US20100303900A1 - Preparation of injectable suspensions having improved injectability - Google Patents

Preparation of injectable suspensions having improved injectability Download PDF

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Publication number
US20100303900A1
US20100303900A1 US12/856,198 US85619810A US2010303900A1 US 20100303900 A1 US20100303900 A1 US 20100303900A1 US 85619810 A US85619810 A US 85619810A US 2010303900 A1 US2010303900 A1 US 2010303900A1
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viscosity
suspension
microparticles
poly
injection
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J. Michael Ramstack
M. Gary I. Riley
Stephen E. Zale
Joyce M. Hotz
OluFunmi L. Johnson
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Alkermes Pharma Ireland Ltd
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Alkermes Controlled Therapeutics Inc
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Priority to US12/856,198 priority Critical patent/US20100303900A1/en
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Priority to US14/085,051 priority patent/US20140193507A1/en
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    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61KPREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K9/00Medicinal preparations characterised by special physical form
    • A61K9/10Dispersions; Emulsions
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61KPREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K47/00Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient
    • A61K47/30Macromolecular organic or inorganic compounds, e.g. inorganic polyphosphates
    • A61K47/34Macromolecular compounds obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds, e.g. polyesters, polyamino acids, polysiloxanes, polyphosphazines, copolymers of polyalkylene glycol or poloxamers
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61KPREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K31/00Medicinal preparations containing organic active ingredients
    • A61K31/33Heterocyclic compounds
    • A61K31/395Heterocyclic compounds having nitrogen as a ring hetero atom, e.g. guanethidine or rifamycins
    • A61K31/495Heterocyclic compounds having nitrogen as a ring hetero atom, e.g. guanethidine or rifamycins having six-membered rings with two or more nitrogen atoms as the only ring heteroatoms, e.g. piperazine or tetrazines
    • A61K31/505Pyrimidines; Hydrogenated pyrimidines, e.g. trimethoprim
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61KPREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K47/00Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient
    • A61K47/06Organic compounds, e.g. natural or synthetic hydrocarbons, polyolefins, mineral oil, petrolatum or ozokerite
    • A61K47/26Carbohydrates, e.g. sugar alcohols, amino sugars, nucleic acids, mono-, di- or oligo-saccharides; Derivatives thereof, e.g. polysorbates, sorbitan fatty acid esters or glycyrrhizin
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61KPREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K47/00Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient
    • A61K47/30Macromolecular organic or inorganic compounds, e.g. inorganic polyphosphates
    • A61K47/36Polysaccharides; Derivatives thereof, e.g. gums, starch, alginate, dextrin, hyaluronic acid, chitosan, inulin, agar or pectin
    • A61K47/38Cellulose; Derivatives thereof
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61KPREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K9/00Medicinal preparations characterised by special physical form
    • A61K9/0012Galenical forms characterised by the site of application
    • A61K9/0019Injectable compositions; Intramuscular, intravenous, arterial, subcutaneous administration; Compositions to be administered through the skin in an invasive manner
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61KPREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K9/00Medicinal preparations characterised by special physical form
    • A61K9/14Particulate form, e.g. powders, Processes for size reducing of pure drugs or the resulting products, Pure drug nanoparticles
    • A61K9/16Agglomerates; Granulates; Microbeadlets ; Microspheres; Pellets; Solid products obtained by spray drying, spray freeze drying, spray congealing,(multiple) emulsion solvent evaporation or extraction
    • A61K9/1605Excipients; Inactive ingredients
    • A61K9/1629Organic macromolecular compounds
    • A61K9/1641Organic macromolecular compounds obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds, e.g. polyethylene glycol, poloxamers
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61KPREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K9/00Medicinal preparations characterised by special physical form
    • A61K9/14Particulate form, e.g. powders, Processes for size reducing of pure drugs or the resulting products, Pure drug nanoparticles
    • A61K9/16Agglomerates; Granulates; Microbeadlets ; Microspheres; Pellets; Solid products obtained by spray drying, spray freeze drying, spray congealing,(multiple) emulsion solvent evaporation or extraction
    • A61K9/1605Excipients; Inactive ingredients
    • A61K9/1629Organic macromolecular compounds
    • A61K9/1641Organic macromolecular compounds obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds, e.g. polyethylene glycol, poloxamers
    • A61K9/1647Polyesters, e.g. poly(lactide-co-glycolide)
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61KPREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K9/00Medicinal preparations characterised by special physical form
    • A61K9/14Particulate form, e.g. powders, Processes for size reducing of pure drugs or the resulting products, Pure drug nanoparticles
    • A61K9/16Agglomerates; Granulates; Microbeadlets ; Microspheres; Pellets; Solid products obtained by spray drying, spray freeze drying, spray congealing,(multiple) emulsion solvent evaporation or extraction
    • A61K9/1605Excipients; Inactive ingredients
    • A61K9/1629Organic macromolecular compounds
    • A61K9/1658Proteins, e.g. albumin, gelatin
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61PSPECIFIC THERAPEUTIC ACTIVITY OF CHEMICAL COMPOUNDS OR MEDICINAL PREPARATIONS
    • A61P25/00Drugs for disorders of the nervous system
    • A61P25/18Antipsychotics, i.e. neuroleptics; Drugs for mania or schizophrenia

