HARD TISSUE PROSTHETICS AND PROCESS FOR THE PREPARATION THEREOF

Abstract: Composite materials useful as hard tissue prosthetics comprising synthetic biodegradable polymers and unsin­ tered calcium phosphate biomaterials optionally porositized by pore-forming agents are described. In addition, an in situ polymerization process is disclosed whereby an α-amino acid N-carboxyanhydride is blended intimately and efficient­ ly with one or more sintered or unsintered calcium phos­ phate biomaterials. The polymerization proceeds at ambient temperature and pressure without the need for initiators or surface modification of the calcium phosphate biomaterials. The composites may be used as hard tissue prosthetics either alone or in conjunction with conventional prostheses.

Description: HARD, TISSUE PROSTEETICS AND PROCESS FOR TRE PREPARATION THEREOF The present invention relates to composite materials comprising synthetic biodegradable polymers and unsintered calcium phosphate biomaterials and method for use thereof. Said composite materials are useful as hard tissue prosthetics such as bone prosthetics. The present ivention also relates to an in situ polymerization process for the preparation of composite materials comprising an a-amino acid polymer and a sintered or unsintered calcium phosphate biomaterial. Calcium phosphates are known in the art as physiologically acceptable biomaterials potentially useful as hard tissue prosthetics. The most widely studied of these are'hydroxyapatite and tricalcium phosphate. When these'materials are shaped and made porous they can be used alone or as a supplement or extender with bone for hard tissue prosthetics. Sunder appropriate conditions and with an appropriate form of calcium phosphate, the calcium phosphate is resorbed and new bone growth results. Calcium phosphate bio-' materials can be molded.by compaction under bigh pres- sure. Pore formation of molded calcium phosphate biomateriale is generally achieved by compaction of calcium phosphate powders containing naghthalene followed by removal of the naphthalene by leaching or sublimation. Hydrothermal exchange of marine coral structures (i.e., calcium carbonate for,calcius phog- phate), and decomposition of hydrogen peroxide have also been employed to generate pore filled $truçtureg. The dense or "green" forms of the calcium phosphate implant materials have esh-nical properties equal to or exceeding that of natural bone, but their respective, porous forms do not, thus s°veFely limiting their usefulness as hard tissue progthetic8. The art teaches that natural and synthetic polymers can be used in conjunction with various inor- ganic mineral fillers such as porous and powdered forms of calcium phosphate to enhance their mechanical pr4p- erties for use as hard tissue prosthetic8 or to enhance the bonding of metallic or plastic prosthetic8 to natural tissue. Natural polymers include collagen and gelatin. Synthetic polymers include polyacrylates, poly(methylmethacrylate), polyethylene, polysulfones, polyamides, polyesters, polytetrafluproethylene, and polycarbonates; polyacetates and polyglyçolates: epox- ides, polyacrylamide, polypropylene, polyurethanes, polyacetals, silicone resins, and furan resins; polyvinyl pyrrolidone, polyvinyl alcohol; and a çross-linked pentapeptide. The natural polymers and some of the synthetic polymers are resorbable, i.e., biodegradable. The art also teaches that nontoxic water soluble substances such as sodium chloride can be incorporated into a mixture of powdered acrylic polymer, liquid monomer, and other ingredients in a mold and the mixture polymerized to produce a shaped composite. The composite can then be made porous by leaching the sodium chloride with water. The various polymer-calciun phosphate com posies are prepared in a number of ways including blending calcium phosphates with polymeric binder and subsequent molding; impregnation of sintered, porous calcium phosphate with polymers under vacuum; impregnation of a porous calcium phosphate body with the melt or solution of prepolymers and solidifying the polymers by further polymerization or curing in the pores or by evaporation of the solvent; impregnation of a porous calcium phosphate body with a very reactive monomer like an a-cyanoacrylate or monomer and catalyst and polymerizing by heating, compression molding of an intimately blended, finely powdered mixture of polymer and calcium phosphate; and embedding ceramic calcium phosphate particles into resins where the calcium phosphate particles have previously been coated with a resin-affinic material to ensure good bonding to the resin, or copolymerizing precoated particles with the resin monomers. Calcium phosphate-polymer composite materials can also be used in conjunction with metallic or plastic prosthetics to facilitate adhesion and bone growth around the prosthetic. The composite can also be applied as a coating, for example, to an anodized titanium/aluminum/vanadium alloy hip prosthetic. The essential element in anchoring prosthetic devices appears to be the induction of new bone growth around the device by assuring that contact with the surrounding tissue is through a sheath of, or a surface laden with, bioactive calcium phosphate. It is desired to have a composite material which is gradually absorbed by the host and is simultaneously replaced with bone tissue without any