CONTROLLED RELEASE TABLET

Abstract: A controlled release tablet including a pharmaceutical agent and an excipient. The excipient includes at least about 50 % of a water swellable polymer and a lubricant. The water swellable polymer is chosen such that the swelling rate of the polymer is equal to the dissolution rate of the swollen polymer. The excipient may also include such other ingredients as diluents, fillers, binders and other pharmacologically inactive compounds. The polymer is chosen with the pharmaceutical agent in mind such that the tablet will be fully dissolved at the same time that the last of the pharmaceutical agent is released.

Description: CONTROLLED RELEASE TABLET The present invention relates to sustained release tablets including any of a wide array of pharmaceutical products and an excipient. Many attempts have been made in the pharmaceutical art to provide a composition which would enable the production of sustained release tablets. These attempts have produced compositions which are able to release pharmaceutical agents over a long period of time. However, such release has not been constant. Rather, prior art sustained release compositions generally release a disproportionate amount of their pharmaceutical agent quickly after ingestion by a patient. This results in a quick spike in the level of medication in the patient's bloodstream. Such a delivery method may be desirable where the pharmaceutical is intended to alleviate particular symptoms of a patient. However, there are many instances where a spike in the medication level in a patient is undesirable, as where pharmaceuticals are used to treat a chronic condition. Further, extended release of biologically active drugs is highly desirable for drugs that have characteristically short half lives. Monolithic systems, composed of hydrophobic polymers and other excipients, are commonly used for extended release dosage forms because they are not costly or difficult to produce. However, such systems often provide a square-root-of-time (sqrt) kinetics (i.e. the amount of pharmaceutical agent released is proportional to the square root of the time since the drug was ingested). There are several ways to improve the release kinetics of extended release dosage forms. Incorporation of hydrophilic polymers into monolithic matrices modifies square root kinetics due to the swelling of the polymer. In particular, monolithic matrix systems controlled by the swelling/erosion processes of hydrophilic polymers can improve the pharmaceutical agent kinetics. However, even in these systems, the release rate of the pharmaceutical agent generally varies significantly with time. Hydrophilic polymers alone have also been investigated for controlled drug release. The hydrophilic polymers such as hydroxypropylmethyl cellulose (HPMC) and polyvinylalcohol (PVA), which form gels upon contact with water and erode slowly, have been utilized for oral drug delivery systems. Cross-linked poly(ethylene oxide) has also been investigated for controlled drug delivery. However, attempts to use these materials to produce a constant, controlled, sustained drug release have thus far proven ineffective. The present invention provides a controlled release tablet including a pharmaceutical agent and an excipient. The excipient includes at least about 50% of a water swellable polymer and a lubricant. The water swellable polymer is chosen such that the swelling rate of the polymer is equal to the dissolution rate of the swollen polymer. The lubricant is generally present in an amount of up to 3% of the excipient as a whole. The excipient may also include such other ingredients as diluents, fillers, binders and other pharmacologically inactive compounds. Further, the polymer and pharmaceutical agent are complementary. In selecting a water swellable polymer, the polymer should be chosen with the pharmaceutical agent in mind such mat the tablet will be fully dissolved at the same time that the last of the pharmaceutical agent is released. The preferred water swellable polymer is polyethylene oxide. The pharmaceutical agent is released from the tablet at a rate which can be expressed by M/M^kf 1 where t is time, M, is the amount of the pharmaceutical agent which has been released at time t, M τ is the total amount of the pharmaceutical agent contained in the tablet, k is a constant, and n is the release kinetics exponent and has a value