Definitions

  • the present invention relates to preparation of injectable compositions. More particularly, the present invention relates to injectable suspensions having improved injectability, and to methods for the preparation of such injectable suspensions.
  • injectable suspensions are heterogeneous systems that typically consist of a solid phase dispersed in a liquid phase, the liquid phase being aqueous or nonaqueous.
  • injectable suspensions should preferably be: sterile; stable; resuspendable; syringeable; injectable; isotonic; and nonirritating. The foregoing characteristics result in manufacturing, storage, and usage requirements that make injectable suspensions one of the most difficult dosage forms to develop.
  • Injectable suspensions are parenteral compositions in that they are introduced into an organism or host by means other than through the gastrointestinal tract. Particularly, injectable suspensions are introduced into a host by subcutaneous (SC) or intramuscular (IM) injection. Injectable suspensions may be formulated as a ready-to-use injection or require a reconstitution step prior to use. Injectable suspensions typically contain between 0.5% and 5.0% solids, with a particle size of less than 5 ⁇ m for IM or SC administration. Parenteral suspensions are frequently administered through needles about one-half to two inches long, 19 to 22 gauge, with an internal diameter in the range of 700 to 400 microns, respectively.
  • Syringeability describes the ability of an injectable suspension to pass easily through a hypodermic needle on transfer from a vial prior to injection. It includes characteristics such as ease of withdrawal, clogging and foaming tendencies, and accuracy of dose measurements. As described in the Floyd et al. Chapter, increase in the viscosity, density, particle size, and concentration of solids in suspension hinders the syringeability of suspensions.
  • Injectability refers to the performance of the suspension during injection. Injectability includes factors such as pressure or force required for injection, evenness of flow, aspiration qualities, and freedom from clogging.
  • Clogging refers to the blockage of syringe needles while administering a suspension. It may occur because of a single large particle, or an aggregate that blocks the lumen of the needle due to a bridging effect of the particles. Clogging at or near the needle end may be caused by restrictions to flow from the suspension. This may involve a number of factors, such as the injection vehicle, wetting of particles, particle size and distribution, particle shape, viscosity, and flow characteristics of the suspension.
  • Resuspendability describes the ability of the suspension to uniformly disperse with minimal shaking after it has stood for some time. Resuspendability can be a problem for suspensions that undergo “caking” upon standing due to settling of the deflocculated particles. “Caking” refers to a process by which the particles undergo growth and fusion to form a nondispersible mass of material.
  • Viscosity describes the resistance that a liquid system offers to flow when it is subjected to an applied shear stress. A more viscous system requires greater force or stress to make it flow at the same rate as a less viscous system.
  • a liquid system will exhibit either Newtonian or non-Newtonian flow based on a linear or a non-linear increase, respectively, in the rate of shear with the shearing stress. Structured vehicles used in suspensions exhibit non-Newtonian flow and are typically plastic, pseudoplastic, or shear-thinning with some thixotropy (exhibiting a decrease in viscosity with an increase in the rate of shear).
  • viscosity enhancers are added in order to retard settling of the particles in the vial and syringe.
  • viscosity is typically kept low, in order to facilitate mixing, resuspension of the particles with the vehicle, and to make the suspension easier to inject (i.e., low force on the syringe plunger).
  • Lupron Depot from TAP Pharmaceuticals (mean particle size of approximately 8 ⁇ m) utilizes an injection vehicle with a viscosity of approximately 5.4 cp.
  • the fluid phase of a suspension of Decapeptyl from DebioPharm (mean particle size of approximately 40 ⁇ m), when prepared as directed, has a viscosity of approximately 19.7 cp.
  • Conventional parenteral suspensions are dilute, with limitations for viscosity because of syringeability and injectability constraints. See, for example, the Floyd, et al. Chapter noted above.
  • Microparticle suspensions may contain 10-15% solids, as compared with 0.5-5% solids in other types of injectable suspensions.
  • Microparticles, particularly controlled release microparticles containing an active agent or other type of substance to be released range in size up to about 250 ⁇ m, as compared with a particle size of less than 5 ⁇ m recommended for IM or SC administration.
  • the higher concentration of solids, as well as the larger solid particle size make it more difficult to successfully inject microparticle suspensions. This is particularly true since it is also desired to inject the microparticle suspensions using as small a needle as possible to minimize patient discomfort.
  • the present invention relates to injectable compositions having improved injectability, and to methods for the preparation of such injectable compositions.
  • a composition suitable for injection through a needle into a host comprises microparticles having a polymeric binder, with a mass median diameter of at least about 10 ⁇ m.
  • the composition also includes an aqueous injection vehicle (the injection vehicle not being the aqueous injection vehicle that consists of 3% by volume sodium carboxymethyl cellulose, 1% by volume polysorbate 20, 0.9% by volume sodium chloride, and a remaining percentage by volume of water).
  • the microparticles are suspended in the injection vehicle at a concentration of greater than about 30 mg/ml to form a suspension, the fluid phase of the suspension having a viscosity of at least 20 cp at 20° C.
  • the fluid phase of the suspension has a viscosity at 20° C. of at least about 30 cp, 40 cp, 50 cp, and 60 cp.
  • the composition may also comprise a viscosity enhancing agent, a density enhancing agent, a tonicity enhancing agent, and/or a wetting agent.
  • the composition can be administered to a host by injection.
  • a method of making a composition suitable for injection through a needle into a host comprises:
  • a composition suitable for injection through a needle into a host is provided.
  • dry microparticles are mixed with an aqueous injection vehicle to form a first suspension.
  • the first suspension is mixed with a viscosity enhancing agent to form a second suspension.
  • the viscosity enhancing agent increases the viscosity of the fluid phase of the second suspension.
  • the first suspension may be withdrawn into a first syringe, prior to mixing with the viscosity enhancing agent.
  • the first suspension may be mixed with the viscosity enhancing agent by coupling the first syringe containing the first suspension to a second syringe that contains the viscosity enhancing agent.
  • the first suspension and the viscosity enhancing agent are then repeatedly passed between the first and second syringes.
  • a method for administering a composition to a host comprises:
  • Another method for administering a composition to a host comprises:
  • a feature of the present invention is that the injectable compositions can be used to inject varying types of microparticles, and varying types of active agents or other substances, into a host.
  • a further feature of the present invention is that it allows microparticles to be wetted to achieve a homogeneous suspension, while improving injectability into a host and reducing in vivo injectability failures.
  • the present invention advantageously provides medically acceptable injectability rates for high concentration suspensions, and for suspensions having large particle size.
  • the present invention also advantageously provides an efficient method of improving in vivo injectability without introducing microbial contamination or compromising aseptic conditions.
  • the present invention relates to injectable compositions having improved injectability, and to methods for the preparation of such injectable compositions.
  • the injectable compositions of the present invention overcome injectability problems, particularly injectability failures that occur upon injection into muscle or subcutaneous tissue. Such injectability failures will be referred to herein as “in vivo injectability failures.” In vivo injectability failures often manifest themselves in the form of a plug at the tip of the needle, and occur immediately or shortly after injection has been initiated. In vivo injectability failures are typically not predicted by laboratory or other in vitro testing.
  • the inventors have unexpectedly discovered that injectability is improved, and in vivo injectability failures significantly and unexpectedly reduced, by increasing the viscosity of the fluid phase of an injectable suspension. This is in contrast to conventional teachings that an increase in the viscosity hinders injectability and syringeability.
  • Viscous vehicles are not optimal for preparing homogeneous suspensions of microparticles because of the relative inability of viscous vehicles to penetrate and wet out a mass of dry particles. Suspensions prepared with viscous vehicles are prone to clump irreversibly. Consequently, such suspensions are not injectable via needles of medically acceptable size. A further disadvantage of viscous suspensions is the lack of ease of transferring such suspensions from the vial or container used to prepare the suspension to the syringe used for injection.
  • the present invention also solves the additional problems that arise from use of a viscous injection vehicle.
  • microparticles are suspended in an injection vehicle having suitable wetting characteristics.
  • the viscosity of the fluid phase of the injectable suspension is increased prior to injecting the suspension in order to improve injectability, and to reduce in vivo injectability failures.
  • microparticles or “microspheres” is meant particles that contain an active agent or other substance dispersed or dissolved within a polymer that serves as a matrix or binder of the particle.
  • the polymer is preferably biodegradable and biocompatible.
  • biodegradable is meant a material that should degrade by bodily processes to products readily disposable by the body and should not accumulate in the body. The products of the biodegradation should also be biocompatible with the body.
  • biocompatible is meant not toxic to the body, is pharmaceutically acceptable, is not carcinogenic, and does not significantly induce inflammation in body tissues.
  • body preferably refers to the human body, but it should be understood that body can also refer to a non-human animal body.
  • weight % or “% by weight” is meant parts by weight per hundred parts total weight of microparticle.
  • 10 wt. % active agent would mean 10 parts active agent by weight and 90 parts polymer by weight. Unless otherwise indicated to the contrary, percentages (%) reported herein are by volume.
  • controlled release microparticle or “sustained release microparticle” is meant a microparticle from which an active agent or other type of substance is released as a function of time.
  • mass median diameter is meant the diameter at which half of the distribution (volume percent) has a larger diameter and half has a smaller diameter.
  • an in vitro sieve test study was conducted to assess and predict in vivo injectability, and to determine the key factors affecting injectability.
  • the following factors were investigated during the in vitro sieve test study: injection vehicle formulation; microparticle morphology; needle diameter; suspension concentration; and particle size as exhibited by sieve screen size used to screen the microparticles during the manufacturing process.
  • Three batches of risperidone microparticles were manufactured at a 125 gm scale using a process substantially the same as that disclosed in U.S. Pat. No. 5,792,477, the entirety of which is incorporated herein by reference (see, for example, Example 1 in U.S. Pat. No. 5,792,477).
  • Three batches of risperidone microparticles were manufactured at a 1 Kg scale using the process described below in Example 7. All batches had similar particle sizes (ranging from a Mass Median Diameter of 91 ⁇ m to 121 ⁇ m) based on Hyac-Royco analysis of representative bulk material sieved through a 180 ⁇ m sieve screen.
  • a 160 mg or 320 mg quantity of the microparticles (equivalent to a 50 or 100 mg dose of the risperidone active agent) was transferred, using a manual Perry powder filler with a 5/16 inch ID barrel, into a 5 cc glass vial, and capped with a Teflon lined septum.
  • the first injection vehicle (“Formula 1”) was an aqueous vehicle consisting of 1.5% by volume carboxymethyl cellulose (CMC), 30% by volume sorbitol, and 0.2% by volume Tween 20 (polysorbate 20). The viscosity of the first injection vehicle was approximately 27 cp at 20° C.
  • the second injection vehicle (“Formula 2”) was an aqueous vehicle consisting of 0.75% by volume CMC, 15% by volume sorbitol, and 0.2% by volume Tween 20 (polysorbate 20). The viscosity of the second injection vehicle was approximately 7 cp at 20° C.
  • the microparticle suspension was prepared as follows. The injection vehicle was aspirated into a 5 cc syringe through a needle. The vehicle was then injected into the glass vial containing the microparticles, and the needle was removed. The glass vial was then rolled between the palms until the microparticles were completely suspended, approximately one minute. The needle was reinserted into the vial so that the bevel of the needle was just through the septum with the opening facing toward the vial bottom. The vial was inverted and the suspension was withdrawn. The syringe was rotated 180° around its axis, and the remaining suspension was aspirated into the syringe.
  • Sieve screens with mesh opening sizes of 180, 212, 250, 300, 355, and 425 ⁇ m were used.
  • the bevel of the syringe needle was placed on the mesh of the sieve screen so that the bevel was in full contact with the mesh.
  • the needle was oriented so the opening of the needle was flush against the mesh of the screen. This prevented the mesh from entering the bevel, while maintaining the required restrictive area.
  • the suspension was tried on the smallest sieve mesh first (highest screen resistance). If the suspension fouled the needle on this sieve mesh, the needle was unclogged by retracting the plunger of the syringe, depressing the plunger while the syringe was in the upward position, and passing an aliquot of suspension through the needle. The injection process was tried again using the next greater mesh size, and repeated until the suspension was successfully injected. All preparations were done in triplicate.
  • a three-factor Box-Behnken statistical designed experiment was constructed to evaluate the following independent variables: manufacturing bulk sieve size (125, 150, and 180 ⁇ m); needle ID (19 TW, 20 RW, and 22 RW gauge-ID of 19 TW (thin wall) equivalent to 18 RW (regular wall)); and suspension concentration (0.074, 0.096, and 0.138 w/w-corresponds to approximately 300 mg microparticle dose diluted with 4, 3, and 2 cc, respectively, of injection vehicle).
  • Table 1 shows the score obtained for screen resistance tests using this scoring system for the 1 Kg and the 125 gm batches for each of the injection vehicles tested.
  • the screen resistance tests showed no significant difference between the two injection vehicles tested. Variations in suspension concentration and injection vehicle viscosity showed little to no effect.
  • the mean scores were identical for the ⁇ 180 manufacturing bulk sieve size, even though the viscosity of the Formula 1 injection vehicle was approximately 27 cp, and the viscosity of the Formula 2 injection vehicle was significantly less, approximately 7 cp.
  • the scores for the other 1 Kg Batch and for the 125 Gm Batches varied modestly (0.2 to 0.5) between the two injection vehicles, thereby indicating that the injection vehicle viscosity had little effect.
  • the tests conducted during the in vitro sieve test study show that in vitro injectability is strongly controlled by microparticle morphology and size.
  • Needle gauge had a more modest effect.
  • in vivo data supported the responses of microparticle morphology, size, and suspension concentration, but contradicted the effect of injection vehicle viscosity. Particularly, the in vivo studies showed a dramatic improvement in injectability with increased injection vehicle viscosity.
  • the injectability of risperidone microparticles was evaluated in Yorkshire weanling pigs. The study revealed that the IM injectability of risperidone microparticles is dependent upon injection vehicle viscosity and microparticle size. Reducing the injection vehicle viscosity led to a higher rate of injection failures due to needle clogging.
  • Risperidone microparticles were manufactured at the 125 gm scale in the same manner noted above for the in vitro sieve test study.
  • the microparticles were sized to ⁇ 125 ⁇ m and ⁇ 150 ⁇ m using USA Standard Testing Sieves Nos. 120 and 100, respectively.
  • the same two injection vehicles (Formula 1 and Formula 2) described above for the in vitro sieve test study were used in the pig study.
  • 19 gauge TW ⁇ 1.5 inch hypodermic needles Becton-Dickinson Precisionglide® catalog number 305187
  • 3 cc hypodermic syringes Becton-Dickinson catalog number 309585
  • the injection experiments were conducted in male and female Yorkshire weanling pigs approximately 6 weeks in age (10-15 kg). The animals were anesthetized with low doses of Telazole and Xylazine and with halothane if needed. Injection sites were shaved and cleansed with betadine swabs prior to microparticle administration.
  • Injections to the hind quarters were administered to the biceps femoris in the upper hind limb. Injection sites in the legs were to the superficial digital flexor muscles in the forelimb, and to the cranial tibial muscle in the hindlimb.
  • Microparticles and injection vehicles were equilibrated to ambient temperature for at least 30 minutes. Using a 3 ml syringe equipped with a 1.5 inch 19 gauge thin wall needle, the prescribed volume of injection vehicle was withdrawn into the syringe, and injected into the vial containing the microparticles. The microparticles were suspended in the injection vehicle by orienting the vial horizontally and rolling it between the palms of the operator's hands. This was done without removing the needle/syringe from the septum. The time required to fully suspend the microparticles was approximately one minute.
  • the suspended microparticles were then withdrawn into the same needle/syringe and injected. Following insertion of the needle and prior to injection of the suspension, the syringe plunger was withdrawn slightly to confirm that the needle was located in the extravascular space. The time interval between aspiration of the suspension and injection was usually less than one minute. Injection regions were evaluated to pinpoint the site of microparticle deposition and to assess the distribution of microparticles in the tissue.
  • Table 2 below shows the effect on injectability as a function of injection vehicle viscosity, injection site, and microparticle concentration.
  • a vehicle viscosity of “high” refers to the injection vehicle of Formula 1 described above, having a viscosity of approximately 27 cp at 20° C.
  • a vehicle viscosity of “low” refers to the injection vehicle of Formula 2 described above, having a viscosity of approximately 7 cp at 20° C.
  • the size of the microparticles for the results shown in Table 2 is 180 ⁇ m.
  • Table 3 summarizes injectability data for microparticles fractionated by size. Similar trends were observed when the system was stressed by decreasing the vehicle viscosity, with failure rates being higher with the ⁇ 180 ⁇ m fraction. The ⁇ 125 ⁇ m fraction and the ⁇ 150 ⁇ m fraction were indistinguishable in terms of failure rate. The low viscosity data show statistically significant differences between ⁇ 180 ⁇ m fraction and ⁇ 150 ⁇ m fraction, and between ⁇ 180 ⁇ m fraction and ⁇ 125 ⁇ m fraction at 1% and 3% confidence levels, respectively (Fisher Exact Test).
  • the in vivo pig study demonstrates a lower injectability failure rate with a higher viscosity injection vehicle, over a range of particle sizes.
  • the in vitro sieve test study did not predict the viscosity dependence observed in the pig study.
  • risperidone microparticles were prepared at the 1 Kg scale using the process described below in Example 7.
  • a batch of placebo microparticles was prepared using the process shown and described in U.S. Pat. No. 5,922,253, the entirety of which is incorporated herein by reference.
  • the two types of microparticles were studied at two suspension concentrations of 150 and 300 mg/ml.
  • Animal injectability tests were conducted using 3 cc syringes and 22 gauge TW ⁇ 1.5 inch needles (Becton-Dickinson).
  • the five injection vehicles were used in Part I.
  • the five injection vehicles were made using one or more of the three injection vehicle formulations shown below:
  • microparticles and injection vehicles were equilibrated to ambient temperature prior to dose suspension.
  • vehicle was aspirated and injected into the microparticle vial.
  • the risperidone microparticles were suspended in 1 ml of vehicle at approximate concentrations of 150 or 300 mg/ml.
  • Placebo microparticles were suspended in 2 or 1 ml of vehicle at approximate concentrations of 150 or 300 mg/ml.
  • the vial was then agitated by hand for approximately 1 minute until the microparticles were suspended.
  • the suspension was then aspirated back into the syringe using the same needle. Care was taken to recover the maximum amount of suspension from the vial. Preparation of dose suspensions was conducted randomly by three individuals.
  • Viscosities were determined by Brookfield Model LVT viscometer fitted with a UL adapter. Densities were measured for Vehicles A, B, and C. Densities for the combination vehicles made up of Vehicles A, B, and C were determined by interpolation based upon the ratio of Vehicles A, B, and C in the combination vehicle.
  • Viscosity Density Conc Vehicle (cp) (mg/ml) (mg/ml) 2 Failures Vehicle A 1.0 1.01 150 8/10 Vehicle B 24.0 1.11 150 1/10 24.0 1.11 300 0/10 Vehicle C 56.0 1.04 150 0/10 56.0 1.04 150 1/10 1 56.0 1.04 300 0/10 3 Parts Vehicle B: 11.1 1.08 300 0/5 1 Part Vehicle A 1 Part Vehicle B: 2.3 1.03 300 7/10 3 Parts Vehicle A 1 Placebo Microparticles. All other results are risperidone microparticles. 2 mg microparticles/ml diluent
