Patent Application
20070190145
The present invention relates to modified-release dosage forms comprising one or more timed, pulsatile-release bead populations comprising a weakly basic nitrogen (N)-containing selective serotonin 5-HT3 blocking agent having a pKa in the range of from about 5 to 14 and a solubility of not more than 200 μg/mL at a pH of 6.8, and one or more pharmaceutically acceptable organic acids. The dosage form exhibits comparable release profiles of both the active and the organic acid after a predetermined delay (lag time) when dissolution tested by United States Pharmacopoeia (USP) dissolution methodology using a two-stage dissolution medium (first 2 hours in 0. 1N HCl followed by testing in a buffer at pH 6.8). In accordance with another aspect of the invention, oral drug delivery systems to target PK (pharmacokinetics, i.e., plasma concentration-time) profiles suitable for a once-daily dosing regimen are disclosed.
Many therapeutic agents are most effective when made available at constant rates at or near the absorption sites. The absorption of therapeutic agents thus made available generally results in desired plasma concentrations leading to maximum efficacy, and minimum toxic side effects. Much effort has been devoted to developing sophisticated drug delivery systems such as osmotic devices for oral application. However, there are instances where maintaining a constant blood level of a drug is not desirable. For example, a major objective of chronotherapy for cardiovascular diseases is to deliver the drug in higher concentrations during the time of greatest need, e.g., the early morning hours, and in lesser concentrations when the need is less, e.g., during the late evening and early sleep hours. In addition to a properly designed drug delivery system, the time of administration is equally important. The unique pharmacokinetic profile needed can be calculated using computer simulation and modeling techniques based on the knowledge of pharmacokinetic parameters, solubility, absorption along the gastrointestinal tract and elimination half-life.
While the orally administered pharmaceutical dosage form passes through the human digestive tract, the drug should be released from the dosage form and be available in solution form at or near the site for absorption from the gastrointestinal (GI) tract to occur. The rate at which the drug goes into solution and is released from a dosage form is important to the kinetics of drug absorption. The dosage form and hence the active ingredient is subjected to varying pHs during the transit, i.e., pH varying from about 1.2 (stomach pH during fasting but may vary between 1.2 and 4.0 upon consumption of food) to about 7.4 (bile pH: 7.0-7.4 and intestinal pH: 5 to 7). Moreover, transit time of a dosage form in individual parts of the digestive tract may vary significantly depending on its size and prevailing local conditions. Other factors that influence drug absorption include physicochemical properties of the drug substance itself such as pKa, solubility, crystalline energy, and specific surface area. The prevailing local conditions that play an important role include properties of luminal contents (pH, surface tension, volume, agitation and buffer capacity) and changes following the ingestion of food. Consequently, it is often difficult to achieve drug release at constant rates.
Basic and acidic drugs exhibit pH-dependent solubility profiles varying by more than 2 orders of magnitude in the physiological pH range. The most difficult candidates to work with are weakly basic pharmaceutically actives, which are practically insoluble at a pH>6 and require high doses to be therapeutically effective. Upon entering into the intestinal region, part of the drug released from the dosage form may precipitate in the hostile pH environment unless the rate of absorption is faster than the rate of drug release. Alternatively, the drug may remain in the supersaturated solution state facilitated by the presence of bile salts and lecithin in the gut. A supersaturation well over an order of magnitude higher than the aqueous solubility has been evident in the prior art. In the event of precipitation, there is evidence of redissolution for absorption at a slower phase.
Functional polymer membranes comprising suitable combinations of synthetic polymers such as water-soluble (e.g., Povidone), water-insoluble (e.g., ethylcellulose insoluble at physiological pHs), gastrosoluble (e.g., Eudragit EPO) or enterosoluble (e.g., gastric-resistant hypromellose phthalate) polymers, have been applied on tablet or pellet cores comprising the active and one or more solubilizers to achieve drug release at constant rates with limited success. Development of pharmaceutical compositions of actives highly water soluble at acidic or basic pHs using pharmaceutically acceptable buffer acids, buffer acid salts, and mixtures thereof, to provide drug release at substantially constant rates have been described. Organic acids have been used to improve bioavailability, to reduce inter- and intra-subject variability, and to minimize food effect in weakly basic pharmaceutical actives. Multi-particulate dosage forms comprising weakly basic drugs to provide extended-release profiles are also described in the literature. These dosage forms are typically obtained by granulating or layering the drug with one or more organic acids and coating with a combination of water-insoluble and water-soluble or enteric polymers.
Although the drug release in these disclosures could be extended moderately, they suffered from two disadvantages, viz., failure to maintain adequate plasma profile to achieve a once-daily dosing regimen and partial to complete in situ formation of the salt form, thus creating a new chemical entity. Even when the organic acid containing cores were coated with a sustained-release polymer membrane, the delivery system failed to prolong the release of the acid for continued dissolution and resulting absorption of the active to provide adequate plasma levels at 24 hrs following oral ingestion. Furthermore, many weakly basic drugs are known to form salts in the presence of organic acids, especially when dissolved in common solvents for drug layering or during granulation. Even in dosage forms wherein the organic acid and the drug layers are separated by a sustained-release (SR) membrane, the drug layering formulation contains an organic acid. Consequently, the active in the finished dosage exists in the partially or fully neutralized salt form. This is not an acceptable situation from regulatory considerations. The regulatory agencies may consider these actives as new drug entities. Thus there is an unmet need to develop drug delivery systems comprising weakly basic drugs with a pKa in the range of from about 5 to 14 and requiring high doses and organic acids in an unaltered form to release the actives so as to maintain target plasma concentrations of Cmax and Cmin in order to be suitable for once-daily dosing regimens. After extensive investigations, it was surprisingly discovered that this unmet need can be met by preventing the organic acid and the weakly basic active agent from coming into contact with each other to form a salt during processing and/or in the dosage form during storage, prior to dropping into an in vitro dissolution medium or prior to oral administration. This could be achieved by applying a dissolution rate-controlling SR membrane between the acid layer on the inert cores and the drug layer applied onto the acid-containing cores to isolate these two components and also an SR and/or a TPR (lag-time coating) membrane on the IR beads in order to synchronize the acid release with that of the drug.
The present invention provides pharmaceutical compositions and methods for creating pulsatile delivery systems, which involves preventing a weakly basic nitrogen (N)-containing selective serotonin 5-HT3 blocking agent having a pKa in the range of from about 5 to 14 and a solubility of not more than 200 μg/mL at a pH of 6.8, and a pharmaceutically acceptable organic acid from coming into contact to form an acid addition compound. Furthermore, the dosage forms described herein provide target drug-release profiles by solubilizing the drug prior to releasing it into the hostile intestinal environment wherein the drug is practically insoluble, thereby enhancing the probability of achieving acceptable plasma concentration at 24 hour post-dosing in order to be suitable for a once-daily dosing regimen. The invention is particularly useful as disclosed in Provisional Patent Application Ser. No. 60/762,766 to provide dosage forms for a twice- or once-daily dosing regimen of weakly basic nitrogen (N)-containing therapeutic agents having a pKa in the range of from about 5 to 14 (typically soluble at acidic pHs, but poorly to practically insoluble at neutral and alkaline pHs) and an elimination half-life of about 2 hours or longer, by delivering the active in solution form throughout the gastrointestinal tract.
