Biodegradable moldable surgical material

Abstract: A moldable biodegradable surgical material is made of a bioabsorbable polymer derived from hydroxyacids, lactones, carbonates, etheresters, anhydrides, orthopsters and copolymers, terpolymers and/or blends thereof, the polymer blended with at least one surface active agent selected from the group consisting of fatty acid ester and poly(oxypropylene)/poly(oxyethylene) block copolymer. In one embodiment, a leaching agent is blended with the above-mentioned surgical material. Methods of making moldable biodegradable surgical material are provided. The surgical material may be used as a moldable bone wax in connection with repair of wounds and is an adaptable aid for any appropriate surgical use, e.g., hemostat, anchor, patch etc.

Description: BACKGROUND 1. Technical Field The present disclosure relates to implantable moldable biodegradable polymeric materials used in medicine for surgical repair. 2. Background of Related Art Biodegradable materials are used in medicine for a variety of purposes including drug delivery devices and as aids in tissue repair. Physical and chemical properties of such materials can vary as in the case of different polymeric materials, e.g., melting point, degradation rate, stiffness, etc. The variability in physical and chemical properties allows products made from such materials to be tailored to suit specific applications. Absorbable sutures can be made from biodegradable polymers such as glycolide and lactide. Biodegradable polymers can be used to coat sutures, e.g., U.S. Patent No. 4,624,256 is directed to caprolactone polymers for suture coating. As described therein, the coating contains high molecular weight polycaprolactone or a high molecular weight copolymer of at least 90% by weight of caprolactone and at most 10% by weight of another biodegradable monomer such as glycolide and lactide. The high molecular weight polycaprolactone may be mixed with up to 50% by weight of lubricating agents which include poly(ethylene oxide). A resorbable bone wax is described in U.S. Patent No. 5,143,730. The bone wax is said to be suitable for mechanical staunching of blood on hard body tissue and is based on oligomers of glycolic acid and/or lactic acid with monofunctional and/or polyfunctional alcohols and/or corresponding carboxylic acids. A content of body-compatible salts of organic and/or inorganic acids is said to be formed by the reaction of any free carboxyl groups. Glycerol or glycerol partial esters are used to regulate the average molecular weight of the oligomer fraction. U.S. Patent No. 4,440,789 is directed to synthetic absorbable hemostatic composition. As described therein, a semisolid bone sealant contains between about 65% and 85% by weight of polydioxanone in a base which may contain ethylene/propylene oxide block copolymers, polyethylene glycols or methoxypolyethylene glycols. U.S. Patent No. 5,080,665 is directed to a deformable absorbable surgical device manufactured from a block or graft copolymer. The copolymer is described as having a plurality of first linkages selected from the group consisting of glycolic acid ester and lactic acid ester linkages and a plurality of second linkages selected from the group consisting of 1,3 dioxane-2-one; 1,4-dioxane-2-one and E-caprolactone linkages. A deformable surgical repair device is described as being manufactured from a blend of a first and second absorbable polymer, the first polymer corresponding to the first above linkages and the second polymer corresponding to the second above linkages. Medical putty for tissue augmentation is described in U.S. Patent No. 4,595,713 and is said to be useful in the regeneration of soft and hard connective tissue. As described therein, an implant material is composed of a copolymer of 60-95% epsilon caprolactone and 40-5% lactide. Catalysts used for the copolymer are metallic esters of carboxylic acids. The polymer is said to become moldable at hot water temperatures of about 46°-71°C (115°-160°F). SUMMARY A moldable biodegradable surgical material is made of a bioabsorbable polymer and a leaching material as defined in the claims. Methods of making moldable biodegradable surgical material are provided. The biodegradable surgical material may be used as a