US20120282298A1 - Corticosteroids for the treatment of joint pain - Google Patents

Corticosteroids for the treatment of joint pain Download PDF

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US20120282298A1
US20120282298A1 US13/368,580 US201213368580A US2012282298A1 US 20120282298 A1 US20120282298 A1 US 20120282298A1 US 201213368580 A US201213368580 A US 201213368580A US 2012282298 A1 US2012282298 A1 US 2012282298A1
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corticosteroid
microparticles
microparticle
lactic acid
class
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US13/368,580
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Neil Bodick
Robert C. Blanks
Anjali Kumar
Michael D. Clayman
Mark Moran
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Pacira Therapeutics Inc
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Priority to US13/368,580 priority Critical patent/US20120282298A1/en
Publication of US20120282298A1 publication Critical patent/US20120282298A1/en
Assigned to FLEXION THERAPEUTICS reassignment FLEXION THERAPEUTICS ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: MORAN, MARK, BLANKS, ROBERT C., BODICK, NEIL, CLAYMAN, MICHAEL D., KUMAR, ANJALI
Priority to US14/107,188 priority patent/US20140242170A1/en
Priority to US15/459,961 priority patent/US9949987B2/en
Priority to US15/937,053 priority patent/US10624905B2/en
Abandoned legal-status Critical Current

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Definitions

  • This invention relates to the use of corticosteroids to treat pain, including pain caused by inflammatory diseases such as osteoarthritis or rheumatoid arthritis, and to slow, arrest or reverse structural damage to tissues caused by an inflammatory disease, for example damage to articular and/or peri-articular tissues caused by osteoarthritis or rheumatoid arthritis. More specifically, a corticosteroid is administered locally as a sustained release dosage form (with or without an immediate release component) that results in efficacy accompanied by clinically insignificant or no measurable effect on endogenous cortisol production.
  • a sustained release dosage form with or without an immediate release component
  • Corticosteroids influence all tissues of the body and produce various cellular effects. These steroids regulate carbohydrate, lipid, protein biosynthesis and metabolism, and water and electrolyte balance. Corticosteroids influencing cellular biosynthesis or metabolism are referred to as glucocorticoids while those affecting water and electrolyte balance are mineralocorticoids. Both glucocorticoids and mineralocorticoids are released from the cortex of the adrenal gland.
  • corticosteroids particularly for extended periods of time
  • HPA hypothalamic-pituitary-adrenal
  • the HPA axis may be suppressed by the administration of corticosteroids, leading to a variety of unwanted side effects.
  • compositions and methods for the treatment of pain and inflammation using corticosteroids use one or more corticosteroids in a microparticle formulation.
  • the corticosteroid microparticle formulations provided herein are effective at treating pain and/or inflammation with minimal long-term side effects of corticosteroid administration, including for example, prolonged suppression of the HPA axis.
  • the corticosteroid microparticle formulations are suitable for administration, for example, local administration by injection into a site at or near the site of a patient's pain and/or inflammation.
  • corticosteroid microparticle formulations provided herein are effective in slowing, arresting, reversing or otherwise inhibiting structural damage to tissues associated with progressive disease with minimal long-term side effects of corticosteroid administration, including for example, prolonged suppression of the HPA axis.
  • the corticosteroid microparticle formulations are suitable for administration, for example, local administration by injection into a site at or near the site of structural tissue damage.
  • prolonged suppression of the HPA axis refers to levels of cortisol suppression greater than 35% by day 14 post-administration, for example post-injection.
  • the corticosteroid microparticle formulations provided herein deliver the corticosteroid in a dose and in a controlled or sustained release manner such that the levels of cortisol suppression are at or below 35% by day 14 post-administration, for example post-injection.
  • the corticosteroid microparticle formulations provided herein deliver the corticosteroid in a dose and in a controlled or sustained release manner such that the levels of cortisol suppression are negligible and/or undetectable by 14 post-administration, for example post-injection.
  • the corticosteroid microparticle formulations provided herein deliver the corticosteroid in a dose and in a controlled or sustained release manner such that the levels of cortisol suppression are negligible at any time post-injection.
  • the corticosteroid microparticle formulations in these embodiments are effective in the absence of any significant HPA axis suppression.
  • Administration of the corticosteroid microparticle formulations provided herein can result in an initial “burst” of HPA axis suppression, for example, within the first few days, within the first two days and/or within the first 24 hours post-injection, but by day 14 post-injection, suppression of the HPA axis is less than 35%.
  • a sustained release form of corticosteroids is administered locally to treat pain and inflammation.
  • Local administration of a corticosteroid microparticle formulation can occur, for example, by injection into the intra-articular space, peri-articular space, soft tissues, lesions, epidural space, perineural space, or the foramenal space at or near the site of a patient's pain.
  • the formulation additionally contains an immediate release component.
  • a sustained release form of corticosteroids is administered (e.g., by single injection or as sequential injections) into an intra-articular space for the treatment of pain, for example, due to osteoarthritis, rheumatoid arthritis, gouty arthritis, bursitis, tenosynovitis, epicondylitis, synovitis or other joint disorder.
  • a sustained release form of corticosteroids is administered (e.g., by single injection or as sequential injections) into soft tissues or lesions for the treatment of inflammatory disorders, for example, the inflammatory and pruritic manifestations of corticosteroid-responsive dermatoses such as psoriasis.
  • a sustained release form of corticosteroids is administered (e.g., by single injection or as sequential injections) into an epidural space, a perineural space, a foramenal space or other spinal space for the treatment of corticosteroid-responsive degenerative musculoskeletal disorders such as Neurogenic Claudication.
  • a sustained release form of corticosteroids is administered (e.g., by single injection or as sequential injections) into an intra-articular space or into soft tissues to slow, arrest, reverse or otherwise inhibit structural damage to tissues associated with progressive disease such as, for example, the damage to cartilage associated with progression of osteoarthritis.
  • a combination of an immediate release form and a sustained release form of corticosteroids is administered (e.g., by single injection or as sequential injections) into an intra-articular space for the treatment of pain, for example, due to osteoarthritis, rheumatoid arthritis or other joint disorder(s).
  • a combination of an immediate release form and a sustained release form of corticosteroids is administered (e.g., by single injection or as sequential injections) into an intra-articular space or into soft tissues to slow, arrest, reverse or otherwise inhibit structural damage to tissues associated with progressive disease such as, for example, the damage to cartilage associated with progression of osteoarthritis.
  • compositions and methods of embodiments of the invention can achieve immediate relief of the acute symptoms (e.g., pain and inflammation) of these diseases or conditions and additionally provide a sustained or long term therapy (e.g., slowing, arresting, reversing or otherwise inhibiting structural damage to tissues associated with progressive disease), while avoiding long term systemic side effects associated with corticosteroid administration, including HPA suppression.
  • a sustained or long term therapy e.g., slowing, arresting, reversing or otherwise inhibiting structural damage to tissues associated with progressive disease
  • a formulation wherein a microparticle matrix (such as PLGA, PLA, hydrogels, hyaluronic acid, etc.) incorporates a corticosteroid, and the corticosteroid microparticle formulation provides at least two weeks, preferably at least three weeks, including up to and beyond 30 days, or 60 days, or 90 days of a sustained, steady state release of the corticosteroid.
  • a microparticle matrix such as PLGA, PLA, hydrogels, hyaluronic acid, etc.
  • a formulation wherein a microparticle matrix (such as PLGA, PLA, hydrogels, hyaluronic acid, etc.) incorporates a corticosteroid, and the corticosteroid microparticle formulation provides at least two weeks, preferably at least three weeks, including up to and beyond 30 days, or 60 days, or 90 days of a sustained, steady state release of the corticosteroid at a rate that does not adversely suppress the HPA axis.
  • a microparticle matrix such as PLGA, PLA, hydrogels, hyaluronic acid, etc.
  • the corticosteroid microparticle formulation retains sustained efficacy even after the corticosteroid is no longer resident at the site of administration, for example, in the intra-articular space, and/or after the corticosteroid is no longer detected in the systemic circulation.
  • the corticosteroid microparticle formulation retains sustained efficacy even after the corticosteroid microparticle formulation is no longer resident at the site of administration, for example, in the intra-articular space, and/or the corticosteroid microparticle formulation is no longer detected in the systemic circulation.
  • the corticosteroid microparticle formulation retains sustained efficacy even after the corticosteroid microparticle formulation ceases to release therapeutically effective amounts of corticosteroid.
  • the corticosteroid released by the microparticle formulation retains efficacy for at least one week, at least two weeks, at least three weeks, at least four weeks, at least five weeks, at least six weeks, at least seven weeks, at least eight weeks, at least nine weeks, at least twelve weeks, or more than twelve-weeks post-administration.
  • the corticosteroid released by the microparticle formulation retains efficacy for a time period that is at least twice as long, at least three times as long, or more than three times as long as the residency period for the corticosteroid and/or the corticosteroid microparticle formulation.
  • the sustained, steady state release of corticosteroid will not adversely suppress the HPA axis.
  • a controlled or sustained-release formulation wherein a microparticle matrix (such as PLGA, hydrogels, hyaluronic acid, etc.) incorporates a corticosteroid, and the formulation may or may not exhibit an initial rapid release, also referred to herein as an initial “burst” of the corticosteroid for a first length of time of between 0 and 14 days, for example, between the beginning of day 1 through the end of day 14, in addition to the sustained, steady state release of the corticosteroid for a second length of time of at least two weeks, preferably at least three weeks, including up to and beyond 30 days, or 60 days, or 90 days.
  • a microparticle matrix such as PLGA, hydrogels, hyaluronic acid, etc.
  • a controlled or sustained-release formulation wherein a microparticle matrix (such as PLGA, hydrogels, hyaluronic acid, etc.) incorporates a corticosteroid, and the formulation may or may not exhibit an initial rapid release, also referred to herein as an initial “burst” of the corticosteroid for a first length of time of between 0 and 14 days, e.g., between the beginning of day 1 through the end of day 14, in addition to the sustained, steady state release of the corticosteroid for a second length of time of at least two weeks, preferably at least three weeks, including up to and beyond 30 days, or 60 days, or 90 days where the sustained, steady state release of corticosteroid is released at a rate that does not suppress the HP
  • the sustained, steady state release of corticosteroid will not adversely suppress the HPA axis, for example, the level of HPA axis suppression at or less than 35% by day 14 post-administration. In some embodiments, the sustained, steady state release of corticosteroid does not significantly suppress the HPA axis, for example, the level of HPA axis suppression is negligible and/or undetectable by day 14 post-injection. In some embodiments, the sustained, steady state release of corticosteroid does not significantly suppress the HPA axis, for example, the level of HPA axis suppression is negligible at all times post-injection. In some embodiments, the length of sustained release is between 21 days and 90 days.
  • the length of sustained release is between 21 days and 60 days. In some embodiments, the length of sustained release is between 14 days and 30 days. In some embodiments, the length of release of the initial “burst” component is between 0 and 10 days, for example between the beginning of day 1 through the end of day 10. In some embodiments, the length of release of the initial “burst” component is between 0 and 6 days, for example between the beginning of day 1 through the end of day 6. In some embodiments, the length of initial “burst,” component is between 0 and 2 days, for example between the beginning of day 1 through the end of day 2. In some embodiments, the length of initial “burst” component is between 0 and 1 day, for example between the beginning of day 1 through the end of day 1.
  • corticosteroid microparticle formulations provided herein can be used in combination with any of a variety of therapeutics, also referred to herein as “co-therapies.”
  • the corticosteroid microparticle formulations can be used in combination with an immediate release corticosteroid solution or suspension, which provides high local exposures for between 1 day and 14 days following administration and which produce systemic exposures that may be associated with transient suppression of the HPA axis.
  • an immediate release corticosteroid solution or suspension which provides high local exposures for between 1 day and 14 days following administration and which produce systemic exposures that may be associated with transient suppression of the HPA axis.
  • 40 mg of immediate release triamcinolone acetonide co-administered with the corticosteroid microparticle formulation in the intra-articular space would be expected to produce high local concentrations lasting for about 12 days.
  • the contribution of the immediate release component to the plasma concentration would be small, less than 0.1 ng/ml, and the contribution to the intra articular concentration of the immediate release component would also be small.
  • the corticosteroid microparticle formulation would continue to release corticosteroid in the intra articular space at a rate that extends the duration of therapeutic effect and does not suppress the HPA axis.
  • the same corticosteroid is used in both the immediate release and sustained release components.
  • the immediate release component contains a corticosteroid that is different from that of the sustained release component.
  • the sustained, steady state release of corticosteroid will not adversely suppress the HPA axis.
  • the period of sustained release is between 21 days and 90 days. In some embodiments, the period of sustained release is between 21 days and 60 days. In some embodiments, the period of sustained release is between 14 days and 30 days. In some embodiments, the high local exposure attributable to the immediate release component lasts for between 1 day and 14 days. In some embodiments, the high local exposure attributable to the immediate release component lasts for between 1 day and 10 days. In some embodiments, the high local exposure attributable to the immediate release component lasts between 1 days and 8 days. In some embodiments, the high local exposure attributable to the immediate release component lasts between 1 days and 6 days. In some embodiments, the high local exposure attributable to the immediate release component lasts for between 1 day and 4 days.
  • the corticosteroid microparticle formulation may provide an initial release of corticosteroid at the site of administration, for example, in the intra-articular space and/or peri-articular space.
  • the controlled or sustained release of the corticosteroid microparticle formulations continues to provide therapeutic (e.g., intra-articular and/or peri-articular) concentrations of corticosteroid to suppress inflammation, maintain analgesia, and/or slow, arrest or reverse structural damage to tissues for an additional period of therapy following administration ( FIG. 1 , top tracings).
  • the systemic exposure associated with the sustained release component does not suppress the HPA axis ( FIG. 1 , bottom tracings).
  • the invention includes therapies and formulations that may exhibit an initial release of corticosteroid followed by controlled or sustained release where the therapy comprises a period of therapy wherein the corticosteroid is released from the sustained release component and the plasma levels of the corticosteroid does not adversely suppress the HPA axis.
  • the length of sustained release is between 21 days and 90 days. In some embodiments, the length of sustained release is between 21 days and 60 days. In some embodiments, the length of sustained release is between 14 days and 30 days. In some embodiments, the length of release of the immediate release form is In some embodiments, the length of release of the immediate release form is between 1 day and 14 days. In some embodiments, the length of release of the immediate release form is between 1 day and 10 days. In some embodiments, the length of release of the immediate release form is between 1 day and 8 days. In some embodiments, the length of release of the immediate release form is between 1 day and 6 days. In some embodiments, the length of release of the immediate release form is between 1 day and 4 days.
  • the invention provides populations of microparticles including a Class B corticosteroid or a pharmaceutically acceptable salt thereof incorporated in, admixed, encapsulated or otherwise associated with a lactic acid-glycolic acid copolymer matrix, wherein the Class B corticosteroid is between 22% to 28% of the microparticles.
  • the invention also provides controlled or sustained release preparation of a Class B corticosteroid that include a lactic acid-glycolic acid copolymer microparticle containing the Class B corticosteroid, wherein the Class B corticosteroid is between 22% to 28% of the lactic acid-glycolic acid copolymer microparticle matrix.
  • the invention also provides formulations that include (a) controlled- or sustained-release microparticles comprising a Class B corticosteroid and a lactic acid-glycolic acid copolymer matrix, wherein the Class B corticosteroid comprises between 22% to 28% of the microparticles and wherein the lactic acid-glycolic acid copolymer has one of more of the following characteristics: (i) a molecular weight in the range of about 40 to 70 kDa; (ii) an inherent viscosity in the range of 0.3 to 0.5 dL/g; (iii) a lactide:glycolide molar ratio of 80:20 to 60:40; and/or (iv) the lactic acid-glycolic acid copolymer is carboxylic acid endcapped.
  • the copolymer is biodegradable.
  • the lactic acid-glycolic acid copolymer is a poly(lactic-co-glycolic) acid copolymer (PLGA).
  • the lactic acid-glycolic acid copolymer has a molar ratio of lactic acid:glycolic acid from the range of about 80:20 to 60:40.
  • the lactic acid-glycolic acid copolymer has a molar ratio of lactic acid:glycolic acid of 75:25.
  • the invention also provides populations of microparticles including a Class B corticosteroid or a pharmaceutically acceptable salt thereof incorporated in, admixed, encapsulated or otherwise associated with a mixed molecular weight lactic acid-glycolic acid copolymer matrix, wherein the Class B corticosteroid is between 12% to 28% of the microparticles.
  • the corticosteroid microparticle formulation includes a Class B corticosteroid and a microparticle made using 75:25 PLGA formulation with two PLGA polymers, one of low molecular weight and one of high molecular weight in a two to one ratio, respectively.
  • the low molecular weight PLGA has a molecular weight of range of 15-35 kDa and an inherent viscosity range from 0.2 to 0.35 dL/g and the high molecular weight PLGA has a range of 70-95 kDa and an inherent viscosity range of 0.5 to 0.70 dL/g.
  • the microparticles have a mean diameter in the range of 10-100 ⁇ M.
  • the microparticles have a mean diameter in the range of 20-100 ⁇ M, 20-90 ⁇ M, 30-100 ⁇ M, 30-90 ⁇ M, or 10-90 ⁇ M. It is understood that these ranges refer to the mean diameter of all microparticles in a given population. The diameter of any given individual microparticle could be within a standard deviation above or below the mean diameter.
  • the invention also provides populations of microparticles including a Class B corticosteroid or a pharmaceutically acceptable salt thereof incorporated in, admixed, encapsulated or otherwise associated with a lactic acid-glycolic acid copolymer matrix containing 10-20% triblock (PEG-PLGA-PEG) having an inherent viscosity in the range from 0.6 to 0.8 dL/g, wherein the Class B corticosteroid is between 22% to 28% of the microparticles.
  • a Class B corticosteroid or a pharmaceutically acceptable salt thereof incorporated in, admixed, encapsulated or otherwise associated with a lactic acid-glycolic acid copolymer matrix containing 10-20% triblock (PEG-PLGA-PEG) having an inherent viscosity in the range from 0.6 to 0.8 dL/g, wherein the Class B corticosteroid is between 22% to 28% of the microparticles.
  • the corticosteroid microparticle formulation includes a Class B corticosteroid and a microparticle made using 75:25 PLGA formulation and containing 10-20% triblock (PEG-PLGA-PEG) having an inherent viscosity in the range from 0.6 to 0.8 dL/g.
  • the microparticles have a mean diameter in the range of 10-100 ⁇ M.
  • the microparticles have a mean diameter in the range of 20-100 ⁇ M, 20-90 ⁇ M, 30-100 ⁇ M, 30-90 ⁇ M, or 10-90 ⁇ M. It is understood that these ranges refer to the mean diameter of all microparticles in a given population. The diameter of any given individual microparticle could be within a standard deviation above or below the mean diameter.
  • Class B corticosteroid microparticle formulations, preparations, and populations thereof when administered to a patient, exhibit reduced undesirable side effects in patient, for example, undesirable effects on a patient's cartilage or other structural tissue, as compared to the administration, for example administration into the intra-articular space of a joint, of an equivalent amount of the Class B corticosteroid absent any microparticle or other type of incorporation, admixture, or encapsulation.
  • the Class B corticosteroid is triamcinolone acetonide or a commercially available chemical analogue or a pharmaceutically-acceptable salt thereof.
  • the total dose of corticosteroid contained in the microparticles is in the range of 10-90 mg, where the Class B corticosteroid is between 12-28% of the microparticle, for example, between 22-28% of the microparticle (i.e., when the corticosteroid is 28% of the microparticle, the microparticle is in the range of 35.7-321.4 mgs, and so on for all values between 22-28% load dose, when the corticosteroid is 25% of the microparticle, the microparticle is in the range of 40-360 mgs, when the corticosteroid is 22% of the microparticle, the microparticle is in the range of 45.5-409.1 mgs, when the corticosteroid is 12% of the microparticle, the microparticle is in the range of 83.3-750 mgs, and
  • the Class B corticosteroid contained in the microparticles is 12-28% of the microparticle, for example, between 22-28% of the microparticle and the total dose of corticosteroid is in a range selected from 10-80 mg, 10-70 mg, 10-60 mg, 10-50 mg, 10-40 mg, 10-30 mg, 10-20 mg, 20-90 mg, 20-80 mg, 20-70 mg, 20-60 mg, 20-50 mg, 20-40 mg, 20-30 mg, 30-90 mg, 30-80 mg, 30-70 mg, 30-60 mg, 30-50 mg, 30-40 mg, 40-90 mg, 40-80 mg, 40-70 mg, 40-60 mg, 40-50 mg, 50-90 mg, 50-80 mg, 50-70 mg, 50-60 mg, 60-90 mg, 60-80 mg, 60-70 mg, 70-90 mg, 70-80 mg, and 80-90 mg.
