|Número de publicación||US4743258 A|
|Tipo de publicación||Concesión|
|Número de solicitud||US 06/722,669|
|Fecha de publicación||10 May 1988|
|Fecha de presentación||12 Abr 1985|
|Fecha de prioridad||27 Abr 1984|
|Número de publicación||06722669, 722669, US 4743258 A, US 4743258A, US-A-4743258, US4743258 A, US4743258A|
|Inventores||Yoshito Ikada, Hiroo Iwata, Masakazu Suzuki|
|Cesionario original||Japan Medical Supply Co., Ltd., Yoshito Ikada|
|Exportar cita||BiBTeX, EndNote, RefMan|
|Citas de patentes (22), Otras citas (4), Citada por (81), Clasificaciones (14), Eventos legales (7)|
|Enlaces externos: USPTO, Cesión de USPTO, Espacenet|
This invention relates to a material which exhibits excellent blood compatibility. More particularly, it relates to a blood-compatible material suitable for small-diameter vascular prostheses.
Vascular prostheses are examples of materials which must be compatible with blood. However, vascular prostheses currently available are prepared from polyester knitted web or porous polytetrafluoroethylene and exhibit insufficient blood compatibility, so that they are usable only for arteries of a large diameter wherein thrombotic occlusion rarely occurs. When these vascular prostheses are employed for arteries of a small diameter or for veins, thrombosis and resultant occlusion often would occur within a short period of time.
Various materials having improved blood compatibility have been proposed as will be described hereinafter. However, each of them is somewhwat unsuitable for use in vascular prostheses of small diameter. In Japanese Patent Publication No. 42759/1971 and Japanese Patent Laid-Open Nos. 150793/1975 and 24651/1976, blood-compatible materials which are prepared from hydrogel obtained by crosslinking hydrophilic polymers such as poly(2-hydroxyethyl methacrylate) and polyvinyl alcohol are disclosed. However, these materials cannot be applied to vascular prostheses because of their insufficient blood compatibility and low strength. Japanese Patent Laid-Open Nos. 125493/1974 and 125978/1976 disclose processes for improving blood compatibility by graft polymerizing the above mentioned hydrophilic polymer(s) onto the surface of a base material. The blood-compatible material which is prepared according to the foregoing processes with the use of an appropriate base material would exhibit satisfactory tensile strength. However, the blood compatibility thereof is similar to those of the hydrophilic polymers. Therefore thrombosis and resulting occlusion would occur within a short period of time if this material were used for vascular prostheses of small diameter.
In addition, Japanese Patent Laid-Open Nos. 66187/1973 and 106778/1978 disclose processes for imparting blood compatibility by fixing anticoagulants such as heparin or urokinase onto the surface of certain materials. The blood compatibility of a material thus obtained is high at the beginning but gradually decreases so that it is impossible to obtain a stable, satisfactory blood compatibility level. This instability may be caused by a decrease in the anticoagulant effect resulting from gradual denaturation of the anticoagulants fixed on the surface of the material. These processes have another disadvantage in the high cost of the anticoagulants themselves as well as the expense required for the fixing treatment.
Thus, despite the numerous proposals as described above, no material which exhibits excellent blood compatibility for a long period of time is available for vascular prostheses of small diameter.
It is an object of the present invention to provide a material which has excellent blood compatibility and can be used in vascular prostheses of small diameter. It is another object of the present invention to provide a material on which there is hardly any adsorption of protein.
The aforementioned objects can be achieved by attaching 1 to 100 μg/cm2, preferably 10 to 50 μg/cm2, of water-soluble and substantially nonionic polymer(s) onto the surface of a polymeric base material.
The term "water-soluble and substantially nonionic polymer(s)" as used herein means those which are soluble in water as a single polymer and have no or few ionic groups. Water-soluble polymers having many ionic groups cannot be employed since they exhibit poor blood compatibility. Examples of preferred polymers are: acrylamide polymers such as polyacrylamide and polydimethylacrylamide; methacrylamide polymers such as polymethylacrylamide; polyvinylpyrrolidone; partially or completely saponified polyvinyl alcohol; polyethylene glycol; and dextran. For blood compatibility, polyacrylamide polymers, polyvinylpyrrolidone and polyvinyl alcohol are particularly preferred. One or more of these polymers may be employed. The polymers may be either homopolymers or copolymers. As described above, the polymer(s) used in the present invention should be water-soluble. However, they need not necessarily be water-soluble at normal temperature and those soluble in water at elevated temperatures are also available.
