NZ232107A - Biodegradable implants formed in-situ; use as slow release carriers and prepolymer compositions - Google Patents

Description

232 107 Priority Date(s): Complete Specification Filed: .......

Class- ISI iCOjAty -2, JoZj Vltlww* Ivf*** •••••••• • *•*•«( • • *rfm • •• •••••■■ M ••••••••»••••«•• (Xl* ■«•••• At i JPi^o \ Y» IQ kii • • • 4 • Nb • a • •••• • • • •XjmJb A » m • • • m • mi • • ••• *t» • • • (li I f\<o\\C{?To^vOO- £ubticatton DatK P.O. Journal, No: ... is.a.fc Patents Form No. 5 NEW ZEALAND PATENTS ACT 1953 COMPLETE SPECIFICATION f' ^ / X <4? \ C '• Z;j ■%oY BIODEGRADABLE IN-SITD FORMING IMPLANTS AND METHODS OF PRODUCING THE SAME WE, SOUTHERN RESEARCH INSTITUTE, a non-profit Alabama Corporation, U.S.A. of 2000 Ninth Avenue, South Birmingham, Alabama 35255-5305, United States of America, hereby declare the invention, for which We pray that a patent may be granted to us, and the method by which it is to be performed, to be particularly described in and by the following statement: (followed by Page 2) 232 1 0 BIODEGRADABLE IN-SITU FORMING IMPLANTS AND METHODS OF PRODUCING THE SAME Technical Field The present invention relates to a method and composition for producing biodegradable polymers, and more particularly to the use of such polymers for providing syringeable, in-situ forming, solid, biodegradable implants.

Background Art Biodegradable polymers have been used for many years in medical applications. These include sutures, surgical clips, staples, implants, and drug delivery systems. The majority of these biodegradable polymers have been thermoplastic materials based upon glycolide, lactide, e-caprolactone, and copolymers thereof. Typical examples are the polyglycolide sutures described in U.S. Patent No. 3,297,033 to Schmitt. the poly(L-lactide-co-glycolide) sutures described in U.S. Patent No. 3,636,956 to Schneider. the poly(L-lactide-co-glycolide) surgical clips and staples described in U.S. Patent No. 4,523,591 to Kaplan %t al. . and the drug'-delivery systems described in U.S. Patent No. 3,773,919 to Bosvell et al.. U.S. Patent No. 3,887,699 to Yolles. U.S. Patent No. 4,155,992 to Schmitt. U.S. Patent No. 4,379,138 to Pitt et al.. and U.S. Patent Nos. 4,130,639 and 4,186,189 to Shalabv et al.

All of the biodegradable polymers described in these patents are thermoplastic materials. Consequently, they can be heated and formed into various shapes such as la (followed by Page 2) 232107 fibers, clips, staples, pins, films, etc. Only when heated above their melting point do these polymers become liquid. During their normal use, they are solids.

Thermoset biodegradable polymers have also been previously described for use in medical applications.

These polymers have been formed by crosslinking reactions which lead to high-molecular-weight materials that do not melt or form flowable liquids at high temperatures. 10 Typical examples of these materials are the crosslinked polyurethanes described in U.S. Patent No. 2,933,477 to Hostettler and U.S. Patent No. 3,186,971 to Hostettler et al. Copolymers based on e-caprolactone and L-lactide or DL-lactide crosslinked via peroxide initiators were 15 described in U.S. Patent Nos. 4,045,418 and 4,057,537, both to Sinclair. Crosslinked caprolactone copolymers have been prepared by incorporation of a bislactone into a monomer feed, as described in U.S. Patent No. 4,379,138 to Pitt et al. Trihydroxy-functional copolymers of €-caprolactone and 20 e-valerolactone have been crosslinked with diisocyanates, thereby affording biodegradable polymers, as described in Pitt et al.. J. Polvm. Sci.: Part A: Polvm Chem. 25:955-966; 1987. These polymers are also solids when crosslinked or cured.

Although these two classes of biodegradable polymers have many useful biomedical applications, there are seyeral important limitations to their use in the body where body is defined as that of humans, animals, birds, 30 fish, and reptiles. Because these polymers are solids, all instances involving their use have required initially forming the polymeric structures outside the body, followed by insertion of the solid structure into the body. For example, sutures, clips, and staples are all formed from 35 thermoplastic biodegradable polymers prior to use. When inserted into the body, they retain their original shape 2 3 2 1 0 7) 3 rather than flow to fill voids or cavities where they may be most needed.

Similarly, drug-delivery systems using these biodegradable polymers have to be formed outside the body. In such instances, the drug is incorporated into the polymer and the mixture shaped into a certain form such a cylinder, disc, or fiber for implantation, with such solid implants, the drug-delivery system has to be inserted into the body through an incision. These incisions are often larger than desired by the medical profession and lead to a reluctance of the patients to accept such an implant or drug-delivery system.

The only way to avoid the incision with these polymers is to inject them as small particles, microspheres, or microcapsules. These may or may not contain a drug which can be released into- the body.

Although these small particles can be injected into the body with a syringe, they do not always satisfy the demand for a biodegradable implant. Because they are particles, they do not form a continuous film or solid implant with the structural integrity needed for certain prostheses.

When inserted into certain body cavities such as the mouth, a periodontal pocket, the eye, or the vagina where there is considerable fluid flow, these small particles, microspheres, or microcapsules are poorly retained because of their small size and discontinuous nature. In addition, microspheres or microcapsules prepared from these polymers and containing drugs for release into the body are sometimes difficult to produce on a large scale, and their storage and injection characteristics present problems. Furthermore, one other major limitation of the microcapsule or small-particle system is their lack of reversibility without extensive surgical intervention. That is, if there are complications after they have been injected, it is 4 232 10 7 considerably more difficult to remove them from the body than with solid implants.

Therefore, there exists a need for a method and composition which provides a biodegradable, polymeric structure useful in overcoming the above-described limitations.

There exists a further need for a method and composition for providing syringeable, in-situ forming, solid, biodegradable implants which can be used as prosthetic devices and/or controlled delivery systems.

Moreover, there exists a need for such a method and composition which can provide implants having a range of properties from soft to rigid, so as to be usable with both soft and hard tissue.

Disclosure of the Invention The present invention relates to the production and use of biodegradable polymers as prosthetic implants and controlled-release, drug-delivery systems which can be administered as liquids via, for example, a syringe and needle, but which coagulate or cure ("set") shortly after dosing to form a solid. The implants are biodegradable because they are made from biodegradable polymers and copolymers comprising two types of polymer systems: thermoplastic and thermosetting.

A thermoplastic system is provided in which a solid, linear-chain, biodegradable polymer or copolymer is dissolved in a solvent, which is nontoxic and water miscible, to form a liquid solution. Once the polymer solution is placed into the body where there is sufficient water, the solvent dissipates or diffuses away from the polymer, leaving the polymer to coagulate or solidify into a solid structure. The placement of the solution can be 232 10 7 anywhere within the body, including soft tissue such as muscle or fat, hard tissue such as bone, or a cavity such as the periodontal, oral, vaginal, rectal, nasal, or a pocket such as a periodontal pocket or the cul-de-sac of the eye. For drug-delivery systems, the biologically active agent is added to the polymer solution where it is either dissolved to form a homogeneous solution or dispersed to form a suspension or dispersion of drug within the polymeric solution. When the polymer solution is exposed to body fluids or water, the solvent diffuses away from the polymer-drug mixture and water diffuses into the mixture where it coagulates the polymer thereby trapping or encapsulating the drug within the polymeric matrix as the implant solidifies. The release of the drug then follows the general rules for diffusion or dissolution of a drug from within a polymeric matrix.

