Plurality of tiny pills in liquid dosage form

Abstract: A delivery system is disclosed for delivering a beneficial agent to an environment of use. The delivery system comprises a plurality of tiny dosage forms comprising a beneficial agent. The delivery system also comprises means for maintaining (a) the physical and chemical integrity of the dosage forms and for (b) inhibiting delivery of the beneficial agent during non-performance of the delivery system.

Description: This invention pertains to a novel and useful drug delivery system. More particularly the invention concerns a drug delivery system comprising a plurality of tiny pills in a pharmaceutically acceptable liquid carrier. Tiny pills manufactured as small, round, solid dosage forms comprising a medicinal agent surrounded by a film are known to the medical and to the pharmaceutical arts. The tiny pills known to the prior art are delivered in a conventional manner to a host dispersed in a solid, dry carrier such as a compressed tablet comprising the tiny pills, or a polymeric matrix comprising the tiny pills. In another dosage form the prior art delivered the tiny pills housed in the dry lumen of a conventional capsule. Tiny or small pills and dosage forms comprising tiny pills in a dry tablet, matrix or dry capsule for dispensing a medicinal agent are known in the following references: Lipowski, G. B. Pat. 523,594; Laboratorie de Rechersches, G. B. Pat. 1,098,006; Blythe, U. S. Pat. No. 2,738,003; Svedres, U. S. Pat. No. 2,793,979; Wagner, U. S. Pat. No. 2,897,121; Reese, U. S. Pat. No. 2,921,883; Swintosky, U. S. Pat. No. 2,951,792; Press, U. S. Pat. No. 2,953,497; Barry, U. S. Pat. No. 2,996,431; Sheppard, U. S. Pat. No. 3,080,294; Eng, U. S. Pat. No. 3,081,233; Sheppard, U. S. Pat. No. 3,109,775; Neville, U. S. Pat. No. 3,139,383; Gaunt, U. S. Pat. No. 3,328,256; Speiser, U. S. Pat. No. 3,390,050; Chester, U. S. Pat. No. 3,492,397; Raghunathan, U. S. Pat. No. 4,221,778; Urquhart and Theeuwes, U. S. Pat. No. 4,434,153; Urquhart and Theeuwes, U. S. Pat. No. 4,578,075; Urquhart and Theeuwes, U. S. Pat. No. 4,642,233; Urquhart and Theeuwes, U. S. Pat. No. 4,649,043 and Urquhart and Theeuwes, U. S. Pat. No. 4,659,558. The above presentation teaches that delivery systems have been provided to deliver tiny pills. While those delivery systems provide for delivering the tiny pills, there are serious and inherent short-comings associated with these delivery systems. For example, tiny pills in a tablet may not be available for instant release to the environment of use. Tablets usually are made in a tabletting machine under an applied pressure of a ton or more and this compressive force absorbed by the tablet can seriously delay the release of the tiny pills. Tiny pills dispersed in a polymeric matrix may not be available because they are entrapped in the molecular structure of the polymer. Additionally, well known serious shortcomings are associated with the administration of dry capsules containing tiny pills. Dry capsules are not a conducive means for administering a drug to a patient with a dry or sore throat, they are bulky and hard to swallow, and they do not lend themselves for administering a needed drug to children. From WO-A-85/03000 a dual coated dosage form in a liquid carrier e.g. water is known. The dual coats are used to keep a drug inside the dosage form. It is this combination of coatings (first and second overcoating of the microspheres) which permit the dosage form to be successfully placed in a liquid carrier vehicle for at least 35 days prior to ingestion. The dual coated dosage form is dispersed in a non-drug liquid carrier. In GB-A-931 532 microscopic capsules present in an injectable liquid carrier, e.g. water and the like, for parenteral, intravenous, intramuscular and other kinds of injection have been proposed, the drug diffuses immediately into the carrier free-of-drug when dispersed. WO-A-87/07833 discloses a saturated solution of drug and its maintaining saturated by releasing drug from to microscapsules into the solution. A constant level of drug is maintained by dissolution of the microcapsules into the solution to replace drug that leaves the solution. It will be appreciated by those versed in the dispensing art, in view of the above presentation, that a critical need exists for a delivery system for making tiny pills available instantly and continuously to an environment of use. The need exists for providing tiny pills for (a) achieving an early therapeutically effective plasma concentration of drug and for (b) achieving a continuous and therapeutically effective plasma concentration of drug. A delivery system is needed for housing and for providing tiny pills for (c) dispersing the drug in a drug receiving environment for (d) increasing the bioavailability of the drug, (e) for concomitantly decreasing the likelyhood of local irritation of mucosal tissue, and (f) for masking the unpleasant taste of many drugs. Accordingly, in view of the above presentation, it is an immediate object of this invention to provide both a novel and useful drug delivery system that makes a substantial contribution to the art by providing a delivery system useful for obtaining better therapy in the management of health and disease. Another object of the claimed invention is to provide a delivery system for the controlled delivery of a drug to an environment of use, the delivery system comprising: (a) a plurality of tiny pills, which pills comprise: (1) a wall formed of a semipermeable cellulosic polymer permeable to the passage of external fluid and impermeable to the passage of drug, which semipermeable wall surrounds: (2) a composition comprising a concentration of beneficial drug; and (b) a pharmaceutically acceptable liquid carrier containing the plurality of tiny pills; and wherein the dosage form is characterised by: (c) drug in tiny pills exhibiting an osmotic pressure gradient across the semipermeable wall, and drug in the liquid carrier exhibiting an osmotic pressure gradient equal to the osmotic pressure of the tiny pills for preventing the release of drug through the semipermeable wall when the tiny pills are in the liquid carrier. Another object of the present invention