The water-soluble and substantially nonionic polymer(s) should be attached onto the surface of a polymeric base material at a ratio of 1 to 100 μg/cm2, which is significantly lower than the amount of hydrophilic polymers used in the conventional graft polymerization. The conventional graft polymerization is based on recognition that a base material coated with hydrophilic polymers would exhibit blood compatibility similar to those of the hydrophilic polymers. Thus approximately 10 to 100 mg/cm2 of hydrophilic polymers are subjected to graft polymerization to thereby completely coat the surface of the base material. Accordingly, the graft polymerization results in an increase in the weight of the sample by approximately 1 to 20%. On the contrary, the water-soluble polymer layer in the process of the present invention is so thin that it hardly brings about any increase in the weight. Thus, it has been unexpectedly found that higher blood compatibility would be obtained by attaching a smaller amount of polymer(s). It is particularly preferred to attach 1 to 50 μg/cm2 of polymer(s).
The water-soluble and substantially nonionic polymer(s) may be attached onto the surface of a base material in a manner well-known in the art under the conditions selected to allow the polymer(s) to be attached in the ratio as determined above. The attachment may be carried out by, for example, (A) forming radicals or peroxides on the surface of a base material and contacting monomer(s) therewith, thus effecting graft polymerization; or (B) previously forming polymer(s) and chemically attaching them onto the surface of the base material by taking advantage of reactive groups thereof. Said radicals or peroxides may be formed by (1) irradiating with high-energy radiation such as electron beam or γ-ray; (2) irradiating with UV light; (3) low-temperature plasma discharge; (4) corona discharge; (5) ozone treatment; and (6) adding a radical polymerization initiator such as benzoyl peroxide. Polymerization may be carried out by adding monomer(s) simultaneously with the base material to be treated at the treatment step or contacting the treated base material with the monomer(s). The amount of the polymer(s) to be attached may be adjusted by controlling various factors such as the condition under which the base material is treated, the period of contact with the monomer(s) and temperature. Examples of available monomers are acrylamide, dimethylacrylamide, methacrylamide, vinylpyrrolidone, vinyl acetate and ethylene oxide. Vinyl acetate may be converted into polyvinyl alcohol by saponifying after the polymerization.
Polymer(s) previously prepared may be attached onto the surface of a base material either by directly reacting reactive group(s) on the surface of the base material with that of the polymer(s) or via certain specific compounds. The latter method is suitable for polymers having hydroxyl group(s) in the molecule, such as polyvinyl alcohol, polyethylene glycol and dextran. These polymers may be preferably attached to the base material having hydroxyl group(s) via a diisocyanate compound.
A wide range of base materials may be used in the present invention; the particular polymeric materials may be used depending on the aimed purpose and usage. Examples of the polymeric material are polyethylene, ethylene/vinyl acetate copolymer optionally saponified partially or completely, polypropylene, propylene copolymer, polyvinyl chloride, polyvinylidene chloride, polystyrene, polyacrylonitrile, polymethyl methacrylate, styrene/butadiene block copolymers, acrylonitrile/butadiene/styrene block copolymers, polybutadiene, polyisoprene, polytetrafluoroethylene, polyethylene terephthalate, polyethylene isophthalate, polybutylene terephthalate, polyether/ester block copolymers, polycarbonate, nylon 6, nylon 66, nylon 12, polyurethane, polysulfone, polyether sulfone, silicone resin, silicone rubber and cellulose and derivatives thereof, and the like. When radicals or peroxides are formed on the surface of the base material to effect graft polymerization, these materials may be used without limitation. On the other hand, when polymer(s) are chemically attached onto the surface of the base material, ethylene/vinyl acetate copolymer optionally saponified partially or completely are preferably used since they have reactive groups on the surface.
The base material may be in any form such as nonporous, porous, fabric or knitted web depending on the purpose. It may also be in any shape such as a tube, a sheet, a plate, a block or fibers. Either a material comprising a single component or a compound material comprising a plurality of components may be used. Water-soluble polymer(s) may be attached onto the whole surface of the base material. Alternatively, they may be selectively attached to a particular part in contact with blood.
The material of the present invention has excellent blood compatibility and is suitable for vascular prostheses, in particular those having internal diameters of several mm or below. It is further available for other instruments and devices in direct contact with blood, such as an intravascular catheter, artificial heart, lung, kidney and liver and blood circuit. It is furthermore available for instruments for transfusion and hematometry since blood cells and platelets would hardly adhere thereto.
The material of the present invention is advantageous in that it may be prepared readily and inexpensively by chemically treating the base material. The non-limited shape thereof makes it available in various ways. Furthermore, it may be readily sterilized with steam or ethylene oxide without lowering the blood compatibility, thus increasing safety in application.
In the process of the present invention, it is essential to adjust the amount of the water-soluble and substantially nonionic polymer(s) to be attached so that is is within the aforementioned range. The amount of the attached polymer(s) may be determined by, e.g., the following methods.
(1) A sample is chemically treated to liberate a part or the whole of the attached polymer(s) to determine the liberated matter.
