US20220370620A1

Movatterモバイル変換

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Publication number: US20220370620A1
Application number: US17/736,028
Authority: US
Inventors: Steven Siegel; Karen Winey
Original assignee: University of Pennsylvania Penn
Current assignee: University of Pennsylvania Penn
Priority date: 2005-07-18
Filing date: 2022-05-03
Publication date: 2022-11-24
Also published as: US8221778B2; US9925268B2; US20200368358A1; US8802127B2; US10111960B2; US10736965B2; US8741327B2; US20170319701A1; US9895447B2; US20090297572A1; US20060153895A1; US9439905B2; US20140343080A1; US20160361421A1; US20170319700A1; US20190105396A1; US20130064773A1; US9717799B2; CN101287423A; US20180125984A1

Abstract

The present invention provides implants comprising a therapeutic drug and a polymer containing polylactic acid (PLA) and optionally polyglycolic acid (PGA). The present invention also provides methods of maintaining a therapeutic level of a drug in a subject, releasing a therapeutic drug at a substantially linear rate, and treating schizophrenia and other diseases and disorders, utilizing implants of the present invention.

Description

FIELD OF INVENTION

BACKGROUND OF THE INVENTION

Medication noncompliance is the highest determinant of relapse in schizophrenia. Therefore, a therapy method that helps patients remain on medication for extended periods would substantially improve clinical outcomes. Current methods of administering anti-schizophrenia medication (e.g. risperidone) provide dosing for one month or less. Thus, methods of providing therapeutic levels of risperidone and other medications are needed in the art.

SUMMARY OF THE INVENTION

In one embodiment, the present invention provides a biodegradable implant comprising (a) a therapeutic drug present in an amount of 10%-60% by mass, relative to the mass of the implant; and (b) a polymer present in an amount of 40%-90% by mass, relative to the mass of the implant, the polymer comprising PLA and optionally PGA in a PLA:PGA molar ratio between 50:50 and 100:0.

In another embodiment, the present invention provides a method for maintaining a therapeutic level of a drug in a subject for a period of at least about 1 month, comprising administering to the subject a set of biodegradable implants, the set of biodegradable implants consisting of one or more individual biodegradable implants comprising (a) a therapeutic drug present in an amount of 10%-60% by mass, relative to the mass of the implant; and (b) a polymer present in an amount of 40%-90% by mass, relative to the mass of the implant, the polymer comprising PLA and optionally PGA in a PLA:PGA molar ratio between 50:50 and 100:0 and wherein the individual biodegradable implants, if more than one in number, do not differ substantially from one another in their PLA:PGA molar ratio, thereby maintaining a therapeutic level of a drug in a subject for a period of at least about 1 month.

BRIEF DESCRIPTION OF THE FIGURES

FIG. 1: Longitudinal detection of haloperidol levels for 443 days in primates as a result of implants.

FIG. 2A,FIG. 2B,FIG. 2C,FIG. 2D andFIG. 2E. Placement of implants during rabbit surgery. A tethered implant (white arrow) is shown. The incision was enlarged to enable a photograph.FIG. 2B) Necropsy in rabbits showing a degraded implant (black arrow) at the tethering location between two hemostats. No fibrosis was observed upon implant removal. Scale bar=20 mm in both images.FIG. 2C) 1HNMR spectra of PLA and 40% (w/w) haloperidol mixture in DMSO-d6. Inset—corresponding haloperidol and PLA chemical structures.FIG. 2D) Rabbit sample in DMSO-d6, peaks correspond to peaks seen for haloperidol in control spectra.FIG. 2E) Rabbit sample in chloroform, peaks at 0.9, 1.2, 3.9, and 4.5 are consistent with the degradation product of PLA, lactic acid.

FIG. 3A andFIG. 3B. Haloperidol serum concentration from polymer implants in rabbit. Each panel displays the mean±SEM for 5 animals.FIG. 3A) Multiple-polymer system.FIG. 3B) Single-polymer system. Each set of data is shown with a trendline to illustrate the pattern of the serum concentration over time.

FIG. 4: Cumulative in vitro concentration from disc & rod-shaped implants. Each point represents the mean for 3 replicates of discs or rods.

FIG. 5A andFIG. 5B. Stability of risperidone in physiological aqueous solution.FIG. 5A) Amount of remaining risperidone vs. time. The y-intercept is 10.42 for HPLC and 10.23 mg for UV spectrophotometry. Similarly, the slope of the linear trendline for HPLC is 0.01 and 0.00 for UV spectrophotometry.FIG. 5B) Values for the positive control solution in A, as well as samples in the surface area to volume ratio study (FIG. 6B) were analyzed and compared using HPLC and UV spectrophotometry. The correlation coefficient for these methods is 0.99 (182 samples), showing that UV spectrophotometry is an accurate measure of drug level in an in vitro solution.

FIG. 6A andFIG. 6B. In vitro risperidone release varies with polymer composition and SA:V ratio:FIG. 6A) Polymer composition—Cumulative in vitro risperidone release from 20% load implants containing 50:50, 65:35, or 75:25 PLGA. Data are expressed as cumulative % total release over time. Each point represents the mean±standard error of the mean (SEM) of 3 implants. Full release occurred at about 40, 80 & 120 days, respectively.FIG. 6B) SA to volume ratio—Rods with the smaller radius, and hence larger SA:V ratio (circles) exhibited faster in vitro release than rods with larger radius (triangles), as evidenced by higher cumulative concentration between 28 and 44 days. Points represent mean±SEM from 4 rods. Data were analyzed with HPLC and UV spectrophotometry, which produced identical results, as inFIG. 5.

FIG. 7A,FIG. 7B,FIG. 7C andFIG. 7D. In vitro cumulative risperidone release from implants containing 85:15 PLGA with 10, 20, 30, 40, 50 or 60% drug load by weight.FIG. 7A) Cumulative mass of risperidone in the in vitro solution (mean±SEM).FIG. 7B) The pattern for the 40% risperidone implants is shown alone for clarity. The trendline, which has a correlation coefficient of 0.99, is included to illustrate the pattern.FIG. 7C) Cumulative mass released from 30, 40, 50, and 60% risperidone implants is expressed as a percentage of the total drug to facilitate comparison of the pattern of release as a function of drug load. The mean value for each type of implant is also depicted. Trendlines for each of these 4 implants had correlation coefficients (R2) of 0.99. 10% and 20% curves were omitted to increase visibility of overlapping lines.FIG. 7D) The 40% drug load group is shown alone for increased clarity.

FIG. 8A andFIG. 8B. Risperidone implants increase PPI (FIG. 8B) but not startle (FIG. 8A). Risperidone implants increased PPI (p=0.052) without a significant change in startle at 14 and 21 days post implantation.

FIG. 9A andFIG. 9B. Risperidone implants increase the P20 and block amphetamine-induced disruption of the N40 evoked potentials.FIG. 9A) Risperidone implants increased P20 amplitude in C57BL/6J mice (p=0.03) andFIG. 9B) attenuated amphetamine reduction of N40 (p=0.02).

FIG. 10. Amount of drug released (normalized to the total amount) as a function of time for different drugs. Although all release profiles follow a similar S shape, the rates were quite different, both in the region of initial release, the slope of the constant release zone (where Df/Dt is constant) and the characteristic time for full release (f=1).

FIG. 11A andFIG. 11B. Fit of the haloperidol (FIG. 11A) and ibuprofene (FIG. 11B) data to the model presented inequation 4, using the fit parameters D and k: For (FIG. 11A) k is approximately 0.1 (1/days) and D is 0.045. For (FIG. 11B) k is approximately 0.164 (1/days) and D is 0.051.

FIG. 12. Relationship between maximal solubility of drugs in water after 14 days (in mg/mL) and D, the diffusion coefficient of water into the polymer/drug complex, as calculated from fit of the data inFIG. 10 toequation 4. D is proportional to solubility to the power of 5.3.

FIG. 13A,FIG. 13B andFIG. 13C: Model for continuous delivery from biodegradable implants:

FIG. 13A) Pattern of serum concentration that results from one or more single-polymer implants. Trendlines represent the drug release pattern.FIG. 13B) Superimposed profiles for each of 4 implantations of the single-polymer implant system. Re-implantation for this polymer-drug combination is performed every 6 months.FIG. 13C) The total serum concentration that results from individual overlapping implantations (dashed lines) is shown with a sold line. Levels oscillate slightly, but remain within the target range for as long as implantations occur near the time of peak concentration for a given material. Arrows mark implantations in all panels.

FIG. 14A andFIG. 14B. Risperidone serum concentration resulting from a multiple-polymer risperidone implant system.FIG. 14A) Serum concentration resulting from a set of 4 rapid-release implants.FIG. 14B) Serum concentration resulting from a 5-polymer system, in which 4 rapidly degrading polymers (“starter set”) are combined with 1 longer lasting polymer that is re-implanted every 6 months as a maintenance set. Overall drug concentration is represented with the solid line, and release profiles from individual polymers are represented by dashed lines. Target drug levels are attained in approximately 1 week, with small oscillations around the target concentration thereafter.

FIG. 15A,FIG. 15B,FIG. 15C,FIG. 15D,FIG. 15E,FIG. 15F,FIG. 15G andFIG. 15H. Insertion and removal of rod-shaped implants.FIG. 15A) Insertion of a 1-cm rod-shaped implant through a 4-mm hole. Insert illustrates a 1-cm implant prior to insertion.FIG. 15B) Insertion of implant through a 4 mm hole using a trochar.FIG. 15C) Implant site after closing with a single stitch. FIG.15D)Mouse 10 minutes later in home cage with no signs of distress.FIG. 15E) Amouse 2 weeks after implantation. Implant site is completely healed, with no signs of distress or adverse events noted.FIG. 15F) A subset of mice had implants removed 2 or 4 weeks after implantation to assess reversibility of the procedure.FIG. 15G) Implants were easily removed at both points without signs of adhesions or local scarring. Insetremoved implant.FIG. 15H) A mouse shown back in itshome cage 10 minutes after implant removal. Mice in these groups were then sacrificed and serum risperidone and 9-OH risperidone levels obtained. Sterile risperidone implants yielded serum risperidone levels of 7.3 at 2 weeks post implantation and 12.8 at 4 weeks post implantation.

FIG. 16. Representative cross-sectional shapes of rods, disks, and cylinders of implants of the present invention (a non-exhaustive listing).

FIG. 17. In vitro risperidone concentration from implants. mean±S.E.M, n=4.

FIG. 18. Release profiles of sterile and non-sterile implants in mice. sterile (S) or un-sterile (U) n=4 each per time point.

FIG. 19. Risperidone content in implants removed from mice, expressed as percentage of implant mass.

FIG. 20A andFIG. 20B.FIG. 20A. Risperidone stability in solutions of pH 7.4, 6.4, 5.4 and 4.4. All samples remained stable, with negligible daily change in drug mass over the first 77 days of testing (0.06% for pH 7.4, 0.04% for pH 6.4, 0.10% for pH 5.4 and 0.00% for pH 4.4).FIG. 20B. Risperidone stability at pH 2.0-7.4.

DETAILED DESCRIPTION OF THE INVENTION

In one embodiment, the present invention provides an implantable, long term delivery system for improving medication adherence in disorders associated with a likelihood of non-compliance. The delivery system, in one embodiment, includes a therapeutic drug in an implantable, rod shaped structure and improves medication adherence in subjects having disorders associated with a likelihood of non-compliance.

The term “implantable” includes, in various embodiments, compositions which can be inserted into the subject, e.g., subcutaneously, intramuscularly, etc. In a further embodiment, the implantable compositions are also removable.

The term “long term” includes, in various embodiments, periods of time greater than about three months, greater than about four months, greater than about five months, greater than about six months, greater than about seven months, greater than about eight months, greater than about nine months, greater than about ten months, greater than about eleven months, greater than about one year or longer.

The language “improving medication adherence” refers, in one embodiment, to increasing the percentage of time subjects with a disorder associated with a likelihood of non-compliance are treated for their disorder with the target therapeutic drug.

The language “disorder associated with a likelihood of non-compliance” includes, in one embodiment, psychotic disorders, such as schizophrenia, bipolar disorder, dementia, delirium, impulse control disorder, psychotic depression, drug addiction, etc. The language “disorder associated with a likelihood of non-compliance” refers, in one embodiment, to disorders which have a high rate of subject non-compliance. It includes, in another embodiment, disorders where the disorder affects the subject's judgment or mental capacity. The language includes, in another embodiment, disorders with a low rate (e.g., in various embodiments, below 90%, below 80%, below 70%, below 60%, below 50%, below 40% and below 30%) of subject compliance.

The term “therapeutic drug” includes, in one embodiment, drugs used to treat disorders associated with a likelihood of non-compliance. In another embodiment, the therapeutic drug exhibits enhanced solubility in a reduced pH environment. In another embodiment, the therapeutic drug is an anti-depressant. In another embodiment, the therapeutic drug is an anti-anxiety agent. In another embodiment, the therapeutic drug is an anti-psychotic agent. In another embodiment, the target therapeutic drug is a birth control drug.

In another embodiment, the present invention provides a biodegradable implant comprising (a) a therapeutic drug present in an amount of 10%-60% by mass, relative to the mass of the implant; and (b) a polymer present in an amount of 40%-90% by mass, relative to the mass of the implant, the polymer comprising PLA and optionally PGA in a PLA:PGA molar ratio between 50:50 and 100:0.

In another embodiment, an implant of methods and compositions of the present invention is a sterile implant. In another embodiment, the implant need not be sterile. In another embodiment, the implant is substantially sterile. In another embodiment, the implant has been sterilized. In another embodiment, the implant is sterile, except for minor contamination introduced between removal from the sterile wrapper and implantation. Each possibility represents a separate embodiment of the present invention.

The term “biodegradable,” as used herein, refers, in one embodiment, to a material that is degraded in a biological environment. In another embodiment, “biodegradable” refers to a material that has a finite half-life in a biological environment. In another embodiment, “biodegradable” refers to a material that has a measurable half-life in a biological environment. In another embodiment, “biodegradable” refers to a material that is degraded inside a living organism. In another embodiment, “biodegradable” refers to a material that has a finite half-life inside a living organism. In another embodiment, “biodegradable” refers to a material that has a measurable half-life inside a living organism. In another embodiment, the term “biodegradable” is equivalent to the term “bioerodible.”