Another embodiment of the invention relates to a multiparticulate pharmaceutical composition containing one or more coated bead populations comprising a weakly basic nitrogen (N)-containing selective serotonin 5-HT3 blocking agent with a solubility of not more than about 200 μg/mL, more particularly not more than about 100 μg/mL at pH 6.8 and a ratio of optimal highest dose to the solubility at pH 6.8 of at least about 100. For example, the dosing regimen for ondansetron, the active in Zofran® (IR tablet) with a solubility of about 0.05 mg/mL at pH 6.8, is typically 8 mg twice- or thrice-a-day and the optimal highest dose is 16 or 24 mg, the ratio of optimal highest dose (mg) to the solubility (mg/mL) at pH 6.8 would be 320. The multiparticulate composition prepared in accordance with one aspect of the present invention will comprise organic acid-containing cores coated with an SR (sustained-release or barrier) membrane, on which a weakly basic therapeutic agent with a pKa in the range of from about 5 to 14, is layered and further coated with an SR membrane and/or a lag-time membrane such that both the organic acid and the weakly basic therapeutic agent exhibit comparable drug-release profiles.
Multiparticulate compositions prepared in accordance with one aspect of the present invention comprise one or more coated bead populations exhibiting similar composite release profiles of both the organic acid and the weakly basic nitrogen (N)-containing selective serotonin 5-HT3 blocking agent when tested for dissolution using United States Pharmacopoeia Apparatus 1 (baskets@100 rpm) or Apparatus 2 (paddles @50 rpm) and a two-stage dissolution methodology (testing in 700 mL of 0.1N HCl (hydrochloric acid) for the first 2 hours and thereafter in 900 mL at pH 6.8 obtained by adding 200 mL of a pH modifier). Another embodiment of the invention relates to a multiparticulate pharmaceutical composition comprising one or more coated bead populations exhibiting the acid-release profile which is more particularly slower in comparison to that of the weakly basic active in order to avoid undissolved active being left behind inside the coated beads.
A multiparticulate pharmaceutical composition in accordance with one aspect of the invention comprises coated bead populations of a weakly basic nitrogen (N)-containing selective serotonin 5-HT3 blocking agent with a pKa in the range of from about 5 to 14 comprising:
The compositions in accordance with particular aspects of the invention typically exhibit desired or target release profiles of both the active and organic acid following a pre-determined lag-time of at least 2 hours when tested for drug and/or organic acid release using the 2-stage dissolution methodology described above.
A pharmaceutical composition of a weakly basic, nitrogen (N)-containing selective serotonin 5-HT3 blocking agent with a solubility of not more than about 200 μg/mL at pH 6.8 and a ratio of optimal highest dose to solubility at pH 6.8 of not less than about 100 such as ondansetron hydrochloride dihydrate may be prepared by filling the corresponding bead populations into a hard gelatin capsule or compressing into a conventional tablet or in the ODT (orally disintegrating tablet) form in accordance with certain embodiments of the present invention.
A pharmaceutical composition of a weakly basic nitrogen (N)-containing selective serotonin 5-HT3 blocking agent in the ODT form prepared in accordance with another embodiment of the present invention disintegrates on contact with saliva in the buccal cavity within about 60 seconds forming a smooth, easy-to-swallow suspension (no gritty or chalky aftertaste). The pharmaceutical composition of a weakly basic pharmaceutical active in the ODT form, which may comprise one or more coated bead populations with an average particle size of not more than about 400 μm, such as taste-masked microcapsules comprising drug-containing cores (crystals, granules, pellets, beads and the like), SR bead and timed, pulsatile-release (TPR) bead populations comprising SR coated acid-containing cores. Taste-masking may be achieved by any of the well-known prior art disclosures. The ODT may also include rapidly-dispersing microgranules with an average particle size of not more than about 400 μm, or in some embodiments not more than about 300 μm, comprising a disintegrant (e.g., Crospovidone, crosslinked polyvinylpyrrolidone) and a sugar alcohol (e.g., mannitol), a saccharide (e.g., lactose) or a combination thereof, each having an average particle size of not more than about 30 μm, and, optionally, pharmaceutically acceptable excipients typically used in ODT formulations, viz., flavors, a sweetener, coloring agents, and additional disintegrant.
The ODT in accordance with one embodiment exhibits the following properties:
The ODT in accordance with one embodiment comprising taste-masked microparticles demonstrating effective taste-masking by releasing not more than 10% in about 3 minutes (the longest typical residence time anticipated for the ODT in the buccal cavity) when dissolution tested in simulated saliva fluid (pH ˜6.8) while releasing not less than about 50% of the dose in about 60 minutes when dissolution tested in 0.1N HCl.
In accordance with certain embodiments, the rapidly-dispersing microgranules and coated beads (taste-masked IR, SR and/or TPR beads) of one or more weakly basic actives may be present in the weight ratio of about 6:1 to 1:1, more particularly from about 4:1 to 2:1, to achieve a smooth (non-gritty) mouth feel. In accordance with certain other embodiments, the coated beads (taste-masked IR, SR and/or TPR beads) of one or more weakly basic actives may be coated with a compressible coating (e.g., fluid-bed coating with a plasticized aqueous dispersion of ethylcellulose) in order to minimize membrane fracture during compression with rapidly-dispersing microgranules.
A pharmaceutical composition of a weakly basic pharmaceutical active in the conventional tablet form in accordance with another embodiment of the present invention, may comprise one or more bead populations, such as IR beads (crystals, granules, pellets, beads and the like), and SR beads and/or TPR beads comprising SR coated acid-containing cores. The pharmaceutical composition of a weakly basic pharmaceutical active in the conventional tablet form disintegrates into constituent beads (taste-masked particles, coated SR beads and/or TPR beads) upon oral ingestion in about 10 minutes. The conventional tablet may also include pharmaceutically acceptable excipients typically used in disintegrating tablet formulations such as compressible diluents, fillers, coloring agents, and optionally a lubricant.
The conventional tablet prepared in accordance with one embodiment exhibits the following properties:
Another embodiment of the invention relates to a multiparticulate pharmaceutical composition comprising one or more coated bead populations comprising one or more weakly basic therapeutic agents having an elimination half-life of about 2 hours or longer, wherein the active is layered onto SR coated organic acid-containing cores. The pulsatile delivery system developed in accordance with this aspect of the present invention may comprise IR bead, SR bead and timed, pulsatile-release (TPR) bead populations. The SR coated organic acid-containing cores are typically prepared by layering an organic acid (e.g., fumaric acid) onto inert particles (e.g., sugar spheres) from a polymeric binder solution and coated with a water-insoluble polymer (e.g., ethylcellulose, with a viscosity of about 10 cps) alone or in combination with a water-soluble polymer (e.g., polyvinylpyrrolidone, Povidone K-25 or polyethylene glycol, PEG 400) or an enteric polymer (e.g., hypromellose phthalate, HPMCP or HP-55). The IR bead population comprising SR coated acid-containing cores are prepared by drug layering onto SR coated acid-containing cores from a polymeric binder solution and providing a protective seal coat of Opadry Clear. The SR and TPR bead populations are prepared by coating IR beads with a water-insoluble polymer (e.g., ethylcellulose) alone or in combination with a water-soluble polymer (e.g., PVP K-25 or PEG 400). In accordance with one aspect of the invention each SR or TPR bead population releases both the drug and the acid at comparable rates, as rapid-release or sustained-release profiles after a pre-determined lag-time (for example, a lag-time of up to 10 hours) upon oral administration. IR beads, if included in the dosage form (capsule or conventional tablet or orally disintegrating tablet), may comprise the drug layered directly onto inert cores and coated with a protective seal coat or a taste-masking membrane, which being part of the total dose, provides for rapid absorption (a bolus dose) upon oral administration.
