WO2008095083A1

WO2008095083A1 - Bioresorbable polymer/calcium sulfate composites and method of formation thereof

Info

Publication number: WO2008095083A1
Application number: PCT/US2008/052624
Authority: WO
Inventors: Jody Redepenning
Original assignee: Board Of Regents Of The University Of Nebraska
Priority date: 2007-01-31
Filing date: 2008-01-31
Publication date: 2008-08-07

Abstract

The present invention relates to implants for bone repair and replacement, and more particularly to polymer-calcium sulfate composites.

Description

BIORESORBABLE POLYMER/CALCIUM SULFATE COMPOSITES AND METHOD OF FORMATION THEREOF

TECHNICAL FIELD

BACKGROUND ART

The successful design of a prosthetic device to replace or repair skeletal tissue requires knowledge of the structure and mechanical properties of bone and an understanding of the means by which such prostheses become incorporated into the body. This information can then be used to define desirable characteristics of the implant to ensure that the graft functions in a manner comparable to organic tissue.

The mechanical properties of bone are related to the internal organization of the material, as reviewed by Roesler, H., "The History of Some Fundamental Concepts in Bone Biomechanics," Journal of Biomechanics, 20, 1025-34 (1987). Cortical bone is classified as a material of less than 30% porosity, as described by Keaveny, T. M. and W. C. Hayes, "Mechanical Properties of Cortical and Trabecular Bone," in Bone Volume 7: Bone Growth-B, B.K. Hall, ed., Boca Raton: CRC Press, 285-344 (1992), as a "solid containing a series of voids (Haversian canals, Volkmann's canals, lacunae and canaliculi). The porosity of cortical bone tissue (typically 10%) is primarily a function of the density of these voids." In contrast, cancellous/trabecular bone is "a network of small, interconnected plates and rods of individual trabeculae with relatively large spaces between the trabeculae." Trabecular bone has a porosity of 50-90% which is a function of the space between the trabeculae.

The material properties of bone are based on determinations of the elastic modulus, compressive and tensile strengths. As a general rule, bone is stronger in compression than in tension and cortical is stronger than trabecular bone. Ranges of reported elastic modulus have been from 10 MPa to 25 GPa (10 MPa to 2 GPa for cancellous bone; 4 to 25 GPa for cortical and cancellous bone); compressive strength between 40 and 280 MPa (40 to 280 MPa for cancellous bone; 138 to 193 MPa for cortical bone); and tensile strength between 3.5 MPa and 150 MPa (3.5 to 150 MPa for cancellous bone; 69 to 133 MPa for cortical bone) (Friedlaender and Goldberg, Bone and Cartilage Allografts Park Ridge: American Academy of Orthopedic Surgeons 1991; Jarcho, "Calcium Phosphate Ceramics as Hard Tissue Prosthetics" Clin. Orthopedics and Related Research 157, 259-278 1981; Gibson, "The Mechanical Behavior of Cancellous Bone" J. Biomechan, 18(5), 317-328 1985; Keaveny and Hayes 1992). Mechanisms by which bone may fail include brittle fracture from impact loading and fatigue from constant or cyclic stress. Stresses may act in tension, compression, or shear along one or more of the axes of the bone. A synthetic bone substitute must resist failure by any of these stresses at their physiological levels. A factor of safety on the strength of the implant may ensure that the implant will be structurally sound when subject to hyperphysiological stresses.

A graft may be necessary when bone fails and does not repair itself in the normal amount of time or when bone loss occurs through fracture or tumor. Bone grafts must serve a dual function: to provide mechanical stability and to be a source of osteogenesis. Since skeletal injuries are repaired by the regeneration of bone rather than by the formation of scar tissue, grafting is a viable means of promoting healing of osseous defects, as reviewed by Friedlaender, G. E., "Current Concepts Review: Bone Grafts." Journal of Bone and Joint Surgery, 69A(5), 786-790 (1987). Osteoinduction and osteoconduction are two mechanisms by which a graft may stimulate the growth of new bone. In the former case, inductive signals of little-understood nature lead to the phenotypic conversion of connective tissue cells to bone cells. In the latter, the implant provides a scaffold for bony ingrowth.

The bone remodeling cycle is a continuous event involving the resorption of pre-existing bone by osteoclasts and the formation of new bone by the work of osteoblasts. Normally, these two phases are synchronous and bone mass remains constant. However, the processes become uncoupled when bone defects heal and grafts are incorporated. Osteoclasts resorb the graft, a process which may take months. More porous grafts revascularize more quickly and graft resorption is more complete. After graft has been resorbed, bone formation begins. Bone mass and mechanical strength return to near normal.

