Indian Patents. 240098:A CONJUGATE OF BIOCOMPATIBLE POLYMER-BIOLOGICALLY ACTIVE MATERIAL, METHOD OF PREPARATION OF THE CONJUGATE AND PHARMACEUTICAL COMPOSITION COMPRISING THE CONJUGATE

Title of Invention	A CONJUGATE OF BIOCOMPATIBLE POLYMER-BIOLOGICALLY ACTIVE MATERIAL, METHOD OF PREPARATION OF THE CONJUGATE AND PHARMACEUTICAL COMPOSITION COMPRISING THE CONJUGATE
Abstract	The present invention relates to conjugates of biocompatible polymers and biologically active molecules wherein the activated biocompatible polymer is conjugated to a carboxyl group of biologically active material at a molar ratio of 1:1 and methods of preparation thereof and a pharmaceutical composition comprising the same. Figure 1 is the representative figure.

Full Text	FIELD OF THE INVENTION The present invention relates to a conjugate of biocompatible polymer-biologically active material, method of preparation of the conjugate and pharmaceutical composition comprising the conjugate. Background of the Invention Use of proteins and peptides as medicinal products generally has been limited by several problems. For example, peptides or proteins are very low in in vivo absorption efficiency because they are easily hydrolyzed or degraded by proteases within a short period of time after being taken into the body, and also induce immune response with repeated administration. Therefore, most protein and peptide drugs have been required to be administered by injection at least once a day or more. This firequent administration by injection, however, causes pain and risk to patients. Also, frequent injections over long periods is costly and inconvenient to the patients. Attempts to develop more stable drugs are required to solve the above problems, and the technology to modify biologically active materials such as proteins or polypeptides with biocompatible polymers has been developed. Conjugates of proteins or pharmaceutically active molecules to biocomatible polymers can afford great advantages when they are applied in vivo and in vitro. When being covalently bonded to biocompatible polymers, biologically active materials can exhibit modified surface properties and solubility, and thus can be increased in solubility within water or organic solvents. Further, the presence of biocompatible polymers can make the proteins and/or polypeptides conjugated to them more stable in vivo, increase biocompatibility of the proteins and reduce immime response, and reduce the clearance rate of the proteins by the intestine, the kidney, the spleen, or the liver. Although the conjugation of the biologically active materials such as a protein or peptide of interest with biocompatible polymers such as PEG has many advantages, some problems remain in conjugating by known methods. The most common conjugation method is achieved by bonding activated PEG to the amino group of amino acid residues such as lysine. When the active site on a protein's surface is conjugated to PEG, the biological activity of protein-polymer conjugates is substantially decreased because one or more jfree lysine residues of rnany proteins are frequently adjacent to the active sites of proteins generally. Also, the reaction between lysine residues of proteins and activated PEG occurs easily and PEG-protein conjugates wherein two or more PEG molecules arc conjugated to one protein molecule are obtained. For example. when more than two PEG molecules bind to the surface of cytokines such as interferon, CSF, and interleukin or polypeptides such as EGF, hGH, and insulin, the biological activity of conjugate is rapidly reduced resulting in loss of function. .Also, these reactions occur randomly and result in a mixture of many kinds of PEG-protcin conjugates, which make the purification of desired conjugates complicated and difficult. If too many polymer molecules are attached to targeting proteins or peptides, the conjugates lose all or much of their biological activity. Also, if an expressively reactive linker has been used or msufficicnt numbers of polymers are attached to targeting protein molecules, the therapeutic efficacy of those conjugates can be decreased. To overcome these problems, many attempts have been made to conjugate biocompatible polymers to amino acid residues of proteins substituted by genetic engineering to conjugate polymers to a specific site of proteins. However, this method generally alters the original properties of proteins. Also the safety of these genetically engineered molecules as therapeutic drugs needs to be proved. Attempts have been made to solve the problems by chemically modifying specific sites of biologically active materials with biocompatible polymers. US patent No. 5,951,974 and 5,985,263 describes conjugation of PEG molecules to the histidine residue of interferon to increase the efficacy of drugs by lengthening half-life in vivo and the like. However, this method still used the reactive amino group and produced isomers of PEG-IFN randomly attached at several histidine sites, and requires an additional purification step using an ion-exchange column to separate the desired 1:1 complex of highly active PEG-IFN conjugate. Further, the imidazolyl group of histidine to which PEG is attached is easily hydrolyzed compared to other amino groups of amino acids, and interferon is easily released from the PEG-intcrfcron conjugate. US Patent No. 5,766,897 describes conjugation of macromolecules and mutant forms thereof at their cysteine residues to activated PEG molecules. Because of disulfide bond most protein moieculcs have either one fi«e or no spare cysteine. Thus, an amino acid which is not related to the active site can be changed to a cysteine residue by mutagenesis to conjugate the new cysteine residue with polymers. This method, however, tends to produce conjugates with significantly decreased activity compared to conjugates at amino or carboxyl groups of proteins, although it has an advantage of attaching the polymer to a specific site of biologically active molecules. US Patent No 5,985,265 describes site-specific coiyugates at N-terminal residues of 0-CSF and IFN with PEG molecules. However, reactivity of these activated polymers is low, and the reaction needs a longer reaction time. In addition, the yield of the reaction is low and stability of proteins is poor. In case that the active site of protein molecules is especially near the N-terminus, conjugation at the N-termiital amino group results in the significant decrease or loss of biological activity. US Patent No 5,824,778 describes conjugates of G-CSF at amino and carboxyl groups by PEG Excess EDAC was added to activate the carboxyl groups of the protein and many PEG molecules were attached to activated carboxyl groups of several residues. The obtained PEG-G-CSF conjugate has been determined to be a heterogeneous mixture having various numbers of PEG molecules attached, and biological activity of the conjugate was significantly reduced. Therefore, if the biological activity of biologically active molecules can be maintained after conjugation with the polymer at a desired ratio, and a homogenous species of site-specific conjugates can be obtained, cliniaical usefulness of such molecules will increase remarkably. Summary of Invention Inventors of present invention prepared PEG-biologically active molecule conjugates at a ratio of 1:1, wherein PEG is attached to a carboxyl group of biologically active molecules. Carboxyl groups of biologically active molecules have lower reactivity than amino groups. It was observed that these conjugates show therapeutic efficacy up to 20-fold higher than native(non-conjugated) proteins because they have an extended half-life and higher stability compared to native proteins. Also they observed that the 1:1 complex showed superior characteristics to conjugates of higher than 1:1 molar ratio at carboxyl groups or conjugates at amino groups. Therefore, the present invention provides conjugates of biologically active molecules with biocompatible polymers wherein biocompatible polymers are specifically attached to a carboxyl group of biologically active molecules at a ratio of 1:1, methods of preparation thereof and a pharmaceutical composition comprising the same. The conjugates of the present invention retain biological activity of native biologically active molecules and have increased stability, bioavailability, and half-life. Brief Description of the Drawings Fig. 1 shows the degree of conjugation for mPEG(,5K)-Hz-G-CSF by HPLC and SDS-PAGE. Fig. 2 shows the degree of conjugation for mPEG(20K)-Hz-G-CSF by HPLC and SDS-PAGE. Fig. 3 shows raPEG(5K)-Hz-IFN with the molar ratio of 1:1 on SDS-PAGE. Fig. 4 shows the prod\ictivity of mPEG(20K)-Hz-IFN conjugate according to the amount of EDAC added on SDS-PAGE. Fig. 5 shows the degree of reactivity for mPEG(20K)-Hz-lFN conjugate according to the addition method of EDAC and the amount of EDAC on SDS-PAGE. Fig. 6 shows SDS-PAGE of mPEG(20K)-Hz;-IFN conjugate purified by an ion-exchange columm. Fig. 7 shows the comparison of the biological activity of mPEG(20K)-Hz-G-CSF conjugate, native G-CSF ,and Neulasta™ (PEG-G-CSF, developed by Amgen, FDA aproved in 2002) by cell based assay. Fig. 8 shows the plasma half-Ufe of mPEG(20K)-H2-G-CSF, native G-CSF, and Neulasta™(PEG-G-CSF, developed by Amgen, FDA approved in 2002).Fig. 9 shows WBC of mPEG(20K)-Hz-G-CSF conjugates, native G-CSF, and Neulasta™(PEG-G-CSF, Developed by Amgen, FDA approved in 2002). Fig. 10 shows biological activity of mPEG(12K)-Hz-IFN conjugate, native IFN, and PEG-IFN(developed by Schering-Plough) by CPE assay. Fig. 11 shows the comparison of biological activity of mPEG(20K)-Hz- IFN conjugate with native IFN by CPE assay. Fig. 12 shows the comparison of biological activity between Di-mPEG-Hz-IFN, two PEG molecules attached to one IFN molecule and mono-mPEG-Hz-IFN, one PEG molecule attached to one DFN molecule, by CPE assay. Fig. 13 shows the comparison of half-life in plasma of PEG(20K)-Hz-IFN conjugate, native IFN, and PEG-IFN(developed by Schering-Plough). Fig. 14 shows the comparison of stability between PEG-IFN conjugated at a carboxyl groiq) and at an amino group. Fig. 15 shows the HPLC chromatogram for native PTH, which has not been modified by biocompatible polymers. Fig. 16 shows the HPLC chromatogram for a reaction mixture(unreacted PTH, mPEG(20K)-Hz-PTH, mPEG(20K)-Hz) of PTH with mPEG(20k)-Hz before purification (peak 1: unreacted PTH with PEG polymer, peak 2: mPEG(20k)-Hz-PTH) Fig. 17 shows HPLC chromatogram of the purified mPEG(20kO)-H2-PTH after corrugating PTH with mPEG(20K)-Hz. Fig. 18 shows SDS-PAGE, stained with Coomassie blue for the reaction product between PTH and mPEG(20k)-Hz (lane 1: MW marker, lane 2: PTH, lane 3: PTH, PTH-mPEG(20k)-Hz conjugate before purification, lane 4: PTH-mPBG(20k)-H2 conjugate after purification. Fig. 19 shows the in vivo biological activity for PTH and PEG-PTH conjugate. Fig. 20 shows the half-life of PTH and PEG-PTH conjugates in rats. Detailed Description of the Invention In an aspect, the present invention relates to the conjugates of biocompatible polymer-biologically active material, wherein the activated biocompatible polymer is conjugated to a carboxyl group of biologically active material at a molar ratio of 1:1. In another aspect, the present invention relates to a pharmaceutical composition comprising a therapeutically effective amotmt of the above biocompatible polymer-biologically active molecule conjugates and pharmaceutically acceptable carriers. In a further aspect, the present invention relates to a method of preparation of conjugates of biocompatible polymer-biologically active material at a molar ratio of 1:1, wherein the biocompatible polymer is conjugated at a carboxyl group of biologically active material, comprising the step of conjugating the biologically active material to the activated the biocompatible polymer with the stepwise addition of coupling reagent under tiie condition wherein the molar ratio of biologically active material to activated the biocompatible polymer is 1:1 to 1:20, the ratio of biologically active material to the coupling reagent is 1:1 to 1:50, and pH is in the range of 2 to 5. In the above method, EDAC, as an example of the coupling reagent, was added stepwise more than 5 times, preferably 5 or 6 times, because EDAC is readily hydrolyzed in aqueous solution. The method described above provides the conjugates wherein biocompatible polymers are attached to a carboxyl group of biologically active molecules at a ratio of 1:1. In other words, the present invention provides site specific conjugation by binding activated polymers to a carboxyl group of biologically active materials at a molar ratio of 1:1. These conjugates retain the biological activity of biologically active materials by preventing the attachment of polymers to active sites. The present invention also provides the conjugates with a molar ratio of 1:1 by avoiding the random reaction with many reactive residues at active sites to produce various kinds of heterogeneous mixtures. Further, the conjugates of the present invention have several advantages such as increased stability in vivo, increase of bioavailibility, and extended half-life caused by biocompatible polymers. Therefore, production of homogeneous biocompatible polymers-biologjcally active material conjugates of the present invention provides the cost and time effective process, as compared to other processes of the prior art W092/16555 describes the reaction of ovalbumin at the carboxyl or carbohydrate group with PEO-hydrazide containing amino acid spacer. However, it only describes the coiyugates with a number of PEG molecules attached without mentioning a method of preparation for conjugates of biologically active materials with biocompatible polymers with the ratio of 1:1, and the biological activity of conjugates. Also, US patem No 5,824,779 describes linkage of PEG to the carboxyl group of G-CSF but the conjugate prepared according to their method had very low activity because several PEG molecules were randomly attached to aspartic acids or glutamic acids of G-CSF. There have been problems to control the reaction condition for specific linkage or the number of attaching polymers using the difference in reactivity according to pKa of amino acids. When an attempt was made to react the amino group of lysine in the range of pH 7 to 8, the histidioe groups also reacted randomly. And, when pH was lowered to about 6 to 6.5, histidine groups became more reactive with PEG than lysine groups(US Patent No. 5,951,974 and US Patent No. 5,985,263). Inventors of the present invention observed that PEG can be attached to carboxyl groups, especially C-terminus of biologically active materials at a ratio of 1:1 at pH equal to or lower than 3 according to the above method. Therefore in one aspect, the present invention relates to the conjugate of biocompatible polymer-biologically active material, wherein the biocompatible polymer is conjugated to the C-terminus of the biologically active material at a molarratio of 1:1. In another aspect, the present invention relates to a pharmaceutical composition comprising a pharmaceutically acceptable amoimt of the conjugate, wherein the biocompatible polymer is conjugated to the C-tenninus of the biologically active material at a molar ratio of 1:1 and pharmaceutically acceptable carriers. In another further aspect, the present invention relates to a method of preparation of conjugate of biocompatible polymer-biologically active material at the C-terminus of the biologically active material with a molar ratio of 1:1, comprising the step of conjugating the biologically active material to the activated the biocompatible polymer with the stepwise addition of coupling reagent under the condition wherein the molar ratio of biologically active material to activated the biocompatible polymer is 1:1 to 1:20, the ratio of biologically active material to the coupling reagent is 1:1 to 1:50, and pH is in the range of 2 to 5. Biocompatible Polymers The term "conjugating material" used for conjugation of biologically active molecules means any biocompatible polymer which can be linked to biologically active molecules such as natural or synthetic polymers. The term "biocompatibility" means biocompatible with living tissues or systems, and being nontoxic, noninflammatory, and noncarcinogenic without causing harm, inflammation, immune response and carcinogenesis in the body. Biocompatible polymers are conjugated with biologically active materials. The useful polymers of the present invention are readily soluble in various solvents and have molecular weight of between about 300 and about 100,000 Da and preferably between about 2,000 and about 40,000 Da. The biocompatible polymers include, but are not limited to, polyethylene glycol (PEG), polypropylene glycol (PPG), polyoxyethylene (POE), polytrimethylene glycol, polylaetic acid and its derivatives, polyacrylic acid and its derivatives, polyamino acid, polyvinylalcohol, poiyurethane, polyphosphazene, poly(L-lysinc), polyalkylene oxide (PAO), polysaccharide, dextran, polyvinyl pyrrolidone, polyacrylamide, copolymers thereof and other noninmnmogenic polymers. Biocompatible polymers of the present invention are intended to include not only linear polymers but also polymers as follows. Biocompatible polymers of the present invention include soluble, non-antigenic polymers linked to an activated functional group that is capable of being nucleophilically substituted through an aliphatic linker residue (US patent No. 5,643,575 and 5,919,455). Also, biocompatible polymers of the present invention include multi-armed, mono-functional and hydrolytically stable polymers, having two linker fragments which have polymer arms around a central carbon atom, a residue which is capable of being activated for attachment to biologically active materials such as proteins, and side chains which can be hydrogen or methyl group, or other linker fragment(US Patent No. 5,932,462). In addition, biocompatible polymers of the present invention include polymers of branched PEG in which the functional groups of polymers are attached to biologically active materials via linker arms having reporter residues(WO 00/33881). Among them, PEG is one of the most common biocompatible polymers of the present invention. In general, PEG is a nontoxic hydrophilic polymer having the repeating unit, HO-(CH2CH2O)n-H. Various proteins are reported to show-extended half-lives, increased solubility, increased stability, and reduced immunogenicity in plasma when being conjugated