Another embodiment of the invention is also provided, namely, a thermosetting system comprising the synthesis of crosslinkable polymers which are biodegradable and which can be formed and cured in-situ. The thermosetting system comprises reactive, liquid, oligomeric polymers which contain no solvents and which cure in place to form solids, usually with the addition of a curing catalyst.

The multifunctional polymers useful in the thermosetting system are first synthesized via copolymerization of either DL-lactide or L-lactide with e-caprolactone using a multifunctional polyol initiator and a catalyst to form polyol-terminated prepolymers. The polyol-terminated prepolymers are then converted to acrylic ester-terminated prepolymers, preferably by acylation of the alcohol terminus with acryloyl chloride via a Schotten-Baumann-1ike technique, i.e.. reaction of acyl halides with alcohols. The acrylic ester-terminated prepolymers may also be synthesized in a number of other ways, including 232 1 6 but not limited to, reaction of carboxylic acids (i.e.. acrylic or methacrylic acid) with alcohols, reaction of carboxylic acid esters (i.e.. methyl acrylate or methyl methacrylate) with alcohols by transesterification, and reaction of isocyanatoalkyl acrylates (i.e.. isocyanatoethyl methacrylate) with alcohols.

The liquid acrylic-terminated prepolymer is cured, preferably by the addition of benzoyl peroxide or azobisisobutyronitrile, to a more solid structure. Thus, for an implant utilizing these crosslinkable polymers, the catalyst is added to the liquid aerylic-terminated prepolymer immediately prior to injection into the body. Once inside the body, the crosslinking reaction will proceed until sufficient molecular weight has been obtained to cause the polymer to solidify. The liquid prepolymer, when injected, will flow into the cavity or space in which it is placed and assume that shape when it solidifies. For drug delivery utilizing this system, biologically active agents are added to the liquid polymer systems in the uncatalyzed state.

In both the thermoplastic and the thermosetting systems, the advantages of liquid application are achieved. For example, the polymer may be injected via syringe and needle into a body while it is in liquid form and then left in-situ to form a solid biodegradable implant structure. The ne%d to form an incision is eliminated, and the implant will assume the shape of its cavity. Furthermore, a drug-delivery vehicle may be provided by adding a biologically active agent to the liquid prior to injection. Once the implant is formed, it will release the agent to the body and then biodegrade. The term "biologically active agent" means a drug or some other substance capable of producing an effect on a body. 23 2 1 07! It is an object of the present invention, therefore, to provide a method and composition for producing biodegradable polymers.

It is also an object of the present invention to provide such a polymer which may be useful in producing syringeable, in-situ forming, solid biodegradable implants.

It is a further object of the present invention 10 to provide such an implant which can be used in a controlled-release delivery system for biological agents.

It is a further object of the present invention to provide implants having a range of properties from soft 15 and elastomeric to hard and rigid, so as to be usable with both soft and hard tissue.

Brief Description of the Figures and Tables Fig. 1 illustrates the synthesis of acrylate-20 terminated prepolymers and subsequent crosslinlcing by free-radical initiators; Fig. 2 illustrates structures for the random copolymer of e-caprolactone and L-lactide initiated "with a 25 diol; Table 1 is a summary of the bifunctional PLC prepolymers synthesized; Table 2 is a summary of the acrylic ester terminated prepolymers synthesized; and Table 3 is a summary of curing studies. 232 107 8 Best Mode of Carrying Out the Invention The present invention relates to biodegradable, in-situ forming implants and methods for producing the same. The present invention also relates to a liquid biodegradable polymeric delivery system that can be injected into a body where it forms a solid and releases a biologically active agent at a controlled rate. Two types of biodegradable polymeric systems are described: thermoplastic polymers' dissolved in a biocompatible solvent and thermosetting polymers that are liquids without the use of solvents.

A. Thermoplastic System A thermoplastic system is provided in which a solid, linear-chain, biodegradable polymer is dissolved in a biocompatible solvent to form a liquid, which can then be administered via a syringe and needle. Examples of biodegradable polymers which can be used in this application are polylactides, polyglycolides, polycaprolactones, polyanhydrides, polyamides, polyurethanes, polyesteramides, polyorthoesters, polydioxanones, polyacetals, polyketals, polycarbonates, polyorthocarbonates, polyphosphazenes, polyhydroxybutyrates, polyhydroxyvalerates, polyalkylene oxalates, polyalkylene succinates, poly(malic acid), poly(amino acids), polyvinylpyrrolidone, polyethylene glycolf polyhydroxycellulose, chitin, chitosan, and copolymers, terpolymers, or combinations or mixtures of the above materials. The preferred polymers are those which have a lower degree of crystallization and are more hydrophobic. These polymers and copolymers are more soluble in the biocompatible solvents than the highly crystalline polymers such as polyglycolide and chitin which also have a high degree of hydrogen-bonding. Preferred materials with the desired solubility parameters are the polylactides, polycaprolactones, and copolymers of these 232 1 0 7 9 with glycolide in which there are more amorphous regions to enhance solubility.

It is also preferred that the solvent for the biodegradable polymer be non-toxic, water miscible, and otherwise biocompatible. Solvents that are toxic should not be used to inject any material into a living body. The solvents must also be biocompatible so that they do not cause severe tissue irritation or necrosis at the site of implantation. Furthermore, the solvent should be water miscible so that it will diffuse quickly into the body fluids and allow water to permeate into the polymer solution and cause it to coagulate or solidify. Examples of such solvents include N-methyl-2-pyrrolidone, 2-pyrrolidone, ethanol, propylene glycol, acetone, methyl acetate, ethyl acetate, methyl ethyl ketone, dimethylformamide, dimethyl sulfoxide, tetrahydrofuran, caprolactam, decylmethy1sulfoxide, oleic acid, and 1-dodecylazacycloheptan-2-one. The preferred solvents are N-methyl-2-pyrrolidone, 2-pyrrolidone, dimethyl sulfoxide, and acetone because of their solvating ability and their compatibility.

The solubility of the biodegradable polymers in the various solvents will differ depending upon their crystallinity, their hydrophilicity, hydrogen-bonding, and molecular weight. Thus, not all of the biodegradable polymers will be soluble in the same solvent, but each polymer or copolymer should have its optimum solvent.

Lower molecular-weight polymers will normally dissolve more readily in the solvents than high-molecular-weight polymers. As a result, the concentration of a polymer dissolved in the various solvents will differ depending upon type of polymer and its molecular weight. Conversely, the higher molecular-weight polymers will normally tend to coagulate or solidify faster than the very low-molecular-weight polymers. Moreover the higher molecular-weight 2 3 2 1 0 7. polymers will tend to give higher solution viscosities than the low-molecular-weight materials. Thus for optimum injection efficiency, the molecular weight and the concentration of the polymer in the solvent have to be controlled.

For example, low-molecular-weight polylactic acid formed by the condensation of lactic acid will dissolve in N-methyl-2-pyrrolidone(NMP) to give a 73% by weight solution which still flows easily through a 23-gauge syringe needle, whereas a higher molecular-weight poly(DL-lactide) (DL-PLA) formed by the additional polymerization of DL-lactide gives the same solution viscosity when dissolved in NMP at only 50% by weight. The higher molecular-weight polymer solution coagulates immediately when placed into water. The low-molecular-weight polymer solution, although more concentrated, tends to coagulate very slowly when placed into water.

