient of anticoagulant drugs such as heparin and coumarin derivatives.
,Various organic polymers'havebeen coated recently with heparin. Although this material displays some degree of thromboresistance, the coating eventually washes away with the flow of blood and it is difficult to fabricate. i
There have been attempts to obtain thromboresistant biomedical articles from fluorinated polymers and sulfonated polymers. However, none of them are performing in a satisfactory manner. This is due, in the opinion of the author of the present invention, to the disposition, the length and the relative lengths of the various groups in the polymer.
SUMMARY OF THE INVENTION.
My invention provides,thromboresistant biomedical articles useful in the fields of subdermal implants, surgical instruments, laboratory apparatus and blood containers. These articles are composed, at least on their surface, of an organic polymeric material having side chains of the formula C,,F ,C,,,l-l ,wherein n and m are integers, n ranging from 1 to 28 and the sum of n and m from 1 to 28, and an anionic group.
DESCRIPTION or THE PREFERRED EMBODIMENT The biomedical articles of this invention are characterized by their thromboresistant surface. The surface of the said articles are characterized by an organic polymeric material having fluoroalkyl side chains of the nF2nJ-l m 2m and m are integers, the range of )1 extending from 1 to 28 and the sum of n and in from 2 to 28. Thenurnberof fluoroalkyl side chains relative to the number of main-chain-atoms in one recurring unit ranges from 1:2 to lzlQ preferably from 1:2 to 1:5.The atoms that arch the main or linear direction of the polymer such as the carbon atoms in polyethylene and poly vinyl alcohol), are the only ones considered main-chain-atoms. Linear fluoroalkyl side chains with values of the integer rt ranging from 8 to 28 are particularly effective ones to give the articles of this invention a high degree of thromboresistance.
The presence of another, generally shorter side chain, which is an anion or one comprising an anion, generally enhances the 'thromboresistivity of the polymer. However, its presence is required only in the cases wherein the said fluoroalkyl side chain is branched (non linear) and in cases wherein the value of the integer n ranges from 1 to 7. i
A feature of the 'said organic polymeric materials of I this invention is thattheir thromboresistant character.
invcntion'have simultaneously low surface tension and negative zeta potential, properties thought necessary for thromboresistance according to certain theories.
The invention is described hereinafter in. greater detail by reference to the examples which show preferred embodiments of the invention. It should be understood however that the examples hereinafter given are for the purposes of illustration only and that the invention in its broader aspects is not limited thereto.
Examples of the said tluorinated side chains are 3( 2)1 CF3(CF2)11(CH2)16 1 a 2)22 2 4 9( 2)10."- H2)2 a 1' The anionic groups can be either in their acidic form, their salt or their partially neutralized form. Example of 3 simple anionic groups are carboxylate, sulfonate, sulfate, phosphate and phosphites. Examples of the salt forming positive ions are sodium, potassium, lithium, ammonium, magnesium, tertiary amines such as N- methylmorpholine.
The ratio of the number of the said fluoroalkyl groups to the number of said anionic groups ranges from 0.511 to 50:1, preferably from 1:1 to 20:1. ln general, this ratio decreases as the ionic strength decreases. The number, strength and degree of neutralization of said anionic groups should be limited in order to avoid solvation or excessive swelling of the fluorinated polymer by the blood.
The said fluoroalkyl side chain may be directly attached to the main chain of the organic polymer. It can also be attached by an intermediate divalent radical,
such as --O, CO, SO, SO SO NH.-, CH O, COO-, NHCO, NH- COO, NHCONH-, POCH POC H SO NCH SO NC l-l Similarly, the anionic group may be directly attached to the main chain of the organic polymer or through an intermediate divalent radical. Such radicals are exemplified by CH C H OC H (CH )s 2 2H43( 2)i5 Biomedical articles of this invention may be entirely composed of the said organic polymeric materialswith the fluoroalkyl side chains. However, the particular mechanical and electrical properties required of the various biomedical articles, or the higher cost involved may require them to comprise a surface portion and a substrate portion. The surface portion is composed of the said thromboresistant organic polymer. The substrate portion may be any solid material that satisfies the properties required of the biomedical article. Thus, substrate materials comprise plastics, rubbers, metals, glass, ceramics. The useof a coating technic is particularly advantageous for making surgical instruments, laboratory apparatus, blood containers and heart valves.
Examples of plastic substrates are isotactic polyolefins, such as polypropylene, polystyrene, polyethylene, poly(4-methylpentane); polyesters such as poly(l,4- cyclohexylene terephthalate), poly(ethylene terephthalate); polyacrylates such as polymethylmethacrylate, polyco (ethylacrylate-acrylic acid); polyurethanes such as the ones prepared from a hydroxy. terminated polyether or polyester and methylenebis (phenylisocyanate); polycarbonates such as poly(2,2- propanebis(4-phenyl carbonate); fluorinated polyole fins such as poly(tetrafluoroethylene); chlorinated polyolefins such as polyvinylchloride; proteins such as wool, casein; cellulose, cellulose derivatives such as cellulose acetate, cellulose acetate butyrate and other polysaccharides. Examples of rubber substrates are silicone rubbers such as poly(dimethylsiloxane poly(rnethylphenyl siloxane); hydrocarbon rubbers such as butyl rubber, ethylene-propylene rubber; nitrile rubbers such as polyco(butadieneacrylonitrile); fluorinated rubbers such as fluorinated ethylene-propylene rubber, fluorinated polyurethanes; urethane rubbers such as the ones prepared from hydroxy terminated polyethers or polyesters and methylenebis(- phenylisocyanate); polyether rubbers such as poly (propylene oxide) and chlorosulfonated rubbers such as chlorosulfonated ethylene-propylene rubber.
Metallic substrates include stainless steel, aluminum, alloys of chromium, nickel, cobalt and magnesium.
