CA2275587C - Injectable depot gel composition and method of preparing the composition - Google Patents
Injectable depot gel composition and method of preparing the composition Download PDFInfo
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- CA2275587C CA2275587C CA002275587A CA2275587A CA2275587C CA 2275587 C CA2275587 C CA 2275587C CA 002275587 A CA002275587 A CA 002275587A CA 2275587 A CA2275587 A CA 2275587A CA 2275587 C CA2275587 C CA 2275587C
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K9/00—Medicinal preparations characterised by special physical form
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K9/00—Medicinal preparations characterised by special physical form
- A61K9/0012—Galenical forms characterised by the site of application
- A61K9/0019—Injectable compositions; Intramuscular, intravenous, arterial, subcutaneous administration; Compositions to be administered through the skin in an invasive manner
- A61K9/0024—Solid, semi-solid or solidifying implants, which are implanted or injected in body tissue
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K38/00—Medicinal preparations containing peptides
- A61K38/16—Peptides having more than 20 amino acids; Gastrins; Somatostatins; Melanotropins; Derivatives thereof
- A61K38/17—Peptides having more than 20 amino acids; Gastrins; Somatostatins; Melanotropins; Derivatives thereof from animals; from humans
- A61K38/19—Cytokines; Lymphokines; Interferons
- A61K38/21—Interferons [IFN]
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K38/00—Medicinal preparations containing peptides
- A61K38/16—Peptides having more than 20 amino acids; Gastrins; Somatostatins; Melanotropins; Derivatives thereof
- A61K38/17—Peptides having more than 20 amino acids; Gastrins; Somatostatins; Melanotropins; Derivatives thereof from animals; from humans
- A61K38/19—Cytokines; Lymphokines; Interferons
- A61K38/21—Interferons [IFN]
- A61K38/212—IFN-alpha
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K38/00—Medicinal preparations containing peptides
- A61K38/16—Peptides having more than 20 amino acids; Gastrins; Somatostatins; Melanotropins; Derivatives thereof
- A61K38/17—Peptides having more than 20 amino acids; Gastrins; Somatostatins; Melanotropins; Derivatives thereof from animals; from humans
- A61K38/22—Hormones
- A61K38/27—Growth hormone [GH] (Somatotropin)
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K47/00—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient
- A61K47/30—Macromolecular organic or inorganic compounds, e.g. inorganic polyphosphates
- A61K47/34—Macromolecular compounds obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds, e.g. polyesters, polyamino acids, polysiloxanes, polyphosphazines, copolymers of polyalkylene glycol or poloxamers
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K9/00—Medicinal preparations characterised by special physical form
- A61K9/0012—Galenical forms characterised by the site of application
- A61K9/0019—Injectable compositions; Intramuscular, intravenous, arterial, subcutaneous administration; Compositions to be administered through the skin in an invasive manner
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
- A61P41/00—Drugs used in surgical methods, e.g. surgery adjuvants for preventing adhesion or for vitreum substitution
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61P—SPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
- A61P5/00—Drugs for disorders of the endocrine system
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K47/00—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient
- A61K47/02—Inorganic compounds
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K47/00—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient
- A61K47/06—Organic compounds, e.g. natural or synthetic hydrocarbons, polyolefins, mineral oil, petrolatum or ozokerite
- A61K47/08—Organic compounds, e.g. natural or synthetic hydrocarbons, polyolefins, mineral oil, petrolatum or ozokerite containing oxygen, e.g. ethers, acetals, ketones, quinones, aldehydes, peroxides
- A61K47/10—Alcohols; Phenols; Salts thereof, e.g. glycerol; Polyethylene glycols [PEG]; Poloxamers; PEG/POE alkyl ethers
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K47/00—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient
- A61K47/06—Organic compounds, e.g. natural or synthetic hydrocarbons, polyolefins, mineral oil, petrolatum or ozokerite
- A61K47/08—Organic compounds, e.g. natural or synthetic hydrocarbons, polyolefins, mineral oil, petrolatum or ozokerite containing oxygen, e.g. ethers, acetals, ketones, quinones, aldehydes, peroxides
- A61K47/14—Esters of carboxylic acids, e.g. fatty acid monoglycerides, medium-chain triglycerides, parabens or PEG fatty acid esters
Abstract
An injectable depot gel composition containing a polymer, a solvent that can dissolve the polymer and thereby form a viscous gel, a beneficial agent: and an emulsifying agent in the form of a dispersed droplet phase in the viscous gel. The injectable depot gel composition can be prepared by mixing the polymer and the solvent so that the solvent dissolves the polymer and forms a viscous gel. The beneficial agent is dissolved or dispersed in the viscous gel and the emulsifying agent is mixed with the beneficial agent containing viscous gel. The emulsifying agent forms a dispersed droplet phase in the viscous gel to provide the injectable depot gel composition. The injectable depot gel composition can deliver a beneficial agent to a human or animal with a desired release profile.
Description
2 PREPARING T'HE COMPOSITION
BACKGROUND OF THE INVENTION
7 Field of the Invention 9 The present invention relates to a depot gel composition that can be injected into a desired location and which can provide sustained release of a beneficial agent.
11 The present invention also relates to a method of preparing the composition.
13 Description of the Related Art Biodegradable polymers have been used for many years in medical 16 applications. Illustrative devices composed of the biodegradable polymers include 17 sutures, surgical clips, staples, implants, and drug delivery systems. The majority 18 of these biodegradable polymers have been based upon glycoside, lactide, 19 caprolactone, and copolymers thereof.
The biodegradable polymers can be thermoplastic materials which means 21 that they can be heated and formed into various shapes such as fibers, clips, staples, 22 pins, films, etc. Alternatively, they can be thermosetting materials formed by 23 crosslinking reactions which lead to high-molecular-weight materials that do not 24 melt or form flowable liquids at high temperatures.
Although thermoplastic and thermosetting biodegradable polymers have 26 many useful biomedical applications, there are several important limitations to their 27 use in the bodies of various animals including humans, animals, birds, fish, and 1 reptiles. Because these polymers are solids, all instances involving their use have 2 required initially forming the polymeric structures outside the body, followed by 3 insertion of the solid structure into the body. For example, sutures, clips, and 4 staples are all formed from thermoplastic: biodegradable polymers prior to use.
When inserted into the body, they retain their original shape. While this 6 characteristic is essential for some uses, it is a drawback where it is desired that the 7 material flow to fill voids or cavities whc;re it may be most needed.
8 Drug delivery systems using thermoplastic or thermosetting biodegradable 9 polymers also have to be formed outside the body. In such instances, the drug is incorporated into the polymer and the mixture is shaped into a certain form such a I1 cylinder, disc, or fiber for implantation. With such solid implants, the drug 12 delivery system has to be inserted into th~° body through an incision. These 13 incisions are sometimes larger than desired by the medical profession and 14 occasionally lead to a reluctance of the patients to accept such an implant or drug delivery system. Nonetheless, both biodf;gradable and non-biodegradable 16 implantable drug delivery systems have been widely used successfully.
17 One reservoir device having a rate-controlling membrane and zero-order 18 release of an agent that Zs particularly designed for intraoral implantation is 19 described in U.S. Patent No. 5,085,866. The device is prepared from a core that is sprayed with a solution having a polymer and a solvent that is composed of a 21 rapidly evaporating, low boiling point first solvent and a slowly evaporating, high 22 boiling second solvent.
23 Other illustrative osmotic delivery systems include those disclosed in U.S.
24 Patent Nos. 3,797,492, 3,987,790, 4,008,719, 4,865,845, 5,057,318, 5,059,423, 5,112,614, 5,137,727, 5,151,093, 5,234,692, 5,234,693, 5,279,608, and 26 5,336,057. Pulsatile delivery devices are also known which deliver a beneficial 27 agent in a pulsatile manner as disclosed in U.S. Patent Nos. 5,209,746, 5,308,348, 28 and 5,456,679.
1 One way to avoid the incision needed to implant drug delivery systems is to 2 inject them as small particles, microspheres, or microcapsules. For example, U.S.
3 Patent No. 5,019,400 describes the preparation of controlled release microspheres 4 via a very low temperature casting process. These materials may or may not contain a drug which can be released into the body. Although these materials can 6 be injected into the body with a syringe, they do not always satisfy the demand for a 7 biodegradable implant. Because they are: particulate in nature, they do not form a 8 continuous film or solid implant with the structural integrity needed for certain 9 prostheses. When inserted into certain body cavities such as a mouth, a periodontal pocket, the eye, or the vagina where there is considerable fluid flaw, these small 11 particles, microspheres, or microcapsules are poorly retained because of their small 12 size and discontinuous nature. Further, the particles tend to aggregate and thus their 13 behavior is hard to predict. In addition, microspheres or microcapsules prepared 14 from these polymers and containing drugs for release into the body are sometimes difficult to produce on a large scale, and their storage and injection characteristics 16 present problems. Furthermore, one other major limitation of the microcapsule or 17 small-particle system is their lack of reversibility without extensive surgical 18 intervention. That is, if there are complications after they have been injected, it is 19 considerably more difficult to remove them from the body than with solid implants.
A still further limitation on microparticle;s or microcapsuiation is the difficulty in 21 encapsulating protein and DNA-based drugs without degradation caused by solvents 22 and temperature extremes.
23 The art has developed various drug delivery systems in response to the 24 aforementioned challenges. For instance, U.S. Patent No. 4,938,763 and its divisional U.S. Patent No. 5,278,201 relate to a biodegradable polymer for use in 26 providing syringeable, in-situ forming, solid biodegradable implants for animals. In 27 one embodiment, a thermoplastic system is used wherein a non-reactive polymer is 28 dissolved in a biocompatible solvent to form a liquid which is placed in the animal 29 wherein the solvent dissipates to produce the solid implant. Alternatively, a I thermosetting system is used wherein effective amounts of a liquid acrylic ester-2 terminated, biodegradable prepolymer and a curing agent are formed and the liquid 3 mixture is placed within the animal wherein the prepolymer cures to form the solid 4 implant. It is stated that the systems provide a syringeable, solid biodegradable delivery system by the addition of an effective level of a biologically active agent to 6 the liquid before the injection into the animal.