undsirable side effects such as extensive inflammation or extensive formation of connective tissue. It is also desirable to have a composite material based on calcium phosphates which has.improved mechanical properties for use as hard tissue prosthetics over calcium phosphates alone. The prior art teaches composites which are comprised of certain polymers and ceratin calcium. phosphates; however, the calcium phosphates in composites of this type are taught as requiring a sintering step. We have suprisingly found that the calcium phosphates in composites of synthetic biodegradable polymers and calcium phosphates do not require a sintering step in order for the composites to have the desirable properties described herein. The elimination of the need for sintering the calcium phosphates in the composites of the present invention is a significant improvement over the teachings in the prior art. Sintering involves heating at high temperatures, such as 1000C to 13000C, which requires substantial levels of energy. Obviating the need for sintering therefore results in reduced energy consumption. In addition, elimination of a sintering step results in a savings of time. Therefore, the composites of the present invention can be prepared at reduced cost. The present invention is directed to a composite material of a calcium phosphate biomaterial and an organic material useful as a hard tissue prosthetic characterized in that said composite material is comprised of from 25 percent to 75 percent by weight of unsintered hydroxyapatite, unsintered tricalcium phosphate, an unsintered calcium pyrophosphate or mixtures thereof, and from 25 percent to 75 percent by weight of a synthetic biodegradable polymer, said percentages by weight being based on the total weight of the calcium phosphate biomaterial plus the organic material, said composite-material also optionally containing up to 30 percent by weight of a water-soluble pore-forming agent, said percent being based on the total weight of the calcium phosphate biomaterial plus organic material plus pore-forming agent. The composites of this invention have desirable mechanical and bioabsorption properties. If a pore-forming agent is present, the composite material can be made porous by leaching the pore-forming agent with water. The composite materials of the present invention preferably contain from 40 to 60 percent by weight of the calcium phosphate biomaterial and from 40 to 60 percent by weight of the organic material, said percentages being based on the total weight of the calcium phosphate biomaterial plus the organic material. It is also preferred that said composite materials contain from 10 to 20 percent by weight of the pore-forming agent, said percent being based on the total weight of the calcium phosphate biomaterial plus organic material plus pore-forming agent. The present invention is also directed to a process for preparing composite materials of an a-aMino acid polymer and sintered or unsintered calcium phosphate biomaterials by the in situ polymerizatinn of the corresponding reactive monomer of the a-amino acid '(i.e., the a-amino acid N-carboxyanhydride) and the sintered or unsintered calcium phosphate biomaterial when the two components are admixed in a suitable solvent vehicle. The composite materials prepared by the in situ process of the present invention can subsequently be blended with a compatible, pore-forming agent and then molded to form dense, shaped objects which can be made porous by leaching out said pore-forming agent as described hereinabove. Suitable synthetic biodegradable polymers for use in the composites of this invention can be made by the polymerization of monomers such as lactic acid, glycolic acid, hydroxybutyrate, amino acids, and the like. Examples of preferred polymers are polyesters of lactic acid, polyesters of glycolic acid, and polyhydroxybutyrate. Most preferred are polymers of a-amino acids. For the purpose of this invention, the term "synthetic biodegradable polymer" includes copolymers which are the polymerization product of at least two of the hereinabove described monomers and further includes mixtures of the hereinabove described polymers. The calcium phosphates of the composites of this invention may be one or more unsintered calcium phosphates such as, for example, calcium phosphate tribasic (CalO(oH)2(Po4)6) also known as hydroxyapatite or simply apatite; unsintered tricalcium phosphate (Ca3(P04)2); various unsintered calcium pyrophosphates or mixtures thereof. Preferable calcium phosphate biomaterials are unsintered hydroxyapatite, unsintered tricalcium phosphate or mixtures thereof. In preparing the composites of this invention, the synthetic biodegradable polymer can be prepolymerized and mixed with powdered unsintered calcium phosphate or the composite can be prepared by imprenating pre-formed unsintered calcium phosphate with monomer, prepolymer or polymer followed by polymer ization if necessary. The most preferred method of preparing the composites of this invention is in situ polymerization of monomer in the presence of the powdered unsintered calcium phosphate. The in situ polymerization is another aspect of the present invention which will be described in detail hereinafter. The in situ process is not limited to unsintered calcium phosphate, that is, said process is also applicable to sintered