Present methods for the repair of bony defects include grafts of organic and synthetic construction. Three types of organic grafts are commonly used: autografts, allografts, and xenografts. An autograft is tissue transplanted from one site to another in the patient. The benefits of using the patient's tissue are that the graft will not evoke a strong immune response and that the material is vascularized, which allows for speedy incorporation. However, using an autograft requires a second surgery, which increases the risk of infection and introduces additional weakness at the harvest site. Further, bone available for grafting may be removed from a limited number of sites, for example, the fibula, ribs and iliac crest. An allograft is tissue taken from a different organism of the same species, and a xenograft from an organism of a different species. The latter types of tissue are readily available in larger quantities than autografts, but genetic differences between the donor and recipient may lead to rejection of the graft.

Synthetic implants may obviate many of the problems associated with organic grafts. Further, synthetics can be produced in a variety of stock shapes and sizes, enabling the surgeon to select implants as his needs dictate, as described by Coombes, A. D. A. and J. D. Heckman, "Gel Casting of Resorbable Polymers: Processing and Applications," Biomaterials, 13(4), 217- 224 (1992). Metals, calcium phosphate ceramics and polymers have all been used in grafting applications.

Calcium phosphate ceramics are used as implants in the repair of bone defects because these materials are non-toxic, non-immunogenic, and are composed of calcium and phosphate ions, the main constituents of bone, in an apatitic structure (Jarcho, 1981; Frame, J. W., "Hydroxyapatite as a biomaterial for alveolar ridge augmentation," Int. J. Oral Maxillofacial Surgery, 16, 642-55 (1987); Parsons, et al "Osteoconductive Composite Grouts for Orthopedic Use," Annals N. Y. Academy of Sciences, 523, 190-207 (1988)). Both tricalcium phosphate (TCP) [Ca₃(PO₄)₂ ] and hydroxyapatite (HA) [Ca_1O(PO₄)_O(OH₂ ] have been widely studied for this reason. Calcium phosphate implants are osteoconductive, and have the apparent ability to become directly bonded to bone, as reported by Jarcho 1981. As a result, a strong bone-implant interface is created.

Calcium phosphate ceramics have a degree of bioresorbability which is governed by their chemistry and material structure. High density HA and TCP implants exhibit little resorption, while porous ones are more easily broken down by dissolution in body fluids and resorbed by phagocytosis. However, TCP degrades more quickly than HA structures of the same porosity in vitro. In fact, HA is relatively insoluble in aqueous environments. The use of calcium phosphates in bone grafting has been investigated because of the chemical similarities between the ceramics and the mineral matrix found in the teeth and bones of vertebrates. This characteristic of the material makes it a good candidate as a source of osteogenesis. However, the mechanical properties of calcium phosphate ceramics make them ill-suited to serve as a structural element. Ceramics are brittle and have low resistance to impact loading.

Biodegradable polymers are used in medicine as suture and pins for fracture fixation. These materials are well suited to implantation as they can serve as a temporary scaffold to be replaced by host tissue, degrade by hydrolysis to non-toxic products, and be excreted, as described by Kulkarai, et al., J. Biomedical Materials Research, 5, 169-81 (1971); Hollinger, J. O. and G. C. Battistone, "Biodegradable Bone Repair Materials," Clinical Orthopedics and Related Research, 207, 290-305 (1986).

Four polymers widely used in medical applications are poly(paradioxanone) (PDS), poly(lactic acid) (PLA), poly(glycolic acid) (PGA), and PLAGA copolymers. Copolymerization enables modulation of the degradation time of the material. By changing the ratios of crystalline to amorphous polymers during polymerization, properties of the resulting material can be altered to suit the needs of the application. For example, PLA is crystalline and a higher PLA content in a PLAGA copolymer results in a longer degradation time, a characteristic which may be desirable if a bone defect requires structural support for an extended period of time. Conversely, a short degradation time may be desirable if ingrowth of new tissue occurs quickly and new cells need space to proliferate within the implant.