between about 0.89 and 1.0. Figure 1 is a graph of the gel thickness and tablet diameter versus time for various molecular weights of PEO polymer. Figure 2 is a graph of the fractional release of theophylline from PEO tablets versus time, for various molecular weights of PEO polymer. Figure 3 is a graph of the fractional release of theophylline from PEO tablets versus time at varying pH levels. Figure 4 is a graph of the fractional release of theophylline and diltiazem hydrochloride from 0.9 x 10 6 molecular weight PEO tablets versus time for varying drug loadings. Figure 5 is a graph of the fractional release of theophylline and diltiazem hydrochloride from 2.0 x 10 6 molecular weight PEO tablets versus time for varying drug loadings. Figure 6 is a graph of the fractional release of theophylline from 0.9 x 10 6 molecular weight PEO tablets versus time for various rates of agitation. Figure 7 is a graph of the release exponent (n) versus solubility of the drug for tablets of PEO of various molecular weights. Figure 8 is a graph of the fractional release of various drugs versus time from tablets of 0.9 x 10 6 molecular weight PEO. Figure 9 is a graph of the fractional release of various drugs versus time from tablets of 2.0 x 10 6 molecular weight PEO. Figure 10 is a graph of the fractional release of various drugs versus time from tablets of 4.0 x 10 6 molecular weight PEO. Figure 1 1 is a graph of the fractional release of theophylline versus time from tablets formed from hydroxypropylmethylcellulose of varying viscosity. Figure 12 is a graph of the fractional release of theophylline from tablets of PEO having a molecular weight of 4.0 x 10 6 and from tablets of HPMC having a viscosity of 1500 - 1800 centipoise and having a hole through the center thereof Figure 13 is a graph of the fractional release from Procardia XL tablets having 30 mg and 60 mg of drug per tablet. Figure 14 is a graph of the fractional release of nifedipine from tablets of PEO having various molecular weights having 10 percent nifedipine. Figure 15 is a graph of the fractional release of nifedipine from tablets of PEO having a molecular weight of 4.0 x 10° and having various amounts of polyethylene giycol added thereto. Figure 16 is a graph of the fractional release of nifedipine from tablets of PEO having a molecular weight of 4.0 x 10° and having various amounts of polyethylene giycol added thereto, compared to the fractional release of nifedipine from a Procardia XL tablets having 30 mg drug per tablet. Figure 17 is a graph of the fractional release of nifedipine from tablets of PEO having a molecular weight of 4.0 x 10 6 having 20 percent nifedipine and having various amounts of polyethylene giycol added thereto. Figure 18 is a graph of the fractional release of nifedipine from tablets of PEO having a molecular weight of 4.0 x 10 6 and having various amounts of polyethylene giycol added thereto, compared to the fractional release of nifedipine from a Procardia XL tablets having 60 mg drug per tablet. Figure 19 is a graph of the fractional release from Procardia XL tablets having 30 mg and 60 mg of drug per tablet compared to the fractional release of nifedipine from tablets of PEO having a molecular weight of 4.0 x 10 6 and having various amounts of nifedipine therein. Figure 20 is a graph of the fractional release of nifedipine from tablets of PEO having a molecular weight of 4.0 x 10 6 and 10 percent nifedipine per tablet. The excipients of the present invention have been formulated to allow controlled sustained release of any one of a number of pharmaceutical agents. The excipients of the present invention generally comprise a hydrophiϋc polymer and a lubricant. Other pharmacologically inactive materials can also be added. The excipients can be mixed with a wide range of medications and directly compressed into solid dosage tablets. The following drugs with which the present invention may be used are set forth as examples only. Any suitable drug may be used with the present invention, including nifedipine, diclofenac NA, salicylic acid, theophylline anhydrous, sulfapyridine, sulfadrazine, propranolol hydrochloride, and diltiazem hydrochloride. Polyethylene giycol is generally used to increase the solubility of relatively insoluble drugs to encourage absorption by the body. The polymers set forth herein may be compressed into tablets directly. Alternatively, binders, fillers, or