calcium phosphates as well. The composite prepared by the in situ polymerization process as described hereinafter that do not contain sintered calcium phosphate are within the scope of the composite materials of the present invention. The composite materials of the present invention may be ground to fine, free-flowing powders making them convenient to use. The free-flowing powders can be readily molded to virtually any shape, preferably a shape capable of anatomical use as a prosthetic device. Such anatomically-shaped forms may then be surgically implanted into animals in need of such prostheses thereby providing supplementation or replacement of hard tissue. It is further contemplated that the composite materials described herein may be used in conjunction with conventional prosthetic devices known to the art. For instance, in total hip joint replacements, it would be possible to mold one or more of the composite materials described herein about the metal stem of the prosthetic which, when implanted into the femur, would present a compatible surface for new-bone growth while being sufficiently strong to support the metal prosthesis. This and other applications of the technology disclosed herein will be readily appreciated by one skilled in the art. Porositization of the composite materials described herein may be attained by intimately blending the powdered composite with a compatible, pore-forming agent. Such pore-forming agents include water-soluble polymers (such as poly(2-ethyl-2-oxazoline), hereinafter referred to as PEOX; polyvinyl pyrrolidone; polyvinyl alcohol; or methylcellulose) and/or water -soluble inert materials (such as sodium chloride or potassium chloride). The mixture obtained may then be molded to the desired configuration, followed by a leaching of the compatible, pore-forming agent with water. Said leaching typically occurs satisfactorily in a time from 2 to 21 days. Preferably, for the porositization process, PEOX or sodium chloride is utilized as the pore-forming agent. Sodium chloride is particularly preferred as a pore-forming agent. The composite materials disclosed herein may be used in a variety of applications such as, for example, hard tssue prosthetics for dental or orthopedic appliances or other applications where one skilled in the art would envision the use of physiologically acceptable and/or resorable materials such as those described herein. Optionally, and preferably, the composite material described herein may subsequently be made porous in order to facilitate tissue ingrowth, a phenomenon where tissue such as bone and tendon continue to grow after the prosthetic device is in place and occupy apertures adjacent to the tissue. The tissue ingrowth provides a means by which a prosthetic device may be secured, thereby providing mechanical stabilization of the implant. The preferred composites containing a-amino acid polymers prepared as described herein are permeable to oxygen and water and are biodegradable, presumably due to the presence of peptide bonds in the a-amino acid polymer matrix making the substances protein-like. As resorption of the calcium phosphate biomaterial occurs followed by a slow degradation of the a-amino acid polymer matrix, further porositization results, thereby facilitating tissue ingrowth. For example, as the calcium phosphate biomaterial is resorbed and the a-amino acid polymer matrix slowly degrades, new, natural, self-supporting hard tissue develops. Further, various combinations of a-amino acids may be polymerized with one or more calcium phosphate biomaterials. By so doing, the characteristics of the resulting composite material may be acid may be polymerized by known techniques without the addition of the above-described protecting groups, or derivatives of glutamic acid may be used. Especially preferred for use herein are the y-ester derivatives of glutamic acid of the formula: EMI10.1 wherein R represents alkyl or aralkyl. As used herein, the term "alkyl" refers to aliphatic, straight or branched chain radicals of from 1 to 10 carbon atoms or cyclic aliphatic radicals of from 3 to 8 carbon atoms; "aralkyl" refers to radicals such as phenylethyl, benzyl, and ring-substituted benzyl. Most particularly preferred for use herein are those compounds of formula I wherein R is methyl or benzyl. The a-amino acid NCA referred to above is prepared by the reaction of the desired a-amino acid with phosgene via procedures known to the art. For purposes of illustration, the N-carboxyanhydride of a compound of formula I is prepared by the following reaction sequence (where R is as defined for formula I): EMI11.1 The a-amino acid NCA is then readily polymerized into the a-amino acid polymer as represented by the following: EMI11.2 wherein R is as defined for Formula I and n is a positive integer. The other a-amino acid polymers alluded to herein may be prepared in a manner analogous to the above-described reactions; the use of compounds of Formula I is merely illustrative. Further, one skilled in the art will appreciate that a-amino acid polymers may be prepared by techniques other than as described herein (i.e., by processes other than polymerization of an a-amino acid NCA monomer) such as by the use of active esters or triphenylphosphite with imidazole and the like. In the process of the present invention, the a-amino acid NCA is polymerized in the