7 U.S. Patent No. 5,242,910 describes a sustained release composition for 8 treating periodontal disease. The composition comprises copolymers of lactide and 9 glycolide, triacetin (as a solvent/plasticizer) and an agent providing relief of oral cavity diseases. The composition can take the form of a gel and can be inserted into 11 a periodontal cavity via a syringe using either a needle or a catheter. As additional 12 optional components, the composition can contain surfactants, flavoring agents, 13 viscosity controlling agents, complexing .agents, antioxidants, other polymers, 14 gums, waxes/oils, and coloring agents. One illustrative viscosity controlling agent set forth in one of the examples is polyethylene glycol 400.
16 With solvent-based depot compositions comprised of a polymer dissolved in 17 a solvent, one problem which exists is that the composition solidifies slowly after 18 injection as solvent diffuses from the depot. Since these compositions need to be 19 non-viscous in order to be injected, a lar~;e percentage of drug is released as the system forms by diffusion of the solvent. This effect is referred to as a "burst"
21 effect. In this respect, it is typical for solvent-based compositions to have a drug 22 burst wherein 30-75 % of the drug contained in the composition is released within 23 one day of the initial injection.
3 The present invention is a significant advance in the art and in one aspect 4 provides an injectable depot gel composition comprising:
5 A) a biocompatible polymer;
6 B) a solvent that dissolves the polymer and forms a viscous gel;
7 C) a beneficial agent; and 8 D) an emulsifying agent in the form of a dispersed droplet phase in the 9 viscous gel.
In a further aspect, the present invention provides a method of preparing an 11 injectable depot gel composition comprising:
12 A) mixing a biocompatible polymer and a solvent whereby the solvent 13 dissolves the polymer and forms a viscous gel;
14 B) dispersing or dissolving a beneficial agent in the viscous gel to form a beneficial agent containing gel; and 16 C) mixing an emulsifying agent with the beneficial agent containing gel, 17 said emulsifying agent forming a dispersed droplet phase in the beneficial agent 18 containing gel so as to provide the injectable depot gel composition.
19 In another aspect, the present iinvf:ntion provides a method of preparing an injectable depot gel composition comprising:
21 A) mixing a biocompatible polymer and a solvent whereby the solvent 22 dissolves the polymer and forms a viscous gel;
23 B) dispersing or dissolving a beneficial agent in an emulsifying agent to 24 form a beneficial agent containing emulsifying agent; and C) mixing the beneficial agent containing emulsifying agent with the viscous 26 gel, said beneficial agent containing emulsifying agent forming a dispersed droplet 27 phase in the viscous gel to provide the injectable depot gel composition.
1 In yet another aspect, the invention provides an injectable depot gel 2 composition comprising:
3 A) a biocompatible polymer;
4 B) a solvent that dissolves the polymer and forms a viscous gel; and C) an emulsifying agent in the form of a dispersed droplet phase in the 6 viscous gel.
7 In an additional aspect, the invention provides a kit adapted to provide an 8 injeetable depot composition comprising ,as kit components: (a) a biocompatible 9 polymer and a solvent that dissolves the polymer and forms a viscous gel;
{b) emulsifying agent; and (c) beneficial agent.
14 The foregoing and other objects, features and advantages of the present invention will be more readily understood. upon reading the following detailed 16 description in conjunction with the drawings in which:
17 Figure 1 is a graph illustrating the dispense force required to dispense the 18 emulsified and non-emulsified viscous gel compositions through a 20 gauge needle 19 in psig at 2 cc/min;
Figure 2 is a graph illustrating the release profiles of lysozyme from three 21 different compositions in days; and 22 Figure 3 is a graph illustrating the viscosity profiles at different shear rates 23 of water alone and of an aqueous mixture of ethanol, and of the viscous gel without 24 emulsifying agent.
3 As explained above, one aspect of the present invention relates to an 4 injectable depot gel composition comprising:
S A) a biocompatible polymer;
6 B) a solvent that dissolves the biocompatible polymer and forms a viscous 7 gel;
8 C) a beneficial agent; and 9 D) an emulsifying agent in the farm of a dispersed droplet phase in the viscous gel.
11 The polymer, solvent and emulsifying agents of the invention must be 12 biocompatible, that is they must not cause irritation or necrosis in the environment 13 of use. The environment of use is a fluid environment and may comprise a 14 subcutaneous or intramuscular portion or body cavity of a human or animal.
Polymers that may be useful in the invention may be biodegradable and may 16 include, but are not limited to polylactides, polyglycolides, polycaprolactones, 17 polyanhydrides, polyamines, polyurethanes, polyesteramides, polyorthoesters, 18 polydioxanones, polyacetals, polyketals, polycarbonates, polyorthocarbonates, 19 polyphosphazenes, succinates, poly(malic: acid), poly(amino acids), polyvinylpyrrolidone, polyethylene glycol, polyhydroxycellulose, chitin, chitosan, 21 and copolymers, terpolymers and mixturc;s thereof.
22 The polymer may be a polylactide, that is, a lactic acid-based polymer that 23 can be based solely on lactic acid or can be a copolymer based on lactic acid and 24 glycolic acid which may include small amounts of other comonomers that do not substantially affect the advantageous results which can be achieved in accordance 26 with the present invention. As used herein, the term "lactic acid" includes the 27 isomers L-lactic acid, D-lactic acid, DL-lactic acid and lactide while the term 28 "glycolic acid" includes glycolide. The polymer may have a monomer ratio of 29 lactic acid/glycolic acid of from about 100:0 to about 15:85, preferably from about 1 60:40 to about 75:25 and an especially useful copolymer has a monomer ratio of 2 lactic acid/glycolic acid of about 50:50.
3 The lactic acid-based polymer has a number average molecular weight of 4 from about 1,000 to about 120,000, preferably from about 10,000 to about 30,000 as determined by gas phase chromatography. As indicated in aforementioned U.S.
6 Patent No. 5,242,910, the polymer can be prepared in accordance with the 7 teachings of U.S. Patent No. 4,443,340. Alternatively, the lactic acid-based 8 polymer can be prepared directly from lactic acid or a mixture of lactic acid and 9 glycolic acid (with or without a further comonomer) in accordance with the techniques set forth in U.S. Patent No. 5,3'10,865.
11 Suitable lactic acid-based polymers are 12 available commercially. For instance, 50:50 lactic acid:glycolic acid copolymers 13 having molecular weights of 10,000, 30,000 and 100,000 are available from 14 Boehringer Ingelheim (Petersburg, VA).
The biocompatible polymer is present in the composition in an amount 16 ranging from about S to about 80% by weight, preferably from about 20 to about .
17 50 % by weight and often 35 to 45 % by weight of the viscous gel, the viscous gel 18 comprising the combined amounts of the biocompatible polymer and the solvent.
19 Once in place in the environment of use, the solvent will diffuse slowly away from the depot and the polymer will slowly degrade by hydrolysis., 21 The solvent must be biocompatible and is selected so as to dissolve the 22 polymer to form a viscous geI that can maintain particles of the benef vial agent 23 dissolved or dispersed and isolated from the environment of use prior to release.
24 Illustrative solvents which can be used in the present invention include but are not limited to triacetin, N-methyl-2-pyrrolidone, 2-pyrrolidone, glycerol formal, methyl 26 acetate, benzyl benzoate, ethyl acetate, methyl ethyl ketone, dimethylformamide, 27 dimethyl sulfoxide, tetrahydrofuran, caprolactam, decylinethylsulfoxide, oleic acid, 28 and 1-dodecylazacyclo-heptan-2-one and mixtures thereof. The preferred solvents 29 are triacetin and N-methyl-2-pyrrolidone. Triacetin provides a high level of 1 polymer dissolution which leads to greater get viscosities, with attendant higher 2 force needed to dispense the viscous gel when compared with other solvents.
These 3 characteristics enable the beneficial agent to be maintained without exhibiting a 4 burst effect, but make it difficult to dispense the gel through a needle.
For instance, as shown in Figure 1, a gel prepared fronn 40% by weight of a 50:50 lactic 6 acid:glycolic polymer and 60% by weigr~t of triacetin required about 40 psig to 7 dispense the gel through a standard 20 gauge needle at 2 cc/min while a gel 8 prepared from the same amount of polymer with 60 % by weight of N-methyl-2-9 pyrrolidone required only about 8 psig. Figure 1 further shows that when the emulsifying agent (in this case 33 % by weight of a 10 % ethanol solution) is added 11 to the viscous gel according to the invention, the dispense force needed is only 12 about 2 psig. The shear thinning characteristics of the depot gel compositions of the 13 present invention allow them be readily injected into an animal including humans 14 using standard gauge needles without reqvuiring undue dispensing pressure.
The solvent is typically present in an amount of from about 95 to about 20%
16 by weight and is preferably present in an amount of from about 80 to about 50 % by 17 weight and often 65 to 5~ % by weight of the viscous gel, that is the combined 18 amounts of the polymer and the solvent. The viscous gel formed by mixing the 19 polymer and the solvent typically exhibits a viscosity of from about 1,000 to about 200,000 poise, preferably from about 5 to about 50,000 poise measured at a 1.0 sec-21 ' shear rate and 25° C using a Haake Viscometer at about 1-2 days after mixing is 22 completed. Mixing the polymer with the solvent can be achieved with conventional 23 low shear equipment such as a Ross double planetary mixer for from about 1 to 24 about 2 hours.
The beneficial agent can be any physiologically or pharmacologically active 26 substance or substances optionally in comlbination with pharmaceutically acceptable 27 carriers and additional ingredients such as antioxidants, stabilizing agents, 28 permeation enhancers, etc. that do not substantially adversely affect the 29 advantageous results that can be attained by the present invention. The beneficial I agent may be any of the agents which are known to be delivered to the body of a 2 human or an animal and that are preferentially soluble in water rather than in the 3 polymer-dissolving solvent. These agents include drug agents, medicaments, 4 vitamins, nutrients, or the like. Included among the types of agents which meet this 5 description are nutrients, vitamins, food supplements, sex sterilants, fertility 6 inhibitors and fertility promoters.
