|Publication number||US3883901 A|
|Publication date||20 May 1975|
|Filing date||27 Nov 1973|
|Priority date||1 Dec 1972|
|Also published as||CA1023493A, CA1023493A1, DE2359865A1|
|Publication number||US 3883901 A, US 3883901A, US-A-3883901, US3883901 A, US3883901A|
|Inventors||Jean Coquard, Michel Ruaud, Pierre Sedivy, Jean Verrier|
|Original Assignee||Rhone Poulenc Sa|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (3), Referenced by (47), Classifications (22)|
|External Links: USPTO, USPTO Assignment, Espacenet|
United States Patent 1 Coquard et al.
 Assignee: Rhone-Poulenc, S.A., Paris, France  Filed: Nov. 27, 1973  Appl. No: 419,450
 Foreign Application Priority Data Dec. 1, 1972 France 72.42838  US. Cl 3/1; 3/D1G. l; 128/92 B; 128/92 C; 128/334 R; l28/335.5; 260/78 A  Int. Cl A61f l/24; A611 17/00  Field of Search 3/1, DIG. 1; 128/334 R, 128/334 C, 335.5, 92 C, 92 CA, 92 B, 92 D;
260/75 R, 75 T, 78 A  References Cited UNITED STATES PATENTS 2,071,250 2/1937 Carothers 260/78 A 1451 May 20, 1975 8/1969 Schmitt et a1 3/1 X 11/1971 Schmitt et a1 128/334 R OTHER PUBLICATIONS Polyesters, by V. V. Korshak, et a1., Pergamon Press, Oxford London, Edinburgh, New York, Paris, Frankfurt, 1965, pp. 31 and 53.
Primary ExaminerRonald L. Frinks Attorney, Agent, or Firm-Cushman, Darby & Cushman  ABSTRACT Implantable surgical articles are provided which are at least partially bioresorbable and which consist at least partially of a polyester of succinic acid possessing a plurality of units of the general formula:
in which R represents a linear or branched alkylene radical containing 2 to 6 carbon atoms. They are particularly suitable as sutures.
15 Claims, N0 Drawings METHOD OF REPLACING OR REPAIRING THE BODY WITH BIORESORBABLE SURGICAL ARTICLES The present invention relates to surgical articles which are biologically partially or completely resorbable after implantation in living human or animal tissues.
It is known that human or animal surgery is making use of more and more articles produced from natural or synthetic materials, in order to restore living tissues or to strengthen, repair and even replace various organs. For this purpose, surgical articles are placed in position either temporarily or permanently. In the case of temporary implantation, it has been considered preferable to make use of bioresorbable materials, that is to say materials which undergo degradation and which disappear after they have been implanted after a certain length of time, due to a biochemical process. It is important that the material used and its degradation products should not cause any unfavourable reaction of the surrounding tissues. With a permanent implantation, for example for replacing or strengthening a failing organ, non-resorbable articles are obviously used; it has been found, however, that in the majority of cases, the integration of the prosthesis and its joining to the adjacent tissues are facilitated if the prosthesis is made partly of a bioresorbable material which is gradually replaced by the adjacent tissues so as to form an intimate join between the latter and the implanted foreign body.
The elements for sutures and for ligatures intended for closing wounds and for repairing blood vessels, nerves and tendons are examples of surgical articles which are implanted temporarily. These elements are generally filaments, but they can also be in other forms, for example as clips or tapes. The most commonly used bioresorbable material for making suture or ligature filaments is catgut prepared from the collegen of mammals; the sub-muccous layer of the small intestine of sheep is most frequently employed. Catgut possesses numerous disadvantages, such as difficulty in obtaining it, the unfavourable reactions which it causes with living tissues and the lack of uniformity of its mechanical properties. Consequently, ways have been sought of replacing it by bioresorbable synthetic materials which can easily be converted into continuous filaments by extrusion techniques, and which possess readily reproducible mechanical properties. Various materials have been proposed for this purpose. Thus Belgian Pats. Nos. 679,726 and 758,156 describe elements for sutures and ligatures and other partially or completely bioresorbable surgical articles, which consist of polyesters of copolyesters derived from lactic acid and produced by polycondensation of a lactide (preferably a L-lactide) alone or combined with other derivatives of acid-alcohols such as glycolide, tetramethylglycolide, B-propiolactone and B-butyrolactone. Although they possess advantages relative to catgut, these polyesters are very sensitive to moisture and this has a detrimental effect on their mechanical properties so that it is necessary to store the surgical elements and especially the suture filaments made from them in hermetically sealed packaging. Hence they are not completely satisfactory.
