MXPA06007289A - Methods and dosage forms for increasing solubility of drug compositions for controlled delivery - Google Patents

Abstract

Dosage forms and devices for enhancing controlled delivery of pharmaceutical agents by use of a drug core composition that increases the solubility of the pharmaceutical agent are described. The present invention provides a means of delivering high doses of poorly soluble drug in oral drug delivery systems that are convenient to swallow, for once-a-day administration.

Description

METHODS AND DOSAGE FORMS TO INCREASE THE SOLUBILITY OF DRUG COMPOSITIONS FOR CONTROLLED ADMINISTRATION FIELD OF THE INVENTION This invention relates to the controlled administration of pharmaceutical methods and agents, dosage forms and devices thereof. In particular, the invention relates to methods, dosage forms and devices for increasing the controlled delivery of pharmaceutical agents through the use of a composition that increases the solubility of the pharmaceutical agent. The present invention provides a means for administering high doses of poorly soluble drugs in solid dosage form systems which it is convenient to swallow.

BACKGROUND OF THE INVENTION The art is replete with descriptions of dosage forms for the controlled release of pharmaceutical agents. Although a variety of sustained release dosage forms could be known for administering certain drugs, not all drugs can be adequately administered from those dosage forms, due to solubility, metabolic processes, absorption and other physical, chemical and physiological parameters. which could be unique to the drug and mode of administration. Similarly, dosage forms that incorporate a drug with low solubility, including a high drug load for the dosage form, provide a significant challenge for the controlled release delivery technology. As such, the systems tend to be so large that patients do not want to or can not swallow them. Devices in which a drug composition is administered in the form of a paste, suspension or solution from a small exit orifice by the action of an expandable layer are described in U.S. Pat. Nos. 5,633,011; 5,190,765; 5,252,338; 5,620,705; 4,931,285; 5,006,346; 5,024,842; and 5,160,743. Typical devices include a tablet comprising an expandable pusher layer and a drug layer, wherein the tablet is surrounded by a semipermeable membrane that has a delivery port. In certain cases, the tablet is provided with a sublayer to retard the release of the drug composition to the environment of use. Devices in which a drug composition is delivered in a dry state from a large exit orifice by the action of an expandable layer are described in US Patents. Us. 4,892,778, 4,915,949, as well as 4,940,465 and 5,023,088. These references describe a dispenser for administering a beneficial agent to an environment of use that includes a semipermeable wall containing a layer of expandable material that pushes a dry layer of drug composition out of the compartment formed by the wall. The outlet orifice in the device has basically the same diameter as the internal diameter of the compartment formed by the wall. In such devices, a substantial area of the drug composition layer is exposed to the environment of use, leading to a release performance that may be subject to the conditions of agitation in that environment. Other similar devices have administered the drug by expelling discrete tablets containing the drug at a controlled rate over time. Patents of E.U.A. Nos. 5,938,654; 4,957,494; 5,023,088; 5,110,597; 5,340,590; 4,824,675; and 5,391, 381. Other devices attempt to administer drugs of low solubility by incorporating liquid formulations of drugs that are released at a controlled rate over time. These devices are described in the Patents of E.U.A. Nos. 4,111, 201; 5,324,280; 5,413,672; 6,174,547. However, such liquid osmotic delivery systems are limited in terms of the concentration of drug in the liquid formulation and, therefore, the available drug loading, leading to delivery systems that may have an unacceptably large size. Still other administration systems use a liquid vehicle to administer short-time pills suspended within the liquid vehicle. Said devices are described in the Patents of E.U.A.

Nos. 4,853,229; 4,961, 932. These suspensions require that the therapeutic dose of the pharmaceutical agent be delivered in volume with measuring devices such as graduated cylinders or measuring spoons, a delivery method which can be disordered and inconvenient for administration to the patient. Although the dosage forms which administer the drug composition to the environment of use in the dry state through a large delivery port, can provide adequate release of the drug over a prolonged period of time, the exposure of the layer of drug to the environment of use of variably turbulent fluid such as the upper gastrointestinal tract, could produce a release of the drug dependent on agitation which, in some circumstances, is difficult to control. In addition, said dosage forms of administration in the dry state to a semi-solid environment lacking sufficient volumes of bulk water, such as in the lower colonic environment of the gastrointestinal tract, could face difficulties in releasing the dried drug composition delivered to the environment. , since the composition with a high solids content tends to adhere to the dosage form at the site of the large orifice. Accordingly, it may be advantageous to release the drug as a well hydrated slurry or paste that can be measured by controlling the rate of expansion of the push layer and in combination with the smaller size of the outlet orifice in the dosage form. , to minimize the effects of localized agitation conditions on the performance of the administration in accordance with this invention. The dosage forms described above administer therapeutic agents at a rate of release of the order of about zero. Recently, dosage forms have been described for administering certain drugs at approximately upward release rates, such as the Concerta® methylphenidate product from ALZA Corporation. PCT Published Requests Nos. US 99/11920 (WO 9/62496); US 97/13816 (WO 98/06380); and US 97/16599 (WO 98/14168). Said dosage forms described involve the use of multiple drug layers with sequentially increasing concentrations of drug in each drug layer, to produce the increasing rate of drug administration over time. Although such multilayer tablet constructions represent a significant advance for the art, these devices also have a limited capacity to administer pharmaceutical agents with low solubility, particularly those associated with relatively large doses of said agents, at a size that is acceptable for the patients swallow it. Therefore, there is still a critical need for a means for administering high doses of drug compounds with low solubility according to different administration patterns that are convenient and viable for patients who must swallow them. The need includes dosage methods, dosage forms and effective devices that will allow the controlled release of the drug compounds over a prolonged period of time by increasing the solubility of the active agent in order to increase the time between dosing, preferably twice a day and, more preferably, to obtain a once-a-day dosing regimen. Preferably, said dosage forms should have the option of administration according to a release rate of the order of zero, ascending or another rhythm of hybrid administration rate suitable for the therapeutic agent to be administered.