7 Drug agents which may be delivered by the present invention include drugs 8 which act on the peripheral nerves, adrenergic receptors, cholinergic receptors, the 9 skeletal muscles, the cardiovascular system, smooth muscles, the blood circulatory 10 system, synoptic sites, neuroeffector juncaional sites, endocrine and hormone 11 systems, the immunological system, the reproductive system, the skeletal system, 12 autacoid systems, the alimentary and excretory systems, the histamine system and 13 the central nervous system. Suitable agents may be selected from, for example, 14 proteins, enzymes, hormones, polynucleotides, nucleoproteins, polysaccharides, glycoproteins, lipoproteins, polypeptides., steroids, analgesics, local anesthetics, 16 antibiotic agents, anti-inflammatory corticosteroids, ocular drugs and synthetic 17 analogs of these species.
18 Examples of drugs which may be delivered by the composition of the present 19 invention include, but are not limited to prochlorperzine edisylate, ferrous sulfate, aminocaproic acid, mecamylamine hydrochloride, procainamide hydrochloride, 21 amphetamine sulfate, methamphetamine hydrochloride, benzamphetamine 22 hydrochloride, isoproterenol sulfate, phenmetrazine hydrochloride, bethanechol 23 chloride, methacholine chloride, pilocarpine hydrochloride, atropine sulfate, 24 scopolamine bromide, isopropamide iodide, tridihexethyl chloride, phenformin hydrochloride, methylphenidate hydrochloride, theophylline cholinate, cephalexin 26 hydrochloride, diphenidol, meclizine hydrochloride, prochlorperazine maleate, 27 phenoxybenzamine, thiethylperzine malea.te, anisindone, diphenadione erythrityl 28 tetranitrate, digoxin, isoflurophate, aceta~:olamide, methazolamide, 29 bendroflumethiazide, chloropromaide, tolazamide, chlormadinone acetate, WO 98/2?962 PCT/US97/23341 1 phenaglycodol, allopurinol, aluminum aspirin, methotrexate, acetyl sulfisoxazoIe, 2 erythromycin, hydrocortisone, hydrocorticosterone acetate, cortisone acetate, 3 dexamethasone and its derivatives such as betamethasone, triamcinolone, 4 methyltestosterone, 17-S-estradiol, ethinyl estradiol, ethinyl estradiol 3-methyl ether, prednisolone, l7oc-hydroxyprogesterone acetate, 19-nor-progesterone, 6 norgestrel, norethindrone, norethisterone, norethiederone, progesterone, 7 norgesterone, norethynodrel, aspirin, indomethacin, naproxen, fenoprofen, 8 sulindac, indoprofen, nitroglycerin, isosorbide dinitrate, propranolol, timolol, 9 atenolol, alprenolol, cimetidine, clonidinc:, imipramine, levodopa, chlorpromazine, methyldopa, dihydroxyphenylalanine, theophylline, calcium gluconate, ketoprofen, 11 ibuprofen, cephalexin, erythromycin, haloperidol, zomepirac, ferrous lactate, 12 vincamine, diazepam, phenoxybenzamine, diltiazem, milrinone, mandol, quanbenz, 13 hydrochlorothiazide, ranitidine, flurbiprofen, fenufen, fluprofen, tolmetin, 14 alclofenac, mefenamic, flufenamic, difuinal, nimodipine, nitrendipine, nisoldipine, nicardipine, felodipine, lidoflazine, tiaparnil, gallopamil, amlodipine, mioflazine, 16 lisinolpril, enalapril, enalaprilat, captopri;l, ramipril, famotidine, nizatidine, 17 sucralfate, etintidine, tetratolol, minoxidil, chlordiazepoxide, diazepam, 18 amitriptyline, and imipramine. Further e;~camples are proteins and peptides which 19 include, but are not limited to, bone morp~hogenic proteins, insulin, colchicine, glucagon, thyroid stimulating hormone, parathyroid and pituitary hormones, 21 caIcitonin, renin, prolactin, corticotrophin, thyrotropic hormone, follicle stimulating 22 hormone, chorionic gonadotropin, gonado~tropin releasing hormone, bovine 23 somatotropin, porcine somatotropin, oxytocin, vasopressin, GRF, somatostatin, 24 lypressin, pancreozymin, luteinizing hormone, LHRH, LHRH agonists and antagonists, leuprolide, interferons, interlf:ukins, growth hormones such as human 26 growth hormone, bovine growth hormone and porcine growth hormone, fertility 27 inhibitors such as the prostaglandins, fertilLity promoters, growth factors, coagultion 28 factors, human pancreas hormone releasing factor, analogs and derivatives of these WO 9$/27962 PCT/US97/23341 1 compounds, and pharmaceutically acceptable salts of these compounds, or their 2 analogs or derivatives.
3 To the extent not mentioned in the: previous paragraph, the beneficial agents 4 described in aforementioned U.S. Patent No. 5,242,910 can also be used. One particular advantage of the present invention is that materials, such as proteins, as 6 exemplified by the enzyme lysozyme, and cDNA, and DNA incorporated into 7 vectors both viral and nonviral, which arc: difficult to microcapsulate or process into 8 microspheres can be incorporated into the; compositions of the present invention 9 without the level of degradation experienced with other techniques.
The beneficial agent is preferably incorporated into the viscous gel formed 11 from the polymer and the solvent in the form of particles typically having an 12 average particle size of from about 0.1 to about 100 microns, preferably from about 13 1 to about 25 microns and often from 2 to 10 microns. For instance, particles 14 having an average particle size of about 5 microns have been produced by spray drying or spray freezing an aqueous mixnure containing 50 % sucrose and SO %o 16 chicken lysozyme (on a dry weight basis). Such particles have been used in certain 17 of the examples illustrated in the figures.
18 To form a suspension of particles of the beneficial agent in the viscous gel 19 formed from the polymer and the solvent, any conventional low shear device can be used such as a Ross double planetary mixer at ambient conditions. In this manner, 21 efficient distribution of the beneficial agent can be achieved substantially without 22 degrading the beneficial agent.
23 The beneficial agent is typically dissolved or dispersed in the composition in 24 an amount of from about 1 to about 50 % by weight, preferably in an amount of from about 5 to about 25 % and often IO to 20% by weight of the combined amounts 26 of the polymer, solvent and beneficial agent. Depending on the amount of 27 beneficial agent present in the composition, one can obtain different release profiles.
28 More specifically, for a given polymer and solvent, by adjusting the amounts of 29 these components and the amount of the beneficial agent, one can obtain a release 1 profile that depends more on the degradation of the polymer than the diffusion of 2 the beneficial agent from the composition or vice versa. In this respect, at lower 3 beneficial agent loading rates, one generally obtains a release profile reflecting 4 degradation of the polymer wherein the release rate increases with time. At higher loading rates, one generally obtains a release profile caused by diffusion of the 6 beneficial agent wherein the release rate decreases with time. At intermediate 7 loading rates, one obtains combined release profiles so that if desired, a 8 substantially constant release rate can be attained. While the particular release rate 9 depends on the particular circumstances, such as the beneficial agent to be administered, release rates on the order of from about 1 to about 10 micrograms/day 11 for periods of from about 7 to about 90 days can be obtained. Further, the dose of 12 beneficial agent may be adjusted by adjusting the amount of injectable depot gel 13 injected. As will be apparent from the following results, one can avoid a burst 14 effect and administer on the order of 1 % by weight of the beneficial agent in the composition during the first day.
16 Figure 2 shows the release rates obtained from the compositions described 17 with regard to Figure 1. The gel preparf;d from 40% by weight of a 50:50 lactic 18 acid:glycolic polymer and 60% by weight triacetin is thick and thus difficult to 19 inject but shows little burst (less than 2% of the beneficial agent is delivered in the first eight days). The gel prepared from 40% by weight of a 50:50 lactic 21 acid:glycolic polymer and 60%o by weight N-methyl-2-pyrrolidone is thin and 22 injectable but shows a large burst (greater than 70% of the beneficial agent is 23 delivered in the first eight days). The gel prepared from 27 % by weight of a 50:50 24 lactic acid:glycolic polymer, 40% by weight triacetin and 33% by weight of a 10%
ethanol, 90 % isotonic saline solution is thin and injectable and shows little burst 26 (less than 10% of the beneficial agent is delivered in the first eight days). In each 27 case, lysozyme is the beneficial agent and comprises 20 % by weight of the 28 combined beneficial agent, polymer and solvent formulation.
1 The emulsifying agent constitutes an important aspect of the present 2 invention. When the emulsifying agent is mixed with the viscous gel formed from 3 the polymer and the solvent using conventional static or mechanical mixing devices, 4 such as an orifice mixer, the emulsifying agent forms a separate phase composed of dispersed droplets of microscopic size that typically have an average diameter of 6 less than about 100 microns. The continuous phase is formed of the polymer and 7 the solvent. The particles of the beneficial agent may be dissolved or dispersed in 8 either the continuous phase or the droplet phase. In the resulting thixotropic 9 composition, the droplets of emulsifying agent elongate in the direction of shear and substantially decrease the viscosity of the viscous gel formed from the polymer and 11 the solvent. For instance, with a viscous gel having a viscosity of from about 5,000 12 to about 50,000 poise measured at 1.0 sec-' at 25°C, one can obtain a reduction in 13 viscosity to less than 100 poise when emulsified with a 10% ethanol/water solution 14 at 25°C as determined by Haake rheometer. Because dispersion and dissolution of the particles of beneficial agent in the emulsifying agent proceeds more rapidly than 16 does dissolution or dispersion of the beneficial agent in the viscous polymer, the 17 beneficial agent can be mixed with the emulsifying agent just prior to the time of 18 use. This permits the beneficial agent to be maintained in a dry state prior to use, 19 which may be advantageous in those instances where long term stability of the beneficial agent in the viscous gel is of concern. Additionally, since the beneficial 21 agent will remain in the droplet phase that is entrapped within the viscous gel as it 22 forms, it is possible to select an emulsifying agent in which the drug is optimally 23 stable and thus prolong stability of the beneficial agent in the gel composition. An 24 added benefit is the opportunity to progra:rn the release of beneficial agent via diffusion through the porous structure of l:he implant, rather than by degradation and 26 dissolution of the polymer structure.