In addition, it is known that it is important that the surgeon should have at his disposal various materials which provide him with a wide range of bioresorbable properties. In fact, the duration of the resorption varies with the nature of the wound and with the nature of the tissues involved in the cicatrization process; it also varies from one individual to another and with the type of insertion in the case of prosthesis. The development of new bioresorabable materials increases the number of possibilities from which the surgeon can choose and there is, consequently, a demand for new bioresorbable materials.
According to the present invention there is provided a surgical article which can be used in human or animal surgery, which is completely or partially bioresorbable and which consists wholly or partially of a bioresorbable material consisting of a polyester of succinic acid possessing a plurality of units of the general formula:
in which R represents a linear or branched alkylene radical containing 2 to 6 carbon atoms. More specifically, R can be an ethylene, methylethylene, 1,2- dimethylethylene, trimethylene, 2-methyltrimethylene, 2,Z-dimethyl-trimethylene, l-methyltrimethylene, tetramethylene, pentamethylene or hexamethylene radical.
The bioresorbable character shown by the polyesters of formula (I), denoted hereafter by the general term polysuccinate, is unexpected because it is known that polyesters such as polyethylene glycol terephthalate are not resorbed by human or animal tissues (see U.S. Pat. No. 3,463,158). It has been found that, in addition to their bioresorbable character, the polysuccinates are particularly well tolerated by the tissues in which they are implanted; thus no inflammatory reaction has been observed after a long-lasting implantation of polyethylene glycol succinate filaments in rats. Moreover, the polysuccinates possess excellent mechanical properties (notably tensile strength, tensile strength at knots and dimensional stability) and are insensitive to moisture, which make them particularly suitable for the manufacture of surgical articles and especially elements for sutures. Polysuccinate filaments are easy to handle and do not necessitate the use of special storage devices.
Polyglycol succinates have been known for a very long time (see, for example, U.S. Pat. No. 2,071,250; and V. V. KORSHAK and S. V. VINOGRADOVA, Polyesters, edited by PERGAMON PRESS Ltd., 1965, pages 31 to 46). They can be prepared by the usual polycondensation processes such as those described by V. V. KORSHAK and S. V. VINO- GRADOVA, loc. cit., or in HOUBEN WEYL, Methoden der Organische Chemie Makromolekulare Stoffe, volume 14/2, pages 1 to 29. Thus it is possible, for example, to use bulk polycondensation of glycols with free succinic acid or dimethyl succinate in the presence of the usual esterification or transesterification catalysts such as sulphuric or p-toluenesulphonic acids, or metal salts or oxides such as calcium oxide, strontium oxide, zinc oxide, aluminium oxide, bismuth oxide, iron oxide, titanium oxide, lead oxide, antimony oxide, cobalt oxide, calcium chloride, zinc acetate and zinc borates.
As glycols which can be used to prepare the polyesters used in the present invention, there may be mentioned ethylene glycol, propylene glycol, propane-1,3- diol, 2-methyl-propanel ,3-diol, 2,2-dimethylpropane-1,3-diol, butane-1,4-diol, butane-1,3-diol, butane-2,3-diol, pentane-1,5-diol and hexane-1,6-diol. These various glycols can be used separately or as a mixture with one another. Use can thus be made of mixtures containing 1 to 99 mol of ethylene glycol and 99 to 1 mol of one or more other glycols such as 2-methylpropane-1,3-diol and 2,2-dimethylpropane-1,3-diol.
The molecular weight of the polysuccinates used for the production of surgical articles according to the present invention can vary within very wide limits but it should generally be sufficiently high to render them suitable for the formation of films and fibres. Generally it should be sufficiently high for the polymer to be converted into filaments and films which can be orientated. The upper limit is not critical, subject to the condition that the product can be processed by the usual moulding or shaping techniques.