  • Part II In order to isolate the effect of injection vehicle viscosity on injectability, additional sheep injectability tests (Part II) were conducted. The injectability results are shown below in Table 5. Viscosities were determined by Brookfield Model LVT viscometer fitted with a UL adapter. In Part II, the suspension concentration was fixed at 300 mg/ml. The tests in Part II were carried out using risperidone microparticles prepared in the same manner as in Part I, using the same injection protocol.
  • the injection vehicles included Vehicle C and Vehicle A as described above, as well as injection vehicles prepared by diluting Vehicle C with Vehicle A.
  • the injection vehicle formulation having a viscosity of 22.9 cp is formulated by combining Vehicle C and Vehicle A in a 1:1 ratio, thereby forming Diluent 1.
  • the effect of a density enhancing agent can be seen by comparing the injectability failures using the vehicle in Table 4 having a viscosity of 11.1 cp with the vehicle in Table 5 having a viscosity of 11.3 cp.
  • the viscosity of these two vehicles is nearly the same.
  • the Table 4 vehicle had 0/5 failures while the Table 5 vehicle had 5/10 failures.
  • the Table 4 vehicle has a higher density (1.08 mg/ml) compared to the Table 5 vehicle (1.02 mg/ml).
  • the Table 4 vehicle includes a density enhancing agent, sorbitol, while the Table 5 vehicle contains no sorbitol or other density enhancing agent.
  • Injectability tests were conducted with several injection vehicles prepared at viscosities exceeding ⁇ 50 cp. Injection vehicles having viscosities in excess of 50 cp were mixed, using a syringe-syringe mixing method described in more detail in Example 5 below, in which the viscosity enhancing agent was introduced after suspending the microparticles in the 50 cp vehicle.
  • Subcutaneous injections of blank (placebo) PLGA (poly(d,l-lactic-co-glycolic acid)) microparticles, having an approximate mass median diameter of 50 ⁇ m, were made into previously harvested pig skin using four injection vehicles having viscosities at ⁇ 25° C. of approximately 53.1 to >1000 cp at the time of formulation.
  • the vehicles were subsequently autoclaved before use, and the final viscosity (viscosity of the fluid phase of the injectable suspension) varied between approximately 5-60% from the nominal starting viscosity value.
  • the most viscous injection vehicle was approximately 13 times the viscosity of the 50 cp formulation.
  • microparticles are first mixed with an injection vehicle having suitable viscosity and wetting characteristics to achieve a homogeneous mono-particulate suspension.
  • the viscosity of the fluid phase of the suspension is then changed, preferably increased, to achieve a viscosity that inhibits suspension separation and clogging under conditions of normal clinical use.
  • dry microparticles are mixed with an aqueous injection vehicle to form a first suspension.
  • the first suspension is mixed with a viscosity enhancing agent to form a second suspension.
  • the viscosity enhancing agent increases the viscosity of the fluid phase of the second suspension.
  • the second suspension is then injected into a host.
  • Vialed dry microparticles are mixed with an aqueous injection vehicle having a viscosity less than about 60 cp at 20° C., preferably about 20-50 centipoise.
  • the concentration of microparticles in the mixture is greater than about 30 mg/ml, preferably about 100-400 mg microparticles/ml.
  • the mixture is agitated until a homogeneous suspension is formed.
  • the homogeneous suspension is withdrawn into a first hypodermic syringe.
  • the first syringe is connected to a second syringe containing a viscosity enhancing agent.
  • a viscosity enhancing agent suitable for use with the present invention is sodium carboxymethyl cellulose (CMC), preferably having a viscosity of from about 1000 to about 2000 cp at 20° C. It should be understood that the present invention is not limited to the use of CMC as the viscosity enhancing agent, and other suitable viscosity enhancing agents may be used.
  • the added volume of the viscosity enhancing agent is approximately 10-25% of the volume of the microparticle suspension.
  • the microparticle suspension and the viscosity enhancing agent are mixed to form the injectable composition by repeatedly passing the microparticle suspension and the viscosity enhancing agent between the first and second syringes.
  • Such a syringe-syringe mixing method was used in the injectability tests described in Example 4 above.
  • the viscosity of the fluid phase of the microparticle suspension is from about 200 cp to about 600 cp at 20° C.
  • a hypodermic needle is attached to the syringe containing the injectable composition, and the injectable composition is injected into a host in a manner well known to one of skill in the art.
  • Dry microparticles are mixed with an aqueous injection vehicle having a viscosity of less than about 60 cp at 20° C. to form a suspension.
  • the viscosity of the fluid phase of the suspension is changed in a manner that will be described in more detail below.
  • the suspension that constitutes the injectable composition is withdrawn into a syringe, and the injectable composition is injected from the syringe into the host.
  • the viscosity of the fluid phase of the suspension is changed after the suspension has been withdrawn into the syringe.
  • the viscosity is changed by changing the temperature of the fluid phase of the injectable suspension.
  • the methods and techniques for changing the viscosity of a liquid by changing the temperature of the liquid are readily apparent to one skilled in the art.
  • the temperature of the fluid phase of the suspension is changed until the desired viscosity of the fluid phase has been reached.
  • the suspension now has the desired fluid phase viscosity for injection into a host, and constitutes the injectable composition. At this point, the suspension is withdrawn into the syringe and injected into the host. Alternatively, the suspension can be withdrawn into the syringe prior to changing the temperature of the fluid phase of the suspension to achieve the desired fluid phase viscosity.
  • an injection vehicle that comprises a polymer solution can be used as the viscosity of polymer solutions is temperature-dependent.
  • a polymer solution can be used to suspend the microparticles under low-viscosity conditions suitable for wetting and suspension formation. Once the microparticles are suspended, the suspension is drawn up into a syringe. The temperature is then changed to induce higher viscosity in the injection vehicle constituting the fluid phase of the suspension, and the suspension having increased viscosity is injected into a host.
  • the viscosity is changed by adding a viscosity enhancing agent to the suspension.
  • the suspension is withdrawn into the syringe, and then the viscosity enhancing agent is added to the suspension in the syringe, thereby increasing the viscosity of the aqueous injection vehicle constituting the fluid phase of the suspension.
  • the suspension now has the desired fluid phase viscosity for injection into a host, and constitutes the injectable composition.
  • the suspension is then injected into the host.
  • the viscosity enhancing agent is added to the suspension immediately prior to injection into the host.
  • Suitable viscosity enhancing agents include sodium carboxymethyl cellulose, polyvinylpyrrolidone (PVP), such as PLASDONE, available from GAF Chemicals Corp., Wayne, N.J., and hydroxypropylmethylcellulose (HPMC), such as Methocel, available from Dow Chemical Co., Midland, Mich.
  • PVP polyvinylpyrrolidone
  • HPMC hydroxypropylmethylcellulose
  • Methocel available from Dow Chemical Co., Midland, Mich.
  • other viscosity enhancing agents may be used, as would be readily apparent to one of skill in the art.
  • the injectable compositions of the present invention are prepared by providing microparticles that comprise a polymeric binder and that have a mass median diameter of at least about 10 ⁇ m.
  • the mass median diameter of the microparticles is preferably less than about 250 ⁇ m, and more preferably, in the range of from about 20 ⁇ m to about 150 ⁇ m.
  • Such microparticles can be made in the manner disclosed and described herein, or in any other manner known to one skilled in the art.
  • An aqueous injection vehicle is provided. Such an aqueous injection vehicle can be made in the manner disclosed and described herein, or in any other manner known to one skilled in the art.
  • the microparticles are suspended in the aqueous injection vehicle at a concentration of greater than about 30 mg/ml to form a suspension, the fluid phase of the suspension having a viscosity of at least 20 cp at 20° C.
  • dry microparticles are mixed with an aqueous injection vehicle containing a viscosity enhancing agent to form a suspension.
  • Suitable viscosity enhancing agents include sodium carboxymethyl cellulose, polyvinylpyrrolidone (PVP), such as PLASDONE, available from GAF Chemicals Corp., Wayne, N.J., and hydroxypropylmethylcellulose (HPMC), such as Methocel, available from Dow Chemical Co., Midland, Mich.
  • PVP polyvinylpyrrolidone
  • HPMC hydroxypropylmethylcellulose
  • the suspension is then dispensed into vials.
  • the vials are lyophilized (or vacuum dried) to remove the water.
  • the vial contents Prior to injection, are reconstituted with sterile water for injection in a quantity sufficient to achieve the desired viscosity for the fluid phase of the reconstituted injectable suspension.
  • the vial contents are reconstituted with a quantity of sterile water for injection sufficient to achieve a viscosity of a fluid phase of the injectable suspension that provides injectability of the composition through a needle ranging in diameter from 18-22 gauge.
  • the injectable compositions of the present invention are suitable for injection through a needle into a host.
  • the injectable compositions comprise microparticles suspended in an aqueous injection vehicle.
  • the microparticles preferably have a mass median diameter of at least about 10 ⁇ m to about 250 ⁇ m, preferably in the range of from about 20 ⁇ m to about 150 ⁇ m.
  • the invention is not limited to microparticles in this size range, and that smaller or larger microparticles may also be used.
  • the microparticles preferably comprise a polymeric binder.
  • suitable polymeric binder materials include poly(glycolic acid), poly-d,l-lactic acid, poly-l-lactic acid, copolymers of the foregoing, poly(aliphatic carboxylic acids), copolyoxalates, polycaprolactone, polydioxanone, poly(ortho carbonates), poly(acetals), poly(lactic acid-caprolactone), polyorthoesters, poly(glycolic acid-caprolactone), polyanhydrides, polyphosphazines, albumin, casein, and waxes.
  • Poly(d,l-lactic-co-glycolic acid) is commercially available from Alkermes, Inc. (Blue Ash, Ohio).
  • a suitable product commercially available from Alkermes, Inc. is a 50:50 poly(d,l-lactic-co-glycolic acid) known as MEDISORB® 5050 DL. This product has a mole percent composition of 50% lactide and 50% glycolide.
  • Other suitable commercially available products are MEDISORB® 6535 DL, 7525 DL, 8515 DL and poly(d,l-lactic acid) (100 DL).
  • Poly(lactide-co-glycolides) are also commercially available from Boehringer Ingelheim (Germany) under its Resomer® mark, e.g., PLGA 50:50 (Resomer® RG 502), PLGA 75:25 (Resomer® RG 752) and d,l-PLA (Resomer® RG 206), and from Birmingham Polymers (Birmingham, Ala.). These copolymers are available in a wide range of molecular weights and ratios of lactic acid to glycolic acid.
  • microparticle suitable for use with the present invention is a sustained-release microparticle that is biodegradable.
  • the present invention is not limited to biodegradable or other types of sustained-release microparticles.
  • the molecular weight of the polymeric binder material for biodegradable microparticles is of some importance. The molecular weight should be high enough to permit the formation of satisfactory polymer coatings, i.e., the polymer should be a good film former. Usually, a satisfactory molecular weight is in the range of 5,000 to 500,000 daltons, preferably about 150,000 daltons.
  • the properties of the film are also partially dependent on the particular polymeric binder material being used, it is very difficult to specify an appropriate molecular weight range for all polymers.
  • the molecular weight of the polymer is also important from the point of view of its influence upon the biodegradation rate of the polymer.
  • the polymer should remain intact until all of the drug is released from the microparticles and then degrade.
  • the drug can also be released from the microparticles as the polymeric binder bioerodes.
  • a microparticle formulation can be made in which the resulting microparticles exhibit both diffusional release and biodegradation release properties. This is useful in according multiphasic release patterns.
  • the microparticles may include an active agent or other type of substance that is released from the microparticles into the host.
  • active agents can include 1,2-benzazoles, more particularly, 3-piperidinyl-substituted 1,2-benzisoxazoles and 1,2-benzisothiazoles.
  • the most preferred active agents of this kind are 3-[2-[4-(6-fluoro-1,2-benzisoxazol-3-yl)-1-piperidinyl]ethyl]-6,7,8,9-tetrahydro-2-methyl-4H-pyrido[1,2-a]pyrimidin-4-one (“risperidone”) and 3-[2-[4-(6-fluoro-1,2-benzisoxazol-3-yl)-1-piperidinyl]ethyl]-6,7,8,9-tetrahydro-9-hydroxy-2-methyl-4H-pyrido[1,2-a]pyrimidin-4-one (“9-hydroxyrisperidone”) and the pharmaceutically acceptable salts thereof.
  • Risperidone (which term, as used herein, is intended to include its pharmaceutically acceptable salts) is most preferred. Risperidone can be prepared in accordance with the teachings of U.S. Pat. No. 4,804,663, the entirety of which is incorporated herein by reference. 9-hydroxyrisperidone can be prepared in accordance with the teachings of U.S. Pat. No. 5,158,952, the entirety of which is incorporated herein by reference.
  • Other biologically active agents include non-steroidal antifertility agents; parasympathomimetic agents; psychotherapeutic agents; tranquilizers; decongestants; sedative hypnotics; steroids; sulfonamides; sympathomimetic agents; vaccines; vitamins; antimalarials; anti-migraine agents; anti-Parkinson agents such as L-dopa; anti-spasmodics; anticholinergic agents (e.g.
  • oxybutynin oxybutynin
  • antitussives bronchodilators
  • cardiovascular agents such as coronary vasodilators and nitroglycerin
  • alkaloids such as coronary vasodilators and nitroglycerin
  • analgesics such as codeine, dihydrocodienone, meperidine, morphine and the like
  • non-narcotics such as salicylates, aspirin, acetaminophen, d-propoxyphene and the like
  • opioid receptor antagonists such as naltrexone and naloxone
  • antibiotics such as gentamycin, tetracycline and penicillins
  • anti-cancer agents anti-convulsants
  • anti-emetics antihistamines
  • anti-inflammatory agents such as hormonal agents, hydrocortisone, prednisolone, prednisone, non-hormonal agents, allopurinol, indomethacin, pheny
  • Still other suitable active agents include estrogens, antibacterials; antifungals; antivirals; anticoagulants; anticonvulsants; antidepressants; antihistamines; and immunological agents.
  • suitable biologically active agents include peptides and proteins, analogs, muteins, and active fragments thereof, such as immunoglobulins, antibodies, cytokines (e.g. lymphokines, monokines, chemokines), blood clotting factors, hemopoietic factors, interleukins (IL-2, IL-3, IL-4, IL-6), interferons ( ⁇ -IFN, ⁇ -IFN and ⁇ -IFN), erythropoietin, nucleases, tumor necrosis factor, colony stimulating factors (e.g., GCSF, GM-CSF, MCSF), insulin, enzymes (e.g., superoxide dismutase, tissue plasminogen activator), tumor suppressors, blood proteins, hormones and hormone analogs (e.g., growth hormone, adrenocorticotropic hormone and luteinizing hormone releasing hormone (LHRH)), vaccines (e.g., tumoral, bacterial and viral antigens, tumor
  • Small molecular weight agents suitable for use in the invention include, antitumor agents such as bleomycin hydrochloride, carboplatin, methotrexate and adriamycin; antipyretic and analgesic agents; antitussives and expectorants such as ephedrine hydrochloride, methylephedrine hydrochloride, noscapine hydrochloride and codeine phosphate; sedatives such as chlorpromazine hydrochloride, prochlorperazine hydrochloride and atropine sulfate; muscle relaxants such as tubocurarine chloride; antiepileptics such as sodium phenyloin and ethosuximide; antiulcer agents such as metoclopramide; antidepressants such as clomipramine; antiallergic agents such as diphenhydramine; cardiotonics such as theophillol; antiarrhythmic agents such as propranolol hydrochloride; vasodilators such as d
  • microparticles can be mixed by size or by type. However, it should be understood that the present invention is not limited to the use of biodegradable or other types of microparticles that contain an active agent.
  • the microparticles are mixed in a manner that provides for the delivery of active agent to the patient in a multiphasic manner and/or in a manner that provides different active agents to the patient at different times, or a mixture of active agents at the same time.
  • secondary antibiotics, vaccines, or any desired active agent either in microparticle form or in conventional, unencapsulated form can be blended with a primary active agent and provided to the patient.
  • the microparticles are preferably suspended in the injection vehicle at a concentration of greater than about 30 mg/ml. In one embodiment, the microparticles are suspended at a concentration of from about 150 mg/ml to about 300 mg/ml. In another embodiment, the microparticles are suspended at a concentration of from about 100 mg/ml to about 400 mg/ml. However, it should be understood that the invention is not limited to a particular concentration.
  • the aqueous injection vehicle preferably has a viscosity of at least 20 cp at 20° C. In one embodiment, the injection vehicle has a viscosity greater than 50 cp and less than 60 cp at 20° C.
  • the viscosity of the injection vehicle preferably provides injectability of the composition through a needle ranging in diameter from 18-22 gauge. As known to one skilled in the art, an 18 gauge regular wall (RW) needle has a nominal inner diameter (ID) of 0.033 in., and a 22 gauge regular wall needle has a nominal inner diameter of 0.016 in.
  • the injection vehicle may comprise a viscosity enhancing agent.
  • a preferred viscosity enhancing agent is sodium carboxymethyl cellulose, although other suitable viscosity enhancing agents may also be used.
  • the injection vehicle may also comprise a density enhancing agent that increases the density of the injection vehicle.
  • a preferred density enhancing agent is sorbitol, although other suitable density enhancing agents may also be used.
  • the injection vehicle may also comprise a tonicity adjusting agent to adjust the tonicity to preclude toxicity problems and improve biocompatibility.
  • a preferred tonicity adjusting agent is sodium chloride, although other suitable tonicity adjusting agents may also be used.
  • the injection vehicle may also comprise a wetting agent to ensure complete wetting of the microparticles by the injection vehicle.
  • Preferred wetting agents include polysorbate 20 (Tween 20), polysorbate 40 (Tween 40), and polysorbate 80 (Tween 80).
  • One preferred injection vehicle is an aqueous injection vehicle that comprises 1.5% sodium carboxymethyl cellulose, 30% sorbitol, and 0.2% polysorbate 20.
  • Another preferred injection vehicle is an aqueous injection vehicle that comprises 3% sodium carboxymethyl cellulose, 0.9% saline, and 0.1% polysorbate 20.
  • a process for preparing microparticles containing risperidone as the active agent will now be described.
  • the following 1 Kg process 400 grams of active agent and 600 grams of polymer) is for a theoretical drug loading of the microparticles of 40%.
  • the actual drug loading that is achieved by the process described below ranges from about 35% to about 39%.
  • a drug solution is prepared by dissolving 400 grams of risperidone (Janssen Pharmaceutica, Beerse, Belgium) in 1267 grams of benzyl alcohol to form a 24 wt. % drug solution.
  • a polymer solution is formed by dissolving 600 grams of MEDISORB® 7525 DL polymer (Alkermes, Inc., Blue Ash, Ohio) in 3000 grams of ethyl acetate to form a 16.7 wt. % polymer solution.
  • the drug solution and the polymer solution are combined to form a first, discontinuous phase.
  • the second, continuous phase is prepared by preparing a 30 liter solution of 1% PVA, the PVA acting as an emulsifier. To this is added 2086 grams of ethyl acetate to form a 6.5 wt. % solution of ethyl acetate.
  • the two phases are combined using a static mixer, such as a 1 ⁇ 2′′ Kenics static mixer available from Chemineer, Inc., North Andover, Mass.
  • a total flow rate of 3 L/min generally provides microparticle size distributions with a mass median diameter (MMD) in the range of about 80-90 ⁇ .
  • MMD mass median diameter
  • the ratio of continuous phase to discontinuous phase is 5:1 (v/v).
  • the length of the static mixer can vary from about 9 inches to about 88 inches. Lengths greater than about 48 inches results in the greatest percent yield in a microparticle size range of 25-150 ⁇ .
  • the quench liquid is 2.5% solution of ethyl acetate and water-for-injection (WFI) at 5-10° C.
  • the volume of the quench liquid is 0.25 L per gram of batch size.
  • the quench step is carried out for a time period greater than about 4 hours, with stirring of the microparticles in the quench tank.
  • the microparticles are transferred to a collecting, de-watering, and drying device.
  • the microparticles are rinsed using a chilled (approximately 5° C.) 17 liter 25% ethanol solution.
  • the microparticles are dried, and then re-slurried in a re-slurry tank using a 25% ethanol solution (extraction medium) maintained at a temperature lower than the T g (glass transition temperature) of the microparticles.
  • the microparticles are then transferred back to the quench tank for washing for a time period of at least 6 hours with another extraction medium (25% ethanol solution) that is maintained at a temperature higher than the T g of the microparticles.
  • the T g of the microparticles is about 18° C. (about room temperature), and the temperature of the extraction medium in the quench tank is greater than about 18° C., preferably 25° ⁇ 1° C.
  • microparticles are transferred back to the collecting, de-watering, and drying device for de-watering and final drying. Drying continues for a time period greater than about 16 hours.