27 When dissolution or dispersion of the beneficial agent in the emulsifying 28 agent is intended, the injectable depot of this invention may be provided as a kit, 29 having kit components comprising (a) a mixture of polymer and solvent, (b) I emulsifying agent and (c) beneficial agent. Prior to use the beneficial agent is mixed 2 with the emulsifying agent, and that solution or suspension is mixed with the 3 polymer/solvent mixture to prepare the injectable depot implant for use.
4 The emulsifying agent is present in an amount ranging from about 5 to about 5 80 % , preferably from about 20 to about 60 % and often 30 to 50 % by weight based 6 on the amount of the injectable depot gel composition, that is the combined amounts 7 of polymer, solvent, emulsifying agent and beneficial agent. Illustrative 8 emulsifying agents are water, alcohols, polyols, esters, carboxylic acids, ketones, 9 aldehydes and mixtures thereof. Preferred emulsifying agents are alcohols, 10 propylene glycol, ethylene glycol, glycerol, water, and solutions and mixtures 11 thereof. Especially preferred are water, ethanol, and isopropyl alcohol and 12 solutions and mixtures thereof. The type of emulsifying agent affects the size of the 13 dispersed droplets. For instance, ethanol will provide droplets that have average 14 diameters that can be on the order of ten times larger than the droplets obtained with 15 an isotonic saline solution containing 0.9~~o by weight of sodium chloride at 21°C.
7 Field of the Invention 9 The present invention relates to a depot gel composition that can be injected into a desired location and which can provide sustained release of a beneficial agent.
11 The present invention also relates to a method of preparing the composition.
13 Description of the Related Art Biodegradable polymers have been used for many years in medical 16 applications. Illustrative devices composed of the biodegradable polymers include 17 sutures, surgical clips, staples, implants, and drug delivery systems. The majority 18 of these biodegradable polymers have been based upon glycoside, lactide, 19 caprolactone, and copolymers thereof.
The biodegradable polymers can be thermoplastic materials which means 21 that they can be heated and formed into various shapes such as fibers, clips, staples, 22 pins, films, etc. Alternatively, they can be thermosetting materials formed by 23 crosslinking reactions which lead to high-molecular-weight materials that do not 24 melt or form flowable liquids at high temperatures.
Although thermoplastic and thermosetting biodegradable polymers have 26 many useful biomedical applications, there are several important limitations to their 27 use in the bodies of various animals including humans, animals, birds, fish, and 1 reptiles. Because these polymers are solids, all instances involving their use have 2 required initially forming the polymeric structures outside the body, followed by 3 insertion of the solid structure into the body. For example, sutures, clips, and 4 staples are all formed from thermoplastic: biodegradable polymers prior to use.
When inserted into the body, they retain their original shape. While this 6 characteristic is essential for some uses, it is a drawback where it is desired that the 7 material flow to fill voids or cavities whc;re it may be most needed.
8 Drug delivery systems using thermoplastic or thermosetting biodegradable 9 polymers also have to be formed outside the body. In such instances, the drug is incorporated into the polymer and the mixture is shaped into a certain form such a I1 cylinder, disc, or fiber for implantation. With such solid implants, the drug 12 delivery system has to be inserted into th~° body through an incision. These 13 incisions are sometimes larger than desired by the medical profession and 14 occasionally lead to a reluctance of the patients to accept such an implant or drug delivery system. Nonetheless, both biodf;gradable and non-biodegradable 16 implantable drug delivery systems have been widely used successfully.
17 One reservoir device having a rate-controlling membrane and zero-order 18 release of an agent that Zs particularly designed for intraoral implantation is 19 described in U.S. Patent No. 5,085,866. The device is prepared from a core that is sprayed with a solution having a polymer and a solvent that is composed of a 21 rapidly evaporating, low boiling point first solvent and a slowly evaporating, high 22 boiling second solvent.
23 Other illustrative osmotic delivery systems include those disclosed in U.S.
24 Patent Nos. 3,797,492, 3,987,790, 4,008,719, 4,865,845, 5,057,318, 5,059,423, 5,112,614, 5,137,727, 5,151,093, 5,234,692, 5,234,693, 5,279,608, and 26 5,336,057. Pulsatile delivery devices are also known which deliver a beneficial 27 agent in a pulsatile manner as disclosed in U.S. Patent Nos. 5,209,746, 5,308,348, 28 and 5,456,679.
1 One way to avoid the incision needed to implant drug delivery systems is to 2 inject them as small particles, microspheres, or microcapsules. For example, U.S.
3 Patent No. 5,019,400 describes the preparation of controlled release microspheres 4 via a very low temperature casting process. These materials may or may not contain a drug which can be released into the body. Although these materials can 6 be injected into the body with a syringe, they do not always satisfy the demand for a 7 biodegradable implant. Because they are: particulate in nature, they do not form a 8 continuous film or solid implant with the structural integrity needed for certain 9 prostheses. When inserted into certain body cavities such as a mouth, a periodontal pocket, the eye, or the vagina where there is considerable fluid flaw, these small 11 particles, microspheres, or microcapsules are poorly retained because of their small 12 size and discontinuous nature. Further, the particles tend to aggregate and thus their 13 behavior is hard to predict. In addition, microspheres or microcapsules prepared 14 from these polymers and containing drugs for release into the body are sometimes difficult to produce on a large scale, and their storage and injection characteristics 16 present problems. Furthermore, one other major limitation of the microcapsule or 17 small-particle system is their lack of reversibility without extensive surgical 18 intervention. That is, if there are complications after they have been injected, it is 19 considerably more difficult to remove them from the body than with solid implants.
A still further limitation on microparticle;s or microcapsuiation is the difficulty in 21 encapsulating protein and DNA-based drugs without degradation caused by solvents 22 and temperature extremes.
23 The art has developed various drug delivery systems in response to the 24 aforementioned challenges. For instance, U.S. Patent No. 4,938,763 and its divisional U.S. Patent No. 5,278,201 relate to a biodegradable polymer for use in 26 providing syringeable, in-situ forming, solid biodegradable implants for animals. In 27 one embodiment, a thermoplastic system is used wherein a non-reactive polymer is 28 dissolved in a biocompatible solvent to form a liquid which is placed in the animal 29 wherein the solvent dissipates to produce the solid implant. Alternatively, a I thermosetting system is used wherein effective amounts of a liquid acrylic ester-2 terminated, biodegradable prepolymer and a curing agent are formed and the liquid 3 mixture is placed within the animal wherein the prepolymer cures to form the solid 4 implant. It is stated that the systems provide a syringeable, solid biodegradable delivery system by the addition of an effective level of a biologically active agent to 6 the liquid before the injection into the animal.
7 U.S. Patent No. 5,242,910 describes a sustained release composition for 8 treating periodontal disease. The composition comprises copolymers of lactide and 9 glycolide, triacetin (as a solvent/plasticizer) and an agent providing relief of oral cavity diseases. The composition can take the form of a gel and can be inserted into 11 a periodontal cavity via a syringe using either a needle or a catheter. As additional 12 optional components, the composition can contain surfactants, flavoring agents, 13 viscosity controlling agents, complexing .agents, antioxidants, other polymers, 14 gums, waxes/oils, and coloring agents. One illustrative viscosity controlling agent set forth in one of the examples is polyethylene glycol 400.
16 With solvent-based depot compositions comprised of a polymer dissolved in 17 a solvent, one problem which exists is that the composition solidifies slowly after 18 injection as solvent diffuses from the depot. Since these compositions need to be 19 non-viscous in order to be injected, a lar~;e percentage of drug is released as the system forms by diffusion of the solvent. This effect is referred to as a "burst"
21 effect. In this respect, it is typical for solvent-based compositions to have a drug 22 burst wherein 30-75 % of the drug contained in the composition is released within 23 one day of the initial injection.
3 The present invention is a significant advance in the art and in one aspect 4 provides an injectable depot gel composition comprising:
5 A) a biocompatible polymer;
6 B) a solvent that dissolves the polymer and forms a viscous gel;
7 C) a beneficial agent; and 8 D) an emulsifying agent in the form of a dispersed droplet phase in the 9 viscous gel.
In a further aspect, the present invention provides a method of preparing an 11 injectable depot gel composition comprising:
12 A) mixing a biocompatible polymer and a solvent whereby the solvent 13 dissolves the polymer and forms a viscous gel;
14 B) dispersing or dissolving a beneficial agent in the viscous gel to form a beneficial agent containing gel; and 16 C) mixing an emulsifying agent with the beneficial agent containing gel, 17 said emulsifying agent forming a dispersed droplet phase in the beneficial agent 18 containing gel so as to provide the injectable depot gel composition.
19 In another aspect, the present iinvf:ntion provides a method of preparing an injectable depot gel composition comprising:
21 A) mixing a biocompatible polymer and a solvent whereby the solvent 22 dissolves the polymer and forms a viscous gel;
23 B) dispersing or dissolving a beneficial agent in an emulsifying agent to 24 form a beneficial agent containing emulsifying agent; and C) mixing the beneficial agent containing emulsifying agent with the viscous 26 gel, said beneficial agent containing emulsifying agent forming a dispersed droplet 27 phase in the viscous gel to provide the injectable depot gel composition.
1 In yet another aspect, the invention provides an injectable depot gel 2 composition comprising:
3 A) a biocompatible polymer;
4 B) a solvent that dissolves the polymer and forms a viscous gel; and C) an emulsifying agent in the form of a dispersed droplet phase in the 6 viscous gel.