BRIEF DESCRIPTION OF THE INVENTION Unexpectedly, the present invention provides a central drug composition for both a dosage form and a method for the controlled administration of high doses of drug compounds with low solubility over a prolonged period of time, preferably providing a once a day administration. This is achieved through the use of three primary components in the central drug composition: a therapeutic agent, a structural polymer carrier and a solubilizing surfactant. The present invention relates to a novel central drug composition for a dosage form to provide once-a-day administration with therapeutic effects over 24 hours, using a convenient single oral dosage form. The dosage form releases a therapeutic agent for up to about 24 hours for once-a-day administration using a central drug composition that releases drug at a controlled rate. The present invention has the ability to adapt for release at rates ranging from zero to ascending and other hybrids, depending on the type and concentration of drug and the type and concentration of solubilizing surfactant. The present invention can be further applied both to osmotic delivery systems and to matrix tablets as much that it can wear away as it can wear out. The central drug composition of the present invention may additionally allow the bioavailability of the therapeutic agent to be increased through the increased absorption of drugs with low solubility in the gastrointestinal tract, especially in the colonic region which, otherwise, is not they would absorb due to the lack of sufficient bulk water to sufficiently solubilize the drug. The central drug composition can further provide improvement of the permeability of the drug through the lining of the mucosa of the gastrointestinal tract by the action of the surfactant on these biological membranes.

The present invention could be incorporated in a semi-permeable membrane that surrounds a bilayer or multilayer center containing at least a first layer of central drug composition, containing a therapeutic agent and excipients, as well as a second expandable layer called the thrust layer that contains osmotic agents and no therapeutic agent. A hole is drilled through the membrane at the drug-layer end of the tablet, to allow release of the active agent into the environment. In the aqueous environment of the gastrointestinal tract (Gl), water is absorbed through the membrane at a controlled rate. This causes the thrust layer to swell and the layer (s) of the central drug composition to hydrate and conform to viscous, but deformable masses. The thrust layer expands against the drug layer, which is pushed through the hole. The drug composition layer leaves the system through the orifice in the membrane over extended periods of time, as water from the gastrointestinal tract is absorbed into the delivery system. Upon completion of the drug release, the biologically inert components of the delivery system are removed as a tablet coating. The present invention can also be incorporated into a matrix tablet delivery system containing at least one first layer of drug core composition, which contains a therapeutic agent, a structural polymer carrier and a solubilizing surfactant. In one aspect, the present invention comprises a central drug composition for a sustained release dosage form adapted for release over a prolonged period of time at a controlled release rate. In another aspect, the invention comprises a method for identifying the type of surfactant suitable for accompanying a particular drug type and producing a dosage form having a central drug composition adapted to deliver the compound at a controlled release rate to over a prolonged period of time. In yet another aspect, the present invention comprises a method for treating a condition in a subject that responds to the administration of a therapeutic agent, comprising orally administering to the subject a dosage form having a central drug composition adapted to deliver the compound at a rate of controlled release over a prolonged period of time. Preferably, the dosage form is administered orally, once a day. In still another aspect, the present invention comprises a central drug composition for a dosage form comprising a wall defining a compartment, the wall having an outlet orifice formed or that can be formed therein and at least a portion of the wall being semipermeable; an expandable layer located within the remote compartment of the exit orifice and in fluid communication with the semipermeable wall portion; and at least one layer of central drug composition located within the compartment, adjacent to the exit orifice, the drug layer comprising a therapeutic agent, a structural polymer carrier and a surfactant. The prior art did not warn that high doses of drugs with low solubility can be integrated into a single controlled release dosage form or a solid therapeutic composition as claimed herein, which provides an effective therapy over 24 hours, with an administration of once a day for 24 hours. The prior art did not realize that a solid dosage form and a therapeutic composition can be made available comprising a structural polymer carrier and a solid surfactant. The prior art does not make obvious a central drug composition for a solid dosage form formulated with a structural polymer vehicle and a surfactant. For example, it is well known that surfactants can be used in liquid drug delivery systems, such as wetting agents, drug solubilizers, meltable vehicles, oily liquid fillers in gel capsules for oral administration, parenteral fluids for injection, eye drops, topical ointments , ointments, lotions and creams, suppositories and in the form of pulmonary and nasal dew. By virtue of its amphipathic molecular structure comprising opposite polar and non-polar hydrophilic portions with opposite physical and chemical properties, surfactants are known to have poor cohesive properties. Accordingly, the surfactants have been limited to the above applications because, at room temperature, said surfactants have the physical form of liquids, pastes or brittle solids, whose physical forms and properties are widely recognized as unacceptable for use. as components in compressed solid tablets durable enough for manufacturing and practical use. These physical properties deviate from the use of surfactants in solid dosage forms, which makes their mode in the present invention not obvious. The central drug composition of the present invention implements a combination of surfactant and structural polymer, wherein the structural polymer is present to provide a double role of imparting structural integrity to the solid drug center in the dry state and to provide viscosity structural in the wet state during the operation of the dosage form. The structural viscosity develops as a result of the formation of a functional hydrogel while the administration system is in operation. The structural polymer comprises a hydrophilic polar polymer that freely interacts with the polar molecules of water to form a structurally viscous mass that has sufficient viscosity - necessary to effectively suspend and conduct the dissolved and dispersed drug as a pumpable mass. from the dosage form. The formation of said hydrogel requires extensive hydrogen bonding with the water molecules that are introduced into the delivery system from the environment of use. However, it is well known that surfactants reduce the attractive forces of the hydrogen bonding between water molecules, which property of surfactant moves away from the use of surfactants in combination with structural hydrogel polymers that they require interaction with these polar water molecules to form the structurally three-dimensional viscous mass. The above presentation indicates the imperative need for a central drug composition for the solid pharmaceutical dosage form and for a therapeutic composition that overcomes the disadvantages of conventional solid osmotic dosage forms and controlled release matrix forms, including tablets and capsules These conventional dosage forms do not allow drug therapy regulated by optimal dosage over a prolonged period of time with high doses of drugs with low solubility. The therapeutic agents in high doses having low solubility are administered by the prior art two or more times per day and with multiple divided dosage forms, which does not lend itself to a controlled and sustained therapy with the once daily administration of a unique dosage form. This rate of drug administration of the prior art indicates the need to have a dosage form and a therapeutic composition that can administer high doses of therapeutic agents with low solubility at a controlled rate dose over a prolonged period of time to provide constant therapy and eliminate multiple dosage from the prior art.