is to provide a delivery system for administering a drug in the gastrointestinal tract by making available a delivery system comprising a multiplicity of miniature pills that spread and deliver drug over a large area of the gastrointestinal tract. Another object of the present invention is to provide a delivery system comprising a multiplicity of orally administrable tiny pills that are simple in construction and exhibit all the practical benefits of controlled and continuous administration of drug in the stomach and in the intestine for executing a therapeutic program. Another object of the present invention is to provide a delivery system comprising a plurality of tiny pills comprising a drug, which tiny pills are dispersed in a pharmaceutically acceptable liquid carrier that exhibits means for substantially preventing a premature delivery of drug from the tiny pills while the tiny pills are in the liquid carrier. Another object of the invention is to provide a pharmaceutically acceptable carrier comprising a plurality of tiny pills wherein the release of drug is delayed from the tiny pills by governing the pH of the carrier for preventing the loss of integrity of the wall of the tiny pills. Another object of the present invention is to provide a delivery system comprising a pharmaceutically acceptable liquid carrier housing a multiplicity of tiny pills wherein the liquid carrier suspends the tiny pills over time. In the drawings, which are not drawn to scale but are set forth to illustrate various embodiments of the invention, the drawing figures are as follows: Figure 1 depicts a container that can be used for containing the delivery systems provided by the invention; Figure 2 is an opened view of a container for depicting a delivery system provided by the invention, which delivery system comprises tiny pills in a fluid medium; Figure 3 is similar to Figure 2 wherein Figure 3 illustrates tiny pills that release a beneficial drug by an osmotic process; Figure 8 illustrates a container with a pouring member useful for storing and then pouring the delivery system to a spoon, or the like, for administering the delivery system to a patient; Figure 9 is a graph depicting the osmotic bursting time for delivery systems provided by the invention; Figure 10 is a graph depicting the rate of delivery of drug from osmotic bursting delivery systems; Figure 11 depicts the rate of release from an osmotic bursting aperture forming delivery system; Figure 12 depicts the effects of deformation on a wall of a delivery system; Figure 13 depicts the zero order rate of release from a delivery system over time; and, Figure 14 is an opened view for illustrating the structure of a delivery system. In the drawings and specifications, like parts in related drawing figures are identified by like numbers. The terms appearing earlier in the specification and in the description of the drawings as well as embodiments thereof are further described elsewhere in the disclosure. Turning now to the drawings in detail, which are an example of the various delivery systems provided by the invention, one example of a delivery system is seen in Figures 1 and 2. In Figure 1 a container 10 is illustrated for housing the delivery system provided by the invention. The container can be any receptacle for holding a liquid, and the like, such as a bottle made of glass or plastic, a capsule, cup, beaker, and the like. In Figure 2 container 10 of Figure 1 is seen in opened-section at 11 for illustrating a lumen 12 that houses a delivery system provided by the invention. The delivery system comprises a multiplicity of tiny pills 13. Tiny pills 13 are a first dispensing means for the controlled delivery of a beneficial agent, such as a drug, both immediately and over a prolonged period of time. Tiny pills 13, an agent dispensing means, comprise a core of beneficial agent 14, such as a drug, surrounded by a wall 15 formed of a release rate controlling material. Tiny pills 13 can have a wall 15, in one embodiment, made from an enteric composition which prevents release of beneficial agent 14 in the stomach, but will release beneficial agent 14 in the intestine. Additionally, the composition comprising wall 15 can be selected, in presently preferred embodiments, from wall-forming nontoxic compositions that release beneficial agent 14 by different physical-chemical mechanisms. These mechanisms include osmosis, diffusion, erosion, disintegration, metabolism, and like mechanisms. Wall 15 can have various thicknesses as an additional aid for providing immediate timed release and prolonged timed release of beneficial agent 14. The delivery system provided by the invention comprises also means 16. Means 16, a pharmaceutically acceptable carrier, comprises a liquid and it is a second dispensing means for (a) containing tiny pills 13, (b) for delivering tiny pills 13 to an environment of use such as a drug receptor, (c) for governing the release of beneficial agent 14 from the tiny pills 13, and (d) for keeping the shelf life of the tiny pills. Means 16 comprises a nontoxic, inert fluidic carrier such as a member selected from the group consisting of an inorganic liquid, an organic liquid, aqueous media, emulsion, suspension, liquid comprising semisolids, elixir, syrup, juice, osmotic solution, viscous solution, hydrogel solution, gel suspension in a water media, pharmacologically acceptable liquid, and a semisolid comprising a liquid. Means 16, in a presently preferred embodiment, governs and substantially prevents a premature release of beneficial agent 14 from tiny pills 13 into a liquid means 16 in container 10. Means 16 governs the release of beneficial agent 14 by exhibiting an osmotic pressure or a concentration in a liquid means 16 that is equal to, or higher than the osmotic pressure or the concentration gradient exhibited by beneficial agent 14 across wall 15 of tiny pills 13 against liquid means 16. For example, for a beneficial agent 14 exhibiting an osmotic pressure of π t , or for a beneficial agent 14 blended with an osmotically effective solute exhibiting an osmotic pressure of π t , the osmotic pressure exhibited by liquid means 16 is equal to π L , or greater than π L , such that