Abstract

Injectable compositions having improved injectability. The injectable compositions include microparticles suspended in an aqueous injection vehicle having a viscosity of at least 20 cp at 20° C. The increased viscosity of the injection vehicle that constitutes the fluid phase of the suspension significantly reduces in vivo injectability failures. The injectable compositions can be made by mixing dry microparticles with an aqueous injection vehicle to form a suspension, and then mixing the suspension with a viscosity enhancing agent to increase the viscosity of the fluid phase of the suspension to the desired level for improved injectability.

Description

    BACKGROUND OF THE INVENTION
  • 1. Field of the Invention
  • The present invention relates to preparation of injectable compositions. More particularly, the present invention relates to injectable suspensions having improved injectability, and to methods for the preparation of such injectable suspensions.
  • 2. Related Art
  • Injectable suspensions are heterogeneous systems that typically consist of a solid phase dispersed in a liquid phase, the liquid phase being aqueous or nonaqueous. To be effective and pharmaceutically acceptable, injectable suspensions should preferably be: sterile; stable; resuspendable; syringeable; injectable; isotonic; and nonirritating. The foregoing characteristics result in manufacturing, storage, and usage requirements that make injectable suspensions one of the most difficult dosage forms to develop.
  • Injectable suspensions are parenteral compositions in that they are introduced into an organism or host by means other than through the gastrointestinal tract. Particularly, injectable suspensions are introduced into a host by subcutaneous (SC) or intramuscular (IM) injection. Injectable suspensions may be formulated as a ready-to-use injection or require a reconstitution step prior to use. Injectable suspensions typically contain between 0.5% and 5.0% solids, with a particle size of less than 5 μm for IM or SC administration. Parenteral suspensions are frequently administered through needles about one-half to two inches long, 19 to 22 gauge, with an internal diameter in the range of 700 to 400 microns, respectively.
  • To develop an effective and pharmaceutically acceptable injectable suspension, a number of characteristics must be evaluated. These characteristics include syringeability, injectability, clogging, resuspendability, and viscosity. As will be readily apparent to one skilled in the art, other characteristics and factors should be considered in developing an injectable suspension (see, for example, Floyd, A. G. and Jain, S., Injectable Emulsions and Suspensions, Chapter 7 in Pharmaceutical Dosage Forms: Disperse Systems Vol. 2, Edited by Lieberman, H. A., Rieger, M. M., and Banker, G. S., Marcel Dekker, New York (1996), the entirety of which is incorporated herein by reference and referred to herein as “the Floyd et al. Chapter”).
  • Syringeability describes the ability of an injectable suspension to pass easily through a hypodermic needle on transfer from a vial prior to injection. It includes characteristics such as ease of withdrawal, clogging and foaming tendencies, and accuracy of dose measurements. As described in the Floyd et al. Chapter, increase in the viscosity, density, particle size, and concentration of solids in suspension hinders the syringeability of suspensions.
  • Injectability refers to the performance of the suspension during injection. Injectability includes factors such as pressure or force required for injection, evenness of flow, aspiration qualities, and freedom from clogging.
  • Clogging refers to the blockage of syringe needles while administering a suspension. It may occur because of a single large particle, or an aggregate that blocks the lumen of the needle due to a bridging effect of the particles. Clogging at or near the needle end may be caused by restrictions to flow from the suspension. This may involve a number of factors, such as the injection vehicle, wetting of particles, particle size and distribution, particle shape, viscosity, and flow characteristics of the suspension.
  • Resuspendability describes the ability of the suspension to uniformly disperse with minimal shaking after it has stood for some time. Resuspendability can be a problem for suspensions that undergo “caking” upon standing due to settling of the deflocculated particles. “Caking” refers to a process by which the particles undergo growth and fusion to form a nondispersible mass of material.
  • Viscosity describes the resistance that a liquid system offers to flow when it is subjected to an applied shear stress. A more viscous system requires greater force or stress to make it flow at the same rate as a less viscous system. A liquid system will exhibit either Newtonian or non-Newtonian flow based on a linear or a non-linear increase, respectively, in the rate of shear with the shearing stress. Structured vehicles used in suspensions exhibit non-Newtonian flow and are typically plastic, pseudoplastic, or shear-thinning with some thixotropy (exhibiting a decrease in viscosity with an increase in the rate of shear).
  • In design of injection vehicles, viscosity enhancers are added in order to retard settling of the particles in the vial and syringe. However, viscosity is typically kept low, in order to facilitate mixing, resuspension of the particles with the vehicle, and to make the suspension easier to inject (i.e., low force on the syringe plunger). For example, Lupron Depot from TAP Pharmaceuticals (mean particle size of approximately 8 μm) utilizes an injection vehicle with a viscosity of approximately 5.4 cp. The fluid phase of a suspension of Decapeptyl from DebioPharm (mean particle size of approximately 40 μm), when prepared as directed, has a viscosity of approximately 19.7 cp. Conventional parenteral suspensions are dilute, with limitations for viscosity because of syringeability and injectability constraints. See, for example, the Floyd, et al. Chapter noted above.
  • Injectable compositions containing microparticle preparations are particularly susceptible to injectability problems. Microparticle suspensions may contain 10-15% solids, as compared with 0.5-5% solids in other types of injectable suspensions. Microparticles, particularly controlled release microparticles containing an active agent or other type of substance to be released, range in size up to about 250 μm, as compared with a particle size of less than 5 μm recommended for IM or SC administration. The higher concentration of solids, as well as the larger solid particle size, make it more difficult to successfully inject microparticle suspensions. This is particularly true since it is also desired to inject the microparticle suspensions using as small a needle as possible to minimize patient discomfort.
  • Thus, there is a need in the art for an injectable composition with improved injectability. There is a particular need in the art for an injectable composition that solves the injectability problems associated with microparticle suspensions. The present invention, the description of which is fully set forth below, solves the need in the art for such injectable compositions.
  • SUMMARY OF THE INVENTION
  • The present invention relates to injectable compositions having improved injectability, and to methods for the preparation of such injectable compositions. In one aspect of the invention, a composition suitable for injection through a needle into a host is provided. The composition comprises microparticles having a polymeric binder, with a mass median diameter of at least about 10 μm. The composition also includes an aqueous injection vehicle (the injection vehicle not being the aqueous injection vehicle that consists of 3% by volume sodium carboxymethyl cellulose, 1% by volume polysorbate 20, 0.9% by volume sodium chloride, and a remaining percentage by volume of water). The microparticles are suspended in the injection vehicle at a concentration of greater than about 30 mg/ml to form a suspension, the fluid phase of the suspension having a viscosity of at least 20 cp at 20° C. In other embodiments, the fluid phase of the suspension has a viscosity at 20° C. of at least about 30 cp, 40 cp, 50 cp, and 60 cp. The composition may also comprise a viscosity enhancing agent, a density enhancing agent, a tonicity enhancing agent, and/or a wetting agent. The composition can be administered to a host by injection.
  • In another aspect of the present invention, a method of making a composition suitable for injection through a needle into a host is provided. The method comprises:
      • (a) providing microparticles comprising a polymeric binder, said microparticles having a mass median diameter of at least about 10 μm;
      • (b) providing an aqueous injection vehicle having a viscosity of at least 20 cp at 20° C., wherein said injection vehicle is not the aqueous vehicle consisting of 3% by volume sodium carboxymethyl cellulose, 1% by volume polysorbate 20, 0.9% by volume sodium chloride, and a remaining percentage by volume of water; and
      • (c) suspending the microparticles in the aqueous injection vehicle at a concentration of greater than about 30 mg/ml to form a suspension.
  • In a further aspect of the present invention, another method for preparing a composition suitable for injection through a needle into a host is provided. In such a method, dry microparticles are mixed with an aqueous injection vehicle to form a first suspension. The first suspension is mixed with a viscosity enhancing agent to form a second suspension. The viscosity enhancing agent increases the viscosity of the fluid phase of the second suspension. The first suspension may be withdrawn into a first syringe, prior to mixing with the viscosity enhancing agent. The first suspension may be mixed with the viscosity enhancing agent by coupling the first syringe containing the first suspension to a second syringe that contains the viscosity enhancing agent. The first suspension and the viscosity enhancing agent are then repeatedly passed between the first and second syringes.
  • In yet a further aspect of the present invention, a method for administering a composition to a host is provided. The method comprises:
      • (a) mixing dry microparticles with an aqueous injection vehicle to form a first suspension;
      • (b) mixing the first suspension with a viscosity enhancing agent to form a second suspension, wherein the viscosity enhancing agent increases the viscosity of the fluid phase of the second suspension; and
      • (c) injecting the second suspension into the host.
  • In still a further aspect of the present invention, another method for administering a composition to a host is provided. The method comprises:
      • (a) mixing dry microparticles with an aqueous injection vehicle to form a suspension, wherein the aqueous injection vehicle has a viscosity at 20° C. of less than about 60 cp;
      • (b) changing the viscosity of the fluid phase of the suspension;
      • (c) withdrawing the suspension into a syringe; and
      • (d) injecting the suspension from the syringe into the host.
        In a further aspect of the invention, step (b) is carried out by changing the temperature of to the fluid phase of the suspension. In another aspect, step (c) is performed prior to step (b). Step (b) may be carried out by adding a viscosity enhancing agent to the suspension in the syringe to thereby increase the viscosity of the fluid phase of the suspension.
      • In still a further aspect of the invention, a method for preparing a composition suitable for injection through a needle into a host is provided. The method comprises:
      • (a) mixing dry microparticles with an aqueous injection vehicle that comprises a viscosity enhancing agent to form a suspension;
      • (b) removing water from the suspension; and
      • (c) reconstituting the suspension with a quantity of sterile water for injection to form an injectable suspension, wherein the quantity of sterile water for injection is sufficient to achieve a viscosity of a fluid phase of the injectable suspension that provides injectability of the composition through a needle ranging in diameter from 18-22 gauge.
    Features and Advantages
  • A feature of the present invention is that the injectable compositions can be used to inject varying types of microparticles, and varying types of active agents or other substances, into a host.
  • A further feature of the present invention is that it allows microparticles to be wetted to achieve a homogeneous suspension, while improving injectability into a host and reducing in vivo injectability failures.
  • The present invention advantageously provides medically acceptable injectability rates for high concentration suspensions, and for suspensions having large particle size.
  • The present invention also advantageously provides an efficient method of improving in vivo injectability without introducing microbial contamination or compromising aseptic conditions.
  • DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS Overview
  • The present invention relates to injectable compositions having improved injectability, and to methods for the preparation of such injectable compositions. The injectable compositions of the present invention overcome injectability problems, particularly injectability failures that occur upon injection into muscle or subcutaneous tissue. Such injectability failures will be referred to herein as “in vivo injectability failures.” In vivo injectability failures often manifest themselves in the form of a plug at the tip of the needle, and occur immediately or shortly after injection has been initiated. In vivo injectability failures are typically not predicted by laboratory or other in vitro testing.
  • The inventors have unexpectedly discovered that injectability is improved, and in vivo injectability failures significantly and unexpectedly reduced, by increasing the viscosity of the fluid phase of an injectable suspension. This is in contrast to conventional teachings that an increase in the viscosity hinders injectability and syringeability.
  • Viscous vehicles, however, are not optimal for preparing homogeneous suspensions of microparticles because of the relative inability of viscous vehicles to penetrate and wet out a mass of dry particles. Suspensions prepared with viscous vehicles are prone to clump irreversibly. Consequently, such suspensions are not injectable via needles of medically acceptable size. A further disadvantage of viscous suspensions is the lack of ease of transferring such suspensions from the vial or container used to prepare the suspension to the syringe used for injection.
  • The present invention also solves the additional problems that arise from use of a viscous injection vehicle. In accordance with the present invention, microparticles are suspended in an injection vehicle having suitable wetting characteristics. The viscosity of the fluid phase of the injectable suspension is increased prior to injecting the suspension in order to improve injectability, and to reduce in vivo injectability failures.
  • To ensure clarity of the description that follows, the following definitions are provided. By “microparticles” or “microspheres” is meant particles that contain an active agent or other substance dispersed or dissolved within a polymer that serves as a matrix or binder of the particle. The polymer is preferably biodegradable and biocompatible. By “biodegradable” is meant a material that should degrade by bodily processes to products readily disposable by the body and should not accumulate in the body. The products of the biodegradation should also be biocompatible with the body. By “biocompatible” is meant not toxic to the body, is pharmaceutically acceptable, is not carcinogenic, and does not significantly induce inflammation in body tissues. As used herein, “body” preferably refers to the human body, but it should be understood that body can also refer to a non-human animal body. By “weight %” or “% by weight” is meant parts by weight per hundred parts total weight of microparticle. For example, 10 wt. % active agent would mean 10 parts active agent by weight and 90 parts polymer by weight. Unless otherwise indicated to the contrary, percentages (%) reported herein are by volume. By “controlled release microparticle” or “sustained release microparticle” is meant a microparticle from which an active agent or other type of substance is released as a function of time. By “mass median diameter” is meant the diameter at which half of the distribution (volume percent) has a larger diameter and half has a smaller diameter.
  • METHOD AND EXAMPLES
  • The following examples are provided to explain the invention, and to describe the materials and methods used in carrying out the invention. The examples are not intended to limit the invention in any manner.
  • Example 1 In vitro Sieve Test Study
  • To evaluate in vivo injectability failures, an in vitro sieve test study was conducted to assess and predict in vivo injectability, and to determine the key factors affecting injectability. The following factors were investigated during the in vitro sieve test study: injection vehicle formulation; microparticle morphology; needle diameter; suspension concentration; and particle size as exhibited by sieve screen size used to screen the microparticles during the manufacturing process.
  • Three batches of risperidone microparticles were manufactured at a 125 gm scale using a process substantially the same as that disclosed in U.S. Pat. No. 5,792,477, the entirety of which is incorporated herein by reference (see, for example, Example 1 in U.S. Pat. No. 5,792,477). Three batches of risperidone microparticles were manufactured at a 1 Kg scale using the process described below in Example 7. All batches had similar particle sizes (ranging from a Mass Median Diameter of 91 μm to 121 μm) based on Hyac-Royco analysis of representative bulk material sieved through a 180 μm sieve screen. A 160 mg or 320 mg quantity of the microparticles (equivalent to a 50 or 100 mg dose of the risperidone active agent) was transferred, using a manual Perry powder filler with a 5/16 inch ID barrel, into a 5 cc glass vial, and capped with a Teflon lined septum.
  • Two injection vehicles were used in the in vitro sieve test study. The first injection vehicle (“Formula 1”) was an aqueous vehicle consisting of 1.5% by volume carboxymethyl cellulose (CMC), 30% by volume sorbitol, and 0.2% by volume Tween 20 (polysorbate 20). The viscosity of the first injection vehicle was approximately 27 cp at 20° C. The second injection vehicle (“Formula 2”) was an aqueous vehicle consisting of 0.75% by volume CMC, 15% by volume sorbitol, and 0.2% by volume Tween 20 (polysorbate 20). The viscosity of the second injection vehicle was approximately 7 cp at 20° C.
  • The microparticle suspension was prepared as follows. The injection vehicle was aspirated into a 5 cc syringe through a needle. The vehicle was then injected into the glass vial containing the microparticles, and the needle was removed. The glass vial was then rolled between the palms until the microparticles were completely suspended, approximately one minute. The needle was reinserted into the vial so that the bevel of the needle was just through the septum with the opening facing toward the vial bottom. The vial was inverted and the suspension was withdrawn. The syringe was rotated 180° around its axis, and the remaining suspension was aspirated into the syringe.
  • Sieve screens with mesh opening sizes of 180, 212, 250, 300, 355, and 425 μm were used. The bevel of the syringe needle was placed on the mesh of the sieve screen so that the bevel was in full contact with the mesh. The needle was oriented so the opening of the needle was flush against the mesh of the screen. This prevented the mesh from entering the bevel, while maintaining the required restrictive area. The suspension was tried on the smallest sieve mesh first (highest screen resistance). If the suspension fouled the needle on this sieve mesh, the needle was unclogged by retracting the plunger of the syringe, depressing the plunger while the syringe was in the upward position, and passing an aliquot of suspension through the needle. The injection process was tried again using the next greater mesh size, and repeated until the suspension was successfully injected. All preparations were done in triplicate.
  • A three-factor Box-Behnken statistical designed experiment was constructed to evaluate the following independent variables: manufacturing bulk sieve size (125, 150, and 180 μm); needle ID (19 TW, 20 RW, and 22 RW gauge-ID of 19 TW (thin wall) equivalent to 18 RW (regular wall)); and suspension concentration (0.074, 0.096, and 0.138 w/w-corresponds to approximately 300 mg microparticle dose diluted with 4, 3, and 2 cc, respectively, of injection vehicle).
  • The following scoring system was used:
  • Score Result
    0 Needle Block
    1 Passes through a 425 μm screen
    2 Passes through a 355 μm screen
    3 Passes through a 300 μm screen
    4 Passes through a 250 μm screen
    5 Passes through a 212 μm screen
  • Table 1 below shows the score obtained for screen resistance tests using this scoring system for the 1 Kg and the 125 gm batches for each of the injection vehicles tested.
  • TABLE 1
    Mean Score
    Mfg Bulk Sieve Size n Formula 2 ≈ 7 cp Formula 1 ≈ 27 cp
    1 Kg Batches
    <180 9 2.3 2.3
    <125 9 3.4 3.7
    125 Gm Batches
    <180 6 1.5 2.0
    <150 6 3.0 2.8
    <125 6 3.0 2.5
  • As shown in Table 1, the screen resistance tests showed no significant difference between the two injection vehicles tested. Variations in suspension concentration and injection vehicle viscosity showed little to no effect. For the 1 Kg Batches, the mean scores were identical for the <180 manufacturing bulk sieve size, even though the viscosity of the Formula 1 injection vehicle was approximately 27 cp, and the viscosity of the Formula 2 injection vehicle was significantly less, approximately 7 cp. The scores for the other 1 Kg Batch and for the 125 Gm Batches varied modestly (0.2 to 0.5) between the two injection vehicles, thereby indicating that the injection vehicle viscosity had little effect. The tests conducted during the in vitro sieve test study show that in vitro injectability is strongly controlled by microparticle morphology and size. Needle gauge had a more modest effect. As will be discussed in more detail below, in vivo data supported the responses of microparticle morphology, size, and suspension concentration, but contradicted the effect of injection vehicle viscosity. Particularly, the in vivo studies showed a dramatic improvement in injectability with increased injection vehicle viscosity.
  • In Vivo Injectability Example 2 Pig Study
  • The injectability of risperidone microparticles was evaluated in Yorkshire weanling pigs. The study revealed that the IM injectability of risperidone microparticles is dependent upon injection vehicle viscosity and microparticle size. Reducing the injection vehicle viscosity led to a higher rate of injection failures due to needle clogging.
  • Risperidone microparticles were manufactured at the 125 gm scale in the same manner noted above for the in vitro sieve test study. The microparticles were sized to <125 μm and <150 μm using USA Standard Testing Sieves Nos. 120 and 100, respectively. The same two injection vehicles (Formula 1 and Formula 2) described above for the in vitro sieve test study were used in the pig study. 19 gauge TW×1.5 inch hypodermic needles (Becton-Dickinson Precisionglide® catalog number 305187) and 3 cc hypodermic syringes (Becton-Dickinson catalog number 309585) were used.
  • The injection experiments were conducted in male and female Yorkshire weanling pigs approximately 6 weeks in age (10-15 kg). The animals were anesthetized with low doses of Telazole and Xylazine and with halothane if needed. Injection sites were shaved and cleansed with betadine swabs prior to microparticle administration.
  • Injections to the hind quarters were administered to the biceps femoris in the upper hind limb. Injection sites in the legs were to the superficial digital flexor muscles in the forelimb, and to the cranial tibial muscle in the hindlimb.
  • Microparticles and injection vehicles were equilibrated to ambient temperature for at least 30 minutes. Using a 3 ml syringe equipped with a 1.5 inch 19 gauge thin wall needle, the prescribed volume of injection vehicle was withdrawn into the syringe, and injected into the vial containing the microparticles. The microparticles were suspended in the injection vehicle by orienting the vial horizontally and rolling it between the palms of the operator's hands. This was done without removing the needle/syringe from the septum. The time required to fully suspend the microparticles was approximately one minute.
  • The suspended microparticles were then withdrawn into the same needle/syringe and injected. Following insertion of the needle and prior to injection of the suspension, the syringe plunger was withdrawn slightly to confirm that the needle was located in the extravascular space. The time interval between aspiration of the suspension and injection was usually less than one minute. Injection regions were evaluated to pinpoint the site of microparticle deposition and to assess the distribution of microparticles in the tissue.
  • Table 2 below shows the effect on injectability as a function of injection vehicle viscosity, injection site, and microparticle concentration. A vehicle viscosity of “high” refers to the injection vehicle of Formula 1 described above, having a viscosity of approximately 27 cp at 20° C. Similarly, a vehicle viscosity of “low” refers to the injection vehicle of Formula 2 described above, having a viscosity of approximately 7 cp at 20° C. The size of the microparticles for the results shown in Table 2 is 180 μm.
  • TABLE 2
    Vehicle Microparticle
    Viscosity Dose Volume Site Failure rate
    High 160 mg 1 mL Hind quarter  0/10
    High 160 mg 1 mL Leg 1/8
    Low 160 mg 1 mL Hind quarter 4/7
    High 320 mg 1 mL Hind quarter 0/4
  • As can be seen from Table 2, increased failure rates were observed with the lower viscosity injection vehicle (4 failures with 7 injections), and when the injection site was in the leg (1 failure per 8 injections). The increased failure rate due to reduced viscosity was statistically significant at the 1% level (Fisher Exact Test).
  • Table 3 below summarizes injectability data for microparticles fractionated by size. Similar trends were observed when the system was stressed by decreasing the vehicle viscosity, with failure rates being higher with the <180 μm fraction. The <125 μm fraction and the <150 μm fraction were indistinguishable in terms of failure rate. The low viscosity data show statistically significant differences between <180 μm fraction and <150 μm fraction, and between <180 μm fraction and <125 μm fraction at 1% and 3% confidence levels, respectively (Fisher Exact Test).
  • TABLE 3
    Avg. %
    Max. delivered
    particle Vehicle Volume Failure (failed
    size (μm) Viscosity (mL) Site rate injections)1
    180 High 2.0 Leg 0/5 n/a
    150 High 2.0 Leg 0/5 n/a
    125 High 2.0 Leg 0/5 n/a
    180 High 1.0 Leg 2/4  0
    150 High 1.0 Leg 0/4 n/a
    125 High 1.0 Leg 0/4 n/a
    180 Low 2.0 Hind quarter  8/10 33
    150 Low 2.0 Hind quarter  2/10 18
    125 Low 2.0 Hind quarter  3/10 80
    1Average fraction of dose delivered prior to needle clog (failed injections only)
  • The in vivo pig study demonstrates a lower injectability failure rate with a higher viscosity injection vehicle, over a range of particle sizes. The in vitro sieve test study did not predict the viscosity dependence observed in the pig study.
  • Example 3 Sheep Study
  • A two-part sheep study was conducted to investigate in vivo injectability as a function of injection vehicle composition and viscosity, and suspension concentration. In Part I, risperidone microparticles were prepared at the 1 Kg scale using the process described below in Example 7. A batch of placebo microparticles was prepared using the process shown and described in U.S. Pat. No. 5,922,253, the entirety of which is incorporated herein by reference. The two types of microparticles were studied at two suspension concentrations of 150 and 300 mg/ml. Animal injectability tests were conducted using 3 cc syringes and 22 gauge TW×1.5 inch needles (Becton-Dickinson).
  • Five injection vehicles were used in Part I. The five injection vehicles were made using one or more of the three injection vehicle formulations shown below:
  • Vehicle A 0.9% Saline; 0.1% Tween 20
    Vehicle B 1.5% CMC; 30% Sorbitol; 0.2% Tween 20
    Vehicle C 3% CMC; 0.1% Tween 20; 0.9% Saline