moldable bone wax in connection with repair of wounds. The moldable, biodegradable nature of the implantable surgical material allow it to be shaped to fit underlying or overlying interior terrain of the body. The biodegradable surgical material is thus an adaptable aid for any appropriate surgical use, e.g., hemostat, anchor, patch, etc. DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS A biodegradable moldable polymeric surgical material (hereinafter "surgical material") as described herein is adaptable for many uses in vivo. The surgical material is implanted and allowed to resorb in place while acting as a hemostat, anchor and/or patch. The surgical material provides excellent moldability and workability at both room and body temperatures and good stability in vivo during the applicable healing period. As a bone wax, after being molded to a desired shape, the surgical material maintains that shape for a prolonged period and is resilient to deformation under normal interior body conditions to provide durable coverage of the intended locus. In one embodiment the biodegradable star polymer is made of a major amount of E-caprolactone and a minor amount of a monomer which may be one or more hydroxyacids, lactones, carbonates and/or mixtures thereof. The polymer is obtained by polymerizing a major amount of E-caprolactone and a minor amount of at least one of the above copolymerizable monomers or mixture of such monomers in the presence of a polyfunctional initiator such as a polyhydric alcohol initiator. The polymerization of these monomers contemplates all of the various types of monomer addition, i.e., simultaneous, sequential, simultaneous followed by sequential, sequential followed by simultaneous, etc. Suitable monomers which can be copolymerized with E-caprolactone include all the known hydroxyacids, lactones and carbonates that, when polymerized, are capable of biodegradation, e.g., glycolide, lactide, p-dioxanone, trimethylene carbonate and the like. Suitable polyhydric alcohol initiators include glycerol, trimethylolpropane, 1,2,4-butanetriol, 1,2,6-hexanetriol, triethanolamine, triisopropanolamine, erythritol, threitol, pentaerythritol, ribitol, arabinitol, xylitol, N,N,N',N'-tetrakis (2-hydroxyethyl)ethylenediamine, N,N,N',N'-tetrakis(2-hydroxypropyl)ethylenediamine, dipentaerythritol, allitol, dulcitol, glycitol, altritol, iditol, sorbitol, mannitol, inositol, and the like. In another embodiment, the biodegradable polymer is made of a major amount of ε-caprolactone and a minor amount of glycolide. The biodegradable polymer herein can contain from about 85 to about 100, and preferably greater than about 90, weight percent E-caprolactone-derived units, the balance of the copolymer being derived from the other copolymerizable monomer(s). The molecular weight of the biodegradable polymer ranges from about 2,000 to about 30,000 and the inherent viscosity of the biodegradable polymer generally ranges from about 0.10 to about 0.60, and preferably from about 0.20 to about 0.50, dl/g when measured in chloroform at a concentration of 0.2500 g/dl at 30_C. The polyhydric alcohol initiator, e.g., mannitol is generally employed in small amounts, e.g., from about 0.5 to about 5, and preferably from about 0.1 to about 2, weight percent of the total monomer mixture. In one embodiment, E-caprolactone is present in an amount of about 90.2 weight percent and glycolide is present in an amount of about 9.8 weight percent of the biodegradable polymer. At least one leaching agent is blended with the above described materials to provide a porous microstructure which is formed as the leaching agent clears out of the surgical material. The resulting porous microstructure allows and encourages bone ingrowth through the interstices created where the leaching agent formerly occupied space. Additionally, incorporation of one or more leaching agents reduces tackiness and improves workability and moldability of the surgical material. Suitable leaching agents include calcium carbonate, calcium chloride, tricalcium phosphate and hydroxyapatite. The amount of leaching agent ranges from about 1 weight percent to about 70 weight percent of the surgical material. The biodegradable moldable surgical material is non-toxic and physiologically inert. Depending