“Polymer” refers, in one embodiment, to a macromolecule composed of individual units, or monomers. In another embodiment, the polymer is a branched polymer. In another embodiment, the polymer is a linear polymer. In another embodiment, the polymer is a cross-linked polymer. In another embodiment, the polymer is any other type of polymer known in the art. Each possibility represents a separate embodiment of the present invention.

PLA:PGA polymers contain PLA and PGA monomers, while PLA polymers contain only PLA monomers. Methods for use and synthesis of PLA polymers and PLA:PGA polymers are well known in the art, and are described, for example, in Fukushima K et al (Macromol Biosci 5(1): 21-9, 2005); Saulnier B et al (Macromol Biosci 15; 4(3): 232-7, 2004); and Park S J et al (J Colloid Interface Sci 271(2): 336-41, 2004). Each method represents a separate embodiment of the present invention.

In one embodiment, an implant of methods and compositions of the present invention is rod shaped. As provided herein, results of the present invention show that rod-shaped implants as well as disk-shaped implants can be used to provide extended delivery of risperidone and other drugs. In another embodiment, the implant is disc shaped. In another embodiment, implant is cylindrical. In another embodiment, implant is a sheet. In another embodiment, the implant is any shape suitable for retention in a body tissue. (e.g. subcutaneous tissue). In another embodiment, the implant is any shape suitable for structural stability in the subcutaneous space. In another embodiment, the implant is any shape suitable for tolerability in the subcutaneous space. In another embodiment, the implant is any other shape known in the art.

In one embodiment, the rods, disks, and cylinders referred to herein have a substantially circular cross-sectional shape. In another embodiment, the cross-sectional shape is ellipsoidal. In another embodiment, the ellipsoidal shape need not be round at the edges. In another embodiment, the cross-sectional shape is any shape inFIG. 16. In another embodiment, the cross-sectional shape is any other shape known in the art. Because the present invention has shown that release rate of drug from an implant is proportional to its surface area, the shape of the implant can be modified, in one embodiment, to confer thereupon desirable characteristics without altering the release rate, provided that the surface area remains constant. The present invention has shown that duration of release of drug from an implant is proportional to its SA:V ratio; thus, the shape of the implant can be modified, in one embodiment, to confer thereupon desirable characteristics without altering the duration of release, provided that the SA:V ratio remains constant. Each shape represents a separate embodiment of the present invention.

In another embodiment, the ratio of the longest to the shortest diameter is any other ratio consistence with a substantially circular shape. In another embodiment, the number is any other number that describes a substantially circular shape. Each possibility represents another embodiment of the present invention.

In another embodiment, the cross-sectional area is substantially constant over the length of the rods, disks, and cylinders of the present invention. In another embodiment, the cross-sectional area is not constant. In another embodiment, the cross-sectional dimensions are substantially constant over the length of the rods, disks, and cylinders of the present invention. In another embodiment, the cross-sectional dimensions are not constant. Each possibility represents a separate embodiment of the present invention.

In another embodiment, an implant of the present invention has a rectangular cross-sectional shape. In another embodiment, the cross-sectional shape is a square. In another embodiment, the cross-sectional shape is any other shape known in the art.

In another embodiment, the implant is monolithic. In another embodiment, the implant is composed of several (10 or fewer) smaller components that are fused together. In another embodiment, the components are linked together. Each possibility represents a separate embodiment of the present invention.

Each of the above overall shapes and cross-sectional shapes represents a separate embodiment of the present invention.

Methods of insertion of implants are well known in the art. In one embodiment, implants are inserted through a minimally invasive approach, using a surgical instrument known as a “trochar.” In another embodiment, the implants are inserted utilizing a procedure and tool set (trochar and obdurator) similar to those used for Norplant (Townsend S “Insertion and removal of Norplant” Netw Fr 6: 8-9, 1991). In another embodiment, rod-shaped implants provide an advantage due to their ease of implantation and lack of subsequent discomfort (FIG. 15). In another embodiment, an advantage of rod-shaped implants is the small incisions required for their insertion; e.g. in various embodiments, about 2 mm, 3 mm, 4 mm, 5 mm, 6 mm, or 7 mm. In another embodiment, implants provide an advantage due to their ability to be implanted on an outpatient basis. The incision site is closed, in another embodiment, with either a single stitch or steristrips (FIG. 15). In another embodiment, the implant is inserted by any other surgical method known in the art. Each method represents a separate embodiment of the present invention.

In another embodiment, implants of the present invention provide an advantage due to their lack of necessity of the subject receiving injections every few weeks, thus increasing patient compliance. In another embodiment, the advantage of the implants is due to the resulting increased patient autonomy. In another embodiment, the advantage of the implants is due to their lack of irritation at the site of administration.

In another embodiment, an advantage of implants of the present invention is due to their stability at body temperature for the delivery period.

In another embodiment, the advantage of the implants is due to their ability to completely erode, thus exhibiting a lack of necessity of removing residual material. In one embodiment, the erosion is primarily surface erosion. In another embodiment, the erosion is primarily bulk erosion. In another embodiment, the erosion is a combination of substantial amounts of surface erosion and bulk erosion. Each possibility represents a separate embodiment of the present invention.

In another embodiment, an implant of methods and compositions of the present is tethered (FIG. 2) to assist in locating it and, if necessary, removing it. As provided herein, the removal process has been successfully tested in mice and rats. In another embodiment, following palpation of the implant, a small incision is made and residual material from the implant is retrieved using forceps.

“Easily removable” refers, in another embodiment, to an ability to be removed using forceps or a similar tool. In another embodiment, the term refers to an ability to be removed without the use of strong suction. In another embodiment, the term refers to an ability to be removed without the necessity to remove surrounding tissue. Each possibility represents a separate embodiment of the present invention.

In another embodiment, implants of the present invention exhibit the advantage that the internal pH environment drops as the polymer degrades to constituent monomers. The drop in pH upon degradation improves the time-dependent release, in another embodiment, of drugs and active agents that are insoluble at neutral pH (and thus locked in the implant), but become increasingly soluble as pH drops. In another embodiment, the implants improve release of drugs with increased solubility at low pH. In another embodiment, the implants improve release of drugs with an acidic pKa. In another embodiment, the increased time-dependent release increases ability of the compound to be released into the systemic circulation.

In another embodiment, the drug with pH-dependent solubility is haloperidol. In another embodiment, the pH-dependent drug is risperidone. In another embodiment, the pH-dependent drug is any other drug with pH-dependent solubility known in the art. Each possibility represents another embodiment of the present invention.

In another embodiment, the drop in pH upon degradation increases the rate of degradation of the polymer with respect to time. In another embodiment, the drop in pH upon degradation results in auto-catalysis of degradation of the polymer. Each possibility represents a separate embodiment of the present invention.

In another embodiment, implants of the present invention exhibit the advantage of a drop in pH upon degradation, which is not observed with smaller dosage forms (e.g. microparticles).

In another embodiment, a polymer utilized in methods and compositions of the present invention comprises PLA but not PGA. In another embodiment, the polymer comprises PLA and PGA. In another embodiment, the polymer consists of PLA alone. In another embodiment, the polymer consists of PLA and PGA. Each possibility represents a separate embodiment of the present invention.

In another embodiment, the drug load of an implant of methods and compositions of the present invention is between 30-60%. As provided herein (Example 7), results of the present invention have demonstrated the efficacy of particular drug load ranges of biodegradable implants. “Drug load” refers, in one embodiment, to the amount of drug in the implant as a percentage by mass. In another embodiment, “drug load” refers to the percentage by weight of the drug. In another embodiment, e.g. if other materials are present in the implant besides the therapeutic drug and the polymer, the drug load is calculated without considering the other materials. Each possibility represents a separate embodiment of the present invention.

Numerical and other ranges used to describe methods and compositions of the present invention are understood to be inclusive of the boundary values. Each value or combination of values within the range represents a separate embodiment of the present invention.

PLA polymers and PLA:PGA polymers exhibit an advantage, in one embodiment, that drugs need not be chemically modified before incorporation therein; rather, they need only be mechanically mixed into the polymeric matrix. Thus, a wide variety of therapeutic agents can be incorporated.

In other embodiments, the therapeutic drug is a dopaminergic agent. In one embodiment, the dopaminergic agent is an agonist. In one embodiment, the dopaminergic agent is an antagonist. In one embodiment, the dopaminergic agent is a partial agonist. In one embodiment, the dopaminergic agent is a monoamine reuptake inhibitor. In one embodiment, the dopaminergic agent is a monoamine uptake facilitators.

In other embodiments, the therapeutic drug is one of the following drugs, or belongs to one of the following classes: antihypertensives, antidepressants, antianxiety agents, anticlotting agents, anticonvulsants, blood glucose-lowering agents, decongestants, antihistamines, antitussives, anti-inflammatories, antipsychotic agents, cognitive enhancers, cholesterol-reducing agents, antiobesity agents, autoimmune disorder agents, anti-impotence agents, antibacterial and antifungal agents, hypnotic agents, anti-Parkinsonism agents, antibiotics, antiviral agents, anti-neoplastics, barbituates, sedatives, nutritional agents, beta blockers, emetics, anti-emetics, diuretics, anticoagulants, cardiotonics, androgens, corticoids, anabolic agents, growth hormone secretagogues, anti-infective agents, coronary vasodilators, carbonic anhydrase inhibitors, antiprotozoals, gastrointestinal agents, serotonin antagonists, anesthetics, hypoglycemic agents, anti-Alzheimer's Disease agents, anti-ulcer agents, platelet inhibitors glycogen phosphorylase inhibitors, and phosphodiesterase inhibitors.

In other embodiments, the therapeutic drug is one of the following drugs: chlorpropamide, fluconazole, atorvastatin calcium, hydroxyzine hydrochloride, doxepin hydrochloride, amlodipine besylate, piroxicam, celicoxib, valdicoxib, carbenicillin indanyl sodium, bacampicillin hydrochloride, troleandomycin, and doxycycline hyclate.

In other embodiments, the therapeutic drug is one of the following drugs, or belongs to one of the following classes: platinum compounds (e.g., spiroplatin, cisplatin, and carboplatin), methotrexate, fluorouracil, adriamycin, mitomycin, ansamitocin, bleomycin, cytosine arabinoside, arabinosyl adenine, mercaptopolylysine, vincristine, busulfan, chlorambucil, melphalan (e.g., PAM, L-PAM or phenylalanine mustard), mercaptopurine, mitotane, procarbazine hydrochloride dactinomycin (actinomycin D), daunorubicin hydrochloride, doxorubicin hydrochloride, paclitaxel and other taxenes, rapamycin, manumycin A, TNP-470, plicamycin (mithramycin), aminoglutethimide, estramustine phosphate sodium, flutamide, leuprolide acetate, megestrol acetate, tamoxifen citrate, testolactone, trilostane, amsacrine (m-AMSA), asparaginase (L-asparaginase) Erwina asparaginase, interferon .alpha.-2a, interferon .alpha.-2b, teniposide (VM-26), vinblastine sulfate (VLB), vincristine sulfate, bleomycin sulfate, hydroxyurea, procarbazine, and dacarbazine; mitotic inhibitors, e.g. etoposide, colchicine, and the vinca alkaloids, radiopharmaceuticals, e.g. radioactive iodine and phosphorus products; hormones, e.g. progestins, estrogens and antiestrogens; anti-helmintics, antimalarials, and antituberculosis drugs; biologicals, e.g. immune serums, antitoxins and antivenoms; rabies prophylaxis products; bacterial vaccines; viral vaccines; respiratory products, e.g. xanthine derivatives theophylline and aminophylline; thyroid agents, e.g. iodine products and anti-thyroid agents; cardiovascular products including chelating agents and mercurial diuretics and cardiac glycosides; glucagon; blood products, e.g. parenteral iron, hemin, hematoporphyrins and their derivatives; biological response modifiers, e.g. muramyldipeptide, muramyltripeptide, microbial cell wall components, lymphokines (e.g., bacterial endotoxin, e.g. lipopolysaccharide, macrophage activation factor), sub-units of bacteria (such as Mycobacteria, Corynebacteria), the synthetic dipeptide N-acetyl-muramyl-L-alanyl-D-isoglutamine; anti-fungal agents, e.g. ketoconazole, nystatin, griseofulvin, flucytosine (5-fc), miconazole, amphotericin B, ricin, cyclosporins, and β-lactam antibiotics (e.g., sulfazecin); hormones, e.g. growth hormone, melanocyte stimulating hormone, estradiol, beclomethasone dipropionate, betamethasone, betamethasone acetate and betamethasone sodium phosphate, vetamethasone disodium phosphate, vetamethasone sodium phosphate, cortisone acetate, dexamethasone, dexamethasone acetate, dexamethasone sodium phosphate, flunisolide, hydrocortisone, hydrocortisone acetate, hydrocortisone cypionate, hydrocortisone sodium phosphate, hydrocortisone sodium succinate, methylprednisolone, methylprednisolone acetate, methylprednisolone sodium succinate, paramethasone acetate, prednisolone, prednisolone acetate, prednisolone sodium phosphate, prednisolone tebutate, prednisone, triamcinolone, triamcinolone acetonide, triamcinolone diacetate, triamcinolone hexacetonide, fludrocortisone acetate, oxytocin, vassopressin, and their derivatives; vitamins, e.g. cyanocobalamin neinoic acid, retinoids and derivatives, e.g. retinol palmitate, and .alpha.-tocopherol; peptides, e.g. manganese super oxide dismutase; enzymes, e.g. alkaline phosphatase; anti-allergic agents, e.g. amelexanox; anti-coagulation agents, e.g. phenprocoumon and heparin; circulatory drugs, e.g. propranolol; metabolic potentiators, e.g. glutathione; antituberculars, e.g. para-aminosalicylic acid, isoniazid, capreomycin sulfate cycloserine, ethambutol hydrochloride ethionamide, pyrazinamide, rifampin, and streptomycin sulfate; antivirals, e.g. amantadine azidothymidine (AZT, DDI, Foscarnet, or Zidovudine), ribavirin and vidarabine monohydrate (adenine arabinoside, ara-A); antianginals, e.g. diltiazem, nifedipine, verapamil, erythritol tetranitrate, isosorbide dinitrate, nitroglycerin (glyceryl trinitrate) and pentaerythritol tetranitrate; anticoagulants, e.g. phenprocoumon, heparin; antibiotics, e.g. dapsone, chloramphenicol, neomycin, cefaclor, cefadroxil, cephalexin, cephradine erythromycin, clindamycin, lincomycin, amoxicillin, ampicillin, bacampicillin, carbenicillin, dicloxacillin, cyclacillin, picloxacillin, hetacillin, methicillin, nafcillin, oxacillin, penicillin including penicillin G and penicillin V, ticarcillin rifampin and tetracycline; antiinflammatories, e.g. diflunisal, ibuprofen, indomethacin, meclofenamate, mefenamic acid, naproxen, oxyphenbutazone, phenylbutazone, piroxicam, sulindac, tolmetin, aspirin and salicylates; antiprotozoans, e.g. chloroquine, hydroxychloroquine, metronidazole, quinine and meglumine antimonate; antirheumatics, e.g. penicillamine; narcotics, e.g. paregoric; opiates, e.g. codeine, heroin, methadone, morphine and opium; cardiac glycosides, e.g. deslanoside, digitoxin, digoxin, digitalin and digitalis; neuromuscular blockers, e.g. atracurium mesylate, gallamine triethiodide, hexafluorenium bromide, metocurine iodide, pancuronium bromide, succinylcholine chloride (suxamethonium chloride), tubocurarine chloride and vecuronium bromide; sedatives (hypnotics), e.g. amobarbital, amobarbital sodium, aprobarbital, butabarbital sodium, chloral hydrate, ethchlorvynol, ethinamate, flurazepam hydrochloride, glutethimide, methotrimeprazine hydrochloride, methyprylon, midazolam hydrochloride, paraldehyde, pentobarbital, pentobarbital sodium, phenobarbital sodium, secobarbital sodium, talbutal, temazepam and triazolam; local anesthetics, e.g. bupivacaine hydrochloride, chloroprocaine hydrochloride, etidocaine hydrochloride, lidocaine hydrochloride, mepivacaine hydrochloride, procaine hydrochloride and tetracaine hydrochloride; general anesthetics, e.g. droperidol, etomidate, fentanyl citrate with droperidol, ketamine hydrochloride, methohexital sodium and thiopental sodium; and radioactive particles or ions, e.g. strontium, iodide rhenium and yttrium.