BRIEF DESCRIPTION OF THE FIGURES The following figures are not drawn to scale and are set to illustrate different embodiments of the invention. Figure 1 illustrates one embodiment of a dosage form of the present invention, illustrating the dosage form prior to administration to a subject. Figure 2 illustrates the dosage form of Figure 1 in open section, describing a dosage form of the present invention comprising a pharmaceutically acceptable, internally-buffered therapeutic composition. Figure 3 illustrates an open view of the Figural drawing, illustrating a dosage form internally comprising a therapeutic composition and a separate and contacting displacement composition comprising means for pushing the therapeutic composition from the dosage form.

Figure 4 illustrates a dosage form provided by the present invention, which additionally includes an instantaneous release overcoat of a therapeutic composition in the dosage form. Figure 5 illustrates an open view of a dosage form of the present invention illustrating a therapeutic composition comprising two drug layer compositions arranged in parallel and a separate and contacting displacement composition comprising means for pushing the composition therapeutic from the dosage form. Figure 6 illustrates the solubility of an active pharmaceutical agent in aqueous solutions of surfactants. The graphs in this Figure represent the method for determining the suitable surfactant for use with a particular active pharmaceutical agent by measuring the effect of different concentrations of surfactants and different types of surfactants on the solubility of the drug. Figures 7 to 9 illustrate the release patterns of an active pharmaceutical agent with poor solubility from osmotic delivery systems formulated with a single solubilizing surfactant in the drug composition and a structural polymer, wherein each system is formulated with relatively high doses. high of the agent, a single layer of drug and a displacement layer.

Figures 10 and 11 illustrate the release patterns of an active pharmaceutical agent with poor solubility that is released from osmotic delivery systems formulated with a binary mixture of solubilizing surfactant in the drug composition and a structural polymer, wherein each system it is formulated with relatively high doses of the agent in a single drug layer and a displacement layer. Figure 12 illustrates a release rate of an active pharmaceutical agent with poor solubility released from osmotic delivery systems formulated with a solubilizing surfactant in the drug composition and a structural polymer, wherein each system is formulated with relatively high dosages of agent in a single drug layer. Figure 13 illustrates a release rate of an active pharmaceutical agent with poor solubility released from osmotic delivery systems formulated with a solubilizing surfactant in the drug composition and a structural polymer, wherein each system is formulated with relatively high doses of agent in two drug layers. Figures 14A to 16B illustrate a rate of release of an active pharmaceutical agent with poor solubility released from osmotic delivery systems formulated with a sugar ester surfactant in the drug composition and a structural polymer, wherein each system is formulates with relatively high doses of the agent in a single layer of drug. In the Figures and specification of the drawings, similar parts in the related figures are identified with equal numbers. The terms that appear previously in the specification and in the description of the Figures of the drawings, as well as the modalities of these, are further described elsewhere in the description.

DETAILED DESCRIPTION OF THE INVENTION The present invention is better understood by reference to the following definitions, the drawings and the description example provided herein.

Definitions Before describing in detail the present invention it should be understood that, unless otherwise indicated, this invention is not limited to drugs, surfactants, specific polymers or the like, since these may vary. It should also be understood that the terminology used herein is for the purpose of describing particular embodiments only and is not intended to limit "the scope of the present invention.