(2) A sample is dissolved in a solvent in which the base material is soluble but the water-soluble polymer(s) are insoluble in order to separate the water-soluble polymer(s), then the amount of polymer(s) is determined.
(3) The monomer(s) or polymer(s) to be used is previously labelled with a radioisotope and the radioactivity of the sample is determined after attachment to the base material.
(4) The amount of the attached polymer(s) is determined by attenuated total reflection infrared spectroscopy (ATR-IR) with the use of calibration curves which have been previously determined.
An appropriate method for determination may be selected depending on the base material and the attached polymer(s).
The following specific examples are furnished in order to illustrate the invention. They constitute exemplification only and are not to be regarded as limitations.
A high-density polyethylene film of 60 μm in thickness was cleaned by extraction with ethanol and irradiated with 60 Co γ-ray at a dose rate of 0.02 Mrad/hr to a dose of 1.5 Mrad in dry air. The irradiated film was stored in a desiccator for two days after the irradiation at room temperature. Then it was immersed in an aqueous solution containing 25% by weight of acrylamide and 5×10-4 mol/liter of FeSO4 in a test tube. After deaeration, the tube was sealed and allowed to stand in a thermostatic water bath at 15° C. to thereby carry out graft polymerization. After 25 hours, the tube was opened and homopolymer adhering to the surface of the film was removed by washing with water, thereby yielding a polyethylene film having polyacrylamide attached thereon.
The amount of the attached polyacrylamide in the sample thus obtained was determined in the following manner. The sample was immersed in 1.5N HCl and treated in an autoclave at 2.5 atm for 30 min to hydrolyze the polyacrylamide. Then it was neutralized with NaOH and a ninhydrin solution was added thereto. After reacting in an autoclave at 3 atm for five min, the absorbance of the reaction mixture was determined at 570 nm. The amount of the attached polyacrylamide was calculated by the determined value and a calibration curve which had been previously determined. The process for determining the attached polymer(s) in the above manner will be referred to as "ninhydrin method" hereinbelow.
The amount of the attached polyacrylamide in the foregoing sample as determined by this method was 12 μg/cm2. On the other hand, the amount of the attached polyacrylamide in a sample treated in the same manner except that it was not irradiated with γ-ray was zero within the range of allowable errors. No difference between the surfaces of the treated and untreated films was observed under a scanning electron microscope. The surface of the treated film was neutralized with NaOH and stained with toluidine blue. Optical microscopic observation of a section thereof revealed the localization of polyacrylamide on the surface of the film.
A commercially available polypropylene film of 50 μm in thickness was cleaned with methanol and subjected to corona discharge at atmospheric pressure in dry air. Two circular plates of stainless steel (φ 7.5 cm) were employed as electrodes and placed at a distance of 5.5 mm. Each electrode was covered with a glass plate of 2 mm in thickness. Slide glass plates were inserted as a spacer and the sample was placed therein. The discharge was conducted at a frequency of 60 Hz and at an applied volage of 9 kV for 30 sec. The corona discharge treated film was then immmersed in an aqueous solution containing 20% by weight of vinylpyrrolidone. After removing dissolved air, the solution was heated to 70° C. for three hours to accelerate graft polymerization of the vinylpyrrolidone. After removing homopolymer, the obtained product was dried and the amount of the attached polyvinylpyrrolidone was determined by infrared absorption with the guidance of the absorption wave number of carbonyl group at 1670 cm-1. Consequently it was found that the amount of the polyvinylpyrrolidone attached to the polypropylene film was 15 μg/cm2. The contact angles of the surfaces of the treated and untreated films to water were 35° and 90°, respectively.
A sheet of 0.1 mm in thickness was prepared from ethylene/vinyl acetate copolymer (EVA) containing 10% by weight of vinyl acetate by hot-pressing. The sheet was cleaned with ethanol and treated with argon gas plasma by a low-temperature plasma surface treatment apparatus at an output of 11.5 W, at a gas flow rate of 20 cm3 /min and at 0.04 Torr for 30 sec. The plasma-pretreated EVA sheet was then taken out and stored in a desiccator. The sheet was immersed in an aqueous solution containing 10% by weight of acrylamide and the air dissolved in the aqueous solution was replaced with nitrogen gas thereby carrying out graft polymerization at 50° C. for two hours. The amount of the attached polyacrylamide determined by the ninhydrin method was 18 μg/cm2. Optical microscopic observation of a stained section of the film revealed that the graft polymerization proceeded to a depth of approximately 0.2 μm from the surface.