other typical compounding agents may be added to adjust the properties of the final tablets. Particularly, but without limitation, the following compounds may be included: lactose, dextrose, sucrose, and calcium phosphate. Specifically, the polymeric materials useful in the present invention will depend to a certain extent on the pharmaceutical agent chosen to be aα'mir-istered. Polymers of choice include uncrosslinked poly(ethylene oxide) (PEO) and hydroxypropyl methylcellulose (HPMC) both of varying molecular weight and viscosity respectively. HPMC is available on the basis of viscosity measured in a 2% solution in water. PEO is availiable on the basis of molecular weight. Both PEO and HPMC are useful alone. Alternatively, mixtures of the two materials, or mixtures of various viscosities or molecular weights of either compound may be used in the present invention. During the release of drugs from hydrophilic matrices of PEO or HPMC, two mechanistic phenomena take place: the swelling and the erosion of the polymer. The release kinetics of the drug from the tablet are dependent upon the relative magnitude of the rate of polymer swelling at the moving rubbery/glassy front and the rate of polymer erosion at the swollen polymer/dissolution medium front. It is most preferable to attain the synchronization of the velocities of the swelling front and the erosion front in order to achieve zero-order release kinetics from hydrophilic polymer matrices. The release kinetics for the release of a pharmaceutical agent from a tablet can be approximated by the following equation: (1) M/M τ =k where t is time, M t is the amount of the pharmaceutical agent which has been released at time t, M τ is the total amount of the pharmaceutical agent contained in the tablet, k is a constant, and n is the release kinetics exponent. This equation is valid so long as n remains nearly constant. When n is about equal to one, the release of the pharmaceutical agent from the tablet has zero-order kinetics. The amount of pharmaceutical agent released is then directly proportional to the time. Where the swelling process of the polymer chosen for the excipient is the primary process controlling the drug release (compared to erosion of the swollen polymer), non-zero order release kinetics result. Generally, these release kinetics dictate a value of n approaching 0.5, leading to square-root Fickian-type release kinetics. Accordingly, a polymer must be chosen which will swell and erode readily, to allow erosion resulting in zero-order release kinetics. Drug release from uncross-linked low molecular weight PEO of MW (molecular weight) equal to about 0.6 x 10 6 (laminated films) ensures a constant release rate by achieving synchronized gel thickness. That is, the rate of swelling of the polymer is approximately equal to the rate of erosion of the swollen polymer. On the other hand, the drug release from the high molecular weight PEO of MW = 4xl0 6 is predominantly controlled by the swelling of the polymer rather man the erosion of the polymer. This can result in a non-constant release induced by the diffusion of drugs through the swollen gel layer, especially in high solubility drugs. Drug release from PEO tablets is governed by swelling/drug diffusion or swelling/polymer erosion depending upon the characteristics of the different molecular weights of the hydrophilic polymers. In order to distinguish between the two mechanisms, swelling experiments involving drug-free tablets of PEO of MWs = 0.9xl0 6 , 2xl0 6 , and 4xl0 6 were carried but although PEO with a molecular weight of up to 8xl0 6 can also be used with more insoluble drugs. The swollen gel thickness and outer diameter of a drug-free PEO tablet are shown in Figure 1. Figure 1 shows that a constant gel thickness is obtained with the PEO tablets of MWs=0.9xl0 6 and 2xl0 whereas the swollen gel thickness from the PEO tablet of 4x10 6 keeps increasing with time. As can be seen from Figure 1 , in the early time of the swelling/erosion process, the overall size of the tablet along with the gel layer increases rapidly due to the immediate swelling of the PEO tablet. The swelling rate of the polymer equals the dissolution rate of the swollen polymer gel, resulting in the synchronization of the gel layer thickness. The release kinetics of the tablet are also dictated by the pharmaceutical agent itself. A drug which is highly soluble will tend to