In another embodiment, the therapeutic drug is a metabolite of risperidone. In another embodiment, the therapeutic drug is a metabolite of one of the above drug. In one embodiment, the metabolite is an active metabolite.

In another embodiment, the therapeutic drug is a drug that is used chronically.

In another embodiment, the therapeutic drug is a high potency drug. “High potency agent” refers, in one embodiment, to a drug that requires a low serum concentration to exert a therapeutic effect. In another embodiment, “high potency agent” refers to a drug that requires a low tissue concentration to exert a therapeutic effect. In another embodiment, “high potency agent” refers to a drug that requires a low systemic concentration to exert a therapeutic effect. Each possibility represents a separate embodiment of the present invention.

Each therapeutic drug represents a separate embodiment of the present invention.

As described above, a wide variety of drugs can be incorporated into PLA polymers and PLA:PGA polymers. Before incorporation, the drug (or “active ingredient”) may be prepared by any method known in the art. The preparation of pharmaceutical compositions that contain an active ingredient, for example by mixing, granulating, or tablet-forming processes, is well understood in the art. The active therapeutic ingredient is mixed, in one embodiment, with excipients that are pharmaceutically acceptable and compatible with the active ingredient. In another embodiment, the active ingredient or one of its physiologically tolerated derivatives such as salts, esters, N-oxides, and the like is mixed with additives customary for this purpose, such as vehicles, stabilizers, or inert diluents.

An active component is, in another embodiment, formulated into the composition as neutralized pharmaceutically acceptable salt forms. Pharmaceutically acceptable salts include the acid addition salts (formed with the free amino groups of the polypeptide or antibody molecule), which are formed with inorganic acids such as, for example, hydrochloric or phosphoric acids, or such organic acids as acetic, oxalic, tartaric, mandelic, and the like. Salts formed from the free carboxyl groups can also be derived from inorganic bases such as, for example, sodium, potassium, ammonium, calcium, or ferric hydroxides, and such organic bases as isopropylamine, trimethylamine, 2-ethylamino ethanol, histidine, procaine, and the like.

Each of the above additives, excipients, formulations and methods of administration represents a separate embodiment of the present invention.

As provided herein (Example 5), results of the present invention have demonstrated the efficacy of particular drug PLA:PGA ratios of biodegradable implants. In one embodiment, the PLA:PGA ratio is a molar ratio. In another embodiment, the PLA:PGA ratio is a mass ratio. In another embodiment, the PLA:PGA ratio is a weight ratio. In another embodiment, the PLA:PGA ratio is a volume ratio. Each of the above PLA:PGA ratios represents a separate embodiment of the present invention.

Each of the above inherent viscosities represents a separate embodiment of the present invention.

“Inherent viscosity” refers, in one embodiment, to a measure of the capability of a polymer in solution to enhance the viscosity of the solution. In another embodiment, intrinsic viscosity increases with increasing polymer molecular weight, is a function of polymerization conditions, and may be varied independently of the PLA:PGA ratio of the polymer. In another embodiment, intrinsic viscosity is defined as the limiting value of the specific viscosity/concentration ratio at zero concentration. Thus, viscosity is determined at different concentrations and then is extrapolated to zero concentration. In another embodiment, “inherent viscosity” is a synonym for “intrinsic viscosity.” Each definition for “inherent viscosity” represents a separate embodiment of the present invention.

Methods for measuring inherent viscosity are well known in the art, and are described, for example, in Meek M F et al (J Biomed Mater Res A 68(1): 43-51, 2004) and Deng X et al (J Control Release 71(2):165-73, 2001). In another embodiment, inherent viscosity is measured as described in Example 1 of the present disclosure. In another embodiment, inherent viscosity is measured in chloroform. In another embodiment, inherent viscosity is measured in hexafluoroisopropanol solution. In another embodiment, inherent viscosity is measured in any other suitable solvent known in the art. In another embodiment, the solvent is an FDA Class III solvent (low toxicity with minimal need for removal of residual solvent). Each method represents a separate embodiment of the present invention.

As provided herein (Example 6), results of the present invention have demonstrated the efficacy of particular SA:V ratio ranges of biodegradable implants. Methods for measuring SA:V ratio are well known in the art. SA:V ratio is measured, in one embodiment, by calculating the surface area and volume from the measurements of the shape (e.g. for a regular shape). In another embodiment (e.g. for an irregular shape), surface area is measured using a BET (Brunauer, Emmett and Teller) apparatus (J de Kanel and J W Morse, J Phys E: Sci Instrum 12: 272-273, 1979). In another embodiment, surface area is measured using any other technique known in the art. In another embodiment, volume is measured by displacement of water or another fluid. In another embodiment, volume is measured using any other technique known in the art. Each possibility represents a separate embodiment of the present invention.

In another embodiment, an implant of methods and compositions of the present invention has a length between about 1-5 mm. “Length,” in one embodiment, refers to the longest dimension of the implant. In another embodiment, “length” refers to the length of the straight-edge dimension—e.g. in the case of a cylindrical-shaped implant. In another embodiment, the “straight-edge dimension” referred to need not be completely straight, but can be, e.g. a slight curve. Each possibility represents a separate embodiment of the present invention.

In another embodiment, an implant of methods and compositions of the present invention has a diameter between about 2-4 mm. “Diameter,” in one embodiment, refers to the distance across the cross-sectional area of the implant. In another embodiment, e.g. in the case of a disk-shaped implant, the distance across the cross-sectional area may be longer than the length described above. In another embodiment, e.g. in the case of a rod-shaped implant, the distance across the cross-sectional area is shorter than the length. In another embodiment, the cross-sectional area referred to need not be a circle, but may be an ellipse, square, rectangle, etc. as described above. Thus, in another embodiment, the diameter is the geometric mean of the longest and shortest diameters of the cross-sectional area. In another embodiment, the diameter is the arithmetic mean of the longest and shortest diameters thereof. In another embodiment, the diameter is the longest of the various diameters thereof. In another embodiment, the diameter is the distance across a diagonal of the cross-sectional area—e.g. in the case of a square or rectangle. In another embodiment, the diameter is the distance across the largest cross-sectional area—e.g. in a case in which the diameter varies over the length of implant. In another embodiment, the diameter is the average distance across the largest cross-sectional area. Each possibility represents a separate embodiment of the present invention.

Each of the above masses represents a separate embodiment of the present invention.

In another embodiment, implants of the present invention exhibit the advantage of having a larger potential drug load than technologies that utilize an emulsion process. In another embodiment, implants of the present invention exhibit the advantage of having a larger potential drug load due to the use of a detergent-free process, e.g. solvent casting. Each possibility represents a separate embodiment of the present invention.

In another embodiment, the invention provides a method for treating a subject for a disorder associated with a likelihood of non-compliance. The method includes administering to a subject a target therapeutic drug in a long-term delivery system comprising an implantable, rod shaped structure and the target therapeutic drug.

In another embodiment, the present invention provides a use of an implant or set of implants of the present invention for the preparation of a of a pharmaceutical composition for treating a subject for a disorder associated with a likelihood of non-compliance.

In another embodiment, the present invention provides a method for maintaining a therapeutic level of a drug in a subject for a period of at least about 1 month, comprising administering to the subject a set of biodegradable implants, the set of biodegradable implants consisting of one or more individual biodegradable implants having (a) a therapeutic drug present in an amount of 10%-60% by mass, relative to the mass of the implant; and (b) a polymer present in an amount of 40%-90% by mass, relative to the mass of the implant, the polymer comprising PLA and optionally PGA in a PLA:PGA molar ratio between 50:50 and 100:0 and wherein the individual biodegradable implants, if more than one in number, do not differ substantially from one another in their PLA:PGA molar ratio, thereby maintaining a therapeutic level of a drug in a subject for a period of at least about 1 month.

In another embodiment, the present invention provides a method for maintaining a therapeutic level of a drug in a subject for a period of at least about 2 months, comprising administering to the subject a set of biodegradable implants, the set of biodegradable implants consisting of one or more individual biodegradable implants having (a) a therapeutic drug present in an amount of 10%-60% by mass, relative to the mass of the implant; and (b) a polymer present in an amount of 40%-90% by mass, relative to the mass of the implant, the polymer comprising PLA and optionally PGA in a PLA:PGA molar ratio between 50:50 and 100:0 and wherein the individual biodegradable implants, if more than one in number, do not differ substantially from one another in their PLA:PGA molar ratio, thereby maintaining a therapeutic level of a drug in a subject for a period of at least about 2 months.

In another embodiment, the present invention provides a method for maintaining a therapeutic level of a drug in a subject for a period of at least about 3 months, comprising administering to the subject a set of biodegradable implants, the set of biodegradable implants consisting of one or more individual biodegradable implants having (a) a therapeutic drug present in an amount of 10%-60% by mass, relative to the mass of the implant; and (b) a polymer present in an amount of 40%-90% by mass, relative to the mass of the implant, the polymer comprising PLA and optionally PGA in a PLA:PGA molar ratio between 50:50 and 100:0 and wherein the individual biodegradable implants, if more than one in number, do not differ substantially from one another in their PLA:PGA molar ratio, thereby maintaining a therapeutic level of a drug in a subject for a period of at least about 3 months.

In another embodiment, the present invention provides a method for maintaining a therapeutic level of a drug in a subject for a period of at least about 4 months, comprising administering to the subject a set of biodegradable implants, the set of biodegradable implants consisting of one or more individual biodegradable implants having (a) a therapeutic drug present in an amount of 10%-60% by mass, relative to the mass of the implant; and (b) a polymer present in an amount of 40%-90% by mass, relative to the mass of the implant, the polymer comprising PLA and optionally PGA in a PLA:PGA molar ratio between 50:50 and 100:0 and wherein the individual biodegradable implants, if more than one in number, do not differ substantially from one another in their PLA:PGA molar ratio, thereby maintaining a therapeutic level of a drug in a subject for a period of at least about 4 months.

In another embodiment, the present invention provides a method for maintaining a therapeutic level of a drug in a subject for a period of longer than 4 months, comprising administering to the subject a set of biodegradable implants, the set of biodegradable implants consisting of one or more individual biodegradable implants having (a) a therapeutic drug present in an amount of 10%-60% by mass, relative to the mass of the implant; and (b) a polymer present in an amount of 40%-90% by mass, relative to the mass of the implant, the polymer comprising PLA and optionally PGA in a PLA:PGA molar ratio between 50:50 and 100:0 and wherein the individual biodegradable implants, if more than one in number, do not differ substantially from one another in their PLA:PGA molar ratio, thereby maintaining a therapeutic level of a drug in a subject for a period of longer than 4 months.

In another embodiment, the present invention provides a use of an implant or set of implants of the present invention for the preparation of a of a pharmaceutical composition for maintaining a therapeutic level of a drug in a subject for one of the above time periods.

In another embodiment, the individual implants are equivalent to one another in another parameter in addition to their PLA:PGA molar ratio, e.g. their drug load, mass, SA:V ratio, length, diameter, or inherent viscosity of the polymer. In another embodiment, the individual implants are equivalent to one another in their PLA:PGA ratio, but not in the other parameters. In another embodiment, the individual implants are equivalent to one another in two of these other parameters in addition to their PLA:PGA ratio. In another embodiment, the individual implants are equivalent to one another in three of these other parameters in addition to their PLA:PGA ratio. In another embodiment, the individual implants are equivalent to one another in four of these other parameters in addition to their PLA:PGA ratio. In another embodiment, the individual implants are equivalent to one another in five of these other parameters in addition to their PLA:PGA ratio. In another embodiment, the individual implants are equivalent to one another in all of these other parameters in addition to their PLA:PGA ratio. Each possibility represents a separate embodiment of the present invention.