A method of manufacturing a multiparticulate pharmaceutical composition wherein a delivery system developed in accordance with certain embodiments of the present invention comprises one or more weakly basic active pharmaceutical ingredients in sufficient quantities to be administered orally to a patient at prescribed once-daily dosing regimen to provide therapeutic efficacy is also provided.
The method of manufacturing a multiparticulate pharmaceutical composition in accordance with particular embodiments includes layering of a pharmaceutically acceptable organic acid such as fumaric acid from a polymeric binder solution onto inert particles selected from the group consisting of sugar spheres and cellulose spheres. Fluid bed or pan coating may be used to apply the organic acid and polymeric binder solution. In accordance with other embodiments, the core particles may be crystals with a desired particle size distribution, microgranules, pellets or beads containing one or more organic acid(s). In accordance with certain embodiments, the microgranules, extruded-spheronized pellets or compressed microtablets comprising one or more organic acids, a polymeric binder, which imparts resilient characteristics to dried microgranules, hydrophilic fillers/diluents, and optionally a flavor, a sweetener and/or a disintegrant. These organic acid-containing particles are barrier coated with an SR (sustained release) polymer membrane comprising a water-insoluble polymer (e.g., ethylcellulose with an average viscosity of 10 cps) alone or in combination with a water-soluble polymer (e.g., polyvinyl pyrrolidone or polyethylene glycol) or an enteric polymer (e.g., hypromellose phthalate (HPMCP or HP-55)). The water-insoluble and water-soluble or enteric polymers may be present at a weight ratio of from about 95:5 to about 50:50, more particularly from about 90:10 to 60:40 and the membrane thickness may vary from about 3% to 50%, more particularly from about 5% to 30% by weight in accordance with particular embodiments.
In accordance with particular embodiments, one or more weakly basic drug(s) are applied onto SR coated acid-containing particles from a polymeric binder solution and also, a protective seal coat with a hydrophilic polymer (e.g., Pharmacoat™ 603 or Opadry® Clear) is applied on drug-layered beads to produce IR beads. The organic acid or drug load depends on the physicochemical as well as the pharmacological properties of the weakly basic actives chosen for development, and the drug and the organic acid may be present at a weight ratio of from about 5:1 to 1:10 or more particularly from about 3:1 to 1:3 depending on whether organic acid crystals or organic acid-containing cores are used in accordance with certain embodiments.
In accordance with certain embodiments of the present invention, the IR beads comprising SR coated acid-containing cores are barrier coated with an SR polymer membrane comprising a water-insoluble polymer (e.g., ethylcellulose with an average viscosity of 10 cps) alone or in combination with a water-soluble polymer (e.g., polyvinyl pyrrolidone or polyethylene glycol). The water-insoluble and water-soluble polymers may be present at a weight ratio of from about 95:5 to about 50:50, more particularly from about 90:10 to 60:40 and the membrane thickness may vary from about 3% to 50%, more particularly from about 5% to 30% by weight in accordance with particular embodiments.
In accordance with other embodiments of the present invention, the SR beads comprising drug-layered beads are coated with a lag-time membrane comprising a combination of a water-insoluble polymer (e.g., ethylcellulose with an average viscosity of 10 cps) and an enteric polymer (e.g., hypromellose phthalate (HPMCP or HP-55)) to produce TPR beads. In accordance with certain other embodiments, the water-insoluble and enteric polymers may be present at a weight ratio of from about 9:1 to about 1:4, more particularly from about 3:1 to 1:1, and the membrane thickness may vary from about 5% to 60%, more particularly from about 15% to 50% by weight in accordance with particular embodiments.
The functional polymeric systems being applied from aqueous or solvent-based compositions typically contain plasticizers at suitable concentrations. The finished dosage form may be a modified-release (MR) capsule, a standard (conventional) tablet or an orally disintegrating tablet (ODT) comprising a coated spherical bead population containing the active substance alone or a combination of two or more coated bead populations to provide target plasma concentrations suitable for a once-daily dosing regimen. For example, a once-daily dosage form of an active with an elimination half-life of about 7 hours may contain a mixture of an IR bead population which allows immediate release, a second, TPR bead population with a shorter lag-time (about 3-4 hours), which allows a delayed, rapid -release and a third TPR bead population with a longer lag-time (about 7-8 hours), which allows typically a delayed, sustained-release profile over about 8-12 hours, to maintain acceptable plasma concentrations at 24 hrs, thus enhancing safety, therapeutic efficacy and patient compliance while reducing cost of treatment. Alternatively, the finished dosage form may comprise an IR bead population and a second, TPR bead population with a lag-time of about 7-8 hours followed by a sustained-release profile over 10-12 hours. The achievable lag time depends on the composition and thickness of the barrier coating, as well as the composition and thickness of the lag-time coating. Specific factors that can affect achieving optimal once-daily dosage forms include, but are not limited to, the therapeutic agent's pKa (and its solubility above a pH of 6.0), elimination half-life, and solubility enhancement in an aqueous solution of an organic acid selected from the group consisting of aspartic acid, citric acid, fumaric acid, maleic acid, oxalic acid, succinic acid, tartaric acid, and the like.
In accordance with certain embodiments of the present invention, a method of manufacturing a multiparticulate composition comprising a weakly basic nitrogen (N)-containing selective serotonin 5-HT3 blocking agent having a pKa in the range of from about 5 to 14 and a solubility of not more than 200 μg/mL at a pH of 6.8 is also provided. The method may comprise the steps of:
The composition comprising one or more bead populations (e.g., a combination of IR and TPR bead populations) may exhibit the following properties:
These and other embodiments, advantages and features of the present invention become clear when detailed descriptions and examples are provided in subsequent sections.
All documents cited are, in relevant part, incorporated herein by reference; the citation of any document is not to be construed as an admission that it is prior art with respect to the present invention.
As used herein, as well as in specific examples thereof, the term “weakly basic pharmaceutical active” includes the base, pharmaceutically acceptable salts, polymorphs, stereoisomers and mixtures thereof. This term, which is more fully defined in a subsequent section, refers to a nitrogen (N)-containing selective serotonin 5-HT3 blocking agent having a pKa in the range of from about 5 to 14 and a solubility of not more than 200 μg/mL at a pH of 6.8 and a ratio of optimal highest dose to solubility at pH 6.8 of not less than about 100.
As used herein, the term “immediate release” refers to release of greater than or equal to about 50% (especially if taste-masked for incorporation into an orally disintegrating tablet dosage form), preferably greater than about 75%, more preferably greater than about 90%, and in accordance with certain embodiments greater than about 95% of the active within about 2 hours, more particularly within about one hour following administration of the dosage form. The term can also refer to the release of the active from a timed, pulsatile release dosage form characterized by an immediate release pulse after the designed lag time. The term “lag-time” refers to a time period wherein less than about 10%, more particularly substantially none, of the dose (drug) is released, and a lag-time of from at least about 2 to 10 hours is achieved by coating typically with a combination of water-insoluble and enteric polymers (e.g., ethylcellulose and hypromellose phthalate).