For polymers that tend to coagulate slowly, a solvent mixture can be used to increase the coagulation rate. Thus one liquid component of the mixture is a good solvent for the polymer, and the other component is a poorer solvent or a non-solvent. The two liquids are mixed at a ratio such that the polymer is still soluble but precipitates with the slightest increase in the amount of non-solvent, such as water in a physiological environment. By necessity, the solvent system must be miscible with both the polymer and water. An example of such a binary solvent system is the use of NMP and ethanol for low-molecular-weight DL-PLA. The addition of ethanol to the NMP/polymer solution increases its coagulation rate significantly.

It has also been found that solutions containing very high concentrations of high-molecular-weight polymers sometimes coagulate or solidify slower than more dilute solutions. It is suspected that the high concentration of Qsswsjfcv*.... 232 1 "7 11 polymer impedes the diffusion of solvent from within the polymer matrix and consequently prevents the permeation of water into the matrix where it can precipitate the polymer chains. Thus, there is an optimum concentration at which 5 the solvent can diffuse out of the polymer solution and water penetrates within to coagulate the polymer.

In one envisioned use of the thermoplastic system, the polymer solution is placed in a syringe and 10 injected through a needle into the body. Once in place, the solvent dissipates, the remaining polymer solidifies, and a solid structure is formed. The implant will adhere to its surrounding tissue or bone by mechanical forces and can assume the shape of its surrounding cavity. Thus, the 15 biodegradable polymer solution can be injected subdermally like collagen to build up tissue or to fill in defects. It can also be injected into wounds including burn wounds to prevent the formation of deep scars. Unlike collagen, the degradation time of the implant can be varied from a few 20 weeks to years depending upon the polymer selected and its molecular weight. The injectable polymer solution can also be used to mend bone defects or to provide a continuous matrix when other solid biodegradable implants such as hydroxyapatite plugs are inserted into bone gaps. The 25 injectable system can also be used to adhere tissue to tissue or other implants to tissue by virtue of its mechanical bonding or encapsulation of tissue and prosthetic devices.

Another envisioned use of the thermoplastic system is to provide a drug-delivery system. In this use, a bioactive agent is added to the polymer solution prior to injection, and then the polymer/solvent/agent mixture is injected into the body. In some cases, the drug will also 35 be soluble in the solvent, and a homogenous solution of polymer and drug will be available for injection. In other cases, the drug will not be soluble in the solvent, and a 232 1 12 suspension or dispersion of the drug in the polymer solution will result. This suspension or dispersion can also be injected into the body. In either case, the solvent will dissipate and the polymer will solidify and 5 entrap or encase the drug within the solid matrix. The release of drug from these solid implants will follow the same general rules for release of a drug from a monolithic polymeric device. The release of drug can be affected by the size and shape of the implant, the loading of drug 10 within the implant, the permeability factors involving the drug and the particular polymer, and the degradation of the polymer. Depending upon the bioactive agent selected for delivery, the above parameters can be adjusted by one skilled in the art of drug delivery to give the desired 15 rate and duration of release.

The term drug or bioactive (biologically active) agent as used herein includes without limitation physiologically or pharmacologically active substances that 20 act locally or systemically in the body. Representative drugs and biologically active agents to be used with the syringeable, in-situ forming solid implant systems include, without limitation, peptide drugs, protein drugs, desensitizing agents, antigens, vaccines, anti-infectives, 25 antibiotics, antimicrobials, antiallergenics, steroidal anti-inflammatory agents, decongestants, miotics, anticholinergecs, sympathomimetics, sedatives, hypnotics, psychiQ energizers, tranquilizers, androgenic steroids, estrogens, progestational agents, humoral agents, 30 prostaglandins, analgesics, antispasmodics, antimalarials, antihistamines, cardioactive agents, non-steroidal anti-inf lammatory agents, antiparkinsonian agents, antihypertensive agents, B-adrenergic blocking agents, nutritional agents, and the benzophenanthridine alkaloids. 35 To those skilled in the art, other drugs or biologically active agents that can be released in an aqueous environment can be utilized in the described injectable 232 1 13 delivery system. Also, various forms of the drugs or biologically active agents may be used. These include without limitation forms such as uncharged molecules, molecular complexes, salts, ethers, esters, amides, etc., 5 which are biologically activated when injected into the body.

The amount of drug or biologically active agent incorporated into the injectable, in-situ, solid forming 10 implant depends upon the desired release profile, the concentration of drug required for a biological effect, and the length of time that the drug has to be released for treatment. There is no critical upper limit on the amount of drug incorporated into the polymer solution except for 15 that of an acceptable solution or dispersion viscosity for injection through a syringe needle. The lower limit of drug incorporated into the delivery system is dependent simply upon the activity of the drug and the length of time needed for treatment.

In all cases, the solid implant formed within the injectable polymer solution will slowly biodegrade within the body and allow natural tissue to grow and replace the —^ impact as it disappears. Thus, when the material is ' 25 injected into a soft-tissue defect, it will fill that defect and provide a scaffold for natural collagen tissue to grow. This collagen tissue will gradually replace the biodegradable polymer. With hard tissue such as bone, the _ biodegradable polymer will support the growth of new bone 'w 30 cells which will also gradually replace the degrading polymer. For drug-delivery systems, the solid implant formed from the injectable system will release the drug contained within its matrix at a controlled rate until the drug is depleted. With certain drugs, the polymer will 35 degrade after the drug has been completely released. With other drugs such as peptides or proteins, the drug will be completely released only after the polymer has degraded to 7. 14 232 107 a point where the non-diffusing drug has been exposed to the body fluids.

B. Thermosetting System -O 5 The injectable, in-situ forming biodegradable implants can also be produced by crosslinking appropriately functionalized biodegradable polymers. The thermosetting system comprises reactive, liquid, oligomeric polymers which cure in place to form solids, usually with the 10 addition of a curing catalyst. Although any of the biodegradable polymers previously described for the thermoplastic system can be used, the limiting criteria is that low-molecular-weight oligomers of these polymers or copolymers must be liquids and they must have functional 15 groups on the ends of the prepolymer which can be reacted with acryloyl chloride to produce acrylic ester capped prepolymers.

The preferred biodegradable system is that 20 produced from poly(DL-lactide-co-caprolactone), or "DL- PLC". Low-molecular-weight polymers or oligomers produced from these materials are flowable liquids at room temperature. Hydroxy-terminated PLC prepolymers may be synthesized via copolymerization of DL-lactide or L-lactide 25 and e-caprolactone with a multifunctional polyol initiator and a catalyst. Catalysts useful for the preparation of these prepolymers are preferably basic or neutral ester-interchange (transesterification) catalysts. Metallic esters of carboxylic acids containing up to 18 carbon atoms 30 such as formic, acetic, lauric, stearic, and benzoic are normally used as such catalysts. Stannous octoate and stannous chloride are the preferred catalysts, both for reasons of FDA compliance and performance.

If a bifunctional polyester is desired, a bifunctional chain initiator such as ethylene glycol is employed. A trifunctional initiator such as 232 1 1 trimethylolpropane produces a trifunctional polymer, etc. The amount of chain initiator used determines the resultant molecular weight of the polymer or copolymer. At high concentrations of chain initiator, the assumption is made n 5 that one bifunctional initiator molecule initiates only one polymer chain. On the other hand, when the concentration of bifunctional initiator is very low, each initiator molecule can initiate two polymer chains. In any case, the polymer chains are terminated by hydroxyl groups, as seen ***) 10 in Figure 1. In this example, the assumption has been made that only one polymer chain is initiated per bifunctional initiator molecule. This assumption allows the calculation of a theoretical molecular weight for the prepolymers.