  • Animal studies were conducted using domestic sheep weighing approximately 100-150 pounds. The animals were anesthetized with Telazole/Xylazine/Atropine intramuscularly and further supplemented with isofluorane gas (approximately 1-2%) during the injection procedure. Prior to injection, the animal's dorsal, gluteal, and upper leg regions were shaved and cleaned with alcohol. Injection sites were visualized prior to and during dosing using ultrasound (EI Medical).
  • The microparticles and injection vehicles were equilibrated to ambient temperature prior to dose suspension. Using a 3 cc syringe and 22 gauge thin-walled needle, the vehicle was aspirated and injected into the microparticle vial. The risperidone microparticles were suspended in 1 ml of vehicle at approximate concentrations of 150 or 300 mg/ml. Placebo microparticles were suspended in 2 or 1 ml of vehicle at approximate concentrations of 150 or 300 mg/ml. The vial was then agitated by hand for approximately 1 minute until the microparticles were suspended. The suspension was then aspirated back into the syringe using the same needle. Care was taken to recover the maximum amount of suspension from the vial. Preparation of dose suspensions was conducted randomly by three individuals.
  • All doses were injected by a single individual into the animal almost immediately after preparation. The rate of injection was maintained constant at approximately 5-10 seconds.
  • The results from Part I are shown in Table 4 below. Viscosities were determined by Brookfield Model LVT viscometer fitted with a UL adapter. Densities were measured for Vehicles A, B, and C. Densities for the combination vehicles made up of Vehicles A, B, and C were determined by interpolation based upon the ratio of Vehicles A, B, and C in the combination vehicle.
  • TABLE 4
    Viscosity Density Conc
    Vehicle (cp) (mg/ml) (mg/ml)2 Failures
    Vehicle A 1.0 1.01 150 8/10
    Vehicle B 24.0 1.11 150 1/10
    24.0 1.11 300 0/10
    Vehicle C 56.0 1.04 150 0/10
    56.0 1.04 150 1/101
    56.0 1.04 300 0/10
    3 Parts Vehicle B: 11.1 1.08 300 0/5 
    1 Part Vehicle A
    1 Part Vehicle B: 2.3 1.03 300 7/10
    3 Parts Vehicle A
    1Placebo Microparticles. All other results are risperidone microparticles.
    2mg microparticles/ml diluent
  • In order to isolate the effect of injection vehicle viscosity on injectability, additional sheep injectability tests (Part II) were conducted. The injectability results are shown below in Table 5. Viscosities were determined by Brookfield Model LVT viscometer fitted with a UL adapter. In Part II, the suspension concentration was fixed at 300 mg/ml. The tests in Part II were carried out using risperidone microparticles prepared in the same manner as in Part I, using the same injection protocol. The injection vehicles included Vehicle C and Vehicle A as described above, as well as injection vehicles prepared by diluting Vehicle C with Vehicle A. For example, the injection vehicle formulation having a viscosity of 22.9 cp is formulated by combining Vehicle C and Vehicle A in a 1:1 ratio, thereby forming Diluent 1.
  • TABLE 5
    Viscosity Density Conc
    Vehicle (cp) (mg/ml) (mg/ml) Failures
    Vehicle C 63.8 1.04 300 2/10
    1:1 Vehicle C:Diluent 1 37.6* 1.03 300 2/10
    1:1 Vehicle C:Vehicle A 22.9 1.03 300 1/10
    (Diluent 1)
    1:1 Diluent 1:Vehicle A 11.3 1.02 300 5/10
    (Diluent 2)
    1:1 Diluent 2:Vehicle A 1.4 1.01 300 7/10
    Vehicle A 1 1.01 300 10/10 
    *estimate, insufficient sample
  • The data for Parts I and II shown in Tables 4 and 5 clearly show that the injection vehicle viscosity has an effect on injectability. Viscosities of at least about 20 cp are necessary for successful and medically acceptable injectability rates. At viscosities of less than or equal to about 11 cp, in vivo injectability failures increase significantly.
  • The effect of a density enhancing agent can be seen by comparing the injectability failures using the vehicle in Table 4 having a viscosity of 11.1 cp with the vehicle in Table 5 having a viscosity of 11.3 cp. The viscosity of these two vehicles is nearly the same. However, the Table 4 vehicle had 0/5 failures while the Table 5 vehicle had 5/10 failures. The Table 4 vehicle has a higher density (1.08 mg/ml) compared to the Table 5 vehicle (1.02 mg/ml). The Table 4 vehicle includes a density enhancing agent, sorbitol, while the Table 5 vehicle contains no sorbitol or other density enhancing agent.
  • Example 4 Ex Vivo Injectability Tests
  • Injectability tests were conducted with several injection vehicles prepared at viscosities exceeding ˜50 cp. Injection vehicles having viscosities in excess of 50 cp were mixed, using a syringe-syringe mixing method described in more detail in Example 5 below, in which the viscosity enhancing agent was introduced after suspending the microparticles in the 50 cp vehicle.
  • Subcutaneous injections of blank (placebo) PLGA (poly(d,l-lactic-co-glycolic acid)) microparticles, having an approximate mass median diameter of 50 μm, were made into previously harvested pig skin using four injection vehicles having viscosities at ˜25° C. of approximately 53.1 to >1000 cp at the time of formulation. The vehicles were subsequently autoclaved before use, and the final viscosity (viscosity of the fluid phase of the injectable suspension) varied between approximately 5-60% from the nominal starting viscosity value. The most viscous injection vehicle was approximately 13 times the viscosity of the 50 cp formulation. In this ex vivo model, increasing the viscosity of the fluid phase of the injectable suspension decreased injection failure rate, even when microparticle concentration was raised from 175 to 250 mg/ml, at a needle size of 22 G. Maximal improvement in injectability, within this range of concentration and needle size, was achieved with injection vehicles having a viscosity of approximately 250 cp.
  • In another study, four injection vehicles having measured viscosities of 53 to 251 cp were evaluated for subcutaneous injectability in anesthetized pigs. Microparticle concentrations were 150 and 190 mg/ml. Injection failure was directly related to microparticle concentration, and inversely related to viscosity level. At 53 cp, approximately 50% of injections failed, while at higher viscosities, failures diminished. At the highest viscosity (251 cp), zero failures were recorded at both microparticle concentrations.
  • Example 5 Methods for Preparing Injectable Compositions
  • Methods for preparing injectable compositions in accordance with the present invention will now be described. In accordance with the present invention, microparticles are first mixed with an injection vehicle having suitable viscosity and wetting characteristics to achieve a homogeneous mono-particulate suspension. The viscosity of the fluid phase of the suspension is then changed, preferably increased, to achieve a viscosity that inhibits suspension separation and clogging under conditions of normal clinical use. In accordance with one method of the present invention, dry microparticles are mixed with an aqueous injection vehicle to form a first suspension. The first suspension is mixed with a viscosity enhancing agent to form a second suspension. The viscosity enhancing agent increases the viscosity of the fluid phase of the second suspension. The second suspension is then injected into a host.
  • One embodiment for carrying out such a method will now be described. Vialed dry microparticles are mixed with an aqueous injection vehicle having a viscosity less than about 60 cp at 20° C., preferably about 20-50 centipoise. The concentration of microparticles in the mixture is greater than about 30 mg/ml, preferably about 100-400 mg microparticles/ml. The mixture is agitated until a homogeneous suspension is formed. The homogeneous suspension is withdrawn into a first hypodermic syringe. The first syringe is connected to a second syringe containing a viscosity enhancing agent. A viscosity enhancing agent suitable for use with the present invention is sodium carboxymethyl cellulose (CMC), preferably having a viscosity of from about 1000 to about 2000 cp at 20° C. It should be understood that the present invention is not limited to the use of CMC as the viscosity enhancing agent, and other suitable viscosity enhancing agents may be used. The added volume of the viscosity enhancing agent is approximately 10-25% of the volume of the microparticle suspension.
  • The microparticle suspension and the viscosity enhancing agent are mixed to form the injectable composition by repeatedly passing the microparticle suspension and the viscosity enhancing agent between the first and second syringes. Such a syringe-syringe mixing method was used in the injectability tests described in Example 4 above. After mixing with the viscosity enhancing agent, the viscosity of the fluid phase of the microparticle suspension is from about 200 cp to about 600 cp at 20° C. A hypodermic needle is attached to the syringe containing the injectable composition, and the injectable composition is injected into a host in a manner well known to one of skill in the art.
  • An alternate embodiment for carrying out the method of the present invention will now be described. Dry microparticles are mixed with an aqueous injection vehicle having a viscosity of less than about 60 cp at 20° C. to form a suspension. The viscosity of the fluid phase of the suspension is changed in a manner that will be described in more detail below. The suspension that constitutes the injectable composition is withdrawn into a syringe, and the injectable composition is injected from the syringe into the host. Preferably, the viscosity of the fluid phase of the suspension is changed after the suspension has been withdrawn into the syringe.
  • In one aspect of this alternate embodiment, the viscosity is changed by changing the temperature of the fluid phase of the injectable suspension. The methods and techniques for changing the viscosity of a liquid by changing the temperature of the liquid are readily apparent to one skilled in the art. The temperature of the fluid phase of the suspension is changed until the desired viscosity of the fluid phase has been reached. The suspension now has the desired fluid phase viscosity for injection into a host, and constitutes the injectable composition. At this point, the suspension is withdrawn into the syringe and injected into the host. Alternatively, the suspension can be withdrawn into the syringe prior to changing the temperature of the fluid phase of the suspension to achieve the desired fluid phase viscosity. For example, an injection vehicle that comprises a polymer solution can be used as the viscosity of polymer solutions is temperature-dependent. A polymer solution can be used to suspend the microparticles under low-viscosity conditions suitable for wetting and suspension formation. Once the microparticles are suspended, the suspension is drawn up into a syringe. The temperature is then changed to induce higher viscosity in the injection vehicle constituting the fluid phase of the suspension, and the suspension having increased viscosity is injected into a host.
  • In another aspect of this alternate embodiment, the viscosity is changed by adding a viscosity enhancing agent to the suspension. The suspension is withdrawn into the syringe, and then the viscosity enhancing agent is added to the suspension in the syringe, thereby increasing the viscosity of the aqueous injection vehicle constituting the fluid phase of the suspension. The suspension now has the desired fluid phase viscosity for injection into a host, and constitutes the injectable composition. The suspension is then injected into the host. Preferably, the viscosity enhancing agent is added to the suspension immediately prior to injection into the host. Suitable viscosity enhancing agents include sodium carboxymethyl cellulose, polyvinylpyrrolidone (PVP), such as PLASDONE, available from GAF Chemicals Corp., Wayne, N.J., and hydroxypropylmethylcellulose (HPMC), such as Methocel, available from Dow Chemical Co., Midland, Mich. However, other viscosity enhancing agents may be used, as would be readily apparent to one of skill in the art.
  • In another embodiment of the invention, the injectable compositions of the present invention are prepared by providing microparticles that comprise a polymeric binder and that have a mass median diameter of at least about 10 μm. The mass median diameter of the microparticles is preferably less than about 250 μm, and more preferably, in the range of from about 20 μm to about 150 μm. Such microparticles can be made in the manner disclosed and described herein, or in any other manner known to one skilled in the art. An aqueous injection vehicle is provided. Such an aqueous injection vehicle can be made in the manner disclosed and described herein, or in any other manner known to one skilled in the art. The microparticles are suspended in the aqueous injection vehicle at a concentration of greater than about 30 mg/ml to form a suspension, the fluid phase of the suspension having a viscosity of at least 20 cp at 20° C.
  • In yet a further embodiment of the present invention, dry microparticles are mixed with an aqueous injection vehicle containing a viscosity enhancing agent to form a suspension. Suitable viscosity enhancing agents include sodium carboxymethyl cellulose, polyvinylpyrrolidone (PVP), such as PLASDONE, available from GAF Chemicals Corp., Wayne, N.J., and hydroxypropylmethylcellulose (HPMC), such as Methocel, available from Dow Chemical Co., Midland, Mich. However, other viscosity enhancing agents may be used, as would be readily apparent to one of skill in the art. The suspension is then dispensed into vials. The vials are lyophilized (or vacuum dried) to remove the water. Prior to injection, the vial contents are reconstituted with sterile water for injection in a quantity sufficient to achieve the desired viscosity for the fluid phase of the reconstituted injectable suspension. Preferably, the vial contents are reconstituted with a quantity of sterile water for injection sufficient to achieve a viscosity of a fluid phase of the injectable suspension that provides injectability of the composition through a needle ranging in diameter from 18-22 gauge.
  • Example 6 Injectable Compositions
  • The injectable compositions of the present invention will now be described. The injectable compositions of the present invention are suitable for injection through a needle into a host. In one embodiment, the injectable compositions comprise microparticles suspended in an aqueous injection vehicle. The microparticles preferably have a mass median diameter of at least about 10 μm to about 250 μm, preferably in the range of from about 20 μm to about 150 μm. However, it should be understood that the invention is not limited to microparticles in this size range, and that smaller or larger microparticles may also be used.
  • The microparticles preferably comprise a polymeric binder. Suitable polymeric binder materials include poly(glycolic acid), poly-d,l-lactic acid, poly-l-lactic acid, copolymers of the foregoing, poly(aliphatic carboxylic acids), copolyoxalates, polycaprolactone, polydioxanone, poly(ortho carbonates), poly(acetals), poly(lactic acid-caprolactone), polyorthoesters, poly(glycolic acid-caprolactone), polyanhydrides, polyphosphazines, albumin, casein, and waxes. Poly(d,l-lactic-co-glycolic acid) is commercially available from Alkermes, Inc. (Blue Ash, Ohio). A suitable product commercially available from Alkermes, Inc. is a 50:50 poly(d,l-lactic-co-glycolic acid) known as MEDISORB® 5050 DL. This product has a mole percent composition of 50% lactide and 50% glycolide. Other suitable commercially available products are MEDISORB® 6535 DL, 7525 DL, 8515 DL and poly(d,l-lactic acid) (100 DL). Poly(lactide-co-glycolides) are also commercially available from Boehringer Ingelheim (Germany) under its Resomer® mark, e.g., PLGA 50:50 (Resomer® RG 502), PLGA 75:25 (Resomer® RG 752) and d,l-PLA (Resomer® RG 206), and from Birmingham Polymers (Birmingham, Ala.). These copolymers are available in a wide range of molecular weights and ratios of lactic acid to glycolic acid.
  • One type of microparticle suitable for use with the present invention is a sustained-release microparticle that is biodegradable. However, it should be understood by one skilled in the art that the present invention is not limited to biodegradable or other types of sustained-release microparticles. As would be apparent to one skilled in the art, the molecular weight of the polymeric binder material for biodegradable microparticles is of some importance. The molecular weight should be high enough to permit the formation of satisfactory polymer coatings, i.e., the polymer should be a good film former. Usually, a satisfactory molecular weight is in the range of 5,000 to 500,000 daltons, preferably about 150,000 daltons. However, since the properties of the film are also partially dependent on the particular polymeric binder material being used, it is very difficult to specify an appropriate molecular weight range for all polymers. The molecular weight of the polymer is also important from the point of view of its influence upon the biodegradation rate of the polymer. For a diffusional mechanism of drug release, the polymer should remain intact until all of the drug is released from the microparticles and then degrade. The drug can also be released from the microparticles as the polymeric binder bioerodes. By an appropriate selection of polymeric materials a microparticle formulation can be made in which the resulting microparticles exhibit both diffusional release and biodegradation release properties. This is useful in according multiphasic release patterns.
  • The microparticles may include an active agent or other type of substance that is released from the microparticles into the host. Such active agents can include 1,2-benzazoles, more particularly, 3-piperidinyl-substituted 1,2-benzisoxazoles and 1,2-benzisothiazoles. The most preferred active agents of this kind are 3-[2-[4-(6-fluoro-1,2-benzisoxazol-3-yl)-1-piperidinyl]ethyl]-6,7,8,9-tetrahydro-2-methyl-4H-pyrido[1,2-a]pyrimidin-4-one (“risperidone”) and 3-[2-[4-(6-fluoro-1,2-benzisoxazol-3-yl)-1-piperidinyl]ethyl]-6,7,8,9-tetrahydro-9-hydroxy-2-methyl-4H-pyrido[1,2-a]pyrimidin-4-one (“9-hydroxyrisperidone”) and the pharmaceutically acceptable salts thereof. Risperidone (which term, as used herein, is intended to include its pharmaceutically acceptable salts) is most preferred. Risperidone can be prepared in accordance with the teachings of U.S. Pat. No. 4,804,663, the entirety of which is incorporated herein by reference. 9-hydroxyrisperidone can be prepared in accordance with the teachings of U.S. Pat. No. 5,158,952, the entirety of which is incorporated herein by reference.
  • Other biologically active agents include non-steroidal antifertility agents; parasympathomimetic agents; psychotherapeutic agents; tranquilizers; decongestants; sedative hypnotics; steroids; sulfonamides; sympathomimetic agents; vaccines; vitamins; antimalarials; anti-migraine agents; anti-Parkinson agents such as L-dopa; anti-spasmodics; anticholinergic agents (e.g. oxybutynin); antitussives; bronchodilators; cardiovascular agents such as coronary vasodilators and nitroglycerin; alkaloids; analgesics; narcotics such as codeine, dihydrocodienone, meperidine, morphine and the like; non-narcotics such as salicylates, aspirin, acetaminophen, d-propoxyphene and the like; opioid receptor antagonists, such as naltrexone and naloxone; antibiotics such as gentamycin, tetracycline and penicillins; anti-cancer agents; anti-convulsants; anti-emetics; antihistamines; anti-inflammatory agents such as hormonal agents, hydrocortisone, prednisolone, prednisone, non-hormonal agents, allopurinol, indomethacin, phenylbutazone and the like; prostaglandins and cytotoxic drugs.
  • Still other suitable active agents include estrogens, antibacterials; antifungals; antivirals; anticoagulants; anticonvulsants; antidepressants; antihistamines; and immunological agents.
  • Other examples of suitable biologically active agents include peptides and proteins, analogs, muteins, and active fragments thereof, such as immunoglobulins, antibodies, cytokines (e.g. lymphokines, monokines, chemokines), blood clotting factors, hemopoietic factors, interleukins (IL-2, IL-3, IL-4, IL-6), interferons (β-IFN, α-IFN and γ-IFN), erythropoietin, nucleases, tumor necrosis factor, colony stimulating factors (e.g., GCSF, GM-CSF, MCSF), insulin, enzymes (e.g., superoxide dismutase, tissue plasminogen activator), tumor suppressors, blood proteins, hormones and hormone analogs (e.g., growth hormone, adrenocorticotropic hormone and luteinizing hormone releasing hormone (LHRH)), vaccines (e.g., tumoral, bacterial and viral antigens); somatostatin; antigens; blood coagulation factors; growth factors (e.g., nerve growth factor, insulin-like growth factor); protein inhibitors, protein antagonists, and protein agonists; nucleic acids, such as antisense molecules; oligonucleotides; and ribozymes. Small molecular weight agents suitable for use in the invention include, antitumor agents such as bleomycin hydrochloride, carboplatin, methotrexate and adriamycin; antipyretic and analgesic agents; antitussives and expectorants such as ephedrine hydrochloride, methylephedrine hydrochloride, noscapine hydrochloride and codeine phosphate; sedatives such as chlorpromazine hydrochloride, prochlorperazine hydrochloride and atropine sulfate; muscle relaxants such as tubocurarine chloride; antiepileptics such as sodium phenyloin and ethosuximide; antiulcer agents such as metoclopramide; antidepressants such as clomipramine; antiallergic agents such as diphenhydramine; cardiotonics such as theophillol; antiarrhythmic agents such as propranolol hydrochloride; vasodilators such as diltiazem hydrochloride and bamethan sulfate; hypotensive diuretics such as pentolinium and ecarazine hydrochloride; antidiuretic agents such as metformin; anticoagulants such as sodium citrate and heparin; hemostatic agents such as thrombin, menadione sodium bisulfite and acetomenaphthone; antituberculous agents such as isoniazide and ethanbutol; hormones such as prednisolone sodium phosphate and methimazole.
  • The microparticles can be mixed by size or by type. However, it should be understood that the present invention is not limited to the use of biodegradable or other types of microparticles that contain an active agent. In one embodiment, the microparticles are mixed in a manner that provides for the delivery of active agent to the patient in a multiphasic manner and/or in a manner that provides different active agents to the patient at different times, or a mixture of active agents at the same time. For example, secondary antibiotics, vaccines, or any desired active agent, either in microparticle form or in conventional, unencapsulated form can be blended with a primary active agent and provided to the patient.
  • The microparticles are preferably suspended in the injection vehicle at a concentration of greater than about 30 mg/ml. In one embodiment, the microparticles are suspended at a concentration of from about 150 mg/ml to about 300 mg/ml. In another embodiment, the microparticles are suspended at a concentration of from about 100 mg/ml to about 400 mg/ml. However, it should be understood that the invention is not limited to a particular concentration.
  • The aqueous injection vehicle preferably has a viscosity of at least 20 cp at 20° C. In one embodiment, the injection vehicle has a viscosity greater than 50 cp and less than 60 cp at 20° C. The viscosity of the injection vehicle preferably provides injectability of the composition through a needle ranging in diameter from 18-22 gauge. As known to one skilled in the art, an 18 gauge regular wall (RW) needle has a nominal inner diameter (ID) of 0.033 in., and a 22 gauge regular wall needle has a nominal inner diameter of 0.016 in.
  • The injection vehicle may comprise a viscosity enhancing agent. A preferred viscosity enhancing agent is sodium carboxymethyl cellulose, although other suitable viscosity enhancing agents may also be used. The injection vehicle may also comprise a density enhancing agent that increases the density of the injection vehicle. A preferred density enhancing agent is sorbitol, although other suitable density enhancing agents may also be used. The injection vehicle may also comprise a tonicity adjusting agent to adjust the tonicity to preclude toxicity problems and improve biocompatibility. A preferred tonicity adjusting agent is sodium chloride, although other suitable tonicity adjusting agents may also be used.
  • The injection vehicle may also comprise a wetting agent to ensure complete wetting of the microparticles by the injection vehicle. Preferred wetting agents include polysorbate 20 (Tween 20), polysorbate 40 (Tween 40), and polysorbate 80 (Tween 80).
  • One preferred injection vehicle is an aqueous injection vehicle that comprises 1.5% sodium carboxymethyl cellulose, 30% sorbitol, and 0.2% polysorbate 20. Another preferred injection vehicle is an aqueous injection vehicle that comprises 3% sodium carboxymethyl cellulose, 0.9% saline, and 0.1% polysorbate 20.
  • Example 7 1 Kg Process
  • A process for preparing microparticles containing risperidone as the active agent will now be described. The following 1 Kg process (400 grams of active agent and 600 grams of polymer) is for a theoretical drug loading of the microparticles of 40%. The actual drug loading that is achieved by the process described below ranges from about 35% to about 39%.
  • A drug solution is prepared by dissolving 400 grams of risperidone (Janssen Pharmaceutica, Beerse, Belgium) in 1267 grams of benzyl alcohol to form a 24 wt. % drug solution. A polymer solution is formed by dissolving 600 grams of MEDISORB® 7525 DL polymer (Alkermes, Inc., Blue Ash, Ohio) in 3000 grams of ethyl acetate to form a 16.7 wt. % polymer solution. The drug solution and the polymer solution are combined to form a first, discontinuous phase.
  • The second, continuous phase is prepared by preparing a 30 liter solution of 1% PVA, the PVA acting as an emulsifier. To this is added 2086 grams of ethyl acetate to form a 6.5 wt. % solution of ethyl acetate.
  • The two phases are combined using a static mixer, such as a ½″ Kenics static mixer available from Chemineer, Inc., North Andover, Mass. A total flow rate of 3 L/min generally provides microparticle size distributions with a mass median diameter (MMD) in the range of about 80-90μ. The ratio of continuous phase to discontinuous phase is 5:1 (v/v). The length of the static mixer can vary from about 9 inches to about 88 inches. Lengths greater than about 48 inches results in the greatest percent yield in a microparticle size range of 25-150μ.
  • The quench liquid is 2.5% solution of ethyl acetate and water-for-injection (WFI) at 5-10° C. The volume of the quench liquid is 0.25 L per gram of batch size. The quench step is carried out for a time period greater than about 4 hours, with stirring of the microparticles in the quench tank.
  • After completion of the quench step, the microparticles are transferred to a collecting, de-watering, and drying device. The microparticles are rinsed using a chilled (approximately 5° C.) 17 liter 25% ethanol solution. The microparticles are dried, and then re-slurried in a re-slurry tank using a 25% ethanol solution (extraction medium) maintained at a temperature lower than the Tg (glass transition temperature) of the microparticles. The microparticles are then transferred back to the quench tank for washing for a time period of at least 6 hours with another extraction medium (25% ethanol solution) that is maintained at a temperature higher than the Tg of the microparticles. The Tg of the microparticles is about 18° C. (about room temperature), and the temperature of the extraction medium in the quench tank is greater than about 18° C., preferably 25°±1° C.
  • The microparticles are transferred back to the collecting, de-watering, and drying device for de-watering and final drying. Drying continues for a time period greater than about 16 hours.
  • CONCLUSION
  • While various embodiments of the present invention have been described above, it should be understood that they have been presented by way of example only, and not limitation. The present invention is not limited to controlled release microparticle injectable suspensions, nor is it limited to a particular active agent, polymer or solvent, nor is the present invention limited to a particular scale or batch size. Thus, the breadth and scope of the present invention should not be limited by any of the above-described exemplary embodiments, but should be defined only in accordance with the following claims and their equivalents.