Unless indicated otherwise, all percentages and ratios are calculated by weight based on the total composition.
An aqueous or a pharmaceutically acceptable solvent medium may be used for preparing organic acid-containing core particles for drug layering, viz., acid-containing beads by layering an acid onto inert cores (e.g., sugar spheres) or IR beads by drug-layering onto acid-containing cores or directly onto sugar spheres from an appropriate polymer binder solution in fluid-bed equipment. Also, an aqueous dispersion of functional polymers, which are available as dispersions or a solvent system may be used for dissolving functional polymers for coating acid-containing beads, IR beads or SR beads.
Many active pharmaceutical ingredients (API) are weakly basic in the sense that these actives are freely to moderately soluble at acidic pHs, but are poorly to practically insoluble at neutral and alkaline pHs. Their pKa values are in the range of about 5 to 14. The pH-dependent solubility data for typical weakly basic actives are presented in
Table 1 lists the solubility enhancement of weakly basic actives in organic acid buffers. Three distinct groups can be identified. Group A actives, as represented by ondansetron hydrochloride, exhibits a dramatic increase in solubility of the weakly basic active in a buffer with a trace of fumaric acid. For example, ondansetron's solubility of about 26 mg/mL in the buffer containing only 0.05 mg/mL of fumaric acid remains unchanged upon increasing the concentration of fumaric acid in the buffer up to 5 mg/mL. In Group B, represented by dipyridamole, carvedilol and lamotrigine, the weakly basic drug's
solubility increases with increasing concentration of the acid. In Group C, represented by clonazepam, the organic acid has very limited impact, i.e., the solubility enhancement amounts typically to less than 3-fold. For example, clonazepam's solubilities are about 11.6 and 6.9 μg/mL in buffers at pH 2.3 and 6.8 containing a higher and lower concentration of fumaric acid, respectively.
Specific embodiments of the invention will be described in further detail with reference to the accompanying
The novelty/utility of the formulations developed in accordance with certain embodiments of the present invention is disclosed using ondansetron hydrochloride as an example of weakly basic nitrogen (N)-containing selective serotonin 5-HT3 blocking agents having a pKa in the range of from about 5 to 14. Ondansetron hydrochloride dihydrate is chemically (±) 1,2,3,9-tetrahydro-9-methyl-3-[(2-methyl-1H-imidazole-1-yl)methyl]-4H-carbazol-4-one monohydrochloride dihydrate. Ondansetron is indicated for the prevention of nausea and vomiting associated with radiotherapy and/or chemotherapy and prevention of postoperative nausea and/or vomiting. Zofran® Tablets (Ondansetron HCl Dihydrate, 4, 8, and 24 mg base equivalent) are commercially available. Drug is administered 8 mg bid for chemotherapy and 8 mg tid for radiotherapy. A once-daily dosing of ondansetron hydrochloride is commercially desirable and would simplify the dosing regimen and enhance patient compliace. Ondansetron exists as a racemate and it contains an a-hydroxyl secondary amine, with a pKa of 7.4. Ondansetron HCl is known to exhibit a pH-dependent solubility profile (solubility decreasing by 2-3 orders of magnitude). Ondansetron is well absorbed from the gastrointestinal tract and undergoes some first-pass metabolism. The elimination half-life averages approximately 3.8±1 hrs. Since the drug dissolution is the rate-limiting factor for absorption in the distal part of the GI tract potentially due to the decrease in solubility, the once-daily dosage form in accordance with one embodiment would comprise at least two bead populations—one IR bead population and another TPR bead population comprising SR coated organic acid cores.
In accordance with certain embodiments of the present invention, the solubility enhancing property of organic acid buffers is taken advantage of, and at the same time, the in situ formation of acid addition compounds is prevented by having an SR coating membrane between the inner organic acid layer and the weakly basic drug layer. The SR coating membrane thus applied precisely controls the release of the organic acid so as to insure no drug is left behind in the dosage form for lack of solubilizing acid in the TPR bead. In one embodiment, the active core of the dosage form of the present invention may comprise an inert particle coated with an organic acid, an SR coating, drug-layered (IR beads), further barrier or SR coated and/or lag-time coated. The amount of organic acid and the drug-load in the core will depend on the drug, the dose, its pH-dependent solubility, solubility enhancement, and elimination half-life. Those skilled in the art will be able to select an appropriate amount of drug/acid for coating onto the core to achieve the desired QD (once-daily) dosing regimen. In one embodiment, the inert particle may be a sugar sphere, a cellulose sphere, a silicon dioxide sphere or the like. Alternatively, organic acid crystals with a desired particle size distribution may function as cores, especially for Group C drugs, and in this case, these crystals are membrane coated to program the acid release, which, in accordance with certain embodiments, is synchronized with that of the drug to ensure complete release of the drug prior to depletion of the acid.
In accordance with one aspect of the present invention, the core of the dosage form may comprise an organic acid (e.g., fumaric acid) crystal with a desired mean particle size or an inert particle such as a sugar sphere layered with an organic acid from a polymer binder solution. Organic acid crystals or acid-containing cores are coated with a water-insoluble polymer alone or in combination with a water-soluble or enteric polymer, and the composition and thickness of the SR membrane is optimized such that the acid release is slower than or synchronized with the drug dissolution/release from the bead, thereby ensuring that the acid release is not complete prior to depletion of the drug release. In certain aspects of the invention, the acid-containing cores may be in the form of microgranules or pellets which may be prepared by rotogranulation, high-shear granulation and extrusion-spheronization or compression (as micro-tablets about 1-1.5 mm in diameter) of the organic acid, a polymeric binder and optionally fillers/diluents.
A weakly basic active agent such as ondansetron hydrochloride dihydrate is layered onto the SR coated fumaric acid-containing beads from a polymeric binder (e.g., povidone) solution and a protective seal-coat comprising a hydrophilic polymer such as Pharmacoat 603 (Hypromellose 2910 3 cps) or Opadry® Clear to form IR beads. In one embodiment, the drug-containing IR beads may be coated twice—an inner barrier coating membrane with a water-insoluble polymer (e.g., ethylcellulose) alone or in combination with a water-soluble polymer and a lag-time coating membrane of a water-insoluble polymer in combination with an enteric polymer to produce TPR beads with a lag-time (release with a delayed-onset) of approximately 1 to 10 hours upon oral administration. The water-insoluble polymer and enteric polymer may be present at a weight ratio of from about 9:1 to about 1:4, preferably at a weight ratio of from about 3:1 to 1:1. The membrane coating typically comprises from about 5% to about 60%, preferably from about 10% to about 50% by weight of the coated beads. In accordance with yet another embodiment, the IR beads may simply be coated with a combination of a water-insoluble polymer and an enteric polymer in the aforementioned amounts.
The unit capsule or conventional tablet dosage form according to the present invention may comprise TPR beads alone or in combination with IR beads while the unit ODT may comprise TPR beads alone or in combination with taste-masked immediate release (IR) beads. IR beads without having a taste-masking membrane will provide rapid release of the weakly basic drug in the gastrointestinal tract within approximately 60 minutes, preferably within 30 minutes following oral administration. If taste-masked, these beads exhibit taste-masking in the buccal cavity and substantially complete release of the weakly basic drug in the gastrointestinal tract within approximately 2 hours, preferably within one hour following oral administration. The TPR beads will release the weakly basic drug over a period of up to approximately 4-20 hours in the gastrointestinal tract after a lag time of about 1-10 hours following oral administration.