It should be noted that, as used in the present description and in the Claims, the singular forms "a / a", "and", "as well as" the "include references in, unless the context clearly indicates what Therefore, for example, the reference to "a surfactant" includes two or more surfactants, the reference to "a pharmaceutical agent" includes two or more pharmaceutical agents, etc. When a scale of values is provided , it is understood that each intervening value, up to one tenth of the unit of the lower limit, unless the context clearly indicates otherwise, between the upper and lower limit of that scale, as well as any other indicated value or that intervene on that established scale, it is encompassed within the invention.The upper and lower limits of these smaller scales can be independently included in the smaller scales and are also encompassed within the invention, their subject to any limit specifically excluded in the established scale. When the established scale includes one or both of the limits, the scales that exclude either or both of those included limits are also included in the invention. By "dosage form" is meant a device or pharmaceutical composition comprising an active pharmaceutical composition, such as topiramate or a pharmaceutically acceptable acid addition salt thereof, a structural polymer, a solubilizing surfactant and the composition or device optionally containing inactive ingredients, i.e., pharmaceutically acceptable excipients, such as disintegrants, binders, diluents, lubricants, stabilizers, antioxidants, osmotic agents, colorants, plasticizers, coatings and the like, which are used to manufacture and administer active pharmaceutical agents. By "active agent", "drug" or "therapeutic agent" is meant an agent, drug or compound having therapeutic characteristics or a pharmaceutically acceptable acid addition salt thereof. By "pharmaceutically acceptable acid addition salt" or "pharmaceutically acceptable salt", which are used interchangeably in the present description, those salts are listed wherein the anion does not contribute significantly to the toxicity or pharmacological activity of the salt and , as such, are the pharmacological equivalents of the bases of the compound. Examples of pharmaceutically acceptable acids that are useful for the purposes of salt formation include, but are not limited to, hydrochloric, hydrobromic, hydroiodic, citric, succinic, tartaric, maleic, acetic, benzoic, mandelic, phosphoric, nitric, mucic, isethionic, palmitic and others. By "poor solubility" and "low solubility" it is meant that the pure therapeutic agent in the absence of surfactant solubilizers has a solubility in water of not more than 100 milligrams per millimeter. The aqueous solubility is determined by adding the therapeutic agent to stirred or stirred water maintained in a bath at a constant temperature of 37 degrees centigrade, until the equilibrium between the dissolved and undissolved states is established and the concentration of the dissolved drug is constant. The resulting solution saturated with active agent is then filtered, typically under pressure through a 0.8-micron Millipore filter, while the concentration in solution is measured by any suitable analytical method, including gravimetric, ultraviolet spectrophotometry, refractive index, refractive index chromatography and the like. By "sustained release" is meant the predetermined continuous release of active agent into an environment for a prolonged period of time. The terms "exit", "exit orifice", "administration orifice" or "drug administration orifice", as well as other similar expressions, as may be used herein, include a member selected from the group consisting of a passage.; an opening orifice; and a perforation. The term also includes an orifice that is formed or can be formed from a substance or polymer that wears, dissolves or is leached from the outer wall to thereby form an outlet orifice. "Drug release rate" refers to the amount of drug released from a dosage form per unit time, ie, milligrams of drug released per hour (mg / hr). The drug release rates for drug dosage forms are generally measured as an in vitro rate of drug release, ie, a quantity of drug released from the dosage form per unit time measured under appropriate conditions and in a suitable fluid. The dissolution tests used in the examples described herein were performed in dosage forms placed on metal coil or metal cage sample holders attached to the Type Vil USP bath indexer in a bath with a constant temperature of 37 ° C. . The aliquots of the release rate solutions were injected into a chromatographic system to quantify the amounts of drug released during the testing intervals. By "release rate assay" is meant a standardized assay for determining the rate of release of a compound from the proven dosage form, using a Type Vil USP interval delivery device. It is understood that reagents of equivalent grade may be substituted in the test in accordance with generally accepted procedures. As used herein, unless otherwise specified, a drug release rate obtained at a specific time "after administration" refers to the rate of in vitro drug release obtained at the specified time after of the implementation of an adequate dissolution test. The time in which a specified percentage of the drug has been released into a dosage form, can be considered as the "Tx" value, where "x" is the percentage of drug that has been released. For example, a reference measurement commonly used to evaluate the release of drugs from the dosage forms is the time when 70% of the drug has been released into the dosage form. This measurement is called "T70" for the dosage form. An "immediate release dosage form" refers to a dosage form that releases drug substantially completely within a short period of time after administration, i.e., generally between the following minutes and approximately 1 hour. By "sustained release dosage form" is meant a dosage form that releases drug substantially continuously for many hours. Sustained-release dosage forms according to the present invention have T70 values of at least about 8 to 20 hours and, preferably, 15 to 18 hours and, more preferably, about 17 hours or more. The dosage forms continuously release drug for sustained periods of at least about 8 hours, preferably 12 hours or more and, preferably, 16 to 20 hours or more. Dosage forms in accordance with the present invention exhibit rates of controlled release of a therapeutic agent over a prolonged period of time within the sustained release period. Release rhythms may include pulsed release, ascending release, and zero-order release, with or without a delay.

By "uniform release rate" or "rate of release of the order of zero" is meant an average rate of release per hour from the center which varies positively or negatively by no more than about 30%, preferably no more than about 25%, and most preferably not more than 10%, of the average rate of release per hour either preceding or subsequent, as determined by the USP Type Vil Interval Release Apparatus, where the cumulative release is between approximately 25% and approximately 75%. As used herein, unless otherwise indicated, the term "basically ascending release rate" will mean an amount of drug dispensed per increasing unit time that increases continuously and gradually over a duration of prolonged time Preferably, the rate of drug release as a function of time increases steadily (rather than step by step). More preferably, an ascending release rate could be characterized as follows. The rate of release as a function of time for a dosage form is measured and plotted as% drug release versus time, or as mg drug release / hour versus time. An upward release rate is characterized by an average rate expressed in mg of drug per hour over a two-hour interval being higher compared to the previous two-hour interval, over the time period from about 4 to about 12 hours. hours, preferably from about 4 hours to about 18 hours, more preferably from about 2 hours to about 18 hours. Preferably, the increase in the average rate is gradual, so that less than 30% of the dose is administered during any 2 hour interval, more preferably less than 25% of the dose is administered during any 2 hour interval. Preferably, the rate of upward release is maintained to at least 50% and, most preferably at least 70% of the drug in the dosage form that has been released. As used herein, the term "pulsed release rate" will mean that the amount of drug released changes abruptly as a function of time, wherein each increase in rate of release is followed by a reduction in the rate of release. , so that the amount of liberation of released drug expressed in mg changes in pulsations or discrete intervals. The amount of drug released during each pulse can be from about 10% to about 2000% more than the amount of drug released during the interval between pulses. Preferably, the amount of drug released is a pulse of at least 10% greater and, more preferably, is at least about 50% greater than the amount of drug released during the interval between beats. Preferably, each pulsation is 0.5 to 2 hours long and the interval between pulsations is at least about 1 hour.