A list of the bifunctional PLC prepolymers that were synthesized is given in Table 1. Appropriate amounts of DL-lactide, e-caprolactone, and ethylene glycol were combined in a flask under nitrogen and then heated in an oil bath at 155° C to melt and mix the monomers. The 20 copolymerizations were then catalyzed by the addition of 0.03 to 0.05 wt % SnCl2. The reaction was allowed to proceed overnight. The hydroxyl numbers of the prepolymers were determined by standard titration procedure. The Gardner-Holdt viscosities of the liquid prepolymers were 25 also determined using the procedures outlined in ASTM D 1545. The highest molecular-weight prepolymer (MW = 5000) was a solid at room temperature; therefore, its Gardner-Holdt viscosity could not be determined. s-^/ 30 The diol prepolymers were converted to acrylic- ester-capped prepolymers via a reaction with acryloyl chloride under Schotten-Baumann-1ike conditions, as seen in Figure 2 and summarized in Table 2. Other methods of converting the diol prepolymers to acrylic-ester-capped 35 prepolymers may also be employed. 232 1 a 16 Both THF and dichloromethane were evaluated as solvents in the acylation reactions. Several problems were encountered when THF was used as the solvent. The triethylamine hydrochloride formed as a by-product in the r\ 5 reaction was so finely divided that it could not be ' efficiently removed from the reaction mixture by filtration. Triethylamine hydrochloride (EtjN'HCl) has been reported to cause polymerization of acrylic species (U.S. Patent No. 4,405,798). In several instances, where 10 attempts to remove all of the Et^N'HCl failed, the acrylic-ester-capped prepolymers gelled prematurely. Thus, to effectively remove all of the EtjN'HCl, it was necessary to extract the prepolymers with water. For reactions carried out in THF, it is preferred that one first evaporate the 15 THF in vacuo, redissolve the oil in CH2C12, filter out the EtjN'HCl, and then extract the CH2C12 layer with water.

Stable emulsions were sometimes encountered during extraction. The acylations were later carried out in CH2C12 instead of THF. The filtration of EtjN'HCl from the 20 reaction mixture was found to be much easier using this solvent, and the organic fraction could be extracted directly with water after filtration.

Both diol and acrylic prepolymers were examined 25 by IR and 1H NMR spectroscopy. The salient feature of the IR spectra of diol prepolymers is a prominent 0-H stretch centered at approximately 3510 cm"1. Upon acylation, the intensity of the O-H stretch decreases markedly, and new absorbances at approximately 1640 cm"1 appear. These new 30 absorbances are attributed to the C-C stretch associated with acrylic groups. Likewise, the presences of acrylic ester groups is apparent in the 1H NMR spectra, the characteristic resonances for the vinyl protons falling in the range of 5.9 to 6.6 ppm.

The acrylic prepolymers and diol prepolymers were then cured, as summarized in Table 3. The general 232 17 l,. - procedure for the curing of the prepolymers is now described: to 5.0 g of acrylic prepolymer contained in a small beaker was added a solution of benzoyl peroxide (BP) in approximately 1 mL of CH2Cl2- In some cases, fillers or 5 additional acrylic monomers were added to the prepolymers prior to the introduction of the BP solution. The mixtures were stirred thoroughly and then poured into small petri dishes. The dishes were placed in a preheated vacuum oven for curing. Some of the samples were cured in air and not 10 in vacuo, and these samples are so indicated in Table 3.

This thermosetting system may be used wherever a biodegradable implant is desired. For example, because the prepolymer remains a liquid for a short time after addition 15 of the curing agent, the liquid prepolymer/curing agent mixture may be placed into a syringe and injected into a body. The mixture then solidifies in-situ, thereby providing an implant without an incision. Furthermore, a drug-delivery system may be provided by adding a 20 biologically active agent to the prepolymer prior to injection. Once in-situ, the system will cure to a solid; eventually, it will biodegrade, and the agent will be gradually released. **** 25 DETAILED DESCRIPTION OF EXAMPLES The following examples are set forth as representative of the present invention. These examples are not to be construed as limiting the scope of the . ^ 30 invention as these and other equivalent embodiments will be -v apparent in view of the present disclosure, figures, and accompanying claims.

EXAMPLE 1 Poly(DL-lactic acid) was prepared by the simple polycondensation of lactic acid. No catalysts were used, and the reaction times were varied to produce polymers with ' 23 2 1 0 7; 18 different theoretical molecular weights. These polymers were designated as DL-PLA oligomers. A quantity of the solid oligomer was dissolved in NMP to give a 68:32 ratio of polymer to solvent. Sanguinarine chloride(SaCl), a benzophenanthridine alkaloid with antimicrobial activity especially toward periodontal pathogens, was added to the polymer solution to give a 2% by weight dispersion of the drug in the total mixture. The dispersion of drug and polymer solution was then injected into a dialysis tribe (diameter of 11.5mm) with a sterile disposable syringe without a needle. Each end of the 6-in. length of dialysis tubing was tied with a knot to prevent loss of the drug/polymer mass, and the tube with the injected material was placed in a pH 7 Sorenson's buffer receiving fluid maintained at 37° C. Upon immersion in the receiving fluid, the drug/polymer mass coagulated into a solid mass, and the drug began to be released from the polymer as indicated by an orange-red color in the receiving fluid. The quantity of solution injected into the dialysis tube was about 250 /zL or about 100 mg of solids.

The dialysis tubing was selected to have a molecular-weight cutoff of about 3,500. With this molecular-weight cutoff, the SaCl released from the polymer could easily diffuse through the walls of the tubing, but any solid polymer would be retained. The dialysis tubing containing the drug/polymer matrix was removed frequently and placed in a bottle of fresh receiving fluid. The old receiving fluid containing the released drug was then acidified to a pH of 2.76 to convert all released drug to the iminium ion form of the drug, and the concentration of drug was determined by measuring the ultraviolet absorption (UV) at a wavelength of 237 nm. The cumulative mass of drug released and the cumulative fraction were then calculated and plotted as a function of time.

Approximately 60% of the drug was released in the first 232107 19 day, 72% after 2 days, 85% after 5 days, 90% after 9 days, and 97% after 14 days.

EXAMPLE 2 Ethoxydihydrosanguinarine(SaEt) , the ethanol ester of sanguinarine, was added to the same DL-PLA oligomer/NMP solution described in Example 1. SaEt dissolved in the polymer solution to give a homogenous solution of drug and polymer. Approximately 250 nL of the solution was added to receiving fluid and the release of drug measured as described in Example 1. The release of SaEt was slower than that for SaCl as expected because of its lower water solubility. After the first day, approximately 45% was released, 52% after 2 days, 60% after 5 days, 70% after 9 days, and 80% after 14 days.

EXAMPLE 3 Poly(DL-lactide) with an inherent viscosity of 0.08 dL/g and a theoretical molecular weight of 2,000 was prepared by the ring-opening polymerization of DL-lactide using lauryl alcohol as the initiator and stannous chloride as the catalyst. This polymer was then dissolved in NMP to give a 40% by weight polymer solution. SaCl was dispersed in the solution of this polymer in NMP to give a 1.5% by weight dispersion of the drug in the solution and the release rate determined as described in Example 1. The release rate of the drug from this higher molecular-weight polymer was slower than from the DL-PLA oligomer. After the first day, approximately 32% was released, 40% after 2 days, 45% after 5 days, and 50% after 15 days.

EXAMPLE 4 SaEt was added to the same polymer solution of DL-PLA in NMP as described in Example 3. A homogenous solution with the drug at 1.5% by weight was obtained. The release of drug from this solution determined using the same procedure described in Example 1 gave a much slower 232 1 release of SaEt than from the DL-PLA oligomer. After the first day approximately 8% was released, 14% after 2 days, 20% after 5 days, 23% after 9 days, and 28% after 14 days.