The insides of a polyether urethane tube and a low-density polyethylene tube, each of 3 mm in internal diameter and 3.5 mm in external diameter, were subjected to corona discharge under various conditions and then polyacrylamide was graft polymerized thereto, thus obtaining tubes to which various amounts of polyacrylamide were attached. In order to examine the blood compatibility of these samples, adsorption of serum protein on the inside of the tubes was examined. Bovine serum albumin (BSA) and immuno-gamma-globulin (IgG) were fluorescently labelled with fluorescein isothiocyanate (FITC). These labelled materials were mixed respectively with non-labelled BSA and IgG to give aqueous protein solutions each containing 2 mg/ml of protein in total. The sample tubes as prepared above were immersed in these aqueous solutions at 37° C. for three hours to allow the adsorption of the protein. Then the surfaces of the tubes were slowly washed with a buffer solution to remove unadsorbed protein. Subsequently the adsorbed protein was hydrolyzed in an autoclave at 3 atm for one hour. The fluorescence intensity of the FITC was determined at an excitation wavelength of 490 nm and a fluorescence wavelength of 520 nm. The amount of the adsorbed protein was determined by the measured values and calibration curves which had been previously determined. Table 1 shows the result.
TABLE 1______________________________________Amount of Adsorbed Protein Adsorbed Attached Protein Polyacrylamide (μg/cm2) (μg/cm2) BSA IgG______________________________________Polyethylene tube 0 0.3 0.9 12 0.1 0.2 30 0.05 0.1 120 0.3 0.4 330 2.0 1.5Polyurethane tube 0 0.2 0.8 5 0.15 0.4 20 0.05 0.2 45 0.10 0.3 250 0.4 0.6 500 1.2 1.4______________________________________
Table 1 suggests that large amounts of protein would be adsorbed by untreated tubes and those to which more than 100 μg/cm2 of acrylamide is attached, while the amounts of the protein adsorbed by those to which 1 to 100 μg/cm2, in particular 10 to 50 μg/cm2, of polyacrylamide is attached are smaller. It is well known that the blood compatibility of a polymeric surface would increase with a decrease in the amount of protein, in particular glucoprotein such as IgG, adsorbed thereby (cf. S. W. Kim, E. S. Lee, J. Polym. Sci., Polym. Symposia, vol. 66, pp. 429-441 (1979)). Therefore, the result as shown above suggests that the material of the present invention has excellent blood compatibility.
A film of ethylene/vinyl alcohol copolymer containing 30 molar percent of ethylene of 50 μm in thickness was subjected to glow discharge. Acrylamide, dimethylacrylamide, acrylamido-2-methylpropane sulfonic acid (AMPS) and dimethylaminoethyl methacrylate (DMAEM) were independently graft polymerized thereto to give films to which 30 to 40 μg/cm2 of polymers were attached.
0.1 ml portions of platelet-rich plasma from which calcium ions had been removed were poured onto these treated films and an untreated film to examine the adhesiveness of the platelets in a conventional manner. Consequently it was found that numerous platelets adhered to the untreated film while none adhered to those to which polyacrylamide and polydimethylacrylamide were graft polymerized. On the other hand, a large number of platelets adhered to those to which anionic polyAMPS and cationic polyDMAEM were graft polymerized, some of which showed pseudopodia.
The result as mentioned above suggests that the attachment of water-soluble and ionic polymers would result in poor blood compatibility.
The same film of ethylene/vinyl alcohol copolymer as used in Example 5 was treated with hexamethylene diisocyanate in toluene in the presence of dibutyltin dilaurate as a catalyst to react the hydroxyl group on the surface of the film with one of the isocyanate groups of the hexamethylene diisocyanate, thereby attaching the hexamethylene diisocyanate and introducing the isocyanate group onto the surface of the film. Dextran of a degree of polymerization of 600 and polyvinyl alcohol of a degree of polymerization of 1700 were independently attached thereto by a urethane coupling reaction to give films to which 30 μg/cm2 and 20 μg/cm2 of polymers were attached.
The obtained films were subjected to the same test as shown in Example 5 to examine the adhesiveness of platelets. It was found that no platelet adhered to either film.
A low-density polyethylene tube of 1 mm in internal diameter and 1.3 mm in external diameter was cut into pieces of a length of 1.5 cm and the pieces were irradiated with electron beams in air at room temperature with the use of a Van De Graaff accelerator at an energy level of 1.5 MeV and at a dose rate of 0.1 Mrad/sec for 30, 70 and 300 sec, thereby preparing three types of samples. These samples were immersed in an aqueous solution containing 8×10-5 mol/liter of FeSO4 and 20% by weight of acrylamide at 15° C. for five hours for graft polymerization to thereby give samples to which 16 μg/cm2, 33 μg/cm2 or 150 μg/cm2 of polyacrylamide were attached. A sample irradiated for 70 sec was immersed in an aqueous solution containing 8×10-5 mol/liter of FeSO4 and 20% by weight of acrylic acid at 15° C. for five hours for graft polymerization thereby giving a sample to which 22 μg/cm2 of polyacrylic acid was attached.