In another embodiment, the individual implants are equivalent to one another in their drug load instead of in their PLA:PGA ratio. In another embodiment, the individual implants are equivalent to one another in their mass instead of in their PLA:PGA ratio. In another embodiment, the individual implants are equivalent to one another in their SA:V ratio instead of in their PLA:PGA ratio. In another embodiment, the individual implants are equivalent to one another in their length instead of in their PLA:PGA ratio. In another embodiment, the individual implants are equivalent to one another in their diameter instead of in their PLA:PGA ratio. In another embodiment, the individual implants are equivalent to one another in the inherent viscosity of their polymer instead of in their PLA:PGA ratio. In another embodiment, the individual implants are equivalent to one another in 2 of these parameters. In another embodiment, the individual implants are equivalent to one another in 3 of these parameters. In another embodiment, the individual implants are equivalent to one another in 4 of these parameters. In another embodiment, the individual implants are equivalent to one another in all of these parameters. Each possibility represents a separate embodiment of the present invention.

As provided herein, the present invention demonstrates that extended maintenance of therapeutic drug levels can be attained with a single-polymer system (e.g. a homogenous set of implants). Furthermore, the single-polymer implant system in rabbits (FIG. 3B) demonstrated that individual polymers approximate a symmetrical pattern of serum concentration. Moreover, as depicted inFIG. 3B, the trendline that described that data with a correlation coefficient (R2) of 0.86 exhibited maximum release values at approximately 6 months.

“Point of peak release” refers, in another embodiment, to the point at which the release is maximal. In another embodiment, the term refers to the average point of peak release in human subjects, based on studies prior to administration of the implant. Each possibility represents another embodiment of the present invention.

In another embodiment, the individual biodegradable implants of the maintenance set, if more than one in number, do not differ substantially from one another in their PLA:PGA molar ratio. In another embodiment, the individual biodegradable implants of the initial set and the maintenance set do not differ substantially from one another, both within and between the sets, in their PLA:PGA molar ratio. Each possibility represents a separate embodiment of the present invention.

In another embodiment, step (b) is repeated as necessary to maintain therapeutic level of the drug for the desired time period in the subject.

In another embodiment, the maintenance set is administered near the time of beginning of decline of drug release of the prior set of implants.

In another embodiment, the present invention provides a use of (a) an initial set of biodegradable implants of the present invention; and (b) a maintenance set of biodegradable implants of the present invention for the preparation of a of a pharmaceutical composition for maintaining a therapeutic level of a drug in a subject for one of the above time periods.

In other embodiments, the individual implants of the maintenance set have any of the characteristics described above for the individual implants of the initial set. Each characteristic represents a separate embodiment of the present invention.

The nearly symmetrical nature of the release profile from single-polymer sets, as demonstrated in the present invention, provides the possibility of using overlapping implantations approximately every 6 months to sustain drug delivery indefinitely (FIG. 13). In one embodiment this approach offsets the steady decline from one set of implants with the gradual onset from a subsequent set.

Each of the above periods represents a separate embodiment of the present invention.

In another embodiment, the implants of the starter set do not differ substantially from one another in their PLA:PGA ratio, drug load, length, diameter, SA:V ratio, and inherent viscosity. In another embodiment, the starter set implants differ substantially from one another in one of these parameters. In another embodiment, the starter set implants differ substantially from one another in more than one of these parameters. In another embodiment, the starter set implants have different release profiles from one another. Each possibility represents a separate embodiment of the present invention.

In other embodiments, the starter set implants have any of the characteristics described above for the individual implants of the initial set. Each characteristic represents a separate embodiment of the present invention.

In another embodiment, the starter set implants enable earlier attainment of therapeutic drug levels, as provided herein (Example 16). In another embodiment, the number of implants required in the initial set of implants is reduced (relative to the maintenance set of implants) due to the present of the starter set implants, as the starter set implants make a contribution to the drug levels that is not present at the time of administration of the maintenance set of implants.

The ability of starter sets to enable more rapid release was shown in the present invention, by comparing the release profiles of the single-polymer design to the multiple-polymer design. Higher serum levels were observed in early time points with the multiple-polymer design (FIGS. 1 and 3A).

In another embodiment, instead of administering a starter set of implants with the initial implantation, the number of implants is increased (relative to the maintenance set of implants) to attain therapeutic levels more quickly.

In another embodiment, the step of administering the initial set of implants is reversible. In another embodiment, the step of administering the starter set of implants is reversible. “Reversible,” in one embodiment, refers to the ability to remove the remains of the set of implants by surgical or other means. In one embodiment, “reversible” refers to the ability to remove the remains of one or more of the implants. In another embodiment, “reversible” refers to the ability to remove the majority of the remains of the set of implants. In another embodiment, “reversible” refers to the ability to remove the majority of the remains of one or more of the implants. Each possibility represents a separate embodiment of the present invention.

In other embodiments, the individual implants of any of the sets described above have any of the lengths of an implant of the present invention. In other embodiments, the individual implants have a combined length equal to any of the lengths of an implant of the present invention.

In another embodiment, the step of administering the individual implants of any of the above sets is reversible. In another embodiment, the step of administering any of the above sets is reversible. In one embodiment, “reversible” refers to one of the meanings provided above. Each possibility represents a separate embodiment of the present invention.

In other embodiments the individual implants of any of the above sets have any of the diameters of an implant of the present invention. In other embodiments, the individual implants have a combined length equal to any of the diameters of an implant of the present invention.

In other embodiments, the individual implants of any of the above sets have any of the SA:V ratios of an implant of the present invention. In other embodiments, the individual implants have a combined length equal to any of the SA:V ratios of an implant of the present invention.

In other embodiments, the individual implants of any of the above sets have any of the masses of an implant of the present invention. In other embodiments, the individual implants have a combined length equal to any of the masses of an implant of the present invention.

In another embodiment, the individual implants of any of the above sets are combined into a single structure (e.g. a rod-shaped structure, a bundle, etc.). In another embodiment, the structure has any of the lengths of an implant of the present invention. In another embodiment, the structure has any of the diameters of an implant of the present invention. In another embodiment, the structure has any of the SA:V ratios of an implant of the present invention. In another embodiment, the structure has any of the masses of an implant of the present invention. In another embodiment, the structure enables reduction of the number of structures implanted. Each possibility represents a separate embodiment of the present invention.

In other embodiments, the individual biodegradable implants of any of the sets described above have any of the characteristics of an implant of the present invention. Each characteristic represents a separate embodiment of the present invention.

In another embodiment, a method of the present invention further comprises administration of the therapeutic drug by a different route, together with the initial administration of implants, in order to reach and maintain therapeutic drug levels until the rate of release of the implants is sufficient. In another embodiment, a different drug with a similar therapeutic effect is administered with the initial set of implants. Any route of administration known in the art may be used. Each route represents a separate embodiment of the present invention.

In another embodiment, the present invention provides a method for releasing a therapeutic drug at a substantially linear rate for a period of several months into a body tissue of a subject, comprising administering to the subject an implant or set of implants of the present invention, thereby releasing a therapeutic drug at a substantially linear rate for a period of several months into a body tissue of a subject.

In another embodiment, the present invention provides a method for releasing thiothixene at a substantially linear rate for a period of several months into a body tissue of a subject, comprising administering to the subject a thiothixene-containing implant of the present invention, thereby releasing thiothixene at a substantially linear rate for a period of several months.

In another embodiment, the present invention provides a method for releasing haloperidol at a substantially linear rate for a period of several months into a body tissue of a subject, comprising administering to the subject a haloperidol-containing implant of the present invention, thereby releasing haloperidol at a substantially linear rate for a period of several months.

In another embodiment, the present invention provides a method for releasing HCTZ at a substantially linear rate for a period of several months into a body tissue of a subject, comprising administering to the subject a HCTZ-containing implant of the present invention, thereby releasing HCTZ at a substantially linear rate for a period of several months.

In another embodiment, the present invention provides a method for releasing ibuprofen at a substantially linear rate for a period of several months into a body tissue of a subject, comprising administering to the subject an ibuprofen-containing implant of the present invention, thereby releasing ibuprofen at a substantially linear rate for a period of several months.

In another embodiment, the present invention provides a method for releasing aspirin at a substantially linear rate for a period of several months into a body tissue of a subject, comprising administering to the subject an aspirin-containing implant of the present invention, thereby releasing aspirin at a substantially linear rate for a period of several months.

In another embodiment, the present invention provides a method for releasing corticosterone at a substantially linear rate for a period of several months into a body tissue of a subject, comprising administering to the subject a corticosterone-containing implant of the present invention, thereby releasing corticosterone at a substantially linear rate for a period of several months.

“Several months” refers, in various embodiments, to any time period of the present invention. Each time period represents a separate embodiment of the present invention.

In another embodiment, the present invention provides a method for releasing a therapeutic drug at a substantially linear rate for a period of several weeks into a body tissue of a subject, comprising administering to the subject an implant or set of implants of the present invention, thereby releasing a therapeutic drug at a substantially linear rate for a period of several weeks into a body tissue of a subject.

The therapeutic drug is, in various embodiments, any therapeutic drug of the present invention. Each drug represents a separate embodiment of the present invention.

In one embodiment, the substantially linear rate of methods and compositions of the present invention is the release rate of the implant during the steady state phase of release. “Steady state,” in one embodiment, refers to the period of time during which an implant exhibits a substantially linear release rate, as exemplified herein in Example 10.

Each of the above rates represents a separate embodiment of the present invention.

In another embodiment, the present invention provides a method for releasing risperidone at a substantially linear rate for a period of at least 1 month into a body tissue of a subject, comprising administering to the subject a risperidone-containing implant or set of implants of the present invention, thereby releasing risperidone at a substantially linear rate for a period of at least 1 month into a body tissue of a subject.

In another embodiment, the present invention provides a method for releasing risperidone at a substantially linear rate for a period of at least 2 months into a body tissue of a subject, comprising administering to the subject a risperidone-containing implant or set of implants of the present invention, thereby releasing risperidone at a substantially linear rate for a period of at least 2 months into a body tissue of a subject.

In another embodiment, the present invention provides a method for releasing risperidone at a substantially linear rate for a period of at least 3 months into a body tissue of a subject, comprising administering to the subject a risperidone-containing implant or set of implants of the present invention, thereby releasing risperidone at a substantially linear rate for a period of at least 3 months into a body tissue of a subject.

In another embodiment, the present invention provides a method for releasing risperidone at a substantially linear rate for a period of at least 4 months into a body tissue of a subject, comprising administering to the subject a risperidone-containing implant or set of implants of the present invention, thereby releasing risperidone at a substantially linear rate for a period of at least 4 months into a body tissue of a subject.

In another embodiment, the present invention provides a method for releasing risperidone at a substantially linear rate for a period of at least 5 months into a body tissue of a subject, comprising administering to the subject a risperidone-containing implant or set of implants of the present invention, thereby releasing risperidone at a substantially linear rate for a period of at least 5 months into a body tissue of a subject.

In another embodiment, the present invention provides a method for releasing risperidone at a substantially linear rate for a period of at least 6 months into a body tissue of a subject, comprising administering to the subject a risperidone-containing implant or set of implants of the present invention, thereby releasing risperidone at a substantially linear rate for a period of at least 6 months into a body tissue of a subject.

In another embodiment, the present invention provides a method for releasing risperidone at a substantially linear rate for a period of at least 7 months into a body tissue of a subject, comprising administering to the subject a risperidone-containing implant or set of implants of the present invention, thereby releasing risperidone at a substantially linear rate for a period of at least 7 months into a body tissue of a subject.

In another embodiment, the present invention provides a method for releasing risperidone at a substantially linear rate for a period of at least 8 months into a body tissue of a subject, comprising administering to the subject a risperidone-containing implant or set of implants of the present invention, thereby releasing risperidone at a substantially linear rate for a period of at least 8 months into a body tissue of a subject.

In another embodiment, the present invention provides a method for releasing risperidone at a substantially linear rate for a period of at least 9 months into a body tissue of a subject, comprising administering to the subject a risperidone-containing implant or set of implants of the present invention, thereby releasing risperidone at a substantially linear rate for a period of at least 9 months into a body tissue of a subject.

In another embodiment, the present invention provides a method for releasing risperidone at a substantially linear rate for a period of at least 10 months into a body tissue of a subject, comprising administering to the subject a risperidone-containing implant or set of implants of the present invention, thereby releasing risperidone at a substantially linear rate for a period of at least 10 months into a body tissue of a subject.

In another embodiment, the present invention provides a method for releasing risperidone at a substantially linear rate for a period of at least 11 months into a body tissue of a subject, comprising administering to the subject a risperidone-containing implant or set of implants of the present invention, thereby releasing risperidone at a substantially linear rate for a period of at least 11 months into a body tissue of a subject.

In another embodiment, the present invention provides a method for releasing risperidone at a substantially linear rate for a period of at least 12 months into a body tissue of a subject, comprising administering to the subject a risperidone-containing implant or set of implants of the present invention, thereby releasing risperidone at a substantially linear rate for a period of at least 12 months into a body tissue of a subject.

In another embodiment, the present invention provides a method for releasing risperidone at a substantially linear rate for a period of at least 14 months into a body tissue of a subject, comprising administering to the subject a risperidone-containing implant or set of implants of the present invention, thereby releasing risperidone at a substantially linear rate for a period of at least 14 months into a body tissue of a subject.

In another embodiment, the present invention provides a method for releasing risperidone at a substantially linear rate for a period of at least 16 months into a body tissue of a subject, comprising administering to the subject a risperidone-containing implant or set of implants of the present invention, thereby releasing risperidone at a substantially linear rate for a period of at least 16 months into a body tissue of a subject.

In another embodiment, the present invention provides a method for releasing risperidone at a substantially linear rate for a period of at least 18 months into a body tissue of a subject, comprising administering to the subject a risperidone-containing implant or set of implants of the present invention, thereby releasing risperidone at a substantially linear rate for a period of at least 18 months into a body tissue of a subject.

In another embodiment, the present invention provides a method for treating a schizophrenia in a human, comprising administering to the human an implant or set of implants of the present invention, thereby treating a schizophrenia in a human.

As provided herein, methods of the present invention are effective in extended delivery of risperidone and in treatment of schizophrenia (Examples 8-9). In vivo risperidone serum concentration was within the target range of 2-15 ng/ml (Foster R H and Goa K L (1998) Pharmacoeconomics 14: 97-133) for a substantial portion of the release interval (FIGS. 1 and 3).