π L ≧ π t , where π t is the osmotic pressure of the tiny pills. This inventive feature provides also means for storing the delivery system essentially-free of drug release during storage. The osmotic pressure or the concentration of liquid means 16 can be regulated by adding a composition of matter to liquid means 16. The composition of matter can be in any physical form such as powder, particle, crystal, strip, film, granules, fiber, and the like. The composition of matter additionally can comprise a beneficial agent, an osmagent or an osmopolymer. Osmagents are known also as osmotically effective compounds and as osmotically effective solutes. The beneficial agent can be a drug that is the same or different than a drug in a tiny pill. Representative osmagents useful for blending with the liquid include carboxylic acids such as dicarboxylic, tricarboxylic, hydroxydicarboxylic, hydroxytricarboxylic and dihydroxycarboxylic acids such as tartaric, citric, maleic, succinic, fumaric, mixtures thereof, and the like; examples of osmotically active solutes include solutes such as sodium chloride, magnesium sulfate, magnesium chloride, potassium chloride, sodium sulfate, lithium sulfate, potassium acid phosphate and the like; carbohydrates such as raffinose, succrose, glucose, lactose, galactose, altrose, monosaccharides, disaccharides, polysaccharides, mixtures thereof, and the like; examples of alcohols include alcohols such as sorbitol, also known as hexanehexol, mannitol and the like; examples of gels include such as gum Arabic, agar, acacia, tragacanth, and the like; Other ingredients that can be added to the liquid include urea, inositol and like osmotic solutes. The osmotic solute is present in any physical form that is compatible with a host, and with the tiny pills. The osmotic pressure of a solution of variously osmotically active compounds and a solution of a beneficial agent such as a drug used for making tiny pills is measured in a commercially available osmometer that measures the vapor pressure difference between pure water and the solution to be analyzed and, according to standard thermodynamic principles, the vapor pressure ratio is converted into an osmotic pressure difference. An osmometer that can be used for the present measurements is identified as Model 320B, Vapor Pressure Osmometer, manufactured by the Hewlett Packard Co., Avondale, PA. Procedures for measuring osmotic pressure using thermodynamic principles are disclosed in U. S. Pat. Nos. 4,160,020 and 4,576,604. Figure 3 is an opened section depicting a delivery system provided by the invention. Figure 3 illustrates a plurality of tiny pills 13 that release a drug by osmotic principles. In Figure 3, tiny pills 13 comprise a wall 15 that releases a beneficial agent 14 by the process of osmotic bursting over time. In a presently preferred embodiment, beneficial agent 14 is a drug. The drug, in one embodiment, is present in the form of an osmotic solute, such as a therapeutically acceptable salt, that exhibits an osmotic pressure gradient across wall 15 against distilled water, or the drug can be mixed with an osmotically effective solute that exhibits an osmotic pressure gradient across wall 15 against distilled water. In Figure 3, in the embodiment illustrated, fluidic means 16 comprises a concentration substantially equal to or larger than the concentration of drug 14 in tiny pill 13 thereby providing an initial concentration gradient substantially equal to zero. The wall forming composition used to manufacture wall 15 comprises those materials permeable to the passage of an external fluid present in an environment of use and substantially impermeable to the passage of drug and osmotic solute. Typical materials include a member selected from the group consisting of cellulose acylate, cellulose diacylate, cellulose triacylate, cellulose acetate, cellulose diacetate, cellulose triacetate, cellulose acetate having a degree of substitution, D.S., up to 1 and an acetyl content of 21%; cellulose diacetate having a D.S. of 1 to 2 and an acetyl content of 21% to 35%; cellulose triacetate having a D.S. of 2 to 3 and an acetyl content of 35% to 44.8%; cellulose acetate propionate, cellulose acetate butyrate, ethyl cellulose semipermeable polyurethane, and the like. The osmotic wall can be coated around the drug in varying thicknesses by pan coating, spray-coating, Wurster® fluid air-suspension coating, coacervation techniques, and the like. The wall is applied using organic solvents such as methylene chloride-methanol, methylene chloride-acetone, methanol-acetone, ethylene dichloride-acetone, and the like. Osmotic wall forming materials, and procedures for forming the wall, and osmotic bursting procedures are disclosed in U. S. Pat. Nos. 2,799,241; 3,952,741; 4,014,334 and 4,016,880. Drug 14, neat, or a combination of drug 14 and osmotically effective solute in pill 13, in one embodiment, will have a particle size of 0.1 to 1000 µm, and a presently preferred particle size of about 0.5 to 300 µm, average. Procedures for measuring the surface area average diameter of agent solutes are reported in J. Am. Chem. Soc. , Vol. 6, p 309, (1938); The Surface Chemistry of Solids , by Gregg, 2nd Ed., (1961), published by Remhold Corp., New York; in Absorption, Surface Area and Porosity , by Gregg et al., (1967), published by Academic Press, New York; in Physical Absorption of Gases , by Yound et al., (1962), published by Butterworth and Co., Ltd., London; and in Fine Particle Measurements , by Valla, (1959), published by Macmillan Co., New York. Procedures for ascertaining the impermeability or the permeability of a polymer film used for providing wall 15 of osmotic bursting pill 13 are known to the art in Proc. Roy. Sci. , London, Series A, Vol: 148, (1935); J. Pharm. Sci. , Vol. 55, pp 1224-29, (1966); in Diffusion in Solids, Liquids and Gases , by Jost, Chapter XI, pp 436-88, (1960), published by Academic Press, Inc., New York. Procedures for measure osmotic bursting aperture formation in a polymeric film by the hydrostatic pressure in the pill exceeding the cohesive integrity of the polymeric film, with the polymer wall 15, can be determined by measurements predicted on pressure-deflection