7 In an additional aspect, the invention provides a kit adapted to provide an 8 injeetable depot composition comprising ,as kit components: (a) a biocompatible 9 polymer and a solvent that dissolves the polymer and forms a viscous gel;
{b) emulsifying agent; and (c) beneficial agent.
14 The foregoing and other objects, features and advantages of the present invention will be more readily understood. upon reading the following detailed 16 description in conjunction with the drawings in which:
17 Figure 1 is a graph illustrating the dispense force required to dispense the 18 emulsified and non-emulsified viscous gel compositions through a 20 gauge needle 19 in psig at 2 cc/min;
Figure 2 is a graph illustrating the release profiles of lysozyme from three 21 different compositions in days; and 22 Figure 3 is a graph illustrating the viscosity profiles at different shear rates 23 of water alone and of an aqueous mixture of ethanol, and of the viscous gel without 24 emulsifying agent.
3 As explained above, one aspect of the present invention relates to an 4 injectable depot gel composition comprising:
S A) a biocompatible polymer;
6 B) a solvent that dissolves the biocompatible polymer and forms a viscous 7 gel;
8 C) a beneficial agent; and 9 D) an emulsifying agent in the farm of a dispersed droplet phase in the viscous gel.
11 The polymer, solvent and emulsifying agents of the invention must be 12 biocompatible, that is they must not cause irritation or necrosis in the environment 13 of use. The environment of use is a fluid environment and may comprise a 14 subcutaneous or intramuscular portion or body cavity of a human or animal.
Polymers that may be useful in the invention may be biodegradable and may 16 include, but are not limited to polylactides, polyglycolides, polycaprolactones, 17 polyanhydrides, polyamines, polyurethanes, polyesteramides, polyorthoesters, 18 polydioxanones, polyacetals, polyketals, polycarbonates, polyorthocarbonates, 19 polyphosphazenes, succinates, poly(malic: acid), poly(amino acids), polyvinylpyrrolidone, polyethylene glycol, polyhydroxycellulose, chitin, chitosan, 21 and copolymers, terpolymers and mixturc;s thereof.
22 The polymer may be a polylactide, that is, a lactic acid-based polymer that 23 can be based solely on lactic acid or can be a copolymer based on lactic acid and 24 glycolic acid which may include small amounts of other comonomers that do not substantially affect the advantageous results which can be achieved in accordance 26 with the present invention. As used herein, the term "lactic acid" includes the 27 isomers L-lactic acid, D-lactic acid, DL-lactic acid and lactide while the term 28 "glycolic acid" includes glycolide. The polymer may have a monomer ratio of 29 lactic acid/glycolic acid of from about 100:0 to about 15:85, preferably from about 1 60:40 to about 75:25 and an especially useful copolymer has a monomer ratio of 2 lactic acid/glycolic acid of about 50:50.
3 The lactic acid-based polymer has a number average molecular weight of 4 from about 1,000 to about 120,000, preferably from about 10,000 to about 30,000 as determined by gas phase chromatography. As indicated in aforementioned U.S.
6 Patent No. 5,242,910, the polymer can be prepared in accordance with the 7 teachings of U.S. Patent No. 4,443,340. Alternatively, the lactic acid-based 8 polymer can be prepared directly from lactic acid or a mixture of lactic acid and 9 glycolic acid (with or without a further comonomer) in accordance with the techniques set forth in U.S. Patent No. 5,3'10,865.
11 Suitable lactic acid-based polymers are 12 available commercially. For instance, 50:50 lactic acid:glycolic acid copolymers 13 having molecular weights of 10,000, 30,000 and 100,000 are available from 14 Boehringer Ingelheim (Petersburg, VA).
The biocompatible polymer is present in the composition in an amount 16 ranging from about S to about 80% by weight, preferably from about 20 to about .
17 50 % by weight and often 35 to 45 % by weight of the viscous gel, the viscous gel 18 comprising the combined amounts of the biocompatible polymer and the solvent.
19 Once in place in the environment of use, the solvent will diffuse slowly away from the depot and the polymer will slowly degrade by hydrolysis., 21 The solvent must be biocompatible and is selected so as to dissolve the 22 polymer to form a viscous geI that can maintain particles of the benef vial agent 23 dissolved or dispersed and isolated from the environment of use prior to release.
24 Illustrative solvents which can be used in the present invention include but are not limited to triacetin, N-methyl-2-pyrrolidone, 2-pyrrolidone, glycerol formal, methyl 26 acetate, benzyl benzoate, ethyl acetate, methyl ethyl ketone, dimethylformamide, 27 dimethyl sulfoxide, tetrahydrofuran, caprolactam, decylinethylsulfoxide, oleic acid, 28 and 1-dodecylazacyclo-heptan-2-one and mixtures thereof. The preferred solvents 29 are triacetin and N-methyl-2-pyrrolidone. Triacetin provides a high level of 1 polymer dissolution which leads to greater get viscosities, with attendant higher 2 force needed to dispense the viscous gel when compared with other solvents.
These 3 characteristics enable the beneficial agent to be maintained without exhibiting a 4 burst effect, but make it difficult to dispense the gel through a needle.
For instance, as shown in Figure 1, a gel prepared fronn 40% by weight of a 50:50 lactic 6 acid:glycolic polymer and 60% by weigr~t of triacetin required about 40 psig to 7 dispense the gel through a standard 20 gauge needle at 2 cc/min while a gel 8 prepared from the same amount of polymer with 60 % by weight of N-methyl-2-9 pyrrolidone required only about 8 psig. Figure 1 further shows that when the emulsifying agent (in this case 33 % by weight of a 10 % ethanol solution) is added 11 to the viscous gel according to the invention, the dispense force needed is only 12 about 2 psig. The shear thinning characteristics of the depot gel compositions of the 13 present invention allow them be readily injected into an animal including humans 14 using standard gauge needles without reqvuiring undue dispensing pressure.
The solvent is typically present in an amount of from about 95 to about 20%
16 by weight and is preferably present in an amount of from about 80 to about 50 % by 17 weight and often 65 to 5~ % by weight of the viscous gel, that is the combined 18 amounts of the polymer and the solvent. The viscous gel formed by mixing the 19 polymer and the solvent typically exhibits a viscosity of from about 1,000 to about 200,000 poise, preferably from about 5 to about 50,000 poise measured at a 1.0 sec-21 ' shear rate and 25° C using a Haake Viscometer at about 1-2 days after mixing is 22 completed. Mixing the polymer with the solvent can be achieved with conventional 23 low shear equipment such as a Ross double planetary mixer for from about 1 to 24 about 2 hours.
The beneficial agent can be any physiologically or pharmacologically active 26 substance or substances optionally in comlbination with pharmaceutically acceptable 27 carriers and additional ingredients such as antioxidants, stabilizing agents, 28 permeation enhancers, etc. that do not substantially adversely affect the 29 advantageous results that can be attained by the present invention. The beneficial I agent may be any of the agents which are known to be delivered to the body of a 2 human or an animal and that are preferentially soluble in water rather than in the 3 polymer-dissolving solvent. These agents include drug agents, medicaments, 4 vitamins, nutrients, or the like. Included among the types of agents which meet this 5 description are nutrients, vitamins, food supplements, sex sterilants, fertility 6 inhibitors and fertility promoters.
7 Drug agents which may be delivered by the present invention include drugs 8 which act on the peripheral nerves, adrenergic receptors, cholinergic receptors, the 9 skeletal muscles, the cardiovascular system, smooth muscles, the blood circulatory 10 system, synoptic sites, neuroeffector juncaional sites, endocrine and hormone 11 systems, the immunological system, the reproductive system, the skeletal system, 12 autacoid systems, the alimentary and excretory systems, the histamine system and 13 the central nervous system. Suitable agents may be selected from, for example, 14 proteins, enzymes, hormones, polynucleotides, nucleoproteins, polysaccharides, glycoproteins, lipoproteins, polypeptides., steroids, analgesics, local anesthetics, 16 antibiotic agents, anti-inflammatory corticosteroids, ocular drugs and synthetic 17 analogs of these species.
18 Examples of drugs which may be delivered by the composition of the present 19 invention include, but are not limited to prochlorperzine edisylate, ferrous sulfate, aminocaproic acid, mecamylamine hydrochloride, procainamide hydrochloride, 21 amphetamine sulfate, methamphetamine hydrochloride, benzamphetamine 22 hydrochloride, isoproterenol sulfate, phenmetrazine hydrochloride, bethanechol 23 chloride, methacholine chloride, pilocarpine hydrochloride, atropine sulfate, 24 scopolamine bromide, isopropamide iodide, tridihexethyl chloride, phenformin hydrochloride, methylphenidate hydrochloride, theophylline cholinate, cephalexin 26 hydrochloride, diphenidol, meclizine hydrochloride, prochlorperazine maleate, 27 phenoxybenzamine, thiethylperzine malea.te, anisindone, diphenadione erythrityl 28 tetranitrate, digoxin, isoflurophate, aceta~:olamide, methazolamide, 29 bendroflumethiazide, chloropromaide, tolazamide, chlormadinone acetate, WO 98/2?962 PCT/US97/23341 1 phenaglycodol, allopurinol, aluminum aspirin, methotrexate, acetyl sulfisoxazoIe, 2 erythromycin, hydrocortisone, hydrocorticosterone acetate, cortisone acetate, 3 dexamethasone and its derivatives such as betamethasone, triamcinolone, 4 methyltestosterone, 17-S-estradiol, ethinyl estradiol, ethinyl estradiol 3-methyl ether, prednisolone, l7oc-hydroxyprogesterone acetate, 19-nor-progesterone, 6 norgestrel, norethindrone, norethisterone, norethiederone, progesterone, 7 norgesterone, norethynodrel, aspirin, indomethacin, naproxen, fenoprofen, 8 sulindac, indoprofen, nitroglycerin, isosorbide dinitrate, propranolol, timolol, 9 atenolol, alprenolol, cimetidine, clonidinc:, imipramine, levodopa, chlorpromazine, methyldopa, dihydroxyphenylalanine, theophylline, calcium gluconate, ketoprofen, 11 ibuprofen, cephalexin, erythromycin, haloperidol, zomepirac, ferrous lactate, 12 vincamine, diazepam, phenoxybenzamine, diltiazem, milrinone, mandol, quanbenz, 13 hydrochlorothiazide, ranitidine, flurbiprofen, fenufen, fluprofen, tolmetin, 14 alclofenac, mefenamic, flufenamic, difuinal, nimodipine, nitrendipine, nisoldipine, nicardipine, felodipine, lidoflazine, tiaparnil, gallopamil, amlodipine, mioflazine, 16 lisinolpril, enalapril, enalaprilat, captopri;l, ramipril, famotidine, nizatidine, 17 sucralfate, etintidine, tetratolol, minoxidil, chlordiazepoxide, diazepam, 18 amitriptyline, and imipramine. Further e;~camples are proteins and peptides which 19 include, but are not limited to, bone morp~hogenic proteins, insulin, colchicine, glucagon, thyroid stimulating hormone, parathyroid and pituitary hormones, 21 caIcitonin, renin, prolactin, corticotrophin, thyrotropic hormone, follicle stimulating 22 hormone, chorionic gonadotropin, gonado~tropin releasing hormone, bovine 23 somatotropin, porcine somatotropin, oxytocin, vasopressin, GRF, somatostatin, 24 lypressin, pancreozymin, luteinizing hormone, LHRH, LHRH agonists and antagonists, leuprolide, interferons, interlf:ukins, growth hormones such as human 26 growth hormone, bovine growth hormone and porcine growth hormone, fertility 27 inhibitors such as the prostaglandins, fertilLity promoters, growth factors, coagultion 28 factors, human pancreas hormone releasing factor, analogs and derivatives of these WO 9$/27962 PCT/US97/23341 1 compounds, and pharmaceutically acceptable salts of these compounds, or their 2 analogs or derivatives.