with PEG The range of molecular weight of PEG molecules conjugated to biologically active materials such as proteins or peptides is from about 1,000 to 100,000 Da and the toxicity of PEG over 1,000 Da is known to be very low. PEGs in the range of from 1,000 to 6.000 Da are distributed to the whole body and cleared in the kidney. Branched PEG with molecular weight of 40,000 Da are distributed in blood or organs including the over, and metabolized in the liver. PEG is the most preferable biocompatible polymer because PEG is commercially available in the various molecular weight ranges, each oxyethylene unit is hydrophilic to be accessible to bind 2-3 water molecules, PEG derivatives with one-terminal functional group from methoxy polyethylene glycol are easy to synthesize, PEG has very low risk of antigen-antibody reaction, and the related technology is well developed. Biologicallv active materials The term "biologically active molecule" means all nucleophiles conjugated with activated biocompatible polymers, and which retain at least some of their biological activity after conjugation. The term "biologically activity" used herein is not limited by physiological or pharmacological activity. For example, some conjugates of aucleopfailic containing enzymes can catalyze reactions in organic solvents. Similarly, some polymer coigugates including proteins such as Con-canavalin A, or immunoglobulin can also be used in diagnostics in the laboratory. In general, biologically active molecules can be isolated firom nature or synthesized recombinantly or chemically, and include proteins, peptides, polypeptides, enzymes, biomedicincs, genes, plasmids, or organic residues. Proteins, peptides, and polypeptides of interest include, but are not limited to, hemoglobin, serum proteins(for example, blood factors including Factor VII, VIII, and IX), immunoglobulins, cytokines(for example, interleukins), a-, P- and 7-interferons, colony stimulating factors including G-CSF and GM-CSF, platelet derived growth factor(PDGF), phospholipase-activating protein(PLAP), and parathyroid hormone(PTH). Other proteins of general biological or therapeutic interest include insulin, plant proteins (for example, lectins and ricins), tumor necrosis factors(TNF) and related alleles, growth factors(for example, tissue growth factors such as TOFa and TGFP and epidermal growth factors), hormones (for example, follicle-stimulating hormone, thyroid-stimulating hormone, antidiuretic hormones, pigmentary hormones, luteal hormone-releasing hormone and derivatives thereof), calcitonin, calcitonin gene related peptide(CGRP), synthetic enkephalin, somatomedins, erythropoietin, hypothalamic releasing factors, prolactin, chorionic gonadotropin, tissue plasminogen activator, growth hormone releasing peptide(OHRP), thymic humoral factor(THF) and the like. Immunoglobulins of interest include IgG, IgE, IgM, IgA, IgD, and fragments thereof When two or more biocompatible polymers are attached to especially low molecular weight polypeptides such as Interferon and G-CSF, these conjugates exhibit considerably low biological activity. Also, two or more polymers are attached when relatively highly reactive amino groups are conjugated and thus the separation of conjugates in a 1:1 complex is not easy. However, the present invention provides the selective preparation of conjugates of biocompatible polymer-IFN or biocompatible polymer-G-CSF in a 1:1 complex, wherein these conjugates show high biological activity, increased half-life, and excellent bioavailibility. The biologcaily active materials of the present invention also mclude any portion of a polypeptide demonstrating in vivo bioactivity. This includes amino acid sequences, antisense oligomers, antibody fragments, linear antigen(Ref. US Patent 4,946,778), binding molecules including fusions of antibodies or fragments, polyclonal antibodies, monoclonal antibodies, catalytic antibodies, nucleotides. oligonucleotides. The biologically active materials also include enzymes. Enzymes of interest include carbobydrate'Specific enzymes, proteolytic enzymes, oxidoreductases, transferases, hydrolases, lyases, isomerases and ligases. Without being limited to particular enzymes, examples of enzymes of interest include asparaginase, arginase, arginine deaminase, adenosine deaminase, superoxide dismutase, endotoxinases, catalases, chymotrypsin. Upases, uiicases, adenosine diphosphatase, tyrosinases and bilirubin oxidase. Carbohydrate-specific enzymes of interest include glucose oxidases, glucosidases, galactosidases, glucocerebrosidases, glucouronidases, etc. Examples described above are examples of suitable biologically active nucleophiles conjugated with activated biocompatible polymers of the present invention. All suitable biologically active materials with nuclcophilic group are to be also included in the present invention although they are not mentioned above. The biologically active materials for the present invention need to possess at least one free carboxyl group for conjugation by polymer. The conjugates of the present invention are biologically active for the purpose of therapeutic ^plication. Mammals can be treated by administering the therapeutically effective dose of polymer conjugates containing biologically active materials. Preparation of biocompatible polvmer-biologifcallv active material conjugates To conjugate biocompatible polymers to the biologically active molecules, one of the end groups of polymers is converted into a reactive functional group. This process is referred to as "activation" and the product is called an "activated" polymer. For instance, to conjugate poly(alkylene oxides, PAO) to peptides or proteins, one of the hydroxyl end groups of the polymer can be converted into a reactive functional group such as carbonate and activated PAO is produced, which is soluble at room temperature. This group includes mono substituted poly(aIkylcnc oxide) derivatives such as mPEG or other suitable alkyl-substitute PAO derivatives containing C1-4 end group. The term "reactive functional group" used in the art and herein is the group or the residue activating biocompatible polymers to bind with biologically active materials. The reactive functional group of the present invention is selected from the functional groups able to react with carboxylic acid and reactive carbonyl group, for example, primary amine, or hydrazine and hydrazide functional groups (such as acyl hydrazide, carbazate, semicarbazate, thiocarbazate etc.). The term "coupling reagent of carboxyl group"(hereinaft6r referred to as coupling reagent) used in the art and herein means any reagent to couple the carboxyl groups of biologically active materials to biocompatible polymers which have been activated at the above reactive functional group. rhe coi^ling reagents of the carboxyl group in the present invention of interest include, but are not limited to, carbodiimidyl coupling agents, for example, EDAC[N-(3-dimethyl-aminopropyl)-N'-ethylcarbodiimide hydrochloride], DIC[l,3-diisopropyl carbodiimide], DCC[dicyclohexyl carbodiimide], and EDC[1-ethyl-3-(3-dimethylamino propyl)-carbodiimidc]. The preferable coupling agent [for the carboxyl group is EDAC. The method of preparing the conjugates of the present invention includes the step of reacting biologically active molecules containing nucleophiles capable of performing the substitution reaction with activated biocompatible polymers under the condition in which sufficient conjugation can be possible while retaining at least a portion of intrinsic bioactivity of biologically active molecules. The biologically active material-biocompatible polymer conjugates with a ratio of 1:1 are obtained by reacting the biologically active materials with a stoichiometric excess amount of polymers. For example, in the preparation of protein-polymer, peptide-polyraer, enzyme-polymer, antibody-polymer, and drug- polymer conjugates, the molar ratio of biologically active material to biocompatible polymer is in the range of from about 1:1 to 1:20, more preferably from 1:1 to 1:10. The reagents to activate carboxyl groups of biologically active materials are selected from the group as follows, but are not limited to them. For example, N-(3-dimethyl-aminopropyl) -N'-ethylcarbodiimide hydrochloride(EDAC), water soluble carbodiiraide group such as 3-[2-morpholinyl-(4)-ethyl], and 5-substituted isoxazolinium salts such as p-toluene sulfonate, Woodward's Reagent K. The molar ratio of biologically active materials to EDAC used in the present invention is in the range of from about 1:1 to 1:50, more preferably from about 1:1 to 1:30, and most preferably from about 1:1 to 1:20. However, increased yield of PEG-biologically active material conjugates was observed when the addition of EDAC was divided to more than 5 times, preferably 5 or 6 times rather than adding 20-fold molar excess of EDAC at once because EDAC is readily hydrolyzed in aqueous solution. The conjugation reaction of biologically active materials with activated polymers is dependent on the pH of water soluble solvents functioning as a buffer. In general, the pH of reaction buffer for proteins/polypeptides is in the range from 2 to 5, preferably from 2.5 to 4.5. The optimum reaction condition for stabilization of these substances and reaction yield has been known in the art. The suitable temperature for the conjugation reaction is in the range of 0 to 60 V. and preferably in the range of 4 to 30 °C. The temperature of the solvents should not exceed the denaturation temperature of proteins or peptides. Also, the reaction time of 10 minutes to 5 hours is preferable in this preparation. The conjugates prepared can be recovered and purified by column chromatography, diafiltration or a combination of above two processes. Pharmaceutical Composition The present invention also relates to a pharmaceutical composition comprising a therapeutically effective dose of the activated biocompatible polymer-biologically active material conjugates as an active ingredient. The term "pharmaceutically acceptable" used in the art and herein means not causing allergic reaction or similar reaction when administered to humans. The biocompatible polymer-biologically active material conjugate as an active ingredient of the phannaceutieal composition can be used itself or formulated in combination with pharmaceuticaUy acceptable carriers for disease prevention and treatment. The term "pharmaccutically acceptable carrier" used in the art and herein means pharmaccutically acceptable molecules, composition, or vehicles such as solutions, diluents, excipients, or solvents to carry the biologically active materials from one organ or tissues to other organs or tissues. The pharmaceutical composition of the present invention can be administered by the route of oral, local, injection or parenteral route and its formulation include therapeutically effective doses of the biocompatibie polymer-biologically active material coiyugates as an active ingredient, The formulation for oral administration of the present invention include pills, tablets, coated tablets, granules, troches, wafws, elixirs, hard and soft gelatin capsules, solutions, syrups, emulsions, suspensions, or sprays etc. and for parenteral administration, injectable solutions, microcapsules, patches, and others are included. The pharmaceutical formulation can be prepared according to the known method by using pharmaceutically acceptable inactive inorganic or oragnic additives. For example, lactose, com starch and its derivatives, talc, or stearic acid and its salts can be used to prepare pills, tablets, and hard gelatin capsules. The additives of soft gelatin capsules and suppositories are for example, oil, wax, semi-solid or liquid polyol, and natural or solidified oil. The suitable additives for preparation of solution or syrup are for example, water, sucrose, invertase, glucose, and polyol. The suitable additives for preparation of injectable solution are water, alcohol, glycerol, polyol, plant oil etc. The injectable solution can be used as the combination of preservatives, indolent agents, solubilizers, and stabilizers. The formulation for local administration can be also used as the combination of gas, diluents, lubricants, and preservatives. The suitable additives for microcapsules or translantation are copolymer or glycolic acid and lactic acid. The dose of the biocompatible polymer-biologically active material conjugates of the present invention varies depending on the absorption rate of the biologically active materials, solubility, patient's age, sex, condition and severity of diseases, etc. as well known in the art. Particularly, the administration of biocompatible polymer-biologically active material conjugates of the present invention reduces the injection intervals from daily or once per two days to weekly or biweekly injection. Therefore, the toxicity and site effects of drugs by frequent administration are reduced substantially. The following examples further describe and demonstrate embodiments within the scope of the present invention. The examples are given solely for the purpose of illustration and are not to intended limit the present invention, as many variations thereof are possible without departing from the spirit and scope of the invention. Examples 1. Preparation of biocompatible Dolvmer-bioloizicallv active material conjugates via a carboxvl group of biologically active material Preparation of mPEG(12000)-Hz-G-CSF conjugate 1 mg of G-CSF solution(0.00005 mmol. Dong-A Pharm. LEUCOSTIM) was dialyzed(Centricon-10, Amicon, USA) against 50 mM MES buffer solution (pH 3.0) to the final concentration of 2 mg/ml. To this protein solution. 6.6 mg of mPEG(12000)-Hz(ISU Chemical, Korea, 0.0005 mmol) was added and followed by 2ul (0.001 mmol, 20-fold molar excess) of ED AC solution prepared by dissolving 2 mg of ED AC in 20 ul of d-HiO. The reaction was carried out for 1 hour at room temperature(20-25t;) with stirring. After 1 hour, unreacted G-CSF and excess reagent were removed by size exclusion column or ion-exchange column. More than 0.3 mg of mPEG(12000)-Hz-G-CSF conjugate was obtained. By changing the amount of EDAC from 20 to 200-fold molar excess and mPEG(12000)-H2 from 10 to 20-fold molar excess, the reaction was repeated. It was observed that two or more raPEG(12000)-Hz were attached to the carboxyl group of G-CSF when the amount of EDAC is over 50-fold molar excess. Preparation of mPEG(5000)-Hz-G-CSF conjugate 1 mg of G-CSF solution(0.00005 mmol) was dialyzed(Centricon-10, Amicon, USA) against 50 mM MES buffer soiution(pH 3.0) to the final concentration of 5 mg/ml. To this protein solution, 1.3 mg of mPEG(5000)-Hz(ISU Chemical, Korea, 0.00025 mmol) was added, followed by 2ul(0.001 nmiol, 20-fold molar excess) of EDAC solution prepared by dissolving 2 mg of EDAC in 20 ul of d-HaO. The reaction was carried out for 1 hour at room temperature(20-251) with stirring. After 1 hour, unreacted G-CSF and excess reagent were removed by size exclusion columm or ion-exchange column. More than 0.3 mg of mPEG(5000)-Hz-G-CSF was obtained FIG. 1 shows the production of mPEG(5000)-Hz-G-CSF conjugate by SDS-FAGE and HPLC profile (size exclusion chromatography). Preparation of mPEG(20000)-Hz-G-CSF conjugate 1 tng of G-CSF solution(0.00005 mmol) was dialyzed against 50 mM MES buffer solution(pH 3.0) by ultrafiltration(Centricon-10, Amicon, USA) to the final concentration of 5 mg/ml. To this protein solution, 5 mg of mPEG(20000)-Hz(lSU Chemical, Korea, 0.00025 mmol) was added, followed by 2ul(0.001 mmol, 20-fold molar excess) of ED AC solution prepared by dissolving 2 mg of ED AC in 20 ul of d-H2O. The reaction was carried out for 1 hour at room temperature(20-251)) with stirring. After 1 hour, imreacted G-CSF and excess reagent were removed by size exclusion coluron or ion-exchange column. More than 0.3 mg of mPEG(20000)-Hz-G-CSF;, was obtained. FIG 2 shows the production of mPEG(20000)-Hz-G-CSF conjugate by SDS-PAGE. Preparation of mPEG(5000)-Hz-IFN conjugate Four tubes each containing 200 ug of IFN solution(0.00001 rmnol, Korea Green Cross Corp., Green Alpha) were dialy2ed(Centricon-10, Amicon, USA) respectively, against 50 mM MES buffer solution(pH 3.0) to the final concentration of 1 mg/ml. To each tube, 2.16 mg of mPEG(5000)-HZ was added, followed by 0.8 ul(40-fold molar excess) of EDAC solution prepared by dissolving 2 mg of EDAC in 20 ul of d-HaO. The reaction was carried out for 1 hour at room temperature(20-25t;) with stirring. After 1 hour, unreacted IFN and excess reagent were removed by size exclusion column or ion-exchange column. FIG 3 shows the conjugation of mPEG(5000)-HZ to ffN molecules by SDS-PAGE. Preparation of mPEG(12000)-Hz-IFN conjugate I mg ot IFNsolution (0.00005 mmol) was dialyzed(Centricon-10, Amicon, USA) against 50 mM MES buffer solution(pH 3.0) to the final concentration of 1 mg/ml. To this protein solution, 6.6 mg of mPEG(12000)-H2(0.0005 mmol) was added, followed by 2µl(0.001 mmol, 20-fold molar excess) of ED AC solution prepared by dissolving 2 mg of EDAC in 20 ul of d-HaO. The reaction was carried out for 1 hour at room temperature(20-25°C) with stirring. After 1 hour, unreacted IFN and excess recent were removed by size exclusion column or ion-exchange column. More than 0.3 mg of mPEG(12000)-Hz-IFN was obtained. Preparation of mPEO(20000)-Hz-IFN conjugate Four tubes containing 200 ug of IFN solution(0.00001 mmol) in each tube were dialyzed(Centricon-10, Amicon, USA) against 50 mM MES buffer solution(pH 3.0) to the final concentration of 2 mg/ml. To each tube, 4.32 mg of mPEG(20000)-Hz(0.0002 mmol, ISU Chemical, Korea) was added, followed by 1 ul(50-fold molar excess) or 4 ul(200-fold molar excess) of EDAC solution prepared by dissolving 2 mg of EDAC in 20 ul of d-H2O. In addition, 30-fold molar excess of sulfo-NHS was added to accelerate the reaction and the results were compared. The reaction was carrired out for 1 hour at room temperature(20-251°C with stirring. The reaction condition of each sample is described in the table below. After 1 hour, unreacted IFN and excess reagent were removed by size exclusion column or ion-exchange column. The yield of each reaction was compared by SDS-PAGE. (Table Removed) As a result, the reaction with 200-fold molar excess of ED AC showed that too many PEOs were attached to the carboxyl group of IFN and separation of the PEG-IFN conjugate with the molar ratio of 1:1 was not successful and estimation of the number of PEOs attached was not easy. Also, the reaction with 50-fold molar excess of ED AC proceeded but PEG-IFN conjugate with the ratio of 1:1 was not readily distinguishable because the PEO-IFN conjugate was diffused on SDS-PAGE due to the excess amount of ED AC used. When sulfo-NHS was added to the reaction to enhance the efficiency, there was no difference from a control in which sulfo-NHS was not odded(FIG 4). Also, the reaction efficiency upon adding EDAC several times was performed according to reaction conditions as described in the table below. (Table Removed) As a result, when EDAC was added stepwise to the reaction mixture, the yield of mPEG-Hz-IFN conjugate with the molar ratio of 1:1 was high(FIG 5). When the amount of EDAC was over 50-fold molar excess although addition of EDAC was performed stepwise, two or more PEGs were randomly attached to the IFN as shown in FIG 5. Preparation of mPBG(20000)-Hz-IFN conjugate 1 mg of IFN solution(0.00005 mmol) was dialyzed(Centricon-10(Amicon, USA)) against 50 mM MES buffer solution(pH 2.5) to the final concentration of 5 mg/mi. To this protein solution, 10.8 mg of mPEG(20000)-Hz(0.0005 mmol, 10-fold molar excess) was added, followed by 2 M(0.001 mmol, 20-fold molar excess) of EDAC solution prepared by dissolving 2 mg of EDAC in 20 ul of d-H2O. The reaction was carried out for I hour at room temperature(20-25t;) with stirring. After 1 hour, unreacted IFN and excess reagent were removed by size exclusion column or ion-exchange column. More than 0.3 mg of mPEG(20000)-Hz-IFN conjuate was obtained. Purification of mPEG(20000)-Hz-IFN conjugates with the molar ratio of 1:1. mPEG(20000)-H2-lFN conjugate(Example 6) was diluted with lOmM sodium acetate buffer(pH4.4) to the final concentration of 1 rag/ml. mPEG(20000)-Hz-IFN reaction mixture was loaded onto SP-sepharose Fast Flow column(5 x 50 mm, total 1 ml column vol.), which had been previously equilibrated with 10 mM sodium acetate buffer 3olution(pH 4.4). After washing the column with 3 column volumes of 10 mM acetate buffer(pH 4.4), a gradient of 10 mM acetate buffer(pH 4.4) containing 500 mM NaCl was used to separate mPEO(20000)-Hz-IFN with the molar ratio of 1:1 from unreacted intact IFN. The above purified mPEG(20000>Hz-IFN was confirmed to be the conjugate wherein one PEG was attached to the carboxyl group of IFN(FIG 6). Determination of Biological activity of PEG-0-CSF conjugate CPE{Cytopalhic effect) assay was performed as follows. 