Claims (12)

1. A composition suitable for injection through a needle into a host, comprising:
microparticles comprising a polymeric binder and an active agent encapsulated within the polymeric binder, the microparticles having a mass median diameter of at least about 10 μm; and
an injection vehicle, wherein the microparticles are suspended in the injection vehicle at a concentration of greater than about 30 mg/ml to form a suspension, wherein a fluid phase of the suspension has a viscosity greater than about 20 cp and less than about 600 cp at 20° C., wherein the viscosity of the fluid phase of the suspension provides injectability of the composition through a needle into a host,
wherein the polymeric binder is selected from the group consisting of poly(glycolic acid), poly-d,l-lactic acid; poly-l-lactic acid, copolymers of the foregoing, poly(aliphatic carboxylic acids), copolyoxalates, polycaprolactone, polydioxanone, poly(ortho carbonates), poly(acetals), poly(lactic acid-caprolactone), polyorthoesters, poly(glycolic acid-caprolactone), polyanhydrides, polyphosphazines, albumin, and casein,
wherein the injection vehicle comprises a viscosity enhancing agent comprising sodium carboxymethyl cellulose; a wetting agent selected from the group consisting of polysorbate 20, polysorbate 40, and polysorbate 80; and a tonicity adjusting agent comprising sodium chloride, and
wherein the viscosity of the fluid phase of the suspension provides injectability of the composition into a host through a needle of medically acceptable size.
2. The composition of claim 1, wherein the active agent is selected from the group consisting of risperidone, 9-hydroxyrisperidone, and pharmaceutically acceptable salts thereof.
3. The composition of claim 1, wherein the polymeric binder is poly(d,l-lactide-co-glycolide) having a molar ratio of lactide to glycolide in the range of from about 85:15 to about 50:50.
4. The composition of claim 1, wherein the microparticles are suspended in the injection vehicle at a concentration of from about 100 mg/ml to about 400 mg/ml.
5. The composition of claim 1, wherein the viscosity of the fluid phase of the suspension provides injectability of the composition into the host through a needle ranging in diameter from 18-22 gauge.
6. The composition of claim 1, wherein the injection vehicle is aqueous.
7. A method of making a composition suitable for injection through a needle into a host, comprising:
(a) providing microparticles comprising a polymeric binder and an active agent encapsulated within the polymeric binder, the microparticles having a mass median diameter of at least about 10 μm;
(b) providing an injection vehicle having a viscosity of at least 20 cp at 20° C.; and
(c) suspending the microparticles in the injection vehicle at a concentration of greater than about 30 mg/ml to form a suspension, wherein the viscosity of a fluid phase of the suspension is in the range of from about 20 cp to about 600 cp at 20° C., wherein the viscosity of the fluid phase of the suspension provides injectability of the composition into a host through a needle of medically acceptable size, wherein the polymeric binder is selected from the group consisting of poly(glycolic acid), poly-d,l-lactic acid; poly-l-lactic acid, copolymers of the foregoing, poly(aliphatic carboxylic acids), copolyoxalates, polycaprolactone, polydioxanone, poly(ortho carbonates), poly(acetals), poly(lactic acid-caprolactone), polyorthoesters, poly(glycolic acid-caprolactone), polyanhydrides, polyphosphazines, albumin, and casein, and
wherein the viscosity enhancing agent comprises sodium carboxymethyl cellulose.
8. The method of claim 7, wherein the active agent is selected from the group consisting of risperidone, 9-hydroxyrisperidone, and pharmaceutically acceptable salts thereof.
9. The method of claim 7, wherein the polymeric binder is poly(d,l-lactide-co-glycolide) having a molar ratio of lactide to glycolide in the range of from about 85:15 to about 50:50.
10. The method of claim 7, wherein the viscosity of the fluid phase of the suspension provides injectability of the composition into the host through a needle ranging in diameter from 18-22 gauge.
11. The method of claim 7, wherein the microparticles are suspended in the injection vehicle at a concentration of from about 100 mg/ml to about 400 mg/ml.
12. The method of claim 7, wherein the injection vehicle is aqueous.
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Cited By (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20100069426A1 (en) * 2008-06-16 2010-03-18 Zale Stephen E Therapeutic polymeric nanoparticles with mTor inhibitors and methods of making and using same
US20100068286A1 (en) * 2008-06-16 2010-03-18 Greg Troiano Drug Loaded Polymeric Nanoparticles and Methods of Making and Using Same
US20100226986A1 (en) * 2008-12-12 2010-09-09 Amy Grayson Therapeutic Particles Suitable for Parenteral Administration and Methods of Making and Using Same
US8211473B2 (en) 2009-12-11 2012-07-03 Bind Biosciences, Inc. Stable formulations for lyophilizing therapeutic particles
US8318211B2 (en) 2008-06-16 2012-11-27 Bind Biosciences, Inc. Therapeutic polymeric nanoparticles comprising vinca alkaloids and methods of making and using same
US8518963B2 (en) 2009-12-15 2013-08-27 Bind Therapeutics, Inc. Therapeutic polymeric nanoparticle compositions with high glass transition temperature or high molecular weight copolymers
US9198874B2 (en) 2008-12-15 2015-12-01 Bind Therapeutics, Inc. Long circulating nanoparticles for sustained release of therapeutic agents
US9877923B2 (en) 2012-09-17 2018-01-30 Pfizer Inc. Process for preparing therapeutic nanoparticles
US9895378B2 (en) 2014-03-14 2018-02-20 Pfizer Inc. Therapeutic nanoparticles comprising a therapeutic agent and methods of making and using the same
US10092524B2 (en) 2008-06-11 2018-10-09 Edge Therapeutics, Inc. Compositions and their use to treat complications of aneurysmal subarachnoid hemorrhage
US10568842B2 (en) * 2017-08-18 2020-02-25 Lance L. Gooberman Anti-inflammatory pharmaceutical compositions and methods of administration