These tubes and an untreated tube were implanted into the common carotid arteries of rats in the following manner. A rat was incised at the cervix to expose the common carotid artery. Approximately 1 cm of the artery was removed and substituted by the tube. Isobutyl cyanoacrylate was applied to the tube to effect anastomosis. After the completion of the anastomosis, blood was allowed to flow again and the artery was observed externally. In the case of the untreated tube, occlusion caused by thrombosis was observed within 5 min. and blood stopped flowing. In the case of the sample to which 22 μg/cm2 of polyacrylic acid was attached, occlusion was also observed within 10 min. On the contrary, blood continued to flow without any occlusion at least for two hours in the case of the samples to which 16 μg/cm2 or 33 μg/cm2 of polyacrylamide was attached. In the case of the sample to which 150 μg/cm2 of polyacrylamide was attached, occlusion was observed after one hour and 30 min.
A polyurethane tube of 3 mm in internal diameter and 3.5 mm in external diameter was formed by coating a bar of low-density polyethylene with a solution of 7% polyether urethane of an Hs hardness of 80 in dimethylformamide and then removing the bar. The obtained tube was immersed in methanol for a long time to remove dimethylformamide and subjected to corona discharge at 10 kV for one min. Acrylamide was immediately graft polymerized to the tube for two and six hours to give tubes to which 22 μg/cm2 and 150 μ/cm2 of polyacrylamide was attached, respectively. After removing homopolymer, the tubes were stored in a physiological saline solution. The cartoid artery of a mongrel dog was removed at a length of 3 cm and 3.5 cm of the polyurethane tube was inserted therein and anastomosed.
Blood was allowed to flow again and the artery was observed by naked eyes. In the case of the untreated tube, occlusion was observed within three hours. On the other hand, blood continued to flow for 20 hours in the case of the polyurethane tube to which 22 μg/cm2 of polyacrylamide was attached, while occlusion was observed after six hours in the case of the tube to which 150 μg/cm2 of polyacrylamide was attached.
|Patente citada||Fecha de presentación||Fecha de publicación||Solicitante||Título|
|US3730753 *||30 Jul 1971||1 May 1973||Eastman Kodak Co||Method for treating a web|
|US3969130 *||5 Feb 1973||13 Jul 1976||General Atomic Company||Carbon-coated articles and method of making same|
|US4008047 *||26 Dic 1974||15 Feb 1977||North Star Research Institute||Blood compatible polymers for blood oxygenation devices|
|US4143949 *||28 Oct 1976||13 Mar 1979||Bausch & Lomb Incorporated||Process for putting a hydrophilic coating on a hydrophobic contact lens|
|US4167045 *||26 Ago 1977||11 Sep 1979||Interface Biomedical Laboratories Corp.||Cardiac and vascular prostheses|
|US4193138 *||17 Ago 1977||18 Mar 1980||Sumitomo Electric Industries, Ltd.||Composite structure vascular prostheses|
|US4326305 *||26 Nov 1980||27 Abr 1982||Davidas Jean P||Method for making artifacts usable in vivo and a artifacts made by said method|
|US4377010 *||31 Oct 1979||22 Mar 1983||The Secretary Of State For Defence In Her Britannic Majesty's Government Of The United Kingdom Of Great Britain And Northern Ireland||Biocompatible material comprising a base polymer bulk graft polymerized with an ethylenically unsaturated carboxylic acid|
|US4378803 *||24 Nov 1980||5 Abr 1983||Unitika, Ltd.||Process for producing antithrombogenic vinyl acetate polymer or hydrolyzate thereof|
|US4387183 *||16 Oct 1981||7 Jun 1983||Atlantic Richfield Company||Thromboresistant molded article and method for its production|
|US4482577 *||16 Dic 1980||13 Nov 1984||Albert Goldstein||Coating process of elastomeric material|
|US4634599 *||2 May 1985||6 Ene 1987||General Electric Company||Method for making ordered monolayers of macromolecules|