2.5 xl06 cells(5xl0' cells/ml) of M-NFS-60 were sub-cultured on 60mm dishes(RPMI-1640 media, 10% PBS, 37°C, 5% CO2). Each of native G-CSF(contTol) and mPEG(20000)-Hz-G-CSF(Example 3) was diluted to the concentration of1ng/ µl and added to the 96 well plate containing 1 x 104 cells in each well, followed by serial dilution. The plate was incubated at 37t for 2 days. Then each well was treated with 50 µl of XTT ]dt(Roche, Germany) and incubated for another 4 hours at 37°C, and O.D. value of the plate was read at 490 nm using ELISA reader. As a result, mPEG(20000)-H2-G-CSF of the present invention was shovra to retain a similar activity to mPEG(20000)-G-CSF conjugate, wherein PEG was attached to the amino growth of G-CSF(FIG 7). Deftermination of half lifs'of PEG-G-CSF conjugate 7-week old Sprague-Dawley rats (5 rats per group) weighing 220-240g were anesthetized using Kctamin/Rompun and a PE tube was inserted to the vena cava of each rat by surgery. After the rat recovered, 100 µg/kg of mPEG(20000)-Hz-G-CSF(Example 3) was administered through intravenous injection. PBS and 100 ug/kg of native G-CSF were used as placebo and control, respectively, for comparison. 300 ul of blood was withdrawn through the cannula at time intervals of 0, 0.5, 1, 2, 4, 6, 12, 24, and 48 hours after injection. The serum was separated by centrifugation{ 13,000 rpm, 10 min, 4 °C and stored at -20 °C for further study. After incubation the cells for 24 hours with G-CSF free media, each well of 96 well plate was added with 1.5 x 104 cells. Each scrum sample stored as described above was diluted 100 times and 50 ul of the diluted samples was added to each well of 96 well plate. The dishes were incubated at 37 °C for 48 hours under CO2 gas. Then each well was treated with 50 µl of XTT kit(Roche, Germany). Plates were incubated for another 4 hours at 37 °C and the O.D. value of the plate was read at 490 mn using an ELISA reader. The half-hfe of mPEG(20000)-Hz-G-CSF(Example 3) is compared to that of native G-CSF and Neulasta™ (PEG attached to N-terminal of G-CSF, Amgen) in FIQ 8. mPEG(20000)-Hz-G-CSF(Exanaple 3) of the present invention showed a much longer half-life compared to native G-CSF, and has similar half-life to that of NeulastaTM Determination of White Blood Cell (WBC) count of PEG-G-CSF-treated rats 7-week old Sprague-Dawley rats weighing 220-24Gg were purchased from Charles River Co.(Atsugi, Japan). 100 ug/kg of mPEG(20000)-Hz-G-CSF (Example 3) was injected to the tail vein of rats. The same amount of native G-CSF and saline solution was injected respectively as a control. Blood samples were withdrawn at time intervals of 0, 6, 12, 24, 48, 72, 96 hrs after injection through the tail vein. WBC count was measured by Automated Hematology Analyzer {Cysmex K-4500) as shown in FIG. 9. As a result, mPEG(20000)-Hz-G-CSF of the present invention showed higher WBC counts than both native G-CSF and Neulasta™. Determination of biological activity of PEG-IFN conjugate MDBK cells counted in a concentration of 7.5x105 cells/ml using a hemocytometer, were suspended in 5% FBS/MEM media. mPEG(12000)-Hz-IFN(Example 5) was diluted to the concentration of 100IU(1 mg/ml = 2 X 108 lU). Each well was supplemented with l00ul of 5% FBS/MEM media and 100 ul of the diluted samples was added to the first well followed by serial dilution. Then 100 ul of cell suspension was added to each well of 96 well plate. The dishes were incubated at 37°C for 20 hours. 100 ul of Vesicular Stomatitis Virus(VSV, ATCC VR-158) diluted 100 times was added to each well and incubated another 20 hours at 37 °C. The growth medium solution containing Vesicular Stomatitis Virus(VSV, ATCC VR-158) of 96 well plate was removed, 50 ul of 0.05 % crystal violet dye solution was added to each well, and O.D. of each well was read at 550nm by ELISA reader to determine the activity of IFN. As a result, the activity of mPEG(12000)-Hz-IFN (Example 5) was found to retain 40-50 % of native DFN activity and showed activity similar to that of the comparative PEG-IFN(Schering-Pbugh, USA, PEG attached to amino group of IFN. approved by FDAKFiG 10). Also, the activity of niPEG(20000)-Hz-IFN (Example 6) was determined to be approximately 40 % of native IFN(FIG 11). Also, the activity of Di-mPEG-Hz-IFN(Two PEGs attached to one IFN) and mono-PEG-IFN(l:l complex, one PEG attached to one IFN) was compared by CPE assay and mono-mPEG-Hz-IFN showed high biological activity(FIG 12). Determination of half-life of PEO-IFN conjugate MDBK cells counted in a concentration of 7.5x10 °C cells/mt were suspended in 5% FBS/MEM media. 100 ul of cell suspension was put in each well of 96 well plate. Scrum was obtained after injecting mPEG(20000)-Hz-INF(Examplc 6) by intravenous route to rats and diluted 50 times. Each well was added with the diluted serum and incubated in a CO2 incubator for 20 hours. Each well was added with 100-fold diluted Vesicular Stomatitis viius(100 ul) and incubated continued for aiwther 20 hours. The virus medium solution in each well was removed, and 50 ui of 0.05 % crystal violet dye solution was added to each well. The absorbance at 550 nm was read by a Microplate reader to measure the half life of IFN. FIG. 13 shows the half-life of mPEG(20000)-Hz-IFN(ExampIc 6) conjugated at the carboxyl group and comparison of mPEG(20000)-Hz-IFN with native IFN and comparative product, PEG-IFN. mPEG(20000)-H2-IFN of the present invention showed a much greater half-life than native IFN and longer half-life than the comparative product, PEG-EFN. Stability of PEG-IFN conjugate The stability of mPEG(20000)-Hz-IFN prepared and purified in Example 6 and PEG-IFN, wherein branched PEG(10lC)2-NHS(attached to the amino group of IFN according to the general method in the literature followed by separating mono PEG-IFN by size exclusion column, Nektar, USA) was determined on SDS-PAGE after incubation at 4 °C in PBS solution by observing the dissociation of intact IFN on the SDS-PAGE. The concentration of each sample was adjusted to the final concentration of 1mg/ml. As a result, it was observed that about 14 % of intact IFN was dissociated from the PEG-IFN conjugated through the amino group of IFN about 2 weeks later, whereas the dissociation of IFN from PEG(20000)-H2-IFN conjugated through the carboxyl group of IFN of the present invention was not detected even after 6 months later(FIG 14). Preparation of mPEG(5000)-Hz-PTH conjugate 1 mg of human PTH(parathyroid hormone, 0.00012 mmol, 1-84 aa, Dong-Kook Pharm., Korea) and 3.0 mg of activated mPEG(5000)-Hz(0.0006 mmol, ISU Chemical, Korea) in 0.5 ml of 50 mM MES buffer solution, pH 4.4 were reacted for 10 minutes with stirring at room temperature. 2.5 ul of EDAC(0.00125 mmol, 10-fold molar excess) prepared at a concentration of 100 ug/ul, was then added and reacted for 1 hour with stirring at room temperature. Unreacted mPEG(5000)-Hz and PTH were removed by using Centricon-IO(Amicon, USA) and 0.4 mg of mPEG(5000)-Hz-PTH was obtained. Preparation of mPEG(12000)-Hz-PTH Conjugates 1 mg of human PTH(0.00012 mmol) and 7.14 mg of activated mPEG(12000)-Hz(0.0006 nmiol, 5 fold molar excess, ISU Chemical, Korea) m 0.5 ml of 50 mM MES buffer solution, pH 4.4 were reacted for 10 minutes with stirring at room temperature. 2.5 ul of EDAC(0.00125 mmol, 10-foid molar excess) prepared at a concentration of 100 ug/ul, was then added and reacted for 1 hour with stirring at room tanperature. Unreacted mPEG(12000)-Hz and PTH were removed by using Centricon-l0(Amicon, USA) aad 0.3 mg of mPEG(12000)-Hz-PTH was obtained. Preparation of mPBG(20000)-Hz-PTH Conjugates 1 mg of human PTH(0.00012 mmol) and 12 mg of activated mPEG(20000)-Hz(0.0006 mmol, 5 fold molar excess, ISU Chemical, Korea) in 0.5 ml of 50 mM MES buffer solution, pH 4.4 were reacted for 10 minutes with stirring at room temperature. 2.5 ul of EDAC(0.00125 mmol, 10-fold molar excess) prepared at a concentration of 100 ug/ul, was then added and reacted for 1 hour with stirring at room temperature. Unreacted mPEG(20000)-Hz and PTH were removed by using Ccntricon-30(Amicon, USA) and 0.3 rag of mPEG(20000)-Hz-PTH was obtained. Prq)aration of mPEG(12000)-Hz-PTH conjugate 1 mg of human PTH(0.00012 mmol) and 14.4 mg of activated mPEG(12000)-H2(0.0012 mmol, 10 fold molar excess, ISU Chemical, Korea) in 0.5 ml of 50 mM MES buffer solution, pH 2.5 were reacted for 10 minutes with stirring at room temperature. 5 ul of EDAC(0.0025 mmol, 20-fold molar excess) prepared at a concentration of 100 ug/ul, was then added and reacted for 1 hour with stirring at room temperature. Unreacted mPEG(12000)-Hz and PTH were removed by using Centricon-10(Amicon, USA) and 0.2 mg of mPEG(12000)-Hz-PTH was obtained. Preparation of mPEG 1 mg of human PTH(0.00012 mmol) and 24 mg of activated mPEG(20000)-Hz(0.0012 mmol, 10-fold molar excess, ISU Chemical, Korea) in 0.5 ml of 50 mM MES buffer solution, pH 2.5 were reacted for 10 minutes with stirring at room temperature. 5 ul of EDAC(0.0025 mmol, 20-fold molar excess) prpared at a concentration of 100 ug/ul, was then added and reacted for 1 hour with stirring at room temperature. Unreacted mPEG(20000)-H2 and PTH were removed by using centricon-10(Amicon, USA) and 0.2 mg of mPEG(20000)-Hz-PTH was obtained. Analysis of mPEG-Hz-PTH conjugate PEG-PTH conjugate and native PTH which were obtained from the above examples were determined as following HPLC condition. Elutiag Condition of HPLC Column: LiChroCART 125-4 RP-8 (5 umXMerck, USA) Solvent: A; deionized water containing 0.1 % TFA, B; acetonitrile containing 0.1 % TFA Flow rate: 0.8 ml/min Detector: UV detector at 220nm Injection volume: 20 ul (Table Removed) By using LiChroCART 125-4 RP-8 (5 um) for HPLC, only PTH and other proteins were detwted at 220nm whereas no PEG was detected at 220nm. The RT of PTH was determined by HPLC. A sharp peak of PTH which is not modified by the polymer was seen around 6.8 min, then slowly increased up to about 18 min, and decreased again(FIG 15). mPEG-Hz-PTH prepared as described above was eluted at 6.8 min for unieacted PTH and 7.3 min for PEG-PTH, respectively, in the range of the elution conditions between number 1 and 2 in the above table. There are three kinds of productsCunreacted PTH, mPEG(20000)-Hz-PTH, mPEG(20000)-Hz) present immediately after the conjugation and before purification. Only two peaks, unreacted PTH and mPEG(20000)-Hz-PTH conjugate, were detected at 220 nm on HPLC while unreacted mPEG(20000)-Hz was not detected at 220 nm(FIG 16). FIG 17 shows the finally purified mPEG{20000)-Hz-PTH on HPLC and FIG. 18 SDS-PAGE stained with Coomassie blue performed after reacting mPEG(20000)-Hz with PTH. Determinatiott of in vitro biological activity of mPEG-PTH Conjugate The activated mPEG-Hz having molecular weights of 5000(5K), 12000(12K), and 20000(20K) were used to determine the biological activity according to molecular weight of PEG The in vitro biological activity of native PTH, mPEG(5000)-Hz-PTH, mPEG(12000)-Hz-PTH, and mPEG20000)-Hz-PTH was compared by determining the amount of c-AMP synthesized by c-AMP kit(Amersham Pharmacia, RPN 225, USA) using UMR-106 cell line. It was found that the biological activity of mPEG-Hz-PTH was decreased as molecular weight of PEG increased. It was also found that mPEG(5000)-Hz-PTH, mPEG{12000)-Hz-PTH. and mPEG(20000)-Hz-PTH at the concentration of l0-8 mole retained 40%, 30%, and 20 % activity of unreacted PTH, respectively(FIG 19). Determination of half-life of mPEG-Hz-PTH 100 ug/kg of PTH and mPEG-Hz-PTH was administered through intraveneous injection, respectively to each of male rats weighing 300-350g. Blood was then withdrawn through the cannula at time mtervals of 0, 5, 10, 15, 30, 60, and 120 min after injection. The serum was separated by centrifugation(10,000 rpm, 10 min, 4 °C and the half life of mPEG-Hz-PTH was indirectly determined by calculating the concentration of remaining PTH by measuring the concentration of cAMP in plasma using c-AMP kit(Amersham Pharmacia, RPN 225, USA). As a result, unreacted PTH and mPEG(5000)-Hz-PTH were not detected after 15 mins after administration. However, mPEG(12000)-Hz-PTH and mPEG(20000)-Hz-PTH were detected after 1 hour and 2 hours, respectively, after administration(FIG 20). Thus, while there have been described the preferred embodiments of the present invention, those skilled in the art will realize that other embodiments can be made without departing from the spirit of the invention, which includes all such further modifications and changes as come within the meaning, true scope of the claims set forth herein and equivalents thereof. The above examples further, describe and demonstrate embodiments within the scope of the present invention. The examples are given solely for the purpose of illustration and are not to be construed as limitations of the present invention, as many variations thereof are possible without departing from the spirit and scope of the invention. Application of the present invention The present invention provides the biocompatible polymer-biologically active material conjugates in a molar ratio of 1:1 wherein the biocompatible polymer is attached to a carboxyl group of the biologically active material such as proteins or peptides and method of preparation thereof. These conjugates having the increased bioavailibility and extended half-life due to their increased in vivo stability can reduce the frequency of administration significantly when used as therapeutic drugs for diseases. We claim: 1. A conjugate of biocompatible polymer-biologically active material, wherein the activated biocompatible polymer is conjugated to a carboxyl group or C-terminus of the biologically active material at a molar ratio of 1:1; wherein the biocompatible polymer is selected from the group consisting of polyethylene glycol, polypropylene glycol, polyoxyethylene, polytrimethylene glycol, polylactic acid and Derivatives thereof, polyacrylic acid and derivatives thereof, poly(amino acid), polyurethane, polyphosphazene, poly(L-lysine), polyalkylene oxide, polysaccharide, dextran, polyvinyl pyrrolidone, polyvinyl alcohol, polyacryl amide, and copolymers thereof; and wherein the biologically active material is selected from the group consisting of a-, p-, A-, y- interferon, parathyroid hormone, asparaginase, arginase, arginine deiminase, adenosine deaminase, superoxide dismutase, endotoxinase, catalase, chymotrypsin, lipase, uricase, adenosine diphosphatase, tyrosinase, glucose oxidase, glucosidase, galactosidase, glucouronidase, hemoglobin, blood factors VII, VIII and IX, immunoglobulin, cytokine, granulocyte colony stimulating factor, granulocyte macrophage colony stimulating factor, platelet derived growth factor, lectin, ricin, tumor necrosis factor, transforming growth factor, epidermal growth factor, calcitonin, insulin, synthetic enkephalin, interleukin, erythropoietin, growth hormone releasing peptide, luteal hormone-releasing hormone and derivatives threreof, hypothalamic releasing factors, calcitonin gene related peptides, thyroid stimulating hormone and thymic humoral factor. 2. The conjugate as claimed in claim 1, wherein the biologically active material is interferon, G-CSF, or parathyroid hormone. 3. A pharmaceutical composition comprising a pharmaceutically acceptable amount of the conjugate claimed in claim 1 and a pharmaceutically acceptable carrier. 4. A method of preparation of the conjugate claimed in claim 1, consisting the steps of: (a) activating biocompatible polymer with a reactive functional group which is able to react with the carboxyl acid and reactive carbonyl group; and (b) conjugating biologically active material to the activated biocompatible polymer with the stepwise addition of coupling reagent, said coupling reagent comprising carbodiimidyl coupling agents, EDAC [N- (3-dimethyl-aminopropyl)-N'-ethylcarbodiimide hydrochloride], DIC [1, 3-diisopropyl carbodiimide], DCC [dicyclohexyl carbodiimide], and EDC [1- ethyl-3- (3-dimethylamino propyl)-carbodiimide], under the condition wherein the molar ratio of the biologically active material to the activated biocompatible polymer is 1:1 to 1:20, the ratio of the biologically active material to said coupling reagent is 1:1 to 1:50, and pH is in the range of 2 to 5.