Families Citing this family (122)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
UA72189C2 (en) 1997-11-17 2005-02-15 Янссен Фармацевтика Н.В. Aqueous suspensions of 9-hydroxy-risperidone fatty acid esters provided in submicron form
US6770478B2 (en) * 2000-02-10 2004-08-03 The Regents Of The University Of California Erythrocytic cells and method for preserving cells
US6495164B1 (en) * 2000-05-25 2002-12-17 Alkermes Controlled Therapeutics, Inc. I Preparation of injectable suspensions having improved injectability
US6824822B2 (en) 2001-08-31 2004-11-30 Alkermes Controlled Therapeutics Inc. Ii Residual solvent extraction method and microparticles produced thereby
US7758890B2 (en) 2001-06-23 2010-07-20 Lyotropic Therapeutics, Inc. Treatment using dantrolene
KR100525189B1 (en) * 2002-10-10 2005-10-31 메디칸(주) Injectable solid material for human soft tissue volume replacement
US7731947B2 (en) 2003-11-17 2010-06-08 Intarcia Therapeutics, Inc. Composition and dosage form comprising an interferon particle formulation and suspending vehicle
EP1589901A4 (en) 2002-12-20 2006-08-09 Generipharm Inc Intracutaneous injection
US7658998B2 (en) * 2003-01-22 2010-02-09 Alkermes Controlled Therapeutics, Inc. Method of preparing sustained release microparticles
CA2516667C (en) * 2003-03-04 2012-05-29 Lyotropic Therapeutics, Inc. Treatment using dantrolene
WO2004103342A2 (en) * 2003-05-16 2004-12-02 Alkermes Controlled Therapeutics, Inc. Injectable sustained release compositions
US20050032811A1 (en) 2003-08-06 2005-02-10 Josiah Brown Methods for administering aripiprazole
US8092527B2 (en) * 2003-09-03 2012-01-10 Brennan William A System and method for breast augmentation
US7169180B2 (en) * 2003-09-03 2007-01-30 Brennan William A System and method for breast augmentation
SI1660009T1 (en) 2003-09-03 2015-07-31 Miscon Trading S.A. Methods for the treatment of endometriosis
US7906125B2 (en) * 2003-09-18 2011-03-15 Boston Scientific Scimed, Inc. Solid or semi-solid therapeutic formulations
US20050064045A1 (en) * 2003-09-18 2005-03-24 Sheng-Ping Zhong Injectable therapeutic formulations
UA82561C2 (en) 2003-10-23 2008-04-25 Оцука Фармасьютикалз Ко., Лтд. Controlled release sterile aripiprazole formulation for injections, method for preparing aripiprazole formulation, and method for treating schizophrenia
WO2005042026A1 (en) * 2003-10-31 2005-05-12 Wakamoto Pharmaceutical Co., Ltd. Water-based composition undergoing reversible thermogelation
KR101040415B1 (en) 2004-04-15 2011-06-09 알케르메스,인코포레이티드 Polymer-based sustained release device
US7456254B2 (en) * 2004-04-15 2008-11-25 Alkermes, Inc. Polymer-based sustained release device
US20060110423A1 (en) * 2004-04-15 2006-05-25 Wright Steven G Polymer-based sustained release device
US20050260272A1 (en) * 2004-05-05 2005-11-24 Alkermes Controlled Therapeutics, Inc. Method of forming microparticles that include a bisphosphonate and a polymer
MXPA06014095A (en) * 2004-06-04 2007-08-07 Camurus Ab Liquid depot formulations.
ITMI20041245A1 (en) * 2004-06-22 2004-09-22 Ibsa Inst Biochimique Sa INJECTABLE PHARMACEUTICAL COMPOSITIONS INCLUDING DICLOFENAC SODIUM AND B-CYCLODESTRINE
EP1679065A1 (en) * 2005-01-07 2006-07-12 OctoPlus Sciences B.V. Controlled release compositions for interferon based on PEGT/PBT block copolymers
US11246913B2 (en) 2005-02-03 2022-02-15 Intarcia Therapeutics, Inc. Suspension formulation comprising an insulinotropic peptide
WO2006083761A2 (en) 2005-02-03 2006-08-10 Alza Corporation Solvent/polymer solutions as suspension vehicles
US8318210B2 (en) * 2005-02-28 2012-11-27 Neos Therapeutics, Lp Compositions and methods of making sustained release liquid formulations
US7862552B2 (en) 2005-05-09 2011-01-04 Boston Scientific Scimed, Inc. Medical devices for treating urological and uterine conditions
US20060251581A1 (en) * 2005-05-09 2006-11-09 Mcintyre Jon T Method for treatment of uterine fibroid tumors
US8263109B2 (en) * 2005-05-09 2012-09-11 Boston Scientific Scimed, Inc. Injectable bulking compositions
PT2347762T (en) 2005-08-19 2019-06-17 Amylin Pharmaceuticals Llc Exendin for treating diabetes and reducing body weight
US8852638B2 (en) 2005-09-30 2014-10-07 Durect Corporation Sustained release small molecule drug formulation
WO2007061896A1 (en) 2005-11-17 2007-05-31 Zogenix, Inc. Delivery of viscous formulations by needle-free injection
US20090038701A1 (en) * 2006-01-17 2009-02-12 Baxter International Inc. Device, system and method for mixing
NZ572003A (en) 2006-05-30 2010-07-30 Intarcia Therapeutics Inc Two-piece, internal-channel osmotic delivery system flow modulator with spiral fluid channel
WO2008021133A2 (en) 2006-08-09 2008-02-21 Intarcia Therapeutics, Inc. Osmotic delivery systems and piston assemblies
JP4941977B2 (en) * 2007-04-11 2012-05-30 大蔵製薬株式会社 Oral jelly-like pharmaceutical composition of benzisoxazole derivative
NZ580447A (en) 2007-04-23 2011-06-30 Intarcia Therapeutics Inc Suspension formulations of insulinotropic peptides and uses thereof
US10010612B2 (en) 2007-05-25 2018-07-03 Indivior Uk Limited Sustained delivery formulations of risperidone compounds
CN101842084B (en) 2007-07-26 2014-11-05 亚克蒂斯Ip有限公司 Microparticles comprising PCL and uses thereof
TWI410255B (en) * 2007-07-31 2013-10-01 Otsuka Pharma Co Ltd Methods for producing aripiprazole suspension and freeze-dried formulation
US20090061005A1 (en) * 2007-08-21 2009-03-05 Actavis Group Ptc Ehf Paliperidone Polymorphs
US9987221B2 (en) * 2007-08-23 2018-06-05 Boston Scientific Scimed, Inc. Injectable hydrogel compositions
US20100286121A1 (en) * 2007-11-05 2010-11-11 Rohrs Brian R Water-Immiscible Materials as Vehicles for Drug Delivery
US8343140B2 (en) 2008-02-13 2013-01-01 Intarcia Therapeutics, Inc. Devices, formulations, and methods for delivery of multiple beneficial agents
EP2756756B1 (en) 2008-04-28 2016-01-06 Zogenix, Inc. Novel formulations for treatment of migraine
ES2552646T3 (en) 2008-05-21 2015-12-01 Amylin Pharmaceuticals, Inc. Exendins to lower cholesterol and triglycerides
US9216152B2 (en) * 2008-06-27 2015-12-22 Tepha, Inc. Injectable delivery of microparticles and compositions therefore
CN104248623B (en) 2008-09-04 2020-04-03 安米林药品有限责任公司 Sustained release formulations using non-aqueous carriers
US20100063879A1 (en) * 2008-09-05 2010-03-11 Yellowpages.Com Llc Systems and Methods to Selectively Provide Information Based on User Interest
NZ624569A (en) 2009-09-28 2016-01-29 Intarcia Therapeutics Inc Rapid establishment and/or termination of substantial steady-state drug delivery
CA2791278C (en) 2010-02-25 2015-11-24 The Johns Hopkins University Sustained delivery of therapeutic agents to an eye compartment
WO2012012460A1 (en) 2010-07-19 2012-01-26 Xeris Pharmaceuticals, Inc. Stable glucagon formulations for the treatment of hypoglycemia
WO2012039979A2 (en) 2010-09-10 2012-03-29 The Johns Hopkins University Rapid diffusion of large polymeric nanoparticles in the mammalian brain
CN107625728A (en) 2010-10-18 2018-01-26 大日本住友制药株式会社 Injectable sustained release preparation
US9327037B2 (en) 2011-02-08 2016-05-03 The Johns Hopkins University Mucus penetrating gene carriers
US20120208755A1 (en) 2011-02-16 2012-08-16 Intarcia Therapeutics, Inc. Compositions, Devices and Methods of Use Thereof for the Treatment of Cancers
KR101978527B1 (en) 2011-03-10 2019-09-03 엑스에리스 파머수티클스, 인크. Stable formulations for parenteral injection of peptide drugs
AU2012332556B2 (en) 2011-10-31 2016-05-26 Xeris Pharmaceuticals, Inc. Formulations for the treatment of diabetes
US9415020B2 (en) 2012-01-19 2016-08-16 The Johns Hopkins University Nanoparticle formulations with enhanced mucosal penetration
AU2013232300B2 (en) 2012-03-16 2015-12-17 The Johns Hopkins University Non-linear multiblock copolymer-drug conjugates for the delivery of active agents
WO2013138343A1 (en) 2012-03-16 2013-09-19 The Johns Hopkins University Controlled release formulations for the delivery of hif-1 inhibitors
US11596599B2 (en) 2012-05-03 2023-03-07 The Johns Hopkins University Compositions and methods for ophthalmic and/or other applications
US9827191B2 (en) 2012-05-03 2017-11-28 The Johns Hopkins University Compositions and methods for ophthalmic and/or other applications
US9056057B2 (en) 2012-05-03 2015-06-16 Kala Pharmaceuticals, Inc. Nanocrystals, compositions, and methods that aid particle transport in mucus
EP3808339A1 (en) 2012-05-03 2021-04-21 Kala Pharmaceuticals, Inc. Pharmaceutical nanoparticles showing improved mucosal transport
CA2872519C (en) 2012-05-04 2017-09-05 The Johns Hopkins University Lipid-based drug carriers for rapid penetration through mucus linings
US9125805B2 (en) 2012-06-27 2015-09-08 Xeris Pharmaceuticals, Inc. Stable formulations for parenteral injection of small molecule drugs
RS61377B1 (en) 2012-07-26 2021-02-26 Camurus Ab Opioid formulations
WO2014124006A1 (en) 2013-02-05 2014-08-14 The Johns Hopkins University Nanoparticles for magnetic resonance imaging tracking and methods of making and using thereof
US9018162B2 (en) 2013-02-06 2015-04-28 Xeris Pharmaceuticals, Inc. Methods for rapidly treating severe hypoglycemia
RU2016136430A (en) * 2014-02-11 2018-03-15 Др. Редди'С Лабораторис Лтд. Parenteral compositions of celecoxib
WO2015127389A1 (en) 2014-02-23 2015-08-27 The Johns Hopkins University Hypotonic enema formulations and methods of use
US11129940B2 (en) 2014-08-06 2021-09-28 Xeris Pharmaceuticals, Inc. Syringes, kits, and methods for intracutaneous and/or subcutaneous injection of pastes
JP6858698B2 (en) * 2014-08-28 2021-04-21 ザ ジェネラル ホスピタル コーポレイション Injectable slurry and its manufacturing method and usage
US11504322B2 (en) 2014-08-28 2022-11-22 The General Hospital Corporation Injectable slurries and methods of manufacturing the same
US11471401B2 (en) 2014-08-28 2022-10-18 The General Hospital Corporation Injectable slurries and methods of manufacturing the same
US9889085B1 (en) 2014-09-30 2018-02-13 Intarcia Therapeutics, Inc. Therapeutic methods for the treatment of diabetes and related conditions for patients with high baseline HbA1c
BR112017012706A2 (en) 2014-12-15 2018-03-13 The Johns Hopkins University sunitinib formulations and methods for their use in the treatment of eye disorders
AU2016211696B2 (en) 2015-01-27 2018-05-10 The Johns Hopkins University Hypotonic hydrogel formulations for enhanced transport of active agents at mucosal surfaces
US20160303281A1 (en) 2015-04-17 2016-10-20 Rochal Industries, Llc Composition and kits for pseudoplastic microgel matrices
EP3297654B1 (en) 2015-05-22 2021-07-07 The Board of Trustees of the Leland Stanford Junior University Treatment of post-bariatric hypoglycemia with exendin(9-39)
MX2017015504A (en) 2015-06-03 2018-05-15 Intarcia Therapeutics Inc Implant placement and removal systems.
US9649364B2 (en) 2015-09-25 2017-05-16 Xeris Pharmaceuticals, Inc. Methods for producing stable therapeutic formulations in aprotic polar solvents
AU2016274442B2 (en) 2015-06-10 2021-08-05 Evonik Operations Gmbh Process for preparing a powder comprising a human coagulation factor protein and a lactic acid polymer
EP3340982B1 (en) 2015-08-26 2021-12-15 Achillion Pharmaceuticals, Inc. Compounds for treatment of immune and inflammatory disorders
AR106018A1 (en) 2015-08-26 2017-12-06 Achillion Pharmaceuticals Inc ARYL, HETEROARYL AND HETEROCYCLIC COMPOUNDS FOR THE TREATMENT OF MEDICAL DISORDERS
US20170079985A1 (en) 2015-09-21 2017-03-23 Teva Pharmaceuticals International Gmbh Sustained release olanzapine formulations
US11590205B2 (en) 2015-09-25 2023-02-28 Xeris Pharmaceuticals, Inc. Methods for producing stable therapeutic glucagon formulations in aprotic polar solvents
CN105310980A (en) * 2015-10-09 2016-02-10 北京万全德众医药生物技术有限公司 Paliperidone controlled-release suspension oral liquid and its preparation method
EP3373978A4 (en) 2015-11-12 2019-06-26 Graybug Vision, Inc. Aggregating microparticles for therapy
FI3377041T3 (en) 2015-11-16 2023-11-30 Medincell S A A method for morselizing and/or targeting pharmaceutically active principles to synovial tissue
SG10201913504XA (en) 2016-02-26 2020-03-30 Massachusetts Gen Hospital Medical ice slurry production and delivery systems and methods
WO2017152014A1 (en) 2016-03-04 2017-09-08 Eiger Biopharmaceuticals, Inc. Treatment of hyperinsulinemic hypoglycemia with exendin-4 derivatives
CN109562107A (en) 2016-05-10 2019-04-02 C4医药公司 Heterocycle degron body for target protein degradation
WO2017197046A1 (en) 2016-05-10 2017-11-16 C4 Therapeutics, Inc. C3-carbon linked glutarimide degronimers for target protein degradation
EP3454862A4 (en) 2016-05-10 2020-02-12 C4 Therapeutics, Inc. Spirocyclic degronimers for target protein degradation
SG11201810102SA (en) 2016-05-16 2018-12-28 Intarcia Therapeutics Inc Glucagon-receptor selective polypeptides and methods of use thereof
USD860451S1 (en) 2016-06-02 2019-09-17 Intarcia Therapeutics, Inc. Implant removal tool
USD840030S1 (en) 2016-06-02 2019-02-05 Intarcia Therapeutics, Inc. Implant placement guide
EP3448389B1 (en) 2016-06-27 2021-09-29 Achillion Pharmaceuticals, Inc. Quinazoline and indole compounds to treat medical disorders
EP3858835A1 (en) 2016-07-01 2021-08-04 G1 Therapeutics, Inc. Pyrimidine-based antiproliferative agents
WO2018057977A1 (en) 2016-09-23 2018-03-29 Delpor, Inc. Stable compositions for incretin mimetic compounds
EP3541366A4 (en) 2016-11-21 2020-08-05 Eiger Biopharmaceuticals, Inc. Buffered formulations of exendin (9-39)
IL307966A (en) 2017-01-03 2023-12-01 Intarcia Therapeutics Inc Methods comprising continuous administration of a glp-1 receptor agonist and co-adminstration of a drug
US10350200B2 (en) * 2017-01-23 2019-07-16 Southwest Research Institute Aqueous suspensions of oximes for autoinjectors
EP3600258A1 (en) 2017-03-20 2020-02-05 Teva Pharmaceuticals International GmbH Sustained release olanzapine formulaitons
EP3600324A4 (en) 2017-03-23 2020-12-09 Graybug Vision, Inc. Drugs and compositions for the treatment of ocular disorders
RU2019139817A (en) 2017-05-10 2021-06-10 Грейбуг Вижн, Инк. DELAYED RELEASE MICROPARTICLES AND THEIR SUSPENSIONS FOR DRUG THERAPY
AU2018275686B2 (en) 2017-06-02 2024-02-01 Xeris Pharmaceuticals, Inc. Precipitation resistant small molecule drug formulations
CN109589304A (en) * 2017-10-01 2019-04-09 万特制药(海南)有限公司 Risperidone oral administration solution and preparation method thereof
CN111902141A (en) 2018-03-26 2020-11-06 C4医药公司 Glucocerebroside binders for IKAROS degradation
US11000479B2 (en) 2018-10-15 2021-05-11 Chong Kun Dang Pharmaceutical Corp. Injectable long-acting naltrexone microparticle compositions
EP3866773A4 (en) 2018-10-16 2022-10-26 Georgia State University Research Foundation, Inc. Carbon monoxide prodrugs for the treatment of medical disorders
AU2021204918A1 (en) * 2020-01-03 2022-07-21 Privo Technologies, Inc. Systems and pharmaceutical compositions for treatment by direct injection of a targeted population of cells
BE1028769B1 (en) * 2020-11-02 2022-05-31 Flanders Color Nv WATER BASED LIQUID RINSE LACQUER
WO2022153262A1 (en) 2021-01-18 2022-07-21 Anton Frenkel Pharmaceutical dosage form
US11241330B1 (en) 2021-04-02 2022-02-08 Brixton Biosciences, Inc. Apparatus for creation of injectable slurry
CA3227324A1 (en) 2021-07-06 2023-01-12 Mark Hasleton Treatment of serotonin reuptake inhibitor withdrawal syndrome
CN114146020B (en) * 2022-02-10 2022-04-29 中国远大集团有限责任公司 Injection beauty product and preparation method and application thereof

Citations (47)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3523906A (en) * 1962-07-11 1970-08-11 Gevaert Photo Prod Nv Process for encapsulating water and compounds in aqueous phase by evaporation
US3691090A (en) * 1969-01-16 1972-09-12 Fuji Photo Film Co Ltd Encapsulation method
US3700215A (en) * 1970-10-21 1972-10-24 Hardman Inc Mixing and dispensing device
US3737337A (en) * 1970-03-04 1973-06-05 Bayer Ag Process for the production of microgranulates
US3773919A (en) * 1969-10-23 1973-11-20 Du Pont Polylactide-drug mixtures
US3891570A (en) * 1972-01-26 1975-06-24 Toyo Jozo Kk Process for preparing microcapsules
US3960757A (en) * 1973-06-27 1976-06-01 Toyo Jozo Co., Ltd. Process for encapsulation of medicaments
US4029782A (en) * 1975-04-28 1977-06-14 Eli Lilly And Company Cefazolin suspension for parenteral administration
US4221862A (en) * 1975-06-27 1980-09-09 Fuji Photo Film Co., Ltd. Method of producing finely divided polymer particles
US4384975A (en) * 1980-06-13 1983-05-24 Sandoz, Inc. Process for preparation of microspheres
US4389330A (en) * 1980-10-06 1983-06-21 Stolle Research And Development Corporation Microencapsulation process
US4530840A (en) * 1982-07-29 1985-07-23 The Stolle Research And Development Corporation Injectable, long-acting microparticle formulation for the delivery of anti-inflammatory agents
US4803075A (en) * 1986-06-25 1989-02-07 Collagen Corporation Injectable implant composition having improved intrudability
US4818517A (en) * 1986-01-24 1989-04-04 Akzo N.V. Pharmaceutical preparation for obtaining a highly viscose hydrogel or suspension
US4940588A (en) * 1984-10-30 1990-07-10 Elan Corporation Controlled release powder and process for its preparation
US5066436A (en) * 1989-01-04 1991-11-19 Gist-Brocades N.V. Process for microencapsulation
US5385738A (en) * 1983-10-14 1995-01-31 Sumitomo Pharmaceuticals Company, Ltd. Sustained-release injection
US5407609A (en) * 1989-05-04 1995-04-18 Southern Research Institute Microencapsulation process and products therefrom
WO1995013799A1 (en) * 1993-11-19 1995-05-26 Alkermes Controlled Therapeutics Inc. Ii Preparation of biodegradable microparticles containing a biologically active agent
US5428024A (en) * 1992-02-28 1995-06-27 Collagen Corporation High concentration homogenized collagen compositions
US5429824A (en) * 1992-12-15 1995-07-04 Eastman Kodak Company Use of tyloxapole as a nanoparticle stabilizer and dispersant
US5478564A (en) * 1990-02-22 1995-12-26 Teva Pharmaceutical Industries, Ltd. Preparation of microparticles for controlled release of water-soluble substances
US5486362A (en) * 1991-05-07 1996-01-23 Dynagen, Inc. Controlled, sustained release delivery system for treating drug dependency
US5540912A (en) * 1992-03-30 1996-07-30 Alza Corporation Viscous suspensions of controlled-release drug particles
US5541172A (en) * 1991-06-28 1996-07-30 Endorecherche, Inc. Controlled release systems and low dose androgens
US5612346A (en) * 1993-04-28 1997-03-18 Janssen Pharmaceutica N.V. Risperidone pamoate
US5627158A (en) * 1990-11-02 1997-05-06 Cho-Chung; Yoon S. Antisense oligonucleotides of human regulatory subunit RI-.sub.α of camp dependent protein kinases for the treatment of cancer
US5631021A (en) * 1983-11-04 1997-05-20 Takeda Chemical Industries, Ltd. Method for producing microcapsule
US5650173A (en) * 1993-11-19 1997-07-22 Alkermes Controlled Therapeutics Inc. Ii Preparation of biodegradable microparticles containing a biologically active agent
US5654010A (en) * 1992-12-02 1997-08-05 Alkermes, Inc. Composition for sustained release of human growth hormone
US5656299A (en) * 1992-11-17 1997-08-12 Yoshitomi Pharmaceutical Industries, Ltd. Sustained release microsphere preparation containing antipsychotic drug and production process thereof
US5656297A (en) * 1992-03-12 1997-08-12 Alkermes Controlled Therapeutics, Incorporated Modulated release from biocompatible polymers
US5658593A (en) * 1992-01-16 1997-08-19 Coletica Injectable compositions containing collagen microcapsules
US5688801A (en) * 1993-11-19 1997-11-18 Janssen Pharmaceutica Method of inhibiting neurotransmitter activity using microencapsulated 3-piperidiny2-substituted 1,2-benzisoxazoles and 1,2-benzisothiazoles
WO1997044039A1 (en) * 1996-05-20 1997-11-27 Janssen Pharmaceutica N.V. Aqueous suspensions of 9-hydroxyrisperidone fatty acid esters
US5747058A (en) * 1995-06-07 1998-05-05 Southern Biosystems, Inc. High viscosity liquid controlled delivery system
US5792477A (en) * 1996-05-07 1998-08-11 Alkermes Controlled Therapeutics, Inc. Ii Preparation of extended shelf-life biodegradable, biocompatible microparticles containing a biologically active agent
US5858410A (en) * 1994-11-11 1999-01-12 Medac Gesellschaft Fur Klinische Spezialpraparate Pharmaceutical nanosuspensions for medicament administration as systems with increased saturation solubility and rate of solution
US5922025A (en) * 1992-02-11 1999-07-13 Bristol-Myers Squibb Company Soft tissue augmentation material
US5942253A (en) * 1995-10-12 1999-08-24 Immunex Corporation Prolonged release of GM-CSF
US6034175A (en) * 1992-05-28 2000-03-07 Zeneca Limited Salts of peptides with carboxy-terminated polyesters
US6306425B1 (en) * 1999-04-09 2001-10-23 Southern Research Institute Injectable naltrexone microsphere compositions and their use in reducing consumption of heroin and alcohol
US6372245B1 (en) * 1992-12-29 2002-04-16 Insite Vision Incorporated Plasticized bioerodible controlled delivery system
US6496164B1 (en) * 1998-05-18 2002-12-17 Fujitsu Limited Plasma display device and method of driving plasma display panel, having first and second representing units
US6495155B1 (en) * 1999-08-27 2002-12-17 Southern Research Institute Injectable opioid partial agonist or opioid antagonist microparticle compositions and their use in reducing consumption of abused substances
US6555544B2 (en) * 1997-11-17 2003-04-29 Janssen Pharmaceutica, N.V. Aqueous suspensions of submicron 9-hydroxyrisperidone fatty acid esters
US6667061B2 (en) * 2000-05-25 2003-12-23 Alkermes Controlled Therapeutics, Inc. Preparation of injectable suspensions having improved injectability