on its particular physical and bioabsorption properties, which are influenced to a large extent by the relative amounts of polymer and surface active agent, the surgical material can be applied as a bone wax to prevent or stop osseous hemorrhage or as a patch to fill voids or as an anchor for loose tissue and/or other surgical aids such as sutures, fasteners and the like. Increasing the percentage of the surface active agent in the surgical material increases softness and allows the material to be molded more easily. The surgeon may optionally heat the material to slightly above ambient temperature to a temperature of about 40°C to facilitate moldability. The material may be heated, kneaded and/or shaped by the surgeon to fit a target terrain and applied to the appropriate locus for the desired affect. The material may be loaded into a syringe and extruded into a desired locus. Such use is suitable for hard to reach areas such as those that are attendant to dental or maxillofacial surgery. The following examples are included for purposes of illustration and are not intended to limit the disclosure herein. Some of the examples have been included for reference purposes only and do not fall under the scope of the claims. EXAMPLE 1 Dry glycolide (300.0 gm), E-caprolactone (2760 gm), stannous octoate as catalyst (0.3 gm) and dry mannitol as initiator (39.0 gm) were mixed under N 2 for one hour. The mixture was heated in a reactor at a temperature of 160°C for 24 hours. Greater than 95 percent conversion of monomers to copolymer was obtained. The polymer has a molecular weight of about 14,000. EXAMPLE 2 In a dry room, distilled glycolide (30 gm), E-caprolactone (270 gm), stannous octoate as catalyst (0.06 gm) and dry mannitol as initiator (1.95 gm) were added to a 500 m1 round bottom flask that has been dried with nitrogen gas. The flask, containing a mechanical stirrer, was placed in an oil bath and heated to 160°C ±3 in approximately 3 hours, and kept at 160°C for 24 hours while mixing under a static nitrogen gas flow. The contents of the flask were placed in a vacuum oven, post-treated at 120°C for 24 hours and then moved to a dry room. The polymer was designated Polymer A and had a molecular weight of about 28,000. EXAMPLE 3 25.0 gm of Polymer A from Example 2 and 20.45 gm of Tween® 40 along with a stir bar were added to a heat dried 250 ml flask. The flask was placed in an oil bath at 160°C for 4 hours under static nitrogen gas. The polymer melted into a liquid which was stirred and then allowed to cool and solidify in a dry room. The resulting product was a hand moldable material having 55/45 Polymer A/Tween® 40 by weight. EXAMPLE 4 15.0 gm of Polymer A from Example 2 and 12.2 gm of Tween® 40 along with a stir bar were added to a clean 100ml round bottom flask. A static nitrogen gas line was added and the flask was placed in an oil bath at 160°C for 3 hours. The polymer melted into a liquid which was stirred and then allowed to cool in a dry room overnight. The resulting product was a hand moldable material having 55/45 Polymer A/Tween® 40 by weight EXAMPLE 5 15.0 gm of Polymer A from Example 1 and 10gm of Tween® 40 along with a stir bar were added to a clean 100 ml round bottom flask. A static nitrogen gas line was added and the flask was placed in an oil bath at 160_C for 3 hours. The contents of the flask were not stirred for the first three hours. The contents were then stirred overnight at 150°C. The resulting product was a hand moldable material having 60/40 Polymer A/Tween® 40 by weight. EXAMPLE 6 Approximately 1 gm of the product of Example 4 was mixed in a 1:1 ratio by weight with fine grain tricalcium phosphate (TCP) commercially available from Hitempco Medical Applications, Inc. The product and TCP were mixed by triturating with a spatula. The resulting product was placed in a dry room for 24 hours. The resulting product exhibited good moldability by hand. EXAMPLE 7 Approximately 1 gm of the product of Example 4 was mixed in a 2:1 ratio by weight with fine grain tricalcium phosphate (TCP) commercially available from Hitempco Medical Applications, Inc. The product and TCP were mixed by triturating with a spatula. The resulting product was placed in a dry room for 24 hours. The resulting product exhibited good