Full Text

FIELD OF THE INVENTION
The present invention relates to a conjugate of biocompatible polymer-biologically active material, method of preparation of the conjugate and pharmaceutical composition comprising the conjugate.
Background of the Invention
Use of proteins and peptides as medicinal products generally has been limited by several problems. For example, peptides or proteins are very low in in vivo absorption efficiency because they are easily hydrolyzed or degraded by proteases within a short period of time after being taken into the body, and also induce immune response with repeated administration. Therefore, most protein and peptide drugs have been required to be administered by injection at least once a day or more. This firequent administration by injection, however, causes pain and risk to patients. Also, frequent injections over long periods is costly and
inconvenient to the patients.
Attempts to develop more stable drugs are required to solve the above problems, and the technology to modify biologically active materials such as proteins or polypeptides with biocompatible polymers has been developed. Conjugates of proteins or pharmaceutically active molecules to biocomatible polymers can afford great advantages when they are applied in vivo and in vitro. When being covalently bonded to biocompatible polymers, biologically active materials can exhibit modified surface properties and solubility, and thus can be increased in solubility within water or organic solvents. Further, the presence of biocompatible polymers can make the proteins and/or polypeptides conjugated to them more stable in vivo, increase biocompatibility of the proteins and reduce immime response, and reduce the clearance rate of the proteins by the intestine, the kidney, the spleen, or the liver.
Although the conjugation of the biologically active materials such as a protein or peptide of interest with biocompatible polymers such as PEG has many advantages, some problems remain in conjugating by known methods.
The most common conjugation method is achieved by bonding activated PEG to the amino group of amino acid residues such as lysine. When the active site on a protein's surface is conjugated to PEG, the biological activity of protein-polymer conjugates is substantially decreased because one or more jfree lysine residues of rnany proteins are frequently adjacent to the active sites of proteins generally. Also, the reaction between lysine residues of proteins and activated PEG occurs easily and PEG-protein conjugates wherein two or more PEG molecules arc conjugated to one protein molecule are obtained. For example.
when more than two PEG molecules bind to the surface of cytokines such as interferon, CSF, and interleukin or polypeptides such as EGF, hGH, and insulin, the biological activity of conjugate is rapidly reduced resulting in loss of function. .Also, these reactions occur randomly and result in a mixture of many kinds of PEG-protcin conjugates, which make the purification of desired conjugates complicated and difficult. If too many polymer molecules are attached to targeting proteins or peptides, the conjugates lose all or much of their biological activity. Also, if an expressively reactive linker has been used or msufficicnt numbers of polymers are attached to targeting protein molecules, the therapeutic efficacy of those conjugates can be decreased.
To overcome these problems, many attempts have been made to conjugate biocompatible polymers to amino acid residues of proteins substituted by genetic engineering to conjugate polymers to a specific site of proteins. However, this method generally alters the original properties of proteins. Also the safety of these genetically engineered molecules as therapeutic drugs needs to be proved.
Attempts have been made to solve the problems by chemically modifying specific sites of biologically active materials with biocompatible polymers. US patent No. 5,951,974 and 5,985,263 describes conjugation of PEG molecules to the histidine residue of interferon to increase the efficacy of drugs by lengthening half-life in vivo and the like. However, this method still used the reactive amino group and produced isomers of PEG-IFN randomly attached at several histidine sites, and requires an additional purification step using an ion-exchange column to separate the desired 1:1 complex of highly active PEG-IFN conjugate. Further, the imidazolyl group of histidine to which PEG is attached is easily hydrolyzed
compared to other amino groups of amino acids, and interferon is easily released from the PEG-intcrfcron conjugate.
US Patent No. 5,766,897 describes conjugation of macromolecules and mutant forms thereof at their cysteine residues to activated PEG molecules. Because of disulfide bond most protein moieculcs have either one fi«e or no spare cysteine. Thus, an amino acid which is not related to the active site can be changed to a cysteine residue by mutagenesis to conjugate the new cysteine residue with polymers. This method, however, tends to produce conjugates with significantly decreased activity compared to conjugates at amino or carboxyl groups of proteins, although it has an advantage of attaching the polymer to a specific site of biologically active molecules.
US Patent No 5,985,265 describes site-specific coiyugates at N-terminal residues of 0-CSF and IFN with PEG molecules. However, reactivity of these activated polymers is low, and the reaction needs a longer reaction time. In addition, the yield of the reaction is low and stability of proteins is poor. In case that the active site of protein molecules is especially near the N-terminus, conjugation at the N-termiital amino group results in the significant decrease or loss of biological activity.
US Patent No 5,824,778 describes conjugates of G-CSF at amino and carboxyl groups by PEG Excess EDAC was added to activate the carboxyl groups of the protein and many PEG molecules were attached to activated carboxyl groups of several residues. The obtained PEG-G-CSF conjugate has been determined to be a heterogeneous mixture having various numbers of PEG molecules attached, and biological activity of the conjugate was significantly