EXAMPLE 5 The effect of drug loading on the release of drug from the polymer solutions were demonstrated by adding SaCl to a 40% by weight of DL-PLA oligomer in NMP. The drug was dispersed in the polymer solution to give 2, 7 and 14% by weight dispersions. The release of drug from these formulations using the same procedure as described in Example 1 showed that the higher drug loadings gave a lower fractional rate of release as normally obtained for matrix delivery systems with diffusional release. The 2%-loaded formulation gave 65% release after 1 day, 75% after 2 days, and 88% after 5 days; the 7%-loaded formulation gave 48% release after 1 day, 52% after 2 days, and 58% after 5 days; and the 14%-loaded formulation gave 38% release after 1 day, 43% after 2 days, and 49% after 5 days.

EXAMPLE 6 Poly(DL-lactide-co-glycolide) was prepared by the ring-opening polymerization of a mixture of DL-lactide and glycolide using lauryl alcohol as the initiator and stannous chloride as the catalyst. The proportions of the two monomers were adjusted so that the final copolymer(DL-PLG) had a 50:50 ratio of the two monomers as determined by nuclear magnetic resonance spectrophotometry. The initiator was also adjusted to give a copolymer with a theoretical molecular weight of 1500 daltons. The copolymer was dissolved in NMP to give a 70% by weight polymer solution. SaCl was added to this solution to give a 2% by weight dispersion of the drug in the polymer solution. The release of drug from this formulation was determined using the same procedure described in Example 1. A much lower release rate was obtained from the copolymer than from the DL-PLA oligomer or DL-PLA 2000 molecular 21 232 1 0 weight materials. After 2 days approximately 7% of the drug was released, 10% after 5 days, 12% after 7 days, and 16% after 14 days.

EXAMPLE 7 SaEt was added to the same solution of DL-PLG in NMP as described in Example 6 to give a 2% by weight solution of the drug. The release of drug from this formulation was determined by the same procedure as io described previously. The release rate of SaEt from this formulation was identical to that for SaCl described in Example 6.

EXAMPLE 8 Tetracycline as the free base (TCB) was added to the same solution of DL-PLG in NMP as described in Example 6. The drug dissolved completely in the polymer solution to give a 2.4% by weight solution of the drug. The release of the drug from this formulation was 20 determined by a similar procedure to that described in Example 1 except the receiving fluid was not acidified to a pH of 2.76 and the concentration of TCB was determined by UV absorption at the wavelength appropriate for the drug. The release of TCB from this formulation was more linear o w 25 and at a much higher rate than that for SaCl or SaEt from the same copolymer. After 1 day approximately 44% of the drug was released, 54% after 2 days, 68% after 5 days, 73% after 6 days, 80% after 7 days, 87% after 9 days, 96% after 12 days, and 100% after 14 days. j 30 EXAMPLE 9 Tetracycline as the hydrochloride salt (TCH) was added to the same solution of DL-PLG in NMP as described in Example 6. The salt form of the drug also dissolved 35 completely in the polymer solution. The release of drug from this formulation was determined as described in Example 8 and found to be similar to that for the free base 232 107 22 except for a slightly lower rate. After 1 day approximately 32% of the drug was released, 40% after 2 days, 57% after 5 days, 64% after 6 days, 75% after 7 days, 82% after 9 days, 92% after 12 days, and 100% after 14 days.

EXAMPLE 10 DL-PLA with an inherent viscosity of 0.26 dL/g and a theoretical molecular weight of approximately 10,000 daltons was prepared by the ring-opening polymerization of DL-lactide using lauryl alcohol as the initiator and stannous chloride as the catalyst. The polymer was dissolved in NMP to give a 50% by weight polymer solution. A quantity of the polymer solution (100 /zL) was injected subdermally into rabbits, and the tissue reaction was compared to that of a USP negative plastic. The test sites were evaluated for signs of local irritation, in accordance with the Draize method, immediately after injection, at 1 and 6 hours post injection, and once daily thereafter until scheduled sacrifice at 7, 14 or 21 days. The reaction at the test sites was equivalent to that at the control USP negative plastic. The polymer solution (100 jxL) was also administered subgingivally into sites created by dental extractions in Beagle dogs. Control sites were flushed with saline solution. The dogs were examined daily for signs of mortality, pharmacotoxic effects, body weights, and local gingival irritation. The animals were sacrificed at 15 and 21 days. No distinct differences were noted between the control and test sites.

EXAMPLE 11 DL-PLA with an inherent viscosity of 0126 dL/g and a molecular weight of about 10,000 was dissolved in NMP to give a 50% by weight polymer solution. SaCl was added to the polymer solution to give a 2.4% by weight dispersion. This material was loaded into a 1-cc disposable syringe fitted with a 23-gauge blunted-end 232 107 syringe needle, and the material was inserted into the periodontal pocket of a greyhound dog. The material flowed easily out of the narrow syringe tip. The polymer precipitated or coagulated into a film or solid mass when it contacted the saliva and fluid within the pocket. The dog was observed over a time of 2 weeks during which the mass of material remained within the pocket, adhering to tissue surrounding the pocket, and slowly changing color from a light orange to a pale white. The crevicular fluid from the pocket containing the implant was sampled during this 2-week period using Periostrips which are small strips of paper that are placed at the entrance to the periodontal pocket to wick up small quantities of the crevicular fluid within the pocket. The volume of fluid collected is determined using a Periotron which measures the changes in conductance of the paper strip. The Periotron is calibrated before use with a known volume of serum. The paper strip containing the collected fluid is then extracted with a solution of 0.5% by volume of hydrochloric acid in methanol and injected into a liquid chromatograph where the quantity of drug is determined by reference to a known concentration of the same compound. The quantity of SaCl extracted from the paper strip is divided by the quantity of crevicular fluid collected to calculate the concentration of drug in the fluid. With this technique, the concentration of SaCl within the crevicular fluid from the periodontal pocket with the polymeric delivery system was determined to be almost constant during the 2 weeks of S observation. The SaCl concentration in the crevicular fluid was 63.2 /xg/mL after 3 days, 80.2 /ig/mL after 7 days, 67.8 /xg/mL after 10 days, and 70.5 jig/mL after 14 days.

EXAMPLE 12 An illustrative method for the synthesis of an acrylate terminated prepolymer is described. To an oven-dried, 500-mL, three-necked, round-bottom flask fitted with an addition funnel, gas inlet adapter, mechanical stirrer 24 23210 7 assembly, and rubber septum was added, under nitrogen, 100.0 g of difunctional hydroxy-terminated prepolymer and 200 mL of freshly distilled THF (from CaH2). The flask was cooled in an ice bath, and 24 mL of dry triethylamine (0.95 equiv/equiv OH) was added via a syringe. The addition funnel was charged with 15.4 g of acryloyl chloride (0.95 equiv/equiv OH) in 15 mL of THF, and the solution was added dropwise to the stirred reaction mixture over 1 hour. The mixture was stirred overnight and allowed to reach room temperature. The precipitated triethylamine hydrochloride was removed by filtration, and the filtrate was evaporated in vacuo, affording a pale yellow oil, which was the acrylate-terminated prepolymer. The acylations employing CHgClj as solvent were conducted in a similar manner. However, the reaction times at 0* C were shortened to 1 hour, whereupon the reaction mixtures were allowed to reach room temperature over 1 hour. EtjN^Cl was filtered out, additional CH2C12 (approximately 800 mL) was added to the filtrate, and the filtrate was extracted several times with 250 mL portions of water. The organic layer was dried over MgS04/Na2S04, filtered, and reduced to an oil in vacuo. The bottles of acrylic prepolymers were wrapped in foil and stored in a refrigerator to safeguard against premature crosslinking. o o o ) TABLE 1. SUMMARY OF DIOL PREPOLYMERS SYNTHESIZED 3 Mole ratio of monomers to initiator (ethylene glycol - 1.0) Catalyst (SnCl2), Theoretical Hydroxyl No., tneq OH (S6.1)/g Gardner Holdt viscosity, approx. Stokes Sample no. DL-lactide e-caprolactone wt X Mn, daltons Observed Theoretical (T - 22.2 *C) C964-114-1 C964-124-1 C964-128-1 C964-136-1 2.4 6.1 2.5 8.0 .0 32.8 5.0 8.0 0.03 0.05 0.03 0.03 993 5036 993 2128 100 19.7 103 113 22.3 113 48 (est.) 52.7 28.0 Solid 28.2 1375 to ui l\3 Cn| ro o o 0 0 TABLE 2. SUMMARY OF ACRYLIC ESTER TERMINATED PREPOLYMERS SYNTHESIZED Sample no.