  • the Class B corticosteroid is released for between 14 days and 90 days.
  • the microparticles have a mean diameter of between 10 ⁇ m to 100 ⁇ m, for example, the microparticles have a mean diameter in the range of 20-100 ⁇ M, 20-90 ⁇ M, 30-100 ⁇ M, 30-90 ⁇ M, or 10-90 ⁇ M. It is understood that these ranges refer to the mean diameter of all microparticles in a given population. The diameter of any given individual microparticle could be within a standard deviation above or below the mean diameter.
  • the microparticles further comprise a polyethylene glycol (PEG) moiety, wherein the PEG moiety comprises between 25% to 0% weight percent of the microparticle.
  • PEG polyethylene glycol
  • the populations, preparations and/or formulations of the invention do not require the presence of PEG to exhibit the desired corticosteroid sustained release kinetics and bioavailability profile.
  • the corticosteroid microparticle formulation includes triamcinolone acetonide (TCA) and a microparticle made using 75:25 PLGA formulation having an inherent viscosity in the range from 0.3 to 0.5 dL/g and/or a molecular weight in the range of 40-70 kDa, for example between 50-60 kDa.
  • TCA triamcinolone acetonide
  • the microparticles have a mean diameter in the range of 10-100 ⁇ m.
  • the microparticles have a mean diameter in the range of 20-100 ⁇ M, 20-90 ⁇ M, 30-100 ⁇ M, 30-90 ⁇ M, or 10-90 ⁇ M. It is understood that these ranges refer to the mean diameter of all microparticles in a given population. The diameter of any given individual microparticle could be within a standard deviation above or below the mean diameter.
  • the range of TCA load percentage is between 22-28%. In one embodiment, the load percentage of TCA in the microparticles in 25%.
  • microparticles in the TCA PLGA microparticle formulations can be formulated using PLGA polymers having a range of molecular weights from 40 to 70 kDa, most preferably from 50 to 60 kDa and range of inherent viscosities from 0.5 to 0.5 dL/g, most preferably from 0.38 to 0.42 dL/g.
  • the total dose of corticosteroid contained in the microparticles is in the range of 10-90 mg, where TCA is between 22-28% of the microparticle (i.e., when TCA is 25% of the microparticle, the microparticle is in the range of 40-360 mgs, when TCA is 22% of the microparticle, the microparticle is in the range of 45.5-409.1 mgs, when TCA is 28% of the microparticle, the microparticle is in the range of 35.7-321.4 mgs, and so on for all values between 22-28% load dose).
  • total dose of corticosteroid contained in the microparticles is in a range selected from 10-80 mg, 10-70 mg, 10-60 mg, 10-50 mg, 10-40 mg, 10-30 mg, 10-20 mg, 20-90 mg, 20-80 mg, 20-70 mg, 20-60 mg, 20-50 mg, 20-40 mg, 20-30 mg, 30-90 mg, 30-80 mg, 30-70 mg, 30-60 mg, 30-50 mg, 30-40 mg, 40-90 mg, 40-80 mg, 40-70 mg, 40-60 mg, 40-50 mg, 50-90 mg, 50-80 mg, 50-70 mg, 50-60 mg, 60-90 mg, 60-80 mg, 60-70 mg, 70-90 mg, 70-80 mg, and 80-90 mg.
  • the microparticles further comprise a polyethylene glycol (PEG) moiety, wherein the PEG moiety comprises between 25% to 0% weight percent of the microparticle.
  • PEG polyethylene glycol
  • the populations, preparations and/or formulations of the invention do not require the presence of PEG to exhibit the desired corticosteroid sustained release kinetics and bioavailability profile.
  • the corticosteroid microparticle formulation includes triamcinolone acetonide (TCA) and a microparticle made using 75:25 PLGA formulation and containing 10-20% triblock (PEG-PLGA-PEG) having an inherent viscosity in the range from 0.6 to 0.8 dL/g.
  • TCA triamcinolone acetonide
  • PEG-PLGA-PEG poly(ethylene glycol)-propyl glycol glycol)
  • the microparticles have a mean diameter in the range of 10-100 ⁇ M.
  • the microparticles have a mean diameter in the range of 20-100 ⁇ M, 20-90 ⁇ M, 30-100 ⁇ M, 30-90 ⁇ M, or 10-90 ⁇ M. It is understood that these ranges refer to the mean diameter of all microparticles in a given population. The diameter of any given individual microparticle could be within a standard deviation above or below the mean diameter.
  • the corticosteroid microparticle formulation includes triamcinolone acetonide (TCA) and a microparticle made using 75:25 PLGA formulation with two PLGA polymers, one of low molecular weight and one of high molecular weight in a two to one ratio, respectively.
  • TCA triamcinolone acetonide
  • the low molecular weight PLGA has a molecular weight of range of 15-35 kDa and an inherent viscosity range from 0.2 to 0.35 dL/g and the high molecular weight PLGA has a range of 70-95 kDa and an inherent viscosity range of 0.5 to 0.70 dL/g.
  • the microparticles have a mean diameter in the range of 10-100 ⁇ M. In some embodiments, the microparticles have a mean diameter in the range of 20-100 ⁇ M, 20-90 ⁇ M, 30-100 ⁇ M, 30-90 ⁇ M, or 10-90 ⁇ M. It is understood that these ranges refer to the mean diameter of all microparticles in a given population. The diameter of any given individual microparticle could be within a standard deviation above or below the mean diameter.
  • TCA microparticle formulations, preparations, and populations thereof when administered to a patient, exhibit reduced undesirable side effects in patient, for example, undesirable effects on a patient's cartilage or other structural tissue, as compared to the administration, for example administration into the intra-articular space of a joint, of an equivalent amount of TCA absent any microparticle or other type of incorporation, admixture, or encapsulation.
  • the Class B corticosteroid is budesonide or a commercially available chemical analogue or pharmaceutically acceptable salt thereof.
  • the budesonide is incorporated in a lactic acid-glycolic acid copolymer matrix, wherein the budesonide (or a commercially available chemical analogue or pharmaceutically acceptable salt thereof) comprises between 22% to 28% of the microparticles.
  • the budesonide or commercially available chemical analogue or pharmaceutically acceptable salt thereof is incorporated in a controlled or sustained release preparation that includes a lactic acid-glycolic acid copolymer microparticle containing the budesonide (or a commercially available chemical analogue or pharmaceutically acceptable salt thereof), wherein the budesonide comprises between 22% to 28% of the lactic acid-glycolic acid copolymer microparticle matrix.
  • the copolymer is biodegradable.
  • the lactic acid-glycolic acid copolymer is a poly(lactic-co-glycolic) acid copolymer (PLGA).
  • the lactic acid-glycolic acid copolymer comprises an acid endcap.
  • the microparticles have a mean diameter of between 10 ⁇ m to 100 ⁇ m. In some embodiments, the microparticles have a mean diameter in the range of 20-100 ⁇ M, 20-90 ⁇ M, 30-100 ⁇ M, 30-90 ⁇ M, or 10-90 ⁇ M. It is understood that these ranges refer to the mean diameter of all microparticles in a given population.
  • the diameter of any given individual microparticle could be within a standard deviation above or below the mean diameter.
  • the lactic acid-glycolic acid copolymer has a molar ratio of lactic acid:glycolic acid from the range of about 80:20 to 60:40. In some embodiments, the lactic acid-glycolic acid copolymer has a molar ratio of lactic acid:glycolic acid of 75:25.
  • the microparticles further include a polyethylene glycol (PEG) moiety, wherein the PEG moiety is between 25% to 0% weight percent of the microparticle.
  • PEG polyethylene glycol
  • the populations, preparations and/or formulations of the invention do not require the presence of PEG to exhibit the desired corticosteroid sustained release kinetics and bioavailability profile.
  • budesonide or commercially available chemical analogue or pharmaceutically acceptable salt thereof is released for between 14 days and 90 days.
  • the budesonide or commercially available chemical analogue or pharmaceutically acceptable salt thereof is incorporated in a formulation that includes controlled or sustained-release microparticles including the budesonide or a commercially available chemical analogue or a pharmaceutically-acceptable salt thereof, wherein the budesonide comprises between 22% to 28% of the microparticles and wherein the lactic acid-glycolic acid copolymer has one of more of the following characteristics: (i) a molecular weight in the range of about 40 to 70 kDa; (ii) an inherent viscosity in the range of 0.35 to 0.5 dL/g; or (iii) a lactide:glycolide molar ratio of 80:20 to 60:40 or a lactide:glycolide molar ratio of 80:20 to 50:50.
  • the copolymer is biodegradable.
  • the lactic acid-glycolic acid copolymer is a poly(lactic-co-glycolic) acid copolymer (PLGA).
  • the lactic acid-glycolic acid copolymer comprises an acid endcap.
  • the microparticles have a mean diameter of between 10 ⁇ m to 100 ⁇ m. In some embodiments, the microparticles have a mean diameter in the range of 20-100 ⁇ M, 20-90 ⁇ M, 30-100 ⁇ M, 30-90 ⁇ M, or 10-90 ⁇ M. It is understood that these ranges refer to the mean diameter of all microparticles in a given population.
  • the diameter of any given individual microparticle could be within a standard deviation above or below the mean diameter.
  • the lactic acid-glycolic acid copolymer has a molar ratio of lactic acid:glycolic acid from the range of about 80:20 to 60:40. In some embodiments, the lactic acid-glycolic acid copolymer has a molar ratio of lactic acid:glycolic acid of 75:25.
  • the microparticles further include a polyethylene glycol (PEG) moiety, wherein the PEG moiety is between 25% to 0% weight percent of the microparticle.
  • budesonide or commercially available chemical analogue or pharmaceutically acceptable salt thereof is released for between 14 days and 90 days.
  • the corticosteroid microparticle formulation includes a Class A, C, or D corticosteroid and a microparticle made using 50:50 PLGA formulation.
  • the Class A corticosteroid is prednisolone.
  • the Class C corticosteroid is betamethasone.
  • the Class D corticosteroid is fluticasone or fluticasone propionate.
  • the microparticles have a mean diameter in the range of 10-100 ⁇ M.
  • the microparticles have a mean diameter in the range of 20-100 ⁇ M, 20-90 ⁇ M, 30-100 ⁇ M, 30-90 ⁇ M, or 10-90 ⁇ M. It is understood that these ranges refer to the mean diameter of all microparticles in a given population. The diameter of any given individual microparticle could be within a standard deviation above or below the mean diameter.
  • the range of corticosteroid load percentage is between 10-40%, for example, between 15%-30%.
  • the range of corticosteroid load percentage is between 8-20%.
  • microparticles in the Class A, C or D PLGA microparticle formulations can be formulated using PLGA polymers having a range of inherent viscosities from 0.35 to 0.5 dL/g and approximated molecular weights from 40 kDa to 70 kDa.
  • Class A, C or D corticosteroid microparticle formulations, preparations, and populations thereof when administered to a patient, exhibit reduced undesirable side effects in patient, for example, undesirable effects on a patient's cartilage or other structural tissue, as compared to the administration, for example administration into the intra-articular space of a joint, of an equivalent amount of the Class A, C or D corticosteroid absent any microparticle or other type of incorporation, admixture, or encapsulation.
  • the invention provides populations of microparticles including a Class A corticosteroid or a pharmaceutically acceptable salt thereof incorporated in, admixed, encapsulated or otherwise associated with a lactic acid-glycolic acid copolymer matrix, wherein the Class A corticosteroid is between 15% to 30% of the microparticles.
  • the invention also provides controlled or sustained release preparations of a Class A corticosteroid including a lactic acid-glycolic acid copolymer microparticle containing the Class A corticosteroid, wherein the Class A corticosteroid is between 10% to 40%, for example between 15% to 30% of the lactic acid-glycolic acid copolymer microparticle matrix.
  • the invention provides formulations that include (a) controlled- or sustained-release microparticles including a Class A corticosteroid and a lactic acid-glycolic acid copolymer matrix, wherein the Class A corticosteroid is between 15% to 30% of the microparticles and wherein the lactic acid-glycolic acid copolymer has one of more of the following characteristics: (i) a molecular weight in the range of about 40 to 70 kDa; (ii) an inherent viscosity in the range of 0.35 to 0.5 dL/g; (iii) a lactide:glycolide molar ratio of 60:40 to 45:55; and/or (iv) the lactic acid-glycolic acid copolymer is carboxylic acid endcapped
  • the copolymer is biodegradable.
  • the lactic acid-glycolic acid copolymer is a poly(lactic-co-glycolic) acid copolymer (PLGA).
  • the lactic acid-glycolic acid copolymer has a molar ratio of lactic acid:glycolic acid from the range of about 60:40 to 45:55.
  • the lactic acid-glycolic acid copolymer has a molar ratio of lactic acid:glycolic acid of 50:50.
  • the Class A corticosteroid is prednisolone or a commercially available chemical analogue or a pharmaceutically-acceptable salt thereof.
  • total dose of the Class A corticosteroid contained in the microparticles is in a range selected from 10-250 mg, where the Class A corticosteroid is between 10-40%, for example, between 15-30% of the microparticle (i.e., when the corticosteroid is 10% of the microparticle, the microparticle is in the range of 100-2500 mgs, when the corticosteroid is 15% of the microparticle, the microparticle is in the range of 66.7-1666.7 mgs, when the corticosteroid is 20% of the microparticle, the microparticle is in the range of 50-1250 mgs, when the corticosteroid is 25% of the microparticle, the microparticle is in the range of 40-1000 mgs, when the corticosteroid is 30% of the microparticle, the microparticle is in the range of 3
  • the total dose of corticosteroid is in the range of 10-225 mg, 10-200 mg, 10-175 mg, 10-150 mg, 10-120 mg, 10-100 mg, 10-75 mg, 10-50 mg, 10-25 mg, 20-250 mg, 20-225 mg, 20-200 mg, 20-175 mg, 20-150 mg, 20-125 mg, 20-100 mg, 20-75 mg, 20-50 mg, 30-250 mg, 30-225 mg, 30-200 mg, 30-175 mg, 30-150 mg, 30-120 mg, 30-100 mg, 30-75 mg, 30-50 mg, 40-250 mg, 40-225 mg, 40-200 mg, 40-175 mg, 40-150 mg, 40-120 mg, 40-100 mg, 40-75 mg, 50-250 mg, 50-225 mg, 50-200 mg, 50-175 mg, 50-150 mg, 50-120 mg, 50-100 mg, 50-120 mg, 50-100 mg, 50-75 mg, 60-250 mg, 60-225 mg, 60-200 mg, 60-175 mg, 60-150 mg, 60-120 mg, 60-1
  • the microparticles have a mean diameter of between 10 ⁇ m to 100 ⁇ m, for example, the microparticles have a mean diameter in the range of 20-100 ⁇ M, 20-90 ⁇ M, 30-100 ⁇ M, 30-90 ⁇ M, or 10-90 ⁇ M. It is understood that these ranges refer to the mean diameter of all microparticles in a given population. The diameter of any given individual microparticle could be within a standard deviation above or below the mean diameter.
  • the microparticles further comprise a polyethylene glycol (PEG) moiety, wherein the PEG moiety comprises between 25% to 0% weight percent of the microparticle.
  • PEG polyethylene glycol
  • the populations, preparations and/or formulations of the invention do not require the presence of PEG to exhibit the desired corticosteroid sustained release kinetics and bioavailability profile.
  • the corticosteroid microparticle formulation includes prednisolone and a microparticle made using 50:50 PLGA formulation having a molecular weight in the range of 40 kDa to 70 kDa.
  • the microparticles have a mean diameter in the range of 10-100 ⁇ M.
  • the microparticles have a mean diameter in the range of 20-100 ⁇ M, 20-90 ⁇ M, 30-100 ⁇ M, 30-90 ⁇ M, or 10-90 ⁇ M.
  • prednisolone/50:50 PLGA microparticle formulations the range of prednisolone load percentage is between 10-40%, for example, between 15-30%.
  • the microparticles further comprise a polyethylene glycol (PEG) moiety, wherein the PEG moiety comprises between 25% to 0% weight percent of the microparticle.
  • PEG polyethylene glycol
  • the populations, preparations and/or formulations of the invention do not require the presence of PEG to exhibit the desired corticosteroid sustained release kinetics and bioavailability profile.
  • the invention provides populations of microparticles including a Class C corticosteroid or a pharmaceutically acceptable salt thereof incorporated in, admixed, encapsulated or otherwise associated with a lactic acid-glycolic acid copolymer matrix, wherein the Class C corticosteroid is between 10% to 40% of the microparticles, for example between 15% to 30% of the microparticles.
  • the invention also provides controlled or sustained release preparations of a Class C corticosteroid including a lactic acid-glycolic acid copolymer microparticle containing the Class C corticosteroid, wherein the Class C corticosteroid is between 15% to 30% of the lactic acid-glycolic acid copolymer microparticle matrix.
  • the invention provides formulations that include (a) controlled- or sustained-release microparticles having a Class C corticosteroid and a lactic acid-glycolic acid copolymer matrix, wherein the Class C corticosteroid is between 15% to 30% of the microparticles and wherein the lactic acid-glycolic acid copolymer has one of more of the following characteristics: (i) a molecular weight in the range of about 40 to 70 kDa; (ii) an inherent viscosity in the range of 0.35 to 0.5 dL/g; (iii) a lactide:glycolide molar ratio of 60:40 to 45:55; and/or (iv) the lactic acid-glycolic acid copolymer is carboxylic acid endcapped.
  • the copolymer is biodegradable.
  • the lactic acid-glycolic acid copolymer is a poly(lactic-co-glycolic) acid copolymer (PLGA).
  • the lactic acid-glycolic acid copolymer has a molar ratio of lactic acid:glycolic acid from the range of about 60:40 to 45:55.
  • the lactic acid-glycolic acid copolymer has a molar ratio of lactic acid:glycolic acid of 50:50.
  • the Class C corticosteroid is betamethasone or a commercially available chemical analogue or a pharmaceutically-acceptable salt thereof.
  • total dose of the Class C corticosteroid contained in the microparticles is in a range selected from 2-250 mg, where the Class C corticosteroid is between 10-40%, for example, between 15-30% of the microparticle (i.e., when the corticosteroid is 10% of the microparticle, the microparticle is in the range of 20-2500 mgs, when the corticosteroid is 15% of the microparticle, the microparticle is in the range of 13.3-1666.7 mgs, when the corticosteroid is 20% of the microparticle, the microparticle is in the range of 10-1250 mgs, when the corticosteroid is 25% of the microparticle, the microparticle is in the range of 8-1000 mgs, when the corticosteroid is 30% of the microparticle, the microparticle is in the range of 6.67-8
  • the total dose of corticosteroid is in the range of 2-225 mg, 2-200 mg, 2-175 mg, 2-150 mg, 2-120 mg, 2-100 mg, 2-75 mg, 2-60 mg, 2-55 mg, 2-50 mg, 2-45 mg, 2-40 mg, 2-35 mg, 2-30 mg, 2-25 mg, 2-20 mg, 2-15 mg, 2-10 mg, 4-225 mg, 4-200 mg, 4-175 mg, 4-150 mg, 4-120 mg, 4-100 mg, 4-75 mg, 4-60 mg, 4-55 mg, 4-50 mg, 4-45 mg, 4-40 mg, 4-35 mg, 4-30 mg, 4-25 mg, 4-20 mg, 4-15 mg, 4-10 mg, 5-225 mg, 5-200 mg, 5-175 mg, 5-150 mg, 5-120 mg, 5-100 mg, 5-75 mg, 5-60 mg, 5-55 mg, 5-50 mg, 5-45 mg, 5-40 mg, 5-35 mg, 5-30 mg, 5-25 mg, 5-20 mg, 5-15 mg, 5-10 mg, 6-225 mg, 6-200 mg, 6-175 mg, 6-
  • the microparticles have a mean diameter of between 10 ⁇ m to 100 ⁇ m, for example, the microparticles have a mean diameter in the range of 20-100 ⁇ M, 20-90 ⁇ M, 30-100 ⁇ M, 30-90 ⁇ M, or 10-90 ⁇ M. It is understood that these ranges refer to the mean diameter of all microparticles in a given population. The diameter of any given individual microparticle could be within a standard deviation above or below the mean diameter.