moldability by hand. EXAMPLE 8 Approximately 1 gm of product of Example 5 that had not yet completely solidified was mixed in a 3:2 ratio by weight with fine grain tricalcium phosphate commercially available from Hitempco Medical Applications, Inc. The product and TCP were mixed by triturating with a spatula. The resulting product was placed in a dry room for 24 hours. The resulting product was harder and less moldable than the products of Examples 6 and 7 above. EXAMPLE 9 Approximately 1 gm of product of Example 5 that had not yet completely solidified was mixed in a 1:1 ratio by weight with fine grain tricalcium phosphate commercially available from Hitempco Medical Applications, Inc. The product and TCP were mixed by triturating with a spatula. The resulting product was placed in a dry room for 24 hours. The resulting product was harder and less moldable than the products of Examples 6 and 7 above. EXAMPLE 10 Approximately 1 gm of product of Example 5 was mixed in a 2:1 ratio by weight with fine grain tricalcium phosphate commercially available from Hitempco Medical Applications, Inc. The product and TCP were mixed by triturating with a spatula. The resulting product was placed in a dry room for 24 hours. The resulting product was moldable by hand and slightly stickier than the product of Example 7 above. EXAMPLE 11 In a dry room glycolide (30 gm), E-caprolactone (270 gm), stannous octoate as catalyst (0.06 gm) and dry mannitol as initiator (3.9 gm) were added to a 500 ml round bottom flask dried with nitrogen gas. The flash, containing a mechanical stirrer, was placed in an oil bath at 160°C ± 3 for approximately 24 hours and mixed under a static nitrogen gas flow. The contents of the flask were placed into a dry room. The polymer was designated Polymer B and had a molecular weight of about 14,000. EXAMPLE 12 10 gm of Polymer B from Example 11 and 7.39 gm of Tween® 40 along with a stir bar were added to a clean 100 ml round bottom flask. A static nitrogen gas line was added to the flask and the flask was placed in an oil bath at 160°C for 4 hours. The polymer melted into a liquid which was stirred and then allowed to cool in a dry room overnight. The resulting product was a hand moldable surgical material having 57.5/42.5 Polymer B/Tween® 40 by weight. The product was slightly softer and stickier than products incorporating Polymer A. EXAMPLE 13 11.25 gm of Polymer B from Example 11 and 13.75 gm of Tween® 40 along with a stir bar were added to a clean 100 ml round bottom flask. A static nitrogen gas line was added to the flask and the flask was placed in an oil bath at 160°C for 5 hours. The polymer melted into a liquid that was stirred and then allowed to cool in a dry room. The resulting material had 45/55 Polymer B /Tween® 40 by weight and was soft. 12.5 gm fine grain tricalcium phosphate was added to the product by triturating with a spatula. The resulting product was moldable by hand and was slightly sticky. EXAMPLE 14 13.75 of Polymer B from Example 11 and 11.25 gm Tween® 40 along with a stir bar were added to a clean 100 ml round bottom flask. A static nitrogen gas line was added to the flask and the flask was placed in an oil bath at between 160°C to 170°C for 5 hours. The polymer melted into a liquid that was stirred and allowed to cool in a dry room. The resulting material had 55/45 Polymer B/Tween® 40 by weight but was too hard to be moldable by hand. 12.5 gm fine grain tricalcium phosphate (Hitempco Medical Applications, Inc.) was mixed into the material by triturating with a spatula. The resulting product was moldable by hand. EXAMPLE 15 5 gm of Polymer B from Example 11 was placed in a flask and heated in a vacuum oven at 107°C under static nitrogen gas until it melted. The contents of the flask were transferred to a scintillation vial along with 7.5 gm of liquid Tween® 40. The contents were mixed by hand. The resulting product was very thin and difficult to work with. EXAMPLE 16 5 gm of Polymer B from Example 11 was placed in a flask and heated in a vacuum oven at 107°C under static nitrogen gas until it melted. The contents of the flask were transferred to a scintillation vial along with 11.67 gm of liquid Tween® 40. The contents were mixed by hand. The resulting product was difficult to mix due to the high concentration