In another embodiment, the present invention provides a method for treating a bipolar disorder in a human, comprising administering to the human an implant or set of implants of the present invention, thereby treating a bipolar disorder in a human.

In another embodiment, the present invention provides a method for treating a dementia in a human, comprising administering to the human an implant or set of implants of the present invention, thereby treating a dementia in a human.

In another embodiment, the present invention provides a method for treating delirium in a human, comprising administering to the human an implant or set of implants of the present invention, thereby treating delirium in a human.

In another embodiment, the present invention provides a method for treating agitation in a human, comprising administering to the human an implant or set of implants of the present invention, thereby treating agitation in a human.

In another embodiment, the present invention provides a method for treating an impulse control disorder in a human, comprising administering to the human an implant or set of implants of the present invention, thereby treating an impulse control disorder in a human.

In another embodiment, the present invention provides a method for treating a psychotic depression in a human, comprising administering to the human an implant or set of implants of the present invention, thereby treating a psychotic depression in a human.

In another embodiment, the present invention provides a method for treating a schizophrenia in a human, comprising performing one of the above methods of maintaining a therapeutic level of a drug in a subject, thereby treating a schizophrenia in a human.

In another embodiment, the present invention provides a method for treating a bipolar disorder in a human, comprising performing one of the above methods of maintaining a therapeutic level of a drug in a subject, thereby treating a bipolar disorder in a human.

In another embodiment, the present invention provides a method for treating a dementia in a human, comprising performing one of the above methods of maintaining a therapeutic level of a drug in a subject, thereby treating a dementia in a human.

In another embodiment, the present invention provides a method for treating delirium in a human, comprising performing one of the above methods of maintaining a therapeutic level of a drug in a subject, thereby treating delirium in a human.

In another embodiment, the present invention provides a method for treating agitation in a human, comprising performing one of the above methods of maintaining a therapeutic level of a drug in a subject, thereby treating agitation in a human.

In another embodiment, the present invention provides a method for treating an impulse control disorder in a human, comprising performing one of the above methods of maintaining a therapeutic level of a drug in a subject, thereby treating an impulse control disorder in a human.

In another embodiment, the present invention provides a method for treating a psychotic depression in a human, comprising performing one of the above methods of maintaining a therapeutic level of a drug in a subject, thereby treating a psychotic depression in a human.

In another embodiment, the present invention provides a use of an implant or set of implants of the present invention for the preparation of a pharmaceutical composition for treating schizophrenia. In another embodiment, the present invention provides a composition comprising an implant or set of implants of the present invention for the treatment of schizophrenia.

In another embodiment, the present invention provides a use of an implant or set of implants of the present invention for the preparation of a pharmaceutical composition for treating bipolar disorder. In another embodiment, the present invention provides a composition comprising an implant or set of implants of the present invention for the treatment of bipolar disorder.

In another embodiment, the present invention provides a use of an implant or set of implants of the present invention for the preparation of a pharmaceutical composition for treating dementia. In another embodiment, the present invention provides a composition comprising an implant or set of implants of the present invention for the treatment of dementia.

In another embodiment, the present invention provides a use of an implant or set of implants of the present invention for the preparation of a pharmaceutical composition for treating delirium. In another embodiment, the present invention provides a composition comprising an implant or set of implants of the present invention for the treatment of delirium.

In another embodiment, the present invention provides a use of an implant or set of implants of the present invention for the preparation of a pharmaceutical composition for treating agitation. In another embodiment, the present invention provides a composition comprising an implant or set of implants of the present invention for the treatment of agitation.

In another embodiment, the present invention provides a use of an implant or set of implants of the present invention for the preparation of a pharmaceutical composition for treating an impulse control disorder. In another embodiment, the present invention provides a composition comprising an implant or set of implants of the present invention for the treatment of an impulse control disorder.

In another embodiment, the present invention provides a use of an implant or set of implants of the present invention for the preparation of a pharmaceutical composition for treating psychotic depression. In another embodiment, the present invention provides a composition comprising an implant or set of implants of the present invention for the treatment of psychotic depression.

The period of treatment of any of the above diseases provided by a method of the present invention may be any of the time periods of the present invention. Each period represents a separate embodiment of the present invention.

“Treating,” in one embodiment, refers to therapeutic intervention. In another embodiment, the term refers to prophylactic intervention. In another embodiment, the term refers to ameliorating the symptoms of a disease or disorder. In another embodiment, the term refers to ameliorating a symptoms, disease or disorder secondary to the disease or disorder being treated. In another embodiment, “treating” refers to slowing the progression of a disease. Each possibility represents a separate embodiment of the present invention.

Methods for diagnosing and assessing the severity of the above disorders are well known in the art, and are described, for example, in the Diagnostic and Statistical Manual of Mental Disorders (DSM), published by the American Psychiatric Association, Washington D.C. Each method represents a separate embodiment of the present invention. In another embodiment, schizophrenia or another of the above disorders is diagnosed by a method described above in the description of methods of assessing the efficacy of risperidone therapy.

Methods of assessing the efficacy of risperidone therapy in animals and humans are well known in the art. In animals efficacy of risperidone therapy may be assessed by, for example, PPI (described below) locomotor activity, rotarod, and catalepsy assessments. Locomotor activity is, in one embodiment, measured in a “home cage” activity monitoring system (MedAssociates, St. Albans, Vt.). This system allows for a standard, clean home cage to be placed in a photobeam frame with two levels of sensors arranged in an 8-beam array strip with 1.25 inch spacing. A computer detection system monitors interruptions of the photobeams for the ambulations parameter. Total ambulations are determined by the number of photobeam interruptions the animal makes while moving about the cage. Data are recorded on Med Associates personal computer-designed software and monitored e.g. at 5-minute intervals for a total of 30 minutes per activity monitoring session. Rats typically receive several days of habituation to the apparatus and task prior to their first exposure to amphetamine.

In another embodiment, rotarod is used to assess the efficacy of risperidone therapy. In one embodiment, the accelerating rotarod treadmill apparatus (Stoelting Co., Wood Dale, Ill.) is used to determine motor function. Rats are placed on the stationary rod in order to acclimate to the apparatus. The speed is then set to gradually increase from 2 to 20 rpm. The maximal score in maintaining equilibrium and posture is fixed (e.g. 5 minutes; Lelas S, Wong H et al, J Pharmacol Exp Ther 309: 293-302, 2004). Testing ends after the period or when the animal falls off of the rod.

In another embodiment, catalepsy assessment is used to assess the efficacy of risperidone therapy. Catalepsy is tested in animals (e.g. rats) to assess motor effects from risperidone implants. Rats are positioned with their fore legs against a cage side, and the amount of time required to resume a normal posture is recorded. Increased latency to resume normal position with all four legs on the bottom of the cage is interpreted as indicative of motor impairment secondary to risperidone.

In another embodiment, the acoustic startle response is used to assess the efficacy of risperidone therapy. The acoustic startle response is a quantifiable, reflexive movement after a loud acoustic stimulus. Prepulse inhibition (PPI) occurs when the startle response is reduced because of the previous presentation of a less intense sensory stimulus (Hoffman H S, Searle J L (1965) J Comp Physiol Psychol 60:53-58). PPI can be attenuated by administration of dopamine (DA) agonists such as apomorphine (APO) and amphetamine (AMPH), and this effect is reversed by dopamine receptor antagonists such as haloperidol and risperidone (Mansbach R S, Geyer M A (1989). Neuropsychopharmacol 2: 299-308; Swerdlow N R et al, (1991). J Pharmacol Exp Ther 256: 530-536; Swerdlow N R et al, Neuropsychopharmacol 18: 50-56). As such, attenuation of PPI by DA receptor agonists is an effective animal model for the deficits in sensory-gating processes observed in schizophrenia (Braff D L, Geyer M A (1990) Arch Gen Psychiatry 47: 181-188).

Methods for recording of auditory evoked potentials are well known in the art. In one embodiment, recording of auditory evoked potentials is achieved via stereotaxic implantation of tripolar electrode assemblies. In another embodiment, these assemblies are used for non-anesthetized recording of auditory evoked potentials. These methods are well known in the art and are described, e.g, in (Connolly et al., 2003; Connolly et al., 2004; Maxwell et al., 2004; Siegel et al., 2005).

An additional method for assessment of risperidone efficacy in animals is behavioral observations, which are well known in the art and are described, for example, Elmer G I, Brockington A et al (Cocaine cross-sensitization to dopamine uptake inhibitors: unique effects of GBR12909. Pharmacol Biochem Behav 53: 911-918, 1996). For example, the following behaviors are observed and scored for their presence or absence during each 5-min interval: still; sniffing; licking; gnawing; grooming; locomotion (all four legs moving); rearing (both front feet off the cage floor); head down (animal standing, walking or running with its nose below horizontal for more than 5 seconds); swaying (rhythmic swaying movements of the animal's head or body for more than 3 seconds); circling (walking or running in a continuous circle for more than 5 seconds).

In another embodiment, the efficacy of risperidone therapy is assessed by quantification of dopamine D₂and/or serotonin 5HT_1A/2A/2Creceptor expression in brain samples (e.g. cortex, hippocampus, striatum and/or cerebellum). Risperidone increases dopamine D₂receptor expression and decreases serotonin 5HT_1A/2A/2Creceptor expression. Serotonin receptor Western blots can utilize polyclonal antibodies AB5406 (Chemicon, Temecula, Calif.), PC176L (Calbiochem, CA), or and AB5655 (Chemicon). D₂receptor Western blots can utilize polyclonal antibody WR-3526, (Research and Diagnostic Antibodies, Berkeley, Calif.). Each possibility represents a separate embodiment of the present invention.

Methods of assessing the efficacy of risperidone therapy in humans are described, e.g, in Heresco-Levy U et al (Biol Psychiatry 2005 57(6): 577-85), Moller H J et al (Int Clin Psychopharmacol. 2005 20(3): 121-30); and Hirschfeld R M et al (Am J Psychiatry. 2004 161(6): 1057-65). In another embodiment, the efficacy of risperidone therapy in humans by assessing the severity of the disorder for which risperidone was described, using the DSM-IV. Each of the above methods for assessing efficacy of risperidone therapy in animals may be utilized for humans and vice-versa.

Each of the above methods for assessment of risperidone efficacy represents a separate embodiment of the present invention.

In another embodiment, the present invention provides an implant having a drug load of a therapeutic drug between about 20-30% by mass, inclusive, and between 70%-80% by mass, inclusive, of a polymer, the polymer comprising PLA and optionally PGA in a PLA:PGA ratio between 80:20 and 100:0 by mass, inclusive, the implant having a radius of R₀according to the equation:

(\frac{{dM}_{d}}{dt}) = 4 π {R_{0}^{2} (1 - \frac{C_{w} \sqrt{D}}{2 R_{0} \sqrt{k}} t)}^{2} \frac{C_{w} \sqrt{D} \erf [\sqrt{kt}]}{2 \sqrt{k}}

wherein:
“erf(x)” refers to

\frac{2}{\sqrt{π}} \int_{0}^{x} e^{- t 2} dt,

dM_d/dt is the desired steady-state release rate of therapeutic drug at time t, D is the diffusion coefficient of water into the matrix, k is the reaction rate and C_wis the concentration of water in the implant at time t;
wherein k is determined by the formula:

\frac{\partial c_{w}}{\partial t} = D \nabla^{2} c_{w} - {kc}_{w}

wherein S is the solubility of therapeutic drug in water; and wherein k is a constant between about 0.05-0.33.

In one embodiment, the therapeutic drug contained in the above implant is risperidone. In another embodiment, the therapeutic drug is haloperidol, in which case D is 1.7×10{circumflex over ( )}−10, and k is 0.07 (Example 10). In another embodiment, the therapeutic drug is thiothixene, in which case D is 9×10{circumflex over ( )}−10, and k is 0.06. In another embodiment, the therapeutic drug is HCTZ, in which case D is 2.1×10{circumflex over ( )}−6, and k is 0.26. In another embodiment, the therapeutic drug is corticosterone, in which case D is 2.5×10{circumflex over ( )}−7, and k is 0.33. In another embodiment, the therapeutic drug is ibuprofen, in which case D is 7.0×10{circumflex over ( )}−6, and k is 0.16. In another embodiment, the therapeutic drug is aspirin, in which case D is 8.0×10{circumflex over ( )}−2, and k is 0.06. In another embodiment, the therapeutic drug is any other therapeutic drug known in the art. Each possibility represents a separate embodiment of the present invention.

In another embodiment, k, the degradation reaction rate coefficient, depends on the drug properties as given by a combination of the drug solubility and the presence of OH groups (Example 11). For drugs with the same water solubility, the rate of polymer hydrolysis increases with the density of OH groups, while for drugs with the same OH group density k decreases with solubility in another embodiment, k is empirically determined, as described in Example 10.

In another embodiment, the presence of the drug affects the polymer degradation rate. In one embodiment, the drug affects the polymer degradation rate by affecting the diffusion of water into the polymeric matrix. In another embodiment, the drug affects the polymer degradation rate by affecting the rate of the degradation reaction. In another embodiment, the drug affects the polymer degradation rate by a combination of the above mechanisms. Each possibility represents a separate embodiment of the present invention.

In another embodiment, the present invention provides a method of designing an implant to deliver a target rate of release of a therapeutic drug, by utilizing an equation of the present invention (e.g. equation 4, 5a, or 5b).

In another embodiment, the present invention provides a method of designing an implant to achieve a target rate serum concentration of a therapeutic drug, by utilizing an equation of the present invention (

e.g. equation

8, 9, or 10; Example 12).

In another embodiment, the present invention provides a method of achieving a drug release rate dM_d/dt at time t, comprising administering an implant whose radius has been determined using an equation of the present invention (e.g. equation 4, 5a, or 5b).

In another embodiment, the present invention provides a method of achieving a serum concentration x at time t, comprising administering an implant whose radius has been determined using an equation of the present invention (

e.g. equation

8, 9, or 10).

Any of the methods of the present invention may utilize any of the implants of the present invention. Each combination of a method of the present invention with an implant of the present invention represents a separate embodiment of the present invention.

In another embodiment, the present invention provides a kit comprising a reagent utilized in performing a method of the present invention. In another embodiment, the present invention provides a kit comprising an implant of the present invention.