presence of one or more sintered or unsintered calcium phosphate biomaterials. The calcium phosphate biomaterial may be, for example, sintered or unsintered calcium phosphate tribasic (Ca1O(OH)2(Po4)6) also known as hydroxyapatite or simply apatite, tricalcium phosphate (Ca3(P04)2), various calcium pyrophosphates or mixtures thereof. The composite materials thus formed contain the same properties of calcium phosphate and a-amino acid polymer as described hereinabove. In preparing the reactive a-amino acid NCA monomer used in the in situ process of the present invention, the desired a-amino acid (having, if necessary, protected side chain, amino and/or carboxyl functionalities) is treated with phosgene. While various phosgenation processes are known to the art, it is preferable that a process substantially the same as that described in U.S. Patent No. 3,658,831 and illustrated in the present examples be utilized in order to prepare an a-amino acid NCA of the desired purity. It is important to obtain very highly pure a-amino acid NCA in order to prepare a-amino acid polymers having a high degree of polymerization and high quality. The a-amino acid NCA thus obtained is then admixed with one or more of the desired calcium phosphate biomaterials in a suitable inert organic solvent such as chloroform, dioxane, tetrahydrofuran (TRF), methylene chloride or mixtures thereof. Preferably, the inert organic solvent utilized is dioxane, TBF or mixtures thereof. The calcium phosphate biomaterial must be in a powdered or particulate form. Typically the calcium phosphate particles are between 0.05 micrometers (pm) and 10 pm in diameter and preferably about 1 pm in diameter. As noted earlier, the composite material may be composed of from 25 to 75 percent by weight, preferably from 40 to 60 percent by weight of one or more calcium phosphate biomaterials, preferably hydroxyapatite, tricalcium phosphate, or mixtures thereof, said percentages being based on total calcium phosphate plus a-amino acid polymer. Correspondingly, the a-amino acid polymer represen'ts from 75 to 25 percent by weight, preferably from 60 to 40 percent by weight of the composite formed, said percentages being based on the total calcium phosphate plus a-amino acid polymer. Typically, the a-amino acid NCA and calcium phosphate biomaterial mixture is stirred for a period of time sufficient to effect formation of the desired composite material (usually from 2 to 12 days) at a temperature of from.l80 to 300C. It is preferred that the mixture be stirred for 3 to 6 days at ambient temperature and pressure. The above-desribed in situ process of the present invention is a significant improvement over the processes taught in the prior art. The in situ process of the present invention does not require exogenous catalysts or initiators for polymerization of the a-amino acid NCA. The polymerization of the cr-amino acid NCA is catalyzed by the surfaces of the calcium phosphate particles. Further, the surfaces of the calcium phosphate particles do not require the presence of resins or other coupling agents. The calcium phosphate particles do not have to be surface modified prior to the in situ polymerization of the a-amino acid NCA. In addition, the in situ polymerization process of the present invention proceeds spontaneously at ambient temperature without the need for heating or cooling. Also, it is unnecessary to use a solvent system in which both the cr-amino acid NCA monomer and resultant a-amino acid polymer are soluble. For example, poly(y-methyl)-L-glutamate is insoluble in dioxane or THF, two solvents frequently used for the polymerization. The in situ process of the present invention is less complicated, is less costly, and requires fewer steps than the prior art processes. In addition to the hereinabove described advantages, the in situ process of the present invention results in an intimate bonding between the resulting a-amino acid polymer and calcium phosphate biomaterial, not merely a mixture of said components. This intimate bonding is not achieved in more complicated processes employing exogenous catalysts or processes which require surface modification of the calcium phosphate particles. The in situ polymerization process results in maximum contact between the polymer and calcium phosphate. The polymer is in a continuous phase which coats the calcium phosphate particles; this results in relatively constant and uniform dispersion of the calcium phosphate particles in the polymer matrix. Once the preferred composite material has been prepared it can be molded by techniques well-known in the art to virtually any desired shape while maintaining the complete integrity of the composite material. The preferred composites can optionally be porositized by using the pore-forming agents at the concentration described herein, 'using the techniques described herein. The following examples are provided as a means.of illustrating the present invention and are not to be construed as a limitation thereon. Example 1 y-Benzyl L-Glutamate 1416 grams (g) of L-glutamic acid, 1560 g of 60% sulfuric acid and 1152 g of benzyl alcohol were placed in a 12 liter round bottom flask equipped with a distillation head. - The mixture was heated to 700C and stirred for 45 minutes. Upon cooling, the resulting solution was stirred and was subjected to a reduced pressure. When the