  • the microparticles further comprise a polyethylene glycol (PEG) moiety, wherein the PEG moiety comprises between 25% to 0% weight percent of the microparticle.
  • PEG polyethylene glycol
  • the populations, preparations and/or formulations of the invention do not require the presence of PEG to exhibit the desired corticosteroid sustained release kinetics and bioavailability profile.
  • the corticosteroid microparticle formulation includes betamethasone and a microparticle made using 50:50 PLGA formulation having a molecular weight in the range of 40 kDa to 70 kDa.
  • the microparticles have a mean diameter in the range of 10-100 ⁇ M.
  • the microparticles have a mean diameter in the range of 20-100 ⁇ M, 20-90 ⁇ M, 30-100 ⁇ M, 30-90 ⁇ M, or 10-90 ⁇ M. It is understood that these ranges refer to the mean diameter of all microparticles in a given population. The diameter of any given individual microparticle could be within a standard deviation above or below the mean diameter.
  • the range of prednisolone load percentage is between 10-40%, for example, between 15-30%.
  • the microparticles further comprise a polyethylene glycol (PEG) moiety, wherein the PEG moiety comprises between 25% to 0% weight percent of the microparticle.
  • PEG polyethylene glycol
  • the populations, preparations and/or formulations of the invention do not require the presence of PEG to exhibit the desired corticosteroid sustained release kinetics and bioavailability profile.
  • the invention provides populations of microparticles including a Class D corticosteroid or a pharmaceutically acceptable salt thereof incorporated in, admixed, encapsulated or otherwise associated with a lactic acid-glycolic acid copolymer matrix, wherein the Class D corticosteroid is between 8% to 20% of the microparticles, for example, between 10% to 20% of the microparticles.
  • the invention also provides controlled or sustained release preparation of a Class D corticosteroid including a lactic acid-glycolic acid copolymer microparticle containing the Class D corticosteroid, wherein the Class D corticosteroid is between 8% to 20%, for example, between 10% to 20% of the microparticles of the lactic acid-glycolic acid copolymer microparticle matrix.
  • the invention provides formulations including (a) controlled- or sustained-release microparticles having a Class D corticosteroid and a lactic acid-glycolic acid copolymer matrix, wherein the Class D corticosteroid is between 8% to 20% of the microparticles, for example, between 10% to 20% of the microparticles, and wherein the lactic acid-glycolic acid copolymer has one of more of the following characteristics: (i) a molecular weight in the range of about 40 to 70 kDa; (ii) an inherent viscosity in the range of 0.35 to 0.5 dL/g; (iii) a lactide:glycolide molar ratio of 60:40 to 45:55; and/or (iv) the lactic acid-glycolic acid copolymer is carboxylic acid endcapped.
  • the copolymer is biodegradable.
  • the lactic acid-glycolic acid copolymer is a poly(lactic-co-glycolic) acid copolymer (PLGA).
  • the lactic acid-glycolic acid copolymer has a molar ratio of lactic acid:glycolic acid from the range of about 60:40 to 45:55.
  • the lactic acid-glycolic acid copolymer has a molar ratio of lactic acid:glycolic acid of 50:50.
  • the Class D corticosteroid is fluticasone propionate, fluticasone, or a commercially available chemical analogue or a pharmaceutically-acceptable salt thereof.
  • total dose of the Class D corticosteroid contained in the microparticles is in a range selected from 1-250 mg, where the Class D corticosteroid is between 8-20% of the microparticle (i.e., when the corticosteroid is 8% of the microparticle, the microparticle is in the range of 12.5-3125 mgs, when the corticosteroid is 10% of the microparticle, the microparticle is in the range of 10-2500 mgs, when the corticosteroid is 15% of the microparticle, the microparticle is in the range of 6.67-1666.7 mgs, when the corticosteroid is 20% of the microparticle, the microparticle is in the range of 5-1250 mgs, and so on for all values between 10-20% load dose).
  • the total dose of corticosteroid is in the range of 1-225 mg, 1-200 mg, 1-175 mg, 1-150 mg, 1-120 mg, 1-100 mg, 1-75 mg, 1-60 mg, 1-55 mg, 1-50 mg, 1-45 mg, 1-40 mg, 1-35 mg, 1-30 mg, 1-25 mg, 1-20 mg, 1-15 mg, 1-10 mg, 2-225 mg, 2-200 mg, 2-175 mg, 2-150 mg, 2-120 mg, 2-100 mg, 2-75 mg, 2-60 mg, 2-55 mg, 2-50 mg, 2-45 mg, 2-40 mg, 2-35 mg, 2-30 mg, 2-25 mg, 2-20 mg, 2-15 mg, 2-10 mg, 3-225 mg, 3-200 mg, 3-175 mg, 3-150 mg, 3-120 mg, 3-100 mg, 3-75 mg, 3-60 mg, 3-55 mg, 3-50 mg, 3-45 mg, 3-40 mg, 3-35 mg, 3-30 mg, 3-25 mg, 3-20 mg, 3-15 mg, 3-10 mg, 4-225 mg, 4-200 mg, 4-175 mg,
  • the microparticles have a mean diameter of between 10 ⁇ m to 100 ⁇ m, for example, the microparticles have a mean diameter in the range of 20-100 ⁇ M, 20-90 ⁇ M, 30-100 ⁇ M, 30-90 ⁇ M, or 10-90 ⁇ M. It is understood that these ranges refer to the mean diameter of all microparticles in a given population. The diameter of any given individual microparticle could be within a standard deviation above or below the mean diameter.
  • the microparticles further comprise a polyethylene glycol (PEG) moiety, wherein the PEG moiety comprises between 25% to 0% weight percent of the microparticle.
  • PEG polyethylene glycol
  • the populations, preparations and/or formulations of the invention do not require the presence of PEG to exhibit the desired corticosteroid sustained release kinetics and bioavailability profile.
  • the corticosteroid microparticle formulation includes fluticasone propionate or fluticasone, and a microparticle made using 50:50 PLGA formulation having a molecular weight in the range of 40 kDa to 70 kDa.
  • the microparticles have a mean diameter in the range of 10-100 ⁇ M.
  • the microparticles have a mean diameter in the range of 20-100 ⁇ M, 20-90 ⁇ M, 30-100 ⁇ M, 30-90 ⁇ M, or 10-90 ⁇ M. It is understood that these ranges refer to the mean diameter of all microparticles in a given population. The diameter of any given individual microparticle could be within a standard deviation above or below the mean diameter.
  • the range of prednisolone load percentage is between 10-20%.
  • the microparticles further comprise a polyethylene glycol (PEG) moiety, wherein the PEG moiety comprises between 25% to 0% weight percent of the microparticle.
  • PEG polyethylene glycol
  • the populations, preparations and/or formulations of the invention do not require the presence of PEG to exhibit the desired corticosteroid sustained release kinetics and bioavailability profile.
  • corticosteroid microparticle formulations have been selected because the combination of class of corticosteroid, type of microparticle, molecular weight of polymers used to create the microparticles, lactide:glycolide molar ratio, and/or load percentage of the corticosteroid exhibit the desired release kinetics. These embodiments also exhibit the desired release kinetics with minimal prolonged HPA axis suppression.
  • the invention provides methods of treating pain or inflammation in a patient comprising administering to said patient a therapeutically effective amount of a population of microparticles selected from the following populations: (i) a population of microparticles comprising a Class B corticosteroid or a pharmaceutically acceptable salt thereof incorporated in a lactic acid-glycolic acid copolymer matrix, wherein the Class B corticosteroid comprises between 22% to 28% of the microparticles; (ii) a population of microparticles comprising a Class A corticosteroid or a pharmaceutically acceptable salt thereof incorporated in a lactic acid-glycolic acid copolymer matrix, wherein the Class A corticosteroid comprises between 15% to 30% of the microparticles; (iii) a population of microparticles comprising a Class C corticosteroid or a pharmaceutically acceptable salt thereof incorporated in a lactic acid-glycolic acid copolymer matrix, wherein the Class C corticosteroid comprises between 15% to
  • the population of microparticles releases the corticosteroid for at least 14 days at a rate that does not adversely suppress the hypothalamic-pituitary-adrenal axis (HPA axis). In some embodiments, the population of microparticles releases the corticosteroid in a controlled or sustained release manner such that the levels of cortisol suppression are at or below 35% by day 14 post-administration, for example post-administration. In some embodiments, the population of microparticles releases the corticosteroid in a controlled or sustained release manner such that the levels of cortisol suppression are negligible and/or undetectable by 14 post-administration. In some embodiments, the population of microparticles releases the corticosteroid in a controlled or sustained release manner such that the levels of cortisol suppression are negligible at any time post-administration.
  • HPA axis hypothalamic-pituitary-adrenal axis
  • the invention provides methods of treating pain or inflammation in a patient comprising administering to said patient a therapeutically effective amount of a controlled or sustained release preparation selected from the following preparations: (i) a controlled or sustained release preparation of a Class B corticosteroid comprising a lactic acid-glycolic acid copolymer microparticle containing the Class B corticosteroid, wherein the Class B corticosteroid comprises between 22% to 28% of the lactic acid-glycolic acid copolymer microparticle matrix; (ii) a controlled or sustained release preparation of a Class A corticosteroid comprising a lactic acid-glycolic acid copolymer microparticle containing the Class A corticosteroid, wherein the Class A corticosteroid comprises between 15% to 30% of the lactic acid-glycolic acid copolymer microparticle matrix; (iii) a controlled or sustained release preparation of a Class C corticosteroid comprising a lactic acid-glycolic acid copoly
  • the controlled or sustained release preparation releases the corticosteroid for at least 14 days at a rate that does not adversely suppress the hypothalamic-pituitary-adrenal axis (HPA axis).
  • the controlled or sustained release preparation releases the corticosteroid in a controlled or sustained release manner such that the levels of cortisol suppression are at or below 35% by day 14 post-administration, for example post-administration.
  • the controlled or sustained release preparation releases the corticosteroid in a controlled or sustained release manner such that the levels of cortisol suppression are negligible and/or undetectable by 14 post-administration.
  • the controlled or sustained release preparation releases the corticosteroid in a controlled or sustained release manner such that the levels of cortisol suppression are negligible at any time post-administration.
  • the invention provides methods of treating pain or inflammation in a patient comprising administering to said patient a therapeutically effective amount of a formulation selected from the following preparations: (i) a formulation comprising (a) controlled- or sustained-release microparticles comprising a Class B corticosteroid and a lactic acid-glycolic acid copolymer matrix, wherein the Class B corticosteroid comprises between 22% to 28% of the microparticles and wherein the lactic acid-glycolic acid copolymer has one of more of the following characteristics: (1) a molecular weight in the range of about 40 to 70 kDa; (2) an inherent viscosity in the range of 0.5 to 0.5 dL/g; or (3) a lactide:glycolide molar ratio of 80:20 to 60:40; (ii) a formulation comprising (a) controlled- or sustained-release microparticles comprising a Class A corticosteroid and a lactic acid-glycolic acid copolymer matrix,
  • the formulation releases the corticosteroid for at least 14 days at a rate that does not adversely suppress the hypothalamic-pituitary-adrenal axis (HPA axis).
  • the formulation releases the corticosteroid in a controlled or sustained release manner such that the levels of cortisol suppression are at or below 35% by day 14 post-administration, for example post-administration.
  • the formulation releases the corticosteroid in a controlled or sustained release manner such that the levels of cortisol suppression are negligible and/or undetectable by 14 post-administration.
  • the formulation releases the corticosteroid in a controlled or sustained release manner such that the levels of cortisol suppression are negligible at any time post-administration.
  • the population of microparticles, the controlled or sustained release preparation or formulation is administered as one or more intra-articular injections.
  • the patient has osteoarthritis, rheumatoid arthritis, acute gouty arthritis, and synovitis.
  • the patient has acute bursitis, sub-acute bursitis, acute nonspecific tenosynovitis, or epicondylitis.
  • a method of treating pain and/or inflammation in a joint of a patient includes administering intra-articularly (e.g., by one or more injections) to a patient with joint disease (e.g., osteoarthritis or rheumatoid arthritis) a formulation that contains one or more corticosteroids, such as those formulations described herein.
  • joint disease e.g., osteoarthritis or rheumatoid arthritis
  • Therapeutically effective amounts of the one or more corticosteroids are released for a period of time at a rate that does not suppress (e.g., adversely and/or measurably) the HPA axis.
  • a method of treating pain and/or inflammation in a joint of a patient includes administering intra-articularly (e.g., by one or more injections) a therapeutically effective amount of one or more corticosteroids in a formulation to a patient with joint disease (e.g., osteoarthritis or rheumatoid arthritis).
  • the formulation has a sustained release microparticle formulation that may or may not release detectable levels of corticosteroid for a length of time following administration and that releases a detectable amount of corticosteroid(s) following administration, where the rate of corticosteroid release from the sustained release microparticle formulation does not adversely suppress the HPA axis.
  • corticosteroid released from the sustained release microparticle formulation will not measurably suppress the HPA axis.
  • the formulation comprises a population of biodegradable polymer microparticles that contain the corticosteroids.
  • the corticosteroids are 2% to 75% (w/w) of the microparticles, preferably about 5% to 50% (w/w) of the microparticles, and more preferably 5% to 40% or 10% to 30% (w/w) of the microparticles.
  • the microparticles have a mass mean diameter of between 10 ⁇ m to 100 ⁇ m.
  • the microparticles are formed from a hydrogel, hyaluronic acid, PLA or PLGA.
  • the microparticles are formed from PLGA with a lactide to glycolide co-polymer ratio of about 45:55 to about 80:20.
  • the corticosteroid is betamethasone, dexamethasone, triamcinolone acetonide, triamcinolone hexacetonide, prednisolone, methylprednisolone, budesonide, mometasone, ciclesonide, fluticasone, salts thereof, esters thereof or combinations thereof.
  • a composition in yet another aspect, includes a population of biodegradable polymer microparticles that contain corticosteroid(s).
  • the corticosteroid is betamethasone, dexamethasone, triamcinolone acetonide, triamcinolone hexacetonide, prednisolone, methylprednisolone, budesonide, mometasone, ciclesonide, fluticasone, salts thereof, esters thereof or combinations thereof.
  • a therapeutically effective amount of corticosteroid(s) is released for a period of time at a rate that does not suppress the HPA axis.
  • the corticosteroid(s) released will not adversely suppress the HPA axis.
  • the corticosteroid(s) released will not measurably suppress the HPA axis.
  • a composition in yet a further aspect, includes a population of biodegradable polymer microparticles that contain corticosteroid(s).
  • the corticosteroid is betamethasone, dexamethasone, triamcinolone acetonide, triamcinolone hexacetonide, prednisolone, methylprednisolone, budesonide, mometasone, ciclesonide, fluticasone, salts thereof, esters thereof or combinations thereof.
  • composition When the composition is administered intra-articularly (e.g., by one or more injections), therapeutically effective amounts of corticosteroid(s) are released following administration from a first component for a first length of time and from a sustained release component for a second length of time. Furthermore, the rate of corticosteroid(s) released from the sustained release component does not suppress the HPA axis. In some embodiments, the corticosteroid(s) released from the sustained release component during the second length of time will not adversely suppress the HPA axis. In some embodiments, the corticosteroid(s) released from the sustained release component during the second length of time will not measurably suppress the HPA axis.
  • the first component comprises a corticosteroid containing solution or suspension. In some embodiments, the first component contains a corticosteroid that is different from that of the sustained release component. In other embodiments, the same corticosteroid is used in both the first and sustained release components.
  • the corticosteroids are 2% to 75% (w/w) of the microparticles, preferably about 5% to 50% (w/w) of the microparticles, and more preferably 5% to 40% (w/w) of the microparticles.
  • the microparticles have a mass mean diameter of between 10 ⁇ m to 100 ⁇ m.
  • the microparticles are formed from a hydrogel, hyaluronic acid, PLA or PLGA.
  • the microparticles are formed from PLGA with a lactide to glycolide co-polymer ratio of about 45:55 to about 80:20.
  • the compositions further comprise a corticosteroid containing solution or suspension.
  • the corticosteroid containing solution or suspension contains a corticosteroid that is different from that found in the microparticles.
  • the invention also provides methods of slowing, arresting or reversing progressive structural tissue damage associated with chronic inflammatory disease in a patient comprising administering to said patient a therapeutically effective amount of a population of microparticles selected from the following populations: (i) a population of microparticles comprising a Class B corticosteroid or a pharmaceutically acceptable salt thereof incorporated in a lactic acid-glycolic acid copolymer matrix, wherein the Class B corticosteroid comprises between 22% to 28% of the microparticles; (ii) a population of microparticles comprising a Class A corticosteroid or a pharmaceutically acceptable salt thereof incorporated in a lactic acid-glycolic acid copolymer matrix, wherein the Class A corticosteroid comprises between 15% to 30% of the microparticles; (iii) a population of microparticles comprising a Class C corticosteroid or a pharmaceutically acceptable salt thereof incorporated in a lactic acid-glycolic acid copoly
  • the invention also provides methods of slowing, arresting or reversing progressive structural tissue damage associated with chronic inflammatory disease in a patient comprising administering to said patient a therapeutically effective amount of a controlled or sustained release preparation selected from the following preparations: (i) a controlled or sustained release preparation of a Class B corticosteroid comprising a lactic acid-glycolic acid copolymer microparticle containing the Class B corticosteroid, wherein the Class B corticosteroid comprises between 22% to 28% of the lactic acid-glycolic acid copolymer microparticle matrix; (ii) a controlled or sustained release preparation of a Class A corticosteroid comprising a lactic acid-glycolic acid copolymer microparticle containing the Class A corticosteroid, wherein the Class A corticosteroid comprises between 15% to 30% of the lactic acid-glycolic acid copolymer microparticle matrix; (iii) a controlled or sustained release preparation of a Class C corticoste
  • the invention also provides methods of slowing, arresting or reversing progressive structural tissue damage associated with chronic inflammatory disease in a patient comprising administering to said patient a therapeutically effective amount of a formulation selected from the following preparations: (i) a formulation comprising (a) controlled- or sustained-release microparticles comprising a Class B corticosteroid and a lactic acid-glycolic acid copolymer matrix, wherein the Class B corticosteroid comprises between 22% to 28% of the microparticles and wherein the lactic acid-glycolic acid copolymer has one of more of the following characteristics: (1) a molecular weight in the range of about 40 to 70 kDa; (2) an inherent viscosity in the range of 0.3 to 0.5 dL/g; or (3) a lactide:glycolide molar ratio of 80:20 to 60:40; (ii) a formulation comprising (a) controlled- or sustained-release microparticles comprising a Class A corticosteroid and
  • the population of microparticles, the controlled or sustained release preparation or formulation is administered as one or more intra-articular injections.
  • the patient has osteoarthritis, rheumatoid arthritis, acute gouty arthritis, and synovitis.
  • the patient has acute bursitis, sub-acute bursitis, acute nonspecific tenosynovitis, or epicondylitis.
  • the invention also provides methods to slow, arrest, reverse or otherwise inhibit progressive structural tissue damage associated with chronic inflammatory disease, for example, damage to cartilage associated with osteoarthritis.
  • the method includes the administration to a patient, for example local administration, of a therapeutically effective amount of one or more corticosteroids in a formulation, wherein the formulation releases the corticosteroid(s) for at least 14 days at a rate that does not adversely suppress the hypothalamic-pituitary-adrenal axis (HPA axis).
  • HPA axis hypothalamic-pituitary-adrenal axis
  • the methods to assess the effect of corticosteroid formulations on disease progression include controlled clinical studies that assess clinical end points and/or employ imaging technologies such as, for example Magnetic Resonance Imaging (MRI), to determine effects on the structure in chronically inflamed tissues, for example the effects on cartilage volume and other articular and peri-articular structures in osteoarthritis and rheumatoid arthritis.