In accordance with particular aspects of the present invention, the pharmaceutical multiparticulate dosage form may comprise at least an IR bead population, a first TPR bead population, and an SR bead population or a second TPR bead population. In certain embodiments, the ratio of IR bead population to the first TPR bead population to the SR bead or second TPR bead populations may vary from about 10:90:0 to about 40:10:50.
The present invention also provides a method for manufacturing a pharmaceutically elegant multiparticulate dosage form having one or more timed, pulsatile release bead populations of one or more weakly basic actives comprising SR-coated organic acid-containing cores, i.e., a well time-controlled, series of pulses so that the active agents and the acid, being deposited in well separated/isolated layers, do not come into contact with each other to form acid-addition compounds until the dosage form comes into contact with a dissolution medium or body fluids following oral ingestion. The dosage form thus produced exhibits composite release profiles of the active agent and the acid that are comparable, more particularly, the acid-release profile is slower than that of the drug so that no undissolved drug is left behind in the dosage form for lack of solubilizing organic acid.
In accordance with one embodiment of the present invention, the method may include the steps of:
In accordance with certain embodiments of the present invention, the method may include the steps of
An aqueous or a pharmaceutically acceptable solvent medium may be used for preparing core particles based on coated inert particles. The type of inert binder that is used to bind the water-soluble organic acid or weakly basic drug to the inert particle or to the SR coated acid-containing core is not critical but usually water soluble or alcohol soluble binders, such as polyvinylpyrrolidone (PVP or povidone) or hydroxypropylcellulose may be used. The binder may be used at any concentration capable of being applied to the inert particle. Typically, the binder is used at a concentration of about 0.5 to 10% by weight. The organic acid or the weakly basic drug may be preferably present in this coating formulation in solution form. The drug concentration may vary depending on the application but typically will be used at concentrations from about 5 to 30% by weight depending on the viscosity of the coating formulation.
In accordance with other embodiments, the organic acid-containing cores may be prepared by rotogranulation, or by granulation followed by extrusion-spheronization or tableting into micro-tablets. The organic acid, a binder, and optionally other pharmaceutically acceptable excipients (e.g., diluents/fillers) may be blended together in a high-shear granulator, or a fluid bed granulator, such as Glatt GPCG granulator, and granulated to form agglomerates. The wet mass can be extruded and spheronized to produce spherical particles (pellets). The blend comprising acid particles, a binder and optionally a filler/diluent or drug-containing granules can also be compressed into micro-tablets (about 1-1.5 mm in diameter) to produce organic acid-containing pellets. In these embodiments, the acid content could be as high as 95% by weight based on the total weight of the granulated, extruded or compressed core. These acid-containing cores are coated with an SR membrane prior to drug-layering and subsequent coating with functional polymers.
The individual polymeric coatings on the acid-containing cores and IR beads will vary from about 5 to 50% by weight depending on the relative solubility of organic acid to active, nature of the active, composition of the barrier coat, and required lag-time. In one embodiment, the acid cores may be provided with a barrier-coat of a plasticized water-insoluble polymer, such as ethylcellulose (EC-10), at about 5-50% by weight to sustain the acid release over about 5-20 hours. In certain other embodiments, the acid cores may be provided with a barrier-coat of a plasticized ethylcellulose and hydroxypropyl methylcellulose (hypromellose) phthalate (HP-55) at about 10-50% by weight while the IR beads are coated with ethylcellulose (EC-10) at 5-20% by weight to achieve the drug-release synchronized with that of the acid. In yet another embodiment of the present invention, the IR beads may not be provided with any barrier coating, and the outer lag-time coating of EC-10/HP-55/plasticizer at about 45.5/40/14.5 for a weight gain of about 30-50% by weight controls the drug-release following the lag-time. The composition of the membrane layer and the individual weights of the polymers are important factors to be considered for achieving a desired drug/acid-release profile and lag time prior to appreciable drug release.
The drug/acid-release profiles from IR beads, barrier/SR-coated beads and TPR beads may be determined according to the following procedure:
Dissolution testing of IR beads, taste-masked or not, is conducted with a USP Apparatus 1 (baskets at 100 rpm) or Apparatus 2 (paddles at 50 rpm) in 900 mL of 0.1N HCl at 37° C. while the dissolution testing of SR and TPR beads is conducted in a USP apparatus using a two-stage dissolution medium (first 2 hours in 700 mL of 0.1N HCl at 37° C. followed by dissolution testing at pH=6.8 obtained by the addition of 200 mL of a pH modifier). Drug/acid-release with time is determined by HPLC on samples pulled at selected intervals.
There are instances wherein the onset of drug release should begin several hours following oral administration to provide adequate plasma concentration to be suitable for a once-daily dosing regimen, depending on the elimination half-life of the active. In accordance with particular aspects of the invention, drug release may be delayed for up to about 8-10 hours after oral administration.
A single targeted sustained-release profile over several hours after oral administration, with or without an immediate release pulse, is provided in accordance with certain embodiments of the present invention.
An aqueous or a pharmaceutically acceptable solvent medium may be used for preparing organic acid-containing core particles or drug-containing IR Beads by layering the drug onto inert cores such as sugar spheres or onto SR-coated acid-containing cores. The type of inert binder that is used to bind the water-soluble organic acid to the inert particle or the weakly basic drug onto SR-coated acid cores is not critical but usually water-soluble or alcohol and/or acetone-soluble binders are used. Representative examples of binders include, but are not limited to, polyvinylpyrrolidone (PVP), hydroxypropyl methylcellulose (HPMC), hydroxypropylcellulose, carboxyalkylcelluloses, polyethylene oxide, polysaccharides such as dextran, corn starch, which may be dissolved or dispersed in water, alcohol, acetone or mixtures thereof. The binders are typically used at a concentration of from about 0.5 to 10% by weight.
Representative inert particles used to layer the acid or the pharmaceutical active include sugar spheres, cellulose spheres and silicon dioxide spheres with a suitable particle size distribution (e.g. 20-25 mesh sugar spheres for making coated beads for incorporation into a capsule formulation and 60-80 mesh sugar spheres for making coated beads for incorporation into an ODT formulation).
Representative pharmaceutically acceptable organic acids which enhance the solubility of the pharmaceutical active include citric acid, fumaric acid, malic acid, maleic acid, tartaric acid, succinic acid, oxalic acid, aspartic acid, glutamic acid and the like. The ratio of organic acid to pharmaceutical active varies from about 5:1 to 1:10 by weight.
Representative examples of water-insoluble polymers useful in the invention include ethylcellulose, polyvinyl acetate (for example, Kollicoat SR#30D from BASF), cellulose acetate, cellulose acetate butyrate, neutral copolymers based on ethyl acrylate and methylmethacrylate, copolymers of acrylic and methacrylic acid esters with quaternary ammonium groups such as Eudragit NE, RS and RS30D, RL or RL30D and the like. Representative examples of water-soluble polymers useful in the invention include polyvinylpyrrolidone (PVP), hydroxypropyl methylcellulose (HPMC), hydroxypropylcellulose (HPC), polyethylene glycol, and the like.