By "prolonged period of time" is meant a continuous period of time of at least about 4 hours, preferably from 6 to 8 hours or more and, more preferably, from 10 hours or more. For example, examples of osmotic dosage forms described herein, generally begin to release therapeutic agent at a uniform rate of release from about 2 to about 6 hours following administration and the rate of uniform release, as defined above. , continues for a prolonged period of time from about 25% to at least about 75% and, preferably, at least about 85% of the drug is released from the dosage form. The release of the therapeutic agent continues later for several more hours, although the rate of release generally slows down than the rate of uniform release. By "C" is meant the concentration of drug in the blood plasma of a subject, generally expressed as mass per unit volume, typically nanograms per millimeter. For convenience, this concentration may be referred to as "plasma drug concentration" or "plasma concentration" in the present disclosure, which is intended to include a drug concentration measured in any suitable tissue or body fluid. The concentration of drug in plasma at any time in units of hours after administration is called Ct¡emp0, as in C9h or C24h, and so on. By "molecular weight" is meant the average molecular weight in units of grams per mole, unless otherwise specified. By "constant state" is meant the condition in which the amount of drug present in the blood plasma of a subject does not vary significantly over a prolonged period of time. A rate of drug accumulation that follows the continuous administration of a constant dose and dosage form at constant dosage intervals finally achieves a "steady state" when the peaks of concentration in plasma and valleys of plasma concentration are basically identical within each of the dosing intervals. As used herein, the maximum plasma (peak) drug concentration in a constant state is called Cmax, while the minimum plasma drug concentration (trough) is designated Cmn. The times that follow the administration of the drug in which the concentrations of valley and peak drug in constant state plasma are produced are called Tmax and Tmin, respectively. The person skilled in the art will notice that the concentrations of drug in plasma obtained in individual subjects, will vary due to the variability between patients in the many parameters that affect the absorption, distribution, metabolism and excretion of the drug. For this reason, unless otherwise indicated, the mean values obtained from groups of subjects are used herein for the purposes of comparing the drug concentration data in plasma and analyzing the relationships between the rates of dissolution of the drug. the in vitro dosage forms and the plasma drug concentrations in vivo. By "high drug loading" is meant a drug loading efficiency of the therapeutic agent within the dosage form, comprising 20% or more, preferably 40% or more, by weight of the tablet center of composition drug layer of the dosage form. Surprisingly, it has been found that sustained release dosage forms incorporating central high dose drug compositions of low solubility therapeutic agent have T70 values of about 10 to 20 and, preferably, 15 to 18 hours and, greater preferably, about 17 hours or more, whose release at a uniform release rate for a prolonged period of time can be prepared. Administration of said dosage forms once a day can provide therapeutically effective average steady state plasma concentrations. Examples of sustained release dosage forms that incorporate the central drug composition of the present invention, methods for preparing said dosage forms, as well as methods for using said dosage forms described herein, refer to dosage forms Osmotic for oral administration. However, in addition to the osmotic systems described herein, there are many other approaches to achieve sustained release of drugs from oral dosage forms known in the art. For example, these different approaches may include broadcast systems such as deposit devices and matrix devices, dissolution systems such as encapsulated dissolution systems (including, for example, "short-time pills") and matrix dissolution systems, using matrixes that can wear out and that can not be worn out, as well as a combination of diffusion / dissolution and ion exchange resin systems, as described in Reminqton's Pharmaceutical Sciences, 1990 ed. , pp. 1682-1685. Dosage forms of therapeutic agent that operate in accordance with these approaches are encompassed by the scope of the claims that appear below to the extent that the drug release characteristics as described in the claims describe those dosage forms, since be literal or equivalent. In general, osmotic dosage forms utilize osmotic pressure to generate a driving force to absorb fluid in a compartment formed, at least partially, by a semipermeable wall that allows fluid-free diffusion, but not of drug or agent (s). ) osmotic (s), if present. A significant advantage for osmotic systems is that the operation is pH independent and, therefore, continues at the osmotically determined rate over a prolonged period of time, even as the dosage form transits the gastrointestinal tract and find divergent microenvironments that have significantly different pH values. A review of such dosage forms is found in Santus and Baker, "Osmotic drug delivery: a review of the patent literature," Journal of Controlled Relay 35 (1995) 1-21, incorporated in its entirety as a reference in the present description. In particular, each of the following U.S. Patents, owned by the assignee of the present application, ALZA Corporation, which refer to osmotic dosage forms, is hereby incorporated in its entirety: Nos. 3,845,770; 3,916,899; 3,995,631; 4,008,719; 4,111, 202; 4,160,020; 4,327,725; 4,519,801; 4,578,075; 4,681, 583; 5,019,397; and 5,156,850. Figure 1 is a perspective view of an embodiment of a sustained release osmotic dosage form in accordance with the present invention. The dosage form 10 comprises the wall 20 surrounding and enclosing an internal compartment (not shown in Figure 1). The inner compartment contains a central drug composition comprising a therapeutic agent or a pharmaceutically acceptable acid addition salt thereof, as described in more detail below: The wall 20 is provided with at least one administration outlet of drug 60 for connecting the internal compartment to the environment of external use Accordingly, after oral ingestion of the dosage form 10, the fluid is absorbed through the wall 20 and the therapeutic agent is released through the from exit 60.