  • imaging technologies such as, for example Magnetic Resonance Imaging (MRI), to determine effects on the structure in chronically inflamed tissues, for example the effects on cartilage volume and other articular and peri-articular structures in osteoarthritis and rheumatoid arthritis.
  • MRI Magnetic Resonance Imaging
  • corticosteroid microparticle formulations appear to exhibit little to no negative effects, e.g., structural tissue damage, and from preliminary data and studies described in the Examples below, these corticosteroid microparticle formulations appear to have a positive effect, e.g., slowing, arresting or reversing structural tissue damage.
  • the invention also provides methods of treating pain and/or inflammation of a patient by administering to the patient a therapeutically effective amount of one or more corticosteroids in a formulation, wherein the formulation releases the corticosteroid(s) for at least 14 days at a rate that does not adversely suppress the hypothalamic-pituitary-adrenal axis (HPA axis).
  • HPA axis hypothalamic-pituitary-adrenal axis
  • the invention also provides methods of manufacturing the corticosteroid microparticle formulations.
  • the microparticle formulations provided herein can be manufactured using any of a variety of suitable methods.
  • the microparticles are manufactured as described in the Examples provided below.
  • the microparticles are manufactured as described in U.S. Pat. No. 7,261,529 and U.S. Pat. No. 7,758,778, the contents of each of which are hereby incorporated by reference in their entirety.
  • the microparticles are manufactured using a solvent evaporation process wherein the Class B corticosteroid is dispersed in a lactic acid-glycolic acid copolymer organic solution and the mixture is treated to remove the solvent from the mixture, thereby producing microparticles.
  • the solvent evaporation process utilizes a spray drying or fluid bed apparatus to remove the solvent and produce microparticles.
  • the solvent evaporation process utilizes a spinning disk.
  • the spinning disk is the spinning disk as described in U.S. Pat. No. 7,261,529 and U.S. Pat. No. 7,758,778.
  • the microparticles are manufactured using a solid in oil in water emulsion process wherein TCA is dispersed in a lactic acid-glycolic acid copolymer organic solution and added to an aqueous solvent to produce microparticles.
  • the microparticles are manufactured as described in the Examples provided below.
  • the microparticles are manufactured as described in PCT Publication No. WO 95/13799, the contents of which are hereby incorporated by reference in their entirety.
  • the microparticles are manufactured using a solid in oil in water emulsion process wherein the Class A corticosteroid, Class C corticosteroid and/or Class D corticosteroid is dispersed in a lactic acid-glycolic acid copolymer organic solution and added to an aqueous solvent to produce microparticles.
  • the invention also provides long-term sustained or controlled release formulations that include a corticosteroid incorporated or otherwise associated with a lactic acid-glycolic acid copolymer microparticle matrix, wherein the microparticle releases the corticosteroid for a period of greater than 45 days, greater than 60 days, greater than 75 days or for at least 90 days.
  • the long-term formulation is a “Ninety-Day Formulation” in which the corticosteroid is released from the microparticle for a period of at least 90 days.
  • the long-term controlled or sustained release preparation includes a Class B corticosteroid that is incorporated or otherwise associated with a lactic acid-glycolic acid copolymer microparticle containing the Class B corticosteroid, wherein the Class B corticosteroid comprises between 5% to 15%, for example, between 6% and 15%, between 7% and 15%, between 8% and 15%, between 9% and 15%, between 10% and 15%, between 6% and 14%, between 7% and 14%, between 8% and 14%, between 9% and 14%, between 10% and 14%, between 6% and 13%, between 7% and 13%, between 8% and 13%, between 9% and 13%, between 10% and 13%, between 6% and 12%, between 7% and 12%, between 8% and 12%, between 9% and 12%, between 10% and 12%, between 6% and 11%, between 7% and 11%, between 8% and 11%, between
  • the copolymer is biodegradable.
  • the lactic acid-glycolic acid copolymer is a poly(lactic-co-glycolic) acid copolymer (PLGA).
  • the Class B corticosteroid is triamcinolone acetonide or a commercially available chemical analogue or a pharmaceutically-acceptable salt thereof.
  • the microparticles have a mean diameter of between 10 ⁇ m to 100 ⁇ m. In some embodiments, the microparticles have a mean diameter in the range of 20-100 ⁇ M, 20-90 ⁇ M, 30-100 ⁇ M, 30-90 ⁇ M, or 10-90 ⁇ M.
  • the lactic acid-glycolic acid copolymer has a molar ratio of lactic acid:glycolic acid from the range of about 80:20 to 60:40 or from the range of about 80:20 to 50:50. In some embodiments, the lactic acid-glycolic acid copolymer has a molar ratio of lactic acid:glycolic acid of 75:25.
  • the microparticles further include a polyethylene glycol (PEG) moiety, wherein the PEG moiety is between 25% to 0% weight percent of the microparticle.
  • PEG polyethylene glycol
  • the populations, preparations and/or formulations of the invention do not require the presence of PEG to exhibit the desired corticosteroid sustained release kinetics and bioavailability profile.
  • the Class B corticosteroid is released for at least 90 days.
  • the lactic acid-glycolic acid copolymer includes an ester endcap.
  • the formulation includes long-term controlled- or sustained-release microparticles having a Class B corticosteroid and a lactic acid-glycolic acid copolymer matrix, wherein the lactic acid-glycolic acid copolymer microparticles release the Class B corticosteroid for a period of at least 75 days, wherein the lactic acid-glycolic acid copolymer microparticles include a mixture of lactic acid-glycolic acid copolymers, wherein the Class B corticosteroid comprises between 5% to 15% of the microparticles, for example, between 6% and 15%, between 7% and 15%, between 8% and 15%, between 9% and 15%, between 10% and 15%, between 6% and 14%, between 7% and 14%, between 8% and 14%, between 9% and 14%, between 10% and 14%, between 6% and 13%, between 7% and 13%, between 8% and
  • the copolymer is biodegradable.
  • the lactic acid-glycolic acid copolymer is a poly(lactic-co-glycolic) acid copolymer (PLGA).
  • the Class B corticosteroid is triamcinolone acetonide or a commercially available chemical analogue or a pharmaceutically-acceptable salt thereof.
  • the microparticles have a mean diameter of between 10 ⁇ m to 100 ⁇ m. In some embodiments, the microparticles have a mean diameter in the range of 20-100 ⁇ M, 20-90 ⁇ M, 30-100 ⁇ M, 30-90 ⁇ M, or 10-90 ⁇ M.
  • the first lactic acid-glycolic acid copolymer, the second lactic acid-glycolic acid copolymer or both have a molar ratio of lactic acid:glycolic acid from the range of about 80:20 to 60:40. In some embodiments, the first lactic acid-glycolic acid copolymer, the second lactic acid-glycolic acid copolymer or both have a molar ratio of lactic acid:glycolic acid of 75:25.
  • the microparticles further include a polyethylene glycol (PEG) moiety, wherein the PEG moiety is between 25% to 0% weight percent of the microparticle.
  • PEG polyethylene glycol
  • the Class B corticosteroid is released for at least 90 days.
  • the first lactic acid-glycolic acid copolymer, the second lactic acid-glycolic acid copolymer or both includes an ester endcap.
  • the Class B corticosteroid is triamcinolone acetonide or a commercially available chemical analogue or a pharmaceutically-acceptable salt thereof, and the total dose of corticosteroid contained in the microparticles is in the range of 10-100 mg, where the Class B corticosteroid is between 5%-15% of the microparticle, for example, about 10% of the microparticle (i.e., when the corticosteroid is 10% of the microparticle, the microparticle is in the range of 90-1000 mgs, and so on for all values between 5%-15% load dose, e.g., when the corticosteroid is 15% of the microparticle, the microparticle is in the range of 66.67-666.67 mgs, when the corticosteroid is 13% of the microparticle, the microparticle is in the range of 76.9-692.3 mgs, when the corticosteroid is 7% of the microparticle,
  • the Class B corticosteroid contained in the microparticles is 5%-15% of the microparticle, for example, about 10% of the microparticle and the total dose of corticosteroid is in a range selected from 10-80 mg, 10-70 mg, 10-60 mg, 10-50 mg, 10-40 mg, 10-30 mg, 10-20 mg, 20-90 mg, 20-80 mg, 20-70 mg, 20-60 mg, 20-50 mg, 20-40 mg, 20-30 mg, 30-90 mg, 30-80 mg, 30-70 mg, 30-60 mg, 30-50 mg, 30-40 mg, 40-90 mg, 40-80 mg, 40-70 mg, 40-60 mg, 40-50 mg, 50-90 mg, 50-80 mg, 50-70 mg, 50-60 mg, 60-90 mg, 60-80 mg, 60-70 mg, 70-90 mg, 70-80 mg, and 80-90 mg.
  • the Class B corticosteroid is released for between 14 days and 90 days, preferably at least 45 days, at least 60 days, at least 75 days or greater
  • the invention also provides methods of treating pain or inflammation in a patient by administering to the patient a therapeutically effective amount of a long-term controlled or sustained release preparation, e.g., a Ninety-Day Formulation.
  • a long-term controlled or sustained release preparation e.g., a Ninety-Day Formulation.
  • the invention also provides methods of treating pain or inflammation in a patient by administering to the patient a therapeutically effective amount of a long-term controlled or sustained release preparation, e.g., a Ninety-Day Formulation, wherein the controlled or sustained release preparation or the formulation releases the corticosteroid for at least 14 days at a rate that does not adversely suppress the hypothalamic-pituitary-adrenal axis (HPA axis).
  • a long-term controlled or sustained release preparation e.g., a Ninety-Day Formulation
  • the invention also provides methods of slowing, arresting or reversing progressive structural tissue damage associated with chronic inflammatory disease in a patient by administering to the patient a therapeutically effective amount of a long-term controlled or sustained release preparation, e.g., a Ninety-Day Formulation.
  • a long-term controlled or sustained release preparation e.g., a Ninety-Day Formulation.
  • the invention also provides methods of slowing, arresting or reversing progressive structural tissue damage associated with chronic inflammatory disease in a patient by administering to the patient a therapeutically effective amount of a controlled or sustained release preparation, e.g., a Ninety-Day Formulation, wherein the population of microparticles, the controlled or sustained release preparation or the formulation releases the corticosteroid for at least 14 days at a rate that does not adversely suppress the hypothalamic-pituitary-adrenal axis (HPA axis).
  • a controlled or sustained release preparation e.g., a Ninety-Day Formulation
  • the controlled or sustained release preparation or formulation is administered as one or more injections.
  • the patient has osteoarthritis, rheumatoid arthritis, acute gouty arthritis, and synovitis.
  • the invention also provides methods of manufacturing long-term controlled or sustained released preparations, e.g., Ninety Day Formulations, using a solvent evaporation process wherein the Class B corticosteroid is dispersed in a lactic acid-glycolic acid copolymer organic solution and the mixture is treated to remove the solvent from the mixture, thereby producing microparticles.
  • the solvent evaporation process utilizes a spray drying or fluid bed apparatus to remove the solvent and produce microparticles.
  • the solvent evaporation process utilizes a spinning disk.
  • FIG. 1 is a graph depicting the intra-articular concentrations (top solid line) and the systemic concentrations (bottom solid line) of the glucocorticoid administered according to certain embodiments of the present invention following intra-articular injection.
  • the systemic glucocorticoid concentration associated with clinically significant suppression of the HPA axis is shown as the bottom dotted line.
  • the top dotted line represents the minimal intra-articular concentration required to maintain efficacy (defined as relief of pain and inflammation, or slowing, arrest, or reversal of structural damage to tissues caused by inflammatory diseases.
  • Sustained release of the corticosteroid provides sufficient intra-articular concentrations to maintain efficacy in the longer term, and has transient, clinically insignificant effect on the HPA axis.
  • FIG. 2 is a graph depicting the change in sensitivity over time to suppression of endogenous cortisol production (EC 50 (ng/mL) vs. time) for triamcinolone acetonide 40 mg given by intra-articular administration.
  • FIG. 3 is a graph depicting the change in sensitivity over time to suppression of endogenous cortisol production (EC 50 (ng/mL) vs. time) for various corticosteroids administered as a single, intra-articular injection in the listed dose.
  • FIG. 4 is a graph depicting plasma levels of endogenous cortisol over time, without (Column 1) adjustment for a change in the sensitivity of the HPA axis after intra-articular corticosteroids and with (Column 2) adjustment for a change in the sensitivity of the HPA axis after intra-articular corticosteroids.
  • FIG. 5 is a graph depicting the cumulative percent release of a nominal 25% (w/w) triamcinolone acetonide in PLGA 75:25 microparticles.
  • FIG. 6 is a graph depicting the calculated human dose to achieve transient cortisol suppression and within 14 days achieve less than 35% cortisol suppression using nominal 25% TCA PLGA 75:25 microparticles.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 7 is a graph depicting calculated human dose that does not affect the HPA axis, less than 35% cortisol suppression using nominal 25% TCA PLGA 75:25 microparticles.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 8 is a graph depicting cumulative percent release of a second preparation of nominal 25% triamcinolone acetonide in PLGA 75:25 microparticles using an alternate preparation.
  • FIG. 9 is a graph depicting calculated human dose to achieve transient cortisol suppression and within 14 days achieve less than 35% cortisol suppression using a second preparation of nominal 25% TCA PLGA 75:25 microparticles made by an alternate preparation.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 10 is a graph depicting: calculated human dose that does not affect the HPA axis, less than 35% cortisol suppression using a second preparation of nominal 25% TCA PLGA 75:25 microparticles made by an alternate preparation.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 11 is a graph depicting cumulative percent release of nominal 25% triamcinolone acetonide in 5% PEG 1450/PLGA 75:25 microparticles.
  • FIG. 12 is a graph depicting cumulative percent release of nominal 25% triamcinolone acetonide in 10% PEG 3350/PLGA 75:25 microparticles.
  • FIG. 13 is a graph depicting calculated human dose to achieve transient cortisol suppression and within 14 days achieve less than 35% cortisol suppression using nominal 25% TCA 5% PEG 1450/PLGA 75:25 microparticles.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 14 is a graph depicting calculated human dose to achieve transient cortisol suppression and within 14 days achieve less than 35% cortisol suppression using nominal 25% TCA 10% PEG 3350/PLGA 75:25 microparticles.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 15 is a graph depicting calculated human dose that does not affect the HPA axis, less than 35% cortisol suppression using nominal 25% TCA 5% PEG 1450/PLGA 75:25 microparticles.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 16 is a graph depicting calculated human dose that does not affect the HPA axis, less than 35% cortisol suppression using nominal 25% TCA 10% PEG 3350/PLGA 75:25 microparticles.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 17 is a graph depicting cumulative percent triamcinolone acetonide release of nominal 40%, 25% 20%, 15% and 10% TCA containing PLGA 75:25 microparticles.
  • FIG. 18 is a graph depicting cumulative percent release of nominal 25% TCA PLGA 75:25 (29 kDa) and PLGA 75:25 (54 kDa) containing microparticles.
  • FIG. 19 is a graph depicting cumulative percent release of triamcinolone acetonide in PLGA 50:50 microparticle formulations.
  • FIG. 20 is a graph depicting cumulative percent release of nominal 28.6% triamcinolone acetonide in PLGA 75:25 plus Triblock microparticle formulations.
  • FIG. 21 is a graph depicting calculated human dose to achieve transient cortisol suppression and within 14 days achieve less than 35% cortisol suppression using nominal 28.6% TCA 10% Triblock/PLGA 75:25 microparticles.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 22 is a graph depicting calculated human dose to achieve transient cortisol suppression and within 14 days achieve less than 35% cortisol suppression using nominal 28.6% TCA 20% Triblock/PLGA 75:25 microparticles.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 23 is a graph depicting calculated human dose that does not affect the HPA axis, less than 35% cortisol suppression using nominal 28.6% TCA 10% Triblock/PLGA 75:25 microparticles.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 24 is a graph depicting calculated human dose that does not affect the HPA axis, less than 35% cortisol suppression using nominal 28.6% TCA 20% Triblock/PLGA 75:25 microparticles.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 25 is a graph depicting cumulative percent release of nominal 16.7% triamcinolone acetonide in mixed molecular weight PLGA 75:25 microparticle formulations.
  • FIG. 26 is a graph depicting calculated human dose to achieve transient cortisol suppression and within 14 days achieve less than 35% cortisol suppression using nominal 16.7% TCA mixed molecular weight PLGA 75:25 microparticles.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 27 is a graph depicting calculated human dose that does not affect the HPA axis, less than 35% cortisol suppression using nominal 16.7% TCA mixed molecular weight PLGA 75:25 microparticles.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 28 is a graph depicting cumulative percent release of nominal 28.6% triamcinolone acetonide in various polymer microparticle formulations.
  • FIG. 29 is a graph depicting cumulative percent release of nominal 28.6% Prednisolone in PLGA 50:50 microparticle formulation.
  • FIG. 30 is a graph depicting calculated human dose to achieve transient cortisol suppression and within 14 days achieve less than 35% cortisol suppression using nominal 28.6% PRED PLGA 50:50 microparticles.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 31 is a graph depicting calculated human dose that does not affect the HPA axis, less than 35% cortisol suppression using nominal 28.6% PRED PLGA 50:50 microparticles.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 32 is a graph depicting cumulative percent release of nominal 28.6% Betamethasone PLGA 50:50 microparticle formulation.
  • FIG. 33 is a graph depicting calculated human dose to achieve transient cortisol suppression and within 14 days achieve less than 35% cortisol suppression using nominal 28.6% BETA PLGA 50:50 microparticles.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 34 is a graph depicting calculated human dose that does not affect the HPA axis, less than 35% cortisol suppression using nominal 28.6% BETA PLGA 50:50 microparticles.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 35 is a graph depicting cumulative percent release of nominal 16.7% Fluticasone Propionate PLGA 50:50 microparticle formulation.
  • FIG. 36 is a graph depicting calculated human dose to achieve transient cortisol suppression and within 14 days achieve less than 35% cortisol suppression using nominal 16.7% FLUT PLGA 50:50 microparticles.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 37 is a graph depicting calculated human dose that does not affect the HPA axis, less than 35% cortisol suppression using nominal 16.7% FLUT PLGA 50:50 microparticles.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 38 is a graph depicting cumulative percent release of various Fluticasone Propionate PLGA microparticle formulations.
  • FIG. 39 is a graph depicting cumulative percent release of nominal 28.6% DEX PLGA 50:50 microparticle formulation.
  • FIG. 40 is a graph depicting calculated human dose to achieve transient cortisol suppression and within 14 days achieve less than 35% cortisol suppression and does not affect the HPA axis, less than 35% cortisol suppression using nominal 28.6% DEX PLGA 50:50 microparticles.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIGS. 41A-41D are a series of graphs depicting the mean concentration-time profiles of various doses of TCA IR and FX006 in rat plasma following single intra-articular doses.
  • Concentrations for the first 72 hr are presented in FIGS. 41C and 41D on a larger time scale.
  • FIG. 42 is a graph depicting corticosteroid inhibition and recovery with TCA IR (immediate release) and FX006 (microparticle formulation) in rats.
  • FIG. 43 is a graph depicting the pharmacokinetic/pharmacodynamic (PK/PD) relationship of systemic TCA levels and corticosterone inhibition.
  • FIGS. 44A-44C are a series of graphs depicting the gait analysis scores, an indicator of pain, in rats injected with doses of either immediate release triamcinolone acetonide (TCA IR) or TCA microparticles (FX006) in a model of osteoarthritis.
  • TCA IR immediate release triamcinolone acetonide
  • FX006 at 0.28, 0.12 and 0.03 mg is expressed as TCA concentrations of the dosing formulation (4.67, 2 and 0.5 mg/ml).
  • TCA concentrations of the dosing formulation 4.67 mg/ml
  • FIG. 44B FX006 at 0.28 mg (TCA dose) is expressed as TCA concentrations of the dosing formulation (4.67 mg/ml).
  • TCA IR at 0.03 mg is expressed as triamcinolone at 0.5 mg/ml.
  • FX006 at 0.28, 0.12 and 0.03 mg (TCA doses) is expressed as TCA concentrations of the dosing formulation (4.67, 2 and 0.5 mg/ml).