Examples of the said organic polymeric materials having linear fluoroalkyl side chains wherein the said integer n ranges between 8 and 28, the sum of n and m between 8 and 28 and the said polymer has no anionic groups attached to the main chain are:
poly( l, l ,2,2- tetrahydropentadecafluorononyl acrylate) poly( l ,ldihydropentacosafluorotridecyl acrylate) poly( l,1dihydropentatetracontafluorotricosyl methacrylate) poly( 1,1 ,2,2-tetrahydrononacosafluorohexadecyl vinyl ehter) poly (vinylperfluorooctadecane) poly (perfluorol octadecene) poly(vinyl perfluorostearate) poly(N-l l dihydropentatriacontafluorooctadecyl hexamethylene urea) I poly(methyll ,l ,2,2-tetrahydrotritriacontafluorooctadecyl siloxane) poly [di( l,l,2,Z-tetrahydrotricosafluorotridecyl) siloxane] I poly( N-l 1 dihydropentatriacontafluorooctadecyl hexamethylene adipamide).
Examples of said organic polymeric materials having linear or branched fluoroalkyl side chains wherein the said integer n ranges between 1 and 28, the sum of n and m between 2 and 28 and the said anionic group is bonded to the main chain of the polymer, are (the propertion of monomers in the copolymers are expressed in mole polyco( l l dihydropentadecafluorooctyl methacrylate 10% sodium acrylate) polyco (l,l,2,2,stetrahydrotrifluoropropyl acrylate 5% maleic acid) polyco( 1,1 ,2,2-tetrahydropentade cafluorononyl acrylate 30% methacrylic acid 15% sodium methacrylate) poly(carboxyethyl-l l ,2,2-tetrahydrotrifluoropropyl siloxane) polyco(methyl-3,3,3-trifluoropropyl siloxane 20% carboxyethyl-methyl siloxane) polymers of fluoroalkyl esters, amides and imides of maleic and fumaric acids The copolymers with ethylene, styrene, methylvinyl ether and vinyl acetate of fluoroalkyl esters, amides and imides of maleic and fumaric acids The copolymers with maleic, fumaric and acrylic acids and their anhydrides of fluoroalkyl esters, amides and imides of maleic and fumaric acids the l,1dihydronanafluoropentyl monoester of polyco (50% ethylene 23% maleic acid 23% potassium maleate) the l,l-dihydropentadecafluorooctyl monoamide of polyco methylvinyl ether 10% fumaric acid 10% sodium fumarate) polyco( vinyl l l dihydropentatriacontafluorooctadecyl carbamate 15% vinyl disodium phosphite) polyco (vinyl perfluoropropianate 10% acrylic acid) These compounds are all linear organic polymers having intrinsic viscosity values higher than 0.04, preferably higher than 0.07. They can, be prepared by conventional polymerization techniques such as the free radical and ionic addition polymerization techniques or heat, oxygen, moisture, radiation, peroxides etc.
condensation polymerization techniques of the monomers. Another method consists of introducing an anigroup. Such compounds are, for example, perfluorooctadecanoyl chloride and l ,l-dihydrotricosafluorodode- 1 cyl alcohol. These techniques are well documented in the art of polymer synthesis.
After preparation, the polymer is then shaped into the desired biomedical articles, e.g. heart valves, blood vessel, tubings etc. The shaping can be done by any conventional means, uch as extruding,'molding, casting. After proper sterilization, the biomedical article is ready for use.
An effective way to prepare a thromboresistant biomedical article of this invention is to react the polymeric material of this invention containing the said anionic group with a stochiometrically defective amount of a cationic type polymer, such as poly-2- vinylpyridine, poly(vinylbenzyldimethylamine), polyco(styrene-4-vinylpyrridine).
Another way to prepare a thromboresistant biomedical article of this invention is to coat the potentially blood contacting surfaces of the shaped article made of a plastic, a rubber, a metal or glass with the said organic polymeric material having the fluoroalkyl side chains exemplified above. Any of the conventional coating procedures can be used, such as coating from a'solution, emulsion, suspension followed by solvent evaporation, or a hot melt coating technique. The bond between he substrate and the coating can be improved, if necessary, by conventional surface treatment techniques, such as corona discharge, flame treatment, irradiation, or priming with a polar polymeric substance. These coating and priming procedures are well documented in the art of coating technology.
A biomedical article of this invention can be prepared by the use of still another technique. This technique consists of coating the shaped article, made of a plastic, a rubber, a metal or glass, with the monomers from which the said organic polymeric materials, having the fiuoroalkyl side chains, and examplified above, are prepared, and let the polymerization proceed on the surface. Similar coating and priming procedures can be used as the onesdescribed above. The polymerization on the surface of the article can be carried out by conventional techniques used in the art of polymer synthesis and coatings, such as the use of catalysts,
Still another way to achieving the objectives of this invention is to graft an anionic group and the said pertluoroalkyl group C F ,C l-l onto the surface of a shaped biomedical article made of a plastic or a rubber. Examples of such surface grafting reactions are as follows:
the grafting of perfluorooctadecanoyl chloride onto a shaped biomedical article made of poly(tet-' ramethylene urea), poly(tetramethylene hexamethylene dicarbamate), cellulose fibers, wool, silk, nylon;
the grafting of sulfuric acid and perfluorohexadecanoic acid onto the shaped article made of poly(vinylalcohol), cellulose, casein;
the grafting of 1,1 ,2,2-tetrahydroheptafluoropentanol, onto a preshaped article made of polyco(acrylic acid sodium acrylate);
the grafting of l,l-dihydropentacosafluorotridecyl' iodide onto a shaped article made of polyco(ethylene-monosodium maleate), and onto sodium cellulose sulfate;
- the radiation grafting of l,l,2,Z-tetrahydrotritriacontafluorooctadecyl vinylether to a shaped article made of poly(ethylene ter'ephtalate);
the grafting of l,l-dihydrohencosafluoroundecyl amine onto a shaped biomedical article made of polyethylene which has been previously sulfonated with concentrated sulfuric acid and the sulfonate groups partially neutralized with a buffer solution having a pH of 7.5.
There are still other meansto prepare the polymers of this invention. For example polymers having unbr'anched higher alkyl side chains can be fiuorinated with fluorine gas. Examples of such polymers are polyvinylstearate, polyco(vinylacetate-docosylmaleate sodium salt).