Although the preferred geometric embodiment in Figure 1 illustrates a standard biconvex round shaped tablet, the geometry may include a capsule, oval, triangular shaped tablet, as well as other forms designed for oral administration, including buccal or oral dosage forms. Sublingual Figure 2 is a sectional view of Figure 1, showing one embodiment of the present invention, with the internal compartment 15 containing a single component layer referred to in the present description as drug layer 30, which comprises the agent drug Therapeutic 31 in a mixture with selected excipients adapted to increase the solubility of the drug layer 30 and provide a gradient of osmotic activity to drive fluid from an external environment through the wall 20 to form a therapeutic agent formulation that can be administered to the absorb the fluid. As described in more detail below, the excipients include a suitable structural polymer referred to in the present drug carrier 32, represented by horizontal dashed lines and a suitable solubilizing agent referred to herein as surfactant 33 and which is represented by hyphens vertical Additionally, the excipients of the drug layer 30 may include a suitable lubricant 34 and an osmotically active agent, osmagent 35, represented by "x" symbols and a suitable binder 36.

In the operation, after oral ingestion of the dosage form 10, the gradient of osmotic activity along the wall 20 causes the aqueous fluid of the gastrointestinal tract to be absorbed through the wall 20, thereby forming a therapeutic drug formulation that can be administered, i.e., a solution or suspension, within the internal compartment. The drug formulation that can be administered is released through the outlet 60, as the "fluid continues to enter the internal compartment." As the release of the drug formulation occurs, the fluid continues to be absorbed, prompting from this In this way, the drug is released in a sustained and continuous manner over a prolonged period of time Figure 3 is a sectional view of Figure 1 with an alternative embodiment of internal compartment 15 having a bilayer configuration In this embodiment, the inner compartment 15 contains a compressed double-layer center having a first component drug layer 30 and a second component pushing layer 40. The drug layer 30, as described above With reference to Figural, it comprises a therapeutic agent in a mixture with selected excipients, as described in more detail below. The second component push layer 40 comprises osmotically active component (s), but does not contain any active therapeutic agent.