of Tween® 40 and did not form a homogenous mixture. EXAMPLE 17 5 gm of Polymer B from Example 11 was placed in a flask and heated in a vacuum oven at 107°C under static nitrogen gas until it melted. The contents of the flask were transferred to a scintillation vial along with 5 gm of liquid Tween® 40. The contents were mixed by hand. The resulting product hardened into a hand moldable material that became thin and sticky after continued kneeding. EXAMPLE 18 10 gm of Polymer B from Example 11 and 10 gm of Tween® 40 along with a stir bar were added to a clean 100 ml round bottom flask. A static nitrogen gas line was added to the flask and the flask was placed in an oil bath at 160°C for 4 hours. The polymer melted into a liquid that was stirred and then allowed to cool overnight in a dry room. The resulting product hardened into a hand moldable material that became thin and sticky after continued kneading. EXAMPLE 19 5 gm of the product of Example 18 was mixed with 0.25 gm fine grain tricalcium phosphate (TCP) (Hitempco Medical Applications, Inc.) by triturating with a spatula, resulting in 5% TCP by weight product. The resulting product was thin and sticky. EXAMPLE 20 5 gm of the product of Example 18 was mixed with 0.75 gm fine grain tricalcium phosphate (TCP) (Hitempco Medical Applications, Inc.) by triturating with a spatula, resulting in a 15% TCP by weight product. The resulting product was thin and sticky after continued kneading. EXAMPLE 21 5 gm of the product of Example 18 was mixed with 1.25 gm fine grain tricalcium phosphate (TCP) (Hitempco Medical Applications, Inc.) by triturating with a spatula, resulting in a 25% TCP by weight product. The resulting product was thin and sticky after continued kneading. EXAMPLE 22 10 gm of Polymer A from Example 2 and 10 gm of Tween® 40 along with a stir bar were added to a clean 100 ml round bottom flask. A static nitrogen gas line was added and the flask was placed in an oil bath at 160°C for 4 hours. The polymer melted into a liquid which was stirred and then allowed to cool in a dry room overnight. The resulting product exhibited good moldability by hand. EXAMPLE 23 In a dry room, dried glycolide (7.8 gm), dried E-caprolactone (69.5 gm), stannous octoate (0.016 gm) as catalyst and dry mannitol (9.1 gm) as initiator were added to a 250 ml round bottom flask that had been dried with nitrogen gas for 24 hours. The flask, containing a mechanical stirrer, was placed in an oil bath at 160°C and stirred for 24 hours. The contents of the flask were post-treated under vacuum at 73°C for 20 hours and placed into a dry room. The polymer was designated Polymer C and had a molecular weight of about 4000. EXAMPLE 24 In a dry room distilled glycolide (9.08 gm), distilled E-caprolactone, (81.24 gm) stannous octoate, (0.018 gm) as catalyst and mannitol (8.1 gm) as initiator were added to a 250 ml round bottom flask that had been dried with nitrogen gas for 1 hour. The flask, containing a mechanical stirrer, was placed in an oil bath at 160°C and stirred for 24 hours. The contents of the flask were placed in a vacuum for 16 hours at 65°C. The polymer was designated Polymer D and had a molecular weight of 4000. EXAMPLE 25 6.5 gm of Polymer D from Example 24 and 3.5 gm of Pluronic® F68 LF pastille and a stir bar were added to a clean 100 ml round bottom flask. A static nitrogen gas line was added and the contents were dried for 1 hour The flask was placed in a sand bath at 160°C for 4 hours. The polymers melted into a liquid which was stirred and then placed into a dry room for 48 hours. The resulting product was a hand moldable hard material having 65/35 Polymer D/Pluronic® F68 LF by weight. EXAMPLE 26 Approximately 1 gm of the product of Example 25 was mixed in a 1:1 ratio by weight with fine grain tricalcium phosphate (TCP) (Hitempco Medical Applications, Inc.). The product and TCP were mixed by triturating with a spatula. The resulting product was a hand moldable hard material after being allowed to stand in a dry room. EXAMPLE 27 7.5 gm of Polymer D from Example 24 and 2.5 gm of Pluronic® F68 LF pastille and a stir bar were added to a clean 100 ml round bottom flask. A static nitrogen gas line was added and the contents were dried for 30 minutes. The flask was placed in a sand bath at 160°C