Coombes and Heckman 1992 and Hollinger 1983 have attempted to create poly(lactide-co- glycolide) [(C₃H₄O₂)x(C₂H₂O₂)_y] implants as bone substitute. Hollinger used a PLAGA of high inherent viscosity (0.92 dl/g) prepared by a solvent-non-solvent casting method. Plugs of this material were implanted in tibial defects of Walter Reed rats, and humoral defects were created as control sites in which no polymer was implanted. Examination of the defects after sacrifice of the animals at 7, 14, 21, 28 and 42 days suggested that polymer may aid in osteoinduction in the early bone repair process. However, by 42 days, the rate of repair was equivalent in controls and experimental defect sites. Coombes and Heckman described a gel casting method for producing a three-dimensional PLAGA matrix. Success of this method, i.e., creation of a strong, rubbery gel, was dependent upon high inherent viscosity of the polymer (0.76-0.79 dl/g). Material properties of the polymer matrix through a degradation cycle were the focus of the research. The modulus of the PLAGA implant before degradation was 130 MPa, equivalent to that of cancellous bone. After eight weeks degradation in phosphate buffered saline (PBS), the strength of the material had deteriorated significantly. Moreover, the microporous structure (pores 205 .mu.m in diameter) has been shown to be too small to permit the ingrowth of cells, as reported by Friedlaender and Goldberg 1991 and Jarcho 1981. From a mechanical as well as a biological standpoint, this matrix is not ideal for use as a substitute bone graft material.

Other workers in this field have formed composites of various forms of hydroxyapatite and numerous polymers or other supplementary materials such as, e.g., collagen, glycogen, chitin, celluloses, starch, keratins, silk, nucleic acids, demineralized bone matrix, derivativized hyaluronic acid, polyanhydrides, polyorthoesters, polyglycolic acid, polylactic acid, and copolymers thereof. In particular, polyesters of .alpha.-hydroxycarboxylic acids, such as poly(L- lactide) (PLLA), poly(D,L-lactide) (PDLLA), polyglycolide (PGA), poly(lactide-co-glycolide (PLGA), poly(D,L-lactide-co-trimethylene carbonate), and polyhydroxybutyrate (PHB), and polyanhydrides, such as poly(anhydride-co-imide) and co-polymers thereof are known to bioerode and are suitable for use in the present invention. »In addition, bioactive glass compositions, such as compositions including SiO₂, Na₂O, CaO, P₂O5, Al₂O₃ and/or CaF₂, may be used. Other useful bioerodible polymers may include polysaccharides, peptides and fatty acids.

Bioerodible polymers are advantageously used in the preparation of bioresorbable hardware, such as but not limited to intermedulary nails, pins, screws, plates and anchors for implantation at a bone site. In preferred bioresorbable hardware embodiments, the supplementary material itself is bioresorbable and is added to the PCA calcium phosphate in particulate or fiber form at volume fractions of 1-50% and preferably, 1-20 wt %. In some preferred embodiments, the bioresorbable fiber is in the form of whiskers which interact with calcium phosphates according to the principles of composite design and fabrication known in the art. Such hardware may be formed by pressing a powder particulate mixture of the PCA calcium phosphate and polymer. In one embodiment, a PCA calcium phosphate matrix is reinforced with PLLA fibers, using PLLA fibers similar to those described by Tormala et al., which is incorporated herein by reference, for the fabrication of biodegradable self-reinforcing composites (Clin. Mater. 10:29- 34 (1992)).

The implantable bioceramic composite may be-be_prepared as a paste by addition of a fluid, such as water or a physiological fluid, to a mixture of a PCA calcium phosphate and a supplemental material. Alternatively, a mixture of the supplementary material with hydrated precursor powders to the PCA calcium phosphate can be prepared as a paste or putty. In cases where the supplementary material is to be dispersed within or reacted with a PCA calcium phosphate matrix, water may be added to one of the precursor calcium phosphates to form a hydrated precursor paste, the resulting paste is mixed with the supplementary material, and the second calcium phosphate source is then added. Alternatively, the calcium phosphate sources which make up the PCA calcium phosphate precursor powder may be premixed, water may then be added and then the supplementary material is added, hi those cases where it is desirable to have the supplementary material serve as the matrix, the fully hardened PCA calcium phosphate will be prepared in the desired form which will most often be of controlled particle size, and added directly to the matrix forming reaction (e.g., to gelling collagen). These materials may then be introduced into molds or be otherwise formed into the desired shapes and hardened at temperatures ranging from about 35-100° C. A particularly useful approach is to form the composite precursor paste into the approximate shape or size and then harden the material in a moist environment at 37° C. The hardened composite may then be precisely milled or machined to the desired shape for use in the surgical setting. The amount of particular PCA calcium phosphate to be incorporated into the supplemental material matrix will most often be determined empirically by testing the physical properties of the hardened composite according to the standards known to the art.