Representative examples of enteric polymers useful in the invention include esters of cellulose and its derivatives (cellulose acetate phthalate, hydroxypropyl methylcellulose phthalate, hydroxypropyl methylcellulose acetate succinate), polyvinyl acetate phthalate, pH-sensitive methacrylic acid-methamethacrylate copolymers and shellac. These polymers may be used as a dry powder or an aqueous dispersion. Some commercially available materials that may be used are methacrylic acid copolymers sold under the trademark Eudragit (L100, S100, L30D) manufactured by Rohm Pharma, Cellacefate (cellulose acetate phthalate) from Eastman Chemical Co., Aquateric (cellulose acetate phthalate aqueous dispersion) from FMC Corp. and Aqoat (hydroxypropyl methylcellulose acetate succinate aqueous dispersion) from Shin Etsu K.K.
The enteric, water-insoluble, and water-soluble polymers used in forming the membranes are usually plasticized. Representative examples of plasticizers that may be used to plasticize the membranes include triacetin, tributyl citrate, triethyl citrate, acetyl tri-n-butyl citrate diethyl phthalate, castor oil, dibutyl sebacate, acetylated monoglycerides and the like or mixtures thereof. The plasticizer, when used, may comprise about 3 to 30 wt. % and more typically about 10 to 25 wt. % based on the polymer. The type of plasticizer and its content depends on the polymer or polymers and nature of the coating system (e.g., aqueous or solvent based, solution or dispersion based and the total solids).
In general, it is desirable to prime the surface of the drug-layered particles before applying the barrier-membrane coatings or to separate the different membrane layers by applying a thin hydroxypropyl methylcellulose (HPMC) (e.g., Pharmacoat 603 or Opadry® Clear) film. While HPMC is typically used, other primers such as hydroxypropylcellulose (HPC) or lower viscosity ethylcellulose can also be used.
The active pharmaceutical ingredients suitable for incorporation into these time-controlled pulsatile release systems include weakly basic active pharmaceutical ingredients, derivatives, or salts thereof, exhibiting a pKa in the range of from about 5 to 14, a solubility of not more than about 200 μg/mL at pH 6.8 and a ratio of optimal highest dose to the solubility at pH 6.8 of at least about 100. The drug substance can be selected from the group of selective serotonin 5-HT3 blocking agents having a pKa in the range of from about 5 to 14. A representative example is ondansetron or its hydrochloride salt with proven pharmacological activity in humans.
The membrane coatings can be applied to the core using any of the coating techniques commonly used in the pharmaceutical industry, but fluid bed coating is particularly useful. The present invention is directed to multi-dose forms, i.e., drug products in the form of multi-particulate dosage forms (hard gelatin capsules, conventional tablets or ODTs (orally disintegrating tablets)) comprising using a rotary tablet press one or more bead populations for oral administration to provide target PK profiles in patients in need of treatment. The conventional tablets rapidly disperse on entry into the stomach while ODTs rapidly disintegrate on contact with saliva in the oral cavity forming a smooth suspension of coated beads for easy swallowing. One or more coated bead populations may be compressed together with appropriate excipients into tablets (for example, a binder, a diluent/filler, and a disintegrant for conventional tablets while a rapidly dispersing granulation may replace the binder-diluent/filler combination in ODTs). Furthermore, compression into ODTs may be accomplished using a tablet press equipped with an external lubrication system to lubricate punches and dies prior to compression.
The following non-limiting examples illustrate the drug delivery dosage forms as capsules, conventional tablets or orally disintegrating tablets comprising one or more pulses, each with a predetermined delayed-onset and the totality of the in vitro drug-release profile or the ensuing in vivo plasma concentration profile upon oral administration of the dosage form should mimic the desired profile to achieve maximum therapeutic efficacy to enhance patient compliance and quality of life. Such dosage forms, when administered at the ‘right time’ or as recommended by the physician, would enable maintaining drug plasma concentration at a level potentially beneficial in minimizing the occurrence of side-effects associated with Cmax or Cmin.
A. SR-Coated Fumaric Acid Crystals
40-80 mesh fumaric acid crystals (3750 g) were charged into a fluid-bed coater, Glatt GPCG 5 equipped with a 9″ bottom spray Wurster insert, 10″ column length and 16 mm tubing. These acid crystals were coated with a solution (at 6% solids) of 250 g of ethylcellulose (Ethocel Premium 10 cps) and 166.7 g of polyethylene glycol (PEG 400) at a ratio of 60/40 dissolved in 98/2 acetone/water (6528.3 g) for a weight gain of up to 10% by weight. The processing conditions were as follows: atomization air pressure: 2.0 bar; nozzle diameter: 1.00 mm; bottom distribution plate: B with 15 gauge 100 mesh screen; spray/shake interval: 30 s/3 s; product temperature maintained at 35±1° C.; inlet air volume: 155-175 cubic feet per minute (cfin) and spray rate increased from about 8 to 30 g/min.
Fumaric acid crystals were also coated as described above using different ratios of ethylcellulose and PEG. More specifically, acid crystals were coated with a solution of EC-10 (Ethocel Premium 10 cps)/PEG 400 at a ratio of either 75/25 or 67.5/32.5 for a weight gain of up to 10% by weight in each case.
B. Ondansetron Hydrochloride IR Beads Comprising SR-Coated Fumaric Acid Crystals
Povidone (PVP K-29/32; 23 g) was slowly added to 50/50 water/Denatured Alcohol 3C, 190 Proof (3699.4 g) while mixing to dissolve. Ondansetron hydrochloride dihydrate (197.2 g) was slowly added to the binder solution to dissolve the drug. SR-coated fumaric acid crystals (3000 g) obtained from above were coated in the Glatt GPCG 5 with the drug solution (5% solids) while maintaining the product temperature at 40±1° C.; and inlet air volume at 180-195 cfin and spray rate being increased from about 8 to 15 g/min. The drug-layered beads were provided with a protective seal-coat of Opadry Clear (hypromellose 2910; 3 cps) (2% weight gain) to form IR beads.
C. Ondansetron Hydrochloride TPR Beads Comprising SR-Coated Fumaric Acid Crystals
Ondansetron hydrochloride IR beads (2800 g) from above were coated by spraying a solution in 98/2 acetone/water (6% solids) of EC-10/HPMCP (HP-55)/TEC (triethyl citrate) at a ratio of 45.5/40/14.5 for a weight gain of up to 50% and dried in the Glatt for about 10 minutes at 60° C. to drive off excess residual solvent. The dried beads were sieved to discard any doubles formed.
In order to assess the type of in vitro release profile needed to achieve a once-daily plasma concentration profile, a modeling exercise was performed using the pharmacokinetic parameters for ondansetron hydrochloride reported in “Ondansetron Absorption in Adults: Effect of Dosage Form, Food, and Antacids” in Journal of Pharmaceutical Sciences Vol. (1994) by Bozigian et al. Mean plasma concentrations achieved in 24 healthy, adult male volunteers, who received a single 8 mg ondansetron hydrochloride IR tablet in the fasted state, were used using the software program, WinNonlin™ Standard Version 2.1 to fit a 1-compartment first order model with a lag-time assuming first order elimination kinetics. The following parameters were obtained:
Primary Parameter: F=1.0 (assumed); Vd=238.26; Ka=1.49 per hour (hr); Ke=0.19 per hr (hence t1/2=3.65 hr); Tlag=0.41 hr. Secondary Parameters: AUC=0.17 mg.hr/L; Cl=46.06 L./hr; Tmax=1.98 hrs; Cm=0.0248 mg/L. These parameters very closely match the values reported in the above reference as well as in PDR.