  • TCA IR at 0.06 and 0.03 mg is expressed as triamcinolone at 1 and 0.5 mg/ml.
  • FIG. 45 is a graph depicting peak pain response following repeated reactivations of arthritis in the right knee. All treatments were administered as a single IA dose in the right knee on Day 0.
  • FIG. 46 is a graph depicting the time course of corticosterone recovery for various groups in the rat study in a model of osteoarthritis.
  • FIGS. 47A-47B are a series of graphs depicting the plasma TCA concentration-time data for various groups in the rat study in a model of osteoarthritis. Only the groups that received injections of TCA microparticles (FX006 groups) are shown in FIG. 47B on an expanded scale.
  • FIG. 48 is a graph depicting the end-of-study histopathology scores for various treatment groups in the rat study in a model of osteoarthritis.
  • FIG. 49 is a graph depicting the cumulative percent release of nominal 10% triamcinolone acetonide in mixed molecular weight PLGA 75:25 microparticle formulation, 15% PLGA emulsion.
  • FIG. 50 is a graph depicting the nominal 10% TCA mixed molecular weight PLGA 75:25 microparticles, 15% PLGA Emulsion and the calculated human dose to achieve transient cortisol suppression and, within 14 days achieve less than 35% cortisol suppression.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 51 is a graph depicting the nominal 10% TCA mixed molecular weight PLGA 75:25 microparticles, 15% PLGA emulsion, and the calculated human dose that does not affect the HPA Axis, less than 35% cortisol suppression.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 52 is a graph depicting the cumulative percent release of nominal 10% triamcinolone acetonide in mixed molecular weight PLGA 75:25 microparticle formulation, 20% PLGA emulsion.
  • FIG. 53 is a graph depicting the nominal 10% TCA mixed molecular weight PLGA 75:25 microparticles, 20% PLGA emulsion, and the calculated human dose to achieve transient cortisol suppression and, within 14 days achieve less than 35% cortisol suppression.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 54 is a graph depicting the nominal 10% TCA mixed molecular weight PLGA 75:25 microparticles, 20% PLGA emulsion, and the calculated human dose that does not affect the HPA axis, less than 35% cortisol suppression.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 55 is a graph depicting the cumulative percent release of nominal 25% budesonide in PLGA 75:25 microparticle formulation.
  • FIG. 56 is a graph depicting the nominal 25% budesonide PLGA 75:25 microparticles, and the calculated human dose to achieve transient cortisol suppression and, within 14 days achieve less than 35% cortisol suppression.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • FIG. 57 is a graph depicting the nominal 25% Budesonide PLGA 75:25 microparticles, and the calculated human dose that does not affect the HPA axis, less than 35% cortisol suppression.
  • the dotted lines represent, from top to bottom of the graph, 50% cortisol inhibition dose, 40% cortisol inhibition dose, 35% cortisol inhibition dose and 5% cortisol inhibition dose.
  • the invention provides compositions and methods for the treatment of pain and inflammation using corticosteroids.
  • the compositions and methods provided herein use one or more corticosteroids in a microparticle formulation.
  • the corticosteroid microparticle formulations provided herein are effective at treating pain and/or inflammation with minimal prolonged suppression of the HPA axis and/or other long term side effects of corticosteroid administration.
  • the corticosteroid microparticle formulations provided herein are effective in slowing, arresting, reversing or otherwise inhibiting structural damage to tissues associated with progressive disease with minimal prolonged suppression of the HPA axis and/or other long term side effects of corticosteroid administration.
  • the corticosteroid microparticle formulations provided herein deliver the corticosteroid in a dose and in a sustained release manner such that the levels of cortisol suppression are at or below 35% by day 14 post-injection.
  • the corticosteroid microparticle formulations provided herein deliver the corticosteroid in a dose and in a controlled or sustained release manner such that the levels of cortisol suppression are negligible and/or undetectable by 14 post-injection.
  • the corticosteroid microparticle formulations in these embodiments are effective in the absence of any significant HPA axis suppression.
  • Administration of the corticosteroid microparticle formulations provided herein can result in an initial “burst” of HPA axis suppression, for example, within the first few days, within the first two days and/or within the first 24 hours post-injection, but by day 14 post-injection, suppression of the HPA axis is less than 35%.
  • corticosteroids are known to be useful for the symptomatic treatment of inflammation and pain.
  • synovitis may be associated with the structural damage, for example, the deterioration of cartilage and other peri-articular associated with the progression of osteoarthritis and rheumatoid arthritis.
  • a structural damage for example, the deterioration of cartilage and other peri-articular associated with the progression of osteoarthritis and rheumatoid arthritis.
  • Brandt K D Doherty M, Lohmander L S, eds. Osteoarthritis. Second ed.
  • the administration of corticosteroids can have a number of unwanted side effects.
  • the HPA axis the interdependent feedback mechanism between the hypothalamus, the pituitary gland and the adrenal cortex, may be suppressed by the administration of corticosteroids, leading to a variety of unwanted side effects.
  • the extent of HPA axis suppression, and related inhibition of endogenous cortisol production, has been attributed to the potency of the corticosteroid, the dose, systemic concentration, protein binding, rate of elimination (Meibohm et al. “Mechanism-based PK/PD model for the lymphocytopenia induced by endogenous and exogenous corticosteroids.” Int J Clin Pharmacol Ther.
  • HPA axis hypothalamic-pituitary-adrenal axis
  • An amount of a corticosteroid that does not “suppress the hypothalamic-pituitary-adrenal axis (HPA axis)” refers to the amount of the sustained release corticosteroid delivered locally to relieve pain due to inflammation, which provides a systemic concentration that will not have a clinically significant effect or “adverse effect” on the HPA axis. Suppression of the HPA axis is generally manifested by a reduction in endogenous glucocorticoid production. It is useful to consider both basal and augmented production of endogenous glucocorticoids. Under ordinary, “unstressed” conditions, glucocorticoid production occurs at a normal, basal level.
  • Endogenous cortisol production may be determined by measuring glucocorticoid concentrations in plasma, saliva, urine or by any other means known in the art. It is known that systemic concentrations of corticosteroids can suppress the HPA axis. For example, on day 3 after an intra-articular injection of 20 mg triamcinolone hexacetonide plasma levels, of approximately 3-4 ng/mL have been observed.
  • administration of the formulation may result in a clinically acceptable HPA suppression, particularly during the initial release period of the therapy.
  • administration of the formulation will not result in any significant level of HPA suppression, including no detectable HPA suppression, particularly during the initial release period of the therapy.
  • additional corticosteroid may be released into the plasma.
  • the plasma levels during this period will generally be less than those during the initial release period, if any corticosteroid release occurs, and will not be associated with HPA axis suppression.
  • the adverse events associated with exogenous corticosteroid administration e.g., hyperglycemia, hypertension, altered mood, etc. will generally not be observed.
  • the number of clinical adverse events during this period will not substantially exceed the number achieved by an immediate release formulation alone or by KENALOGTM or its bioequivalent and will, preferably, be fewer than during the prior, initial release period of the therapy, if any corticosteroid release occurs.
  • the formulation can be considered as avoiding clinically significant (or adverse) suppression of the HPA axis where the endogenous cortisol level is substantially the same in the steady state between a patient population receiving a therapeutically beneficial amount of an immediate release formulation and those receiving a therapeutically beneficial amount of a sustained release formulation.
  • Such a formulation would be deemed to have no clinically significant effect on the HPA axis.
  • a small but measurable reduction in steady-state glucocorticoid production can result from the formulation during the sustained release period of the therapy with adequate preservation of the augmented, stress response needed during infection or trauma can be deemed a clinically insignificant suppression of the HPA axis.
  • Endogenous glucocorticoid production may be assessed by administering various doses of adrenocorticotropin hormone or by other tests known to those skilled in the art.
  • Embodiments of the current invention provide for controlling the release of corticosteroid, as may be desired, to achieve either no measurable effect on endogenous glucocorticoid production or a target, or a measurable effect that is, however, without adverse clinical consequence.
  • intra-articular doses of corticosteroids that suppress cortisol production by 20-35%, and sometimes more provide very useful sustained anti-inflammatory and analgesic activity.
  • HPA axis suppression “Recovery of the hypothalamic-pituitary-adrenal (HPA) axis in patients with rheumatic diseases receiving low-dose prednisolone.” Am. J. Med. 95 (1993): 258-264). Therefore, up to approximately 40% suppression will be clinically well tolerated and very unlikely to be associated with importantly adverse clinical events such as hypoadrenalism or soft-tissue or bony or metabolic changes indicative of long-term glucocorticoid excess.
  • HPA hypothalamic-pituitary-adrenal
  • Patient refers to a human diagnosed with a disease or condition that can be treated in accordance to the inventions described herein. In some embodiments it is contemplated that the formulations described herein may also be used in horses.
  • Delivery refers to any means used to place the drug into a patient. Such means may include without limitation, placing matrices into a patient that release the drug into a target area.
  • matrices may be delivered by a wide variety of methods, e.g., injection by a syringe, placement into a drill site, catheter or canula assembly, or forceful injection by a gun type apparatus or by placement into a surgical site in a patient during surgery.
  • treatment and “treating” a patient refer to reducing, alleviating, stopping, blocking, or preventing the symptoms of pain and/or inflammation in a patient.
  • treatment includes partial alleviation of symptoms as well as complete alleviation of the symptoms for a time period. The time period can be hours, days, months, or even years.
  • an “effective” amount or a “therapeutically effective amount” of a drug or pharmacologically active agent is meant a nontoxic but sufficient amount of the drug or agent to provide the desired effect, e.g., analgesia.
  • An appropriate “effective” amount in any individual case may be determined by one of ordinary skill in the art using routine experimentation.
  • Site of a patient's pain refers to any area within a body causing pain, e.g., a knee joint with osteoarthritis, nerve root causing sciatic pain, nerve fibers growing into annular tears in discs causing back pain, temporomandibular joint (TMJ) pain, for example TMJ pain associated with temporomandibular joint disorder (TMD) or pain radiating from epidural or perineural spaces.
  • TMJ temporomandibular joint
  • TMD temporomandibular joint disorder
  • the pain perceived by the patient may result from inflammatory responses, mechanical stimuli, chemical stimuli, thermal stimuli, as well as allodynia.
  • the site of a patient's pain can comprise one or multiple sites in the spine, such as between the cervical, thoracic, or lumbar vertebrae, or can comprise one or multiple sites located within the immediate area of inflamed or injured joints such as the shoulder, hip, or other joints.
  • a “biocompatible” material refers to a material that is not toxic to the human body, it is not carcinogenic and it should induce limited or no inflammation in body tissues.
  • a “biodegradable” material refers to a material that is degraded by bodily processes (e.g., enzymatic) to products readily disposable by the body or absorbed into body tissue. The biodegraded products should also be biocompatible with the body.
  • such polymers may be used to fabricate, without limitation: microparticles, micro-spheres, matrices, microparticle matrices, micro-sphere matrices, capsules, hydrogels, rods, wafers, pills, liposomes, fibers, pellets, or other appropriate pharmaceutical delivery compositions that a physician can administer into the joint.
  • the biodegradable polymers degrade into non-toxic residues that the body easily removes or break down or dissolve slowly and are cleared from the body intact.
  • the polymers may be cured ex-vivo forming a solid matrix that incorporates the drug for controlled release to an inflammatory region.
  • Suitable biodegradable polymers may include, without limitation natural or synthetic biocompatible biodegradable material.
  • Natural polymers include, but are not limited to, proteins such as albumin, collagen, gelatin synthetic poly(aminoacids), and prolamines; glycosaminoglycans, such as hyaluronic acid and heparin; polysaccharides, such as alginates, chitosan, starch, and dextrans; and other naturally occurring or chemically modified biodegradable polymers.
  • Synthetic biocompatible biodegradable materials include, but are not limited to, poly(lactide-co-glycolide) (PLGA), polylactide (PLA), polyglycolide (PG), polyhydroxybutyric acid, poly(trimethylene carbonate), polycaprolactone (PCL), polyvalerolactone, poly(alpha-hydroxy acids), poly(lactones), poly(amino-acids), poly(anhydrides), polyketals poly(arylates), poly(orthoesters), polyurethanes, polythioesters, poly(orthocarbonates), poly(phosphoesters), poly(ester-co-amide), poly(lactide-co-urethane, polyethylene glycol (PEG), polyvinyl alcohol (PVA), PVA-g-PLGA, PEGT-PBT copolymer (polyactive), methacrylates, poly(N-isopropylacrylamide), PEO-PPO-PEO (pluronics), PEO-PPO-PAA cop
  • the biocompatible biodegradable material can include a combination of biocompatible biodegradable materials.
  • the biocompatible biodegradable material can be a triblock, or other multi-block, formation where a combination of biocompatible biodegradable polymers are joined together.
  • the triblock can be PLGA-PEG-PLGA.
  • a corticosteroid microparticle formulation can occur, for example, by injection into the intra-articular space, peri-articular space, soft tissues, lesions, epidural space, perineural space, or the foramenal space at or near the site of a patient's pain and/or structural tissue damage.
  • Local injection of the formulations described herein into articular or periarticular spaces may be useful in the treatment of, for example, juvenile rheumatoid arthritis, sciatica and other forms of radicular pain (e.g., arm, neck, lumbar, thorax), psoriatic arthritis, acute gouty arthritis, Morton's neuroma, acute and subacute bursitis, acute and subacute nonspecific tenosynovitis and epicondylitis, acute rheumatic carditis and ankylosing spondylitis.
  • radicular pain e.g., arm, neck, lumbar, thorax
  • psoriatic arthritis e.g., acute gouty arthritis
  • Morton's neuroma e.g., acute and subacute bursitis, acute and subacute nonspecific tenosynovitis and epicondylitis
  • Injection of the microparticles described herein into soft tissues or lesions may be useful in the treatment of, for example, alopecia greata, discoid lupus, erythematosus; keloids, localized hypertrophic, infiltrated inflammatory lesions of granuloma annulare, lichen planus, lichen simplex chronicus (neurodermatitis), psoriasis and psoriatic plaques; necrobiosis lipoidica diabeticorum, and psoriatic arthritis.
  • Injection of the microparticles described herein into epidural spaces may be useful in the treatment of, for example, neurogenic claudication.
  • Intramuscular or other soft tissues or lesions injections may also be useful in providing systemic exposures that are effective in the control of incapacitating allergic conditions (including but not limited to asthma, atopic dermatitis, contact dermatitis, drug hypersensitivity reactions, seasonal or perennial allergic rhinitis, serum sickness, transfusion reactions), bullous dermatitis herpetiformis, exfoliative dermatitis, mycosis fungoides, pemphigus, severe erythema multiforme (Stevens-Johnson syndrome), Primary or secondary adrenocortical insufficiency in conjunction with mineralocorticoids where applicable; congenital adrenal hyperplasia, hypercalcemia associated with cancer, nonsupportive thyroiditis, exacerbations of regional enteritis and ulcerative colitis, acquired (autoimmune) hemolytic anemia, congenital (erythroid) hypoplastic anemia (Diamond blackfan anemia), pure red cell aplasia, select cases of secondary thrombocytopenia, trichinosis with neurologic
  • the corticosteroid microparticle formulations provided herein are useful in treating, alleviating a symptom of, ameliorating and/or delaying the progression of sciatica. In one embodiment, corticosteroid microparticle formulations provided herein are useful in treating, alleviating a symptom of, ameliorating and/or delaying the progression of temporomandibular joint disorder (TMD).
  • TMD temporomandibular joint disorder
  • the corticosteroid microparticle formulations provided herein are useful in treating, alleviating a symptom of, ameliorating and/or delaying the progression of neurogenic claudication secondary to lumbar spinal stenosis (LSS).
  • LSS implies spinal canal narrowing with possible subsequent neural compression (classified by anatomy or etiology).
  • Neurogenic Claudication (NC) is a hallmark symptom of lumbar stenosis, in which the column of the spinal cord (or the canals that protect the nerve roots) narrows at the lower back. This narrowing can also occur in the spaces between the vertebrae where the nerves leave the spine to travel to other parts of the body.
  • the microparticles of the invention are used to treat, alleviate a symptom of, ameliorate and/or delay the progression patients suffering from NC secondary to LSS.
  • the corticosteroid microparticle formulations can be administered, for example, by epidural steroid injection (ESI).
  • a corticosteroid microparticle formulation e.g., a TCA microparticle formulation
  • a corticosteroid microparticle formulation e.g., a TCA microparticle formulation
  • administration of a corticosteroid microparticle formulation is considered successful if one or more of the symptoms associated with the disease is alleviated, reduced, inhibited or does not progress to a further, i.e., worse, state.
  • Administration of a corticosteroid microparticle formulation is considered successful if the disease, e.g., an arthritic or other inflammatory disease, enters remission or does not progress to a further, i.e., worse, state.
  • Corticosteroids associated with embodiments of the present invention can be any naturally occurring or synthetic steroid hormone. Naturally occurring corticosteroids are secreted by the adrenal cortex or generally the human body.
  • Corticosteroid molecules have the following basic structure:
  • Corticosteroids have been classified into four different groups (A, B, C, and D). (See e.g., Foti et al. “Contact Allergy to Topical Corticosteroids: Update and Review on Cross-Sensitization.” Recent Patents on Inflammation & Allergy Drug Discovery 3 (2009): 33-39; Coopman et al., “Identification of cross-reaction patterns in allergic contact dermatitis to topical corticosteroids.” Br J Dermatol 121 (1989): 27-34). Class A corticosteroids are hydrocortisone types with no modification of the D ring or C20-C21 or short chain esters on C20-C21.
  • Class A corticosteroids include prednisolone, hydrocortisone and methylprednisolone and their ester acetate, sodium phosphate and succinate, cortisone, prednisone, and tixocortol pivalate.
  • Class B corticosteroids are triamcinolone acetonide (TCA) types with cis/ketalic or diolic modifications on C16-C17.
  • Main examples of Class B corticosteroids include triamcinolone acetonide (TCA), fluocinolone acetonide, amcinonide, desonide, fluocinonide, halcinonide, budesonide, and flunisolide.
  • Class C corticosteroids are betamethasone types with a —CH3 mutilation on C16, but no esterification on C17-C21.
  • Main examples of Class C corticosteroids include betamethasone, dexamethasone, desoxymethasone, fluocortolone, and halomethasone.
  • Class D corticosteroids are clobetasone or hydrocortisone esterified types with a long chain on C17 and/or C21 and with no methyl group on C16.
  • Class D corticosteroids include fluticasone, clobetasone butyrate, clobetasol propionate, hydrocortisone-17-aceponate, hydrocortisone-17-butyrate, beclomethasone dipropionate, betamethasone-17-valerate, betamethasone dipropionate, methylprednisolone aceponate, and prednicarbate.
  • corticosteroids may include: betamethasone, betamethasone acetate, betamethasone dipropionate, betamethasone 17-valerate, cortivazol, dexamethasone, dexamethasone acetate, dexamethasone sodium phosphate, hydrocortisone, hydrocortisone aceponate, hydrocortisone acetate, hydrocortisone butyrate, hydrocortisone cypionate, hydrocortisone probutate, hydrocortisone sodium phosphate, hydrocortisone sodium succinate, hydrocortisone valerate, methylprednisolone, methylprednisolone aceponate, methylprednisolone acetate, methylprednisolone sodium succinate, prednisolone, prednisolone acetate, prednisolone metasulphobenzoate, prednisolone sodium phosphate, prednisolone, predni
  • Embodiments of the invention include using sustained release corticosteroids delivered to treat pain at dosages that do not adversely suppress the HPA axis. Such amounts delivered locally to relieve pain due to inflammation, will provide a systemic concentration that does not have a measurable adverse effect on the HPA axis (differences if any are not significant because any such differences are within normal assay variability) or, as desired, may have a measurable but clinically insignificant effect on the HPA axis (basal cortisol is suppressed to some measurable extent but stress responses are adequately preserved). Further embodiments of the invention include doses during a second period of time selected to adjust for a change in sensitivity of the HPA axis to suppression following exposure during a first period of time to the corticosteroid ( FIG. 1 ).
  • Additional embodiments include doses during first and/or the second period of time selected to adjust for corticosteroid-specific (or corticosteroid- and potentially dose-specific) changes in the rate of change of sensitivity of the HPA axis to suppression that begin with initial exposure.