for 4 hours. The polymers melted into a liquid which was stirred and then placed into a dry room overnight. The resulting product was a hand moldable hard material having 75/25 Polymer D/Pluronic® F68 LF by weight. EXAMPLE 28 Approximately 1 gm of the product of Example 27 was mixed in a 1:1 ratio with fine grain tricalcium phosphate (TCP) (Hitempco Medical Applications, Inc.). The product and TCP were mixed by triturating with a spatula. The resulting product was a hand moldable hard material after being allowed to stand in a dry room. EXAMPLE 29 8.5 gm of Polymer D from Example 24 and 1.5 gm of Pluronic ® F68 LF pastille and a stir bar were added to a clean 100 ml round bottom flask. A static nitrogen gas line was added and the contents were dried for 30 minutes. The flask was placed in a sand bath at 160°C for 4 hours. The polymers melted into a liquid which was stirred and then placed into a dry room overnight. The resulting product was a hand moldable hard material having 85/15 Polymer D/Pluronic® F68 LF by weight. The product was softer than the product of Example 25 above. EXAMPLE 30 Approximately 1 gm of the product of Example 29 was mixed in a 1:1 ratio with fine grain tricalcium phosphate (TCP) (Hitempco Medical Applications, Inc.). The product and TCP were mixed by triturating by hand. The resulting product was a hand moldable hard material after being allowed to stand in a dry room. EXAMPLE 31 7.0 gm Polymer C from Example 23 and 3.0 gm of Pluronic ® F68 LF pastille and a stir bar were added to a clean 100 ml round bottom flask. A static nitrogen gas line was added and the contents dried for 1 hour. The flask was placed in an oil bath at 160°C for 4 hours. The polymers melted into a liquid which was stirred and then placed into a dry room overnight. The resulting product was a hand moldable hard material having 70/30 Polymer C/Pluronic® F68 LF by weight. EXAMPLE 32 Approximately 1 gm of the product of Example 31 was mixed in a 1:1 ratio by weight with fine grain tricalcium phosphate (TCP) (Hitempco Medical Applications, Inc.). The product and TCP were mixed by triturating with a spatula. The resulting product exhibited good moldability by hand. EXAMPLE 33 6.0 gm of Polymer C from Example 23 and 4.0 gm of Pluronic® F68 LF pastille and a stir bar were added to a clean 100 ml round bottom flask. A static nitrogen gas line was added and the contents dried for 2 hours. The flask was placed in a sand bath at 160°C for 4 hours. The polymers melted into a liquid which was stirred and then placed into a dry room for 48 hours. The resulting product was a hand moldable hard material having 60/40 Polymer C/Pluronic® F68 LF by weight. EXAMPLE 34 Approximately 1 gm of the product of Example 33 was mixed in a 1:1 ratio by weight with fine grain tricalcium phosphate (TCP) (Hitempco Medical Applications, Inc.). The product and TCP were mixed by triturating with a spatula. The resulting product exhibited good moldability by hand. EXAMPLE 35 Approximately 1 gm of the product of Example 33 was mixed in a 1:2 ratio by weight with fine grain tricalcium phosphate (TCP) (Hitempco Medical Applications, Inc.). The product and TCP were mixed by triturating with a spatula. The resulting product exhibited good moldability by hand. When compared to the product of Example 34 above, it was slightly harder and less sticky. EXAMPLE 36 Approximately 1 gm of the product of Example 33 was mixed in a 1:3 ratio by weight with fine grain tricalcium phosphate (TCP) (Hitempco Medical Applications, Inc.). The product and TCP were mixed by triturating with a spatula. The resulting product exhibited good moldability by hand. When compared to the product of Example 34 above, it was slightly harder and less sticky. EXAMPLE 37 Approximately 2 gm of Polymer C from Example 23 was mixed in a 1:1 ratio by weight with fine grain tricalcium phosphate (TCP) (Hitempco Medical Applications, Inc.). The polymers and TCP were mixed by triturating with a spatula. The resulting product was moldable by hand and sticky. EXAMPLE 38 Approximately 2 gm of Polymer C from Example 23 was mixed in a 1:2 ratio by weight with fine grain tricalcium phosphate (TCP) (Hitempco Medical Applications, Inc.). The polymer and TCP were mixed by triturating with a spatula. The resulting product was