The primary parameters were then input into another software, Stella Version 6.01 using a previously established model with slight modifications. Different in vitro release profiles were generated, and from target once-daily release profiles, desired in vitro release (medium, target and fast) profiles were generated by deconvolution. These simulated plasma profiles are shown in
A. Fumaric Acid-Containing Cores
Hydroxypropyl cellulose (Klucel LF, 23.9 g) was slowly added to denatured SD 3C 190 proof alcohol at 4% solids while stirring rigorously to dissolve and then fumaric acid (215.4 g) was slowly added to dissolve. Glatt GPCG 5 equipped with a 9″ bottom spray Wurster insert, 10″ partition column and 16 mm tubing was charged with 3750 g of 25-30 mesh sugar spheres. The sugar spheres were layered with the fumaric acid solution while maintaining the product temperature at about 33-34° C. and inlet air velocity at flap opening of 38%. The acid cores were dried in the unit for 10 min to drive off residual solvent/moisture and sieved through 20-30 mesh screens.
B. SR-Coated Fumaric Acid Cores
The fumaric acid cores (3750 g) from above were coated with a solution of EC-10 and PEG 400 dissolved in 98/2 acetone/water (6% solids) for a weight gain of 10% by weight at two ratios, viz., (B.1) 60/40 and (B.2) 75/25 to examine its effect on the drug release from SR and TPR beads.
C. Ondansetron Hydrochloride IR Beads Comprising SR-Coated Acid Cores
Povidone (PVP K-29/32, 19.5 g) was slowly added to 50/50 water/Denatured Alcohol 3C, 190 Proof (3699.4 g) while mixing to dissolve. Ondansetron hydrochloride dihydrate (175.2 g) was slowly added to the binder solution to dissolve the drug. SR-coated acid cores (3700 g) obtained from B.1 and B.2 above were coated in the Glatt GPCG 5 with the drug solution (5% solids).
D. Ondansetron Hydrochloride SR Beads
Ondansetron hydrochloride IR beads (3700 g) from above were barrier-coated (SR coated) by spraying a solution (7.5% solids) of 90/10 EC-10/TEC (triethyl citrate) at 5 and 10% by weight and dried in the Glatt for 10 minutes to drive off excess residual solvent. The dried beads were sieved to discard any doubles if formed.
E. Ondansetron Hydrochloride TPR Beads
Ondansetron hydrochloride SR beads (3500 g) from Example 3D were further coated with a lag-time coating membrane of EC-10/HP-55/TEC (triethyl citrate) at a ratio of 45.5/40.0/14.5 for a weight gain of about 30%, 40% and 50%. The TPR beads were dried in the Glatt at the same temperature to drive off residual solvent and sieved.
A. Fumaric Acid-Containing Cores
Fumaric acid-containing cores were prepared by the procedure described in Example 3A excepting that 90/10 Denatured Alcohol (SD 3C, 190 Proof)/water was used instead of the alcohol alone.
B. SR-Coated Fumaric Acid-Containing Cores
The fumaric acid cores (3750 g) from above were coated with a solution of EC-10 and either PEG 400 (B.1) at a ratio of 60/40 or TEC (B.2) at a ratio of 90/10 as the plasticizer, dissolved in 98/2 acetone/water (6% solids) for a weight gain of 10%.
C. Ondansetron Hydrochloride IR Beads
Ondansetron hydrochloride IR beads from B.1 and B.2 above were prepared as disclosed in Example 3 C. The drug-layered beads were provided with a protective seal-coat with Pharmacoat 603 (hypromellose 2910; 3 cps) for a weight gain of 2%.
D. Ondansetron Hydrochloride SR Beads
Ondansetron hydrochloride IR beads (1080 g) were barrier-coated (SR coated) by spraying a solution of EC-10 and either PEG 400 (D.1) at a ratio of 60/40 or TEC (D.2) at a ratio of 90/10 as the plasticizer, dissolved in 98/2 acetone/water (7.5% solids) for a weight gain of 10% and dried in the Glatt at the same temperature for 10 minutes to drive off excess residual solvent. The dried beads were sieved to discard any doubles if formed.
E. Ondansetron Hydrochloride TPR Beads
Ondansetron hydrochloride SR beads from D.1 and D.2 above were further coated with a lag-time coating membrane of EC-10/HP-55/TEC at three ratios of 45.5/40/14.5 (E.1-lot#1084-066), 50.5/35/14.5 (E.2-lot#1117-025) and 60.5/25/14.5 (E.3-lot#1117-044) dissolved in 90/10 acetone/water (7.5% solids) for a gain of up to 50% by weight. The TPR beads were dried in the Glatt to drive off residual solvent and sieved through a 18 mesh sieve.
(1) TPR beads lot#1084-066-The coating of EC-10/HP-55/TEC at a ratio of 45.5/40/14.5 at 50% by weight applied on IR beads coated with 60/40 EC-10/PEG 400 at 10% while IR beads (5% drug layered from 90/10 ondansetron/PVP) comprise fumaric acid cores (4% layered on sugar spheres from acid/Klucel) coated with 60/40 EC-10/PEG 400 at 10%.
(2) TPR beads lot#1117-025-The coating of EC-10/HP-55/TEC at a ratio of 50.5/35/14.5 at 50% by weight applied on IR beads coated with 90/10 EC-10/TEC at 10% while IR beads (6% drug layered from 90/10 ondansetron/ Klucel LF) comprise fumaric acid cores (layered on sugar spheres from acid/PVP) coated with 90/10 EC-10/TEC at 10%.
(3) TPR beads lot# 1117-044-The coating of EC-10/HP-55/TEC at a ratio of 60.5/25/14.5 at 50% by weight applied on IR beads coated with 90/10 EC-10/TEC at 10% while IR beads (6% drug layered from 90/10 ondansetron/Klucel LF) comprise fumaric acid cores (layered on sugar spheres from acid/PVP) coated with 90/10 EC-10/TEC at 10%.
A. Fumaric Acid-Containing Cores
Fumaric acid-containing cores were prepared by the procedure described in Example 3A excepting that fumaric content in the acid-containing cores was 11.25% instead of 6% in Example 4A.
B. SR-Coated Fumaric Acid-Containing Cores
The fumaric acid-containing cores (3750 g) from above were coated with a solution of EC-10/TEC at a ratio of 90/10 dissolved in 95/5 acetone/water (7.5% solids) for a weight gain of 5%.
C. Ondansetron Hydrochloride IR Beads
Ondansetron hydrochloride IR beads from above were prepared as disclosed in Example 3 C.
D. Ondansetron Hydrochloride SR Beads
Ondansetron hydrochloride IR beads (3500 g) were barrier-coated by spraying a solution (7.5% solids) of 90/10 EC-10/TEC dissolved in 95/5 acetone/water at 10% by weight and dried in the Glatt for 10 minutes to drive off excess residual solvent. The dried beads are sieved through a 18 mesh sieve to discard any doubles if formed.