EXAMPLE 1 Ninety grams (0.1 moles) of 1,1- dihydrotritriacontafluoroheptadecyl acrylate and 1.14 grams (0.0l moles) of l-hexenoic acid are copolymerized by using 0.5% azobisisobutyronitrile asthe initia-' tor and toluene as the solvent medium. The reaction is carried out in crew cup vials at 75-80C. for 16 hours. The copolymer is then purified by adding methanol to the solution, filtered, redissolved in 1,2,2-trichlorotrifluoroethane, and this procedure is repeated three times. The solid polymer is then dried in a vacuum oven at 60C. for 64 hours. The intrinsic viscosity measured 'in hexafluorodimethyl benzene is 0.2.
A glass tube is then treated with a 5% 'trichloro trifluoroethylene solution of the copolymer by filling the tube, inverting it and allowing the excess liquid to drain out. Following evaporation of the solvent, the coated test tube is sterilized.
Five (5) ml of freshly drawn whole blood from the lower vena cava of a rabbit as added and the test tube is periodically tipped to observe clot formation. No evidence of clot formation is observed for severalhours. A control test tube, not coated with a layer of the co polymer, is tested in an identical manner, and clotting occurs within 7 minutes.
EXAMPLE 2 EXAMPLE 3 A copolymer of octadecyl vinyl ether with 1- dodecenoic'acid sodium salt is used to coat, from a 5% toluene solution, a commercially available 'fluoropolymer heart valve previously submitted to electron radiation to obtain better adhesion. It is then fluorinated in the dark by exposure to 5% fluorine diluted with nitrogen at room temperature for 2.weeks. The coated heart valve is then sterilized and when implanted in an animal, such as a dog, the implant, in accordance with EXAMPLE 4 A silicone rubber having a fluoroalkyl side chain is .prepared by the following customary procedure.
Methyl trichlorosilane is reacted with -l,1,2,2,3,3,4,4- octahydropentadecafluorohexadecyl magnesium chloride, the dichloro product separated from the reactive mixture by vacuum distillation and followed by polymerization with the addition of water. It is then mixed with 2% dimethyltindilaurate catalyst, molded into a tube of 0.05 inch inside diameter and cured at 150C. for 48 hours under nitrogen.
The tubing is tested in vivo using a jugular vein of a dog. The vein is exposed and severed in a standard surgical manner. The tube, after sterilization, is formed into a loop and to each end of the vein is attached one end of the tubing. Circulation through the vein is resumed and blood now is passing through the tubing.
The implanted artifical vein, in accordance with this invention, will not be found to be harmful to the life of the animal.
, EXAMPLE 5 l-perfluorooctadecene,'88.l g (0.1 mol), is copolymerized with maleic anhydride, 9.6 g(0.l mole), using a technique similar to that described in Example 1. The copolymer is then boiled in an aqueous sodium hydroxide solution containing a small amount of a fluorinated anionic surfactant. This reaction yields the sodium salt of the maleic acid portion of the polymer. The polymer is then purified by a repeated solutionpreceipitation technique.
A cannula made of polypropylene is surface oxidized in a circulating air oven at 1 10 C. to obtain better adhesion. It is then coated with a 5% trichlorotrifluoroethylene solution of the polymer prepared in this example and the'solvent evaporated in an air iven at 60C. After sterilization, the cannula is used as conduit replacement in a heart-lung machine. After several months of use no evidence of thrombus formation on the cannula will be reported.
EXAMPLE 6 Poly(vinyl alcohol) of 120,000 molecular weight, g(1 mole), is sulfated with-sulfur trioxide dissolved in sulfuric acid to yield the sulfate ester. As deduced by titration with sodium hydroxide one out of every 10 hydroxyl groups is sulfated. The polymer is further reacted with perfluorohexadecanoyl chloride in N- EXAMPLE 7 A 121' copolymer of methylvinylether maleic anhyclride, 15.6 g (0.1 mole) having an intrinsic viscosity of 2.5 in methylethyl ketone, is reacted in 500 ml of methylethyl ketone at the boil with l,l,2,2-tetrahydrohencosafluorododecyl amine, 66.3 g (0.1 mole). The fluorinated acid-amid is then precipitated in methanol, filtered, washed, and reacted with sodium hydroxide dissolved in alcohol. The polymer thus obtained. is polyco[methylvinyl ether-sodium salt of maleic acid mono( l l ,2,2-tetrahydrohencosafluorododecyl )amide], which is then purified by repeated solvationprecipitation.
The fluorinated copolymer is then molded in a hot press into a 0.05 in. inside diameter catheter having a wall thickness of 0.005 in. and sterilized. When surgically implanted in the jugular vein of a dog, similar results to those obtained in Example 4 will be reported.
EXAMPLE 8 Vinyl perfluorodocosyl ether, 11.8 g (0.1 mole) is polymerized and purified using a technique similar to that described in Example 1. The intrinsic viscosity measured in trichlorotrifluoroethane is 0.2. A stainless steel tubing is coated with a 5% trichlorotrifluoroethylene solution of this polymer, and the solvent evaporated at 60C. in a vacuum oven. After sterilization the tubing is used as an arterialvenous bypass in a hemidialysis machine. No thrombus formation will be evident after usage of the machine for several months.
EXAMPLE 9 A cannula made of polyethylene is phosphorilated on the surface with phosphorous trichloride at 60C. in the presence of oxygen, and then boiled in aqueous sodium hydroxide. This procedure provides sodium phosphate groups at the surface. A subsequent grafting of perfluorotetradecene using an electron radiation techniques yields the desired surface, which is then cleaned with bis(trifluoromethyl) benzene and ethanol. After through sterilization, the cannula, when tested in a heart-lung machine, will yield comparable result to those obtained in Example 5.
. EXAMPLE 10 101.6 grams (0.1 mole) of perfluorooctadecylperfluorovinyl ether and 16 grams (0.02 moles) of perfluoro-l-hexadecenoic acid are dissolved in bis(trifluoro)benzene and coated on a commercially available silicone rubber heart valve previously primed to obtain better adhesion. After'solvent evaporation, the coated heart valve is then irradiated with an electron beam of 5 MeV under argon to polymerize the coating. Following extraction of the residual monomers and sterilization, the heart valve, when evaluated as in Example 3, yields similar results.
It will be apparent that many widely different embodiments of this invention may be made without de parting from the spirit and scope thereof. Therefore, the invention is not intended to be limited except as indicated in the appended claims.