be released faster than drugs which have low solubility. Where a drug has high solubility, polymer swelling and erosion must take place rapidly to maintain a zero order release kinetics. If the swelling and erosion take place too slowly, the swelling process of the polymer is the primary process controlling the drug release (since the drug will diffuse from the swollen polymer before the polymer erodes). In this situation, non-zero order release kinetics result. As a result, the administration of a highly soluble pharmaceutical agent requires a relatively rapidly swelling and eroding excipient. To use such a material to produce a tablet which will last for 24 hours can require a large pill. To overcome this difficulty, a doughnut-shaped tablet with a hole though the middle can be used with a less rapidly swelling and eroding polymer. With such a tablet, the surface area of the tablet increases as the tablet erodes. This exposes more polymer, resulting in more polymer swelling and erosion as the tablet shrinks in size. The type of tablet can also be used with very highly soluble pharmaceutical agents to maintain zero order release kinetics. Conversely, the delivery of an insoluble pharmaceutical agent is dictated only by the erosion of the swollen polymer layer, since there will be no diffusion and dissolution of the pharmaceutical agent out of the swollen polymer matrix. Accordingly, relatively slow swelling and eroding polymers can be used. In this case, if a sufficiently slow polymer is used, a tablet can be made very small with a higher concentration of pharmaceutical agent than would be used in a normal-sized tablet. This would result in a very small but very effective sustained release tablet. EXAMPLE POLYOX-WSR NFs (non-crosslinked polyethylene oxide) of average molecular weight of 0.9x10 6 , 2xl0\ and 4xl ) was obtained from Union Carbide Corporation (Danbury, Connecticut). Theophylline anhydrous U.S. P. and magnesium stearate U.S. P. were obtained from Amend Co. (Irving, New Jersey) and Mallinckrodt Chemical (Jersey City, New Jersey), respectively. Diltiazem HC1 was obtained from Sigma Chemical Co. (St. Louis, Missouri). Hydroxypropylmethylcellulose was obtained from Dow Chemical (Midland, Michigan) and Shin-Etsu Chemical Co., Ltd. (Tokyo, Japan). The materials were used as received. The ingredients (PEO, drug, and magnesium stearate) were mixed and then tableted using a single punch tablet machine (Stokes Model F, Philadelphia, Pennsylvania). A set of tablet punches with flat surfaces were used to prepare tablets with an 8.1 mm diameter. They were charged with the formulation, and the compression was exerted by turning over the machine by hand. The hardness of the resulting tablets was 5.5 to 7.0 Kp (Schleuniger Model 2E/106, Switzerland). The resulting tablets weighed about 160 mg. In vitro release of drugs from the different formulation tablets was carried out by using the USP basket procedure in distilled/deionized water at a stirring rate of 100 rpm and 37°C, if not otherwise stated. Theophylline and diltiazem HC1 were chosen as model drugs. The release of theophylline and diltiazem HC1 was assayed by a HP8252A (Hewlett Packard Corporation) diode-array spectrophotometer at 244 nm and 266 nm, respectively. The release kinetic data (up to 60% release) were treated by equation ( 1) above. After this point, frequently n was no longer constant, and therefore equation ( 1 ) did not apply. According to the criteria for release kinetics from a swellable matrix (cylindrical shape), zero-order and anomalous transport kinetics are represented by 0.89 < n < 1.0 and 0.45 < n < 0.89, respectively. A linear regression analysis (Microsoft Excel 5.0) of the logarithmic form of equation ( 1) was carried out with R 2 > 0.99. Both circular faces of the cylindrical tablet were covered with two transparent Mylar sheets, fixed onto the bases via an epoxy glue. The covered tablet was then introduced into water as a dissolution medium. The tablet was withdrawn periodically, and the moving boundaries both at the glassy/rubbery interface and at the matrix/dissolution medium interface were measured via a stereo microscope (Olympus SZ60) with a measuring device attachment. The tablet was then returned to the bath. As can be seen from Figure 1, the synchronization of the gel layer thickness takes place earlier with the low molecular weight PEO and shortly after the outer