3 To the extent not mentioned in the: previous paragraph, the beneficial agents 4 described in aforementioned U.S. Patent No. 5,242,910 can also be used. One particular advantage of the present invention is that materials, such as proteins, as 6 exemplified by the enzyme lysozyme, and cDNA, and DNA incorporated into 7 vectors both viral and nonviral, which arc: difficult to microcapsulate or process into 8 microspheres can be incorporated into the; compositions of the present invention 9 without the level of degradation experienced with other techniques.
The beneficial agent is preferably incorporated into the viscous gel formed 11 from the polymer and the solvent in the form of particles typically having an 12 average particle size of from about 0.1 to about 100 microns, preferably from about 13 1 to about 25 microns and often from 2 to 10 microns. For instance, particles 14 having an average particle size of about 5 microns have been produced by spray drying or spray freezing an aqueous mixnure containing 50 % sucrose and SO %o 16 chicken lysozyme (on a dry weight basis). Such particles have been used in certain 17 of the examples illustrated in the figures.
18 To form a suspension of particles of the beneficial agent in the viscous gel 19 formed from the polymer and the solvent, any conventional low shear device can be used such as a Ross double planetary mixer at ambient conditions. In this manner, 21 efficient distribution of the beneficial agent can be achieved substantially without 22 degrading the beneficial agent.
23 The beneficial agent is typically dissolved or dispersed in the composition in 24 an amount of from about 1 to about 50 % by weight, preferably in an amount of from about 5 to about 25 % and often IO to 20% by weight of the combined amounts 26 of the polymer, solvent and beneficial agent. Depending on the amount of 27 beneficial agent present in the composition, one can obtain different release profiles.
28 More specifically, for a given polymer and solvent, by adjusting the amounts of 29 these components and the amount of the beneficial agent, one can obtain a release 1 profile that depends more on the degradation of the polymer than the diffusion of 2 the beneficial agent from the composition or vice versa. In this respect, at lower 3 beneficial agent loading rates, one generally obtains a release profile reflecting 4 degradation of the polymer wherein the release rate increases with time. At higher loading rates, one generally obtains a release profile caused by diffusion of the 6 beneficial agent wherein the release rate decreases with time. At intermediate 7 loading rates, one obtains combined release profiles so that if desired, a 8 substantially constant release rate can be attained. While the particular release rate 9 depends on the particular circumstances, such as the beneficial agent to be administered, release rates on the order of from about 1 to about 10 micrograms/day 11 for periods of from about 7 to about 90 days can be obtained. Further, the dose of 12 beneficial agent may be adjusted by adjusting the amount of injectable depot gel 13 injected. As will be apparent from the following results, one can avoid a burst 14 effect and administer on the order of 1 % by weight of the beneficial agent in the composition during the first day.
16 Figure 2 shows the release rates obtained from the compositions described 17 with regard to Figure 1. The gel preparf;d from 40% by weight of a 50:50 lactic 18 acid:glycolic polymer and 60% by weight triacetin is thick and thus difficult to 19 inject but shows little burst (less than 2% of the beneficial agent is delivered in the first eight days). The gel prepared from 40% by weight of a 50:50 lactic 21 acid:glycolic polymer and 60%o by weight N-methyl-2-pyrrolidone is thin and 22 injectable but shows a large burst (greater than 70% of the beneficial agent is 23 delivered in the first eight days). The gel prepared from 27 % by weight of a 50:50 24 lactic acid:glycolic polymer, 40% by weight triacetin and 33% by weight of a 10%
ethanol, 90 % isotonic saline solution is thin and injectable and shows little burst 26 (less than 10% of the beneficial agent is delivered in the first eight days). In each 27 case, lysozyme is the beneficial agent and comprises 20 % by weight of the 28 combined beneficial agent, polymer and solvent formulation.
1 The emulsifying agent constitutes an important aspect of the present 2 invention. When the emulsifying agent is mixed with the viscous gel formed from 3 the polymer and the solvent using conventional static or mechanical mixing devices, 4 such as an orifice mixer, the emulsifying agent forms a separate phase composed of dispersed droplets of microscopic size that typically have an average diameter of 6 less than about 100 microns. The continuous phase is formed of the polymer and 7 the solvent. The particles of the beneficial agent may be dissolved or dispersed in 8 either the continuous phase or the droplet phase. In the resulting thixotropic 9 composition, the droplets of emulsifying agent elongate in the direction of shear and substantially decrease the viscosity of the viscous gel formed from the polymer and 11 the solvent. For instance, with a viscous gel having a viscosity of from about 5,000 12 to about 50,000 poise measured at 1.0 sec-' at 25°C, one can obtain a reduction in 13 viscosity to less than 100 poise when emulsified with a 10% ethanol/water solution 14 at 25°C as determined by Haake rheometer. Because dispersion and dissolution of the particles of beneficial agent in the emulsifying agent proceeds more rapidly than 16 does dissolution or dispersion of the beneficial agent in the viscous polymer, the 17 beneficial agent can be mixed with the emulsifying agent just prior to the time of 18 use. This permits the beneficial agent to be maintained in a dry state prior to use, 19 which may be advantageous in those instances where long term stability of the beneficial agent in the viscous gel is of concern. Additionally, since the beneficial 21 agent will remain in the droplet phase that is entrapped within the viscous gel as it 22 forms, it is possible to select an emulsifying agent in which the drug is optimally 23 stable and thus prolong stability of the beneficial agent in the gel composition. An 24 added benefit is the opportunity to progra:rn the release of beneficial agent via diffusion through the porous structure of l:he implant, rather than by degradation and 26 dissolution of the polymer structure.
27 When dissolution or dispersion of the beneficial agent in the emulsifying 28 agent is intended, the injectable depot of this invention may be provided as a kit, 29 having kit components comprising (a) a mixture of polymer and solvent, (b) I emulsifying agent and (c) beneficial agent. Prior to use the beneficial agent is mixed 2 with the emulsifying agent, and that solution or suspension is mixed with the 3 polymer/solvent mixture to prepare the injectable depot implant for use.
4 The emulsifying agent is present in an amount ranging from about 5 to about 5 80 % , preferably from about 20 to about 60 % and often 30 to 50 % by weight based 6 on the amount of the injectable depot gel composition, that is the combined amounts 7 of polymer, solvent, emulsifying agent and beneficial agent. Illustrative 8 emulsifying agents are water, alcohols, polyols, esters, carboxylic acids, ketones, 9 aldehydes and mixtures thereof. Preferred emulsifying agents are alcohols, 10 propylene glycol, ethylene glycol, glycerol, water, and solutions and mixtures 11 thereof. Especially preferred are water, ethanol, and isopropyl alcohol and 12 solutions and mixtures thereof. The type of emulsifying agent affects the size of the 13 dispersed droplets. For instance, ethanol will provide droplets that have average 14 diameters that can be on the order of ten times larger than the droplets obtained with 15 an isotonic saline solution containing 0.9~~o by weight of sodium chloride at 21°C.
16 While normally no other components are present in the composition, to the 17 extent that conventional optional ingredients are desired, such as polyethylene 18 glycol, hydroscopic agents, stabilizing agents and others, they are used in an 19 amount that does not substantially affect tile advantageous results which can be attained in accordance with the present invention.
21 To illustrate various aspects of the invention further, Figure 3 shows the 22 viscosities at different shear rates using water alone and an aqueous mixture 23 containing 10% by volume of ethanol at a weight ratio of 2:1 (gel:emulsifying 24 agent) using a viscous gel formed from SO % by weight of a 50:50 lactic acid:glycolic acid copolymer and 50% by weight of triacetin compared to the 26 viscosities of the viscous gel without emulsifying agent.
27 It is to be understood that the emulsifying agent of the present invention does 28 not constitute a mere diluent that reduces viscosity by simply decreasing the 29 concentration of the components of the composition. The use of conventional 1 diluents can reduce viscosity, but can also cause the burst effect mentioned 2 previously when the diluted composition is injected. In contrast, the injectable 3 depot composition of the present invention can be formulated to avoid the burst 4 effect by selecting the emulsifying agent so that once injected into place, the emulsifying agent has little impact on the release properties of the original system.
6 Further compositions without beneficial agent may be useful for wound healing, 7 bone repair and other structural support purposes.