Reaction conditions Estimated Diol concentration precursor of acrylic groups, sample no. meq/g Temp, *C Time, h Solvent Comments C964-118-1 C964-114-1 C964-125-1 C964-114-1 C964-132-1 C964-128-1 C964-137-1 C964-128-1 C964-139-1 C964-136-1 C964-144-1 C964-136-1 C964-146-1 C964-124-1 1.78 1.78 1.84 1.84 0.81 0.81 0.33 O-RT O-RT 0 0 0 0 17 THF No problems, stable. 17 THF Gelled. Overnight exposure to EtjN-HCl at RT.. 2 THF 100 ppm MEHQ added before workup. 2 Et20 Difficult workup. Low yield. 2 THF Gelled. Overnight exposure to residual Et3N'HCl in refrigerator. 1 CHjClj No problems, stable. 1 CH2C1j No problems, stable. o o o 0 TABLE 3. SUMMARY OF CURING STUDIES Sample no.

Acrylic Benzoyl prepolymer peroxide sanple no. ' ' wt % Other Curing conditions Initial additives, Shore A wt % Temp. "C Time, h hardness Comments C964-120-1 C964-118-1 2.0 none 82 16 Rubbery, breaks when bent 180°, weak.

C964-120-2 C964-118-1 1.0 none 82 16 83 Less brittle than C964-120-1.

C964-121-1 C964-118-1 2.0 none 82 16 77 Rubbery, breaks when bent 180°, weak.

C964-121-2 C964-118-1 1.0 none 82 16 80 Slightly stronger than C964-121-1.

C964-121-3 C964-118-1 0.5 none 82 16 78 Slightly more elastic than C964-121-2 C964-121-4 C964-118-1 0.1 none 82 16 69 Same as C964-121-3. (continued) O O .0 0 3 TABLE 3. SUMMARY OF CURING STUDIES (continued) Acrylic J^nzoyl other prepolymer peroxide additives Sample no. sairple no. wt % wt % Curing conditions Tenp. #C Time, h Initial Shore A hardness Comments C964-122-1 C964-118-1 1.0 TMPEBTA0 46 82 C964-122-2 C964-118-1 0.5 IMPTETA 46 82 2.5 94 2.5 91 Less rubbery than C964-120 and C964-121; brittle.

Same as C964-122-1, more flexible to 09 C964-122-3 C964-118-1 1.0 TMPIETA 175 82 C964-122-4 C964-118-1 0.5 TMPTETA 175 82 (continued) 2.5 95 2.5 93 Not rubbery at all, brittle, weak.

Similar to C964-122-3. ro CnI ro >4 O O O ) 1 TABLE 3. SUMMARY OF CURING STUDIES (continued) Acrylic Benzoyl Other Curing conditions Initial prepolymer peroxide additives Shore A Sample no. sample no. wt % wt % Temp. °c Time, h hardness Garments C964-123-1 C964-118-1 0.1 C964-123-2 C964-118-1 0.25 TMPTETA 46 TMETEIA 46 C964-123-3 C964-118-1 0.1 C964-134-1 C964-132-1 0.05 (AIBN)C C964-134-2 C964-132-1 0.10 (AIBN) none 82 82 1MPTBEA 175 82 60° none 60 (continued) 2.5 2.5 2.5 17 17 89 83 92 Liquid Liquid Rubbery, stronger than C964-120 and C964-121, not flexible.

About the same as C964-123-1, may be more brittle.

Not rubbery; strong, brittle.

No cure. No cure. to to rv> C*4 ro ♦ - : * t i i) o o :> TABDE 3. SUMMARY OF CURING STODIES (continued) Acrylic Benzoyl Other Curlm conditions Initial prepolymer peroxide additives Shore A Sample no. sanple no. wt % wt % Temp. °C Time, h hardness Ooranents C964-134-3 C964-132-1 0.24 (AIBN) none 60d 17 Liquid No cure.

C964-134-4 C964-132-1 0.50 (AIBN) none 60d 17 Liquid No cure.

C964-134-5 C964-132-1 1.00 (AIBN) none 60d 17 Liquid Slightly thickened C964—135-1 C964-132-1 0.05 none 80d 17 Liquid No cure.

C964-135-2 C964-132-1 0.10 none "°o 00 17 Liquid No cure.

C964-135-3 C964-132-1 0.25 none 80d 17 Liquid No cure.

C964-135-4 C964-132-1 0.50 none 00 17 Liquid No cure.

C964-135-5 C964-132-1 1.00 none 80d 17 Liquid Slightly thickened C964-135-6 C964-128-1® 0.05 none CO 17 Liquid No cure.

C964-135-7 C964-128-1® 0.10 none CO 17 Liquid No cure.

C964-135-8 C964-128-1® 0.25 none 80d 17 Liquid No cure. o (continued) ro CM ro o o o O 0 TABIE 3. SUMMARY OF CURING STODIES (continued) Acrylic Benzoyl Other Curing nravti felons Initial prepolymer peroxide additives Shore A Sample no. sample no. wt % wt % Temp. *C Time, h hardness Garments C964-135-9 C964-135-10 C964-135-11 C964-135-12 C964-135-13 C964-135-14 C964—135-15 C964-141-1 C964-141-2 C964-141-3 C964-128-1® C964-128-1® C964-124-1® C964-124-1® C964-124-1® C964-124-1® C964-124-1® C964-137-1 C964-137-1 C964-137-1 0.50 1.00 0.05 0.10 0.25 0.50 1.00 0.10 0.25 0.50 none none none none none none none none none 80° 80 80 80° 80° 80 80 80 80 17 17 17 17 17 17 17 1 none 80 (continued) Liquid Liquid ND ND ND ND ND 66 71 72 No cure.

No cure.

No cure.

No cure.

No cure.

No cure.

No cure.

Flexible elastomer.

Flexible elastomer.

Flexible elastomer. o o o 0 TABLE 3. SUMMARY OF CURING STUDIES (continued) Sairple no.

Acrylic prepolymer sample no.

Benzoyl peroxide wt % Other additives wt % Curim conditions Temp. 'C Time, h Initial Shore A hardness Garments C964-141-4 C964-137-1 1.00 none 80 l 72 Flexible elastaner.

C964-141-5 C964-128-1 0.10 none 80 1 Liquid No cure.

C964-141-6 C964-128-1 0.25 none 80 1 Liquid No cure.

C964-141-7 C964-128-1 0.50 none 80 1 Liquid No cure.

C964-141-8 C964-128-1 1.00 none 80 1 Liquid No cure.