E. Ondansetron Hydrochloride TPR Beads
Ondansetron hydrochloride SR beads (2600 g) from above were further coated with a lag-time coating membrane of EC-10/HP-55/TEC at a ratio of 60.5/25/14.5 dissolved in 90/10 acetone/water (7.5% solids) for a weight gain of 30%, 45%, and 50%. The coated beads were cured at 60° C. for 30 minutes in the same unit and sieved through a 18 mesh sieve after cooling to ambient temperature.
F. Ondansetron Hydrochloride MR Capsules
Ondansetron hydrochloride IR beads (PE364EA0001) and TPR beads (lot#PE366EA0001 with a lag-time coating of 30%, lot# PE367EA0001 with a lag-time coating of 45%, and lot# PE368EA0001 with a lag-time coating of 50%) were encapsulated at a ratio of 35%/65% into hard gelatin capsules to produce MR (modified-release) Capsules, 16 mg (lots# PF380EA0001, lots# PF381EA0001, and lots# PF382EA0001) QD (dosed once-daily) for a pilot bioavailability study in humans in comparison to marketed Zofran® 8 mg (as ondansetron) dosed bid (two times a day).
A. Fumaric Acid-Containing Cores
60-80 mesh sugar spheres (933.3 g) would be layered with fumaric acid (240 g) from a solution (4% solids) of Klucel LF (26.7 g) as disclosed in Example 3 to achieve an acid load of 20% by weight. The acid cores are dried in the unit for 10 min to drive off residual solvent/moisture and sieved through 40-80 mesh screens.
B. SR-Coated Fumaric Acid Cores
The acid cores (910 g) from above are coated with a solution of 441.5 g of ethylcellulose (EC-10) and 49 g of triethyl citrate (TEC) at a ratio of 90/10 dissolved in 95/5 acetone/water (7.5% solids) for a weight gain of 35%.
C. Ondansetron Hydrochloride IR Beads
IR beads of ondansetron hydrochloride dihydrate with a drug load of 11.13% by weight would be produced following the procedures disclosed in Example 5C. Ondansetron hydrochloride dihydrate (140.4 g) and Klucel LF (15.6 g) solution would be layered onto SR-coated acid-containing cores (1080 g) and a seal-coat of Pharmacoat 603 would be applied for a weight gain of 2%.
D. Ondansetron Hydrochloride SR Beads
Ondansetron hydrochloride IR beads 1080 g would be barrier-coated (SR coated) by spraying a solution (7.5% solids) of 90/10 EC-10/TEC at 5 and 10% by weight and dried in the Glatt at the same temperature for 10 minutes to drive off excess residual solvent. The dried beads are sieved to discard any doubles if formed.
E. Ondansetron Hydrochloride TPR Beads
Ondansetron hydrochloride SR beads would be further coated with a lag-time coating membrane of EC-10/HP-55/TEC at a ratio of 60.5/25/14.5 for a weight gain of 30%, 35% and 40%. The TPR beads would be cured at 60° C. for 30 minutes in the Glatt to drive off residual solvent and sieved through 30 mesh sieve.
F. Rapidly-Dispersible Microgranules
The rapidly-dispersible microgranules comprising a sugar alcohol such as mannitol and a disintegrant such as crospovidone would be prepared following the procedure disclosed in the co-pending US Patent Application Publication No. U.S. 2005/0232988, published Oct. 20, 2005, the contents of which are hereby incorporated by reference. D-mannitol (152 kg) with an average particle size of approximately 20 μm or less (Pearlitol 25 from Roquette, France) is blended with 8 kg of cross-linked povidone (Crospovidone XL-10 from ISP) in a high shear granulator (GMX 600 from Vector) and granulated with purified water (approximately 32 kg) and wet-milled using Comil from Quadro and dried in Glatt GPCG 200. The rapidly-dispersible microgranules thus obtained would have an average particle size in the range of approximately 125-200 μm.
G. Ondansetron Hydrochloride MR ODT, 12 mg:
Rapidly-dispersible microgranules (2541.2 g) would be blended with TPR beads (460.8 g), SR beads (479.0 g), IR beads (377.4 g) and other pharmaceutical acceptable ingredients (142.0 g), such as flavor, sweetener, and additional disintegrant, in a twin shell V-blender for a sufficient time to get homogeneously distributed blending for compression. Tablets weighing approximately 400 mg would be compressed using a production scale tablet press equipped with an external lubrication system at a mean hardness of about 4-5 kP. Ondansetron Hydrochloride Dihydrate MR ODT, 12 mg thus produced would rapidly disintegrate in the oral cavity creating a smooth, easy-to-swallow suspension comprising coated ondansetron hydrochloride beads, which would provide a target profile suitable for a once-daily dosing regimen.
A 4-arm crossover pilot POC (proof of concept) study was conducted which included 12 Caucasian male, healthy volunteers aged 18 to 55 years with a wash-out period of 7 days. Each volunteer was dosed with 250 mL of mineral water a single dose of 16 mg Test Formulation (either A (PF380EA0001), B (PF381EA0001), or C (PF382EA0001) of Example 4) at 8 AM or two 8 mg Zofran® (i.e., one at 8 AM and the other at 4:30 PM after an overnight fasting (at least 12 hrs), and lunch was served at 11 AM. Blood samples were drawn at 0 (pre-dose), 20 min, 40 min, 1 hr, 1.5 hrs, 2 hrs, 3 hrs, 4 hrs, 6 hrs, 8.5 hrs (before second dose), 9 hrs 10 min, 9.5 hrs, 10 hrs, 10.5s, 11.5 hrs, 12.5 hrs, 14.5 hrs, 17 hrs, 20 hrs, 22 hrs, 24 hrs and 36 hrs. The PK (pharmacokinetics) parameters are presented in Table 2. The table demonstrates that the plasma profiles of Test Formulations A (PE280EA0001), B (PE281EA0001), and C (PE282EA0001) are those characteristic of sustained release formulations, i.e., apparent half-life is significantly longer than that with Zofran. AUC or Cmax of Test Formulations does not deviate substantially from that of Zofran (i.e., AUC within ±25% and Cmax approximately 70% of Zofran). The actual Cmax for Zofran 8 mg was 30 ng/mL in comparison to the predicted 24 ng/mL while the actual Cmax for the IR component was about 24 ng/mL when normalized. Approximately 70% of Zofran 8 mg bid (twice-dosed) was absorbed in 24 hrs. Test Formulations A to C exhibited the expected trend post-dosing up to the crossover point at about 15-16 hrs; thereafter, Formula C continued to exhibit a lower plasma concentration-time profile contrary to the predicted behavior.
From these demonstrations, it is apparent that the incorporation of an organic acid, as the solubilizer for the weakly basic drugs exhibiting a pH-dependent solubility profile (i.e., showing a decrease in solubility at the intestinal pH 6.8 by about 2 orders of magnitude in comparison to its maximum solubility in the GI fluid) and functional coating of the acid before applying the active pharmaceutical ingredient has significant impact on the lag time, a desired but complete drug release profile prior to depletion of the buffer. Furthermore, the active pharmaceutical ingredient remains in the unaltered form in the solid dosage form until it is released for absorption in the GI tract.
This application claims the benefit of U.S. Provisional Application No. 60/762,750 filed Jan. 27, 2006, the contents of which are hereby incorporated by reference.
| Number | Date | Country | |
|---|---|---|---|
| 60762750 | Jan 2006 | US |