8 To further understand the various aspects of the present invention, the results 9 set forth in the previously described Figures were obtained in accordance with the following examples.
12 Example 1 13 Lysozyme particles were made by spray drying 50 % sucrose and SO %
14 chicken lysozyme (on a dry weight basis).
A viscous gel material was preparE:d by heating 60 % by weight of triacetin 16 with 40% by weight of a 50:50 lactic acid:glycolic acid copolymer to 37°C
17 overnight. The viscous gel was allowed to cool to room temperature while mixing 18 continued. The lysozyme particles were added to the viscous gel in a ratio of 20:80 19 lysozyme particles:gel (by weight). The combination was mixed for 5 minutes.
Immediately prior to use, a 10 % ethanol, 90 % isotonic saline solution was added as 21 the emulsifying agent. The emulsifying agent comprised 1/3 of the total injectable 22 depot gel composition. 0.5 grams of this injectable depot composition was then 23 injected into a rat.
24 Exalr~ple 2 A viscous gel material is prepared by heating 60 % by weight of triacetin 26 with 40% by weight of a 50:50 lactic acid:glycolic acid copolymer to 37°C
27 overnight. The viscous gel is allowed to cool to room temperature while mixing is 28 continued. Immediately prior to use, lyso:ayme particles, prepared as in Example 1 29 and in the same amount, are combined with a 10% ethanol, 90% isotonic saline 1 solution, as an emulsifying agent, in the amount used in Example 1. The 2 emulsifying agent-lysozyme solution is mixed with the amount of gel material used 3 in Example 1 to form an injectable depot gel composition. The fabricated injectable 4 depot gel composition is suitable for injection into an animal.
In accordance with various aspects of the present invention, one or more 6 significant advantages can be obtained. lvlore specifically, using simple processing 7 steps, one can obtain a depot gel composition that can be injected into place in an 8 animal without surgery using a low dispensing force through standard needles.
9 Once in place, the composition will quickly return to its original viscosity and may exhibit rapid hardening so as to substantially avoid a burst effect and provide the 11 desired beneficial agent release profile. Furthermore, once the beneficial agent has 12 been fully administered, there is no need to remove the composition since it is fully 13 biodegradable. As a still fixrther advanta~;e, the present invention avoids the use of 14 microparticle or microcapsulation techniqvues which can degrade certain beneficial agents, like peptide and nucleic acid-based drugs and which microparticles and 16 microcapsules maybe difficult to remove from the environment of use. Since the 17 viscous gel is formed without the need for water, temperature extremes, or other 18 solvents, suspended particles of beneficial agent remain dry and in their original 19 configuration, which contributes to the stability of thereof. Further, since a mass is formed, the injectable depot gel composition may be retrieved from the environment 21 of use if desired.
22 The above-described exemplary err~bodiments are intended to be illustrative 23 in all respects, rather than restrictive, of the present invention. Thus the present 24 invention is capable of many variations in detailed implementation that can be derived from the description contained herein by a person skilled in the art.
All 26 such variations and modifications are considered to be within the scope and spirit of 27 the present invention as defined by the following claims.
21 To illustrate various aspects of the invention further, Figure 3 shows the 22 viscosities at different shear rates using water alone and an aqueous mixture 23 containing 10% by volume of ethanol at a weight ratio of 2:1 (gel:emulsifying 24 agent) using a viscous gel formed from SO % by weight of a 50:50 lactic acid:glycolic acid copolymer and 50% by weight of triacetin compared to the 26 viscosities of the viscous gel without emulsifying agent.
27 It is to be understood that the emulsifying agent of the present invention does 28 not constitute a mere diluent that reduces viscosity by simply decreasing the 29 concentration of the components of the composition. The use of conventional 1 diluents can reduce viscosity, but can also cause the burst effect mentioned 2 previously when the diluted composition is injected. In contrast, the injectable 3 depot composition of the present invention can be formulated to avoid the burst 4 effect by selecting the emulsifying agent so that once injected into place, the emulsifying agent has little impact on the release properties of the original system.
6 Further compositions without beneficial agent may be useful for wound healing, 7 bone repair and other structural support purposes.
8 To further understand the various aspects of the present invention, the results 9 set forth in the previously described Figures were obtained in accordance with the following examples.
12 Example 1 13 Lysozyme particles were made by spray drying 50 % sucrose and SO %
14 chicken lysozyme (on a dry weight basis).
A viscous gel material was preparE:d by heating 60 % by weight of triacetin 16 with 40% by weight of a 50:50 lactic acid:glycolic acid copolymer to 37°C
17 overnight. The viscous gel was allowed to cool to room temperature while mixing 18 continued. The lysozyme particles were added to the viscous gel in a ratio of 20:80 19 lysozyme particles:gel (by weight). The combination was mixed for 5 minutes.
Immediately prior to use, a 10 % ethanol, 90 % isotonic saline solution was added as 21 the emulsifying agent. The emulsifying agent comprised 1/3 of the total injectable 22 depot gel composition. 0.5 grams of this injectable depot composition was then 23 injected into a rat.
24 Exalr~ple 2 A viscous gel material is prepared by heating 60 % by weight of triacetin 26 with 40% by weight of a 50:50 lactic acid:glycolic acid copolymer to 37°C
27 overnight. The viscous gel is allowed to cool to room temperature while mixing is 28 continued. Immediately prior to use, lyso:ayme particles, prepared as in Example 1 29 and in the same amount, are combined with a 10% ethanol, 90% isotonic saline 1 solution, as an emulsifying agent, in the amount used in Example 1. The 2 emulsifying agent-lysozyme solution is mixed with the amount of gel material used 3 in Example 1 to form an injectable depot gel composition. The fabricated injectable 4 depot gel composition is suitable for injection into an animal.
In accordance with various aspects of the present invention, one or more 6 significant advantages can be obtained. lvlore specifically, using simple processing 7 steps, one can obtain a depot gel composition that can be injected into place in an 8 animal without surgery using a low dispensing force through standard needles.
9 Once in place, the composition will quickly return to its original viscosity and may exhibit rapid hardening so as to substantially avoid a burst effect and provide the 11 desired beneficial agent release profile. Furthermore, once the beneficial agent has 12 been fully administered, there is no need to remove the composition since it is fully 13 biodegradable. As a still fixrther advanta~;e, the present invention avoids the use of 14 microparticle or microcapsulation techniqvues which can degrade certain beneficial agents, like peptide and nucleic acid-based drugs and which microparticles and 16 microcapsules maybe difficult to remove from the environment of use. Since the 17 viscous gel is formed without the need for water, temperature extremes, or other 18 solvents, suspended particles of beneficial agent remain dry and in their original 19 configuration, which contributes to the stability of thereof. Further, since a mass is formed, the injectable depot gel composition may be retrieved from the environment 21 of use if desired.
22 The above-described exemplary err~bodiments are intended to be illustrative 23 in all respects, rather than restrictive, of the present invention. Thus the present 24 invention is capable of many variations in detailed implementation that can be derived from the description contained herein by a person skilled in the art.
All 26 such variations and modifications are considered to be within the scope and spirit of 27 the present invention as defined by the following claims.
Claims (32)
1. An injectable depot gel composition comprising:
A) a biocompatible polymer;
B) a solvent that dissolves the biocompatible polymer and forms a viscous gel;
C) a beneficial agent; and D) an emulsifying agent in the form of a dispersed droplet phase in the viscous gel.
A) a biocompatible polymer;
B) a solvent that dissolves the biocompatible polymer and forms a viscous gel;
C) a beneficial agent; and D) an emulsifying agent in the form of a dispersed droplet phase in the viscous gel.
2. The injectable gel depot composition of claim 1 wherein the biocompatible polymer is selected from the group consisting of polylactides, pelyglycolides, polycaprolactones, polyanhydrides, polyamines, polyurethanes, polyesteramides, polyorthoesters, polydioxanones, polyacetals, polyketals, polycarbonates, polyorthocarbonates, polyphosphazenes, succinates, poly(malic acid), poly(amino acids), polyvinylpyrrolidone, polyethylene glycol, polyhydroxycellulose, chitin, chitosan, and copolymers, terpolymers and mixtures thereof.
3. The injectable depot gel composition of claim 1 wherein the biocompatible polymer is a lactic acid-based polymer.
4. The injectable depot gel composition of claim 3, wherein the lactic acid-based polymer has a monomer ratio of lactic acid to glycolic acid in the range of 100:0 to about 15:85.
5. The injectable depot gel composition of claim 3, wherein the lactic acid-based polymer has a number average molecular weight of from 1,000 to 120,000.
6. The injectable depot gel composition of any one of claims 1 to 5, wherein the solvent that dissolves the biocompatible polymer and forms a viscous gel is selected from the group consisting of triacetin, N-methyl-2-pyrrolidone, 2-pyrrolidone, glycerol formal, methyl acetate, ethyl acetate, methyl ethyl ketone, dimethylformamide, dimethyl sulfoxide, tetrahydrofuran, caprolactam, decylmethylsulfoxide, oleic acid, and 1-dodecylazacyclo-heptan-2-one and mixtures thereof.
7. The injectable depot gel composition of any one of claims 1 to 5, wherein the solvent is selected from the group consisting of triacetin and N-methyl-2-pyrrolidone, and mixtures thereof.
8. The injectable depot gel composition of any one of claims 1 to 5, wherein the solvent is triacetin.
9. The injectable depot gel composition of any one of claims 1 to 8, wherein the polymer is present in an amount of from 5 to 80% by weight of the combined amounts of the polymer and the solvent.
10. The injectable depot gel composition of any one of claims 1 to 9, wherein the solvent is present in an amount of from 95 to 20% by weight of the combined amounts of the polymer and the solvent.
11. The injectable depot gel composition of any one of claims 1 to 10, wherein the viscous gel formed by the polymer and the solvent has a viscosity of from 1,000 to 200,000 poise.