diameter starts becoming smaller. The higher the molecular weight, the later the synchronization takes place. However, for a higher molecular weight PEO tablet (4x l0 6 ) the synchronization of the gel layer did not occur and the gel layer thickness increased until the entire tablet was in gel form. After the front meets at the core of tablets, the swollen PEO gel lasts a much longer time than other swellable/erodible polymers such as PMMA/MAA and PVA. The swollen PEO gel layer can last 2 to 4 hours depending upon the molecular weight of the PEO. As a result of this long residence time of the gel layer, it is expected that the release kinetics are governed by the erosion/drug diffusion process after the swelling front meets at the core of the tablet. Figure 2 shows the effect of PEO molecular weight on drug release of theophylline from tablets. The rate of dissolution (erosion) of hydrophilic polymers decreases with increasing molecular weight. This causes different molecular weights of PEO to have different values for the release exponent (n). For the release of theophylline from PEO tablets, the value of the release exponent (n) was 0.99 (±0.024), 0.80 (±0.004), and 0.83 (±0.019) for tablets formed from PEO having molecular weights of 0.9x l0 6 , 2xl0 6 , and 4xl0 6 , respectively. The lower molecular weight PEO (MW=0.9xl0 6 ) tablet exhibits a constant release rate, whereas PEO tablets having molecular weights of 2xl0 6 and 4xl0 6 may vary, depending on the solubility of the drug used. Accordingly, the synchronized gel thickness plays an important role on the release kinetics at the early time of drug release. As the molecular weight of the polymer increases, the dissolution rate of the polymer decreases compared to the swelling rate of the polymer. The "dissolution rate" and the "erosion rate" are used here interchangeably. In actuality, the decrease in the size of the swollen gel layer is due both to erosion and dissolution. Due to the low dissolution rate, die thickness of the polymer layer increases. Drug diffusion through the swollen gel layer then becomes the foremost process controlling the release mechanism. With high molecular weight (or high viscosity grade) polymers of PEO and HPMC, the swelling of the polymer is the dominant step in controlling release kinetics over the erosion of swollen polymer. With low molecular weight polymers of PEO and HPMC, the erosion of the polymer is the rate determining step for the release kinetics. However, the degree of swelling of PEO is higher than HPMC resulting in more favorable kinetics for PEO than for HPMC. The release of theophylline from PEO tablets is not significantly influenced by the pH variation of the dissolution medium, as shown in Figure 3. Therefore PEO may be a good candidate for oral drug delivery systems because oral dosage forms travel along the gastrointestinal tract in which the pH changes from an acidic environment (pH < 2) in the stomach to a weak base (pH about 8) in the intestines. PEO tablets having varying loadings of pharmaceutical agents were tested to determine the effect of loading on the release kinetics. The results are shown in Figures 4 and 5. No significant difference in release rate was observed with the different drug loadings in PEO tablets. The release kinetics of PEO tablets of MW=0.9x 10 6 remain unchanged with the exponent n ranging from 0.90 (±0.016) to 0.99 (±0.024) even though the drug loading is increased. Even for PEO tablets of MW=2x l0 6 , the release profiles of theophylline from 20% and 39% loaded tablets are superimposed with the exponent n ranging from 0.80 (±0.004) to 0.82 (±0.007). In these cases, the diffusion of theophylline (< 1.0% solubility in water) through the swollen gel layer does not play an important role in the release mechanism in PEO tablets. Rather it is the rate of erosion of the gel layer which dictates die rate of release of the drug. The diffusion of water into the matrices is not greatly facilitated by the water uptake of drugs but rather by the water uptake of the hydrophilic polymer This demonstrates that the swelling/erosion of the polymer is the controlling variable rather than the diffusion of drugs through the swollen gel layer. This may not be true when a highly water-soluble drug (diltiazem HC1, solubility >50%) is employed. Figures 4 and 5 show the effect of drug solubility on the release of drugs from PEO tablets. With a low