Family Cites Families (19)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
IL51791A0 (en) * 1976-04-14 1977-05-31 Exxon Research Engineering Co New injectable medicinal compositions
JPS60112713A (en) * 1983-11-21 1985-06-19 Sumitomo Chem Co Ltd Useful slow-releasing injection
JPH0657658B2 (en) * 1985-04-11 1994-08-03 住友製薬株式会社 Sustained release formulation
US4804663A (en) 1985-03-27 1989-02-14 Janssen Pharmaceutica N.V. 3-piperidinyl-substituted 1,2-benzisoxazoles and 1,2-benzisothiazoles
WO1989003678A1 (en) 1987-10-30 1989-05-05 Stolle Research & Development Corporation Low residual solvent microspheres and microencapsulation process
US5158952A (en) 1988-11-07 1992-10-27 Janssen Pharmaceutica N.V. 3-[2-[4-(6-fluoro-1,2-benzisoxozol-3-yl)-1-piperidinyl]ethyl]-6,7,8,9 tetrahydro-9-hydroxy-2-methyl-4H-pyrido [1,2-a]pyrimidin-4-one, compositions and method of use
US5019400A (en) 1989-05-01 1991-05-28 Enzytech, Inc. Very low temperature casting of controlled release microspheres
IT1243390B (en) 1990-11-22 1994-06-10 Vectorpharma Int PHARMACEUTICAL COMPOSITIONS IN THE FORM OF PARTICLES SUITABLE FOR THE CONTROLLED RELEASE OF PHARMACOLOGICALLY ACTIVE SUBSTANCES AND PROCEDURE FOR THEIR PREPARATION.
US20020009443A1 (en) * 1991-12-02 2002-01-24 Vanitha Ramakrishman Inhibitory immunoglobulin polypeptides to human pdgf beta receptor
US5453425A (en) 1994-07-11 1995-09-26 Janssen Pharmaceutica N.V. Risperidone oral formulation
US5922253A (en) 1995-05-18 1999-07-13 Alkermes Controlled Therapeutics, Inc. Production scale method of forming microparticles
US5904935A (en) 1995-06-07 1999-05-18 Alza Corporation Peptide/protein suspending formulations
HUP9700322A3 (en) * 1995-06-09 2001-03-28 Euro Celtique Sa Formulations and methods for providing prolonged local anesthesia
SE505146C2 (en) * 1995-10-19 1997-06-30 Biogram Ab Particles for delayed release
DK0885002T3 (en) * 1996-03-04 2011-08-22 Penn State Res Found Materials and methods for enhancing cellular internalization
IL129951A0 (en) 1997-07-02 2000-02-29 Euro Celtique Sa Prolonged anesthesia in joints and body spaces
GB9718986D0 (en) 1997-09-09 1997-11-12 Danbiosyst Uk Controlled release microsphere delivery system
US6143314A (en) * 1998-10-28 2000-11-07 Atrix Laboratories, Inc. Controlled release liquid delivery compositions with low initial drug burst
US6194006B1 (en) * 1998-12-30 2001-02-27 Alkermes Controlled Therapeutics Inc. Ii Preparation of microparticles having a selected release profile

Patent Citations (55)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3523906A (en) * 1962-07-11 1970-08-11 Gevaert Photo Prod Nv Process for encapsulating water and compounds in aqueous phase by evaporation
US3691090A (en) * 1969-01-16 1972-09-12 Fuji Photo Film Co Ltd Encapsulation method
US3773919A (en) * 1969-10-23 1973-11-20 Du Pont Polylactide-drug mixtures
US3737337A (en) * 1970-03-04 1973-06-05 Bayer Ag Process for the production of microgranulates
US3700215A (en) * 1970-10-21 1972-10-24 Hardman Inc Mixing and dispensing device
US3891570A (en) * 1972-01-26 1975-06-24 Toyo Jozo Kk Process for preparing microcapsules
US3960757A (en) * 1973-06-27 1976-06-01 Toyo Jozo Co., Ltd. Process for encapsulation of medicaments
US4029782A (en) * 1975-04-28 1977-06-14 Eli Lilly And Company Cefazolin suspension for parenteral administration
US4221862A (en) * 1975-06-27 1980-09-09 Fuji Photo Film Co., Ltd. Method of producing finely divided polymer particles
US4384975A (en) * 1980-06-13 1983-05-24 Sandoz, Inc. Process for preparation of microspheres
US4389330A (en) * 1980-10-06 1983-06-21 Stolle Research And Development Corporation Microencapsulation process
US4530840A (en) * 1982-07-29 1985-07-23 The Stolle Research And Development Corporation Injectable, long-acting microparticle formulation for the delivery of anti-inflammatory agents
US5385738A (en) * 1983-10-14 1995-01-31 Sumitomo Pharmaceuticals Company, Ltd. Sustained-release injection
US5631021A (en) * 1983-11-04 1997-05-20 Takeda Chemical Industries, Ltd. Method for producing microcapsule
US4940588A (en) * 1984-10-30 1990-07-10 Elan Corporation Controlled release powder and process for its preparation
US4818517A (en) * 1986-01-24 1989-04-04 Akzo N.V. Pharmaceutical preparation for obtaining a highly viscose hydrogel or suspension
US4803075A (en) * 1986-06-25 1989-02-07 Collagen Corporation Injectable implant composition having improved intrudability
US5066436A (en) * 1989-01-04 1991-11-19 Gist-Brocades N.V. Process for microencapsulation
US5407609A (en) * 1989-05-04 1995-04-18 Southern Research Institute Microencapsulation process and products therefrom
US5478564A (en) * 1990-02-22 1995-12-26 Teva Pharmaceutical Industries, Ltd. Preparation of microparticles for controlled release of water-soluble substances
US5627158A (en) * 1990-11-02 1997-05-06 Cho-Chung; Yoon S. Antisense oligonucleotides of human regulatory subunit RI-.sub.α of camp dependent protein kinases for the treatment of cancer
US5486362A (en) * 1991-05-07 1996-01-23 Dynagen, Inc. Controlled, sustained release delivery system for treating drug dependency
US5541172A (en) * 1991-06-28 1996-07-30 Endorecherche, Inc. Controlled release systems and low dose androgens
US5658593A (en) * 1992-01-16 1997-08-19 Coletica Injectable compositions containing collagen microcapsules
US5922025A (en) * 1992-02-11 1999-07-13 Bristol-Myers Squibb Company Soft tissue augmentation material
US5428024A (en) * 1992-02-28 1995-06-27 Collagen Corporation High concentration homogenized collagen compositions
US5656297A (en) * 1992-03-12 1997-08-12 Alkermes Controlled Therapeutics, Incorporated Modulated release from biocompatible polymers
US5540912A (en) * 1992-03-30 1996-07-30 Alza Corporation Viscous suspensions of controlled-release drug particles
US6034175A (en) * 1992-05-28 2000-03-07 Zeneca Limited Salts of peptides with carboxy-terminated polyesters
US5656299A (en) * 1992-11-17 1997-08-12 Yoshitomi Pharmaceutical Industries, Ltd. Sustained release microsphere preparation containing antipsychotic drug and production process thereof
US5871778A (en) * 1992-11-17 1999-02-16 Yoshitomi Pharmaceutical Industries, Ltd. Sustained release microsphere preparation containing antipsychotic drug
US5654010A (en) * 1992-12-02 1997-08-05 Alkermes, Inc. Composition for sustained release of human growth hormone
US6500448B1 (en) * 1992-12-02 2002-12-31 Alkermes Controlled Therapeutics, Inc. Composition for sustained release of human growth hormone
US5667808A (en) * 1992-12-02 1997-09-16 Alkermes, Inc. Composition for sustained release of human growth hormone
US5429824A (en) * 1992-12-15 1995-07-04 Eastman Kodak Company Use of tyloxapole as a nanoparticle stabilizer and dispersant
US6372245B1 (en) * 1992-12-29 2002-04-16 Insite Vision Incorporated Plasticized bioerodible controlled delivery system
US5612346A (en) * 1993-04-28 1997-03-18 Janssen Pharmaceutica N.V. Risperidone pamoate
US5965168A (en) * 1993-11-19 1999-10-12 Alkermes Controlled Therapeutics, Inc. Ii Microencapsulated 3-piperidinyl-substituted 1,2-benzisoxazoles and 1,2-benzisothiazoles
US5654008A (en) * 1993-11-19 1997-08-05 Alkermes Controlled Therapeutics Inc. Ii Preparation of biodegradable microparticles containing a biologically active agent
WO1995013799A1 (en) * 1993-11-19 1995-05-26 Alkermes Controlled Therapeutics Inc. Ii Preparation of biodegradable microparticles containing a biologically active agent
US5770231A (en) * 1993-11-19 1998-06-23 Alkermes Controlled Therapeutics, Inc. Ii Microencapsulated 3-piperidinyl-substituted 1,2-benzisoxazoles 1,2-benzisothiazoles
US5650173A (en) * 1993-11-19 1997-07-22 Alkermes Controlled Therapeutics Inc. Ii Preparation of biodegradable microparticles containing a biologically active agent
US5688801A (en) * 1993-11-19 1997-11-18 Janssen Pharmaceutica Method of inhibiting neurotransmitter activity using microencapsulated 3-piperidiny2-substituted 1,2-benzisoxazoles and 1,2-benzisothiazoles
US5858410A (en) * 1994-11-11 1999-01-12 Medac Gesellschaft Fur Klinische Spezialpraparate Pharmaceutical nanosuspensions for medicament administration as systems with increased saturation solubility and rate of solution
US5747058A (en) * 1995-06-07 1998-05-05 Southern Biosystems, Inc. High viscosity liquid controlled delivery system
US5942253A (en) * 1995-10-12 1999-08-24 Immunex Corporation Prolonged release of GM-CSF
US5916598A (en) * 1996-05-07 1999-06-29 Alkermes Controlled Therapeutics Inc. Ii Preparation of biodegradable, biocompatible microparticles containing a biologically active agent
US5792477A (en) * 1996-05-07 1998-08-11 Alkermes Controlled Therapeutics, Inc. Ii Preparation of extended shelf-life biodegradable, biocompatible microparticles containing a biologically active agent
US6077843A (en) * 1996-05-20 2000-06-20 Janssen Pharmaceutica, N.V. Aqueous suspensions of 9-hydroxyrisperidone fatty acid esters
WO1997044039A1 (en) * 1996-05-20 1997-11-27 Janssen Pharmaceutica N.V. Aqueous suspensions of 9-hydroxyrisperidone fatty acid esters
US6555544B2 (en) * 1997-11-17 2003-04-29 Janssen Pharmaceutica, N.V. Aqueous suspensions of submicron 9-hydroxyrisperidone fatty acid esters
US6496164B1 (en) * 1998-05-18 2002-12-17 Fujitsu Limited Plasma display device and method of driving plasma display panel, having first and second representing units
US6306425B1 (en) * 1999-04-09 2001-10-23 Southern Research Institute Injectable naltrexone microsphere compositions and their use in reducing consumption of heroin and alcohol
US6495155B1 (en) * 1999-08-27 2002-12-17 Southern Research Institute Injectable opioid partial agonist or opioid antagonist microparticle compositions and their use in reducing consumption of abused substances
US6667061B2 (en) * 2000-05-25 2003-12-23 Alkermes Controlled Therapeutics, Inc. Preparation of injectable suspensions having improved injectability

Cited By (45)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US10092524B2 (en) 2008-06-11 2018-10-09 Edge Therapeutics, Inc. Compositions and their use to treat complications of aneurysmal subarachnoid hemorrhage
US8617608B2 (en) 2008-06-16 2013-12-31 Bind Therapeutics, Inc. Drug loaded polymeric nanoparticles and methods of making and using same
US9393310B2 (en) 2008-06-16 2016-07-19 Bind Therapeutics, Inc. Drug loaded polymeric nanoparticles and methods of making and using same
US20100069426A1 (en) * 2008-06-16 2010-03-18 Zale Stephen E Therapeutic polymeric nanoparticles with mTor inhibitors and methods of making and using same
US8609142B2 (en) 2008-06-16 2013-12-17 Bind Therapeutics, Inc. Drug loaded polymeric nanoparticles and methods of making and using same
US20100068286A1 (en) * 2008-06-16 2010-03-18 Greg Troiano Drug Loaded Polymeric Nanoparticles and Methods of Making and Using Same
US8293276B2 (en) 2008-06-16 2012-10-23 Bind Biosciences, Inc. Drug loaded polymeric nanoparticles and methods of making and using same
US8318208B1 (en) 2008-06-16 2012-11-27 Bind Biosciences, Inc. Drug loaded polymeric nanoparticles and methods of making and using same
US8318211B2 (en) 2008-06-16 2012-11-27 Bind Biosciences, Inc. Therapeutic polymeric nanoparticles comprising vinca alkaloids and methods of making and using same
US9579386B2 (en) 2008-06-16 2017-02-28 Pfizer Inc. Drug loaded polymeric nanoparticles and methods of making and using same
US8420123B2 (en) 2008-06-16 2013-04-16 Bind Biosciences, Inc. Drug loaded polymeric nanoparticles and methods of making and using same
US9579284B2 (en) 2008-06-16 2017-02-28 Pfizer Inc. Therapeutic polymeric nanoparticles with mTOR inhibitors and methods of making and using same
US8603534B2 (en) 2008-06-16 2013-12-10 Bind Therapeutics, Inc. Drug loaded polymeric nanoparticles and methods of making and using same
US9351933B2 (en) 2008-06-16 2016-05-31 Bind Therapeutics, Inc. Therapeutic polymeric nanoparticles comprising vinca alkaloids and methods of making and using same
US9375481B2 (en) 2008-06-16 2016-06-28 Bind Therapeutics, Inc. Drug loaded polymeric nanoparticles and methods of making and using same
US8206747B2 (en) 2008-06-16 2012-06-26 Bind Biosciences, Inc. Drug loaded polymeric nanoparticles and methods of making and using same
US8613954B2 (en) 2008-06-16 2013-12-24 Bind Therapeutics, Inc. Drug loaded polymeric nanoparticles and methods of making and using same
US8613951B2 (en) 2008-06-16 2013-12-24 Bind Therapeutics, Inc. Therapeutic polymeric nanoparticles with mTor inhibitors and methods of making and using same
US8663700B2 (en) 2008-06-16 2014-03-04 Bind Therapeutics, Inc. Drug loaded polymeric nanoparticles and methods of making and using same
US8623417B1 (en) 2008-06-16 2014-01-07 Bind Therapeutics, Inc. Therapeutic polymeric nanoparticles with mTOR inhibitors and methods of making and using same
US20100068285A1 (en) * 2008-06-16 2010-03-18 Zale Stephen E Drug Loaded Polymeric Nanoparticles and Methods of Making and Using Same
US8652528B2 (en) 2008-06-16 2014-02-18 Bind Therapeutics, Inc. Drug loaded polymeric nanoparticles and methods of making and using same
US8905997B2 (en) 2008-12-12 2014-12-09 Bind Therapeutics, Inc. Therapeutic particles suitable for parenteral administration and methods of making and using same
US20100226986A1 (en) * 2008-12-12 2010-09-09 Amy Grayson Therapeutic Particles Suitable for Parenteral Administration and Methods of Making and Using Same
US8563041B2 (en) 2008-12-12 2013-10-22 Bind Therapeutics, Inc. Therapeutic particles suitable for parenteral administration and methods of making and using same
US9198874B2 (en) 2008-12-15 2015-12-01 Bind Therapeutics, Inc. Long circulating nanoparticles for sustained release of therapeutic agents
US9308179B2 (en) 2008-12-15 2016-04-12 Bind Therapeutics, Inc. Long circulating nanoparticles for sustained release of therapeutic agents
US9498443B2 (en) 2009-12-11 2016-11-22 Pfizer Inc. Stable formulations for lyophilizing therapeutic particles
US8357401B2 (en) 2009-12-11 2013-01-22 Bind Biosciences, Inc. Stable formulations for lyophilizing therapeutic particles
US8956657B2 (en) 2009-12-11 2015-02-17 Bind Therapeutics, Inc. Stable formulations for lyophilizing therapeutic particles
US8916203B2 (en) 2009-12-11 2014-12-23 Bind Therapeutics, Inc. Stable formulations for lyophilizing therapeutic particles
US8211473B2 (en) 2009-12-11 2012-07-03 Bind Biosciences, Inc. Stable formulations for lyophilizing therapeutic particles
US8637083B2 (en) 2009-12-11 2014-01-28 Bind Therapeutics, Inc. Stable formulations for lyophilizing therapeutic particles
US8603535B2 (en) 2009-12-11 2013-12-10 Bind Therapeutics, Inc. Stable formulations for lyophilizing therapeutic particles
US9872848B2 (en) 2009-12-11 2018-01-23 Pfizer Inc. Stable formulations for lyophilizing therapeutic particles
US9835572B2 (en) 2009-12-15 2017-12-05 Pfizer Inc. Therapeutic polymeric nanoparticle compositions with high glass transition temperature or high molecular weight copolymers
US9295649B2 (en) 2009-12-15 2016-03-29 Bind Therapeutics, Inc. Therapeutic polymeric nanoparticle compositions with high glass transition temperature or high molecular weight copolymers
US8518963B2 (en) 2009-12-15 2013-08-27 Bind Therapeutics, Inc. Therapeutic polymeric nanoparticle compositions with high glass transition temperature or high molecular weight copolymers
US8912212B2 (en) 2009-12-15 2014-12-16 Bind Therapeutics, Inc. Therapeutic polymeric nanoparticle compositions with high glass transition temperature or high molecular weight copolymers
US9877923B2 (en) 2012-09-17 2018-01-30 Pfizer Inc. Process for preparing therapeutic nanoparticles
US9895378B2 (en) 2014-03-14 2018-02-20 Pfizer Inc. Therapeutic nanoparticles comprising a therapeutic agent and methods of making and using the same
US10071100B2 (en) 2014-03-14 2018-09-11 Pfizer Inc. Therapeutic nanoparticles comprising a therapeutic agent and methods of making and using the same
US10568842B2 (en) * 2017-08-18 2020-02-25 Lance L. Gooberman Anti-inflammatory pharmaceutical compositions and methods of administration
US20200138725A1 (en) * 2017-08-18 2020-05-07 Lance L. Gooberman Anti-inflammatory pharmaceutical compositions and methods of administration
US11033510B2 (en) * 2017-08-18 2021-06-15 Lance L. Gooberman Anti-inflammatory pharmaceutical compositions and methods of administration

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