Polysuccinates can be used for the production of extremely diverse surgical articles, such as those described in Handbook of Biomedical Plastics, H. LEE and K. NEVILLE, 1971, Pasadena Technology Press. They are particularly suitable for the production of elements for surgical sutures and ligatures, especially in the form of twisted or non-twisted filaments, tapes, bristles, tents or spun fibres. They can also be used in the form of single filaments, twisted filaments, stranded filaments, gathered filaments, texturized filaments or lapped filaments; these various terms are used in accordance with the definition which is given of them in French Standard Specification NF G -005. These various elements for sutures can consist wholly or partially of the bioresorbable polysuccinates. Thus use can be made of a filament of the polysuccinate or of a filament comprising a core of a non-resorbable synthetic material such as polyethylene glycol terephthalate, polyamide or polypropylene, and an outer coating of polysuccinates. It is likewise possible to use a composite element consisting of a yarn of natural material, e.g., linen or silk, or synthetic material covered with a polysuccinate, or of a yarn of variable structure comprising bioresorbable filaments and nonresorbable filaments.
Amongst the other surgical articles for which the polysuccinates of the formula (1) can be used, there may be mentioned knitted fabrics comprising resorbable yarns and optionally non-resorbable yarns or nonresorbable yarns covered with a layer of polysuccinate; non-woven fabrics prepared from non-bioresorbable fibresand a resorbable binder; and sheets made from non-resorbable materials covered on one or both faces by a polysuccinate. The wholly or partially resorbable knitted and woven fabrics can be used in the form of sheaths intended to facilitate the implantation of diverse prostheses such as that described in French Pat. Nos. 2,031,699 and 2,071,172 for correcting valvular illnesses, and especially of the mitral valve; tubes for the removal of biological liquids (in particular, artificial ureters) as described in French Pat. No. 2,133,083, and vascular prostheses such as those described in French Pat. No. 2,112,032.
The polysuccinates of formula (1) are also very suitable for the production of surgical articles such as tubes of various shapes, for example Y-shaped tubes and T- shaped tubes, bars, plates, rings and screws, intended to be implanted temporarily or permanently. Partially or completely bioresorbable tubular prostheses have been described in US Pat. Nos. 2,127,903, 3,272,204, 3,304,557, 3,316,557, and 3,479,670 to which reference should be made for further details.
The shaping of the polysuccinates of formula (I) for the production of surgical articles can be carried out by the usual methods. Thus filaments, tapes or sheets can be produced by extrusion of the polymer in the molten state, followed by stretching at a sufficiently high ratio to cause the orientation of the chains of the polymer, and the fixing of the article thus produced.
The polysuccinates of formula (I) can contain various adjuvants such as fillers, dyestuffs and plasticizers which are chemically inert and do not bring about any reactions with the living tissues.
They can be used alone or mixed with nonbioresorbable materials, as indicated above, or with materials which are more or less resorbable in themselves, for example, respectively, polyesters of the polyethylene glycol terephthalate or adipate type, or of the polylactide or polyglycolide type.
The surgical articles according to the invention can be sterilized easily by the techniques usually employed in surgery, for example by radiation treatment.
The following Examples further illustrate the present invention.
EXAMPLE 1 1. Preparation of polyethylene glycol succinate 174g. (1 mol) of diethyl succinate, 93 g. (1.5 mols) of ethylene glycol, 0.280 g. of zinc acetate and 0.070 g. of antimony trioxide are introduced, under a stream of nitrogen, into a 300 cm glass flask equipped with a scraping stirrer, a gas inlet tube, a gas outlet tube, a thermometer, a thermostatically controlled metal heating bath and a distillation column provided with a condenser and a receiving container. The contents of the flask are heated to 180C., with stirring, and these conditions are maintained for 1 hour 30 minutes. The temperature of the reaction mixture is then raised to 240C., over the course of 50 minutes and the apparatus is connected to a vacuum pump in order to reduce the pressure in the apparatus to 0.1 mm.Hg over the course of 30 minutes. The whole is maintained under these conditions for 6 hours 30 minutes. The viscous, light brown reaction mixture is dissolved in hot dioxane and then reprecipitated with methanol. A product is obtained which is filtered off and dried at 80C. in a vacuum oven. In this way, 112 g. of polymer are obtained.