molecular weight PEO, the solubility of the drug does not markedly affect the release of drugs from PEO tablets as may occur with other hydrophilic polymers. PEO tablets were also tested to determine the effect of stirring on the release of a drug from the tablet. The results are shown in Figure 6. As may be seen from Figure 6, the rate of release of the drug from the PEO tablet increased as stirring was increased with an increase in the stirring rate from 50 to 100 rpm. However, above 100 rpm, the rate of release of the drug was insensitive to the amount of stirring. The insensitivity of PEO tablets to the stirring rate also makes PEO a good candidate for oral dosage forms since the release rate will not vary as the tablet is subjected to turbulence in the stomach and intestine. The change in release constant with solubility of the drug is shown in Figure 7. As the solubility of the drug increases, diffusion from the gel layer increases. Where the erosion of the gel layer is not fast enough to keep up with the diffusion, n decreases indicating non-constant release. As would be expected, this occurs more readily in higher molecular weight polymers. This effect is further demonstrated in Figures 8, 9, and 10. There, the particular drugs used for testing are shown along with their typical solubilities. The most constant release over the longest period of time is exhibited by sulfadiazine, the drug with the lowest solubility. The least constant release is exhibited by the more soluble drugs such as diclofenac NA and theophylline. The non-constant release worsens with higher molecular weight polymers. Figure 11 shows some linearity of drug delivery with HPMC, particularly where a low viscosity HPMC is used. HPMC having a viscosity of up to 100,000 centipoise can also be used with the present invention. However, as shown by Figure 12, the results achieved are improved substantially by the formation of a hole in the tablet. Forming a hole in the tablet allows the surface area of the tablet to increase as the tablet dissolves. This increases the amount of polymer which is exposed to the environment, and thus increases die amount of polymer which swells. This increases the dissolution rate of the polymer which makes the drug administration rate linear. This improves performance provided the hole in the tablet is not so small as to substantially disappear from the swelling which occurs when the tablet is first contacted with moisture. Figure 13 shows the release characteristics of Procardia XL nifedipine tablets of 30 and 60 milligrams (Pfizer, Inc., New York, NY). This figure may be compared to Figures 14 through 19 which show nifedipine tablets having various compositions made in accordance witii the present invention. In each figure, the compositions of the tablets tested are shown as molecular weight of PEO (x 10 6 ), percent of PEO, percent nifedipine, percent polyethylene giycol (PEG), and weight of tablet. Thus a tablet indicated to be, 'O.9m59, 10,30,300mg" has 59% PEO with a molecular weight of 0.9 x 10 6 , 10% nifedipine (or 30 mg), 30% PEG, in a 300 milligram tablet. The remaining 1% would comprise fillers and lubricants such as magnesium s tear ate. In the tablets tested in Figures 14-19, PEG is used as a solubilizing agent to increase the solubility of the low solubility drug nifedipine. For the purposes of this application for calculating the composition of the excipient and the tablet as a whole, such a solubilizing agent is considered part of die drug, and not part of die excipient. This has been done since d e use and proportion of die solubilizing agent is dependent on die particular drug used and die amount thereof. Other solubilizing agents useful in the present invention include cyclodextrins, hydroxypropylcyclodextrins, polyvinylpyrrolidone (PVP) and otiier solubilizing agents commonly employed in drug compounding. Figure 16 shows that a 300 mg PEO tablet having 40 to 50% PEG and 30 mg nifedipine performs very similarly to a 30 mg Procardia XL tablet. Figure 18 shows that a 300 mg PEO tablet having about 35% PEG and 60 mg nifedipine performs very similarly to a 60 mg Procardia XL tablet. Figure 20 shows d e fractional release of nifedipine from tablets of PEO having a molecular weight of 4x 10 6 . The tablets were tested both in water (w 300 mg) and 0.54% sodiumlauryl sulfate. a common dissolution medium. The tablets were found to perform well.