EXPERIMENTAL DETAILS SECTIONExample 1: Extended Haloperidol Release from PLGA Implants in MonkeysMaterials and Experimental MethodsSubjects

Two monkeys (Macaca fascicularis, Rangos Research Facility) were utilized, each of which received 6 copolymer PLGA (poly(d,l-lactic-glycolic acid))—containing implants. For the experimental monkey, the implants contained 40% haloperidol by mass, with the other 60% consisting of one of the PLGA polymers depicted in Table 2 below. The implants administered to the control monkey contained 100% of the PLGA polymers depicted in Table 2. PLGA polymers were provided by Medisorb® Alkermes, (Cincinnati, Ohio). Haloperidol dosing averaged 1 mg/kg/day over 12 months to achieve a serum concentration of 2-10 ng/ml.

TABLE 2

Polylactic acid:polyglycolic acid (PLA:PGA) molar ratios and inherent
viscosities of the PLGA polymers in the implants used in the primate
experiment. Inherent viscosities in the table are expressed in units
of dl/g in chloroform, and were measured at 30° C., 0.5 dl/g
using asize 25 Cannon-Fenske glass capillary viscometer.

Implant number	PLA:PGA molar ratio	Inherent viscosity (IV)

1	75:25	0.66-0.80
2	85:15	0.66-0.80
3	90:10	High (0.87)
4	90:10	Low (0.68)
5	95:5	0.66-0.80
6	100:0	0.66-0.80

Implant Manufacture

Polymers and haloperidol (Sigma, St. Louis, Mo.) were mixed in a proportion of 60/40 by mass and solvent cast from acetone (Fisher Scientific, Pittsburgh, Pa.). The resulting film was compression molded to disk-shaped implants of 20 mm diameter with average thickness of 1.22±0.0 mm, mass 493±2 mg and density of 1.28±0.0 g/cc.

Pharmacokinetic Determination

Blood was drawn twice per month. Blood was centrifuged and serum frozen at −80° C. until analysis. Serum risperidone and 9-OH risperidone concentrations were determined in duplicate at each time point for each animal. Specimens were separated by centrifugation and haloperidol levels were assayed by high-pressure liquid chromatography (HPLC) with ultraviolet (UV) detection (FIG. 1). Assays from control animals yielded drug levels of zero.

Results

Throughout the Examples, implants were well tolerated, and no adverse skin reactions were observed. As depicted inFIG. 1, haloperidol release was measured over a total of 443 days. Mean serum concentration was 10.5±1.5 ng/ml during the first 224 days, with the exception of one value (27.1 ng/ml on day 40). During the subsequent 176 days, serum haloperidol levels were sustained at a lower mean concentration of 4.0±0.4 ng/ml. Levels decreased during the last 45 days of the study (mean serum concentration 1.2±0.3 ng/ml).

Thus, 14 months of haloperidol release was achieved in monkeys using biodegradable implants.

Example 2: Extended Haloperidol Release from PLGA Implants in RabbitsMaterials and Experimental MethodsExperimental Design

Two implant systems were tested, the first containing five different single-polymer implants (similar to Example 1), and the second containing five implants comprised of a single polymer. The aim of the single-polymer model was to reduce the initial spike while maintaining release for one year.

Subjects

Rabbits (N=12, Covance, Denver, Pa.) ranged from 4.0 to 5.7 kg. Five animals received implants composed of a single polymer, 100% PLA, with 40% haloperidol load for a total drug content of 418±7 mg/kg, yielding a daily dose of 1.13±0.02 mg/kg/day for anticipated delivery of 365 days. Five additional animals received implants of a combined-polymer system including 75:25, 85:15, 90:10 high IV, 90:10 low IV and 100:0 PLGA. The mean dose in this group was 473±4 mg/kg with an expected delivery of 365 days, yielding a mean dose of 1.29±0.03 mg/kg/day. Two rabbits received implants without drug as a control. One control received 100% PLA implants to mimic the single-polymer condition, the other received implants composed of 75:25, 85:15, 90:10 high IV, 90:10 low IV & 100:0 PLGA to mirror the combined-polymer system.

Implant Manufacture

Implants were made using procedures described in Example 1, in this case with an average mass of 536±2 mg and density of 1.24±0.00 g/cc. Implants were tethered to assist in locating implant sites at necropsy.

Pharmacokinetic Determination

Solid phase extraction (SPE) was performed using the Waters 20-position SPE vacuum manifold and Waters Oasis MCX SPE cartridges, (3 ml/60 μg cartridges). Cartridges were conditioned with methanol and water, samples containing 2% phosphoric acid were loaded, then cartridges were washed with 5% methanol in 0.1 N hydrochloric acid, then 100% acetonitrile, then eluted with 5% NH₄OH in 100% acetonitrile. Samples were dried under nitrogen in an 80° C. water bath, reconstituted in 100 μl of mobile phase, vortexed, and centrifuged for 5 minutes. 75 μl of the reconstituted samples were loaded into an autosampler and 50 μl was injected. HPLC was performed using a Waters XTerra RP 18 5 um, 4.6×150 mm column, flow rate 1.0 ml/min,run time 30 min. Mobile phase and sample buffer were composed of 55% H₂O with 35% acetonitrile and 10% 100 mM ammonium bicarbonate,pH 10. Peaks were detected at a wavelength of 280 nm. Standard solutions of risperidone and 9-OH risperidone were prepared in normal rat serum (range 1.25-50 ng/ml), extracted, and included within each run to provide the standard curve and retention time for each compound. The retention times for risperidone and 9-OH risperidone were 8.6 and 5.9 min, respectively.

Histopathology

Five rabbits were sacrificed after nine months to obtain interim pathological analyses, with remaining seven rabbits sacrificed after an additional four months. Remains of implants were found tethered in place in all animals that received implants (FIG. 2).

At removal, the average residual implant was 17% of its original mass at 282 days and 5% of its original mass at 423 days post implantation. HPLC/UV and NMR spectroscopy confirmed the presence of haloperidol and PLGA breakdown products in residual implants. HPLC analyses of drug content in residual implants indicate that implants removed at 282 days were an average of 10% risperidone by weight and those removed at 423 days were an average of 9% risperidone by weight. NMR was performed at 25° C. on aVarian Unity Inova 300 Mhz instrument and spectra were analyzed using Vnmr 6.1b software (Varian, Inc., Palo Alto, Calif.) (FIG. C3). Control samples of PLA (Alkermes 100DL High IV) and haloperidol were run in DMSO and chloroform (CDCl3) to define peaks of interest for each compound (FIG. 3D-E, respectively). Implants were removed from rabbits and were dissolved initially in DMSO-d6 and residual solids then removed by filtration and dissolved in chloroform. All expected haloperidol peaks were present in DMSO. Small peaks from 5.2-5.4 ppm were indicative of the —CH peak in PLA, as the corresponding —CH3 peaks from PLA would have been obscured by the haloperidol peaks at low polymer concentrations. The CDCl3 sample contained characteristic haloperidol peaks at 8.1 and 7.4 ppm at lower magnitude than the DMSO sample, presumably because most of the haloperidol was extracted in DMSO. The chloroform fraction contained peaks at 0.9, 1.2, 3.9, and 4.5, consistent with lactic acid, the degradation product of PLA.

Implants did not cause capsule formation, leading to a simple removal process. HPLC/UV and NMR spectroscopy confirmed the presence of haloperidol and PLGA breakdown products in residual implants. Histological analyses showed all organ systems in all rabbits were within normal limits.

Results

Thus, the findings obtained with rabbits confirmed the monkey findings, showing that 12 months of haloperidol release can be achieved using biodegradable implants. These results also show that at least in some cases, a more symmetric release profile can be achieved with a single-polymer system than with a multiple-polymer system.

Example 3: Effect of Implant Geometry on Release RateMaterials and Experimental Methods

Implants containing 40% Haloperidol and 60% of a 50:50 PLGA polymer were manufactured by solvent casting. Material was compression molded into discs or slowly extruded into rods using a high pressure piston extruder (DACA Instruments, Goleta, Calif.) at 100° C. Rods & discs were matched for weight. The surface area to volume (SA:V) ratios for these geometries are 1.92 for discs (3 mm radius, 1.6 mm thickness) and 1.56 for rods (1.8 mm radius, 4.5 mm length).

To measure release profiles, implants were placed in 500 milliliter (ml) phosphate buffered saline (PBS), pH 7.0, 37° C., 40 rpm, in the dark.

Results

The effect of implant geometry (rods vs. disks) on haloperidol release was examined. Release profiles were nearly identical for both geometries (FIG. 4), demonstrating that rods have very similar release profiles to disks. Thus, rods-shaped implants can be used to deliver maintain therapeutic levels of a drugs in a subject over an extended period of time.

Example 4: Stability of Risperidone in Physiological Aqueous Solution

To evaluate the long-term stability of risperidone in physiological solution, 10 mg Risperidone was dissolved in 100 μl of acetonitrile for subsequent dissolution in 1,000 ml of PBS (0.9% NaCl, 0.01 M NaOH, 0.01 M NaH₂PO₄, pH 7.0) to yield a final solution of 10,000 nanograms (ng)/ml. The solution was shaken at 40 revolutions per minute in a light-safe amber bottle at 37° C. Drug concentration of a 1-ml sample was measured three times per week by UV spectroscopy (Amersham Biosciences, Buckinghamshire, UK). The concentration of drug exhibited only a slight change (1.4% over 343 days, equivalent to 0.004% per day; linear trendline: y=−0.0004x+9.777). Studies were replicated using UV spectrophotometry and HPLC (FIG. 5). There was a 0.99 correlation coefficient between HPLC and UV spectrophotometry, indicating that the UV spectrophotometry method is an accurate method for in vitro analysis of risperidone concentration.

Thus, risperidone is stable over extended time periods in physiological solution.

Example 5: Effect of PLA:PGA Ratio on Risperidone Release

Risperidone release from different polymers including 50:50, 65:35 and 75:25 PLGA was evaluated to assess the effects of PLA:PGA ratio on in vitro risperidone release. Implants were made as described for Example 1, in this case with 20% risperidone (RBI, Flanders, N.J.) and 80% PLGA (Alkermes). Three replicates of each implant type were placed in separate light-safe bottles of 500 ml PBS and shaken at 37° C., 40 rpm). 1 ml aliquots were taken from eachbottle 3 times per week and analyzed by UV spectrophotometry, after which 1 ml of buffer was reintroduced to maintain constant volume. The 75:25 polymer exhibited the slowest release profile (FIG. 6A).

In an additional study, the consistency of the effect between mice was determined. Eight mice were administered 75:25 PLA:PGA, 20% drug load risperidone implants, and the risperidone and 9-OH-risperidone serum concentrations assessed after 42 days. Results are shown in Table 1, together with the mg/kg/day release rate, calculated by dividing the weight of the risperidone in the implant/the weight of the mouse/the estimated number of days of release (120).

TABLE 1

Top eight mice were administered risperidone-containing implants,
bottom five were administered control implants with no risperidone.
Risperidoneimplants mouse serum 42 days after implantation

	post	mg/	Risperidone	9-OH Risperidone
mouse#	day	kg/day	Concentration (ng/ml)	Concentration (ng/ml)

1648	42	2.5	6.0	5.7
1649	42	2.5	10.1	12.6
1650	42	3.2	5.0	7.4
1651	42	2.5	6.3	7.0
1652	42	2.6	6.2	7.1
1653	42	2.8	10.2	11.8
1654	42	3.2	7.0	5.2
1655	42	2.7	7.8	8.2
average			7.3	8.1
1642	42	0	0	0
1643	57	0	0	0
1644	42	0	0	0
1646	57	0	0	0
1647	42	0	0	0
average			0	0

Example 6: Effect of Surface Area to Volume Ratio on Risperidone ReleaseMaterials and Experimental Methods

Studies utilized 4 rods per condition with surface area to volume (SA:V) ratios of 2.75 and 6.17, both utilizing a 30% risperidone drug load, 75:25% PLGA. Rods were placed in separate bottles of PBS at 37° C. at 40 rpm. 0.3 ml samples were drawn 3 times per week analyzed by HPLC and UV spectrophotometry (Bio-teck Instruments, Winooski, Vt.).

Results

To determine the effect of SA:V ratio on risperidone release, risperidone release was measured from rods with identical composition but different SA:V ratios. The pattern of release among these 2 SA:V ratios differed during the first 44 days of release with the smaller radius rods (larger SA:V) exhibiting more rapid release (FIG. 6B). Thus, larger diameter rods, which have a smaller SA:V ratio, provide more extended delivery than smaller diameter rods.

These results confirm and augment the results of Example 3 by demonstrating that release from biodegradable implants is a function of SA:V ratio, as described further below in equation (8). Thus, rods as well as disks can be used to achieve extended release of drugs in biodegradable implants.

Example 7: Determination of Optimal Risperidone Drug Load in Implants

To determine the optimal risperidone concentration for implants, implants were prepared using a single polymer (85:15 PLGA) combined with risperidone at ratios of 10%, 20%, 30%, 40%, 50% or 60% drug by weight (FIG. 7). Implants each had a mass of approximately 50 mg, and thus contained drug masses of 5, 10, 15, 20, 25 and 30 mg, respectively. A large fraction of the total drug load of the 10% and 60% drug-loaded implants was released within the first 30 days, while the 20%, 30%, 40%, and 50% drug-release their risperidone more slowly. The most linear pattern of release was achieved with the 40% and 50% risperidone-loaded implants, with similar slopes throughout the entire time tested.