reduced. Therefore, if the biological activity of biologically active molecules can be maintained after conjugation with the polymer at a desired ratio, and a homogenous species of site-specific conjugates can be obtained, cliniaical usefulness of such molecules will increase remarkably.
Summary of Invention
Inventors of present invention prepared PEG-biologically active molecule conjugates at a ratio of 1:1, wherein PEG is attached to a carboxyl group of biologically active molecules. Carboxyl groups of biologically active molecules have lower reactivity than amino groups. It was observed that these conjugates show therapeutic efficacy up to 20-fold higher than native(non-conjugated) proteins because they have an extended half-life and higher stability compared to native proteins. Also they observed that the 1:1 complex showed superior characteristics to conjugates of higher than 1:1 molar ratio at carboxyl groups or conjugates at amino groups.
Therefore, the present invention provides conjugates of biologically active molecules with biocompatible polymers wherein biocompatible polymers are specifically attached to a carboxyl group of biologically active molecules at a ratio of 1:1, methods of preparation thereof and a pharmaceutical composition comprising the same. The conjugates of the present invention retain biological activity of native biologically active molecules and have increased stability, bioavailability, and half-life.
Brief Description of the Drawings
Fig. 1 shows the degree of conjugation for mPEG(,5K)-Hz-G-CSF by HPLC and SDS-PAGE.
Fig. 2 shows the degree of conjugation for mPEG(20K)-Hz-G-CSF by HPLC and SDS-PAGE.
Fig. 3 shows raPEG(5K)-Hz-IFN with the molar ratio of 1:1 on SDS-PAGE.
Fig. 4 shows the prod\ictivity of mPEG(20K)-Hz-IFN conjugate according to the amount of EDAC added on SDS-PAGE.
Fig. 5 shows the degree of reactivity for mPEG(20K)-Hz-lFN conjugate according to the addition method of EDAC and the amount of EDAC on SDS-PAGE.
Fig. 6 shows SDS-PAGE of mPEG(20K)-Hz;-IFN conjugate purified by an ion-exchange columm.
Fig. 7 shows the comparison of the biological activity of mPEG(20K)-Hz-G-CSF conjugate, native G-CSF ,and Neulasta™ (PEG-G-CSF, developed by Amgen, FDA aproved in 2002) by cell based assay.
Fig. 8 shows the plasma half-Ufe of mPEG(20K)-H2-G-CSF, native G-CSF, and Neulasta™(PEG-G-CSF, developed by Amgen, FDA approved in 2002).Fig. 9 shows WBC of mPEG(20K)-Hz-G-CSF conjugates, native G-CSF, and Neulasta™(PEG-G-CSF, Developed by Amgen, FDA approved in 2002).
Fig. 10 shows biological activity of mPEG(12K)-Hz-IFN conjugate, native IFN, and PEG-IFN(developed by Schering-Plough) by CPE assay.
Fig. 11 shows the comparison of biological activity of mPEG(20K)-Hz-
IFN conjugate with native IFN by CPE assay.
Fig. 12 shows the comparison of biological activity between Di-mPEG-Hz-IFN, two PEG molecules attached to one IFN molecule and mono-mPEG-Hz-IFN, one PEG molecule attached to one DFN molecule, by CPE assay.
Fig. 13 shows the comparison of half-life in plasma of PEG(20K)-Hz-IFN conjugate, native IFN, and PEG-IFN(developed by Schering-Plough).
Fig. 14 shows the comparison of stability between PEG-IFN conjugated at a carboxyl groiq) and at an amino group.
Fig. 15 shows the HPLC chromatogram for native PTH, which has not been modified by biocompatible polymers.
Fig. 16 shows the HPLC chromatogram for a reaction mixture(unreacted PTH, mPEG(20K)-Hz-PTH, mPEG(20K)-Hz) of PTH with mPEG(20k)-Hz before purification (peak 1: unreacted PTH with PEG polymer, peak 2: mPEG(20k)-Hz-PTH)
Fig. 17 shows HPLC chromatogram of the purified mPEG(20kO)-H2-PTH after corrugating PTH with mPEG(20K)-Hz.
Fig. 18 shows SDS-PAGE, stained with Coomassie blue for the reaction product between PTH and mPEG(20k)-Hz (lane 1: MW marker, lane 2: PTH, lane 3: PTH, PTH-mPEG(20k)-Hz conjugate before purification, lane 4: PTH-mPBG(20k)-H2 conjugate after purification.
Fig. 19 shows the in vivo biological activity for PTH and PEG-PTH conjugate.
Fig. 20 shows the half-life of PTH and PEG-PTH conjugates in rats.
Detailed Description of the Invention
In an aspect, the present invention relates to the conjugates of biocompatible polymer-biologically active material, wherein the activated biocompatible polymer is conjugated to a carboxyl group of biologically active material at a molar ratio of 1:1.
In another aspect, the present invention relates to a pharmaceutical composition comprising a therapeutically effective amotmt of the above biocompatible polymer-biologically active molecule conjugates and pharmaceutically acceptable carriers.
In a further aspect, the present invention relates to a method of preparation of conjugates of biocompatible polymer-biologically active material at a molar ratio of 1:1, wherein the biocompatible polymer is conjugated at a carboxyl group of biologically active material, comprising the step of conjugating the biologically active material to the activated the biocompatible polymer with the stepwise addition of coupling reagent under tiie condition wherein the molar ratio of biologically active material to activated the biocompatible polymer is 1:1 to 1:20, the ratio of biologically active material to the coupling reagent is 1:1 to 1:50, and pH is in the range of 2 to 5.
In the above method, EDAC, as an example of the coupling reagent, was added stepwise more than 5 times, preferably 5 or 6 times, because EDAC is readily hydrolyzed in aqueous solution.
The method described above provides the conjugates wherein
biocompatible polymers are attached to a carboxyl group of biologically active molecules at a ratio of 1:1. In other words, the present invention provides site specific conjugation by binding activated polymers to a carboxyl group of biologically active materials at a molar ratio of 1:1. These conjugates retain the biological activity of biologically active materials by preventing the attachment of polymers to active sites. The present invention also provides the conjugates with a molar ratio of 1:1 by avoiding the random reaction with many reactive residues at active sites to produce various kinds of heterogeneous mixtures. Further, the conjugates of the present invention have several advantages such as increased stability in vivo, increase of bioavailibility, and extended half-life caused by biocompatible polymers. Therefore, production of homogeneous biocompatible polymers-biologjcally active material conjugates of the present invention provides the cost and time effective process, as compared to other processes of the prior art
W092/16555 describes the reaction of ovalbumin at the carboxyl or carbohydrate group with PEO-hydrazide containing amino acid spacer. However, it only describes the coiyugates with a number of PEG molecules attached without mentioning a method of preparation for conjugates of biologically active materials with biocompatible polymers with the ratio of 1:1, and the biological activity of conjugates.
Also, US patem No 5,824,779 describes linkage of PEG to the carboxyl group of G-CSF but the conjugate prepared according to their method had very low activity because several PEG molecules were randomly attached to aspartic acids or glutamic acids of G-CSF.
There have been problems to control the reaction condition for specific
linkage or the number of attaching polymers using the difference in reactivity according to pKa of amino acids.
When an attempt was made to react the amino group of lysine in the range of pH 7 to 8, the histidioe groups also reacted randomly. And, when pH was lowered to about 6 to 6.5, histidine groups became more reactive with PEG than lysine groups(US Patent No. 5,951,974 and US Patent No. 5,985,263). Inventors of the present invention observed that PEG can be attached to carboxyl groups, especially C-terminus of biologically active materials at a ratio of 1:1 at pH equal to or lower than 3 according to the above method.
Therefore in one aspect, the present invention relates to the conjugate of biocompatible polymer-biologically active material, wherein the biocompatible polymer is conjugated to the C-terminus of the biologically active material at a molarratio of 1:1.
In another aspect, the present invention relates to a pharmaceutical composition comprising a pharmaceutically acceptable amoimt of the conjugate, wherein the biocompatible polymer is conjugated to the C-tenninus of the biologically active material at a molar ratio of 1:1 and pharmaceutically acceptable carriers.
In another further aspect, the present invention relates to a method of preparation of conjugate of biocompatible polymer-biologically active material at the C-terminus of the biologically active material with a molar ratio of 1:1, comprising the step of conjugating the biologically active material to the activated the biocompatible polymer with the stepwise addition of coupling reagent under the condition wherein the molar ratio of biologically active material to activated
the biocompatible polymer is 1:1 to 1:20, the ratio of biologically active material to the coupling reagent is 1:1 to 1:50, and pH is in the range of 2 to 5.
Biocompatible Polymers
The term "conjugating material" used for conjugation of biologically active molecules means any biocompatible polymer which can be linked to biologically active molecules such as natural or synthetic polymers.
The term "biocompatibility" means biocompatible with living tissues or systems, and being nontoxic, noninflammatory, and noncarcinogenic without causing harm, inflammation, immune response and carcinogenesis in the body.
Biocompatible polymers are conjugated with biologically active materials. The useful polymers of the present invention are readily soluble in various solvents and have molecular weight of between about 300 and about 100,000 Da and preferably between about 2,000 and about 40,000 Da. The biocompatible polymers include, but are not limited to, polyethylene glycol (PEG), polypropylene glycol (PPG), polyoxyethylene (POE), polytrimethylene glycol, polylaetic acid and its derivatives, polyacrylic acid and its derivatives, polyamino acid, polyvinylalcohol, poiyurethane, polyphosphazene, poly(L-lysinc), polyalkylene oxide (PAO), polysaccharide, dextran, polyvinyl pyrrolidone, polyacrylamide, copolymers thereof and other noninmnmogenic polymers.
Biocompatible polymers of the present invention are intended to include not only linear polymers but also polymers as follows. Biocompatible polymers of the present invention include soluble, non-antigenic polymers linked to an
activated functional group that is capable of being nucleophilically substituted through an aliphatic linker residue (US patent No. 5,643,575 and 5,919,455). Also, biocompatible polymers of the present invention include multi-armed, mono-functional and hydrolytically stable polymers, having two linker fragments which have polymer arms around a central carbon atom, a residue which is capable of being activated for attachment to biologically active materials such as proteins, and side chains which can be hydrogen or methyl group, or other linker fragment(US Patent No. 5,932,462). In addition, biocompatible polymers of the present invention include polymers of branched PEG in which the functional groups of polymers are attached to biologically active materials via linker arms having reporter residues(WO 00/33881).
Among them, PEG is one of the most common biocompatible polymers of the present invention. In general, PEG is a nontoxic hydrophilic polymer having the repeating unit, HO-(CH2CH2O)n-H. Various proteins are reported to show-extended half-lives, increased solubility, increased stability, and reduced immunogenicity in plasma when being conjugated with PEG
The range of molecular weight of PEG molecules conjugated to biologically active materials such as proteins or peptides is from about 1,000 to 100,000 Da and the toxicity of PEG over 1,000 Da is known to be very low. PEGs in the range of from 1,000 to 6.000 Da are distributed to the whole body and cleared in the kidney. Branched PEG with molecular weight of 40,000 Da are distributed in blood or organs including the over, and metabolized in the liver.
PEG is the most preferable biocompatible polymer because PEG is
commercially available in the various molecular weight ranges, each oxyethylene unit is hydrophilic to be accessible to bind 2-3 water molecules, PEG derivatives with one-terminal functional group from methoxy polyethylene glycol are easy to synthesize, PEG has very low risk of antigen-antibody reaction, and the related technology is well developed.
Biologicallv active materials
The term "biologically active molecule" means all nucleophiles conjugated with activated biocompatible polymers, and which retain at least some of their biological activity after conjugation. The term "biologically activity" used herein is not limited by physiological or pharmacological activity. For example, some conjugates of aucleopfailic containing enzymes can catalyze reactions in organic solvents. Similarly, some polymer coigugates including proteins such as Con-canavalin A, or immunoglobulin can also be used in diagnostics in the laboratory. In general, biologically active molecules can be isolated firom nature or synthesized recombinantly or chemically, and include proteins, peptides, polypeptides, enzymes, biomedicincs, genes, plasmids, or organic residues.
Proteins, peptides, and polypeptides of interest include, but are not limited to, hemoglobin, serum proteins(for example, blood factors including Factor VII, VIII, and IX), immunoglobulins, cytokines(for example, interleukins), a-, P- and 7-interferons, colony stimulating factors including G-CSF and GM-CSF, platelet derived growth factor(PDGF), phospholipase-activating protein(PLAP), and parathyroid hormone(PTH). Other proteins of general biological or therapeutic interest include insulin, plant proteins (for example, lectins and ricins), tumor
necrosis factors(TNF) and related alleles, growth factors(for example, tissue growth factors such as TOFa and TGFP and epidermal growth factors), hormones (for example, follicle-stimulating hormone, thyroid-stimulating hormone, antidiuretic hormones, pigmentary hormones, luteal hormone-releasing hormone and derivatives thereof), calcitonin, calcitonin gene related peptide(CGRP), synthetic enkephalin, somatomedins, erythropoietin, hypothalamic releasing factors, prolactin, chorionic gonadotropin, tissue plasminogen activator, growth hormone releasing peptide(OHRP), thymic humoral factor(THF) and the like. Immunoglobulins of interest include IgG, IgE, IgM, IgA, IgD, and fragments thereof
When two or more biocompatible polymers are attached to especially low molecular weight polypeptides such as Interferon and G-CSF, these conjugates exhibit considerably low biological activity. Also, two or more polymers are attached when relatively highly reactive amino groups are conjugated and thus the separation of conjugates in a 1:1 complex is not easy. However, the present invention provides the selective preparation of conjugates of biocompatible polymer-IFN or biocompatible polymer-G-CSF in a 1:1 complex, wherein these conjugates show high biological activity, increased half-life, and excellent bioavailibility.
The biologcaily active materials of the present invention also mclude any portion of a polypeptide demonstrating in vivo bioactivity. This includes amino acid sequences, antisense oligomers, antibody fragments, linear antigen(Ref. US Patent 4,946,778), binding molecules including fusions of antibodies or fragments, polyclonal antibodies, monoclonal antibodies, catalytic antibodies, nucleotides.
oligonucleotides.
The biologically active materials also include enzymes. Enzymes of interest include carbobydrate'Specific enzymes, proteolytic enzymes, oxidoreductases, transferases, hydrolases, lyases, isomerases and ligases. Without being limited to particular enzymes, examples of enzymes of interest include asparaginase, arginase, arginine deaminase, adenosine deaminase, superoxide dismutase, endotoxinases, catalases, chymotrypsin. Upases, uiicases, adenosine diphosphatase, tyrosinases and bilirubin oxidase. Carbohydrate-specific enzymes of interest include glucose oxidases, glucosidases, galactosidases, glucocerebrosidases, glucouronidases, etc.
Examples described above are examples of suitable biologically active nucleophiles conjugated with activated biocompatible polymers of the present invention. All suitable biologically active materials with nuclcophilic group are to be also included in the present invention although they are not mentioned above. The biologically active materials for the present invention need to possess at least one free carboxyl group for conjugation by polymer.
The conjugates of the present invention are biologically active for the purpose of therapeutic ^plication. Mammals can be treated by administering the therapeutically effective dose of polymer conjugates containing biologically active materials.
Preparation of biocompatible polvmer-biologifcallv active material conjugates
To conjugate biocompatible polymers to the biologically active molecules, one of the end groups of polymers is converted into a reactive functional
group. This process is referred to as "activation" and the product is called an "activated" polymer. For instance, to conjugate poly(alkylene oxides, PAO) to peptides or proteins, one of the hydroxyl end groups of the polymer can be converted into a reactive functional group such as carbonate and activated PAO is produced, which is soluble at room temperature. This group includes mono substituted poly(aIkylcnc oxide) derivatives such as mPEG or other suitable alkyl-substitute PAO derivatives containing C1-4 end group.
The term "reactive functional group" used in the art and herein is the group or the residue activating biocompatible polymers to bind with biologically active materials.
The reactive functional group of the present invention is selected from the functional groups able to react with carboxylic acid and reactive carbonyl group, for example, primary amine, or hydrazine and hydrazide functional groups (such as acyl hydrazide, carbazate, semicarbazate, thiocarbazate etc.).
The term "coupling reagent of carboxyl group"(hereinaft6r referred to as coupling reagent) used in the art and herein means any reagent to couple the carboxyl groups of biologically active materials to biocompatible polymers which have been activated at the above reactive functional group.
rhe coi^ling reagents of the carboxyl group in the present invention of
interest include, but are not limited to, carbodiimidyl coupling agents, for example,
EDAC[N-(3-dimethyl-aminopropyl)-N'-ethylcarbodiimide hydrochloride],
DIC[l,3-diisopropyl carbodiimide], DCC[dicyclohexyl carbodiimide], and EDC[1-ethyl-3-(3-dimethylamino propyl)-carbodiimidc]. The preferable coupling agent [for the carboxyl group is EDAC.
The method of preparing the conjugates of the present invention includes the step of reacting biologically active molecules containing nucleophiles capable of performing the substitution reaction with activated biocompatible polymers under the condition in which sufficient conjugation can be possible while retaining at least a portion of intrinsic bioactivity of biologically active molecules.
The biologically active material-biocompatible polymer conjugates with a
ratio of 1:1 are obtained by reacting the biologically active materials with a
stoichiometric excess amount of polymers. For example, in the preparation of
protein-polymer, peptide-polyraer, enzyme-polymer, antibody-polymer, and drug-
polymer conjugates, the molar ratio of biologically active material to
biocompatible polymer is in the range of from about 1:1 to 1:20, more preferably
from 1:1 to 1:10. The reagents to activate carboxyl groups of biologically active
materials are selected from the group as follows, but are not limited to them. For
example, N-(3-dimethyl-aminopropyl) -N'-ethylcarbodiimide
hydrochloride(EDAC), water soluble carbodiiraide group such as 3-[2-morpholinyl-(4)-ethyl], and 5-substituted isoxazolinium salts such as p-toluene sulfonate, Woodward's Reagent K.
The molar ratio of biologically active materials to EDAC used in the present invention is in the range of from about 1:1 to 1:50, more preferably from about 1:1 to 1:30, and most preferably from about 1:1 to 1:20. However, increased yield of PEG-biologically active material conjugates was observed when the addition of EDAC was divided to more than 5 times, preferably 5 or 6 times rather than adding 20-fold molar excess of EDAC at once because EDAC is readily hydrolyzed in aqueous solution.
The conjugation reaction of biologically active materials with activated polymers is dependent on the pH of water soluble solvents functioning as a buffer. In general, the pH of reaction buffer for proteins/polypeptides is in the range from 2 to 5, preferably from 2.5 to 4.5. The optimum reaction condition for stabilization of these substances and reaction yield has been known in the art. The suitable temperature for the conjugation reaction is in the range of 0 to 60 V. and preferably in the range of 4 to 30 °C. The temperature of the solvents should not exceed the denaturation temperature of proteins or peptides. Also, the reaction time of 10 minutes to 5 hours is preferable in this preparation. The conjugates prepared can be recovered and purified by column chromatography, diafiltration or a combination of above two processes.
Pharmaceutical Composition
The present invention also relates to a pharmaceutical composition comprising a therapeutically effective dose of the activated biocompatible polymer-biologically active material conjugates as an active ingredient.
The term "pharmaceutically acceptable" used in the art and herein means not causing allergic reaction or similar reaction when administered to humans.
The biocompatible polymer-biologically active material conjugate as an active ingredient of the phannaceutieal composition can be used itself or formulated in combination with pharmaceuticaUy acceptable carriers for disease prevention and treatment.
The term "pharmaccutically acceptable carrier" used in the art and herein means pharmaccutically acceptable molecules, composition, or vehicles such as
solutions, diluents, excipients, or solvents to carry the biologically active materials from one organ or tissues to other organs or tissues. The pharmaceutical composition of the present invention can be administered by the route of oral, local, injection or parenteral route and its formulation include therapeutically effective doses of the biocompatibie polymer-biologically active material coiyugates as an active ingredient, The formulation for oral administration of the present invention include pills, tablets, coated tablets, granules, troches, wafws, elixirs, hard and soft gelatin capsules, solutions, syrups, emulsions, suspensions, or sprays etc. and for parenteral administration, injectable solutions, microcapsules, patches, and others are included.