  • the rate of change of the sensitivity of the HPA axis to exogenous corticosteroids is both non-uniform and non-linear ( FIG. 2 ).
  • the rate and pattern of change in such sensitivity varies widely as a function of the particular corticosteroid that is selected ( FIG. 3 ).
  • EC 50 ⁇ final EC 50 ⁇ initial + [EC 50 ⁇ final ⁇ EC 50 ⁇ initial ] ⁇ [1 ⁇ e ( ⁇ time) ]
  • corticosteroids can be administered successfully by intra-articular injection, maximizing the likelihood of observing anti-inflammatory and analgesic responses while minimizing or eliminating adverse events from HPA axis suppression or otherwise excessive tissue exposure, is of profound clinical consequence for improving the treatment of patients with arthritis.
  • Corticosteroid Concentration in Plasma (ng/mL) associated with the Target Levels of Cortisol Inhibition (%) Corticosteroid 5% 10% 20% 35% 50% betamethasone (ng/mL) 0.33 0.70 1.57 3.38 6.27 budesonide (ng/mL) 0.60 1.27 2.85 6.14 11.40 des-ciclesonide (ng/mL) 0.55 1.16 2.61 5.63 10.45 dexamethasone (ng/mL) 0.21 0.44 1.00 2.15 3.99 flunisonide (ng/mL) 0.18 0.38 0.86 1.84 3.42 fluticasone (ng/mL) 0.04 0.08 0.19 0.41 0.76 mometasone (ng/mL) 0.15 0.32 0.71 1.54 2.85 methylprednisolone (ng/mL) 0.68 1.44 3.23 6.96 12.92 prednisolone (ng/mL) 1.64 3.
  • a single component sustained release formulation releases a dose (in mg/day) that suppresses the HPA axis by no more than between 5-40% at steady state as shown in Table 2, more preferably no more than between 10-35% at steady state as shown in Table 2. These doses are therapeutically effective without adverse side effects.
  • a single component sustained release formulation releases a dose (in mg/day) that does not measurably suppress the HPA axis at steady state. These doses are therapeutically effective without adverse side effects.
  • immediate release dose would be as shown in Table 4 and the sustained release dose would be a dose (in mg/day) that suppresses the HPA axis by no more than between 5-40% as shown in Table 2, more preferably no more than between 10-35% as shown in Table 2.
  • sustained release doses described previously will follow immediate release doses as shown in Table 4.
  • microparticles or methods of making biodegradable polymer microparticles are known in the art.
  • Microparticles from any of the biodegradable polymers listed below can be made by, but not limited to, spray drying, solvent evaporation, phase separation, spray drying, fluidized bed coating or combinations thereof.
  • the microparticles are made from a biodegradable polymer that may include, without limitation, natural or synthetic biocompatible biodegradable materials.
  • Natural polymers include, but are not limited to, proteins such as albumin, collagen, gelatin synthetic poly(aminoacids), and prolamines; glycosaminoglycans, such as hyaluronic acid and heparin; polysaccharides, such as alginates, chitosan, starch, and dextrans; and other naturally occurring or chemically modified biodegradable polymers.
  • Synthetic biocompatible biodegradable materials include, but are not limited to the group comprising of, poly(lactide-co-glycolide) (PLGA), polylactide (PLA), polyglycolide (PG), polyhydroxybutyric acid, poly(trimethylene carbonate), polycaprolactone (PCL), polyvalerolactone, poly(alpha-hydroxy acids), poly(lactones), poly(amino-acids), poly(anhydrides), polyketals poly(arylates), poly(orthoesters), poly(orthocarbonates), poly(phosphoesters), poly(ester-co-amide), poly(lactide-co-urethane, polyethylene glycol (PEG), polyvinyl alcohol (PVA), PVA-g-PLGA, PEGT-PBT copolymer(polyactive), polyurethanes, polythioesters, methacrylates, poly(N-isopropylacrylamide), PEO-PPO-PEO (pluronics), PEO-P
  • the microparticles are formed from poly(d,l-lactic-co-glycolic acid) (PLGA), which is commercially available from a number of sources.
  • PLGA poly(d,l-lactic-co-glycolic acid)
  • Biodegradable PLGA copolymers are available in a wide range of molecular weights and ratios of lactic to glycolic acid. If not purchased from a supplier, then the biodegradable PLGA copolymers may be prepared by the procedure set forth in U.S. Pat. No. 4,293,539 (Ludwig, et al.), the disclosure of which is hereby incorporated by reference in its entirety.
  • Ludwig prepares such copolymers by condensation of lactic acid and glycolic acid in the presence of a readily removable polymerization catalyst (e.g., a strong acid ion-exchange resin such as Dowex HCR—W2-H).
  • a readily removable polymerization catalyst e.g., a strong acid ion-exchange resin such as Dowex HCR—W2-H.
  • any suitable method known in the art of making the polymer can be used.
  • a suitable biodegradable polymer is dissolved in an organic solvent.
  • Suitable organic solvents for the polymeric materials include, but are not limited to acetone, halogenated hydrocarbons such as chloroform and methylene chloride, aromatic hydrocarbons such as toluene, halogenated aromatic hydrocarbons such as chlorobenzene, and cyclic ethers such as dioxane.
  • the organic solvent containing a suitable biodegradable polymer is then mixed with a non-solvent such as silicone based solvent. By mixing the miscible non-solvent in the organic solvent, the polymer precipitates out of solution in the form of liquid droplets.
  • the liquid droplets are then mixed with another non-solvent, such as heptane or petroleum ether, to form the hardened microparticles.
  • the microparticles are then collected and dried. Process parameters such as solvent and non-solvent selections, polymer/solvent ratio, temperatures, stirring speed and drying cycles are adjusted to achieve the desired particle size, surface smoothness, and narrow particle size distribution.
  • phase separation In the phase separation or phase inversion procedures entrap dispersed agents in the polymer to prepare microparticles. Phase separation is similar to coacervation of a biodegradable polymer.
  • a nonsolvent such as petroleum ether
  • the polymer is precipitates from the organic solvent to form microparticles.
  • a suitable biodegradable polymer is dissolved in an aqueous miscible organic solvent.
  • Suitable water miscible organic solvents for the polymeric materials include, but are not limited to acetone, as acetone, acetonitrile, and tetrahydrofuran.
  • the water miscible organic solvent containing a suitable biodegradable polymer is then mixed with an aqueous solution containing salt.
  • Suitable salts include, but are not limited to electrolytes such as magnesium chloride, calcium chloride, or magnesium acetate and non-electrolytes such as sucrose.
  • the polymer precipitates from the organic solvent to form microparticles, which are collected and dried. Process parameters such as solvent and salt selection, polymer/solvent ratio, temperatures, stirring speed and drying cycles are adjusted to achieve the desired particle size, surface smoothness, and narrow particle size distribution.
  • the microparticles may be prepared by the process of Ramstack et al., 1995, described in published international patent application WO 95/13799, the disclosure of which is incorporated herein in its entirety.
  • the Ramstack et al. process essentially provides for a first phase, including an active agent and a polymer, and a second phase, that are pumped through a static mixer into a quench liquid to form microparticles containing the active agent.
  • the first and second phases can optionally be substantially immiscible and the second phase is preferably free from solvents for the polymer and the active agent and includes an aqueous solution of an emulsifier.
  • a suitable biodegradable polymer is dissolved in an organic solvent and then sprayed through nozzles into a drying environment provided with sufficient elevated temperature and/or flowing air to effectively extract the solvent.
  • surfactants such as sodium lauryl sulfate can improve the surface smoothness of the microparticles.
  • a suitable biodegradable polymer can be dissolved or dispersed in supercritical fluid, such as carbon dioxide.
  • supercritical fluid such as carbon dioxide.
  • the polymer is either dissolved in a suitable organic solvent, such as methylene chloride, prior to mixing in a suitable supercritical fluid or directly mixed in the supercritical fluid and then sprayed through a nozzle.
  • Process parameters such as spray rate, nozzle diameter, polymer/solvent ratio, and temperatures, are adjusted to achieve the desired particle size, surface smoothness, and narrow particle size distribution.
  • the drug is dissolved in an organic solvent along with the polymer.
  • the solution is then processed, e.g., through a Wurster air suspension coating apparatus to form the final microcapsule product.
  • the microparticles can be prepared in a size distribution range suitable for local infiltration or injection.
  • the diameter and shape of the microparticles can be manipulated to modify the release characteristics.
  • other particle shapes such as, for example, cylindrical shapes, can also modify release rates of a sustained release corticosteroid by virtue of the increased ratio of surface area to mass inherent to such alternative geometrical shapes, relative to a spherical shape.
  • the microparticles have a mass mean diameter ranging between about 0.5 to 500 microns. In a preferred embodiment, the microparticles have a mass mean diameter of between 10 to about 100 microns.
  • Biodegradable polymer microparticles that deliver sustained release corticosteroids may be suspended in suitable aqueous or non-aqueous carriers which may include, but is not limited to water, saline, pharmaceutically acceptable oils, low melting waxes, fats, lipids, liposomes and any other pharmaceutically acceptable substance that is lipophilic, substantially insoluble in water, and is biodegradable and/or eliminatable by natural processes of a patient's body. Oils of plants such as vegetables and seeds are included.
  • oils made from corn, sesame, cannoli, soybean, castor, peanut, olive, arachis, maize, almond, flax, safflower, sunflower, rape, coconut, palm, babassu, and cottonseed oil; waxes such as carnoba wax, beeswax, and tallow; fats such as triglycerides, lipids such as fatty acids and esters, and liposomes such as red cell ghosts and phospholipid layers.
  • preferred loadings of said corticosteroid are from about 5% to about 40% (w/w) of the polymer, preferably about 5% to about 30%, more preferably about 5% to about 28% of the polymer.
  • the pharmacokinetic release profile of the corticosteroid by the biodegradable polymer may be first order, zero order, bi- or multi-phasic, to provide desired treatment of inflammatory related pain.
  • the bio-erosion of the polymer and subsequent release of the corticosteroid may result in a controlled release of a corticosteroid from the polymer matrix. The rate of release at dosages that do not suppress the HPA axis are described above.
  • the release rate of the corticosteroid from a biodegradable polymer matrix can be modulated or stabilized by adding a pharmaceutically acceptable excipient to the formulation.
  • An excipient may include any useful ingredient added to the biodegradable polymer depot that is not a corticosteroid or a biodegradable polymer.
  • compositions may include without limitation lactose, dextrose, sucrose, sorbitol, mannitol, starches, gum acacia, calcium phosphate, alginates, tragacanth, gelatin, calcium silicate, microcrystalline cellulose, PEG, polysorbate 20, polysorbate 80, polyvinylpyrrolidone, cellulose, water, saline, syrup, methyl cellulose, and carboxymethyl cellulose.
  • An excipient for modulating the release rate of a corticosteroid from the biodegradable drug depot may also include without limitation pore formers, pH modifiers, reducing agents, antioxidants, and free radical scavengers.
  • formulations of the invention can be effected by intra-articular injection or other injection using a needle.
  • needles having a gauge of about 14-28 gauge are suitable. It will be appreciated by those skilled in the art that formulations of the present invention may be delivered to a treatment site by other conventional methods, including catheters, infusion pumps, pens devices, injection guns and the like.
  • the microparticle formulation contains a copolymer of DL-lactide (or L-lactide) and glycolide in a 45:55 molar ratio (up to 75:25 molar ratio) with an inherent viscosity ranging from 0.15 to 0.60 dL/g with either an ester or acid end group plus either the corticosteroid betamethasone or triamcinolone acetonide. If betamethasone is used, then the betamethasone is in the form of either betamethasone acetate, betamethasone diproprionate or a combination thereof. The total amount of betamethasone or triamcinolone acetonide incorporated into the microparticle ranges from 10% to 30% (w/w).
  • the microparticles are formulated to mean mass range in size from 10 to 100 microns.
  • the population of microparticles is formulated to be delivered through a 19 gauge or higher needle. Additional excipients may be added such as, but not limited to, carboxymethylcellulose sodium, mannitol, polysorbate-80, sodium phosphate, sodium chloride, polyethylene glycol to achieve isotonicity and promote syringeability. If betamethasone is used, then the betamethasone incorporated into the microparticle population provides an initial release (burst) of about 5-20 mg of drug over a period of 1 to 12 hours, followed by a steady state release of drug at a rate of about 0.1 to 1.0 mg/day over a period of 14 to 90 days.
  • the drug incorporated into the microparticle population provides an initial release (burst) of about 10-40 mg of drug over a period of 1 to 12 hours, followed by a steady state release of drug at a rate of about 0.2 to 1.7 mg/day over a period of 14 to 90 days.
  • the microparticle formulation of Example 1 is further admixed with an immediate release betamethasone or triamcinolone acetonide component, such as a betamethasone or triamcinolone acetonide containing solution.
  • an immediate release betamethasone or triamcinolone acetonide component such as a betamethasone or triamcinolone acetonide containing solution.
  • betamethasone is used, then the betamethasone in the immediate release component is in the form of either betamethasone acetate, betamethasone diproprionate or a combination thereof.
  • the immediate release component provides an initial release of a total of about 5 to 20 mg of betamethasone over the first 1-10 days, while the sustained release component releases betamethasone at a rate of about 0.1 to 1.0 mg/day over the first 14 to 90 days following administration.
  • the immediate release component provides an initial release of a total of 10 to 40 mg of drug over the first 1-10 days, while the sustained release component releases drug at a rate of about 0.2 to 1.7 mg/day over the first 14 to 90 days following administration.
  • a pharmaceutical depot was prepared comprised of the corticosteroid, triamcinolone acetonide (TCA, 9 ⁇ -Fluoro-11 ⁇ ,16 ⁇ ,17 ⁇ ,21-tetrahydroxy-1,4-pregnadiene-3,20-dione 16,17-acetonide; 9 ⁇ -Fluoro-16 ⁇ -hydroxyprednisolone 16 ⁇ ,17 ⁇ -acetonide) incorporated into PLGA microparticles.
  • TCA triamcinolone acetonide
  • PLGA lactide:glycolide molar ratio of 75:25, inherent viscosity of 0.4 dL/g and molecular weight of 54 kDa
  • the dispersion was atomized into micro-droplets by adding the dispersion to the feed well of a rotating disk, rotating at a speed of approximately 3300 rpm inside a temperature controlled chamber maintained at 38-45° C.
  • the solvent was evaporated to produce solid microparticles.
  • the microparticles were collected using a cyclone separator and, subsequently, sieved through a 150 ⁇ m sieve.
  • Particle size of the TCA incorporated microparticles was determined using laser diffraction (Malvern Mastersizer 2000) by dispersing a 250 mg aliquot in water, with the refractive index (RI) for water and PLGA, set at 1.33 and 1.46 respectively. Sonication was maintained as the sample was stirred at 2500 rpm and measurements taken every 15 seconds, with the average of three measurements reported. 10 mg of TCA containing microparticles were added to 10 mL of dimethylsulfoxide (DMSO), mixed until dissolved and an aliquot analyzed by HPLC to determine the microparticle drug load.
  • DMSO dimethylsulfoxide
  • TCA containing microparticles were suspended in 20 mL of phosphate buffered saline (PBS) containing 0.5% sodium dodecyl sulfate (SDS) maintained at 37° C.
  • PBS phosphate buffered saline
  • SDS sodium dodecyl sulfate
  • 0.5 mL of the media was removed at regular intervals, replaced at each interval with an equivalent amount of fresh media to maintain a constant volume, and analyzed by HPLC to determine microparticle in vitro release. Analysis by HPLC was conducted using a C18 (Waters Nova-Pack C-18, 3.9 ⁇ 150 mm) and 35% acetonitrile mobile phase at 1 ml/min flow rate with UV detection at 240 nm. The results are shown in Table 5.
  • the in vitro cumulative release profile is graphed in FIG. 5 .
  • the amount of TCA released per day was calculated based on a human dose, as exemplified in Table 2, that would achieve a transient suppression of endogenous cortisol (greater than 50%) and, within 14 days, achieve cortisol suppression of endogenous cortisol of less than 35% as shown in FIG. 6 .
  • the amount of triamcinolone acetonide released per day was calculated based on a human dose, as exemplified in Table 2 that would not suppress the HPA axis, i.e. endogenous cortisol suppression never exceeding 35% as shown in FIG. 7 .
  • These calculated doses equal 376 mg of microparticles containing 94 mg of TCA and 80 mg of microparticles containing 20 mg of TCA, respectively.
  • polyethylene glycol was added to the PLGA 75:25 polymers while keeping the target amount of triamcinolone acetonide constant.
  • PEG/PLGA blends are known to allow for more complete and faster release of pharmaceutical agents incorporated into microparticles than PLGA alone (Cleek et al. “Microparticles of poly(DL-lactic-coglycolic acid)/poly(ethylene glycol) blends for controlled drug delivery.” J Control Release 48 (1997): 259-268; Morlock, et al.
  • 250 mg of triamcinolone acetonide, 50 mg of polyethylene glycol (PEG 1450) and 700 mg of PLGA (lactide:glycolide molar ratio of 75:25, inherent viscosity of 0.4 dL/g and molecular weight of 54 kDa) were dispersed in 14 grams of dichloromethane.
  • 250 mg of triamcinolone acetonide, 100 mg of polyethylene glycol (PEG 3350) and 650 mg of PLGA (lactide:glycolide molar ratio of 75:25, inherent viscosity of 0.4 dL/g and molecular weight of 54 kDa) were dispersed in 13 grams of dichloromethane.
  • the dispersions were atomized into micro-droplets by adding the dispersion to the feed well of a rotating disk, rotating at a speed of approximately 3300 rpm inside a temperature controlled chamber maintained at 38-45° C.
  • the solvent was evaporated to produce solid microparticles.
  • the microparticles were collected using a cyclone separator and, subsequently, sieved through a 150 ⁇ m sieve.
  • microparticles were analyzed as described above and the data is shown in Table 7.
  • the in vitro cumulative release profile is graphed in FIG. 11 and FIG. 12 .
  • PEG did not seem to enhance the release of the TCA in either formulation, as would be expected.
  • the release rate was slower.
  • the amount of TCA released per day was calculated based on a human dose, as exemplified in Table 2, that would achieve a temporary suppression of endogenous cortisol (greater than 50%) and, within 14 days, achieve cortisol suppression of endogenous cortisol of less than 35% as shown in FIG. 13 and FIG. 14 .
  • These calculated doses equal 296 mg of microparticles containing 74 mg of TCA and 316 mg of microparticles containing 79 mg of TCA, respectively.
  • the amount of triamcinolone acetonide released per day was calculated based on a human dose, as exemplified in Table 2 that would not suppress the HPA axis, i.e. endogenous cortisol suppression never exceeding 35% as shown in FIGS. 15 and 16 .
  • These calculated doses equal 68 mg of microparticles containing 17 mg of TCA and 88 mg of microparticles containing 22 mg of TCA, respectively.
  • TCA containing formulations were tried with PEG and PLGA 75:25 without success.
  • a PLGA microparticle formulation containing 25% TCA and 25% PEG 1450 agglomerated during manufacture and storage.
  • Another PLGA formulation containing 40% TCA and 15% PEG 1450 gave similar results to the microparticles containing 40% TCA and no PEG.
  • Triamcinolone acetonide containing microparticle depots were prepared and analyzed, as described above, with the exception of using 100 mg, 150 mg, 200 mg and 400 mg triamcinolone acetonide and adding to a 5% PLGA dichloromethane solution. The physical characteristics of these formulations are shown in Table 8.
  • the in vitro cumulative release profiles for these four other TCA containing PLGA 75:25 microparticle depots are graphed in FIG. 17 , along with the preferred formulation (25% TCA).
  • the tabulated data and graph show the impact of the percent TCA incorporated in the PLGA microparticles on the in vitro release profile.
  • the 10%, 15% and 20% TCA containing PLGA microparticles exhibit a slower release profile, with a significant less cumulative release over 28 days, less than 20%, 30% and 55% respectively, than the 25% TCA PLGA depot exemplified in Example 4.
  • the 40% TCA containing depot exhibits a faster release profile, with greater than 80% of the triamcinolone released by day 7 with a similar total cumulative release, than the 25% TCA PLGA depot exemplified in Example 4.
  • triamcinolone acetonide was incorporated in PLGA of the same lactide to glycolide molar ratio as cited in Example 4 but of a lower molecular weight.