vacuum had stabilized at about 100 millimeters (mm) the reaction temperature was again raised to 700C and water was distilled off for about 4.5 hours. Upon standing overnight, the reaction mixture became viscous and was slowly added to a stirred mixture of 1613 g of sodium bicarbonate, 1.2 kilograms (kg) of ice and 12 liters of water. A precipitate formed which was collected by filtration and subsequently washed with about 8 liters of carbon dioxide-free water and 8 liters of acetone and subsequently air-dried. The precipitate was triturated with 2 liters of ether and dried, yielding 1044 g of the desired y-benzyl L-glutamate, melting point (m.p.) 156Q-1570C. Thin layer chromatography detected the presence of unreacted glutamic acid in the crude product. The crude product was recrystallized from 12.5 liters of hot water and filtered through a plug of glass wool suspended in the neck of a heated glass funnel. After cooling, and overnight refrigeration, the recrystallized product was collected, and washed with 2 liters of cold water, then 2 liters of TIFF. The product was air dried overnight and then dried in vacuo at room temperature for three hours. 693 g of y-benzyl L-glutamate was recovered as white, shiny plates, m.p. 156,50-1570C. Following a procedure substantially the same as that described in Example 1, the following two compounds were prepared using the requisite starting materials. Example 2 y-Benzyl D,L-Glutamate, m.p. 1450-1460C. Example 3 y-Eexyl L-Glutamate, m.p. 162.5"-163"C. Example 4 y-Methyl L-Glutamate A cold solution of 300 ml of acetyl chloride was slowly added to a flask containing 3 liters of methanol. To this mixture was added 442 g of L-glutamic acid. The flask was stoppered and shaken for several minutes to effect solution. The flask was then allowed to stand at room temperature with intermittent shaking for 24 hours. 300 ml of pyridine was added causing a precipitate to form. Upon standing for an additional 48 hours, the precipitate was collected on sintered glass and washed with two 600 ml portions of ethanol and a 250 ml portion of ether. The precipitate was dried in vacuo at room temperature for 3 hours and then in a vacuum desiccator over anhydrous calcium sulfate (Drierite) for 5 hours. Pyridine vapors were still perceptible from the precipitate which was further triturated with ether and dried again yielding 201.5 g of the desired y-methyl L-glutamate as white, shiny plates, m.p. 1680-1690C. Example S y-Methyl D,L-Glutamate y-Methyl D,L-glutamate was prepared by sub stantially the same method as described in Example 4, yielding white, powder-like crystals, m.p. 1660-166.30C. Example 6 y-Benzyl L-Glutamate'N-Carboxyanhydride 92.7 g of y-benzyl L-glutamate and 840 ml of TRF were mixed and heated in a 3 liter reaction flask. Nitrogen and phosgene were bubbled in and the reaction temperature was maintained between 450-500C until complete solution of the starting material had occurred (about 2 hours). Heating and phosgene flow were then stopped, but stirring and nitrogen flow were continued as the reaction mixture cooled slowly to 309C (approximately 45 minutes). The reaction flask was carefully removed from the phosgenation apparatus and stoppered. The reaction mixture was then concentrated in vacuo to about 250 ml with the aid of a rotary evaporator (maximum bath temperature about 350C). The residual concentrate was transferred to a dry flask and diluted carefully with an equal volume of hexane and seeded. After allowing crystallization to proceed at room temperature for about an hour, the reaction mixture was further diluted with about 500 ml of hexane and was maintained at -30 C for about 8-10 hours. After warming to room temperature the product was collected on a sintered glass funnel, care being taken to minimize contact with atmospheric moisture. The product was rinsed with a mixture of TEF-hexane (1:3) and then hexane, covered with a filter paper and dried in a vacuum desiccator over anhydrous calcium sulfate (Drierite). 92.6 g of the desired y-benzyl L-glutamate N-carboxyanhydride was recovered as white crystals, m.p. 950-960C. Example 7 y-Methyl L-Glutamate N-Carboxyanhydride 100 g of y-methyl L-glutamate and 600 ml of THF were placed in a 2 liter flask under nitrogen. The ensuing phosgenation reaction was carried out as described in Example 6, above. The reaction temperature was maintained between 440-490C for about 3 hours. Beating and phosgene addition were discontinued and stirring of the reaction mixture under nitrogen continued for about 1 hour before working up. 93.9 g of the desired y-methyl L-glutamate N-carboxyanhydride was recovered as dense, white crystals, m.p. 97.50-990C. Example 8 Tricalcium Phosphate Tricalcium phosphate (B-whitlockite crystalline form) was prepared by the following technique. A solution of 141.7 grams of calcium nitrate tetrahydrate in 400 ml of water was prepared and the pH adjusted to about pE 11 with concentrated ammonium hydroxide. This solution was then diluted to about 900 ml with water and placed in a three liter flask fitted with a dropping funnel and mechanical stirring apparatus. Separately, 66.1 grams of ammonium phosphate dibasic was added to 750 ml of water. The pH of the resulting solution was adjusted to about pB 11 with concentrated ammonium hydroxide resulting in the formation of a precipitate which was subsequently