The thrust layer components typically comprise an osmagent 42 and one or more osmopolymers 41, which have relatively large molecular weights that swell as the fluid is absorbed. Additional excipients such as binder 43, lubricant 44, antioxidant 45 and dye 46 may also be included in push layer 40. The second component layer 40 is referred to herein as a push or expandable layer as, as the fluid is absorbed, the osmopolymer (s) swells and pushes against the drug formulation that can be administered from the first component drug layer, thereby facilitating the release of the drug formulation from the dosage form. In the operation, after oral ingestion of the dosage form 10 as shown in Figure 3, the gradient of osmotic activity along the wall 20 causes the aqueous fluid to be absorbed through the wall 20., thereby forming a drug layer 30 in a formulation that can be administered and at the same time swelling the osmopolymer (s) in the push layer 40. The drug layer 30 that can be delivered is released through the outlet 60. , as the fluid continues to enter the inner compartment 15 and the pushing layer 40 continues to swell. As the release of the drug layer 30 occurs, the fluid continues to be absorbed and the pusher layer continues to swell, thereby promoting continuous release. In this way, the therapeutic agent is released in a sustained and continuous manner over a prolonged period of time. The drug layer 30, as described with reference to Figures 2 and 3, comprises a therapeutic agent in a mixture with selected excipients. The push layer 40, as described with reference to Figure 3, comprises osmotically active component (s), but does not contain any therapeutic agent. The drug layer 30 of the present invention comprises a central drug composition formed of three components: a pharmaceutically effective amount of therapeutic agent drug 31 or a pharmaceutically acceptable salt thereof, a carrier 32 and a solubilizing surfactant 33. The drug of therapeutic agent with poor solubility may include any therapeutic agent with poor solubility, or, derivatives of soluble therapeutic agents or salts with poor solubility. In particular, the therapeutic agent with poor solubility can be a member selected from the group consisting of acenocoumarol, acetaminophen, acetazolaminide, acetophenazine, acyclovir, albuterol, allopurinol, aprazolam, alteplase, amantidine, aminopyrine, amiloride, amiodarone, amitriptyline, amlodipine, amoxapine. , amoxicillin, amphotericin B, ampicillin, apomorphine, aspirin, astemizole, atenolol, atracurium, atropine, auranofin, azathioprine, aztreonam, bacitracin, baclofen, beclomethasone, benazepril, bendroflumetrazide, betamethasone, biperiden, bitolterol, bromocriptine, buclizine, bumetanide, buprenorphine, busulfan, butorphanol, cadralazine, calcitriol, carbamazepine, carbidopa, carboplatin, cefaclor, cefazolin, cefoxitin, ceftazidime, cephalexin, chloramphenicol, chlordiazepoxide, chlorpheniramine, chlorpromazine, chlorpropamide, chlorthalidone, chlorzoxazone, cholestyramine, cimetidine, ciprofloxacin, cisapride, cisplatin, clarithromycin, clemastine, clonazepam, clotrimazole, clo Zapine, codeine, cyclozine, cyclobarbital, cyclosporine, cytarabine, chlorothiazide, cyclophosphamide, dacarbazine, deflazacort, deserpidine, desanoside, desogestrel, deoximetasone, dexamethasone, dextromethorphan, dezocin, diazepam, diclofenac, dicyclomine, diflunisal, digitoxin, digoxin, dihydroergotamine, dimenhydrinate, diphenoxylate, dipyridamole, disopyramide, dobutamine, domperidone, dopexamine, doxazosin, doxorubicin, doxycycline, droperidol, enalapril, enoximone, ephedrine, epinephrine, ergotoloids, ergovina, erythromycin, estazolam, estradiol, ethinyl estradiol, etodolac, etoposide, famotidine, felodipine, fenfluramine , fenoprofen, fentanyl, filgrastim, finasteride, fluconazole, fludrocortisone, flumazenil, flunisolide, fluocinonide, fluorurcil, fluoxetine, fluoxymesterone, fluphenazine, fluphenazine, flurbiprofen, flutamide, fluticasone, furosemide, ganciclovir, gemfibrizil, glipizide, glyburide, gramicidin, granisetron, guaifenesin guanbenz, guanadrel, guanfacine, halope Ridol, heparin, homatropine, hydralazine, hydrochlorothiazide, hydrocodone, hydrocortisone, hydromorphone, hydroxyzine, hyoscyamine, ibudilast, ibuprofen, isosorbide dinitrate, pseudoephedrine, colchicine, secoverine, progesterone, naloxone, imipramine, indapamide, indomethacin, insulin, ipratropium, isocarboxazide, isopropamide, isosorbide, isotretinoin, isradipine, itraconazole, ketoconazole, ketoprofen, levonorgestrel, levorphanol, lidocaine, lindane, liothyronine, lisinopril, lithium, lomefloxacin, loperamide, loratadine, lorazepam, lovastatin, loxapine, mabuterol, maprotiline, mazindol, meclizine, medroxyprogesterone, mefenamic acid, melatonin, meperidine, mefentermine, mesalazine, mestranol, metdilazine, methotimeprazine, methotrexate, methoxsalen, methoxypsoralen, methyclothiazide, methylphenidate, methylprednisolone, methyltestosterone, methysergide, metocurine iodide, metolazone, metronidazole, miconazole, midazolam, milrinone, minocycline, minoxidil, mitomycin, molsidomine, mometasone, morphine, mupirocin, muroctasin, nabumetone, nadolol, naltrexone, neostigmine, nicardipine, nicorandil, nicotine, nifedipine, nimodipine, nitrendipine, nitrofurantoin, nitroglycerin, norfloxacin, nystatin, octreotide, ofloxacin, omeprazole, oxaprozin, oxazepam, oxycodone, oxyphencyclimine, oxytetracycline, paclitaxel, parametasone, paroxetine, pemoline, penicillin, pentaerythritol, pentamidine, pentazocine, pergolide, perphenazine, phenazopyridine, phenelzine, phenobarbitol , phenoxybenzamine, phenytoin, physostigmine, pimozide, pindolol, politizide, prazepam, prazosin, prednisolone, prednisone, probucol, procloperazine, procyclidine, propofol, propranolol, propylthiuracil, pyrimethamine, quinidine, ramipril, rescimlamin, reserpine, rifabutin, rifapentine, respiridone, salmeterol , sertraline, siagoside, simvastatin, spironolactone, sucralfate, sulfadiazine, sulfamethoxazole, sulfametizole, sulindac, sulpiride, tamoxifen, tandospirone, temazepam, terazosin, terbinafine, terconazole, terfenadine, tetracaine, tetracycline, theophylline, thiethylperazine, thioridazine, thiothixene, thyroxine, timolol , topiramate, traylcypromine, trazodone, tretinoin, triamcinolone, trimethoprim, triazolam, triclomnetiazide, trihexfenidyl, trioxsalen, tubocurarine, valproic acid, verapamil, vinblastine, vitamin B, warfarin, zidovudine and derivatives with poor solubility, prodrugs, isomers, solvates, hydrates and salts of the above. The doses of these drugs to be incorporated in the dosage form of the present invention can range from 1 microgram or less to about 750 milligrams, with an especially preferred scale of 10 mg to 250 mg. These drugs generally have aqueous solubilities of less than 100 mg / ml, with those most preferred for the present invention having aqueous solubilities of less than 50 mg / ml. The salts of the therapeutic agents include any pharmaceutically acceptable salt, including those represented by a member selected from the group consisting of the following: salts of anions such as acetate, adipate, benzenesulfonate, benzoate, bicarbonate, bitartrate, bromide, calcium edetate, camsylate , carbonate, chloride, citrate, dihydrochloride, edetate, edisilate, estolate, fumarate, gluceptate, gluconate, glutamate, glycolylaminosanilate, hexylreorinate, hydrabamine, hydrobromide, hydrochloride, hydroxynaphthoate, iodide, setionate, lactate, lactobionate, malate, maleate, mandelate, mesylate, methyl bromide, methylnitrate, mucate, napsylate, nitrate, pamoate, pantothenate, phosphate, diphosphate, polygalacturonate, salicylate, stearate, subacetate, succinate, sulfate, tannate, tartrate, theoclate, triethiodide, or cation salts such as benzathine, chloroprocaine, choline, diethanolamine, ethylenediamine, meglumine, procaine, aluminum, calcium, lithium, magnesium, potassium, sodium or zinc, or drug / polymer complexes such as cyclodextrins, polyvinyl pyrrolidonates