and mechanical behavior measurement techniques reported in Modern Plastics , Vol. 41, pp 143-44, 146 and 186, (1964); Handbook of Common Polymers , by Scott et a., pp 588-609, (1971), published by CRC Press, Cleveland, OH; in Machine Design , pp 107-11, (1975); in J. Sci. Instruments , Vol. 42, pp 591-96, (1965); and by measuring mechanical stress-strain patterns of polymers using the Instron ® Testing Machine, available from the Instron Corporation of Canton, MA. The tiny pills provided by the invention, in presently preferred optional embodiments, can comprise an enteric coat. The enteric coat can be in contact with the outer surface of the wall comprising the tiny pill, or the wall can be made of an enteric composition. The enteric coat is made from an enteric materials that do not dissolve or disintegrate in the stomach during the period of time the tiny pill passes through the stomach. The enteric materials suitable for forming enteric coat or wall include: (a) enteric materials that are digestible by enzymes in the small intestine; (b) enteric materials containing an ionizable polyacid; (c) enteric materials that are a long-chain polymer with an ionizable carboxyl group, and the like. Representative enteric materials include: (d) a member selected from the group of phthalates consisting essentially of cellulose acetyl phthalate, cellulose diacetyl phthalate, cellulose triacetyl phthalate, cellulose acetate phthalate, hydroxypropyl methylcellulose phthalate, sodium cellulose acetate phthalate, cellulose ester phthalate, cellulose ether phthalate, hydroxypropyl cellulose phthalate, alkali salts of cellulose acetate phthalate, alkaline earth salts of cellulose acetate phthalate, calcium salt of cellulose acetate phthalate, ammonium salt of hydroxypropyl methylcellulose phthalate, cellulose acetate hexahydrophthalate, hydroxpropl methylcellulose hexahydrophthalate, polyvinyl acetate phthalate, and the like; (e) a member selected from the group consisting of keratin, keratin sandarac-tolu, salol, salol beta-napthyl benzoate and acetotannin, salol with balsam of Peru, salol with tolu, salol with gum mastic, salol and stearic acid, and salol and shellac; (f) a member selected from the group consisting of formalized protein, formalized gelatin, and formalized cross-linked gelatin and exchange resins; (g) a member selected from the group consisting of myristic acid-hydrogenated castor oil-cholesterol, stearic acid-mutton tallow, stearic acid-balsam of tolu, and stearic acid-castor oil; (h) a member selected form the group consisting of shellac, ammoniated shellac, ammoniated shellac-salol, shellac-wool fat, shellac-acetyl alcohol, shellac-stearic acid-balsam of tolu, and shellac-n-butyl stearatel (i) a member selected from the group consisting of abietic acid, methyl abietate, benzoin, balsam of tolu, sandarac, mastic with tolu, and mastic with acetyl alcohol; (j) a member selected form the group consisting of cellulose acetate with shellac, starch acetate phthalate, polyvinyl acid phthalate, 2-ethoxy-5-(2-hydroxyethoxymethyl)-cellulose phthalic acid, acid phthalates of carbohydrates, zein, alkyl resin-unsaturated fatty acids-shellac, colophony, mixtures of zein and carboxymethylcellulose, and the like. The enteric materials are discussed in Remington's Pharmaceutical Sciences , 13th Ed., pp 604-05, (1965), published by Mack Publishing Co., Easton, PA. The rate of release of drug 21 through wall 22 can be determined easily by standard procedures. In this manner particularly materials used as the wall as the drug release rate controlling barrier for release of drug from the tiny pills can be selected. Various techniques, such as the transmission method, the sorption/desorption method, and the like, can be used as measurers of permeability. One technique that has been found to be eminently well suited is to cast or hot press a film of the material to a thickness in the rate of 25 to 1500 µm (1 to 60 mils). The film is used as a barrier between a rapidly stirred (e. g., 150 rpm) saturated solution of the drug and a rapidly stirred solvent bath, both maintained at constant temperature (typically 37°C). Samples are periodically withdrawn from the solvent bath and analyzed for drug concentration. By plotting the agent's concentration in the solvent bath, versus time, the permeability constant P of the material is determined by the Fick's First Law of Diffusion. Slope of plot = (Q₂ - Q₁)/(t₂ - t₁) = p AC/h, wherein Q₁ = cumulative amount of drug in receptor solvent at t₁ Q₂ = cumulative amount of drug in receptor solvent at t₂ t₁ = elapsed time to first sample, i.e., Q₁ t₂ = elapsed time to second sample, i.e., Q₂ A = area of membrane in cm² C = initial concentration of drug h = thickness of membrane in cm By determining the scope of the plot, i.e., (Q₂ - Q₁)/(t₂ - t₁) and solving the equation using the known or measured values of A, C, and h, the permeability P constant in cm²/time of the material for a given drug is readily determined. The release rate through different drug release controlling materials can be easily ascertained by standard techniques known to the art as recorded in J. Pharm. Sci. , Vol. 52, pp 1,145 to 1,149; and ibid. , Vol. 53, pp 798-802, (1964); ibid. , Vol. 54, pp 1,459 to 1,464, (1965); ibid. , Vol. 55, pp 840-43 and 1,224 to 1,239, (1966); Encyl. Polymer Sci. Technol. , Vols. 5 and 9, pp 65-82 and 794-807, (1968); the references cited therein, in U. S. Pat. Nos. 3,845,480; 3,845,761 and 3,896,819. In the specification and in the accompanying claims the term, "beneficial agent" includes drug. The term, "drug" includes pharmacologically active substances that produce a local or systemic effect in animals, which term includes warm-blooded mammals such as humans. The active drug that can be delivered includes drugs that act on the central nervous system, depressants, hypnotics, sedatives, psychic energizers, tranquilizers, anticonvulsants, muscle relaxants, anti-Parkinson agents, analgesics, anti-inflammatories, hormonal agents, anti-histamines, contraceptives, sympathomimetics, nasal decongestants, diuretics, anti-parasites, neoplastics, hypoglycemics, opthalmics, electrolytes, cardiovascular drugs, and the like. Exemplary