|US4666437 *||5 Mar 1986||19 May 1987||Astra Meditec Aktiebolag||Hydrophilic coating|
|US4670313 *||27 Mar 1986||2 Jun 1987||Polymed Laboratories||Method for parting rubber and products formed thereby, and a method of making a blood vessel|
|JP46042759A *||Título no disponible|
|JPS4866187A *||Título no disponible|
|JPS5124651A *||Título no disponible|
|JPS5269985A *||Título no disponible|
|JPS49125493A *||Título no disponible|
|JPS50150793A *||Título no disponible|
|JPS51125978A *||Título no disponible|
|JPS52106778A *||Título no disponible|
|1||*||Polymors in Medicine; Ed: Chiellini et al.; Author:Jansen; pp. 287 295; 1983, Plenum Press, N.Y., N.Y.|
|2||Polymors in Medicine; Ed: Chiellini et al.; Author:Jansen; pp. 287-295; 1983, Plenum Press, N.Y., N.Y.|
|3||*||S. W. Kim, E. S. Lee, J. Polym. Sci., Polym. Symposia, vol. 66, pp. 429 441 (1979).|
|4||S. W. Kim, E. S. Lee, J. Polym. Sci., Polym. Symposia, vol. 66, pp. 429-441 (1979).|
|Patente citante||Fecha de presentación||Fecha de publicación||Solicitante||Título|
|US4834757 *||28 Mar 1988||30 May 1989||Brantigan John W||Prosthetic implant|
|US4878907 *||6 Nov 1987||7 Nov 1989||Ube-Nitto Kasei Co., Ltd.||Synthetic vascular prosthesis|
|US4941870 *||30 Dic 1988||17 Jul 1990||Ube-Nitto Kasei Co., Ltd.||Method for manufacturing a synthetic vascular prosthesis|
|US4955899 *||26 May 1989||11 Sep 1990||Impra, Inc.||Longitudinally compliant vascular graft|
|US4965112 *||1 Mar 1989||23 Oct 1990||Stichting Voor De Technische Wetenschappen||Method for applying a blood-compatible coating to polyether-urethane moulded articles and the polymether-urethane moulded articles coated in this way|
|US5010009 *||22 Ago 1989||23 Abr 1991||Commonwealth Scientific & Industrial Research Organisation & Telectronics Pty. Limited||Material for cell attachment and growth|
|US5055316 *||20 Abr 1988||8 Oct 1991||Washington Research Foundation||Tight binding of proteins to surfaces|
|US5061751 *||2 Jun 1989||29 Oct 1991||Exxon Chemical Patents Inc.||Vinylpyrrolidone grafted polyolefins in polymer blends and composites|
|US5085632 *||10 Abr 1990||4 Feb 1992||Japan Medical Supply Co., Ltd.||Catheter and method for the manufacture thereof|
|US5100422 *||26 May 1989||31 Mar 1992||Impra, Inc.||Blood vessel patch|
|US5104400 *||28 Ago 1991||14 Abr 1992||Impra, Inc.||Blood vessel patch|
|US5116361 *||7 Jun 1990||26 May 1992||Korea Institute Of Science And Technology||Sulfonated polyethyleneoxide-substituted polymers with improved blood compatibility|
|US5152782 *||26 May 1989||6 Oct 1992||Impra, Inc.||Non-porous coated ptfe graft|
|US5180392 *||15 Nov 1990||19 Ene 1993||Einar Skeie||Anastomotic device|
|US5216087 *||17 May 1991||1 Jun 1993||Korea Institute Of Science And Technology||Process for the preparation of sulfonated polyethyleneoxide-substituted polymers with improved blood compatibility|
|US5217492 *||3 Abr 1991||8 Jun 1993||Bio-Metric Systems, Inc.||Biomolecule attachment to hydrophobic surfaces|
|US5258041 *||19 Mar 1991||2 Nov 1993||Bio-Metric Systems, Inc.||Method of biomolecule attachment to hydrophobic surfaces|
|US5263992 *||24 Oct 1991||23 Nov 1993||Bio-Metric Systems, Inc.||Biocompatible device with covalently bonded biocompatible agent|
|US5330428 *||14 May 1991||19 Jul 1994||Scimed Life Systems, Inc.||Dilatation catheter having a random copolymer balloon|
|US5342386 *||26 Oct 1992||30 Ago 1994||Cordis Corporation||Catheter with multiple flexibilities along the shaft|
|US5348538 *||29 Sep 1992||20 Sep 1994||Scimed Life Systems, Inc.||Shrinking balloon catheter having nonlinear or hybrid compliance curve|
|US5358677 *||17 Mar 1992||25 Oct 1994||United States Surgical Corporation||Methods of forming bioabsorbable objects from polyvinyl alcohol|
|US5403340 *||18 May 1994||4 Abr 1995||Scimed Lifesystems Inc.||Shrinking balloon catheter having nonlinear compliance curve|
|US5433713 *||22 Jul 1993||18 Jul 1995||Cordis Corporation||Polyetheramide tubing for medical devices|