In all, 2 mols of ethanol, 0.368 mol of ethylene glycol and 0.07 mol of diethyl succinate are collected in the various distillates from the reaction. Taking account of the fact that a further 5 g. of polyester are recovered on the walls of the apparatus, the degree of polycondensation rises to 85.5%
The polyester thus obtained has a viscosity of 69 cm"*/g., measured at 25C., on a 4 g/l solution in chloroform and a viscosity of 70 cm/g, measured at 25C. in a 2 g/l solution in meta-cresol. lt melts at 104C., and is not decomposed by heating under nitrogen at 300C.
A filament of gauge 20 decitex is prepared from this polyester by inelt spinning under 30 bars and stretching the yarn issuing from the spinneret in a ratio of 7 at 55C. This filament possesses the following mechanical properties:
tensile strength in accordance with Standard Specification NF G 07,008, April 1961, 2 g/dicitex, elongation at break in accordance with Standard Specification NF G 07,008, 50%, tensile strength at knots, in accordance with Standard Specification NF G 07,008, 1.66 g/decitex, shrinkage in water at 40C. in accordance with Standard Specification BNMP 14,732/27 of February 1972 4% 2. Determination of the local tolerance of implant in rats Using the polyethylene glycol succinate obtained as described above, a stretched filament of diameter 300 to 400 p. is produced and is sterilized by immersion for 1 hour in 70 GL ethyl alcohol.
Samples of length 1 cm are implanted, with a curved needle, in rats (Caesarean Originated, Barrier Sustained) weighing 250 to 350 g; the implantation is carried out, on the one hand, in the paravertebral muscles, and on the other hand, under the skin of one of the sides of each animal. Four rats (2 male and 2 female) each received two implants. Two months after the implantation, the animals are killed and the muscular implantation region (implant and paravertebral muscular mass) and the subcutaneous implantation region (skin, implant and underlying muscular portion) are removed in each case. The following examinations are carried out on each specimen removed:
a. Macroscopic examination after transverse section of one of the ends of the muscular mass (intramuscular implant) or detachment of the skin at one end (subcutaneous implant) of each specimen.
b. Histological examination after fixing the specimens in BOUIN liquid, inclusion in paraffin, cutting of 5 p. thick sections and colouration by means of hemalun-phloxine saffron. The following results were obtained:
a. Macroscopic examination Two months after the implantation, no macroscopically detectable tissue reaction was observed either at the muscle level or at the subcutaneous tissue level.
b. Histological examination Reaction of the tissues This reaction is limited to a very inconspicuous fibrous sheath around the implant and to the presence of a few multinucleate giant macrophage and histiocyte cells situated in contact with the implant itself.
No change which could relate to a possible toxic effect of the material was detected on the sections.
In short, the local tolerance in rats is very good from the macroscopic point of view and from the histological point of view.
3. Determination of the bioresorbability in vitro The bioresorbability of the polyethylene glycol succinate produced above is determined by measuring the variation in the reduced viscosity of a sample of polymer taken in the form of flakes and incubated for varying periods of time in an enzyme extract. The test was carried out in the following manner:
a. Preparation of the enzyme extract Fauves de Bourgogne rabbits, of approximately 2.5 kg, are killed with chloroform. The muscles from the back and the thighs are removed and are frozen at 20C. They are then ground rapidly in a meat mincing machine. 300 g. of ground material are dispersed in 500 ml. of 0.2 M citrate buffer of pH 4.1, which have previously been cooled to +2". The suspension obtained is ground again twice for 1 minute (grinder turning at 2,000 revolutions/minute), with external cooling (ice and salt mixture at about -13C.) to keep the temperature of the homogenized material below +l0C. during the operation.