In PCT application No. PCT/US05/27257 (publication no. WO 2006/015316} there is described bioresorbable composites comprising an apatitic calcium phosphate and a compatible polymer as well as methods for forming such composites.

It is an object of the invention to provide novel bioresorbable composites comprising a calcium sulfate and a compatible polymer.

It is a further object of the invention to provide a novel method for forming such composites.

It is a further object of the invention to provide articles of manufacture comprising the composites.

DISCLOSURE OF INVENTION

The above and other objects are realized by the present invention, one embodiment of which relates to a composite comprising a bioabsorbable polymer or copolymer of a lactone monomer or mixture thereof and a salt, the composite having been prepared by the salt initiated ring- opening polymerization or copolymerization of the lactone monomer, wherein the salt is calcium sulfate or an osteoconductive, bioabsorbable derivative thereof.

A further embodiment of the invention concerns a method of preparing a composite comprising a bioabsorbable polymer or copolymer of a lactone monomer or mixtures thereof and a salt, comprising polymerizing or copolymerizing the lactone monomer by ring-opening polymerization initiated by the salt, wherein the salt is calcium sulate or an osteoconductive, bioabsorbable derivative thereof.

An additional embodiment of the invention is to provide an article of manufacture comprising the above-described composite.

BRIEF DESCRIPTION OF THE DRAWINGS

Fig. 1 is an NMR spectrum of the organic constituents of a composite.

Fig. 2 is an NMR spectrum of the organic constituents of a composite.

Fig. 3 is an NMR spectrum of the organic constituents of a composite.

BEST MODE FOR CARRYING OUT THE INVENTION

The present invention is predicated on the discovery that a superior bioresorbable composite comprising calcium sulfate or a suitable derivative thereof and certain polymers comprising specific lactones may be formed by the ring-opening polymerization of the lactone, either alone or in the presence of monomers suitable for copolymerization therewith, in the presence of the calcium sulfate which initiates the ring-opening polymerization. The resulting product is a composite containing the calcium sulfate completely entrapped within the polymeric matrix.

The lactone monomers that may be polymerized or copolymerized according to the method of the invention include those having the formula:

O

^{2 X™}^RI wherein:

straight or branched chain alkyl group, or HOCH₂-, and where all R's are independent on each y or z carbon atom and independent of each other; or

wherein: R₁-R₄ = H-, Ci-Cj₆ straight or branched chain alkyl group, or HOCH₂-, and where all R's are independent of each other.

Suitable lactone monomers that may be employed in the practice of the invention include any that form a bioabsorbable polymer or copolymer such as, but not limited to caprolactone, t- butyl caprolactone, zeta-enantholactone, deltavalerolactones, the monoalkyl-delta- valerolactones, e.g., the monomethyl-, monoethyl-, monohexyl-deltavalerolactones, and the like; the nonalkyl, dialkyl, and trialkyl-epsilon-caprolactones, e.g., the monomethyl-, monoethyl-, monohexyl-, dimethyl-, di-n-propyl-, di-n-hexyl-, trimethyl-, triethyl-, tri-n-epsilon- caprolactones, 5-nonyl-oxepan-2-one, 4,4,6- or 4,6,6-trimethyl-oxepan-2-one, 5-hydroxymethyl- oxepan-2-one, and the like; beta-lactones, e.g., beta-propiolactone, beta-butyrolactone gamma- lactones, e.g., gammabutyrolactone or pivalolactone, dilactones, e.g., lactide, dilactides, glycolides, e.g., tetramethyl glycolides, alkyl derivatives thereof and the like, ketodioxanones, e.g. l,4-dioxan-2-one, 1 ,5-dioxepan-2-one, and the like. The lactones can consist of the optically pure isomers or two or more optically different isomers or can consist of mixtures of isomers.

The salt employed in the practice of the invention is calcium sulfate or any osteoconductive, bioabsorbable derivative thereof that will initiate the ring-opening polymerization of any of the above lactones. Suitable salts include but are not limited to calcium sulfate hemihydrate, dihydrate or nonstoichiometric hydrates of calcium sulfate and the like or mixtures thereof. Suitable derivatives of anhydrous calcium sulfate may also be employed such as osteoconductive, bioabsorbable calcium sulfate derivatives such as anhydrous calcium sulfate that has been surface-exchanged with suitable nucleophiles capable of initiating the polymerization.

The composites of the invention are of interest for hard tissue replacement and fixation (bone fixation plates, pins, bars, plates and screws. There is no tissue reaction due to corrosion byproducts often associated with metal devices. Such compositions exhibit mechanical properties (compressive strength and elastic modulus) that approach those of living bone. Furthermore, these composites are not as hard or as brittle as ceramic materials often used for implants.