drugs that are soluble in water and can be delivered by the devices of this invention include prochlorperazine edisylate, ferrous sulfate, aminocaproic acid, potassium chloride, mecamylamine hydrochloride, procianamide hydrochloride, amphetamine sulfate, benzhetamine hydrochloride, isoproternol sulfate, methamphetamine hydrochloride, phenmetrazine hydrochloride, bethanechol chloride, methacholine chloride, atropine sulfate, methascopolamine bromide, isopropamide iodide, tridihexethyl chloride, oxprenolol hydrochloride, methoprolol hydrochloride, cimetidine hydrochloride, dextromethorphan, and the like. Exemplary drugs that have limited solubility in water and can be delivered by devices of this invention include meclizine hydrochloride, phenoxybenzamine, thiethylperazine maleate, anisindone, erythrityl titranitrate, dizoxin, reserpine, acetazolamide, methazolamide, bendroflumethiazide, chlorpropamide, tolazamide, chlormadinone acetate, aluminum aspirin, methotrexate, acetyl sulfisoxazole, erytbhromycin, progestins, estrogine, progestational, corticosteroids, and the like. Examples of other drugs that can be delivered by the devices include aspirin, indomethacin, naproxen, fenoprofen, sulidac, diclofenac, indoprofen, propanolol, metroprolol, oxprenolol, timolol, clonidine, theophylline, ferrous lactate, phenoxybenzamine, baclofen, furosemide, and the like. The beneficial drugs are known in the art in Pharmaceutical Sciences , by Remington, 14th Ed., 1979, published by Mack Publishing Co.; The Drug, The Nurse, The Patient, Including Current Drug Handbook , by Falconer et al., (1974-1976), published by Saunder Company; and Medicinal Chemistry , 3rd Ed., Vols. 1 and 2, by Burger, published by Wiley-Interscience Co. The drug can be present in the tiny pill in various forms, such as unchanged molecules, molecular complexes, therapeutically acceptable salts such as hydrochlorides, hydrobromides, sulfates, oleates, and the like. For acid drugs, salts of metals, amines, or organic cations, quaternary ammonium salts can be used. Derivatives of drugs such as esters, ethers and amides can be used. Also, a drug that is water insoluble can be used in a form that is the water soluble derivative thereof to serve as a solute and, on its release from the device, is converted by enzymes, hydrolyzed by body pH or other metabolic process to the original biologically active form. The amount of drug present in a tiny timed pill generally is from about 10 mg to 50 mg. The number of tiny pills in a given amount of liquid means is from 10 to 1000 in, for example, a cm³ of liquid, or more. The tiny pills comprising an exterior wall and an inner core of drug generally have a diameter of about 50 µm to a diameter of 4000 µm and in a presently preferred embodiment a diameter of at least 200 µm. The wall thickness can vary as an aid in controlling the release of drug, with wall thickness exemplified as from 0.01 mm to 3.00 mm and the like. EXAMPLE 1 An orally administrable dosage form comprising tiny pills of a cough suppressant housed in a liquid member is prepared as follows: first, dextromethorphan hydrobromide and succinic acid in a ratio of 0.5 to 1 are blended and blended with hydroxypropylmethylcellulose in bead form, and then divided in three equal fractions of three different sizes of 0.1, 0.2 and 0.3 mm radius. The spherical beads are coated next with a wall forming composition. The composition comprises a blend of cellulose acetate having an acetyl content of 39.8% and cellulose acetate butyrate comprising an acetyl content of 29% and a butyryl content of 17%. The cellulose acetate and the cellulose acetate butyrate are present in a 50:50 blend, the cellulose acetate butyrate has a permeability k equal to 5 · 10⁻⁹ cm²/h 2 X 10⁻⁵ cm.mil/h), and the cellulose acetate has a permeability k of 2,5 · 10⁻⁸ cm²/h (10⁻⁴ cm.mil/h). The wall forming composition is applied from an organic solution containing methylene chloride and to the wall applied in a ratio of 1 to 1. Next, the solvent is stripped from the pills and the tiny pills permitted to dry at room temperature. Then the tiny pills are added to a liquid means comprising 5 cm³ of lemon tincture, 5 cm³ of orange tincture, 0.5 g sodium saccharide, 65 cm³ propylene glycol, 15 ml glycerin and sorbitol solution to 100 cm³. The dosage form optionally can be stored in Container 30, as seen in Figure 8. Container 30 is equipped with a pouring member 31 for delivering tiny pills 13 in liquid means 16 to a spoon, or the like, for administering to a patient. EXAMPLE 2 Another dosage form is prepared by following the procedure of Example 1, except that in this example dextromethorphan and mannitol are blended as dry particles in a ratio of 10 to 1. The particles are coated in a fluid air suspension machine with a composition of ethyl cellulose in ethanol to surround the drug core with a wall of the cellulose to yield tiny pills thereof. After the solvent is vacuum stripped from the tiny pills, the pills are blended with a solution comprising sorbitol, propylene glycol, alcohol, water and orange oil. EXAMPLE 3 Another dosage form is provided by coating a drug core composition comprising phenylpropanolamine hydrochloride, lactose and magnesium stearate in a fluid air suspension machine with a composition comprising ethyl cellulose in ethanol to surround the drug core with a wall of ethyl cellulose to yield tiny pills thereof. After the solvent is vacuum stripped from the tiny pills, the pills are blended with a solution comprising sorbitol, propylene glycol, alcohol, water and orange oil. EXAMPLE 4 The above manufacture can be repeated by replacing the ethyl cellulose and ethanol with cellulose acetate having an acetyl content of 39% in methylene chloride-methanol wall-forming solvent; the tiny pills are added to a hypertonic liquid means. EXAMPLE 5 A dosage form is manufactured by first preparing sustained release tiny pills by blending 40 g of polyvinyl pyrrolidone with 375 g of theophylline, the blend kneaded and passed through an extrusion granulation machine to produce drug cores with an average radius of 0.1 mm. After drying at 46-49°C (115°-120°F), the drug cores are coated with a wall of ethyl cellulose in an air suspension