Polyco(methacrylic acid-3,333,3,3'-hexafluoroisobutyl methacrylate) is prepared in emulsion at 65C for 6 hours with the following recipe, added in the order shown:
Parts Water 30.0 Trimethyloctodecylammonium bromide 1.0 Mcthacrylic'acid 2.0
- Contmued 3,3,3,3,3,3' hexafluoroisobutyl methacrylate 100 Acetone 1 5.0 Azodiisobutyramidine dihydrochloride 0.2
EXAMPLE 12 A thromboresistant artificial heart is molded from poly(methyl-3,3,3-trifluoropropyl siloxane) wherein about one fifth of the methyl groups is replaced with carboxyethyl groups. This copolymer is prepared as follows; Methyldichlorosilane is reacted with acrylonitrile under reflux conditions (60l,15C) for about ten hours by using catalytic amounts of the following materials: cuprous chloride, tetramethylethylene diamine and triethylamine. The reaction product, which is cyanoethyl-methyldichlorosilane, is hydrolyzed in the presenggg fam' HCl solution under reflux conditions until complete diappearance of the-nitrile group. After separation from theaqueous layer, the organic layer consists of poly(carboxyethylmethylsiloxane). This is equilibrated at 60100C, for 4-6 hours, with 20% by weight of 3,3,3-trifluoropropyl-methylsiloxane fluid commercially available from Dow Corning Co., Inc until constant viscosity is reached. The product is then washed with aqueous sodium carbonate, water, separate from the aqueous layer, and stripped off from the low boilers by distillation. It is then blended with 100 phr finely divided silica and 1 phr dicumyl peroxide, molded into a human heart and cured at 125C for 5 EXAMPLE l3 Acrylic acid, mole is copolymerized with. 80 mole of bis [2-(N-ethyl perfluorohexylsulfonamido) ethyl] itaconate, as in Example 1. After purification and coating on a test tube, the polymer passes the same test as the one described in Example '1.
Having thus described my invention and in what manner it may be manufactured and used, what I claim and desire to protect by Letters Patent is:
1.. A method-or maintaining the normal integrity of blood which comprises placing it in contact with a physiologically acceptable article at least the surface of which consists of an organic polymeric material having fluoroalkyl side chains of the formula C F C H wherein n and m are integers, n ranging 1 to 28, and the sum of n and m from 2 to 28, the number of said fluoroalkyl side chains relative to the number of main chain atoms in one recurring unit ranges from 1:2 to 1:10; and said polymeric material having another side group chemically bonded to the main chain, said side group being selected from the group consisting of Hydrogen, hologen, aryl, lower alkyl and anionic groups.
2. The method defined in'claim 1 wherein the said fiuoroalkyl side chains are linear, the said integers n and m range from 8 to 28 and the sum of n and m from 8 to 28.
3. The method definedin claim 1 wherein the said integer n ranges from 1 to 7, the sum of n and m from 2 to 28 and the said side group is an anionic group.
4. The method defined in claim 1 wherein said physi- 5 ological acceptable article comprises a substrate portion and a surface coating. portion, said surface coating portion at least being of said polymeric material defined in claiml.
5. The method defined in claim 1 wherein the said anionic group is a member selected from the group the said organic polymeric material by an intermediate divalent radical.
8. The method defined in claim 1 wherein the said anionic group is bonded to the said organic polymeric material by an intermediate divalent radical.
9. The method defined in claim 7 wherein the said intermediate divalent radical is a member selected from the group consisting of O, -'CO,v SO,
10. The method defined in claim 8 wherein the said intermediate divalent radical is a member selected from the group consisting of --CH C H *OCZHQ, 2)B' F2)15 'f z H z 11. The method defined in claim 1 wherein said physiologically acceptable article is a subdermal surgical implant.
12. The method defined in claim 1 wherein said physiologically acceptable article is a surgical instrument.
13. The method defined in claim 1 wherein said physiologically acceptable article is a laboratory apparatus used for handling blood.
14. The method defined in claim 1 wherein said physiologically acceptable article is a blood container.
15. The method defined in claim 4 wherein the said substrate portion is selected from the group consisting of plastics, rubbers, metals, glass and ceramics.
16. The method defined in claim l wherein said organic polymeric material is selected from the group consisting of copolymers prepared from a fiuoroalkyl acrylate and acrylic acid, a fiuoroalkyl methacrylate and methacrylic acid and the mixtures of these monomers.
17. The method defined in claim 16 wherein said polymeric acrylates are selected from the group consisting of:
poly(l,ldihydropentacosafluorotridecyl acrylate) poly( 1 l -dihydropentatetracontafluorotricosyl methacrylate) polyco( l l dihydropentadecafluorooctyl methacrylate 10% sodium acrylate) polyco(1,1,2,2-tetrahydrotrifluoropropyl acrylate 5% maleic acid) polyco( 1 l ,2,2tetrahydropentadecafluorononyl acrylate 30% methacrylic acid 15% sodium methacrylate) 12 19. The method defined in claim 1 wherein said organic polymeric material is selected from the group consisting of:
polymers of fluoroalkyl esters, amides and imides of maleic and fumaric acids, the copolymers with ethylene, styrene, methylvinyl ether and vinyl acetate of fluoroalkyl esters, amides and imides of maleic and fumaric acids, the copolymers with maleic, fumaric and acrylic acids and their anhydrides of fluoroalkyl esters,
amides and imides of maleic and fumaric acids.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US3633578 *||Jun 24, 1970||Jan 11, 1972||American Cyanamid Co||Method of maintaining the integrity of blood|
|US3663288 *||Sep 4, 1969||May 16, 1972||American Cyanamid Co||Physiologically acceptible elastomeric article|
|US3722599 *||Aug 17, 1971||Mar 27, 1973||Minnesota Mining & Mfg||Fluorocyanoacrylates|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US4008047 *||Dec 26, 1974||Feb 15, 1977||North Star Research Institute||Blood compatible polymers for blood oxygenation devices|
|US4178329 *||May 5, 1978||Dec 11, 1979||Hoechst Aktiengesellschaft||Plastics material having an improved blood tolerance|
|US4219520 *||Aug 30, 1978||Aug 26, 1980||Medical Evaluation Devices And Instruments Corp.||Method of making thrombo-resistant non-thrombogenic objects formed from a uniform mixture of a particulate resin and colloidal graphite|
|US4484894 *||Feb 23, 1982||Nov 27, 1984||Eiichi Masuhara||Sheet for lining denture base|
|US4622237 *||Jun 11, 1985||Nov 11, 1986||Giulio Lori||Method of flame activation of substrates|
|US4632842 *||Jun 20, 1985||Dec 30, 1986||Atrium Medical Corporation||Glow discharge process for producing implantable devices|
|US4656083 *||Mar 11, 1985||Apr 7, 1987||Washington Research Foundation||Plasma gas discharge treatment for improving the biocompatibility of biomaterials|
|US4687482 *||Apr 27, 1984||Aug 18, 1987||Scripps Clinic And Research Foundation||Vascular prosthesis|
|US4718907 *||Jun 20, 1985||Jan 12, 1988||Atrium Medical Corporation||Vascular prosthesis having fluorinated coating with varying F/C ratio|
|US4994298 *||Apr 18, 1990||Feb 19, 1991||Biogold Inc.||Method of making a biocompatible prosthesis|
|US5034265 *||Aug 21, 1989||Jul 23, 1991||Washington Research Foundation||Plasma gas discharge treatment for improving the compatibility of biomaterials|
|US5356668 *||Dec 9, 1991||Oct 18, 1994||Vascutek Limited||Fluorinating polymer surfaces|
|US5383903 *||Aug 20, 1992||Jan 24, 1995||United States Surgical Corporation||Dimethylsiloxane-alkylene oxide copolymer coatings for filaments|
|US5637113 *||Dec 13, 1994||Jun 10, 1997||Advanced Cardiovascular Systems, Inc.||Polymer film for wrapping a stent structure|
|US5700286 *||Aug 22, 1996||Dec 23, 1997||Advanced Cardiovascular Systems, Inc.||Polymer film for wrapping a stent structure|
|US5907017 *||Jan 31, 1997||May 25, 1999||Cornell Research Foundation, Inc.||Semifluorinated side chain-containing polymers|
|US6022344 *||Dec 4, 1997||Feb 8, 2000||Npbi International B.V.||Cryopreservation bag|
|US6060639 *||Mar 4, 1994||May 9, 2000||Mentor Corporation||Testicular prosthesis and method of manufacturing and filling|
|US6114467 *||Aug 11, 1998||Sep 5, 2000||Cornell Research Foundation, Inc.||Semifluorinated acid halides and fluorinated polymers produced therefrom|
|US6464723||Apr 22, 1999||Oct 15, 2002||Advanced Cardiovascular Systems, Inc.||Radiopaque stents|
|US6527801||Apr 13, 2000||Mar 4, 2003||Advanced Cardiovascular Systems, Inc.||Biodegradable drug delivery material for stent|
|US6585757||Sep 15, 1999||Jul 1, 2003||Advanced Cardiovascular Systems, Inc.||Endovascular stent with radiopaque spine|
|US6602287||Dec 8, 1999||Aug 5, 2003||Advanced Cardiovascular Systems, Inc.||Stent with anti-thrombogenic coating|
|US6605114||Oct 29, 1999||Aug 12, 2003||Advanced Cardiovascular Systems, Inc.||Heparin delivery method|
|US6652579||Jun 22, 2000||Nov 25, 2003||Advanced Cardiovascular Systems, Inc.||Radiopaque stent|
|US6776792||Apr 24, 1997||Aug 17, 2004||Advanced Cardiovascular Systems Inc.||Coated endovascular stent|
|US7077860||Jun 24, 2004||Jul 18, 2006||Advanced Cardiovascular Systems, Inc.||Method of reducing or eliminating thrombus formation|
|US7105018||Dec 30, 2002||Sep 12, 2006||Advanced Cardiovascular Systems, Inc.||Drug-eluting stent cover and method of use|
|US7144422||Nov 13, 2002||Dec 5, 2006||Advanced Cardiovascular Systems, Inc.||Drug-eluting stent and methods of making the same|
|US7163715||Dec 30, 2002||Jan 16, 2007||Advanced Cardiovascular Systems, Inc.||Spray processing of porous medical devices|
|US7186789||Jun 11, 2003||Mar 6, 2007||Advanced Cardiovascular Systems, Inc.||Bioabsorbable, biobeneficial polyester polymers for use in drug eluting stent coatings|
|US7198675||Sep 30, 2003||Apr 3, 2007||Advanced Cardiovascular Systems||Stent mandrel fixture and method for selectively coating surfaces of a stent|
|US7201940||Jun 12, 2001||Apr 10, 2007||Advanced Cardiovascular Systems, Inc.||Method and apparatus for thermal spray processing of medical devices|
|US7229471||Sep 10, 2004||Jun 12, 2007||Advanced Cardiovascular Systems, Inc.||Compositions containing fast-leaching plasticizers for improved performance of medical devices|
|US7258891||Apr 7, 2003||Aug 21, 2007||Advanced Cardiovascular Systems, Inc.||Stent mounting assembly and a method of using the same to coat a stent|
|US7285304||Jun 25, 2003||Oct 23, 2007||Advanced Cardiovascular Systems, Inc.||Fluid treatment of a polymeric coating on an implantable medical device|