dissolved by the addition of water (about 2000 ml total volume of the solution). The ammonium phosphate dibasic solution was then slowly added to the reaction flask containing the calcium nitrate tetrahydrate solution and the resulting mixture was stirred overnight. A precipitate formed which was collected by centrifugation, washed with water and again collected by centrifugation. The precipitate was then suspended in a 2 percent agueous ammonium sulfate solution and filtered leaving a residue which was subsequently dried in vacuo at 900C leaving 63.7 g of tricalcium phosphate. The tricalcium phosphate was then sintered at 11500C for one hour, and then ground to a fine powder. Example 9 Hydroxya'patite-Poly(y-Methyl-L-Glutamate) Composite 5.0 g of y-methyl L-glutamate N-carboxyanhydride was added to 50 ml of a mixture of dioxane-THF (3:1). Upon solubilization, S.9 g of dry unsintered calcium phosphate tribasic (i.e., hydroxyapatite) was added and the mixture was stirred at room temperature for seven days. The mixture was then poured with stirring into 300 ml of methanol and the product composite was collected by filtration, washed with methanol and dried in vacuo at 800C for 6 hours. 9.58 g of a soft, white, homogeneous solid was obtained and subsequently identified as hydroxyapatite-poly(y-methyl L-glutamate) composite consisting of 61% (by weight) hydroxyapatite. This composite material was easily ground to a fine powder. Example 10 Hydroxyapatite-Poly(y-Methyl L-Glutamate) Composite Following a procedure substantially the same as that described in Example 9, 65.2 g of y-methyl L-glutamate N-carboxyanhydride, 50 g of unsintered hydroxyapatite and 675 ml of a mixture of dioxane-THF (3:1) were stirred continuously for 5 days. Two liters of methanol were then added to the mixture and the desired composite material was recovered as described in Example 9. 98 g of the desired hydroxyapatite-poly (y-methyl L-glutamate) composite material consisting of 50% (by weight) hydroxyapatite was subsequently recovered. Example 11 Hydroxyapatite-Poly(y-Benzyl L-Glutamate) Composite 72.6 g of y-benzyl L-glutamate N-carboxyanhydride, 40 g of unsintered hydroxyapatite, and 700 ml of a mixture of dioxane-THF (3:1) were continuously stirred for four days. The reaction mixture was then poured with stirring into 250Q ml of ethanol and collected. by filtration. The residue from the filtration was washed with ethanol, air dried and then dried in vacuo at 600-700C for six hours. 98 g of the desired hydroxyapatite-poly(y-benzyl L-glutamate) composite material (60 percent by weight hydroxyapatite) was obtained as a white, short fiber-like solid. Example 12 Tricalcium Phosphate-Poly(y-Benzyl L-Glutamate) Composite y-Benzyl L-glutamate N-carboxyanhydride (2.05 g) and sintered tricalcium phosphate (1.14 g) were combined in 40 ml of a mixture of dioxane-THF (3:1) and continuously stirred for 9 days. The resulting composite material was collected by pouring the reaction mixture into 200 ml of ethanol (with stirring) followed by filtration on a fritted glass filter leaving a solid residue. The residue was washed with ethanol and dried in vacuo to give 2.73 g of the desired tricalcium phosphate-poly(y-benzyl L-glutamate) composite material (60 percent by weight tricalcium phosphate). Example 13 Tricalcium Phosphate-Poly(y-Methyl L-Glutamate) Composite y-Methyl L-glutamate N-carboxyanhydride (129.3 g) was dissolved in 1600 ml of a mixture of dioxane-TSF (3:1). While maintaining a positive nitrogen flow through the system, 98.9 g of sintered tricalcium phosphate was added and the resulting mixture was continuously stirred for 12 days. The composite material thus formed was collected by pouring the reaction mixture into about 1500 ml of methanol followed by filtration on a fritted glass filter leaving a solid residue. The residue was washed with three 500 ml portions of methanol and then dried in vacuo at 700C for 20 hours to give 194.2 g of the desired tricalcium phosphate-poly(y-methyl L-glutamate) composite material (50 percent by weight tricalcium phosphate) as a soft, white, powdery material. Example 14 A hydroxyapatite-poly(y-benzyl L-glutamate) composite was ground and sieved through a 20-mesh screen. PEOX (molecular weight about 200,000) was ground and sieved through a 35-mesh screen. Enough PEOX was added to the ground composite to constitute 15 percent by weight of the total mixture (i.e., composite plus PEOX) and the mixture was blended by tumbling on a roller for 2 hours. This mixture was then compression molded in nickel plated stainless steel pressurized dies held in a ram press under a 2267.96 kilogram (2.5 ton) load at 1600C. One die was cylindrical in shape and produced a pressure of 175816.3 kilopascals (kPa) Similarly, tricalcium phosphate-poly(y-benzyl L-glutamate) composite material was admixed with a sufficient quantity of sodium chloride to constitute 15 percent sodium chloride by weight of the total mixture (i.e., composite plus sodium chloride). The mixture was blended and then molded as described in Example 14. Example 17 The same procedures utilized in Examples 14 and 15 were again repeated using sodium chloride in place of PEOX as the pore-forming agent. Again, the resulting molded products were white, smooth, homogeneous objects. Example 18 In order to illustrate the porositization technique, a 2.934 g molded