machine to yield tiny pills. The tiny pills are added to a liquid means comprising 0.8 g of powdered gelatin type A, 50 cm³ of edible oil and sufficient water to 100 cm³. The liquid means is prepared by following the procedure in Pharmaceutical Sciences , by Remington, 14th Ed., (1970), p 1492, published by Mack Publishing Co., Easton, PA. The dosage form can be used for orally administering the bronchodilator for the management of status asthmaticus and as a pulmonary vasodilator and smooth muscle relaxant. Other forms of theophylline can be used in the subject dosage form such as theophylline sodium acetate, theophylline sodium glycinate, [7-(2,3-dihydroxypropyl)] theophylline, theophylline meglumine, and theophylline monoethanolamine. EXAMPLE 6 In another manufacture, the dosage form is made by first preparing sustained release tiny pills by blending 400 cm³ of ethyl cellulose-water, 70:30 solution, 7.5% w:v, with 375 g of theophylline, 150 g of mannitol and 475 g of magnesium stearate and the blend kneaded and passed through an extrusion granulation machine. After drying at 46 - 49 °C (115°-120° F), the core are passed through a 840 µm (20 mesh) screen and coated with a wall of ethyl cellulose in an air suspension machine to yield tiny pills. The tiny pills are added to a liquid means comprising 0.8 g of powdered gelatin type A, 0.8 g of tartaric acid 0.1 g of citric acid, 0.1 g of ascorbic acid, 6 cm³ of alcohol, 50 cm³ of edible oil and sufficient water to 100 cm³. The liquid means is prepared by following the procedure in Pharmaceutical Sciences , by Remington, 14th Ed., (1970), p 1492, published by Mack Publishing Co., Easton, PA. The dosage form can be used for orally administering the bronchodilator for the management of status asthmaticus and as a pulmonary vasodilator and smooth muscle relaxant. Other forms of theophylline can be used in the subject dosage form such as theophylline sodium acetate, theophylline sodium glycinate, [7-(2,3-dihydroxypropyl)] theophylline, theophylline meglumine, and theophylline monoethanolamine. EXAMPLE 7 Other delivery systems comprising tiny pills are made by spraying non-pareil cores with an edible adhesive and then dusting the adhesive coated core with a drug. The drug coated core then is coated with an appropriate edible enteric coat to provide enteric coated tiny pills. In a preferred manufacture at least one enteric coat is applied in this embodiment of the invention, but more than one coat, usually 1 to 20 separate coats, can be used for the present purpose. Manufacturing procedures for tiny pills are taught in U. S. Pat No. 3,365,365. EXAMPLE 8 In another embodiment the tiny pills can be made from a core of carbohydrate, such as sucrose, dusted with a mixture of talc, starch and galactose, moistened with distilled or deionized water, and the desired medicinal such as the antibiotic erythromycin. The pills are dried and then coated with an outer layer of a nontoxic, enteric wall former selected from the group consisting of keratin, calcium alginate, shellac, partially hydrolyzed styrene-maleic acid copolymer, polyvinyl acetate phthalate, polyvinyl hydrogenphthalate, and the like. Finally, the tiny pills are dispersed and/or suspended in an acidic liquid means adapted for oral admittance into the gastrointestinal tract. Procedures for manufacturing the tiny pills are described in U. S. Pat. No. 3,081,233. EXAMPLE 9 A drug with an osmotic pressure of 10 MPa (100 atmospheres, atm,) as ascertained by using an osmometer, is granulated into particles of various size radius from 0.1 to 0.5 mm. A wall forming polymer is coated in a ratio of 1:1 onto the drug. The elongation defined as the ratio of the increase in radius at bursting to the original radius of the particle is 0.5. The polymer selected for the coating process can have a variety of water sorption characteristics resulting in a water content of up to 30 percent, or X = 0.3. The bursting time by osmosis for each tiny pill is given in accompanying Figure 9. In Figure 9, Tb(Hr) is the bursting time in hours for a tiny pill, R o is the radius in mm of the uncoated particle, and X is the fraction of water in the wall. From Figure 9, it is clear that a total mass of formulation can be prepared with various mass fractions of particle sizes which are coated with various polymers of different elongation and water sorption. EXAMPLE 10 A drug delivery system is prepared comprising tiny pills in a liquid means. The tiny pills deliver the drug by osmotic bursting of the wall to form in the gastrointestinal environment a drug release orifice in the wall of the tiny pill. The tiny pills were prepared from osmotic particles of drug exhibiting an osmotic pressure of 40 atm, and the drug was shaped into spheres of 0.1, 0.2 and 0.3 mm. The liquid means has an equivalent or higher osmotic pressure. The polymer comprising the wall had an elongation of 0.5 mm and a water permeability of 25 X 10⁻⁸ cm²/h. The drug has a density of 1.2 g/cm³. One gram of the drug exhibited a bursting time and a delivery rate dependent of the radius of the particle as shown in accompanying Figure 10. In Figure 10, R o (mm) is the radius of the particles in mm, and Rate (g/h) is the rate of drug delivery in grams per hour. The study indicates, from the accompanying Figure 10, that a mixture of particles can be provided to give a release rate given by Equation (a) wherein f₁, f₂, f₃ are in Equation (a) the fraction of particles present of rate R₁, R₂ and R₃, respectively. R = f₁ R₁ + f₂ R₂ + f₃ R₃ (a) The drug dextromethorphan hydrobromide exhibits an osmotic pressure of 4 MPa (40 atm). The osmotic solute sucrose in aqueous solution is formulated to an osmotic pressure exceeding 4 MPa (40 atm). EXAMPLE 11 The delivery of a drug from a tiny pill that releases the drug by osmotic bursting of the wall to provide a drug releasing orifice is seen from the following presentation and the accompanying equations. The tiny osmotic bursting pills in an aqueous media that is hypotonic compared to the compositon inside the tiny pills imbibes water into the tiny pills. In the absence of a preformed orifice in the wall of the tiny pill, the imbibed aqueous fluid causes the tiny pill to swell