|US7291166||May 18, 2005||Nov 6, 2007||Advanced Cardiovascular Systems, Inc.||Polymeric stent patterns|
|US7297159||Jul 21, 2004||Nov 20, 2007||Advanced Cardiovascular Systems, Inc.||Selective coating of medical devices|
|US7297758||Aug 2, 2005||Nov 20, 2007||Advanced Cardiovascular Systems, Inc.||Method for extending shelf-life of constructs of semi-crystallizable polymers|
|US7301001||Dec 20, 2006||Nov 27, 2007||Advanced Cardiovascular Systems, Inc.||Bioabsorbable, biobeneficial polyester polymers for stent coatings|
|US7312299||Dec 20, 2006||Dec 25, 2007||Advanced Cardiovascular Systems, Inc.||Bioabsorbabl, biobeneficial polyester polymers for stent coatings|
|US7329366||Jun 18, 2004||Feb 12, 2008||Advanced Cardiovascular Systems Inc.||Method of polishing implantable medical devices to lower thrombogenecity and increase mechanical stability|
|US7381048||Apr 12, 2005||Jun 3, 2008||Advanced Cardiovascular Systems, Inc.||Stents with profiles for gripping a balloon catheter and molds for fabricating stents|
|US7390333||Jan 10, 2003||Jun 24, 2008||Advanced Cardiovascular Systems, Inc.||Biodegradable drug delivery material for stent|
|US7413574||Aug 1, 2006||Aug 19, 2008||Advanced Cardiovascular Systems, Inc.||Drug-eluting stent cover method of use|
|US7416558||Aug 1, 2006||Aug 26, 2008||Advanced Cardiovascular Systems, Inc.||Drug-eluting stent cover and method of use|
|US7435255||Sep 22, 2003||Oct 14, 2008||Advnaced Cardiovascular Systems, Inc.||Drug-eluting stent and methods of making|
|US7470283||Jan 10, 2003||Dec 30, 2008||Advanced Cardiovascular Systems, Inc.||Biodegradable drug delivery material for stent|
|US7476245||Aug 16, 2005||Jan 13, 2009||Advanced Cardiovascular Systems, Inc.||Polymeric stent patterns|
|US7514122||Oct 17, 2006||Apr 7, 2009||Advanced Cardiovascular Systems, Inc.||Method and apparatus for spray processing of porous medical devices|
|US7553377||Apr 27, 2004||Jun 30, 2009||Advanced Cardiovascular Systems, Inc.||Apparatus and method for electrostatic coating of an abluminal stent surface|
|US7563324||Dec 29, 2003||Jul 21, 2009||Advanced Cardiovascular Systems Inc.||System and method for coating an implantable medical device|
|US7604700||Jan 16, 2007||Oct 20, 2009||Advanced Cardiovascular Systems, Inc.||Stent mandrel fixture and method for selectively coating surfaces of a stent|
|US7622070||Jun 20, 2005||Nov 24, 2009||Advanced Cardiovascular Systems, Inc.||Method of manufacturing an implantable polymeric medical device|
|US7632307||Dec 16, 2004||Dec 15, 2009||Advanced Cardiovascular Systems, Inc.||Abluminal, multilayer coating constructs for drug-delivery stents|
|US7658880||Jul 29, 2005||Feb 9, 2010||Advanced Cardiovascular Systems, Inc.||Polymeric stent polishing method and apparatus|
|US7662326||Apr 27, 2007||Feb 16, 2010||Advanced Cardiovascular Systems, Inc.||Compositions containing fast-leaching plasticizers for improved performance of medical devices|
|US7699890||Jan 28, 2004||Apr 20, 2010||Advanced Cardiovascular Systems, Inc.||Medicated porous metal prosthesis and a method of making the same|
|US7708548||Apr 10, 2008||May 4, 2010||Advanced Cardiovascular Systems, Inc.||Molds for fabricating stents with profiles for gripping a balloon catheter|
|US7731890||Jun 15, 2006||Jun 8, 2010||Advanced Cardiovascular Systems, Inc.||Methods of fabricating stents with enhanced fracture toughness|
|US7740791||Jun 30, 2006||Jun 22, 2010||Advanced Cardiovascular Systems, Inc.||Method of fabricating a stent with features by blow molding|
|US7757543||Jul 13, 2006||Jul 20, 2010||Advanced Cardiovascular Systems, Inc.||Radio frequency identification monitoring of stents|
|US7758881||Mar 24, 2005||Jul 20, 2010||Advanced Cardiovascular Systems, Inc.||Anti-proliferative and anti-inflammatory agent combination for treatment of vascular disorders with an implantable medical device|
|US7761968||May 25, 2006||Jul 27, 2010||Advanced Cardiovascular Systems, Inc.||Method of crimping a polymeric stent|
|US7794495||Jul 17, 2006||Sep 14, 2010||Advanced Cardiovascular Systems, Inc.||Controlled degradation of stents|
|US7794776||Jun 29, 2006||Sep 14, 2010||Abbott Cardiovascular Systems Inc.||Modification of polymer stents with radiation|
|US7823263||Jul 9, 2007||Nov 2, 2010||Abbott Cardiovascular Systems Inc.||Method of removing stent islands from a stent|
|US7829008||May 30, 2007||Nov 9, 2010||Abbott Cardiovascular Systems Inc.||Fabricating a stent from a blow molded tube|
|US7842737||Sep 29, 2006||Nov 30, 2010||Abbott Cardiovascular Systems Inc.||Polymer blend-bioceramic composite implantable medical devices|
|US7867547||Dec 19, 2005||Jan 11, 2011||Advanced Cardiovascular Systems, Inc.||Selectively coating luminal surfaces of stents|
|US7875233||Jul 18, 2005||Jan 25, 2011||Advanced Cardiovascular Systems, Inc.||Method of fabricating a biaxially oriented implantable medical device|
|US7875283||Jun 16, 2005||Jan 25, 2011||Advanced Cardiovascular Systems, Inc.||Biodegradable polymers for use with implantable medical devices|
|US7886419||Jul 18, 2006||Feb 15, 2011||Advanced Cardiovascular Systems, Inc.||Stent crimping apparatus and method|
|US7901452||Jun 27, 2007||Mar 8, 2011||Abbott Cardiovascular Systems Inc.||Method to fabricate a stent having selected morphology to reduce restenosis|
|US7923022||Sep 13, 2006||Apr 12, 2011||Advanced Cardiovascular Systems, Inc.||Degradable polymeric implantable medical devices with continuous phase and discrete phase|