Example 8: Risperidone Implants Increase PPI and P20 Amplitude and Block Amphetamine-Induced Disruption of N40-Evoked Potentials at 14 and 21 Days Post-ImplantationMaterials and Experimental Methods

Risperidone implants yielded serum risperidone concentration of 7.3±0.68 ng/ml (mean±SEM) and serum 9-OH risperidone of 8.1±0.95 ng/ml at 42 days after implantation. Brain levels were 6.2±1.45 & 4.6±0.52 ng/gm for risperidone & 9-OH risperidone respectively. Disc shaped implants (SA:V ratio of 2.34) were made from 85:15 PLGA, 0.66-0.80 IV, with 20% risperidone drug load. Mice (C57BL/6J) received either implants containing risperidone (n=8) or polymer alone (n=8) prior to stereotaxic implantation of tripolar electrode assemblies (PlasticsOne Inc., Roanoke, Va.) for non-anesthetized recording of auditory evoked potentials (Connolly et al., 2003; Connolly et al., 2004; Maxwell et al., 2004; Siegel et al., 2005). Studies on startle and prepulse inhibition (PPI) of the acoustic startle response were performed between 14 and 21 days after implantation as described in (Gould T J et al, Sensorimotor gating deficits in transgenic mice expressing a constitutively active form of Gs alpha. Neuropsychopharmacol 29: 494-501). Recording of evoked potentials was performed 28 days after implantation of electrodes. Recording for the drug exposure trial began six minutes after injection ofamphetamine 2 mg/kg i.p. and was compared to the pre-amphetamine recording session. Stimuli were generated by Micro1401 hardware andSpike 5 software (CED, Cambridge, England) and were delivered through speakers attached to the cage top. A series of 50 white noise clicks (10 ms duration) were presented in pairs 500 ms apart with a 9 second inter-pair interval at 85 db compared to background of 70 db. Waveforms were filtered between 1 and 500 Hz, baseline corrected at stimulus onset and individual sweeps were rejected for movement artifact based on a criteria of two times the root mean squared amplitude. Average waves were created from 50 ms pre-stimulus to 200 ms post stimulus. Mice were allowed fifteen minutes to acclimate to the Faraday cage prior to stimulus onset.

Results

Mice (C57BL/6J) received either implants containing risperidone (n=8) or polymer alone, then were subjected to non-anesthetized recording of auditory evoked using implanted tripolar electrode assemblies. While risperidone implants did not alter startle amplitude (FIG. 8A), they did increase PPI relative to controls (FIG. 8B). In addition, risperidone implants increased the amplitude of P20 (the human P50 analogue) in control animals (FIG. 9A), and attenuated amphetamine-induced reduction of the amplitude of N40 (the human N100 analogue) (FIG. 9B). Abnormalities in the P50 and N100 components reflect abnormal neuronal architecture related to the generation and modulation of auditory responses and are informative about more generalized neurological impairments in schizophrenia (Adler L E, Olincy A et al, Schizophr Bull 24: 189-202, 1998; Freedman R, Adler L E et al, Hary Rev Psychiatry 2: 179-192, 1994).

Example 9: Risperidone Implants Increase PPI and P20 Amplitude and Block Amphetamine-Induced Disruption of N40-Evoked Potentials at Later Time Points

Experiments are performed to determine the effect of the risperidone implants of Example 8 on startle, PPI, P20, and N40, at later time points after implantation. In this case, significant effects are observed for all these parameters in animals receiving the risperidone implants, consistent with the larger release rate and subsequently higher plasma concentration attained at later time points, as shown in Examples 5-7.

Example 10: Release Rate from Hydrolysable Bio-Degradable Implants can be Determined Based on Drug Solubility and the Rate of Degradation of the ImplantMaterials and Experimental MethodsDrugs

Six drugs were examined:

1). Thiothixene: N,N-dimethyl-9-[3-(4-methylpiperazin-1-yl)propylidene]thioxanthene-2-sulfonamid.

2). Haloperidol: 4-[4-(4-chlorophenyl)-4-hydroxy-1-piperidyl]-1-(4-fluorophenyl)-butan-1-one.

3). Hydrochlorothiazide (HCTZ): 9-chloro-5,5-dioxo-5λ⁶-thia-2,4-diazabicyclo[4.4.0]deca-6,8,10-triene-8-sulfonamide.

4). Corticosterone: 11-hydroxy-17-(2-hydroxyacetyl)-10,13-dimethyl-1,2,6,7,8,9,10,11,12, 13,14,15,16,17-tetradecahydrocyclopenta[a]phenanthren-3-one.

5). Ibuprofen: 2-[4-(2-methylpropyl)phenyl]propanoic acid.

6). Aspirin: 2-acetyloxybenzoic acid

Properties of the drugs are listed in Table 3. All drugs were obtained from Sigma-Aldrich, Inc.

TABLE 3

Properties of drugs utilized in this Example.

						OH group
			Water			density (OH
	Molecular	Molecular	solubility			groups/unit
Drug	formula	weight	(mg/mL)*	D**	k**	mass)

Haloperidol	C₂₁H₂₃ClFNO₂	375.87	0.13	1.7*10⁻¹⁰	0.07	2.66*10⁻³
Thiothixene	C₂₃H₂₉N₃O₂S₂	443.64	0.14	9*10⁻¹⁰	0.06	0
HCTZ	C₇H₈ClN₃O₄S₂	297.75	2.00	2.1*10⁻⁶	0.26	0
Corticosterone	C₂₁H₃₀O₄	346.47	0.50	2.5*10⁻⁷	0.33	5.77*10⁻³
Ibuprofen	C₁₃H₁₈O₂	206.29	0.47	7*10⁻⁶	0.16	4.85*10⁻³
Aspirin	C₉H₈O₄	180.16	4.99	8*10⁻²	0.06	5.55*10⁻³

*Measured after 14 days as described below.
**k is units of 1/day, and D dimensionless. Obtained by fitting the data plotted in FIG. 10 to equation (4), as demonstrated in FIG. 11.

Ultraviolet (UV) Scanning

Drugs were dissolved in PBS, pH 7.4, to the expected in vitro solubility. Absorbance scans were performed on drug solutions within the range of 200 nm to 400 nm, using a blank cuvette containing saline solution as a reference. A characteristic UV footprint was generated for each drug, and the wavelength at which the relevant maximum peak occurred was utilized in subsequent in vitro assays. Standard curves were prepared for each drug in PBS so that absorbencies could be converted to concentrations using the Lambert-Bear law.

Polymer/Drug Pellet Fabrication

400 mg of 50:50 PLGA and 100 mg of drug were solvent cast to obtain a 20% by mass drug-load. Polymer and drug were dissolved in 45 milliliters (mL) acetone (Fisher Scientific, Inc.) and vortexed, then poured into an evaporation dish and placed in a vacuum oven at 40° C. under vacuum (3 inches Hg) with trace airflow. After seven days, dishes were removed from the oven. Evaporation residue was a thin film mixture of polymer and drug with homogenous appearance. The film was carefully weighed to confirm complete removal of solvent and pressed into four uniform disk-shaped pellets with 1 mm thickness and 1.2 mm diameter, using a Teflon®-coated pellet press set at 25 (kilo-pounds) klb and 60° C. Pellets were carefully weighed and measured to determine densities. Negative control pellets with a 0% drug load were fabricated in the same manner, using 500 mg polymer and no drug.

Drug Solubility in Water

Ascending mass of drug, ranging from 0.5 to 200 mg, of each drug was mixed into a capped glass jar (Wheaton, Inc.) containing 10 to 50 mL distilled water and subjected to moderate mixing for 14 days at 21° C. 1-mL aliquots were removed at fixed time intervals and analyzed by UV Spectroscopy to determine maximum saturation concentration.

In Vitro Drug Release Assay

Assays were performed in triplicate using three of each set of four uniform pellets. Each pellet was added to an amber-glass, capped jar (Wheaton, Inc.) containing 500 mL of a PBS solution and subjected to moderate shaking in the dark, at 37° C. 1-mL aliquots of were analyzed by UV Spectroscopy at fixed time intervals and. Positive control jars contained PBS and 10 mg of drug, the expected maximum release for a 20% drug-loaded pellet with a mass of 50 mg, and were also used to determine stability of each drug in saline solution over the course of the experiment.

Results

Release of six drugs from PLGA matrices was examined. f, the fraction of the drug released from the pellet, is plotted inFIG. 10 as a function of time t. At long time periods all drug was released and f≈1. Preceding this full release limit was a region wherein the release rate was fairly constant, as evidenced by a linear relationship between the fraction of released drug (Δf) and the time (Δt).

These results show that linear drug release can be obtained with a single type of biodegradable polymer.

Two additional features emerge from the above drug-release measurement: First, some drugs (e.g. thiothixene) were released as soon as the experiment begins, while others (e.g. haloperidol) exhibited an induction time, during which no measurable amount of drug was released. In addition, during steady state release (constant Δf/Δt), different drugs exhibited different release rates. As a result, variation was observed in both the rate of steady state release and the overall period of time over which the drug is released. Visual observations confirmed that pellets containing different drugs dissolved at different rates, and become invisible to the naked eye after different periods of time that correlated to the time at which f≈1 as measured by UV Spectroscopy. Thus, drug release rate of the polymers can be characterized by two global parameters: The delay period (i.e. the time required to reach the steady state release rate) and the steady state release rate.

The same polymer was utilized in each of the above matrices. Thus, the differences in the delay period and steady state release rates of the matrices were due to the drug component of the matrix. Differences in the release rate of a drug matrix may attributed to different diffusion and leaching rates of the drugs within the polymeric matrix, and/or to different polymer degradation rates. Polymer degradation rates vary among the matrices utilized in this experiment, as evidenced by different rates of disappearance of the pellets. Thus, the presence of the drug affects the polymer degradation rate.

To understand the effect of an incorporated drug on the polymer degradation, the following model of the degradation process was developed, based on the data of the present invention: The mobility (diffusion) of the drug in the polymeric matrix is likely to be negligible compared to the polymer degradation rate. Thus, drug release occurs chiefly via polymer degradation. The polymer PLGA degradation into lactic acid and glycolic acid occurs through a reaction with water:

(C₃H₄O₂)_x(C₂H₂O₂)_y+2 H₂O→CH₃CHOHCOOH+HCHOHCOOH.

Thus, the rate of degradation depends on the availability of water molecules. In systems where the diffusion of water into the pellet is suppressed, this indicates surface erosion. In systems where the diffusivity of water into the polymer is high, this leads to bulk erosion.

The degradation reaction is likely to be a 1^storder reaction between the polymer and water, and is thus proportional to the local concentration of both species. However, since the polymer comprises the majority of the pellet, its concentration is fixed everywhere. Thus, the degradation reaction is proportional to the local concentration of water (a function of the diffusivity) times a constant. Defining the diffusion coefficient of water into the polymer pellet as D, the diffusion/reaction equation for water is written as (1):

\begin{matrix} \frac{\partial c_{w}}{\partial t} = D \nabla^{2} c_{w} - {kc}_{w} & (1) \end{matrix}

where k the reaction rate, which includes the local polymer concentration, is constant. Appropriate boundary conditions are that the concentration of water at the particle edge is fixed by the solution value c_w⁰, and that initially (at t=0) the concentration of water in the particle is zero.

Equation (1) indicates that in systems where D is close to 0, there is no diffusion into the polymeric particle, c_wis zero within the pellet, and all reactions take place at the polymer/solution interface. In systems where the diffusion rate is large compared to the reaction rate, water will penetrate and degrade the entire particle volume through bulk erosion. The water concentration profile is solved by assuming that the pellet is a semi-infinite medium. This assumption is appropriate for the initial and steady-state stages of the degradation when the diffusion distance of the water is small compared to pellet dimensions.

Defining the distance from the polymer/solution interface as x, it was found that:

\begin{matrix} \frac{c_{w}}{c_{w}} = e^{- kt} (1 - \erf [\frac{x}{\sqrt{Dt}}]) + k \int_{0}^{t} e^{- {kt}^{'}} (1 - \erf [\frac{x}{\sqrt{{Dt}^{'}}}]) {dt}^{'} & (2) \end{matrix}

The amount of polymer that reacted, at any given location (x), with water and degraded was then obtained through integration over time:

\begin{matrix} {dM}_{p} (x, t) = k \int_{0}^{t} c_{w} (x, t^{'}) {dt}^{'} & (3. a) \end{matrix}

where dM_p(x,t) is the change in polymer pellet mass at point x. Thus, the overall mass of degraded polymer is described by

\begin{matrix} Δ M_{p} = \int_{x = 0}^{\infty} {dM}_{p} (x, t) dx = k \int_{x = 0}^{\infty} \int_{0}^{t} c_{w} (x, t^{'}) {dt}^{'} dx & (3. b) \end{matrix}

and the amount of released drug M_d(neglecting drug diffusion) is

\begin{matrix} M_{d} (t) = ϕ {dM}_{p} = ϕ k \int_{0}^{\infty} \int_{0}^{t} c_{w} (x, t^{'}) {dt}^{'} dx & (4) \end{matrix}

where ϕ is the weight fraction of the drug in the particle. Initially, when t is small, M_dis described by

\begin{matrix} M_{d} \approx \frac{2 ϕ c_{w}^{} D^{1 / 2} t^{3 / 2}}{3 π^{1 / 2}} \sim t^{3 / 2} & (5. a) \end{matrix}

while at later time points, the release rate is given by

\begin{matrix} M_{d} \approx \frac{ϕ c_{w}^{0} D^{1 / 2} t}{2 k^{1 / 2}} \sim t & (5. b) \end{matrix}

It was thus determined that, initially, the amount of drug released increases with time to the power of (3/2), with a release rate (the slope) that is dependent only upon the water diffusion coefficient D. As time increases, the amount of released drug becomes linear with time. In this regime the system reaches “steady state” when the degradation rate and the amount of drug released are constant with time. Accordingly, the release rate varies with the ratio between the diffusion and reaction constants.

The model described by Equation (4) fit well the drug release data shown inFIG. 10 for all six drugs tested, with values of D and k as listed in Table 2 (the curves for haloperidol and aspirin are depicted inFIG. 11). This is notable because the drugs tested are diverse; e.g. haloperidol and aspirin are very different. The deviations seen at late time points arose from the finite size of the pellets.

Thus, the release rate of drugs from bio-degradable matrices can be accounted for by a model containing only two fit parameters: D and k.

Example 11: Parameters D and K in the Release Equation can be Determined from the Solubility of the Drug and its Density of Hydroxyl Groups

It was observed that the parameter k, the coefficient for the degradation reaction, varied over less than an order of magnitude for all drugs (0.05-0.33); by contrast, D, the diffusion coefficient, varied over 8 orders of magnitude (Table 2).