The pharmaceutical formulation can be prepared according to the known method by using pharmaceutically acceptable inactive inorganic or oragnic additives. For example, lactose, com starch and its derivatives, talc, or stearic acid and its salts can be used to prepare pills, tablets, and hard gelatin capsules. The additives of soft gelatin capsules and suppositories are for example, oil, wax, semi-solid or liquid polyol, and natural or solidified oil. The suitable additives for preparation of solution or syrup are for example, water, sucrose, invertase, glucose, and polyol. The suitable additives for preparation of injectable solution are water, alcohol, glycerol, polyol, plant oil etc. The injectable solution can be used as the combination of preservatives, indolent agents, solubilizers, and stabilizers. The formulation for local administration can be also used as the combination of gas, diluents, lubricants, and preservatives. The suitable additives for microcapsules or translantation are copolymer or glycolic acid and lactic acid.
The dose of the biocompatible polymer-biologically active material
conjugates of the present invention varies depending on the absorption rate of the biologically active materials, solubility, patient's age, sex, condition and severity of diseases, etc. as well known in the art.
Particularly, the administration of biocompatible polymer-biologically active material conjugates of the present invention reduces the injection intervals from daily or once per two days to weekly or biweekly injection. Therefore, the toxicity and site effects of drugs by frequent administration are reduced substantially.
The following examples further describe and demonstrate embodiments within the scope of the present invention. The examples are given solely for the purpose of illustration and are not to intended limit the present invention, as many variations thereof are possible without departing from the spirit and scope of the invention.
Examples
1. Preparation of biocompatible Dolvmer-bioloizicallv active material conjugates via a carboxvl group of biologically active material
Preparation of mPEG(12000)-Hz-G-CSF conjugate
1 mg of G-CSF solution(0.00005 mmol. Dong-A Pharm. LEUCOSTIM) was dialyzed(Centricon-10, Amicon, USA) against 50 mM MES buffer solution (pH 3.0) to the final concentration of 2 mg/ml. To this protein solution. 6.6 mg of mPEG(12000)-Hz(ISU Chemical, Korea, 0.0005 mmol) was added and followed
by 2ul (0.001 mmol, 20-fold molar excess) of ED AC solution prepared by dissolving 2 mg of ED AC in 20 ul of d-HiO. The reaction was carried out for 1 hour at room temperature(20-25t;) with stirring. After 1 hour, unreacted G-CSF and excess reagent were removed by size exclusion column or ion-exchange column. More than 0.3 mg of mPEG(12000)-Hz-G-CSF conjugate was obtained. By changing the amount of EDAC from 20 to 200-fold molar excess and mPEG(12000)-H2 from 10 to 20-fold molar excess, the reaction was repeated. It was observed that two or more raPEG(12000)-Hz were attached to the carboxyl group of G-CSF when the amount of EDAC is over 50-fold molar excess.
Preparation of mPEG(5000)-Hz-G-CSF conjugate
1 mg of G-CSF solution(0.00005 mmol) was dialyzed(Centricon-10, Amicon, USA) against 50 mM MES buffer soiution(pH 3.0) to the final concentration of 5 mg/ml. To this protein solution, 1.3 mg of mPEG(5000)-Hz(ISU Chemical, Korea, 0.00025 mmol) was added, followed by 2ul(0.001 nmiol, 20-fold molar excess) of EDAC solution prepared by dissolving 2 mg of EDAC in 20 ul of d-HaO. The reaction was carried out for 1 hour at room temperature(20-251) with stirring. After 1 hour, unreacted G-CSF and excess reagent were removed by size exclusion columm or ion-exchange column. More than 0.3 mg of mPEG(5000)-Hz-G-CSF was obtained FIG. 1 shows the production of mPEG(5000)-Hz-G-CSF conjugate by SDS-FAGE and HPLC profile (size exclusion chromatography).
Preparation of mPEG(20000)-Hz-G-CSF conjugate
1 tng of G-CSF solution(0.00005 mmol) was dialyzed against 50 mM MES buffer solution(pH 3.0) by ultrafiltration(Centricon-10, Amicon, USA) to the final concentration of 5 mg/ml. To this protein solution, 5 mg of mPEG(20000)-Hz(lSU Chemical, Korea, 0.00025 mmol) was added, followed by 2ul(0.001 mmol, 20-fold molar excess) of ED AC solution prepared by dissolving 2 mg of ED AC in 20 ul of d-H2O. The reaction was carried out for 1 hour at room temperature(20-251)) with stirring. After 1 hour, imreacted G-CSF and excess reagent were removed by size exclusion coluron or ion-exchange column. More than 0.3 mg of mPEG(20000)-Hz-G-CSF;, was obtained. FIG 2 shows the production of mPEG(20000)-Hz-G-CSF conjugate by SDS-PAGE.
Preparation of mPEG(5000)-Hz-IFN conjugate
Four tubes each containing 200 ug of IFN solution(0.00001 rmnol, Korea Green Cross Corp., Green Alpha) were dialy2ed(Centricon-10, Amicon, USA) respectively, against 50 mM MES buffer solution(pH 3.0) to the final concentration of 1 mg/ml. To each tube, 2.16 mg of mPEG(5000)-HZ was added, followed by 0.8 ul(40-fold molar excess) of EDAC solution prepared by dissolving 2 mg of EDAC in 20 ul of d-HaO. The reaction was carried out for 1 hour at room temperature(20-25t;) with stirring. After 1 hour, unreacted IFN and excess reagent were removed by size exclusion column or ion-exchange column. FIG 3 shows the conjugation of mPEG(5000)-HZ to ffN molecules by SDS-PAGE.
Preparation of mPEG(12000)-Hz-IFN conjugate
I mg ot IFNsolution (0.00005 mmol) was dialyzed(Centricon-10, Amicon, USA) against 50 mM MES buffer solution(pH 3.0) to the final concentration of 1 mg/ml. To this protein solution, 6.6 mg of mPEG(12000)-H2(0.0005 mmol) was added, followed by 2µl(0.001 mmol, 20-fold molar excess) of ED AC solution prepared by dissolving 2 mg of EDAC in 20 ul of d-HaO. The reaction was carried out for 1 hour at room temperature(20-25°C) with stirring. After 1 hour, unreacted IFN and excess recent were removed by size exclusion column or ion-exchange column. More than 0.3 mg of mPEG(12000)-Hz-IFN was obtained.
Preparation of mPEO(20000)-Hz-IFN conjugate
Four tubes containing 200 ug of IFN solution(0.00001 mmol) in each tube were dialyzed(Centricon-10, Amicon, USA) against 50 mM MES buffer solution(pH 3.0) to the final concentration of 2 mg/ml. To each tube, 4.32 mg of mPEG(20000)-Hz(0.0002 mmol, ISU Chemical, Korea) was added, followed by 1 ul(50-fold molar excess) or 4 ul(200-fold molar excess) of EDAC solution prepared by dissolving 2 mg of EDAC in 20 ul of d-H2O. In addition, 30-fold molar excess of sulfo-NHS was added to accelerate the reaction and the results were compared. The reaction was carrired out for 1 hour at room temperature(20-251°C with stirring. The reaction condition of each sample is described in the table below. After 1 hour, unreacted IFN and excess reagent were removed by size exclusion column or ion-exchange column. The yield of each reaction was compared by SDS-PAGE.
(Table Removed)
As a result, the reaction with 200-fold molar excess of ED AC showed that too many PEOs were attached to the carboxyl group of IFN and separation of the PEG-IFN conjugate with the molar ratio of 1:1 was not successful and estimation of the number of PEOs attached was not easy. Also, the reaction with 50-fold molar excess of ED AC proceeded but PEG-IFN conjugate with the ratio of 1:1 was not readily distinguishable because the PEO-IFN conjugate was diffused on SDS-PAGE due to the excess amount of ED AC used. When sulfo-NHS was added to the reaction to enhance the efficiency, there was no difference from a control in which sulfo-NHS was not odded(FIG 4).
Also, the reaction efficiency upon adding EDAC several times was performed according to reaction conditions as described in the table below.
(Table Removed)
As a result, when EDAC was added stepwise to the reaction mixture, the yield of mPEG-Hz-IFN conjugate with the molar ratio of 1:1 was high(FIG 5). When the amount of EDAC was over 50-fold molar excess although addition of EDAC was performed stepwise, two or more PEGs were randomly attached to the IFN as shown in FIG 5.
Preparation of mPBG(20000)-Hz-IFN conjugate
1 mg of IFN solution(0.00005 mmol) was dialyzed(Centricon-10(Amicon, USA)) against 50 mM MES buffer solution(pH 2.5) to the final concentration of 5 mg/mi. To this protein solution, 10.8 mg of mPEG(20000)-Hz(0.0005 mmol, 10-fold molar excess) was added, followed by 2 M(0.001 mmol, 20-fold molar excess) of EDAC solution prepared by dissolving 2 mg of EDAC in 20 ul of d-H2O. The reaction was carried out for I hour at room temperature(20-25t;) with stirring. After 1 hour, unreacted IFN and excess reagent were removed by size exclusion column or ion-exchange column. More than 0.3 mg of mPEG(20000)-Hz-IFN conjuate was obtained.
Purification of mPEG(20000)-Hz-IFN conjugates with the molar ratio of 1:1.
mPEG(20000)-H2-lFN conjugate(Example 6) was diluted with lOmM sodium acetate buffer(pH4.4) to the final concentration of 1
rag/ml. mPEG(20000)-Hz-IFN reaction mixture was loaded onto SP-sepharose Fast Flow column(5 x 50 mm, total 1 ml column vol.), which had been previously equilibrated with 10 mM sodium acetate buffer 3olution(pH 4.4). After washing the column with 3 column volumes of 10 mM acetate buffer(pH 4.4), a gradient of 10 mM acetate buffer(pH 4.4) containing 500 mM NaCl was used to separate mPEO(20000)-Hz-IFN with the molar ratio of 1:1 from unreacted intact IFN. The above purified mPEG(20000>Hz-IFN was confirmed to be the conjugate wherein one PEG was attached to the carboxyl group of IFN(FIG 6).
Determination of Biological activity of PEG-0-CSF conjugate CPE{Cytopalhic effect) assay was performed as follows.
2.5 xl06 cells(5xl0' cells/ml) of M-NFS-60 were sub-cultured on 60mm dishes(RPMI-1640 media, 10% PBS, 37°C, 5% CO2). Each of native G-CSF(contTol) and mPEG(20000)-Hz-G-CSF(Example 3) was diluted to the concentration of1ng/ µl and added to the 96 well plate containing 1 x 104 cells in each well, followed by serial dilution. The plate was incubated at 37t for 2 days. Then each well was treated with 50 µl of XTT ]dt(Roche, Germany) and incubated for another 4 hours at 37°C, and O.D. value of the plate was read at 490 nm using ELISA reader.
As a result, mPEG(20000)-H2-G-CSF of the present invention was shovra to retain a similar activity to mPEG(20000)-G-CSF conjugate, wherein PEG was attached to the amino growth of G-CSF(FIG 7).
Deftermination of half lifs'of PEG-G-CSF conjugate
7-week old Sprague-Dawley rats (5 rats per group) weighing 220-240g were anesthetized using Kctamin/Rompun and a PE tube was inserted to the vena cava of each rat by surgery. After the rat recovered, 100 µg/kg of mPEG(20000)-Hz-G-CSF(Example 3) was administered through intravenous injection. PBS and 100 ug/kg of native G-CSF were used as placebo and control, respectively, for comparison.
300 ul of blood was withdrawn through the cannula at time intervals of 0, 0.5, 1, 2, 4, 6, 12, 24, and 48 hours after injection. The serum was separated by centrifugation{ 13,000 rpm, 10 min, 4 °C and stored at -20 °C for further study.
After incubation the cells for 24 hours with G-CSF free media, each well of 96 well plate was added with 1.5 x 104 cells. Each scrum sample stored as described above was diluted 100 times and 50 ul of the diluted samples was added to each well of 96 well plate. The dishes were incubated at 37 °C for 48 hours under CO2 gas. Then each well was treated with 50 µl of XTT kit(Roche, Germany). Plates were incubated for another 4 hours at 37 °C and the O.D. value of the plate was read at 490 mn using an ELISA reader.
The half-hfe of mPEG(20000)-Hz-G-CSF(Example 3) is compared to that of native G-CSF and Neulasta™ (PEG attached to N-terminal of G-CSF, Amgen) in FIQ 8. mPEG(20000)-Hz-G-CSF(Exanaple 3) of the present invention showed a much longer half-life compared to native G-CSF, and has similar half-life to that of NeulastaTM
Determination of White Blood Cell (WBC) count of PEG-G-CSF-treated rats
7-week old Sprague-Dawley rats weighing 220-24Gg were purchased from Charles River Co.(Atsugi, Japan). 100 ug/kg of mPEG(20000)-Hz-G-CSF (Example 3) was injected to the tail vein of rats. The same amount of native G-CSF and saline solution was injected respectively as a control. Blood samples were withdrawn at time intervals of 0, 6, 12, 24, 48, 72, 96 hrs after injection through the tail vein. WBC count was measured by Automated Hematology Analyzer {Cysmex K-4500) as shown in FIG. 9. As a result, mPEG(20000)-Hz-G-CSF of the present invention showed higher WBC counts than both native G-CSF and Neulasta™.
Determination of biological activity of PEG-IFN conjugate
MDBK cells counted in a concentration of 7.5x105 cells/ml using a hemocytometer, were suspended in 5% FBS/MEM media. mPEG(12000)-Hz-IFN(Example 5) was diluted to the concentration of 100IU(1 mg/ml = 2 X 108 lU). Each well was supplemented with l00ul of 5% FBS/MEM media and 100 ul of the diluted samples was added to the first well followed by serial dilution. Then 100 ul of cell suspension was added to each well of 96 well plate. The dishes were incubated at 37°C for 20 hours. 100 ul of Vesicular Stomatitis Virus(VSV, ATCC VR-158) diluted 100 times was added to each well and incubated another 20 hours at 37 °C. The growth medium solution containing Vesicular Stomatitis Virus(VSV, ATCC VR-158) of 96 well plate was removed, 50 ul of 0.05 % crystal violet dye solution was added to each well, and O.D. of each well was read at 550nm by ELISA reader to determine the activity of IFN. As a result, the activity of mPEG(12000)-Hz-IFN (Example 5) was found to
retain 40-50 % of native DFN activity and showed activity similar to that of the comparative PEG-IFN(Schering-Pbugh, USA, PEG attached to amino group of IFN. approved by FDAKFiG 10).
Also, the activity of niPEG(20000)-Hz-IFN (Example 6) was determined to be approximately 40 % of native IFN(FIG 11).
Also, the activity of Di-mPEG-Hz-IFN(Two PEGs attached to one IFN) and mono-PEG-IFN(l:l complex, one PEG attached to one IFN) was compared by CPE assay and mono-mPEG-Hz-IFN showed high biological activity(FIG 12).
Determination of half-life of PEO-IFN conjugate
MDBK cells counted in a concentration of 7.5x10 °C cells/mt were suspended in 5% FBS/MEM media. 100 ul of cell suspension was put in each well of 96 well plate. Scrum was obtained after injecting mPEG(20000)-Hz-INF(Examplc 6) by intravenous route to rats and diluted 50 times. Each well was added with the diluted serum and incubated in a CO2 incubator for 20 hours.
Each well was added with 100-fold diluted Vesicular Stomatitis viius(100 ul) and incubated continued for aiwther 20 hours. The virus medium solution in each well was removed, and 50 ui of 0.05 % crystal violet dye solution was added to each well. The absorbance at 550 nm was read by a Microplate reader to measure the half life of IFN. FIG. 13 shows the half-life of mPEG(20000)-Hz-IFN(ExampIc 6) conjugated at the carboxyl group and comparison of mPEG(20000)-Hz-IFN with native IFN and comparative product, PEG-IFN. mPEG(20000)-H2-IFN of the present invention showed a much greater half-life than native IFN and longer half-life than the comparative product, PEG-EFN.
Stability of PEG-IFN conjugate
The stability of mPEG(20000)-Hz-IFN prepared and purified in Example 6 and PEG-IFN, wherein branched PEG(10lC)2-NHS(attached to the amino group of IFN according to the general method in the literature followed by separating mono PEG-IFN by size exclusion column, Nektar, USA) was determined on SDS-PAGE after incubation at 4 °C in PBS solution by observing the dissociation of intact IFN on the SDS-PAGE. The concentration of each sample was adjusted to the final concentration of 1mg/ml. As a result, it was observed that about 14 % of intact IFN was dissociated from the PEG-IFN conjugated through the amino group of IFN about 2 weeks later, whereas the dissociation of IFN from PEG(20000)-H2-IFN conjugated through the carboxyl group of IFN of the present invention was not detected even after 6 months later(FIG 14).
Preparation of mPEG(5000)-Hz-PTH conjugate
1 mg of human PTH(parathyroid hormone, 0.00012 mmol, 1-84 aa, Dong-Kook Pharm., Korea) and 3.0 mg of activated mPEG(5000)-Hz(0.0006 mmol, ISU Chemical, Korea) in 0.5 ml of 50 mM MES buffer solution, pH 4.4 were reacted for 10 minutes with stirring at room temperature. 2.5 ul of EDAC(0.00125 mmol, 10-fold molar excess) prepared at a concentration of 100 ug/ul, was then added and reacted for 1 hour with stirring at room temperature. Unreacted mPEG(5000)-Hz and PTH were removed by using Centricon-IO(Amicon, USA) and 0.4 mg of mPEG(5000)-Hz-PTH was obtained.
Preparation of mPEG(12000)-Hz-PTH Conjugates
1 mg of human PTH(0.00012 mmol) and 7.14 mg of activated mPEG(12000)-Hz(0.0006 nmiol, 5 fold molar excess, ISU Chemical, Korea) m 0.5 ml of 50 mM MES buffer solution, pH 4.4 were reacted for 10 minutes with stirring at room temperature. 2.5 ul of EDAC(0.00125 mmol, 10-foid molar excess) prepared at a concentration of 100 ug/ul, was then added and reacted for 1 hour with stirring at room tanperature. Unreacted mPEG(12000)-Hz and PTH were removed by using Centricon-l0(Amicon, USA) aad 0.3 mg of mPEG(12000)-Hz-PTH was obtained.
Preparation of mPBG(20000)-Hz-PTH Conjugates
1 mg of human PTH(0.00012 mmol) and 12 mg of activated mPEG(20000)-Hz(0.0006 mmol, 5 fold molar excess, ISU Chemical, Korea) in 0.5 ml of 50 mM MES buffer solution, pH 4.4 were reacted for 10 minutes with stirring at room temperature. 2.5 ul of EDAC(0.00125 mmol, 10-fold molar excess) prepared at a concentration of 100 ug/ul, was then added and reacted for 1 hour with stirring at room temperature. Unreacted mPEG(20000)-Hz and PTH were removed by using Ccntricon-30(Amicon, USA) and 0.3 rag of mPEG(20000)-Hz-PTH was obtained.
Prq)aration of mPEG(12000)-Hz-PTH conjugate
1 mg of human PTH(0.00012 mmol) and 14.4 mg of activated mPEG(12000)-H2(0.0012 mmol, 10 fold molar excess, ISU Chemical, Korea) in 0.5 ml of 50 mM MES buffer solution, pH 2.5 were reacted for 10 minutes with
stirring at room temperature. 5 ul of EDAC(0.0025 mmol, 20-fold molar excess) prepared at a concentration of 100 ug/ul, was then added and reacted for 1 hour with stirring at room temperature. Unreacted mPEG(12000)-Hz and PTH were removed by using Centricon-10(Amicon, USA) and 0.2 mg of mPEG(12000)-Hz-PTH was obtained.
Preparation of mPEG 1 mg of human PTH(0.00012 mmol) and 24 mg of activated mPEG(20000)-Hz(0.0012 mmol, 10-fold molar excess, ISU Chemical, Korea) in 0.5 ml of 50 mM MES buffer solution, pH 2.5 were reacted for 10 minutes with stirring at room temperature. 5 ul of EDAC(0.0025 mmol, 20-fold molar excess) prpared at a concentration of 100 ug/ul, was then added and reacted for 1 hour with stirring at room temperature. Unreacted mPEG(20000)-H2 and PTH were removed by using centricon-10(Amicon, USA) and 0.2 mg of mPEG(20000)-Hz-PTH was obtained.
Analysis of mPEG-Hz-PTH conjugate
PEG-PTH conjugate and native PTH which were obtained from the above examples were determined as following HPLC condition.
Elutiag Condition of HPLC
Column: LiChroCART 125-4 RP-8 (5 umXMerck, USA) Solvent: A; deionized water containing 0.1 % TFA, B; acetonitrile containing 0.1 % TFA
Flow rate: 0.8 ml/min Detector: UV detector at 220nm Injection volume: 20 ul
(Table Removed)
By using LiChroCART 125-4 RP-8 (5 um) for HPLC, only PTH and other proteins were detwted at 220nm whereas no PEG was detected at 220nm. The RT of PTH was determined by HPLC. A sharp peak of PTH which is not modified by the polymer was seen around 6.8 min, then slowly increased up to about 18 min, and decreased again(FIG 15).
mPEG-Hz-PTH prepared as described above was eluted at 6.8 min for unieacted PTH and 7.3 min for PEG-PTH, respectively, in the range of the elution conditions between number 1 and 2 in the above table.
There are three kinds of productsCunreacted PTH, mPEG(20000)-Hz-PTH, mPEG(20000)-Hz) present immediately after the conjugation and before purification. Only two peaks, unreacted PTH and mPEG(20000)-Hz-PTH conjugate, were detected at 220 nm on HPLC while unreacted mPEG(20000)-Hz was not detected at 220 nm(FIG 16).
FIG 17 shows the finally purified mPEG{20000)-Hz-PTH on HPLC and FIG. 18 SDS-PAGE stained with Coomassie blue performed after reacting mPEG(20000)-Hz with PTH.
Determinatiott of in vitro biological activity of mPEG-PTH Conjugate
The activated mPEG-Hz having molecular weights of 5000(5K), 12000(12K), and 20000(20K) were used to determine the biological activity according to molecular weight of PEG The in vitro biological activity of native PTH, mPEG(5000)-Hz-PTH, mPEG(12000)-Hz-PTH, and mPEG20000)-Hz-PTH was compared by determining the amount of c-AMP synthesized by c-AMP kit(Amersham Pharmacia, RPN 225, USA) using UMR-106 cell line. It was found that the biological activity of mPEG-Hz-PTH was decreased as molecular weight of PEG increased. It was also found that mPEG(5000)-Hz-PTH, mPEG{12000)-Hz-PTH. and mPEG(20000)-Hz-PTH at the concentration of l0-8 mole retained 40%, 30%, and 20 % activity of unreacted PTH, respectively(FIG 19).
Determination of half-life of mPEG-Hz-PTH
100 ug/kg of PTH and mPEG-Hz-PTH was administered through intraveneous injection, respectively to each of male rats weighing 300-350g. Blood was then withdrawn through the cannula at time mtervals of 0, 5, 10, 15, 30, 60, and 120 min after injection. The serum was separated by centrifugation(10,000 rpm, 10 min, 4 °C and the half life of mPEG-Hz-PTH was indirectly determined by calculating the concentration of remaining PTH by measuring the concentration of cAMP in plasma using c-AMP kit(Amersham Pharmacia, RPN 225, USA).
As a result, unreacted PTH and mPEG(5000)-Hz-PTH were not detected after 15 mins after administration. However, mPEG(12000)-Hz-PTH and mPEG(20000)-Hz-PTH were detected after 1 hour and 2 hours, respectively, after administration(FIG 20).
Thus, while there have been described the preferred embodiments of the present invention, those skilled in the art will realize that other embodiments can be made without departing from the spirit of the invention, which includes all such further modifications and changes as come within the meaning, true scope of the claims set forth herein and equivalents thereof. The above examples further, describe and demonstrate embodiments within the scope of the present invention. The examples are given solely for the purpose of illustration and are not to be construed as limitations of the present invention, as many variations thereof are possible without departing from the spirit and scope of the invention.
Application of the present invention
The present invention provides the biocompatible polymer-biologically active material conjugates in a molar ratio of 1:1 wherein the biocompatible polymer is attached to a carboxyl group of the biologically active material such as proteins or peptides and method of preparation thereof. These conjugates having the increased bioavailibility and extended half-life due to their increased in vivo stability can reduce the frequency of administration significantly when used as therapeutic drugs for diseases.