The homogenized material is then subjected to an ultrasonic treatment (frequency: 20 kHz) for 2 minutes with the same cooling precautions. It is then centrifuged at 6,500 G, at 0 for 20 minutes. The supernatant liquid, filtered through glass wool, forms the enzyme extract; its pH is approximately 4.5.
b. Reaction between the product to be investigated and the enzyme extract A sample of 100 mg. of the polymer to be investigated is incubated at 37C., with agitation (shaking table turning at revolutions/minute), in the following reaction mixture:
Enzyme extract 40 ml. Streptomycin sulphate 2 mg. Sodium salt of penicillin G 2 mg. Sodium nitride 8 mg.
This reaction mixture is renewed every day; during each renewal, the samples are carefully washed with distilled water.
In parallel,.other samples of mg. of the product to be investigated are incubated in reaction mixtures in which the enzyme extract is replaced by an inactivated enzyme extract (heating for 30 minutes at 100C.) or by 0.2 M citrate buffer of pH 4.5.
The product to be investigated, in the form of flakes, is enclosed in a guaze bag for the incubation.
c. Examination of the polymer after reaction After hours of incubation, the samples of the product to be investigated are recovered,washed several times with distilled water, drained on filter paper and dried under reduced pressure at 50C.
The reduced specific viscosity of solutions of the product in 1,2-dichloro-ethane, at 40C., as well as that of the product before incubation, is then determined.
The following results were obtained:
Nature of the incubation Reduced medium specific viscosity None 52 Citrate buffer 54 inactivated enzyme extract 56 Active enzyme extract 34 It is found, under these conditions, that incubation in the active enzyme extract results in considerable degradation of the polyester.
EXAMPLES 2 1. Preparation of polybutane-1,4-diol succinate 1 hour and then to 240C. over the course of 30 minutes, and the pressure is reduced to 0.1 mm.Hg over the course of 40 minutes. After 4 hours 40 minutes under these conditions, the reaction is stopped.
In this way, 146.7 g. (degree of polycondensation 85.3%) of greyish polymer are obtained which are dissolved in 400 cm of hot dioxane. The polymer is reprecipitatedby introducing the solution into 3 l. of methanol, and is then filtered off and dried at 50C., in vacuo. 138 g. of white polymer, having a viscosity of 94-97 cm lg, measured at 25C., in a 2 g/l solution in meta-cresol, and having a melting point of 1 14C., are recovered.
Filaments of gauge 21 decitex are prepared from the polymer thus produced by melt spinning under 61 bars and stretching at 85C.
The filaments possess the following mechanical properties:
elongation at break (Standard Specification NF G 07,008, April 1961) 50% tensile strength (Standard Specification NF G 07,008)
2. Implantation of a braid in rats The implantation is carried out on four rats of the same origin as in Example 1 and in a rigorously identical manner. After two months of implantation, the rats are killed and the same samples are removed and the same examinations carried out as in Example 1. The results obtained were as follows:
A. Macroscopic examination Two months after the implantation, no macroscopically detectable tissue reaction was observed either at the muscle level or at the subcutaneous tissue level.
B. Histological examination Reaction of the tissues The local tolerance is good; reaction to the implantation is limited to the immediate periphery of the implant and remains inconspicuous. No change in the tissue due to a toxic effect of the products was detected.
Resorption of the implants After two months of implantation, the number of strands visible in the sections of the intramuscular implants is 3 out of the originally present.
1. in a method of repairing or replacing a part of the body of a human of non-human animal by incorporating either temporarily or permanently, a surgical article, the improvement wherein the surgical article consists at least partially of a polyester of succinic acid possessing a plurality of units of the general formula:
'c l C-0- in which represents a linear or branched alkylene radical containing 2 to 6.carbon atoms having a filmor filament-forming molecular weight.
2. The method according to claim 1 in which the polyester is polyethylene glycol succinate 3. The method according to claim 1 in which the surgical article is in the form of a suture element.
4. The method according to claim 3 in which the surgical article is in the form of a filament, bristle, single filament, twisted filament, stranded filament, gathered filament, texturized filament of lapped filament, tape, tent or spun fibre.