|US7951185||Jan 6, 2006||May 31, 2011||Advanced Cardiovascular Systems, Inc.||Delivery of a stent at an elevated temperature|
|US7951194||May 22, 2007||May 31, 2011||Abbott Cardiovascular Sysetms Inc.||Bioabsorbable stent with radiopaque coating|
|US7955381||Jun 29, 2007||Jun 7, 2011||Advanced Cardiovascular Systems, Inc.||Polymer-bioceramic composite implantable medical device with different types of bioceramic particles|
|US7959857||Jun 1, 2007||Jun 14, 2011||Abbott Cardiovascular Systems Inc.||Radiation sterilization of medical devices|
|US7959940||May 30, 2006||Jun 14, 2011||Advanced Cardiovascular Systems, Inc.||Polymer-bioceramic composite implantable medical devices|
|US7964210||Mar 31, 2006||Jun 21, 2011||Abbott Cardiovascular Systems Inc.||Degradable polymeric implantable medical devices with a continuous phase and discrete phase|
|US7967998||Jan 3, 2008||Jun 28, 2011||Advanced Cardiocasvular Systems, Inc.||Method of polishing implantable medical devices to lower thrombogenecity and increase mechanical stability|
|US7971333||May 30, 2006||Jul 5, 2011||Advanced Cardiovascular Systems, Inc.||Manufacturing process for polymetric stents|
|US7989018||Mar 31, 2006||Aug 2, 2011||Advanced Cardiovascular Systems, Inc.||Fluid treatment of a polymeric coating on an implantable medical device|
|US7998404||Jul 13, 2006||Aug 16, 2011||Advanced Cardiovascular Systems, Inc.||Reduced temperature sterilization of stents|
|US8003156||May 4, 2006||Aug 23, 2011||Advanced Cardiovascular Systems, Inc.||Rotatable support elements for stents|
|US8007529||Aug 1, 2008||Aug 30, 2011||Advanced Cardiovascular Systems, Inc.||Medicated porous metal prosthesis|
|US8016879||Jun 27, 2007||Sep 13, 2011||Abbott Cardiovascular Systems Inc.||Drug delivery after biodegradation of the stent scaffolding|
|US8017237||Jun 23, 2006||Sep 13, 2011||Abbott Cardiovascular Systems, Inc.||Nanoshells on polymers|
|US8034287||May 15, 2007||Oct 11, 2011||Abbott Cardiovascular Systems Inc.||Radiation sterilization of medical devices|
|US8043553||Sep 30, 2004||Oct 25, 2011||Advanced Cardiovascular Systems, Inc.||Controlled deformation of a polymer tube with a restraining surface in fabricating a medical article|
|US8048441||Jun 25, 2007||Nov 1, 2011||Abbott Cardiovascular Systems, Inc.||Nanobead releasing medical devices|
|US8048448||Jun 15, 2006||Nov 1, 2011||Abbott Cardiovascular Systems Inc.||Nanoshells for drug delivery|
|US8099849||Dec 13, 2006||Jan 24, 2012||Abbott Cardiovascular Systems Inc.||Optimizing fracture toughness of polymeric stent|
|US8109994||Jan 2, 2008||Feb 7, 2012||Abbott Cardiovascular Systems, Inc.||Biodegradable drug delivery material for stent|
|US8128687||Aug 25, 2006||Mar 6, 2012||Advanced Cardiovascular Systems, Inc.||Drug-eluting stent with filament strands|
|US8128688||Jun 19, 2007||Mar 6, 2012||Abbott Cardiovascular Systems Inc.||Carbon coating on an implantable device|
|US8172897||Jun 28, 2004||May 8, 2012||Advanced Cardiovascular Systems, Inc.||Polymer and metal composite implantable medical devices|
|US8173062||Sep 30, 2004||May 8, 2012||Advanced Cardiovascular Systems, Inc.||Controlled deformation of a polymer tube in fabricating a medical article|
|US8197879||Jan 16, 2007||Jun 12, 2012||Advanced Cardiovascular Systems, Inc.||Method for selectively coating surfaces of a stent|
|US8202528||Jun 5, 2007||Jun 19, 2012||Abbott Cardiovascular Systems Inc.||Implantable medical devices with elastomeric block copolymer coatings|
|US8241554||Jun 29, 2004||Aug 14, 2012||Advanced Cardiovascular Systems, Inc.||Method of forming a stent pattern on a tube|
|US8262723||Apr 9, 2007||Sep 11, 2012||Abbott Cardiovascular Systems Inc.||Implantable medical devices fabricated from polymer blends with star-block copolymers|
|US8293260||Jun 5, 2007||Oct 23, 2012||Abbott Cardiovascular Systems Inc.||Elastomeric copolymer coatings containing poly (tetramethyl carbonate) for implantable medical devices|
|US8293367||Jul 15, 2011||Oct 23, 2012||Advanced Cardiovascular Systems, Inc.||Nanoshells on polymers|
|US8333000||Jun 19, 2006||Dec 18, 2012||Advanced Cardiovascular Systems, Inc.||Methods for improving stent retention on a balloon catheter|
|US8343530||Dec 22, 2006||Jan 1, 2013||Abbott Cardiovascular Systems Inc.||Polymer-and polymer blend-bioceramic composite implantable medical devices|
|US8414642||Dec 1, 2008||Apr 9, 2013||Advanced Cardiovascular Systems, Inc.||Biodegradable stent of a polyorthoester polymer or a polyanhydride polymer|
|US8425591||Jun 11, 2007||Apr 23, 2013||Abbott Cardiovascular Systems Inc.||Methods of forming polymer-bioceramic composite medical devices with bioceramic particles|
|US8435550||Aug 13, 2008||May 7, 2013||Abbot Cardiovascular Systems Inc.||Anti-proliferative and anti-inflammatory agent combination for treatment of vascular disorders with an implantable medical device|
|US8465789||Jul 18, 2011||Jun 18, 2013||Advanced Cardiovascular Systems, Inc.||Rotatable support elements for stents|
|US8470014||Aug 14, 2007||Jun 25, 2013||Advanced Cardiovascular Systems, Inc.||Stent-catheter assembly with a releasable connection for stent retention|
|US8486135||Apr 9, 2007||Jul 16, 2013||Abbott Cardiovascular Systems Inc.||Implantable medical devices fabricated from branched polymers|
|US8535372||Jun 18, 2007||Sep 17, 2013||Abbott Cardiovascular Systems Inc.||Bioabsorbable stent with prohealing layer|