C964—143-1 C964—137—1 0.25 Cab-o-sil PTG, 5.0 80 1 74 No cure.

C964-143-2 C964-137-1 0.25 Cab-o-Sil PTG, 2.0 80 1 73 No cure.

C964-143-3 C964-137-1 0.25 L-P1A (IV=0.8), 5.0 80 1 75 No cure.

C964-143-4 C964-137-1 0.25 L-P1A (I\H).8), 2.5 80 1 78 No cure. w to ro CM ro (continued) o o ; TABLE 3. SUMMARY OF CURING STUDIES (continued) Acrylic Benzoyl Other prepolymer peroxide additives Sample no. sample no. wt % wt % Curlm conditions Teirp. °c Time, h Initial Shore A hardness Ocmoents C964-148-1 C964-144-1 0.5 none 80 17 Liquid No cure.

C964-148-2 C964-144-1 0.10 none 80 17 Liquid No cure.

C964-148-3 C964-144-1 0.25 none 80 2 66 C964-148-4 (continued) and C964-148-6 were about the same in toughness, and both were better than C964-148-3 and C964-148-5. w U) IV> CM ro o C.) (.') TABLE 3. SUMMARY OF CURING STUDIES (continued) Acrylic Benzoyl Other Curing conditions Initial prepolymer peroxide additives Shore A Sample no. sample no. wt % wt % Temp. °C Time, h hardness Garments C964-148-4 C964-144-1 0.50 none 80 68 C964-148-4 and C964-148-6 were about the same in toughness, and both were better than C964-148-3 and C964-148-5. (continued) (; O O 0 TABIE 3. SUM1ARY OP CURING STODIES (continued) Acrylic Benzoyl Other Curing conditions Initial prepolymer peroxide additives Shore A Sairple no. sarqple no. wt % wt % Tamp. °C Time, h hardness Ocnroerrts C964-148-5 C964-144-1 1.00 none 80 2 67 C964-148-4 and C964-148-6 were about the same in toughness, and both were better than C964-148-3 and C964-148-5. (continued) (.) O O -) TABIE 3. SUMMARY OF CURING STODIES (continued) Acrylic fifsnzoyl Other Curing conditions Initial prepolymer peroxide additives Shore A Sample no. sample no. wt % wt % Temp. °C Time, h hardness Garments C964-148-6 C964-144-1 2.00 none 80 69 C964-149-1 C964-144-1 C964-149-2 C964-144-1 C964-149-3 C964-144-1 0.15 0.20 0.25 none none none 80 80 80 (continued) 2 2 2 64 64 66 C964-148-4 and C964-148-6 were about the same in toughness, and both were better than C964-148-3 and C964-148-5. w a rv) Og ro TABLE 3. SUMMARY OF CURING STUDIES (continued) Acrylic Betffeoyl Other curing oorditlons Initial prepolymer peroxide additives Shore A Sample no. sample no. wt % wt % Tenp. *c Time, h hardness Ccranents C964-149-4 C964-144-1 0.15 Cab-0-Sil N70-TS 5.0 80 ND C964-149-5 C964-144-1 0.20 Cab-O-Sil N70-TS 5.0 80 ND C964-149-6 C964-144-1 0.25 Cab-O-Sil N70-TS 5.0 80 ND C964-150-1 C964-146-1 0.05 none 80 (continued) 17 ND Sanples too porous, did not have any flat area for hardness measurement.

Samples too porous, did not have any flat area for hardness measurement.

Sanples too porous, did not have any flat area for hardness measurement.

Only partially cured.

(J O O ) 3 TABLE 3. SUMMARY OF CUKENG STODIES (continued) Acrylic prepolymer Sample no. sanple no.

Benzoyl Other peroxide additives wt % wt % Carina oondltiona Tenp. "C Time, h Initial Shore A hardness Ccmments C964-150-2 C964-146-1 0.10 none C964-150-3 C964—146-1 0.25 none C964-150-4 C964-146-1 0.50 none C964-150-5 C964-146-1 1.00 none 80 80 80 80 72 57 56 50 Elastic, flexible, moderately strong.

Elastic, flexible, moderately strong.

Elastic, flexible, moderately strong.

Elastic, flexible, moderately strong.

U> 00 ro CM K> (continued) ■J o o O 0 ) TABUE 3. SUMMARY OF CURING STUDIES (continued) Acrylic Benzoyl Other prepolymer ]i&roxide additives Sanple no. sample no. wt % wt % Curing conditions Temp. 'C Time, h Initial Shore A hardness Comments C964-150-6 C964-146-1 2.00 none 80 51 Elastic, flexible, moderately strong.

^Result not determined. w TMPTBTA = trinvethylolpropane triethoxy triacrylate. ^ ^AIBN = azobisisobutyronitrile.

Cured in air at atmospheric pressure. eDiol prepolymer used.

C:\vpf \H^tebles.enK> ro CM ro *4 - rs 232107 40

Claims (57)

WHAT WE CLAIM IS: Tr:jiT re ouirir-p =e

1. A method of forming an iaplant in-situ, in a non-human body, comprising the steps of: a) dissolving a non-reactive polymer in a biocompatible solvent to form a liquid; b) placing said liquid within said body; and c) allowing said solvent to dissipate to produce a solid implant.

2. The method of Claim 1, wherein said polymer is selected from the group consisting of polylactides, polyglycolides, polycaprolactones, polydicxanones, polycarbonates, polyhydroxybutvrates, 15 polyalkylene oxalates, polyanhydrides, polyamides, polyester amides, polyurethanes, polyacetates, polyketals, polyorthocarbonates, polyphosphazenes, polyhydroxyvalerates, polyalkylene succinates, poly (sialic acid), poly (amino acids), polyvinylpyrrolidone, 20 polyethylene glycol, polyhydroxycellulose, chitin, chitosan, and polyorthoesters, and copolymers, terpolyaers and combinations and mixtures thereof.

3. The method of Claim 1, wherein said polymer is 25 selected from the group consisting of polylactides, polycaprolactones and copolymers thereof with glycolide.

4. The method of Claim 1, wherein said solvent is 3 0 selected from the group consisting of JJ-methyl- 2-pyrrolidone, 2-pyrrolidone, ethanol, propylene glycol, acetone, ethyl acetate, methyl acetate, methyl ethyl ketone, dimethylformamide, dimethyl sulfoxide, tetrahydrofuran, caprolactam, decylmethylsulfoxide, oleic 35 acid and l-dodecylazacycloheptan-2-cne.-^nd--eoB&iinA£jL9|isand mixtures thereof. 41 232107

5. The aethod of Claim 1, wherein said solvent is selected from the group consisting of 27-aethyl-2-pyrrolidone, 2-pyrrol idone, diaethyl sulfoxide and acetone, and a coabination or mixture thereof.

6. The aethod of Claim 1, wherein said polymer is biodegradable.

7. The aethod of Claim 6 , and further comprising the step of adding an effective amount of biologically active agent to said liquid to provide an implant which releases said agent by diffusion and/or by erosion as said implant bi odegrades.

8. The aethod of Claim 1, and further comprising delivering said liquid in-situ through a needle.

9. The aethod of Claim 1, wherein said solvent is coaprised of a binary solvent mixture having a first solvent capable of dissolving said polyaer and a second solvent incapable of dissolving said polymer, said first and second solvents being present in said mixture at a ratio such that said polyaer is soluble therein, so that said polyaer is precipitated from said liquid upon the placing of said liquid within said animal, thereby resulting in an increase in said ratio of said second solvent to said first solvent.