and a volume increase occurs during which time period (Δ t₁) the delivery rate from the system is low. When the internal hydrostatic pressure exceeds the pressure necessary to rupture the wall, the release rate increases to a maximum during the period Δt₂, after which the rate again decreases when all the solid excess drug from the core is delivered. A typical curve depicted in Figure 11. The release rate from the osmotic bursting tiny pills is described by Equation (1) with (dV/dt) t given by Equation (2). wherein in Equation (1) and Equation (2), C is the concentration of the drug solution hydrodynamically pumped, (dm/dt) D is the amount of drug delivered by diffusion through the wall, (dV/dt) t is the total volume of solution hydrodynamically pumped from the tiny pill which is equal to the volume of water imbibed by the tiny pill as set forth in Equation (3), minus the volume increase of the tiny pill per unit time (dV/dt) V . Further, wherein A is the wall area, h is the wall thickness, σ the reflection coefficient of the wall, Δπ and ΔP are the osmotic and hydrostatic pressure difference between the inside and outside of the wall. From the time, t=0, a small amount of drug is usually delivered in the absence of an orifice by diffusion through the wall as described by (dm/dt) D . During this time period, Δt₁, the volume increase is equal to the volume imbibed, as set forth in Equation (3a). The effect of the volume stretching during the period Δt₁ is twofold: 1. delay in delivery and 2. the system potential zero order delivery profile is substantially shortened since the amount of drug that is delivered at a non-zero order rate is seen in Equation (4): wherein V is the volume at the time of bursting, which is larger than the undeformed volume. S is drug solubility. According to Equation (5) the mass not delivered at zero order is: since the volume deformation associated with Figure 11 is largely plastic or permanent deformation. Thus, by selecting the mechanical properties of the wall and thereby controlling the function (dV/dt) V , as a function of pressure or elongation, several release rate profiles can be programmed for the tiny pills as described by the basic spike type curve obtained by plastic deformation of the wall as seen in Figure 11, and by selecting an elastic wall a curve can be obtained as seen in Figure 12. In Figure 12, Δt is the elastic deformation, Δt₂ is the elastic recovery and Δt₃ is the osmotic pump kinetics. Thus, by selecting a brittle wall wherein early aperture formation occurs without deformation, a zero order rate profile can be obtained for the tiny pills, as seen in Figure 13, wherein a is the brittle fracture and G is the release rate for a conventional zero order curve. Accompanying Figure 14 illustrates in opened section a tiny pill designed for releasing a drug by an osmotic bursting mechanism. In Figure 14, a pill 10 is seen comprising an osmotically active drug core 32 surrounded by a semipermeable wall 33. In operation, when pill 10 is in a water environment, it imbibes water by osmosis and the internal volume increase per unit time is described by Equation (6): wherein A is the area of the semipermeable wall, h is the thickness of the wall, k is the permeation constant, Δπ is the osmotic pressure difference between the solution inside and outside the tiny pill, and ΔP is the hydrostatic pressure differences between the inside and the outside of the pill. The internal volume expands from V o , the volume at time zero, to V b , the volume at bursting time, t b . The bursting time is obtained from Equation (6) and given by Equation (7): The quantities h, k, A, π, and P are all functions of volume; and during the initial stages of swelling when the solution inside the system is saturated, Equation (8) holds: Δπ = π o (8) and when the osmotic pressure of the outside solution is negligible, π o is the osmotic pressure inside the system up to a volume V, as expressed by Equation (9): wherein M p is the mass of the drug particle and S is the solubility of the drug. Thus, for most applications, the volume at bursting V b is smaller than V as given by Equation (8) and Equation (9). The quantities A, h, and V can conveniently be expressed as a function of the system radius r as seen in Equation (10) and Equation (11): A = 4 πr² (10) V = 4 3 πr³ (11) Assuming that the drug wall deforms at constant volume results in Equation (12): For a thin walled system, the mass of the wall is given by Equation (13): M c = 4 π r o ² . h o . ρ c (13) wherein ρ c is the density of the wall. The mass of the drug is given by Equation (14): M p = 4 3 πr o ³ . ρ p (14) wherein ρ p is the density of the drug. The ratio of drug to the wall weight from Equation (13) and Equation (14) is combined in Equation (15): accompanied by the assumption ρ p ≅ ρ c , then Equation (16) follows: Thus, for a soft walled system wherein the hydrostatic pressure P can be neglected compared to the osmotic pressure, Equation (7) can be simplified to Equation (17) by substituting Equation (12) as follows: Equation (17) results in Equation (18) and Equation (20) by substituting Equation (19) and Equation (16) as follows: The zero order delivery rate from the capsule pill system follows the osmotic bursting of each wall of the pill system wherein delivery of drug by osmosis is given by Equation (21): dm dt = k . π o . A h . S (21) For a total mass of drug M to containing N particles of mass M o the total surface area is A to such that Equation (22) and Equation (23) result in Equation (24) set forth as follows: A to = N . 4 πr o ² (22) M to = N . 