Another advantage of the composites of the invention and the methods for their preparation include is the fact a significant fraction of the living anion of the polymerization reaction is electrostatically bound to the salt. Consequently, there is improved interfacial strength between the salt and polymer. Interfacial strength is often limited when an inorganic compound or ceramic is merely admixed with an already formed organic polymer. The fact that the composites are produced in a single step and that no solvent is required to prepare the composite or process it is another unexpected advantage. The inorganic component of the composite, which is dispersed in the liquid phase monomer, serves as the polymerization initiator. The initiator can be removed easily from the polymer product and both the chemistry and the processing are environmentally benign. The macroscopic shape of the composites is determined by the shape of cast in which the polymerization occurs, or by standard machining techniques.

The process of the invention for manufacturing the composites is relatively simple, inexpensive, and can be carried out on large scales. The salt or derivative thereof attacks the lactone ring and opens it. The resulting "living anion" acts as a nucleophile to open another lactone ring, and the process repeats itself to propagate the polymerization until a chain- terminating step occurs.

The exact polymerization mechanism involved in the method of the invention is presently unknown. The identity of the reaction that initiates the ring opening process, the mechanism that leads to chain propagation, and what events lead to chain termination are presently also unknown. In fact, given the complexity of the system, there may well be more than one mechanism that contributes to each of these events.

While not wishing to be bound by any theory as to the exact mechanisms of the methods of the invention, some preliminary experimental results have provided some clues concerning the possible polymerization mechanisms. The first attempt at polymerizing lactide with a solid-state initiator involved the use of a surface-modified hydroxyapatite. Hydroxyapatite has well known ion exchange properties. The original hypothesis was that methoxide ions could be exchanged into the surface of hydroxyapatite and that these methoxide ions could serve as the nucleophile to initiate the ring-opening polymerization of lactide (1) to structure (2), which could in turn act as the nucleophile in chain propagation steps that would ultimately lead to polymer (3), as outlined below.

That first experiment using methoxide-exchanged HA to initiate the polymerization of lactide in a melt was successful. A number of subsequent experiments were performed in rapid success to determine the influence of temperature and lactide/HA ratio on the polymerization process. Shortly thereafter, it was decided to run a control. A pure sample of hydroxyapatite, i.e., one that was not exchanged with methoxide, produced a HA/polylactide composite that exhibited physical properties very similar to that observed for the methoxide-exchanged HA. It became clear that the methoxide was not necessary.

Polymer chemists who are familiar with this class of reactions will recall that water can play an important role during ring-opening polymerizations. It is also true that the surface of hydroxyapatite can be quite hydrophilic. Hence, it seemed plausible that surface-bound water might he initiating the polymerization of lactide, not hydroxyapatite. If it is present, water may well play a role as an initiator in this system, but preliminary results clearly demonstrate that the presence of water is not required. The hydroxyapatite used to perform the kinetics experiment shown in Fig. 2, was dried at 400°C and stored in an inert atmosphere box prior to use. Additionally, before performing any polymerization, the lactide was sublimed to remove water that is frequently present therein when purchased. It seems plausible that water might react with the alkoxide end of 2 or 3 to give an inactive terminal alcohol. It is unclear whether this terminal alcohol might be reactivated in a subsequent reaction with hydroxide ions of HA.

In the following scheme, if hydroxide is the nucleophile that initiates the original ring- opening event to produce 4, it is noteworthy that the carboxylic acid terminus of 4 should react with its own alkoxide terminus, or with the alkoxide terminus of another polymer chain, in (what could be) a chain-terminating step to produce 5.

It is possible that 5 might be re-activated in a reaction between the terminal alcohol and a hydroxide in the surface of the hydroxyapatite.

Whatever the mechanistic details ultimately prove to be, preliminary results suggest that the polymerization of cyclic esters, i.e., lactones with calcium sulfate is surface initiated, but not completely surface confined.

Consequently, in early stages of the polymerization it seems likely that the short polymer chains are tightly associated with the surface through electrostatic interactions. In other words, if an anionic mechanism generates species 2 as shown above, the resulting anionic end of the chain and the remaining cationic surface cannot stray from each other to any appreciable extent; however, this does not preclude the existence of chain transfer steps, which are presently unidentified, from displacing the polymer chain from the surface to give a neutral salt surface and neutral polymer chain in the melt. It seems likely that such chain transfer steps are possible under appropriate conditions. In lieu of such steps it would be impossible to extract polymer from the composite for later characterization by solution phase NMR,

Both glycolide and ε-caprolactone and have been polymerized by ring-opening mechanisms similar to that used above for lactide. Homopolymers of poly-lactide are often quite brittle, but by copolymerizing glycolide and/or ε-caprolactone with lactide, one can gain some control of the mechanical properties and the rates at which the resulting polymers are absorbed in the body.