5. The method according to claim 1 in which the surgical article is in the form of a textile fabric.
6. The method according to claim 1 in which the polyester is combined with another material which is bioresorbable.
7. The method according to claim 6 in which the other material is selected from the group consisting of 11. The method according to claim 1 in which the surgical article is in the form of a tube.
12. The method according to claim 1 in which the surgical article is in the form of a bar.
13. The method according to claim 1 in which the surgical article is in the form of a plate.
14. The method according to claim 1 in which the surgical articleis in the form of a screw.
15. The method according to claim 1 in which the surgical article is in the form of a ring.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US2071250 *||3 Jul 1931||16 Feb 1937||Du Pont||Linear condensation polymers|
|US3463158 *||9 Jan 1967||26 Aug 1969||American Cyanamid Co||Polyglycolic acid prosthetic devices|
|US3620218 *||25 Aug 1969||16 Nov 1971||American Cyanamid Co||Cylindrical prosthetic devices of polyglycolic acid|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US3960152 *||14 Mar 1975||1 Jun 1976||American Cyanamid Company||Surgical sutures of unsymmetrically substituted 1,4-dioxane-2,5-diones|
|US4032993 *||25 Jun 1975||5 Jul 1977||Rhone-Poulenc Industries||Bioresorbable surgical articles|
|US4080969 *||29 May 1975||28 Mar 1978||American Cyanamid Company||Suture or ligature carrying on the exposed surface thereof a coating of a polyester resin|
|US4128612 *||3 Nov 1975||5 Dec 1978||American Cyanamid Company||Making absorbable surgical felt|
|US4141087 *||19 Jan 1977||27 Feb 1979||Ethicon, Inc.||Isomorphic copolyoxalates and sutures thereof|
|US4186189 *||28 Sep 1977||29 Jan 1980||Ethicon, Inc.||Absorbable pharmaceutical compositions based on poly(alkylene oxalates)|
|US4329743 *||27 Apr 1979||18 May 1982||College Of Medicine And Dentistry Of New Jersey||Bio-absorbable composite tissue scaffold|
|US4343931 *||17 Dec 1979||10 Aug 1982||Minnesota Mining And Manufacturing Company||Synthetic absorbable surgical devices of poly(esteramides)|
|US4388926 *||22 Dec 1980||21 Jun 1983||Ethicon, Inc.||High compliance monofilament surgical sutures comprising poly[alkylene terephthalate-co-(2-alkenyl or alkyl)succinate]|
|US4396746 *||6 Apr 1982||2 Aug 1983||Daicel Chemical Industries, Ltd.||Thermoplastic polyester copolymer|
|US4411027 *||23 Feb 1982||25 Oct 1983||University Of Medicine And Dentistry Of New Jersey||Bio-absorbable composite tissue scaffold|
|US4441496 *||8 Feb 1982||10 Apr 1984||Ethicon, Inc.||Copolymers of p-dioxanone and 2,5-morpholinediones and surgical devices formed therefrom having accelerated absorption characteristics|
|US4481353 *||7 Oct 1983||6 Nov 1984||The Children's Medical Center Corporation||Bioresorbable polyesters and polyester composites|
|US4529792 *||6 May 1982||16 Jul 1985||Minnesota Mining And Manufacturing Company||Process for preparing synthetic absorbable poly(esteramides)|
|US4594407 *||20 Sep 1983||10 Jun 1986||Allied Corporation||Prosthetic devices derived from krebs-cycle dicarboxylic acids and diols|
|US4603695 *||29 Jun 1984||5 Aug 1986||Japan Medical Supply Co., Ltd.||Use of molded polymeric material for preventing adhesion of vital tissues|
|US4652264 *||25 Apr 1985||24 Mar 1987||American Cyanamid Company||Prosthetic tubular article|
|US4662884 *||25 Apr 1984||5 May 1987||University Of Utah Research Foundation||Prostheses and methods for promoting nerve regeneration|