disc containing 87 percent hydroxyapatite-poly ( -methyl L-glutamate) composite material (50 percent by weight of each constituent) and 13 percent PEOX blended therein was placed in 20 ml of water in a closed container for a total of six days (the water was changed after four days). The disc was removed and dried by blotting with absorbent paper and then further dried in an oven at 600C. 0.325 g of weight was lost representing 85.3 percent of the available PEOX in the molded disc. Microscopy of a section of the porositized product showed pore sizes of 10-25 microns. Utilizing the above procedure, a molded disc containing 85 percent hydroxyapatite-poly(y-methyl L-glutamate) composite (50 percent by weight of each component) and 15 percent by weight sodium chloride blended therein was placed in water in a closed container (48 percent of the available sodium chloride was removed). Microscopy of a section of the disc showed varied pore sizes, some in excess of 100 microns. Similarly, a molded bar weighing 9.92 g containing 85 percent by weight tricalcium phosphate-poly (y-methyl L-glutamate) composite (50 percent by weight of each constituent) blended with 15 percent by weight sodium chloride was placed in 250 ml of water in a closed container. After 10 days, the bar was removed, dried in vacuo for 7 hours at 900C and weighed. 77.3 percent (1.15 g) of the available sodium chloride had been removed. The process of the present invention can be uasd to prepare composites such as those described herein having desirable properties. Utilizing procedures described herein, additional composite mater tals set forth in Table 1 were prepared. Table 2 describes the mechanical properties of various molded composite materials. TABLE 1 Composition Material Porositization Mode Calcium Phosphate Ammount Example No. Polymera Biomaterialb (Weight %) Agent (Ammount)c Removedd 19 PGMLG HA (50) None 20 PGMLG HA (50) None 21 PGMLG HA (50) PEOX (15) 80 22 PGMLG HA (50) PEOX (15) 122e 23 PGMLG HA (50) NaCl (15) 48 24 PGBLG HA (40) None 25 PGBLG HA (40) None 26 PGBLG HA (40) PEOX (15) 29 27 PGBLG HA (40) PEOX (15) 59 28 PGMLG TCP (50) NaCl (15) 63 29 PGMLG TCP (50) None 30 PGMLG TCP (50) NaCl (15) 65 31 PGMLG TCP (50) None 32 PGMLG HA (50) NaCl (10) 55 33 PGMLG HA (50) NaCl (20) 40 34 PGMLG HA (75) NaCl (15) 78 aAbbrevations: PGMLG = poly(&gamma;-methyl L-glutamate) PGBLG = poly(&gamma;-benzyl L-glutamtate) bAbbrevations: HA = hydroxyapatite TCP = tricalcium phosphate cWeight percent of the porositizing agent based on the total weight of the composite material plus porositizing agent. dRefers to the percent by weight of porositizing agent removed (based on the theoretical amount of porositizing agent available) by leaching with water. eResult due to error in weighing. TABLE 2 MECHANICAL PROPERTIES OF VARIOUS COMPOSITE MATERIALS Compression Data Composite of Vicat Heat Strenght Deformation Recoverya Modulus Example No. Distorsion (psi) kPa (%) (%) (psi x 105) kPa x 106 19 - (12,380) 0.20 - (4.28) 85357.1 2.95 20 230 C - - - 21 - (5,177) - - 35694.2 22 230 C - - - 23 - (9,029) 3.6 27.8 (3.75) 62252.8 2.59 24 - (3,809) 1.25 42.4 (1.78) 26262.1 1.23 25 99 C - - - 26 - (3,542) - - 24421.2 27 91 C - - - 28 - (4,824) - - (3.13) 33260.3 2.16 29 - (8,034) 3.61 31.8 (3.77) 55392.5 2.60 34 - (8,017) 1.26 20.0 (4.30) 55275.3 2.96 a = After 24 hours. Example 35 Molded discs containing 85 percent hydroxy apatite-poly(y-methyl L-glutamate) composite (50 percent by weight of each component) and 15 percent sodium chloride blended therein (hereafter referred to as the 15 percent NaCl composite discs) were porositized by the general techniques described herein. Similarly, molded discs containing 80 percent hydroxyapatite -poly(y-methyl L-glutamate) composite (50 percent by weight of each component) and 20 percent sodium chloride blended therein (hereafter referred togas the 20 percent NaCl composite discs) were also prepared and porositized for evaluation in the study described below. Small pieces of the above-described molded composites were cut from the larger discs with a diamond blade and subsequently autoclaved for sterilization. The sterilized pieces were then surgically implanted into rabbits in an incision in the paravertebral muscles of the lumbar region and in a hole drilled in the iliac crest. X-rays taken 6 and 12 weeks later of the rabbits implanted with the 15 percent NaCl composite discs showed no remarkable soft -tissue response in the lumbar paravertebral muscles indicating absence of a chronic inflammatory reaction. The bony implant sites exhibited healing and a regeneration of new bone incorporating the surgically implanted composite material. The animals were sacrificed at 14 weeks and the discs and surrounding musculature of the paravertebral implant were excised for microscopic evaluation. Likewise, iliac crest sections containing the implant sites were surgically removed, decalcified and were subsequently made into paraffin embedded sections. Upon examination, the discs showed a thin, fibrous encapsulation of from 10 to 50 microns evidencing only a minor foreign body response. Animals implanted with the 20 percent NaCl composite discs showed a similar clinical history except that eight weeks after implantation there was no fibrous capsule formation around the implants and marrow was observed growing into the pores of the discs.