|US8568469||Jun 28, 2004||Oct 29, 2013||Advanced Cardiovascular Systems, Inc.||Stent locking element and a method of securing a stent on a delivery system|
|US8585754||Jan 13, 2012||Nov 19, 2013||Abbott Cardiovascular Systems Inc.||Stent formed of a Biodegradable material|
|US8592036||Sep 20, 2012||Nov 26, 2013||Abbott Cardiovascular Systems Inc.||Nanoshells on polymers|
|US8596215||Jul 18, 2011||Dec 3, 2013||Advanced Cardiovascular Systems, Inc.||Rotatable support elements for stents|
|US8603530||Jun 14, 2006||Dec 10, 2013||Abbott Cardiovascular Systems Inc.||Nanoshell therapy|
|US8637110||Jul 18, 2011||Jan 28, 2014||Advanced Cardiovascular Systems, Inc.||Rotatable support elements for stents|
|US8741379||Jul 18, 2011||Jun 3, 2014||Advanced Cardiovascular Systems, Inc.||Rotatable support elements for stents|
|US8747878||Apr 28, 2006||Jun 10, 2014||Advanced Cardiovascular Systems, Inc.||Method of fabricating an implantable medical device by controlling crystalline structure|
|US8747879||May 31, 2006||Jun 10, 2014||Advanced Cardiovascular Systems, Inc.||Method of fabricating an implantable medical device to reduce chance of late inflammatory response|
|US8752267||Aug 9, 2013||Jun 17, 2014||Abbott Cardiovascular Systems Inc.||Method of making stents with radiopaque markers|
|US8752268||Aug 9, 2013||Jun 17, 2014||Abbott Cardiovascular Systems Inc.||Method of making stents with radiopaque markers|
|US8778256||Sep 30, 2004||Jul 15, 2014||Advanced Cardiovascular Systems, Inc.||Deformation of a polymer tube in the fabrication of a medical article|
|US8808342||Apr 23, 2013||Aug 19, 2014||Abbott Cardiovascular Systems Inc.||Nanoshell therapy|
|US8846070||Jul 29, 2008||Sep 30, 2014||Advanced Cardiovascular Systems, Inc.||Biologically degradable compositions for medical applications|
|US8925177||Jul 17, 2012||Jan 6, 2015||Abbott Cardiovascular Systems Inc.||Methods for improving stent retention on a balloon catheter|
|US9038260||May 8, 2014||May 26, 2015||Abbott Cardiovascular Systems Inc.||Stent with radiopaque markers|
|US9072820||Jun 26, 2006||Jul 7, 2015||Advanced Cardiovascular Systems, Inc.||Polymer composite stent with polymer particles|
|US9173733||Aug 21, 2006||Nov 3, 2015||Abbott Cardiovascular Systems Inc.||Tracheobronchial implantable medical device and methods of use|
|US9198785||Dec 4, 2013||Dec 1, 2015||Abbott Cardiovascular Systems Inc.||Crush recoverable polymer scaffolds|
|US9248034||Aug 23, 2005||Feb 2, 2016||Advanced Cardiovascular Systems, Inc.||Controlled disintegrating implantable medical devices|
|US9259341||Feb 27, 2013||Feb 16, 2016||Abbott Cardiovascular Systems Inc.||Methods for improving stent retention on a balloon catheter|
|US9283099||Aug 25, 2004||Mar 15, 2016||Advanced Cardiovascular Systems, Inc.||Stent-catheter assembly with a releasable connection for stent retention|
|US9295570||Feb 23, 2005||Mar 29, 2016||Abbott Laboratories Vascular Enterprises Limited||Cold-molding process for loading a stent onto a stent delivery system|
|US9358325||Apr 22, 2015||Jun 7, 2016||Abbott Cardiovascular Systems Inc.||Stents with radiopaque markers|
|US20030171804 *||Jun 18, 1998||Sep 11, 2003||Werner Krause||Stents coated with fluoroalkyl groups|
|US20060271165 *||Aug 1, 2006||Nov 30, 2006||Yip Philip S||Drug-eluting stent cover and method of use|
|US20060271170 *||May 31, 2005||Nov 30, 2006||Gale David C||Stent with flexible sections in high strain regions|
|US20060287709 *||Aug 25, 2006||Dec 21, 2006||Advanced Cardiovascular Systems, Inc.||Drug-eluting stent and methods of making the same|
|US20070073383 *||Aug 1, 2006||Mar 29, 2007||Yip Philip S||Drug-eluting stent cover and method of use|
|US20070282434 *||Sep 19, 2006||Dec 6, 2007||Yunbing Wang||Copolymer-bioceramic composite implantable medical devices|
|DE2945138A1 *||Nov 8, 1979||May 29, 1980||Peter John Fydelor||Biokompatibles material und seine verwendung|
|DE3709069A1 *||Mar 19, 1987||Oct 1, 1987||Ohi Seisakusho Co Ltd||Drahtbefestigungseinrichtung fuer eine fenster-reguliervorrichtung|
|EP0061312A1 *||Mar 18, 1982||Sep 29, 1982||Board Of Regents The University Of Texas System||Alkyl-substituted polymers having enhanced albumin affinity|
|EP0073978A2 *||Aug 18, 1982||Mar 16, 1983||Asahi Glass Company Ltd.||Antithrombogenic materials|
|EP0073978A3 *||Aug 18, 1982||Sep 28, 1983||Asahi Glass Company Ltd.||Antithrombogenic materials|
|EP0076714A1 *||Sep 13, 1982||Apr 13, 1983||COMMISSARIAT A L'ENERGIE ATOMIQUE Etablissement de Caractère Scientifique Technique et Industriel||Polymeric bone joint prosthesis and method of preparing the same|
|EP0873756A2 *||Mar 13, 1998||Oct 28, 1998||Hüls Aktiengesellschaft||Antibacterial blood compatible modified surfaces|
|WO1988006026A2 *||Feb 17, 1988||Aug 25, 1988||Alberto Arpesani||Internal prosthesis for the substitution of a part of the human body particularly in vascular surgery|
|WO1988006026A3 *||Feb 17, 1988||Oct 6, 1988||Alberto Arpesani||Internal prosthesis for the substitution of a part of the human body particularly in vascular surgery|
|U.S. Classification||424/422, 428/421, 433/169, 623/1.1|
|International Classification||A61K6/08, A61F2/06, A61L33/06, A61F2/00, A61K6/083|
|Cooperative Classification||A61F2/0077, A61F2/06, A61K6/08, A61K6/083, A61L33/066|
|European Classification||A61K6/083, A61L33/06B2, A61K6/08, A61F2/06, A61F2/00L|