The calcium sulfates employed herein may conveniently be prepared according to any conventional method. Moreover, calcium sulfates of virtually any convenient and desirable particle size may be utilized in the practice of the invention. It seems likely that the rate of polymerization will be proportional to the surface area of the salt present in the reaction mixture, not to the number of moles of salt.

Generally, the composites are prepared by polymerizing or copolymerizing the lactone(s) in the presence of the salt initiator as a melt, utilizing no solvent. The salt may be intimately admixed with the monomer(s) during the polymerization phase to produce a composite with the salt as evenly dispersed therein as possible. Alternatively, the salt may be arranged in any desired configuration or shape and allowed to polymerize in the presence of the initiating salt to produce an article having certain unique desired properties. Generally, temperatures of from about 90° to about 200° C are sufficient to start the polymerization, which becomes self- sustaining. It will be understood by those skilled in the art, however, that temperatures above and below the above-cited range may be utilized in certain applications, depending upon the particular monomer(s) and initiator employed.

The composites may be formed in molds of virtually any shape to produce an article of the desired shape or configuration or the latter may be obtained by machining and finishing a blank composite having the desired composition. Generally, the composite contains from about 1% to about 99%, preferably from about 25% to about 60%, by weight, of the salt distributed and entrapped within the polymer matrix, depending, of course, upon the properties desired in the end product.

We have discovered that solid substances can be used to induce the ring-opening polymerization of cyclic lactone monomers such as lactide, glycolide, and caprolactone. Composite materials containing the solid substance and the polymer are produced. If desired, the polymer can be isolated by extracting it from the composite. In many cases it appears that the polymerization is initiated by a nucleation step that occurs at or near the surface of the solid. The composite is typically prepared by heating together the inorganic substance and the monomer without the addition of solvent, catalyst, or initiator. We have found that solid substances containing at least one nucleophilic component, such as a nucleophilic anion, are particularly effective in initiating the desired polymerizations. Examples include (but are not limited to) CaO, Ca(OH)₂, and alumina.

For cases in which the solid substance does not contain a nucleophilic component that will initiate the desired polymerization, hydrated forms of the solid substance can be used to initiate the polymerization. These hydrated forms can contain either stoichiometric or nonstoichiometric amounts of water. Examples include (but are not limited to) powdered or pellitized CaSO₄χH₂O, where it is typically true that 0< χ< 2. Alternatively, if the solid substance does not contain a nucleophilic component that will initiate the desired polymerization, it can be mixed with another solid substance that does induce the ring-opening polymerization. A composite containing both solid substances and the desired polymer is formed. Examples include (but are not limited to) mixtures OfCaSO₄ and hydroxyapatite, Ca₅(PO₄)₃OH.

We have also discovered that pure solid substances that do not induce ring-opening polymerization of cyclic lactones can be modified with nucleophiles to effectively induce the polymerization. This modification can include the purposeful addition of a nucleophile, or can be due to the fact that the solid substance has not been purchased or prepared in a highly pure form. One example is pure, anhydrous CaSO₄, which in our hands polymerizes lactide very slowly. Inexpensive preparations OfCaSO₄ can contain obtain impurities such as hydroxide or oxide. The impure CaSO₄ can effectively polymerize lactide to produce composites that are predominately CaSO₄ and polylactide.

Alternatively, the nucleophilic inclusions can be purposefully added. The inclusions can include (but are not limited to) hydroxide, oxide, lactate or commonly used polymerization nucleopbiles containing octanoate. Found below is an example of non-optimized conditions under which calcium sulfate hemihydrate (CaSO₄ /4H₂O) can be used to form a composite with poly-L-Lactide. hi this case the composite is prepared using approximately 90% by weight calcium sulfate hemihydrate and 10% lactide. Composites of this type may be interesting because of the likelihood that the polyL-Lactide will slow the dissolution rate of the calcium sulfate in vivo.