Claims: CLAIMS 1. A controlled release tablet consisting essentially of a single homogeneous mixture of a pharmaceutical agent and an excipient, wherein said excipient comprises: a) at least 50% of water swellable polymer; and b) a lubricant, wherein the swelling rate of said polymer is equal to the dissolution rate of said polymer when swollen. 2. A controlled release tablet consisting essentially of a single homogeneous mixture of a pharmaceutical agent and an excipient, wherein said excipient comprises: a) a water swellable polymer; and b) a lubricant, wherein said water swellable polymer and said pharmaceutical agent are selected such that tablet dissolution completion is coincident widi pharmaceutical agent release completion. 3. A controlled release tablet according to claims 1 or 2 wherein said water swellable polymer is selected from the group consisting of hydroxypropylmethyl cellulose, polyethylene oxide and mixtures thereof. 4. A controlled release tablet according to claim 3 wherein said water swellable polymer is hydroxypropylmethyl cellulose having a viscosity of about 100 cps to about 15,000 cps. 5. A controlled release tablet according to claim 3 wherein said water swellable polymer is polyethylene oxide having an average molecular weight of about 900,000 to about 4,000,000. 6. A controlled release tablet according to claims 1 or 2 wherein said lubricant is magnesium stearate. 7. A controlled release tablet according to claims 1 or 2 wherein said lubricant is present in an amount up to 3% by weight of said excipient. 8. A controlled release tablet according to claims 1 or 2 wherein said excipient further comprises a diluent. 9. A controlled release tablet according to claim 8 wherein said diluent is selected from the group consisting of lactose, dextrose, sucrose, and calcium phosphate. 10. A controlled release tablet according to claim 8 wherein said diluent is present in an amount of up to 50% by weight of said excipient. 11. A controlled release tablet according to claims 1 or 2 further comprising a solubilizing agent. 12. A controlled release tablet according to claim 11 wherein said solubilizing agent is selected from the group consisting of polyethylene giycol, cyclodextrins, hydroxypropylcyclodextrins and polyvinylpyrrolidone (PVP). 13. A controlled release tablet according to claim 11 wherein said solubilizing agent is polyetiiylene giycol. 14. A controlled release tablet according to claim 11 wherein said solubilizing agent is present in an amount up to 150% of said excipient. 15. A controlled release tablet according to claims 1 or 2 wherein said pharmaceutical agent is present in an amount of from about 10% to about 40% by weight of said tablet. 16. A controlled release tablet according to claims 1 or 2 wherein said pharmaceutical agent is selected from the group consisting of nifedipine, diclofenac sodium, salicylic acid, theophylline, sulfapyridine, sulfadrazine, propranolol hydrochloride, and diltiazem hydrochloride. 17. A controlled release tablet according to claim 16 wherein said pharmaceutical agent is nifedipine. 18. A controlled release tablet according to claim 17 wherein said water swellable polymer is polyetiiylene oxide having an average molecular weight of about 900,000 to 4,000,000. 19. A controlled release tablet according to claim 16 wherein said pharmaceutical agent is theophylline. 20. A controlled release tablet according to claim 19 wherein said water swellable polymer is hydroxypropylmeti yl cellulose having a viscosity of about 100 cps to about 15,000 cps. 21. A controlled release tablet according to claim 16 wherein said pharmaceutical agent is diltiazem hydrocholoride. 22. A controlled release tablet according to claim 21 wherein said water swellable polymer is polyetiiylene oxide having an average molecular weight of about 900,000 to about 4,000,000. 23. A controlled release tablet according to any of the preceding claims wherein said tablet has an aperture therethrough.

Inventors: KIM CHERNG-JU, KIM, CHERNG-JU
Applicants: UNIV TEMPLE, TEMPLE UNIVERSITY OF THE COMMONWEALTH SYSTEM OF HI
Application year: 1996
Main classification: A61K9
IPC codes: A61K9, A61K31, A61K47