12. The injectable depot gel composition of any one of claims 1 to 11, wherein the beneficial agent is a drug.
13. The injectable depot gel composition of any one of claims 1 to 11, wherein the beneficial agent is a peptide.
14. The injectable depot gel composition of any one of claims 1 to 11, wherein the beneficial agent is a protein.
15. The injectable depot gel composition of any one of claims 1 to 11, wherein the beneficial agent is growth hormone.
16. The injectable depot gel composition of any one of claims 1 to 15, wherein the beneficial agent is present in an amount of from 1 to 50% by weight of the combined amounts of the polymer, the solvent and the beneficial agent.
17. The injectable depot gel composition of any one of claims 1 to 16, wherein the beneficial agent is in the form of particles dispersed or dissolved in the viscous gel.
18. The injectable depot gel composition of claim 17, wherein the beneficial agent is in the form of particles having an average particle size of from 0.1 to 100 microns.
19. The injectable depot gel composition of any one of claims 1 to 18, wherein the emulsifying agent is selected from the group consisting of water, alcohols, polyols, esters, carboxylic acids, ketones, aldehydes and mixtures thereof.
20. The injectable depot gel composition of any one of claims 1 to 18, wherein the emulsifying agent is selected from the group consisting of alcohols, propylene glycol, ethylene glycol, glycerol, water and solutions and mixtures thereof.
21. The injectable depot gel composition of any one of claims 1 to 18, wherein the emulsifying agent is selected from the group consisting of ethanol, isopropyl alcohol, water, solutions thereof, and mixtures thereof.
22. The injectable depot gel composition of any one of claims 1 to 18, wherein the emulsifying agent is water.
23. The injectable depot gel composition of any one of claims 1 to 22, wherein the emulsifying agent is present in an amount of from 5 to 80% by weight of the injectable depot gel composition.
24. A method of preparing an injectable depot gel composition comprising:
A) mixing a biocompatible polymer and a solvent whereby the solvent dissolves the polymer and forms a viscous gel;
B) dispersing or dissolving a beneficial agent in the viscous gel to form a beneficial agent containing viscous gel; and C) mixing an emulsifying agent with the beneficial agent containing viscous gel, said emulsifying agent forming a dispersed droplet phase in the beneficial agent containing viscous gel to provide the injectable depot gel composition.
A) mixing a biocompatible polymer and a solvent whereby the solvent dissolves the polymer and forms a viscous gel;
B) dispersing or dissolving a beneficial agent in the viscous gel to form a beneficial agent containing viscous gel; and C) mixing an emulsifying agent with the beneficial agent containing viscous gel, said emulsifying agent forming a dispersed droplet phase in the beneficial agent containing viscous gel to provide the injectable depot gel composition.
25. A method of preparing an injectable depot gel composition comprising:
A) mixing a biocompatible polymer and a solvent whereby the solvent dissolves the polymer to form a viscous gel;
B) dispersing or dissolving a beneficial agent in an emulsifying agent to form a beneficial agent containing emulsifying agent; and C) mixing the beneficial agent containing emulsifying agent with the viscous gel, said beneficial agent containing emulsifying agent forming a dispersed droplet phase in the viscous gel to provide the injectable depot composition.
A) mixing a biocompatible polymer and a solvent whereby the solvent dissolves the polymer to form a viscous gel;
B) dispersing or dissolving a beneficial agent in an emulsifying agent to form a beneficial agent containing emulsifying agent; and C) mixing the beneficial agent containing emulsifying agent with the viscous gel, said beneficial agent containing emulsifying agent forming a dispersed droplet phase in the viscous gel to provide the injectable depot composition.
26. An injectable depot gel composition comprising:
A) a biocompatible polymer;
B) a solvent that dissolves the polymer and forms a viscous gel; and C) an emulsifying agent in the form of a dispersed droplet phase in the viscous gel.
A) a biocompatible polymer;
B) a solvent that dissolves the polymer and forms a viscous gel; and C) an emulsifying agent in the form of a dispersed droplet phase in the viscous gel.
27. A kit adapted to provide an injectable depot composition comprising as kit components: (a) a biocompatible polymer and a solvent that dissolves the polymer and forms a viscous gel; (b) emulsifying agent; and (c) beneficial agent.
28. The injectable depot gel composition of claim 26, wherein the biocompatible polymer is selected from the group consisting of polylactides, polyglycolides, polycaprolactones, polyanhydrides, polyamines, polyurethanes, polyesteramides, polyorthoesters, polydioxanones, polyacetals, polyketals, polycarbonates, polyorthocarbonates, polyphosphazenes, succinates, poly(malic acid), poly(amino acids), polyvinylpyrrolidone, polyethylene glycol, polyhydroxycellulose, chitin, chitosan, and copolymers, terpolymers and mixtures thereof.
29. The injectable depot gel composition of claim 26 or 28, wherein the solvent that dissolves the biocompatible polymer and forms a viscous gel is selected from the group consisting of triacetin, N-methyl-2-pyrrolidone, 2-pyrrolidone, glycerol formal, methyl acetate, ethyl acetate, methyl ethyl ketone, dimethylformamide, dimethyl sulfoxide, tetrahydrofuran, caprolactam, decylmethylsulfoxide, oleic acid, and 1-dodecylazacyclo-heptan-2-one and mixtures thereof.
30. The injectable depot gel composition of claim 26, 28 or 29, wherein the polymer is present in an amount of from 5 to 80% by weight of the combined amounts of the polymer and the solvent and the solvent is present in an amount of from 95 to 20% by weight of the combined amounts of the polymer and the solvent.
31. The injectable depot gel composition of claim 26, 28, 29 or 30, wherein the emulsifying agent is selected from the group consisting of water, alcohols, polyols, esters, carboxylic acids, ketones, aldehydes and mixtures thereof.
32. The injectable depot gel composition of claim 26, 28, 29 or 30, wherein the emulsifying agent is selected from the group consisting of alcohols, propylene glycol, ethylene glycol, glycerol, water and solutions and mixtures thereof.
Applications Claiming Priority (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US3343996P | 1996-12-20 | 1996-12-20 | |
| US60/033,439 | 1996-12-20 | ||
| PCT/US1997/023341 WO1998027962A2 (en) | 1996-12-20 | 1997-12-18 | Injectable depot gel composition and method of preparing the composition |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2275587A1 CA2275587A1 (en) | 1998-07-02 |
| CA2275587C true CA2275587C (en) | 2006-10-24 |
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| CA2275525A Expired - Fee Related CA2275525C (en) | 1996-12-20 | 1997-12-18 | Gel composition and methods |
| CA2591581A Expired - Fee Related CA2591581C (en) | 1996-12-20 | 1997-12-18 | Gel composition and methods |
| CA002275587A Expired - Fee Related CA2275587C (en) | 1996-12-20 | 1997-12-18 | Injectable depot gel composition and method of preparing the composition |
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| Application Number | Title | Priority Date | Filing Date |
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| CA2275525A Expired - Fee Related CA2275525C (en) | 1996-12-20 | 1997-12-18 | Gel composition and methods |
| CA2591581A Expired - Fee Related CA2591581C (en) | 1996-12-20 | 1997-12-18 | Gel composition and methods |
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| US (6) | US6331311B1 (en) |
| EP (2) | EP0949905B1 (en) |
| JP (4) | JP4642946B2 (en) |
| KR (1) | KR100616793B1 (en) |
| CN (1) | CN1146402C (en) |
| AT (2) | ATE318580T1 (en) |
| AU (2) | AU5609798A (en) |
| CA (3) | CA2275525C (en) |
| DE (2) | DE69705746T2 (en) |
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| NZ (1) | NZ335851A (en) |
| PT (2) | PT949905E (en) |
| WO (2) | WO1998027962A2 (en) |
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1997
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- 1997-12-18 IL IL13053297A patent/IL130532A0/en unknown
- 1997-12-18 US US08/993,031 patent/US6331311B1/en not_active Expired - Lifetime
- 1997-12-18 ES ES97952507T patent/ES2158611T3/en not_active Expired - Lifetime
- 1997-12-18 DK DK97952575T patent/DK0959873T3/en active
- 1997-12-18 AU AU56097/98A patent/AU5609798A/en not_active Abandoned
- 1997-12-18 WO PCT/US1997/023341 patent/WO1998027962A2/en active IP Right Grant
- 1997-12-18 CA CA2275525A patent/CA2275525C/en not_active Expired - Fee Related
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- 1997-12-18 CA CA2591581A patent/CA2591581C/en not_active Expired - Fee Related
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- 1997-12-18 AU AU56154/98A patent/AU739469B2/en not_active Ceased
- 1997-12-18 KR KR1019997005514A patent/KR100616793B1/en not_active IP Right Cessation
- 1997-12-18 AT AT97952575T patent/ATE318580T1/en active
- 1997-12-18 JP JP52891698A patent/JP2002512597A/en not_active Withdrawn
- 1997-12-18 NZ NZ335851A patent/NZ335851A/en not_active IP Right Cessation
- 1997-12-18 DK DK97952507T patent/DK0949905T3/en active
- 1997-12-18 PT PT97952507T patent/PT949905E/en unknown
- 1997-12-18 PT PT97952575T patent/PT959873E/en unknown
- 1997-12-18 ES ES97952575T patent/ES2256898T3/en not_active Expired - Lifetime
- 1997-12-18 AT AT97952507T patent/ATE203157T1/en active
- 1997-12-18 WO PCT/US1997/023659 patent/WO1998027963A2/en active IP Right Grant
- 1997-12-18 EP EP97952575A patent/EP0959873B1/en not_active Expired - Lifetime
- 1997-12-18 US US08/993,208 patent/US6130200A/en not_active Expired - Lifetime
- 1997-12-18 CA CA002275587A patent/CA2275587C/en not_active Expired - Fee Related
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1999
- 1999-11-12 HK HK99105227A patent/HK1020009A1/en not_active IP Right Cessation
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2000
- 2000-03-21 US US09/532,337 patent/US6673767B1/en not_active Expired - Fee Related
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- 2000-07-13 US US09/615,568 patent/US6468961B1/en not_active Expired - Fee Related
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2001
- 2001-09-12 GR GR20010401458T patent/GR3036599T3/en unknown
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2002
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2010
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