|US5451428 *||31 Mar 1992||19 Sep 1995||Hewlett-Packard Company||Method for pretreating the surface of a medical device|
|US5456666 *||26 Abr 1994||10 Oct 1995||Boston Scientific Corp||Medical balloon folding into predetermined shapes and method|
|US5476509 *||9 Jun 1994||19 Dic 1995||Medtronic, Inc.||Articles having graft polymer bioactive surfaces|
|US5500181 *||3 Ene 1995||19 Mar 1996||Scimed Life Systems, Inc.||Shrinking balloon catheter having nonlinear compliance curve|
|US5512329 *||27 Dic 1993||30 Abr 1996||Bsi Corporation||Substrate surface preparation|
|US5531717 *||6 Feb 1995||2 Jul 1996||Rtc, Inc.||Non-contaminating probe and methods of making and using same|
|US5545213 *||27 Abr 1995||13 Ago 1996||Medtronic, Inc.||Method for administering a bioactive agent|
|US5584875 *||13 Abr 1994||17 Dic 1996||C. R. Bard, Inc.||Method for making vascular grafts|
|US5585057 *||17 Jul 1995||17 Dic 1996||Cordis Corporation||Method for retarding blooming of polyetheramide tubing for medical devices|
|US5676688 *||1 Jul 1996||14 Oct 1997||Rtc, Inc.||Variably inflatable medical device|
|US5741551 *||23 Abr 1996||21 Abr 1998||Bsi Corporation||Preparation of polymeric surfaces|
|US5769781 *||13 Nov 1995||23 Jun 1998||Chappuis; James L.||Protector retractor|
|US5897535 *||8 Abr 1996||27 Abr 1999||Rtc, Inc.||Non-contaminating probe and methods of making and using same|
|US5928206 *||15 Oct 1997||27 Jul 1999||Mitsubishi Chemical Corporation||Medical device|
|US5977252 *||7 Mar 1996||2 Nov 1999||University Of Pittsburgh||Covalent modification of surfaces with polymers to increase biocompatibility|
|US6013055 *||13 Nov 1997||11 Ene 2000||Boston Scientific Corporation||Catheter balloon having selected folding characteristics|
|US6056993 *||17 Abr 1998||2 May 2000||Schneider (Usa) Inc.||Porous protheses and methods for making the same wherein the protheses are formed by spraying water soluble and water insoluble fibers onto a rotating mandrel|
|US6110192 *||8 Ene 1999||29 Ago 2000||Boston Scientific Corporation||Catheter balloon having raised radial segments|
|US6358557 *||10 Sep 1999||19 Mar 2002||Sts Biopolymers, Inc.||Graft polymerization of substrate surfaces|
|US6391052||29 Oct 1997||21 May 2002||Scimed Life Systems, Inc.||Stent with collagen|
|US6648836 *||30 Ago 2001||18 Nov 2003||Becton, Dickinson And Company||Blood gas syringe having improved blood barrier|
|US6695833||27 Sep 2000||24 Feb 2004||Nellix, Inc.||Vascular stent-graft apparatus and forming method|
|US6787179 *||29 Jun 2001||7 Sep 2004||Ethicon, Inc.||Sterilization of bioactive coatings|
|US6830782 *||28 Dic 2000||14 Dic 2004||Hitoshi Kanazawa||Hydrophilic polymer treatment of an activated polymeric material and use thereof|
|US6939377||20 Ago 2001||6 Sep 2005||Thoratec Corporation||Coated vascular grafts and methods of use|
|US7204947 *||30 Sep 2004||17 Abr 2007||Orthoplastics Limited||Method of crosslinking polyolefins|
|US7252856 *||23 Jul 2003||7 Ago 2007||Becton, Dickinson And Company||Blood gas syringe having improved blood barrier|
|US7700147||19 Ene 2004||20 Abr 2010||Lars- Laboratoire D'application Et De Recherche Scientifique||Biomimetic prosthetic ligament and production method thereof|
|US7993358||9 Ago 2011||Boston Scientific Scimed, Inc.||Cutting balloon catheter having increased flexibility regions|
|US7993566 *||9 Ago 2011||Dsm Ip Assets B.V.||Method for the production of medical implants|
|US8801768||23 Ene 2012||12 Ago 2014||Endologix, Inc.||Graft systems having semi-permeable filling structures and methods for their use|
|US8870941||31 Oct 2011||28 Oct 2014||Nellix||Graft systems having filling structures supported by scaffolds and methods for their use|
|US8906084||7 Ene 2010||9 Dic 2014||Nellix, Inc.||System and methods for endovascular aneurysm treatment|
|US8926682||23 Sep 2011||6 Ene 2015||Nellix, Inc.||Stent graft delivery system|