The diffusion constant of molecules in solid polymeric media is described by D₀e sup[−δ
], where D₀is a proportionality coefficient, ε is an activation, or interaction energy and δ is a thermodynamic constant that depends, among other things, on the system temperature. In the present case, the polymeric matrix is the same, as is the temperature; thus, D₀and
are the same for all polymer/drug pellets. The activation energy ε, however, is sensitive to the specific interactions between the diffusant and the matrix, and thus varies with drug type and loading (mass fraction). The drug solubility in water (assuming an ideal mixture) can also be described in terms of ε: S, the solubility, is equal to S₀e−sup[−δ
], where S₀is a proportionality coefficient and σ is a thermodynamic constant. Combining the relationships for D and S leads to the following relationship:
D=(D₀S₀^−δ/σ)S^δ/σ (6)
wherein the term in parenthesis is, in the present case, a system constant.
As depicted inFIG. 12, the solubility data was fit to equation (6). The dependence of D on the solubility was described through a power law, with a coefficient of approximately 5.3.
In conclusion, the model described by Equation (4) can be used to predict the drug release rate during the steady state for PLGA implants containing 20% drug load. D is proportional to the solubility to the power of 5.3, and k is a number within the range of about 0.05-0.33.

Example 12: Determination of Drug Release from PLGA Polymer Implants and Resulting Serum Drug Concentration as a Function of Time and Implant Properties

Since the focus of Examples 10-11 was to examine the effect of drug/polymer/water interactions on the degradation and release rate, the original model utilized an implant of infinitely large size. The present Example describes the time-dependent concentration of drug in vivo. To that end, the previous model was modified to account for (1) finite implant size and (2) drug absorption and clearance (metabolic rate). The rate of drug release from an implant is proportional to the implant surface area (SA). Correcting for change in implant mass, the SA of the implant, A, can be described asequation 7, where R(t) is the implant radius as a function of time t, R₀is the initial radius, D is the diffusion coefficient of water into the matrix, k the reaction rate and C_wthe concentration of water.
$\begin{matrix} A = 4 π R^{2} (t) = 4 π {R_{0}^{2} (1 - \frac{C_{w} \sqrt{D}}{2 R_{0} \sqrt{k}} t)}^{2} & (7) \end{matrix}$
The rate of drug release per unit time can therefore be calculated asequation 8.
$\begin{matrix} (\frac{{dM}_{d}}{dt}) = A (t) \frac{C_{w} \sqrt{D} \erf [\sqrt{kt}]}{2 \sqrt{k}} 4 π {R_{0}^{2} (1 - \frac{C_{w} \sqrt{D}}{2 R_{0} \sqrt{k}} t)}^{2} \frac{C_{w} \sqrt{D} \erf [\sqrt}{2 \sqrt{k}} & (8) \end{matrix}$
where “erf(x)” refers to
$\frac{2}{\sqrt{π}} \int 0^{x} e^{- t 2} dt,$
The metabolic rate of risperidone can be written as an exponential decay of drug in blood, with a characteristic decay rate τ that varies as a function of drug and metabolic rate, yielding a complex function for the effective drug concentration shown inequation 9. The function can be asymmetric, and its degree of asymmetry is set by the value of τ, the typical metabolizing time for the given drug. A high value of τ indicates slow metabolic rate, and thus the function is more symmetrical. A low value of τ indicates fast metabolism and the function becomes more asymmetric as the peak moves closer to t=0.
$\begin{matrix} (\frac{{dM}_{d}}{dt}) = 4 π {R_{0}^{2} (1 - \frac{C_{w} \sqrt{D}}{2 R_{0} \sqrt{k}} t)}^{2} \frac{C_{w} \sqrt{D} \erf [\sqrt{kt}]}{2 \sqrt{k}} (1 - e^{t / τ}) & (9) \end{matrix}$
The concentration of drug as a function of time is a complex function. The error function can be approximated as erf(x)˜1−e^−7x/4, yieldingequation 10 for the drug concentration. a₁is a constant equal to the total drug content of the implant, variable a₂is a constant equal to the metabolic rate, variable a₃reflects diffusion of drug from the implant and variable a₄reflects polymer degradation and influences total release interval. Fitting rabbit haloperidol data, we extract the coefficient τ≈0.027, indicating a serum half-life for haloperidol in rabbit of about 130 minutes, consistent with published data (Wurzburger R J, Miller R L et al, J Pharmacol Exp Ther 217: 757-763). This equation fits prior in vivo rabbit data with a correlation coefficient (R²) of 0.87.
$\begin{matrix} (\frac{{dM}_{d}}{dt}) \sim a_{1} (1 - e^{- a_{2} t}) (1 + e^{a_{3} \sqrt{t}}) {(1 - a_{4} t)}^{2} & (10) \end{matrix}$

Example 13: Determination of the Contribution of Polymer Composition and Inherent Viscosity on Drug Release from PLGA Polymer Implants

Polymer composition and inherent viscosity are varied as described in Examples 1-7 to determine the additional contributions of these variables to drug release from PLGA polymer implants. Additional equations are produced, incorporating these variables.

Example 14: Scaling-Up of Risperidone Implants to Human Subjects

Considerable interspecies differences exist in the metabolism of risperidone, with both rabbits and monkeys requiring approximately 15 to 30 fold higher doses than humans for equivalent plasma concentrations (Bacopoulos N G, Redmond D E, et al, J Pharmacol Exp Ther 212: 1-5; Jibiki I, Kubota T, et al, Jpn J Psychiatry Neurol 47: 627-629; Klintenberg R, Gunne L, Andren P E (2002) Mov Disord 17: 360-365). Thus, the absolute doses used in the above animal studies approximate the amount of drug needed for a human, despite the difference in body mass. Since humans require approximately 1 mg/kg/month of risperidone (typically about 1.8 mg/day) when administered as a depot preparation, an implant system containing 600 mg would provide one year of treatment for a 50 kg patient. Thus, the implant design used in the animal studies necessitates about 1.5 grams of material with 40% drug load for one year of risperidone. At a density of 1.2 g per cc and diameter of 3.6 mm, this requires approximately 6.5 cm of implant rods.
Risperidone implants within the following parameters are administered to humans:
drug load between about 30%-60%, inclusive.
PLA:PGA molar ratio between about 50:50 and 100:0, inclusive.
Rod-shaped.
SA:V ratio between 1.5 and 2.
For example, rod-shaped implants with length between about 3-5 mm, inclusive and diameter between 2 and 3.6 mm, inclusive, exhibit the target SA:V ratio. By administration of 1 or more implants, a substantially symmetrical concentration profile is achieved, as seen in Example 2, with peak levels reached at approximately 6 months and therapeutic risperidone levels achieved between 2 and 8 months post implantation (FIG. 13A).

Example 15: Cyclical Administration or Risperidone Implants Achieves Long-Term Therapeutic Risperidone Levels

The symmetrical release profile described in Example 14 is used to provide long-term therapeutic drug levels by introducing a new set of implants approximately every 6 months (FIG. 13B). For example, two rods of 3.2 cm length with 100% PLA are administered every 6 months. As depicted, each subsequent set of implants increases medication levels at the same rate that the contribution from the previous set is declining, such that the overall rate of release remains approximately constant (FIG. 13C).

Example 16: Improvement of Initial Drug Levels by Inclusion of Faster-Release Polymers in the Initial Implantation

A limitation of a single-polymer system is a lag in reaching therapeutic levels following the initial implantation. Thus, additional implants that provide a more rapid time to peak concentration are included in the initial implantation. One or more of the implants depicted in Table 4 is included. Release rates of the rapid-release implants in Table 4 and resulting serum concentrations are derived from equations 8-10 by varying the parameters a1 and a4, which are related to drug content (total dose) and polymer degradation (PLGA ratio and inherent viscosity).

TABLE 4

Additional polymer implants utilized with initial implantation.
Implants contain between 40-60% risperidone load, inclusive,
and exhibit a target delivery of 0.15 mg/day. Each rod has a
3.6 mm diameter with density of 1.2 grams per cubic centimeter
(g/cc), yielding rods with approximately 125 mg/cm of implant.

	Days to
	maximum	Days to	mg implant	total cm implant
	concen-	full	mass 0%, 40%,	length 0%, 40%,
Polymer	tration	release	50%, 60%	50%, 60%

50:50 L	20	40	60, 60, 48, 40	0.5, 0.5, 0.4, 0.3
50:50 H	28	55	83, 83, 66, 55	0.6, 0.6, 0.5, 0.4
65:35 L	45	90	135, 135, 108, 90	1.1, 1.1, 0.8, 0.7
65:35 H	55	110	165, 165, 132, 110	1.1, 1.4, 1.1, 0.9
75:25 L	60	120	180, 180, 144, 120	1.5, 1.5, 1.2, 1.0
75:25 H	70	140	210, 210, 168, 140	1.7, 1.7, 1.3, 1.1
85:15 L	75	150	225, 225, 180, 150	1.8, 1.8, 1.4, 1.2
85:15 H	90	180	270, 270, 216, 180	2.1, 2.1, 1.7, 1.4
100:0 L	175	350	525, 525, 420, 350	4.2, 4.2, 3.4, 2.8
100:0 H	190	380	570, 570, 456, 380	4.5, 4.5, 3.6, 3.0

Positive Controls	Days of exposure = 30, 60, 90, 120, 180, 360

For example,FIG. 14A illustrates the drug release from four rapid-release implants having half-lives of approximately 2, 4, 8 and 12 weeks and full release intervals of approximately 4, 8, 16 and 24 weeks, respectively. For example, a set of implants containing half of the first 6 months of medication includes 4 implants with an average length of 0.8 cm, composed of 50:50, 65:35, 75:25 and 85:15 PLGA respectively. This set is given in combination with the slower-release implants, which provides the other half of the medication. When this combination of implants is administered at the first implantation, therapeutic drug levels are attained within a few days of implantation, and are sustained indefinitely via implantation of the slower-release implants at 6-month intervals thereafter (FIG. 14B).

Example 17: Sterile, Biodegradable PLGA-Risperidone Implants Provide Extended Risperidone Release

In vitro release profiles from sterile implants risperidone implants were measured. As depicted inFIG. 17, the implants released drug from day 0-58, after which no further drug was released. Thus, sterile PLGA-risperidone implants provide a release profile suitable for methods of the present invention.
To further characterize the properties of sterile vs. non-sterile implants, mice were implanted with either sterile or un-sterile PLGA-risperidone implants using the methods described for Example 5. Implants were removed at 14, 27, 56, or 83 days, mice were sacrificed, and serum risperidone concentration was assessed. In the first 3 groups, which were sacrificed at 56 days, serum levels from were 7-10 ng/ml at 14 days and increased to 15-20 ng/ml at 27 and 56 days. When implants were removed at 83 days, there was no detectable drug in serum (FIG. 18), consistent with both in vitro release patterns (above Examples) and residual risperidone content (below Examples).
In summary, sterile and non-sterile implants delivered drug for 56 days, while retaining coherence and removability until 83 days. Thus, sterile and non-sterile implants exhibited no significant differences. Accordingly, all of the properties of implants demonstrated in the above Examples apply to both sterile and non-sterile implants.

Example 18: Residual Risperidone Content in Implants Following Removal

Residual risperidone content was assessed following removal from mice of the previous Example. As depicted inFIG. 19, the percent drug load decreased over time from its initial value of 30% (i.e. drug was released at a faster rate than polymer was degraded). Thus, the implants remained coherent and removable well past the period during wherein drug was released, showing that implants of the present invention can be removed throughout the desired delivery interval. However, because they are biodegradable, the implants do not require removal.

Example 19: In Vitro Stability of Risperidone at Low pH

To determine whether low pH environment would affect stability of risperidone, risperidone was stored at pH 4.4 to 7.4 for 172 days and was found to be completely stable (FIG. 20). Similar results were observed at pH values of 2.0 and 3.0 over a 68-day experiment. Thus, risperidone is stable at both a neutral pH and low pH.

Claims

1.-81. (canceled)

82. An implant comprising a therapeutic drug and a polymer, said polymer comprising polylactic acid (PLA) and optionally polyglycolic acid (PGA) in a PLA:PGA molar ratio between 50:50 and 100:0, wherein said therapeutic drug is present in an amount of about 10%-30% (w/w), wherein the presence of said polymer in said implant extends the release duration of said therapeutic drug in a subject for a period of 1 to 6 months, and wherein said therapeutic drug is risperidone or 9-OH-risperidone.

83. The implant ofclaim 82, wherein said drug is present in an amount of about 30% (w/w).

84. The implant ofclaim 82, wherein said drug is present in an amount of about 20% (w/w).

85. The implant ofclaim 82, wherein said drug is present in an amount of about 15% (w/w).

86. The implant ofclaim 82, wherein said drug is present in an amount of about 10% (w/w).

87. The implant ofclaim 82, wherein said drug is risperidone.

88. The implant ofclaim 82, wherein said drug is 9-OH-risperidone

89. The implant ofclaim 82, wherein said polymer is a biodegradable polymer.

90. The implant ofclaim 82, wherein said polymer is present in an amount of about 40-70% (w/w).

91. The implant ofclaim 82, wherein said polymer is present in an amount of about 35-75% (w/w).

92. The implant ofclaim 82, wherein said implant is a subcutaneous implant.

93. A method for treating schizophrenia in a subject in need thereof, the method comprising subcutaneously administering to the subject a composition for providing an implant comprising a therapeutic drug and a biodegradable polymer, said polymer comprising polylactic acid (PLA) and optionally polyglycolic acid (PGA) in a PLA:PGA molar ratio between 50:50 and 100:0, wherein said therapeutic drug is present in an amount of about 10%-30% (w/w), wherein the presence of said polymer in said implant extends the release duration of said therapeutic drug in a subject for a period of 1 to 6 months, and wherein said therapeutic drug is risperidone or 9-OH-risperidone.

94. The method ofclaim 93, wherein said drug is present in an amount of about 30% (w/w).

95. The method ofclaim 93, wherein said drug is present in an amount of about 20% (w/w).

96. The method ofclaim 93, wherein said drug is present in an amount of about 15% (w/w).

97. The method ofclaim 93, wherein said drug is present in an amount of about 10% (w/w).

98. The method ofclaim 93, wherein said drug is risperidone.

99. The method ofclaim 93, wherein said drug is 9-OH-risperidone

100. The method ofclaim 93, wherein said polymer is present in an amount of about 40-70% (w/w).

101. The method ofclaim 93, wherein said polymer is present in an amount of about 35-75% (w/w).