We claim:
1. A conjugate of biocompatible polymer-biologically active material, wherein the activated biocompatible polymer is conjugated to a carboxyl group or C-terminus of the biologically active material at a molar ratio of 1:1; wherein the biocompatible polymer is selected from the group consisting of polyethylene glycol, polypropylene glycol, polyoxyethylene, polytrimethylene glycol, polylactic acid and Derivatives thereof, polyacrylic acid and derivatives thereof, poly(amino acid), polyurethane, polyphosphazene, poly(L-lysine), polyalkylene oxide, polysaccharide, dextran, polyvinyl pyrrolidone, polyvinyl alcohol, polyacryl amide, and copolymers thereof; and wherein the biologically active material is selected from the group consisting of a-, p-, A-, y- interferon, parathyroid hormone, asparaginase, arginase, arginine deiminase, adenosine deaminase, superoxide dismutase, endotoxinase, catalase, chymotrypsin, lipase, uricase, adenosine diphosphatase, tyrosinase, glucose oxidase, glucosidase, galactosidase, glucouronidase, hemoglobin, blood factors VII, VIII and IX, immunoglobulin, cytokine, granulocyte colony stimulating factor, granulocyte macrophage colony stimulating factor, platelet derived growth factor, lectin, ricin, tumor necrosis factor, transforming growth factor, epidermal growth factor, calcitonin, insulin, synthetic enkephalin, interleukin, erythropoietin, growth hormone releasing peptide, luteal hormone-releasing hormone and derivatives threreof, hypothalamic releasing factors, calcitonin gene related peptides, thyroid stimulating hormone and thymic humoral factor.
2. The conjugate as claimed in claim 1, wherein the biologically active material is interferon, G-CSF, or parathyroid hormone.
3. A pharmaceutical composition comprising a pharmaceutically acceptable amount of the conjugate claimed in claim 1 and a pharmaceutically acceptable carrier.
4. A method of preparation of the conjugate claimed in claim 1, consisting the steps of:

(a) activating biocompatible polymer with a reactive functional group which is able to react with the carboxyl acid and reactive carbonyl group; and
(b) conjugating biologically active material to the activated biocompatible polymer with the stepwise addition of coupling reagent, said coupling reagent comprising
carbodiimidyl coupling agents, EDAC [N- (3-dimethyl-aminopropyl)-N'-ethylcarbodiimide hydrochloride], DIC [1, 3-diisopropyl carbodiimide], DCC [dicyclohexyl carbodiimide], and EDC [1- ethyl-3- (3-dimethylamino propyl)-carbodiimide], under the condition wherein the molar ratio of the biologically active material to the activated biocompatible polymer is 1:1 to 1:20, the ratio of the biologically active material to said coupling reagent is 1:1 to 1:50, and pH is in the range of 2 to 5.

Documents:

4276-delnp-2005-abstract.pdf

4276-delnp-2005-claims cancelled.pdf

4276-delnp-2005-claims.pdf

4276-delnp-2005-complete specification(granted).pdf

4276-delnp-2005-correspondence-others.pdf

4276-delnp-2005-correspondence-po.pdf

4276-delnp-2005-description (complete).pdf

4276-delnp-2005-drawings.pdf

4276-delnp-2005-form-1.pdf

4276-delnp-2005-form-18.pdf

4276-delnp-2005-form-2.pdf

4276-delnp-2005-form-26.pdf

4276-delnp-2005-form-3.pdf

4276-delnp-2005-form-5.pdf

4276-delnp-2005-pct-210.pdf

4276-delnp-2005-petition-137.pdf

4276-delnp-2005-petition-138.pdf

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Patent Number

240098

Indian Patent Application Number

4276/DELNP/2005

PG Journal Number

30/04/2010

Publication Date

30-Apr-2010

Grant Date

27-Apr-2010

Date of Filing

22-Sep-2005

Name of Patentee

BIOPOLYMED INC

Applicant Address

711, KOREA TECHNOCOMPLEX, 126-16, 5-GA, ANAM-DONG, SUNGBUK-GU, SEOUL 136-701 (KR).

Inventors:

#	Inventor's Name	Inventor's Address
1	PARK, MYUNG-OK	#107-1403 HAKYULCHUNGGU APT., HAGYE-DONG, NOWON-GU, SEOUL 139-230 (KR)

PCT International Classification Number

A61K 47/48

PCT International Application Number

PCT/KR2004/000701

PCT International Filing date

2004-03-27

PCT Conventions:

#	PCT Application Number	Date of Convention	Priority Country
1	10-2004-0007983	2004-02-06	Republic of Korea
2	10-2003-0019734	2003-03-28	Republic of Korea