Claims: EMI28.1 1. A composite material of a calcium phosphate biomaterial and an organic material useful as a hard tissue prosthetic characterized in that said composite material is comprised of from 25 percent to 75 percent by weight of unsintered hydroxyapatite, unsintered tricalcium phosphate an unsintered calcium pyrophosphate or mixtures thereof, and from 25 percent to 75 percent by weight of a synthetic biodegradable polymer, said percentage by weight being based on the total weight of the calcium phosphate biomaterial plus the organic material, said composite material also optionally containing up to 30 percent by weight of a water soluble pore-forming agent, said percent being based on the total weight of the calcium phosphate biomaterial, plus organic material, plus pore-forming agent. 2. The composite material of Claim 1 containing from 40 to 60 percent by weight of the calcium phosphate biomaterial, from 40 to 60 percent by weight of the organic material, said percentages being based on the total weight of the calcium phosphate biomaterial plus the organic material, said composite material also containing from 10 to 20 percent by weight of a pore -forming agent, said percent being based on the total weight of the calcium phosphate biomaterial, plus organic material, plus pore-forming agent. 3. The composite material of Claim 1 wherein the synthetic biodegradable polymer is a polyester of lactic acid, a polyester of glycolic a-cid,,polyhydroxy- butyrate, or an a-amino acid polymer, and the pore -forming agent is poly(2-ethyl-2-oxazoline), polyvinyl pyrrolidone, polyvinyl alcohol, methylcellulose, sodium chloride or potassium chloride. 4. The composite material of Claim 1 wherein the calcium phosphate biomaterial is unsintered hydroxyapatite, the synthetic biodegradable polymer is a glutamic acid--ester, and the pore-forming agent is poly(2-ethyl-2-oxazaline) or sodium chloride. 5. A process for preparing a composite material comprised of from 25 percent to 75 percent by weight of sintered or unsintered calcium phosphate biomaterial and 2S percent to 75 percent by weight of an a-amino acid polymer, said percentages being based on the total weight of the calcium phosphate biomaterial plus a-amino acid polymer, characterized in that said process comprises polymerizing in situ an N-carboxyanhydride of an a-amino acid in the presence of a powdered calcium phosphate biomaterial, said polymerization taking place in an inert organic solvent. '6. The process of Claim'S wherein said N-carboxyanhydride is glutamic acid N-carboxyanhydride and said calcium phosphate biomaterial is sintered or unsintered hydroxyapatite, tricalcium phosphate, or mixtures thereof. 7. The process of Claim 5 wherein said composite material contains from 40 to 60 percent by weight of a calcium phosphate biomaterial and from 40 to 60 percent by weight of an a-amino acid polymer. 8. The process of Claim 5 including the additional step of adding a pore-forming agent to the composite material'prepared by said in situ polymerization. 9. The process of Claim 5 wherein said inert organic solvent is chloroform, dioxane, tetra- hydrofuran, methylene chloride, or mixtures thereof. 10. A method for the prosthetic supplementation or replacement of hard tissue characterized in that said method comprises molding into an anatom- ically-shaped form a composite material containing from 25 percent to 75 percent by weight of an unsintered calcium phosphate biomaterial and 25 percent to 75 percent by weight of a synthetic biodegradable polymer, said percentages being based on the total weight of the calcium phosphate biomaterial plus the synthetic biodegradable polymer, and implanting said anatomically-shaped form into an animal in need thereof.

Inventors: DORMAN, LINNEAUS C., MEYERS, PAUL A.
Applicants: THE DOW CHEMICAL COMPANY
Application year: 1986
Main classification: A61L27
IPC codes: A61F2, A61L27, C08G69