moldable by hand and slightly sticky. EXAMPLE 39 Approximately 2 gm of Polymer D from Example 24 was mixed in a 1:1 ratio by weight with tricalcium phosphate (TCP) (Hitempco Medical Applications, Inc.). The polymer and TCP were mixed by triturating with a spatula. The resulting product was initially hard but moldable by hand and became softer after continued kneading. EXAMPLE 40 Approximately 2 gm of Polymer D from Example 24 was mixed in a 1:2 ratio by weight with tricalcium phosphate (TCP) (Hitempco Medical Applications, Inc.). The polymer and TCP were mixed by triturating with a spatula. The resulting product was moldable by hand and was slightly harder and less sticky than the product of Example 39 above. EXAMPLE 41 10 gm of Polymer A from Example 2 and 6.67 gm of Pluronic® L 122 and a mechanical stirrer were added to a dry 100 ml round bottom flask. The flask and contents were dried overnight under static nitrogen gas. The flask was placed in a sand bath at 160°C and stirred for 8 hours. The resulting product was non-homogeneous and was placed in a dry room for 24 hours. The product did not harden. EXAMPLE 42 10 gm of Polymer A from Example 2 and 6.67 gm of Pluronic® L64 and a mechanical stirrer were added to a dry 100 ml round bottom flask. The flask and contents were dried overnight under static nitrogen gas. The flask was placed in a sand bath at 160°C and stirred for 4 hours. The resulting product was 60/40 Polymer A/Pluronic® L64 by weight and was homogeneous and a hand moldable hard material. EXAMPLE 43 2 gm of product from Example 42 was mixed in a 1:1 ratio with tricalcium phosphate (TCP) (Hitempco Medical Applications, Inc.). The product and TCP were mixed by triturating with a spatula. The resulting product was moldable by hand. EXAMPLE 44 10.5 gm of Polymer A from Example 2 and 4.5 gm of Pluronic® L64 and a mechanical stirrer were added to a dry 100 ml round bottom flask. A static nitrogen gas line was added and the contents were dried for 1 hour. The flask was placed in a sand bath at 160°C for 4 hours. The polymer melted into a liquid which was stirred and then placed in a dry room for 24 hours. The resulting product was a hand moldable hard material having 70/30 Polymer A/Pluronic® L64 by weight. EXAMPLE 45 2 gm of product from Example 44 was mixed in a 1:1 ratio with tricalcium phosphate (TCP) (Hitempco Medical Applications, Inc.). The product and TCP were mixed by triturating with a spatula. The resulting product was superiorly moldable and workable by hand. EXAMPLE 46 9.75 gm of Polymer A from Example 2 and 5.25 gm Pluronic® L64 and a mechanical stirrer were placed in a clean 100 ml round bottom flask. A static nitrogen gas line was added and the contents were dried for 1 hour. The flask was placed in a sand bath at 160°C for 5 hours. The polymer melted into a liquid which was stirred and then placed in a dry room overnight. The resulting product was a hand moldable hard material having 65/35 Polymer A/Pluronic® L64 by weight. EXAMPLE 47 2 gm of product from Example 46 was mixed in a 1:1 ratio with tricalcium phosphate (TCP) (Hitempco Medical Applications, Inc.). The product and TCP were mixed by triturating with a spatula. The resulting product was superiorly moldable and workable by hand. EXAMPLE 48 3.5 of Polymer A from Example 2 and 6.5 gm Pluronic® L64 and a mechanical stirrer were placed in a clean 100 m1 round bottom flask. A static nitrogen gas line was added and the contents were dried for 1 hour. The flask was placed in a sand bath at 160°C for 4 hours. The polymer melted into a liquid which was stirred and then placed in a dry room overnight. The resulting product did not mix well and was non-homogeneous. EXAMPLE 49 7.0 gm of Polymer B from Example 11 and 7.0 gm of Pluronic® F77 and a stir bar were added to a clean 100 ml round bottom flask. A static nitrogen gas line was added and the contents were dried for 1 hour. The flask was placed in a sand-bath at 160°C for 4 hours. The polymers melted into a liquid which was stirred and then placed into a dry room for 24 hours. The resulting product was a hand moldable hard material. EXAMPLE 50 7.0 gm of Polymer C from Example 23 and 7.0 gm of Pluronic® F77 and a stir bar are added to a clean 100 ml round bottom flask. A static nitrogen gas line is added