A total of 6.30 grams of calcium sulfate hemihydrate and 0.70 grams of L-lactide were weighed out at room temperature and then placed in a sealed vessel under nitrogen gas. The vessel was rotated at 1 rpm to assure that the components were mixed without causing significant mechanical damage to the calcium sulfate hemihydrate. The vessel was heated at 138° C for approximately 18 hours. At the end of this time no liquid monomer was observed visually. The sample was cooled to room temperature and the organic constituents were extracted from the composite with deuterated chloroform. The nuclear magnetic resonance (NMR) spectrum of this sample showed that these conditions were sufficient to convert most of the monomer to polymer. Figure 1 is a NMR spectrum of the organic constituents in the composite. Comparison of the integrated intensity for the polymer multiplet at approximately 5.18ppm with the integrated intensity for the monomer quartet at approximately 5.03 ppm shows that the polymeπmonomer ratio is approximately 22: 1. Found below is an example of non-optimized conditions under which hydroxyapatite can be used to initiate the polymerization of L-lactide in the presence of calcium sulfate. A composite of calcium sulfate, hydroxyapatite and poly-L-lactide is formed. In this case the composite is prepared using approximately 80% by weight anhydrous calcium sulfate, 10% hydroxyapatite, and 10% lactide. Composites of this type are interesting because of the likelihood that the poly- L-lactide will slow the dissolution rate of the calcium sulfate in vivo.

A total of 4.00 grams of anhydrous calcium sulfate, 0.50 grams of hydroxyapatite, and 0.50 grams of L-lactide were weighed out at room temperature and then placed in a scaled vessel under nitrogen gas. The vessel was rotated at 1 rpm to assure that the components were mixed without causing significant mechanical damage to inorganic components. The vessel was heated at 130° C for approximately 33 hours. At the end of this time, no liquid monomer was observed visually. The sample was cooled to room temperature and the organic constituents were extracted from the composite with deuterated chloroform. The nuclear magnetic resonance (NMR) spectrum of this sample showed that these conditions were sufficient to convert most of the monomer to polymer. Figure 2 is a NMR spectrum of the organic constituents in the composite. Comparison of the integrated intensity for the polymer multiplet at approximately 5.18ppm with the integrated intensity for the monomer quartet at approximately 5.03ppm shows that the polymer.monomer ratio is approximately 33:1.

Found below is an example of non-optimized conditions under which basic alumina (Al₂O₃) can be used to initiate the polymerization of L-lactide to form a composite OfA^O₃ with poly- Lactide. In this case the composite is prepared using approximately 33% by weight A^O₃ and 67% L-lactide.

A total of 0.4989 grams of basic alumina and 0.9976 grams of L-lactide were weighed out at room temperature and then placed in a sealed vessel under nitrogen gas. The contents were heated at 120° C for approximately 48 hours while being stirred magnetically. Over this period of time a large increase in viscosity was observed. At the end of the 48 hours of reaction time, the molten composite was cooled to room temperature and the organic constituents were extracted with deuterated chloroform. The nuclear magnetic resonance (NMR) spectrum of this sample showed that these conditions were sufficient to convert most of the monomer to polymer. Figure 3 is a NMR spectrum of the organic constituents in the composite. Comparison of the integrated intensity for the polymer multiplet at approximately 5.18ppm with the integrated intensity for the monomer quartet at approximately 5.03 ppm shows that the polymer :monomer ratio is approximately 20: 1.

Claims

CLAIMSWhat is claimed is:

1. A composite comprising a bioabsorbable polymer or copolymer of a lactone monomer or mixture thereof and a salt, said composite having been prepared by the salt initiated ring-opening polymerization or copolymerization of said lactone monomer, wherein said salt is calcium sulfate or an osteoconductive, bioabsorbable derivative thereof.

2. A composite of claim 1 wherein said lactone monomer has the formula:

wherein: X=nil, -O-, or — O-C=O; z=l-3; y=l-4; R₁-R₄ = H-, C_rC_]6, straight or branched chain alkyl group, or HOCH₂-, and where all R's are independent on each y or z carbon atom and independent of each other; or

wherein R₁-R₄ = H-, C₁-Ci₆ straight or branched chain alkyl group, or HOCH₂-, and where all R's are independent of each other.