|US4670286 *||26 Dec 1985||2 Jun 1987||Allied Corporation||Method of forming prosthetic devices|
|US4738255 *||7 Apr 1986||19 Apr 1988||Biotron Labs, Inc.||Suture anchor system|
|US4773416 *||4 Feb 1987||27 Sep 1988||Hourahane Donald H||Surgery in horses|
|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|
|US4844067 *||9 Feb 1988||4 Jul 1989||Japan Medical Supply Co., Ltd.||Sucrose fatty acid ester coated suture|
|US4870966 *||1 Feb 1988||3 Oct 1989||American Cyanamid Company||Bioabsorbable surgical device for treating nerve defects|
|US4871365 *||24 Dec 1986||3 Oct 1989||American Cyanamid Company||Partially absorbable prosthetic tubular article having an external support|
|US4915893 *||15 Jul 1983||10 Apr 1990||Medtronic, Inc.||Method of preparing polyester filament material|
|US5061281 *||17 Dec 1986||29 Oct 1991||Allied-Signal Inc.||Bioresorbable polymers and implantation devices thereof|
|US5110852 *||27 Oct 1988||5 May 1992||Rijksuniversiteit Te Groningen||Filament material polylactide mixtures|
|US5180392 *||15 Nov 1990||19 Jan 1993||Einar Skeie||Anastomotic device|
|US5403346 *||31 Dec 1992||4 Apr 1995||Loeser; Edward A.||Self-affixing suture assembly|
|US5434238 *||23 Nov 1994||18 Jul 1995||Eastman Chemical Company||Copolyesters having repeat units derived from succinic acid|
|US5480962 *||7 Mar 1994||2 Jan 1996||Eastman Chemical Company||Copolyesters having repeat units derived from succinic acid|
|US5498453 *||2 Jun 1995||12 Mar 1996||Eastman Chemical Company||Copolyesters having repeat units derived from succinic acid|
|US5527342 *||14 Dec 1993||18 Jun 1996||Pietrzak; William S.||Method and apparatus for securing soft tissues, tendons and ligaments to bone|
|US5589566 *||1 Mar 1996||31 Dec 1996||Eastman Chemical Company||Copolyesters having repeat units derived from succinic acid|
|US5616681 *||31 Oct 1995||1 Apr 1997||Nippon Shokubai Co., Ltd.||Process for producing aliphatic polyester|
|US5632753 *||4 Apr 1995||27 May 1997||Loeser; Edward A.||Surgical procedures|
|US5843573 *||25 Oct 1995||1 Dec 1998||Nippon Shokubai Co., Ltd.||Polyester resin composition|
|DE3249111C2 *||9 Sep 1982||6 Feb 1986||United States Surgical Corp., Norwalk, Conn., Us||Title not available|
|DE19857067B4 *||10 Dec 1998||28 Jul 2005||Ykk Corp.||Verschlußelement aus biologisch abbaubarem Kunststoff|
|EP0144534A2 *||16 Aug 1984||19 Jun 1985||Allied Corporation||prosthetic devices|
|EP0144534A3 *||16 Aug 1984||17 Dec 1986||Allied Corporation||Prosthetic devices|
|EP1482000A3 *||13 Jul 1994||25 May 2005||Eastman Chemical Company||Copolyesters having repeat units derived from succinic acid|
|WO1995003347A1 *||13 Jul 1994||2 Feb 1995||Eastman Chemical Company||Copolyesters having repeat units derived from succinic acid|
|WO1996022055A1||29 Dec 1995||25 Jul 1996||Inbae Yoon||Surgical stapling system and method of applying staples from multiple staple cartridges|
|WO2004108792A2 *||7 Apr 2004||16 Dec 2004||Vinod Chintamani Malshe||Novel biodegradable aliphatic polyesters and pharmaceutical compositions and applications thereof|
|WO2004108792A3 *||7 Apr 2004||24 Mar 2005||Padma Venkitachalam Devarajan||Novel biodegradable aliphatic polyesters and pharmaceutical compositions and applications thereof|
|U.S. Classification||128/898, 57/243, 528/279, 623/1.38, 528/285, 528/272, 606/231|
|International Classification||A61L27/00, C08G63/16, A61L17/00, A61L17/14, C08G63/00, A61L17/10, A61L27/18|
|Cooperative Classification||C08G63/16, A61L17/105, A61L17/145, A61L27/18|
|European Classification||A61L27/18, C08G63/16, A61L17/10B, A61L17/14C|