and the contents are dried for 24 hours. The flask is placed in an oil bath at 160°C for 4 hours. The polymers melt into a liquid which is stirred and then placed into a dry room for 24 hours. The resulting material is moldable and workable by hand. EXAMPLE 51 8.0 gm of Polymer C from Example 23 and 2.0 gm of Pluronic® F68 LF pastille and a stir bar were added to a clean 100 ml round bottom flask. The flask was placed in an oil bath at 160°C for 4 hours under static nitrogen gas. The polymers melted into a liquid which was stirred and then placed in a dry room overnight. The resulting product was a hand moldable hard material having 80/20 Polymer C/Pluronic® F68 by weight. EXAMPLE 52 2 gm of the product of Example 51 was mixed in a 1:1 ratio with fine grain tricalcium phosphate (TCP) (Hitempco Medical Applications, Inc.). The product and TCP were mixed by triturating with a spatula. The resulting material was slightly thin and sticky. After standing in a dry room for 24 hours the material became harder and less sticky and exhibited good hand moldability. EXAMPLE 53 7 gm of Polymer C from Example 23 and 3 gm of Pluronic® F68 CS and a stir bar were added to a clean 100 ml round bottom flask. The flask was placed in an oil bath at 160°C for 4 hours under static nitrogen gas. The polymer melted into a liquid which was stirred and then placed in a dry room for 24 hours. The resulting material was hard and not moldable by hand, having 70/30 Polymer C/Pluronic F68 CS by weight. EXAMPLE 54 A portion of the product of Example 34 above (60/40 Polymer C/Pluronic® F68 LF mixed 1:1 with tricalcium phosphate) was used to stop bleeding of a tibial bone defect in a dog. The product was kneaded by hand and applied to the defect. Bleeding stopped, but the product disbanded and bleeding resumed. EXAMPLE 55 A portion of the product of Example 32 above, (70/30 Polymer C/Pluronic® F68 LF mixed 1:1 with tricalcium phosphate) was used to stop bleeding of the same tibial bone defect in the dog from Example 54 above. The product was kneaded by hand and applied over residual disbanded product left from Example 54 above. Bleeding stopped but some of the applied product disbanded. 100 minutes later the defect was reexamined and inconsistent topography was noted. EXAMPLE 56 A portion of the product of Example 52 above, (80/20 Polymer C/Pluronic® F68 mixed 1:1 with tricalcium phosphate) was used to stop bleeding of a tibial bone defect in a dog. The product was kneaded by hand and applied to the defect. Bleeding stopped. The product was easy to apply and did not disband. 100 minutes later the defect was reexamined and the product was coherent and there was no bleeding at the defect.

Claims: A moldable biodegradable surgical material including a bioabsorbable star polymer made of a major amount of ε-caprolactone and a minor amount of a monomer selected from hydroxyacids, lactones, carbonates and/or mixtures thereof, and a leaching agent selected from calcium carbonate, calcium chloride, tricalcium phosphate and hydroxyapatite wherein the leaching agent is present in an amount ranging from 1 % to 70 % by weight of the material. A moldable biodegradable surgical material including a bioabsorbable polymer made of a major amount of ε-caprolactone and a minor amount of glycolide and a leaching agent selected from calcium carbonate, calcium chloride, tricalcium phosphate and hydroxyapatite, wherein the leaching agent is present in an amount ranging from 1 % to 70 % by weight of the material. A moldable biodegradable surgical material according to claim 2 wherein the bioabsorbable polymer is a star polymer of glycolide and caprolactone. A moldable biodegradable surgical material according to claim 3 wherein glycolide is present in an amount of about 9.8 weight percent and caprolactone is present in an amount of about 90.2 weight percent. Use of the moldable biodegradable surgical material according to any of the preceding claims for the preparation of a material to be used as bone wax, hemostat, anchor, or patch.

Inventors: BENNETT STEVEN L, JIANG YING, SKALLA WALTER, BENNETT, STEVEN L., JIANG, YING, SKALLA, WALTER
Applicants: UNITED STATES SURGICAL CORP, UNITED STATES SURGICAL CORPORATION
Application year: 1996
Main classification: A61L27
IPC codes: A61L27, A61L24