10. The method of Claim 9, wherein said polymer is a lactide polyaer and said second solvent is selected^jEt^ia the group consisting of water, etharsol 'and L. r. N propylene glycol. ;z 232107 42

11. A aethod of forming an implant in-situ in a non-human body, cxsmprising the steps of: a) placing a liquid, biocompatible polymer within said body; and b) curing said polyaer in-situ to form said implant.

12. . The method of Claim 11, and wherein said liquid polymer is an acrylic-ester-terminated prepolymer and a curing agent is added to said prepolymer prior to placement of said prepolymer and allowing said prepolymer to cure in-situ.

13. The method of Claim 12, and further comprising the step of synthesizing said prepolymer via copolymerization of DL-lactide with c-caprolactone.

14. The method of Claim 12, and further comprising the step of synthesizing said prepolymer via copo^merization of L-lactide with e-caprolactone.

15. A method of forming a solid implant in-situ within a non-human body, comprising the steps of: a) mixing together effective amounts of liquid acrylic-ester-terminated, biodegradable prepolymer and a curing agent to form a mixture in a liquid form? and 43 23210 7 b) delivering said mixture within said body while said mixture is in a liquid form so as to allow said prepolymer to cure to form said solid implant.

16. The method of Claim 15, and further comprising the step of forming said liquid acrylic-ester-terminated prepolymer by converting a polyol-terminated prepolymer.

17. The method of Claim 16, and further comprising the step of forming said polyol-terminated prepolymer by copolymerization of DL-lactide and e-caprolactone with a polyol initiator.

18. The method of Claim 17, and further comprising the step of adding a catalyst to said copolymerization step.

19. The method of Claim 18, wherein said catalyst is stannous octoate.

20. ? The method of Claim 18, wherein said catalyst is stannous chloride.

21. The method of Claim 16, and further comprising the step of forming said polyol-terminated prepolymer by copolymerization of L-lactide and e-caprolactone with a polyol initiator. '■N 44 232 107

22. The method of Claim 21, and further comprising the step of adding a catalyst to said copolymerization step. 5

23. The method of Claim 22, wherein said catalyst is stannous octoate.

24. The method of Claim 22, wherein said catalyst is stannous chloride. 10

25. The method of Claim 15, wherein said curing agent is azobisisobutyronitrile.

26. The method of Claim 15, wherein said curing agent 15 is benzoyl peroxide.

27. The method of Claim 15, and further comprising the step of adding a biologically active agent to said prepolymer and curing agent mixture to provide, upon 20 curing, a biodegradable implant which releases said biologically active agent by diffusion or erosion as said implant biodegrades. 25

28. The method of Claim 15, wherein said delivering step comprises injecting said mixture into said body by means of a syringe and needle. 232107 45

29. A biodegradable iaplant for a body produced according to the aethod of Claim 1.

30. A biodegradable iaplant for a body produced according to the aethod of Claia 12.

32. A biodegradable iaplant for a body produced according to the aethod of Claia 25.

32. A coapcsition for foraing a biodegradable iaplant in-situ within a body, comprising an effective aaount of a non-reactive biocoapatible polyaer dissolved within a biocoapatible solvent vhich is capable of dissipating upon placeaent within a body to fora said iaplant.

33. The coapcsition of Claia 32, wherein said polyaer is selected froa the group consisting of polylactides, polyglycolides, polycaprolactones, polydioxanones, polycarbonates, polyhydroxybutyrates, polyalkylene oxalates, polyanhydrides, polyanides, polyesteraaides, polyurethanes, polyacetates, polyJcetals, polyorthocarbonates, polyphosphazenes, polyhydroxyvalerates, polyalJcylene succinates, poly(aalic acid), poly(aaino acids), polyvinylpyrrolidone, polyethylene glycol, polyhydroxycellulose, chitin, chitosan, polyorthoesters, and copolymers, terpolyaers and 232107 46

34. The composition of Claim 32, wherein said polymer is selected from the group consisting ■ of polylactides, polycaprolactones and copolymers thereof with glycolide.

35. The composition of Claim 32, wherein said solvent is selected from the group consisting of N-roethyl-2-pyrrolidone, ethanol, propylene glycol, 2- pyrrolidone, acetone, methyl acetate, ethyl acetate, methyl ethyl ketone,, dimethylformamide, dimethyl sulfoxide, tetrahydrofuran, caprolactam, decylmethylsulfoxide, oleic acid and 1-dodecyla zacycloheptan-2-one and combinations and mixtures thereof.

36. The composition of claim 32, wherein said solvent is selected from the group consisting of N- roethyl-2-pyrrolidone, 2-pyrrolidone, dimethyl sulfoxide and acetone, and a combination or mixture thereof.

37. The composition of Claim 32, and further comprising an effective amount of a biologically active agent.

38. A composition for forming a polymer which is curable in-situ within a body to produce a biodegradable implant, comprising a liquid acrylic-ester-terminated prepolymer capable of being cured into said implant upon addition of an effective amount of a curing agent. 232 1 0 47

39. The composition of Claim 38, wherein said liquid acrylic ester terminated prepolymer is a product of a conversion of a polyol-terminated prepolymer.

40. The composition of Claim 39, wherein said polyol-terminated prepolymer is a product of co-polymerization of DL-lactide and e-caprolactone with a polyol initiator.

41. The composition of Claim 39, wherein said polyol-terminated prepolymer is a product of co-polymerization of L-lactide and €-caprolactone with a polyol initiator.

42. The composition of Claim 38, wherein said curing agent is azobisisbutyronitrile.

43. The composition of Claim 38, wherein said curing agent is benzoyl peroxide.

44. The composition of Claim 38, and further comprising an effective amount of a biologically active agent.

45. A composition for forming a biodegradable implant in-situ within an animal, comprising a biocompatible solvent and an effective amount of a biocompatible polymer dissolved within said solvent, said solvent comprising a first solvent which dissolves said polymer and a second «&*■;232107;48;solvent which does not dissolve said polymer, said first and second solvents being present in a ratio such that said polymer is soluble therein but is precipitated therefrom upon an increase in the amount of said second solvent which is present within said animal.;

46. A method of forming an implant in-situ, as claimed in claim 1, substantially as herein described with reference to any one of the Examples.;

47. A biodegradeable implant formed according to the method of any one of claims 1 to 28 inclusive, substantially as herein described with reference to any of the Examples.;

48. A composition for forming a biodegradable implant, as claimed in claim 32, substantially has herein described with reference to any one of the Examples.;

49. The method of Claim 7, wherein said implant is formed in a periodontal pocket in said body.;—'

50. The method of Claim 49, wherein said biologically-active agent is selected from the group consisting of benzophenanthridine alkaloid and tetracycline.;

51. The method of Claim 7, wherein said biologically-active O' agent comprises a benzophenanthridine alkaloid.;

52. The method of Claim 51, wherein said alkaloid comprises sanguinarine chloride.;

53. The method of Claim 51, wherein said alkaloid comprises ethoxydihydrosanguinarine.;NX PATEWT OFFICE;-if 17 APR1991;l;232107;49;

54. The method of Claim 7, wherein said biologically-active agent comprises tetracycline base.;

55. The method of Claim 7, wherein said biologically-active agent comprises tetracycline hydrochloride.;

56. A biodegradable drug delivery implant for a body produced according to the method of Claim 7.;

57. The composition of Claim 32, wherein said solvent comprises a first liquid which dissolves said polymer and a second liquid which does not dissolve said polymer, said first and second liquids being present in a ratio such that said polymer is soluble therein but is precipitated therefrom upon an increase in the amount of said second liquid which is present within said body.;by their attorneys Baldwin, Son & Carey;";NZ. PATENT OFFICE;17 APR 1991*