3. The composite of claim 2 wherein said monomer is caprolactone, t-butyl caprolactone, zeta-enantholactone, deltavalcrolactones, the monoalkyl-delta-valerolactones, e.g., the monomethyl-, monoethyl-, monohexyl-deltavalerolactones, and the like; the nonalkyl, dialkyl, and trialkyl-epsilon-caprolactones, e.g., the monomethyl-, monoethyl-, monohexyl-, dimethyl-, di-n-propyl-, di-n-hexyl-, trimethyl-, triethyl-, tri-n-epsilon-caprolactones, 5-nonyl-oxepan-2- one, 4,4,6- or 4,6,6-trimethyl-oxepan-2-one, 5-hydroxymethyl-oxepan-2-one, and the like; beta- lactones, e.g., beta-propiolactone, beta-butyrolactone gamma-lactones, e.g., gammabutyrolactone or pivalolactone, dilactones, e.g., lactide, dilactides, glycolides, e.g., tetramethyl glycolides, alkyl derivatives thereof and the like, ketodioxanones, e.g., 1 ,4-dioxan-2-one, l,5-dioxepan-2-one, and the like.

4. A composite of claim 3 wherein said composite comprises a polymer or copolymer of lactide and one or more monomers that copolymerize therewith to form an osteoconductive, bioabsorbable polymer, said composite having been prepared by the said ring-opening copolymerization of lactide with said one or monomers.

5. A composite of claim 1 wherein said composite contains from about 1% to about 99%, by weight, of said salt, distributed throughout and entrapped by said polylactide polymer or copolymer.

6. A composite of claim 5 wherein said composite contains from about 25% to about 60%, by weight, of said salt.

7. A composite of claim 1 wherein said salt is calcium sulfate hemihydrate, dihydrate or nonstoichiometric hydrates of calcium sulfate and the like or mixtures thereof.

8. A composite of claim 1 wherein said salt is anhydrous calcium sulfate that has been surface-exchanged with a nucleophile capable of initiating the polymerization.

9. A method of preparing a composite comprising a bioabsorbable polymer or copolymer of a lactone monomer or mixtures thereof and a salt, comprising polymerizing or copolymerizing said lactone monomer by ring-opening polymerization initiated by said salt, wherein said salt is calcium sulfate or an osteoconductive, bioabsorbable derivative thereof.

10. The method of claim 9 wherein said lactone monomer has the formula:

wherein X=nil, -O-, or — 0-C=O; z=l-3; y=l-4; R₁-R₄ — H-, Ci-C₁₆ straight or branched chain alkyl group, or HOCH₂-, and where all R's are independent on each y or z carbon atom and independent of each other; or

wherein R₁-R₄ — H-, Ci-Ci₆ straight or branched chain alkyl group, or HOCH₂-, and where all R's are independent of each other.

11. The method of claim 10 wherein said lactone monomer is caprolactone, t-butyl caprolactone, zeta-cnantholactone, deltavalerolactones, the monoalkyl-delta-valerolactones, e.g., the monomethyl-, monoethyl-, monohexyl-deltavalerolactones, and the like; the nonalkyl, dialkyl, and trialkyl-epsilon-caprolactones, e.g., the monomethyl-, monoethyl-, monohexyl-, dimethyl-, di-n-propyl-, di-n-hexyl-, trimethyl-, triethyl-, tri-n-epsilon-caprolactones, 5-nonyl- oxepan-2-one, 4,4,6- or 4,6,6-trimethyl-oxepan-2-one, 5-hydroxymethyl-oxepan-2-one, and the like; beta-lactones, e.g., beta-propiolactone, beta-butyrolactone gamma-lactones, e.g., gammabutyrolactone or pivalolactone, dilactones, e.g., lactide, dilactides, glycolides, e.g., tetramethyl glycolides, alkyl derivatives thereof and the like, ketodioxanones, e.g., l,4-dioxan-2- one, l,5-dioxepan-2-one, and the like.

12. The method of claim 11 wherein said composite comprises a polymer of or a copolymer of lactide and one or monomers that polymerize therewith to form an osteoconductive, bioabsorbable polymer, and said ring-opening polymerization of lactide is conducted in the presence of said one or monomers.

13. The method of claim 9 wherein said composite contains from about 1% to about 99%, by weight, of said salt, substantially homogenously distributed throughout and entrapped by said polylactide polymer or copolymer.

14. The method of claim 9 wherein said composite contains from about 25% to about 60%, by weight, of said salt.

15. The method of claim 9 wherein said salt is calcium sulfate hemihydrate, dihydrate or nonstoichiometric hydrates of calcium sulfate and the like or mixtures thereof.

16. The method of claim 9 wherein said salt is anhydrous calcium sulfate that has been surface-exchanged with a nucleophile capable of initiating the polymerization.

17. An article of manufacture comprising the composite of claim 1.

18. The article of manufacture of claim 17 comprising a bioprosthesis or bone fixation device.

19. The article of claim 18 wherein said bone fixation device is a pin, screw, bar or plate.