  • Low molecular weight PLGA is known to allow for more complete and faster release of pharmaceutical agents incorporated into microparticles than their higher molecular weight counterparts.
  • Particle size of the TCA incorporated microparticles was determined using laser diffraction (Malvern Mastersizer 2000) by dispersing a 250 mg aliquot in water, with the refractive index (RI) for water and PLGA, set at 1.33 and 1.46 respectively. Sonication was maintained as the sample was stirred at 2500 rpm and measurements taken every 15 seconds, with the average of three measurements reported. 10 mg of TCA containing microparticles were added to 10 mL of dimethylsulfoxide (DMSO), mixed until dissolved and an aliquot analyzed by HPLC to determine the microparticle drug load.
  • DMSO dimethylsulfoxide
  • TCA containing microparticles were suspended in 20 mL of phosphate buffered saline (PBS) containing 0.5% sodium dodecyl sulfate (SDS) maintained at 37° C.
  • PBS phosphate buffered saline
  • SDS sodium dodecyl sulfate
  • 0.5 mL of the media was removed at regular intervals, replaced at each interval with an equivalent amount of fresh media to maintain a constant volume, and analyzed by HPLC to determine microparticle in vitro release. Analysis by HPLC was conducted using a C18 (Waters Nova-Pack C-18, 3.9 ⁇ 150 mm) and 35% acetonitrile mobile phase at 1 ml/min flow rate with UV detection at 240 nm. The results are shown in Table 9.
  • PLGA equimolar lactide to glycolide ratio
  • PLGA 75:25
  • PLGA 50:50
  • PLGA is known to allow for faster degradation and release of pharmaceutical agents incorporated into microparticles than PLGA's with greater lactide versus glycolide content
  • Anderson et al. “Biodegradation and biocompatibility of PLA and PLGA microspheres.” Advanced Drug Delivery Reviews 28 (1997): 5-24; Bouissou et al., “Poly(lactic-co-glycolicacid) Microspheres.” Polymer in Drug Delivery (2006): Chapter 7).
  • Multiple formulations using PLGA 50:50 with differing amounts of triamcinolone acetonide, with and without PEG, different PLGA molecular weights and different PLGA endcaps were exemplified.
  • Formulations were prepared with 200 mg, 250 mg, 300 mg and 350 mg of triamcinolone acetonide and corresponding amount of PLGA (lactide:glycolide molar ratio of 50:50, inherent viscosity of 0.48 dL/g and molecular weight of 66 kDa) to yield 1000 mg total solids were dispersed into a quantity of dichloromethane to a achieve a 5% PLGA solution.
  • PLGA lactide:glycolide molar ratio of 50:50, inherent viscosity of 0.48 dL/g and molecular weight of 66 kDa
  • 300 mg of triamcinolone acetonide, 100 mg of polyethylene glycol (PEG 3350) and 650 mg of PLGA (lactide:glycolide molar ratio of 50:50, inherent viscosity of 0.48 dL/g and molecular weight of 66 kDa) were dispersed in 14.25 grams of dichloromethane.
  • 300 mg of triamcinolone acetonide and 700 mg of PLGA (lactide:glycolide molar ratio of 50:50, inherent viscosity of 0.18 dL/g and molecular weight of 18 kDa) to yield 1000 mg total solids were dispersed in 14.25 grams of dichloromethane.
  • the dispersions were atomized into micro-droplets by adding the dispersion to the feed well of a rotating disk, rotating at a speed of approximately 3300 rpm inside a temperature controlled chamber maintained at 38-45° C.
  • the solvent was evaporated to produce solid microparticles.
  • the microparticles were collected using a cyclone separator and, subsequently, sieved through a 150 ⁇ m sieve.
  • Particle size of the TCA incorporated microparticles was determined using laser diffraction (Malvern Mastersizer 2000) by dispersing a 250 mg aliquot in water, with the refractive index (RI) for water and PLGA, set at 1.33 and 1.46 respectively. Sonication was maintained as the sample was stirred at 2500 rpm and measurements taken every 15 seconds, with the average of three measurements reported. 10 mg of TCA containing microparticles were added to 10 mL of dimethylsulfoxide (DMSO), mixed until dissolved and an aliquot analyzed by HPLC to determine the microparticle drug load.
  • DMSO dimethylsulfoxide
  • TCA containing microparticles were suspended in 20 mL of phosphate buffered saline (PBS) containing 0.5% sodium dodecyl sulfate (SDS) maintained at 37° C.
  • PBS phosphate buffered saline
  • SDS sodium dodecyl sulfate
  • 0.5 mL of the media was removed at regular intervals, replaced at each interval with an equivalent amount of fresh media to maintain a constant volume, and analyzed by HPLC to determine microparticle in vitro release. Analysis by HPLC was conducted using a C18 (Waters Nova-Pack C-18, 3.9 ⁇ 150 mm) and 35% acetonitrile mobile phase at 1 ml/min flow rate with UV detection at 240 nm. The results are shown in Table 10.
  • TCA PLGA 75:25 formulations As observed with TCA PLGA 75:25 formulations, increasing the amount of TCA increases the rate of release and allows for more TCA to be released before entering the lag phase. Similarly, the addition of PEG has minimal influence on the release rate of TCA, while lower molecular weight PLGA 50:50 decrease the release rate as observed with PLGA 75:25 formulations.
  • the Class B corticosteroid microparticle formulations for example, the TCA microparticle formulations, exhibiting the desired release kinetics have the following characteristics: (i) the corticosteroid is between 22%-28% of the microparticle; and (ii) the polymer is PLGA having a molecular weight in the range of about 40 to 70 kDa, having an inherent viscosity in the range of 0.3 to 0.5 dL/g, and or having a lactide:glycolide molar ratio of 80:20 to 60:40.
  • a pharmaceutical depot was prepared comprised of the corticosteroid, triamcinolone acetonide (TCA, 9 ⁇ -Fluoro-11 ⁇ ,16 ⁇ ,17 ⁇ ,21-tetrahydroxy-1,4-pregnadiene-3,20-dione 16,17-acetonide; 9 ⁇ -Fluoro-16 ⁇ -hydroxyprednisolone 16 ⁇ ,17 ⁇ -acetonide) incorporated into microparticles.
  • TCA triamcinolone acetonide
  • Formulations were prepared by dissolving approximately 1 gram of PLGA in 6.67 mL of dichloromethane (DCM). To the polymer solution, 400 mg of triamcinolone acetonide was added and sonicated. Subsequently, the corticosteroid containing dispersion was poured into 200 mL of 0.3% polyvinyl alcohol (PVA) solution while homogenizing with a Silverson homogenizer using a rotor fixed with a Silverson Square Hole High Shear ScreenTM, set to rotate at approximately 2,000 rpm to form the microparticles.
  • PVA polyvinyl alcohol
  • the beaker was removed, and a glass magnetic stirrer) added to the beaker, which was then placed onto a multi-way magnetic stirrer and stirred for four hours at 300 rpm to evaporate the DCM.
  • the microparticles were then washed with 2 liters of distilled water, sieved through a 100 micron screen. The microparticles were then lyophilized for greater than 96 hours and vacuum packed.
  • Particle size of the TCA incorporated microparticles was determined using laser diffraction (Beckman Coulter LS 230) by dispersing a 50 mg aliquot in water, with the refractive index (RI) for water and PLGA, set at 1.33 and 1.46 respectively. The sample was stirred at the particle size measurement measurements taken and the results reported. Drug load was determined by suspending a nominal 10 mg of microparticles in 8 ml HPLC grade methanol and sonicating for 2 hours. Samples were then centrifuged at 14,000 g for 15 mins before an aliquot of the supernatant was assayed via HPLC as described below.
  • Corticosteroid-loaded microparticle samples nominally 1 g were placed in 22 ml glass vials in 8-20 ml of 0.5% v/v Tween 20 in 100 mM phosphate buffered saline and stored in a 37° C. incubator with magnetic stirring at 130 rpm. Each test sample was prepared and analyzed in duplicate to monitor possible variability. At each time point in the release study, microparticles were allowed to settle, and an aliquot of between 4-16 ml of supernatant were taken, and replaced with an equal volume of fresh 0.5% v/v Tween 20 in 100 mM phosphate buffered saline.
  • Drug load and in vitro release samples were analyzed by HPLC using a Hypersil C18 column (100 mm, i.d. 5 mm, particle size 5 ⁇ m; ThermoFisher) and Beckman HPLC. All samples were run using a sample injection volume of 5 ⁇ m, and column temperature of 40° C. An isocratic mobile phase of 60% methanol and 40% water was used at a flow rate of 1 ml/min, with detection at a wavelength of 254 nm.
  • the PLGA is an ester end capped PLGA (lactide:glycolide molar ratio of 75:25, inherent viscosity of 0.71 dL/g and molecular weight of 114 kDa) with 10% or 20% triblock (TB) polymer (PLGA-PEG-PLGA).
  • Triblock polymer was synthesized using a method described by Zentner et al 2001 (Zentner et al.
  • the amount of TCA released per day was calculated based on a human dose, as exemplified in Table 2, that may achieve a temporary suppression of endogenous cortisol (greater than 50%) and, within 14 days, achieve cortisol suppression of endogenous cortisol of less than 35%.
  • These calculated doses equal 149 mg of microparticles containing 35 mg of TCA and 252 microparticles containing 62 mg of TCA, for the 10% and 20% triblock formulations respectively ( FIG. 21 and FIG. 22 ).
  • the amount of TCA released per day was calculated based on a human dose, as exemplified in Table 2, that would not have an suppress the HPA axis, i.e. endogenous cortisol suppression more than 35%.
  • These calculated doses equal 66 mg of microparticles containing 16 mg of TCA and 47 microparticles containing 12 mg of TCA, for the 10% and 20% triblock formulations respectively ( FIG. 23 and FIG. 24 ).
  • the PLGA polymer In another suitable formulation lasting greater than 30 days and up to 90 days, the PLGA polymer consists of two different molecular weight PLGA 75:25 polymers in a two to one ratio, PLGA 75:25 (lactide:glycolide molar ratio of 75:25, inherent viscosity of 0.27 dL/g and molecular weight of 29 kDa) and ester end capped PLGA 5.5 E (lactide:glycolide molar ratio of 75:25, inherent viscosity of 0.58 dL/g and molecular weight of 86 kDa), respectively.
  • the formulation was processed as described above with the exception that 200 mg of triamcinolone acetonide was used in the formulation instead of 400 mg and similarly analyzed as describe for other formulations. The results are shown in the Table 12.
  • the amount of TCA released per day was calculated based on a human dose, as exemplified in Table 2, which may achieve a temporary suppression of endogenous cortisol (greater than 50%) and, within 14 days, achieve cortisol suppression of endogenous cortisol of less than 35%.
  • This calculated dose equals 317 mg of microparticles containing 46 mg of TCA.
  • the amount of TCA released per day was calculated based on a human dose, as exemplified in Table 2, that would not have an suppress the HPA axis, i.e. endogenous cortisol suppression more than 35%. This calculated dose equals 93 mg of microparticles containing 14 mg of TCA.
  • PLGA depots were formulated in the same manner as described above with different polymers including polycaprolactone (14 kDa), PLGA 50:50 (carboxylic acid end-capped, 0.44 dL/g, MW 56 kDa), PLGA 85:15 (carboxylic acid end-capped, 0.43 dL/g, 56 kDa) and a mixed molecular weight formulation using PLGA 75:25 (carboxylic acid end capped, 0.27 dL/g, MW 29 kDa) and PLGA 75:25 (ester end-capped, 0.57 dL/g, MW 86 kDa) in a two to one ratio.
  • polycaprolactone 14 kDa
  • PLGA 50:50 carboxylic acid end-capped, 0.44 dL/g, MW 56 kDa
  • PLGA 85:15 carboxylic acid end-capped, 0.43 dL/g, 56 kDa
  • the in vitro cumulative percent release of triamcinolone acetonide is shown in FIG. 28 . None of these formulations were suitable for a nominal thirty day or longer duration pharmaceutical depot. Polycaprolactone release all the triamcinolone acetonide prior to 14 days.
  • the PLGA 50:50 microparticles released about 35% of its content by day 12 and then entered a lag phase where no drug was released up to 30 days.
  • the PLGA 85:15 microparticles exhibited similar in vitro release kinetics as the PLGA 50:50, releasing about 30% of its content by day 12 and then entered a lag phase where no drug was released up to 30 days (See FIG. 28 ).
  • a similar phenomenon is seen as shown in Example 4, where the mixed molecular weight PLGA 75:25 unexpectedly exhibits faster initial release of the triamcinolone acetonide than PLGA 50:50.
  • the Class B corticosteroid microparticle formulations for example, the TCA microparticle formulations, exhibiting the desired release kinetics have the following characteristics: (i) the corticosteroid is between 12%-28% of the microparticle; and (ii) the polymer is (1) PLGA having a molecular weight in the range of about 40 to 70 kDa, having an inherent viscosity in the range of 0.3 to 0.5 dL/g, containing 10%-20% Triblock and/or having a lactide:glycolide molar ratio of 80:20 to 60:40 or (2) a mixture of low and high molecular weight PLGAs in a two to one ratio.
  • the corticosteroid is between 12%-28% of the microparticle
  • the polymer is (1) PLGA having a molecular weight in the range of about 40 to 70 kDa, having an inherent viscosity in the range of 0.3 to 0.5 dL/g, containing 10%-20% Triblock and/or having
  • the low molecular weight PLGA has a molecular weight of range of 15-35 kDa and an inherent viscosity range from 0.2 to 0.35 dL/g, and the high molecular weight PLGA has a range of 70-95 kDa and an inherent viscosity range of 0.5 to 0.70 dL/g.
  • a pharmaceutical depot was prepared comprised of the corticosteroid, prednisolone (PRED, 11 ⁇ ,17,21-trihydroxypregna-1,4-diene-3,20-dione) incorporated into microparticles in PLGA 50:50.
  • PRED prednisolone
  • Formulations were prepared by dissolving approximately 1 gram of PLGA 50:50 (lactide:glycolide molar ratio of 50:50, inherent viscosity 0.44 dL/g, MW 56 kDa) in 6.67 mL of dichloromethane (DCM). To the polymer solution, 400 mg of prednisolone was added and sonicated. Subsequently, the corticosteroid containing dispersion was poured into 200 mL of 0.3% polyvinyl alcohol (PVA) solution while homogenizing with a Silverson homogenizer using a rotor fixed with a Silverson Square Hole High Shear ScreenTM, set to spin at 2,000 rpm to form the microparticles.
  • PVA polyvinyl alcohol
  • the beaker was removed, and a glass magnetic stirrer) added to the beaker, which was then placed onto a multi-way magnetic stirrer and stirred for four hours at 300 rpm to evaporate the DCM.
  • the microparticles were then washed with 2 liters of distilled water, sieved through a 100 micron screen. The microparticles were then lyophilized for greater than 96 hours and vacuum packed.
  • Particle size of the PRED incorporated microparticles was determined using laser diffraction (Beckman Coulter LS 230) by dispersing a 50 mg aliquot in water, with the refractive index (RI) for water and PLGA, set at 1.33 and 1.46 respectively. The sample was stirred at the particle size measurement measurements taken and the results reported. Drug load was determined by suspending a nominal 10 mg of microparticles in 8 ml HPLC grade methanol and sonicating for 2 hours. Samples were then centrifuged at 14,000 g for 15 mins before an aliquot of the supernatant was assayed via HPLC as described below.
  • Corticosteroid-loaded microparticle samples nominally 1 g were placed in 22 ml glass vials in 8-20 ml of 0.5% v/v Tween 20 in 100 mM phosphate buffered saline and stored in a 37° C. incubator with magnetic stirring at 130 rpm. Each test sample was prepared and analyzed in duplicate to monitor possible variability. At each time point in the release study, microparticles were allowed to settle, and an aliquot of between 4-16 ml of supernatant were taken, and replaced with an equal volume of fresh 0.5% v/v Tween 20 in 100 mM phosphate buffered saline.
  • Drug load and in vitro release samples were analyzed by HPLC using a Hypersil C18 column (100 mm, i.d. 5 mm, particle size 5 ⁇ m; ThermoFisher) and Beckman HPLC. All samples were run using a sample injection volume of 5 ⁇ m, and column temperature of 40° C. An isocratic mobile phase of 60% methanol and 40% water was used at a flow rate of 1 ml/min, with detection at a wavelength of 254 nm. The analytical results are shown in the Table 13.
  • FIG. 29 In vitro release profile of the prednisolone PLGA microparticles is shown in FIG. 29 .
  • This formulation is suitable for a 30 day formulation or greater.
  • the amount of prednisolone released per day was calculated based on a human dose, as exemplified in Table 2, which may achieve a temporary suppression of endogenous cortisol (greater than 50%) and, within 14 days, achieve cortisol suppression of endogenous cortisol of less than 35% ( FIG. 30 ).
  • the calculated dose equals 699 mg of microparticles containing 133 mg of PRED.
  • the amount of PRED released per day was calculated based on a human dose, as exemplified in Table 2 that would not suppress the HPA axis, i.e. endogenous cortisol suppression of less than 35% ( FIG. 31 ). This calculated dose equals 377 mg of microparticles containing 72 mg of PRED.
  • the Class A corticosteroid microparticle formulations for example, the prednisolone microparticle formulations, exhibiting the desired release kinetics have the following characteristics: (i) the corticosteroid is between 10%-40% of the microparticle, for example, between 15%-30% of the microparticle; and (ii) the polymer is PLGA having a molecular weight in the range of about 45 to 75 kDa, having an inherent viscosity in the range of 0.35 to 0.5 dL/g, and or having a lactide:glycolide molar ratio of 60:40 to 45:55.
  • a pharmaceutical depot was prepared comprised of the corticosteroid, betamethasone (BETA, 9-Fluoro-11 ⁇ ,17,21-trihydroxy-16 ⁇ -methylpregna-1,4-diene-3,20-dione) incorporated into microparticles in PLGA 50:50.
  • a formulation was prepared by dissolving approximately 1 gram of PLGA 50:50 (lactide:glycolide molar ratio of 50:50, inherent viscosity 0.44 dL/g, MW 56 kDa) in 6.67 mL of dichloromethane (DCM). To the polymer solution, 400 mg of betamethasone was added and sonicated. Subsequently, the corticosteroid containing dispersion was poured into 200 mL of 0.3% polyvinyl alcohol (PVA) solution while homogenizing with a Silverson homogenizer using a rotor fixed with a Silverson Square Hole High Shear ScreenTM, set to spin at 2,000 rpm to form the microparticles.
  • PVA polyvinyl alcohol
  • the beaker was removed, and a glass magnetic stirrer) added to the beaker, which was then placed onto a multi-way magnetic stirrer and stirred for four hours at 300 rpm to evaporate the DCM.
  • the microparticles were then washed with 2 liters of distilled water, sieved through a 100 micron screen. The microparticles were then lyophilized for greater than 96 hours and vacuum packed.
  • Particle size of the BETA incorporated microparticles was determined using laser diffraction (Beckman Coulter LS 230) by dispersing a 50 mg aliquot in water, with the refractive index (RI) for water and PLGA, set at 1.33 and 1.46 respectively. The sample was stirred at the particle size measurement measurements taken and the results reported. Drug load was determined by suspending a nominal 10 mg of microparticles in 8 ml HPLC grade methanol and sonicating for 2 hours. Samples were then centrifuged at 14,000 g for 15 mins before an aliquot of the supernatant was assayed via HPLC as described below.
  • Corticosteroid-loaded microparticle samples nominally 1 g were placed in 22 ml glass vials in 8-20 ml of 0.5% v/v Tween 20 in 100 mM phosphate buffered saline and stored in a 37° C. incubator with magnetic stirring at 130 rpm. Each test sample was prepared and analyzed in duplicate to monitor possible variability. At each time point in the release study, microparticles were allowed to settle, and an aliquot of between 4-16 ml of supernatant were taken, and replaced with an equal volume of fresh 0.5% v/v Tween 20 in 100 mM phosphate buffered saline.