|US8945199||4 Jun 2009||3 Feb 2015||Nellix, Inc.||Sealing apparatus and methods of use|
|US9113999||22 Oct 2007||25 Ago 2015||Nellix, Inc.||Methods for deploying a positioning anchor with a stent-graft|
|US9289536||7 Mar 2014||22 Mar 2016||Endologix, Inc.||Method for forming materials in situ within a medical device|
|US20020065552 *||20 Ago 2001||30 May 2002||Jayaraman Ramesh B.||Coated vascular grafts and methods of use|
|US20030087982 *||28 Dic 2000||8 May 2003||Hitoshi Kanazawa||Method of modifying polymeric material and use thereof|
|US20030175408 *||29 Jun 2001||18 Sep 2003||Timm Debra A.||Sterilization of bioactive coatings|
|US20040116997 *||22 Sep 2003||17 Jun 2004||Taylor Charles S.||Stent-graft with positioning anchor|
|US20040131794 *||23 Jul 2003||8 Jul 2004||Cohen Richmond R.||Blood gas syringe having improved blood barrier|
|US20040167607 *||24 Feb 2004||26 Ago 2004||Frantzen John J.||Vascular stent-graft apparatus|
|US20050042612 *||30 Jul 2002||24 Feb 2005||Hubbard Michael Anthony||Graft polymer martrices|
|US20050070625 *||30 Sep 2004||31 Mar 2005||Perplas Limited||Method of crosslinking polyolefins|
|US20060136057 *||19 Ene 2004||22 Jun 2006||Lars Laboratoire D'application Et De Recherche Sci||Biomimetic prosthetic ligament and production method thereof|
|US20060184191 *||11 Feb 2005||17 Ago 2006||Boston Scientific Scimed, Inc.||Cutting balloon catheter having increased flexibility regions|
|US20070073328 *||12 Sep 2006||29 Mar 2007||Wilson-Cook Medical Inc.,||Incrementally expandable balloon|
|US20080012181 *||2 Jul 2007||17 Ene 2008||Cartifical A/S||Prosthetic device|
|US20080167724 *||17 Dic 2007||10 Jul 2008||Med Institute, Inc.||Stent graft with releasable therapeutic agent and soluable coating|
|US20100106087 *||7 Ene 2010||29 Abr 2010||Nellix, Inc.||System and methods for endovascular aneurysm treatment|
|EP0361814A2 *||22 Sep 1989||4 Abr 1990||Pall Corporation||Fluid treatment system having low affinity for proteinaceous materials|
|WO1997032617A1 *||7 Mar 1997||12 Sep 1997||University Of Pittsburgh||Covalent modification of surfaces with polymers to increase biocompatibility|
|WO2001017575A1 *||4 Ago 2000||15 Mar 2001||Sts Biopolymers, Inc.||Graft polymerization of substrate surfaces|
|WO2001076652A1 *||30 Mar 2001||18 Oct 2001||Therapeutiques Substitutives||Vascular prosthesis impregnated with crosslinked dextran|
|WO2001087184A1 *||16 May 2001||22 Nov 2001||Frantzen John J||Radially expandable stent featuring aneurysm covering surface|
|WO2004067051A1 *||19 Ene 2004||12 Ago 2004||L.A.R.S. - Laboratoire D'application Et De Recherche Scientifique||Biomimetic prosthetic ligament and production method thereof|
|Clasificación de EE.UU.||623/1.49, 623/1.44, 428/341, 427/255.6, 427/2.25, 428/36.9|
|Clasificación internacional||A61L33/00, A61F2/06|
|Clasificación cooperativa||Y10T428/273, A61F2/06, A61L33/0088, Y10T428/139|
|Clasificación europea||A61F2/06, A61L33/00R4|
|1 Jul 1985||AS||Assignment|
Owner name: JAPAN MEDICAL SUPPLY CO., LTD, 12-17, KAKO-MACHI,
Free format text: ASSIGN TO EACH ASSIGNEE 50% INTEREST;ASSIGNORS:IKADA, YOSHITO;IWATA, HIROO;SUZUKI, MASAKAZU;REEL/FRAME:004422/0887
Effective date: 19850601
Owner name: YOSHITO IKADA, 2-182 HIROOKADANI GOKASHO, UJI-CITY
Free format text: ASSIGN TO EACH ASSIGNEE 50% INTEREST;ASSIGNORS:IKADA, YOSHITO;IWATA, HIROO;SUZUKI, MASAKAZU;REEL/FRAME:004422/0887
Effective date: 19850601
|19 Ago 1991||FPAY||Fee payment|
Year of fee payment: 4
|14 Jun 1994||AS||Assignment|
Owner name: JMS CO., LTD., JAPAN
Free format text: CHANGE OF NAME;ASSIGNOR:JAPAN MEDICAL SUPPLY CO., LTD.;REEL/FRAME:007095/0629
Effective date: 19940401
|18 Sep 1995||FPAY||Fee payment|
Year of fee payment: 8
|30 Nov 1999||REMI||Maintenance fee reminder mailed|
|7 May 2000||LAPS||Lapse for failure to pay maintenance fees|
|18 Jul 2000||FP||Expired due to failure to pay maintenance fee|
Effective date: 20000510