4 3 πr o ³ . ρ p (23) The delivery rate given by Equation (21) contains the ratio A/h of area and a wall thickness at the time of bursting. This ratio can be calculated as a function of the original value A o /h o and the elongation Eℓ . According to Equation (12) it follows that Equation (25) results. substituting Equation (12) in Equation (25) yields Equation (26). r = (Eℓ + 1) r o (27) Equation (27) exists according to Equation (19) such that Equation (26) and Equation (27) result in Equation (28): The total release rate of N particles of drug follows from Equation (21) and Equation (28) to yield Equation (29) as follows: Since N . A o is given by Equation (24), Equation (30) results as follows: The drug loading is defined by Equation (31): followed by substituting Equation (16) in Equation (30), results in Equation (32) as follows: and for a single particle system, Equation (33) and Equation (34) are presented as follows: Control over the bursting time and release rate can then be programmed by selecting drug and osmotic properties, respectively π o and S, loading L, drug particle size, r o , and the wall composition which defines k, and Eℓ for the above described system with a wall from which delivery occurs in the extended state at r = r b , the release rate and bursting time are inversely proportional as can be seen by eliminating r o ² between Equation (33) and Equation (20) as shown in Equation (35): The duration of the zero order rate over t z of such a particle is given by Equation (36) where Z is the zero order rate: wherein M pz is the mass delivered at zero order rate given by Equation (37). which is the same relation for an elementary osmotic pump for which r = r o . The ratio of r/r o from Equation (19) yields Equation (38): From Equation (38) and Equation (33) it follows that: Thus, for mathematically ascertaining the time course from the initial burst to the end of the zero order delivery period, it now is possible to calculate the ratio of t z to t b from Equation (39) and Equation (20), the resulting Equation (40): wherein Equation (40) holds for the delivery system except for the conditions Eℓ = 0 when t b = 0. The non-zero order rate of release from the tiny pill systems can be expressed by the equations presented below. Thus, according to this study, beyond the zero order time t z the bursted pills deliver in a manner like an elementary osmotic pump; however, at an extended volume consistent with the burst radius. This non zero order rate can be described in the usual probability declining manner where Z is the zero order rate according to Equation (41) as follows: Combining Equation (11) and Equation (19) leads to Equation (42): From Equation (20), Equation (39), Equation (34) and Equation(40) it is evident that the delivery profile of such particles is strongly dependent on the elongation Eℓ. For small values of Eℓ ≅ 0.5, the zero order time is a small fraction of the bursting time t z /t b = 0.3 for an average drug with a particle density 1 g/ml and drug solubility 0.3 g/cm³. Thus, each individual pill will mostly have a small amount of its drug delivered at zero order. The design of a pill formulation will, by choice, be composed of a mixture of drug with different membrane compositions to adjust k and the bursting time. In addition to coating loading L and osmotic pressure of the drug formulation as well as pill size are very useful variables to control for several of the weight fractions of the formulation. The wall permeability k is a function of the water sorption X defined by the fraction of water in the saturated wall. This function is described by Equation (43) to describe the data X = 0.02 to X = 0.5 as follows: k = 3.5 x 10⁻⁸ exp(19.7 X) (43) k is in units [cm²/h · 0.1 MPa] From Equation (20) and Equation (43) the aperture bursting time in a tiny pill system up to 24 hours is in the approximate range of elongations of 0.1 to 0.5, a drug loading L = 0.1 to 3, osmotic pressures up to 30 MPa (300 atm), the preferred drug particle size is r o = 0.001 to 0.1 cm, with wall permeabilities up to 9 X 10⁻⁵ cm²/h · 0.1 MPa (cm²/hr.atm). The expressions also indicate that longer bursting times can be achieved for polymers with higher elongations. EXAMPLE 12 A beneficial drug is administered to an animal host, such as a human at a controlled rate, comprising the steps of: (A) admitting orally into the gastrointestinal tract of a human a delivery system comprising: (1) drug dispensing means comprising: (a) a core of a beneficial drug; and (2) wall means for controlling the release of the beneficial drug from the dispensing means, which wall means surrounds the core of beneficial drug; and (2) means for delaying the release of the beneficial drug from the drug dispensing means, said means a liquid composition comprising a plurality of the drug dispensing means; and (B) delivering the beneficial drug by permitting the environment of the gastrointestinal tract to contact and dilute the liquid composition, whereby the drug dispensing means release the beneficial drug at a controlled rate to the gastrointestinal tract over a prolonged period of time. EXAMPLE 13 Another dosage form is provided by coating a drug core composition comprising procainamide hydrochloride, lactose and magnesium stearate in a fluid air suspension machine with a composition comprising ethyl cellulose in ethanol to surround the drug core with a wall of ethyl cellulose to yield tiny pills thereof. After the solvent is vacuum stripped from the tiny pills, the pills are blended with a solution comprising sorbitol , propylene glycol, alcohol, water and organe oil. It will be appreciated by those versed in the art the present invention makes available novel and useful delivery system for dispensing a beneficial drug over a prolonged period of time.

Claims: A delivery system for the controlled delivery of a drug to an environment of use, the delivery system comprising: (a) a plurality of tiny pills, which tiny pills comprise: (1) a wall formed of a semipermeable cellulosic polymer permeable to the passage of external fluid and impermeable to the passage of drug, which semipermeable wall surrounds: (2) a composition comprising a concentration of beneficial drug; and (b) a pharmaceutically acceptable liquid carrier containing the plurality of tiny pills; and wherein the dosage form is characterized by: (c) drug in the tiny pills exhibiting an osmotic pressure gradient across the semipermeable wall, and drug in the liquid carrier exhibiting an osmotic pressure gradient equal to the osmotic pressure of the tiny pills for preventing release of drug through the semipermeable wall when the tiny pills are in the liquid carrier.

Inventors: THEEUWES FELIX, THEEUWES, FELIX
Applicants: ALZA CORP, ALZA CORPORATION
Application year: 1988
Main classification: A61K9
IPC codes: A61K9