  • Drug load and in vitro release samples were analyzed by HPLC using a Hypersil C18 column (100 mm, i.d. 5 mm, particle size 5 ⁇ m; ThermoFisher) and Beckman HPLC. All samples were run using a sample injection volume of 5 ⁇ m, and column temperature of 40° C. An isocratic mobile phase of 60% methanol and 40% water was used at a flow rate of 1 ml/min, with detection at a wavelength of 254 nm. The analytical characteristics of the betamethasone PLGA microparticles are shown in the Table 14.
  • FIG. 32 In vitro release profile of the betamethasone PLGA microparticles is shown in FIG. 32 . This formulation is suitable for a 30 day formulation or greater.
  • the amount of betamethasone released per day was calculated based on a human dose, as exemplified in Table 2, which may achieve a temporary suppression of endogenous cortisol (greater than 50%) and, within 14 days, achieve cortisol suppression of endogenous cortisol of less than 35%.
  • This calculated dose equals 111 mg of microparticles containing 25 mg of betamethasone.
  • the amount of betamethasone released per day was calculated based on a human dose, as exemplified in Table 2 that would not suppress the HPA axis, i.e. endogenous cortisol suppression never exceeding 35%.
  • This calculated dose equals 38 mg of microparticles containing 9 mg of betamethasone.
  • the Class C corticosteroid microparticle formulations for example, the betamethasone microparticle formulations, exhibiting the desired release kinetics have the following characteristics: (i) the corticosteroid is between 10%-40% of the microparticle, for example, between 15%-30% of the microparticle; and (ii) the polymer is PLGA having a molecular weight in the range of about 40 to 70 kDa, having an inherent viscosity in the range of 0.35 to 0.5 dL/g, and or having a lactide:glycolide molar ratio of 60:40 to 45:55.
  • a pharmaceutical depot was prepared comprised of the corticosteroid, fluticasone propionate (FLUT, S-(fluoromethyl) 6 ⁇ ,9-difluoro-11 ⁇ ,17-dihydroxy-16 ⁇ -methyl-3-oxoandrosta-1,4-diene-17 ⁇ -carbothioate, 17-propionate) incorporated into microparticles in PLGA 50:50.
  • a formulation was prepared by dissolving approximately 1 gram of PLGA 50:50 (lactide:glycolide molar ratio of 50:50, inherent viscosity 0.45 dL/g, molecular weight 66 kDa) in 6.67 mL of dichloromethane (DCM). To the polymer solution, 200 mg of fluticasone propionate was added and sonicated. Subsequently, the corticosteroid containing dispersion was poured into 200 mL of 0.3% polyvinyl alcohol (PVA) solution while homogenizing with a Silverson homogenizer using a rotor fixed with a Silverson Square Hole High Shear ScreenTM, set to spin at 2,000 rpm to form the microparticles.
  • PVA polyvinyl alcohol
  • the beaker was removed, and a glass magnetic stirrer) added to the beaker, which was then placed onto a multi-way magnetic stirrer and stirred for four hours at 300 rpm to evaporate the DCM.
  • the microparticles were then washed with 2 liters of distilled water, sieved through a 100 micron screen. The microparticles were then lyophilized for greater than 96 hours and vacuum packed.
  • Particle size of the FLUT incorporated microparticles was determined using laser diffraction (Beckman Coulter LS 230) by dispersing a 50 mg aliquot in water, with the refractive index (RI) for water and PLGA, set at 1.33 and 1.46 respectively. The sample was stirred at the particle size measurement measurements taken and the results reported. Drug load was determined by suspending a nominal 10 mg of microparticles in 8 ml HPLC grade methanol and sonicating for 2 hours. Samples were then centrifuged at 14,000 g for 15 mins before an aliquot of the supernatant was assayed via HPLC as described below.
  • Corticosteroid-loaded microparticle samples nominally 1 g were placed in 22 ml glass vials in 8-20 ml of 0.5% v/v Tween 20 in 100 mM phosphate buffered saline and stored in a 37° C. incubator with magnetic stirring at 130 rpm. Each test sample was prepared and analyzed in duplicate to monitor possible variability. At each time point in the release study, microparticles were allowed to settle, and an aliquot of between 4-16 ml of supernatant were taken, and replaced with an equal volume of fresh 0.5% v/v Tween 20 in 100 mM phosphate buffered saline.
  • FIG. 35 In vitro release profile of the fluticasone propionate PLGA microparticles is shown in FIG. 35 . This formulation is suitable for a 30 day formulation or greater.
  • the amount of fluticasone propionate released per day was calculated based on a human dose, as exemplified in Table 2, which may achieve a temporary suppression of endogenous cortisol (greater than 50%) and, within 14 days, achieve cortisol suppression of endogenous cortisol of less than 35%.
  • This calculated dose equals 178 mg of microparticles containing 15 mg of fluticasone propionate.
  • the amount of fluticasone propionate released per day was calculated based on a human dose, as exemplified in Table 2 that would not suppress the HPA axis, i.e. endogenous cortisol suppression never exceeding 35%.
  • This calculated dose equals 24 mg of microparticles containing 2 mg of fluticasone propionate.
  • fluticasone propionate PLGA depots were formulated in the same manner as described above with different PLGA polymers or amounts fluticasone propionate.
  • a PLGA polymer with a higher lactide to glycolide ratio (PLGA 75:25 (ester end-capped PLGA 75:25, lactide:glycolide molar ratio of 75:25, 0.58 dL/g, MW 86 kDa) was used instead of the PLGA 50:50 as previously described.
  • the Class D corticosteroid microparticle formulations for example, the fluticasone or fluticasone propionate microparticle formulations, exhibiting the desired release kinetics have the following characteristics: (i) the corticosteroid is between 8%-20% of the microparticle, and (ii) the polymer is PLGA having a molecular weight in the range of about 40 to 70 kDa, having an inherent viscosity in the range of 0.35 to 0.5 dL/g, and or having a lactide:glycolide molar ratio of 60:40 to 45:55.
  • the corticosteroid is between 8%-20% of the microparticle
  • the polymer is PLGA having a molecular weight in the range of about 40 to 70 kDa, having an inherent viscosity in the range of 0.35 to 0.5 dL/g, and or having a lactide:glycolide molar ratio of 60:40 to 45:55.
  • a pharmaceutical depot was prepared comprised of the corticosteroid, dexamethasone (DEX, 9-Fluoro-11 ⁇ ,17,21-trihydroxy-16 ⁇ -methylpregna-1,4-diene-3,20-dione) incorporated into microparticles in PLGA 50:50.
  • DEX dexamethasone
  • a formulation was prepared by dissolving approximately 1 gram of PLGA 50:50 (lactide:glycolide molar ratio of 50:50, inherent viscosity 0.45 dL/g, molecular weight 66 kDa) in 6.67 mL of dichloromethane (DCM). To the polymer solution, 200 mg of dexamethasone was added and sonicated. Subsequently, the corticosteroid containing dispersion was poured into 200 mL of 0.3% polyvinyl alcohol (PVA) solution while homogenizing with a Silverson homogenizer using a rotor fixed with a Silverson Square Hole High Shear ScreenTM, set to spin at 2,000 rpm to form the microparticles.
  • PVA polyvinyl alcohol
  • the beaker was removed, and a glass magnetic stirrer) added to the beaker, which was then placed onto a multi-way magnetic stirrer and stirred for four hours at 300 rpm to evaporate the DCM.
  • the microparticles were then washed with 2 liters of distilled water, sieved through a 100 micron screen. The microparticles were then lyophilized for greater than 96 hours and vacuum packed.
  • Particle size of the DEX incorporated microparticles was determined using laser diffraction (Beckman Coulter LS 230) by dispersing a 50 mg aliquot in water, with the refractive index (RI) for water and PLGA, set at 1.33 and 1.46 respectively. The sample was stirred at the particle size measurement measurements taken and the results reported. Drug load was determined by suspending a nominal 10 mg of microparticles in 8 ml HPLC grade methanol and sonicating for 2 hours. Samples were then centrifuged at 14,000 g for 15 mins before an aliquot of the supernatant was assayed via HPLC as described below.
  • Corticosteroid-loaded microparticle samples nominally 1 g were placed in 22 ml glass vials in 8-20 ml of 0.5% v/v Tween 20 in 100 mM phosphate buffered saline and stored in a 37° C. incubator with magnetic stirring at 130 rpm. Each test sample was prepared and analyzed in duplicate to monitor possible variability. At each time point in the release study, microparticles were allowed to settle, and an aliquot of between 4-16 ml of supernatant were taken, and replaced with an equal volume of fresh 0.5% v/v Tween 20 in 100 mM phosphate buffered saline.
  • Drug load and in vitro release samples were analyzed by HPLC using a Hypersil C18 column (100 mm, i.d. 5 mm, particle size 5 ⁇ m; ThermoFisher) and Beckman HPLC. All samples were run using a sample injection volume of 5 ⁇ m, and column temperature of 40° C. An isocratic mobile phase of 60% methanol and 40% water was used at a flow rate of 1 ml/min, with detection at a wavelength of 254 nm. The analytical results for the dexamethasone PLGA microparticles are shown in Table 16.
  • the amount of dexamethasone released per day was calculated based on a human dose, as exemplified in Table 2, which may achieve a temporary suppression of endogenous cortisol (greater than 50%) and, within 14 days, achieve cortisol suppression of endogenous cortisol of less than 35%.
  • the amount of dexamethasone released per day was calculated based on a human dose, as exemplified in Table 2 that would not suppress the HPA axis, i.e. endogenous cortisol suppression never exceeding 35%.
  • both calculated human doses are the same; 36 mg of microparticles containing 8 mg of dexamethasone.
  • the doses are graphically represented in FIG. 40 .
  • TCA immediate release TCA immediate release
  • FX006 75:25 PLGA formulation microparticles
  • FX006 dosed at 1.125 mg resulted in a very slow absorption of TCA in the systemic circulation and a markedly lower C max as compared to TCA IR.
  • the mean AUC 0-t values of TCA following 1.125 mg administration of FX006 were 2.1-fold lower than those observed for TCA IR (i.e., 2856 vs. 6065 ng ⁇ h/mL, respectively).
  • the mean C max values of TCA following 1.125 mg administration of FX006 were 15-fold lower than those observed for TCA IR (i.e., 125 vs. 8.15 ng/mL, respectively).
  • the absorption of TCA following administration of FX006 was slower than that observed for TCA IR, with mean T max values observed at 3.33 and 1.00 h, respectively.
  • the elimination half-life of TCA following administration of 1.125 mg FX006 and TCA IR were 451 and 107 h, respectively.
  • the initial “burst” (i.e., exposure up to 24 h) accounted for less than 10% of the total systemic exposure of FX006.
  • the initial burst accounted for ⁇ 23-62% of the total exposure for the TCA IR product, as shown in Table 20.
  • FX006-treated animals had normal articular cartilage despite the presence of catabolic effects on other joint structures, which was likely more readily observed on account of the young age of the animals.
  • a PK-PD analysis demonstrated that inhibition of corticosterone was correlated with systemic TCA levels and followed a classical inhibitory model as shown in FIG. 43 .
  • the IC 50 was about 1 ng/mL and the E max was achieved at 50-80 ng/mL.
  • corticosteroid microparticle formulations provided herein as compared to immediate release corticosteroid formulations. While the studies herein use TCA, it is understood that other corticosteroids, including other Class B corticosteroids, Class A corticosteroids, Class C corticosteroids, and Class D corticosteroids, can be evaluated using these materials, methods and animal models.
  • Efficacy of single intra-articular (IA) doses of FX006 (TCA in 75:25 PLGA formulation microparticles) and TCA IR (immediate release) was evaluated in a rat model of osteoarthritis of the knee via sensitization and challenge by peptidoglycan polysaccharide (PGPS).
  • FIG. 46 plots the time course of corticosterone recovery for all study groups. On balance, across all groups that received the corticosteroid, there was recovery.
  • Plasma levels of TCA were measured in samples taken from all rats at baseline (Day ⁇ 4), Days 0 (2 hr post dosing), 1, 3, 8, 14, 17, 21, 28, and 31. Concentration-time curves for all treatment groups are shown in FIG. 47A .
  • FIG. 47B shows only the FX006 dose groups on a larger scale since maximal plasma concentrations with FX006 were far lower than those with TCA IR.
  • Histopathological evaluation of the knees taken from all animals at the end of the study demonstrated statistically significant improvement by FX006 at the high and mid-range doses (0.28 and 0.12 mg) in the composite histological score and each component score (inflammation, pannus, cartilage damage and bone resorption) as shown in FIG. 48 .
  • the dose of 0.28 mg FX006 demonstrated strong efficacy (i.e. analgesic activity) throughout all 3 reactivations, whereas the dose of 0.12 mg was active but to a lesser degree through all 3 reactivations.
  • a pharmaceutical depot for Ninety-Day sustained release formulations was prepared comprised of the corticosteroid, triamcinolone acetonide (TCA, 9 ⁇ -Fluoro-11 ⁇ ,16 ⁇ ,17 ⁇ ,21-tetrahydroxy-1,4-pregnadiene-3,20-dione 16,17-acetonide; 9 ⁇ -Fluoro-16 ⁇ -hydroxyprednisolone 16 ⁇ ,17 ⁇ -acetonide) incorporated into microparticles.
  • TCA triamcinolone acetonide
  • the beaker was removed, and a glass magnetic stirrer) added to the beaker, which was then placed onto a multi-way magnetic stirrer and stirred for four hours at 300 rpm to evaporate the DCM.
  • the microparticles were then washed with 2 liters of distilled water, sieved through a 100 micron screen. The microparticles were then lyophilized for greater than 96 hours and vacuum packed.
  • Particle size of the TCA incorporated microparticles was determined using laser diffraction (Beckman Coulter LS 230) by dispersing a 50 mg aliquot in water, with the refractive index (RI) for water and PLGA, set at 1.33 and 1.46 respectively. The sample was stirred at the particle size measurement measurements taken and the results reported. Drug load was determined by suspending a nominal 10 mg of microparticles in 8 ml HPLC grade methanol and sonicating for 2 hours. Samples were then centrifuged at 14,000 g for 15 mins before an aliquot of the supernatant was assayed via HPLC as described below.
  • Corticosteroid-loaded microparticle samples nominally 1 g were placed in 22 ml glass vials in 8-20 ml of 0.5% v/v Tween 20 in 100 mM phosphate buffered saline and stored in a 37° C. incubator with magnetic stirring at 130 rpm. Each test sample was prepared and analyzed in duplicate to monitor possible variability. At each time point in the release study, microparticles were allowed to settle, and an aliquot of between 4-16 ml of supernatant were taken, and replaced with an equal volume of fresh 0.5% v/v Tween 20 in 100 mM phosphate buffered saline.
  • Drug load and in vitro release samples were analyzed by HPLC using a Hypersil C18 column (100 mm, i.d. 5 mm, particle size 5 ⁇ m; ThermoFisher) and Beckman HPLC. All samples were run using a sample injection volume of 5 ⁇ m, and column temperature of 40° C. An isocratic mobile phase of 60% methanol and 40% water was used at a flow rate of 1 ml/min, with detection at a wavelength of 254 nm.
  • the PLGA is a combination of ester end capped PLGA 8 E (lactide:glycolide molar ratio of 75:25, inherent viscosity of 0.81 dL/g and molecular weight of 129 kDa) with PLGA 3.5 E (lactide:glycolide molar ratio of 75:25, inherent viscosity of 0.36 dL/g and molecular weight of 49 kDa) in a 2:1 ratio.
  • the analytical results for these formulations are shown in Table 21, and the TCA cumulative release profiles are shown in FIGS. 49 and 52 .
  • the amount of TCA released per day was calculated based on a human dose, as exemplified in Table 2, which may achieve a temporary suppression of endogenous cortisol (greater than 50%) and, within 14 days, achieve cortisol suppression of endogenous cortisol of less than 35% ( FIG. 50 ).
  • This calculated dose equal 769 mg of microparticles containing 75 mg of TCA.
  • the amount of TCA released per day was calculated based on a human dose, as exemplified in Table 2, that would not have an suppress the HPA axis, i.e. endogenous cortisol suppression more than 35% ( FIG. 51 ).
  • This calculated dose equals 410 mg of microparticles containing 40 mg of TCA.
  • the amount of TCA released per day was calculated based on a human dose, as exemplified in Table 2, which may achieve a temporary suppression of endogenous cortisol (greater than 50%) and, within 14 days, achieve cortisol suppression of endogenous cortisol of less than 35% ( FIG. 53 ).
  • This calculated dose equal 909 mg of microparticles containing 77 mg of TCA.
  • the amount of TCA released per day was calculated based on a human dose, as exemplified in Table 2, that would not have an suppress the HPA axis, i.e. endogenous cortisol suppression more than 35% ( FIG. 54 ). This calculated dose equals 483 mg of microparticles containing 41 mg of TCA.
  • a pharmaceutical depot was prepared comprised of the corticosteroid, budesonide ((RS)-11 ⁇ ,16 ⁇ ,17,21-tetrahydroxypregna-1,4-diene-3,20-dione cyclic 16,17-acetal) incorporated into microparticles.
  • Formulations were prepared by dissolving approximately 1 gram of PLGA in 6.67 mL of ethyl acetate, to form a PLGA solution. To the polymer solution, 400 mg of budesonide was added and sonicated. Subsequently, the corticosteroid containing dispersion was poured into 200 mL of 0.3% polyvinyl alcohol (PVA) solution while homogenizing with a Silverson homogenizer using a rotor fixed with a Silverson Square Hole High Shear ScreenTM, set to rotate at approximately 4,000 rpm to 6000 rpm to form the microparticles.
  • PVA polyvinyl alcohol
  • the beaker was removed, and a glass magnetic stirrer) added to the beaker, which was then placed onto a multi-way magnetic stirrer and stirred for four hours at 300 rpm to evaporate the ethyl acetate.
  • the microparticles were then washed with 2 liters of distilled water, sieved through a 100 micron screen. The microparticles were then lyophilized for greater than 96 hours and vacuum packed.
  • Particle size of the budesonide incorporated microparticles was determined using laser diffraction (Beckman Coulter LS 230) by dispersing a 50 mg aliquot in water, with the refractive index (RI) for water and PLGA, set at 1.33 and 1.46 respectively. The sample was stirred at the particle size measurement measurements taken and the results reported. Drug load was determined by suspending a nominal 10 mg of microparticles in 8 ml HPLC grade methanol and sonicating for 2 hours. Samples were then centrifuged at 14,000 g for 15 mins before an aliquot of the supernatant was assayed via HPLC as described below.
  • Corticosteroid-loaded microparticle samples nominally 1 g were placed in 22 ml glass vials in 8-20 ml of 0.5% v/v Tween 20 in 100 mM phosphate buffered saline and stored in a 37° C. incubator with magnetic stirring at 130 rpm. Each test sample was prepared and analyzed in duplicate to monitor possible variability. At each time point in the release study, microparticles were allowed to settle, and an aliquot of between 4-16 ml of supernatant were taken, and replaced with an equal volume of fresh 0.5% v/v Tween 20 in 100 mM phosphate buffered saline.
  • Drug load and in vitro release samples were analyzed by HPLC using a Hypersil C18 column (100 mm, i.d. 5 mm, particle size 5 ⁇ m; ThermoFisher) and Beckman HPLC. All samples were run using a sample injection volume of 5 ⁇ m, and column temperature of 40° C. An isocratic mobile phase of 60% methanol and 40% water was used at a flow rate of 1 ml/min, with detection at a wavelength of 254 nm.
  • the PLGA is an acid end capped PLGA 4.5 A (lactide:glycolide molar ratio of 75:25, inherent viscosity of 0.44 dL/g and molecular weight of 57 kDa).
  • the analytical results for these formulations are shown in Table 22, and the cumulative release profile is shown in FIG. 55 .
  • the amount of budesonide released per day was calculated based on a human dose, as exemplified in Table 2, which may achieve a temporary suppression of endogenous cortisol (greater than 50%) and, within 14 days, achieve cortisol suppression of endogenous cortisol of less than 35% ( FIG. 56 ).
  • This calculated dose equal 175 mg of microparticles containing 41 mg of budesonide.
  • the amount of budesonide released per day was calculated based on a human dose, as exemplified in Table 2, that would not have an suppress the HPA axis, i.e. endogenous cortisol suppression more than 35% ( FIG. 57 ). This calculated dose equals 91 mg of microparticles containing 21 mg of budesonide.
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