and the like. When the drug 31 is present in high dose amounts, more than 20% of the drug layer 30 by weight, the present invention provides a beneficial increased solubility of the drug with low solubility, to allow the creation of a drug layer 30. that can be administered. Additionally, the present invention provides a potentially beneficial increased bioavailability of the drug with low solubility by increasing its solubility and wetted surface for greater bioadhesion to the mucosa of the gastrointestinal tract and increasing the absorption of the drug. The wetting properties of the solubilizing surfactants, may also have the effect of preventing the released drug and the hydrogel vehicle from agglomerating, thereby leading to a more complete spread of the drug composition dispensed onto the absorbable surfaces of the gastrointestinal tract, whose surface area Increased surface area provides more absorption to increase the rate and degree of the drug absorbed and increase the therapeutic response. In addition, the solubilizing surfactant can impart an adhesive character to the drug / hydrogel dispensed, this adhesive character being able to prolong in time the contact that the drug / hydrogel maintains with the mucosal tissue that can be absorbed from the gastrointestinal tract, thus providing more time for the drug to spread and absorb once administered. In yet another potential beneficial effect, the solubilizing surfactant can additionally increase the permeability of the mucous membranes to the drug molecule, wherein the improvement of permeability can also lead to a better bioavailability of the drug and a better therapeutic response. When the drug 31 of the present invention is present in low amounts of doses, less than 20% of the drug layer 30, the present invention provides a beneficial increased bioavailability of the drug with low solubility by increasing its solubility and wet surface for a greater bioadhesion to the mucosa of the gastrointestinal tract and increased permeability of mucosal surfaces. The greater solubility of the drug, the greater surface contact area in the mucosal tissue, the longer contact time with the mucosal tissue and the improvement of the permeability of the mucosal tissue to the drug molecule, can contribute individually or joint to the general therapeutic improvement of the drug by the present invention. Drug 31 is exemplified herein through the use of topiramate, which has poor solubility and is therapeutically required to be administered at high doses. This drug is in the therapeutic category of anti-convulsants, although it could be therapeutic for other indications as well. The solubility of pure topiramate was measured in deionized water at 37 degrees centigrade to be 13 mg / ml. The recommended therapy of topiramate involves an initial dosage of 25-50 mg / day, followed by titration in weekly increments of an additional 25-50 mg up to an effective dose. Typical effective doses can be up to 400 mg per day. The solubility of phenytoin is 0.02 mg / ml, as reported in Analytical Profiles of Drug Substances, Volume 13, edited by Klaus Florey (Academic Press, New York, 1984) p. 425. The recommended therapy for phenytoin is a dose of 100 mg three to four times a day. The recommended dosages and dosing regimens of both drugs are described in the Physician's Desk Reference, 56th Edition (Medical Economics Company, New Jersey, 2002). 2595 and 2626. The structural polymer vehicle 32 comprises a hydrophilic polymer that provides cohesion to the mixture, so that durable tablets can be manufactured. The structural polymer also provides, during operation of the delivery system of the present invention, a hydrogel with viscosity. This viscosity suspends the drug particles to promote a partial or complete dissolution of the drug prior to administration from the dosage form. If the present invention is used in a wear matrix application, the molecular weight of the structural polymer is selected to modify the wear rate of the system. High molecular weight polymers are used to produce a low wear rate and slow administration of the drug, while low molecular weight polymers produce a faster wear rate and faster administration of the drug. A mixture of structural polymers of high and low molecular weight produces an intermediate administration rate. If the present invention is used in a non-porous, non-wearing matrix, the molecular weight of the structural polymer is selected to provide a hydrogel with viscosity within the pores of the matrix. This viscosity suspends the drug particles to promote the total or partial dissolution of the drug in the presence of the solubilizing surfactant prior to administration from the pores of the dosage form. Vehicle 32 provides a hydrophilic polymer particle in the drug composition that contributes to the controlled administration of active agent. Representative examples of these polymers are poly (alkylene oxide) with a number average molecular weight of 50,000 to 8 million, and most preferably 100,000 to 750,000, including poly (ethylene oxide), poly (methylene oxide), poly (butylene oxide) and poly (hexylene oxide); and a poly (carboxymethylcellulose) with a number average molecular weight of 40,000 to 1,000,000,000,000, represented by poly (alkylene carboxymethylcellulose), poly (sodium carboxymethylcellulose), poly (potassium carboxymethylcellulose), poly (calcium carboxymethylcellulose) and poly (lithium) carboxymethylcellulose). The drug composition may comprise a hydroxypropyl alkylcellulose with a number average molecular weight of from 9,200 to 125,000, to increase the administration properties of the dosage form represented by bihydroxypropylethylcellulose, hydroxypropylmethylcellulose, hydroxypropylbutylcellulose and hydroxypropylpentylcellulose; and a poly (vinylpyrrolidone) with a number average molecular weight of 7,000 to 75,000, to increase the flow properties of the dosage form. Among these polymers, poly (ethylene oxide) with a number average molecular weight of 100,000 to 300,000 are preferred. Vehicles that wear out in the gastric environment, that is to say biodegradable vehicles, are especially preferred. Other vehicles that can be incorporated into the drug layer include carbohydrates that exhibit sufficient osmotic activity to be used on their own or with other osmagents. Said carbohydrates comprise monosaccharides, disaccharides and polysaccharides. Representative examples include maltodextrins (ie, glucose polymers produced by the hydrolysis of starch from grains such as corn starch or rice) and the sugars comprise lactose, glucose, raffinose, sucrose, mannitol, sorbitol, cilitol and the like. Preferred maltodextrins are those having a dextrose equivalence (DE) of 20 or less, preferably with an ED ranging from about 4 to about 20 and, frequently, from 9 to 20. The maltodextrin which it has an OD from 9 to 12 and a molecular weight from about 1, 600 to 2,500 has proved to be the most useful.

The carbohydrates described above, preferably maltodextrins, can be used in drug layer 30 without the addition of an osmagent and obtain the desired release of therapeutic agent from the dosage form, while at the same time providing a therapeutic effect throughout. a prolonged period of time and up to 24 hours with a dosage once a day. The preferred scale herein for the concentration of structural polymer within the present invention for osmotic delivery systems is from 5 to 50 weight percent polyoxyethylene, with a molecular weight of 200,000 (Polyox® N80), with an especially preferred scale of 5 to 15 weight percent. The drug layer 30 further comprises a therapeutically acceptable solubilizing agent, the surfactant 33 depicted with vertical dashes in Figure 2 and Figure 3. Acceptable solubilizing agents include, for example, polyoxyl stearates such as polyoxyl 40 stearate, stearate polyoxyl 50, polyoxyl 100 stearate, polyoxyl 12 distearate, polyoxyl 32 distearate and polyoxyl 150 distearate, or mixtures thereof. Yet another class of surfactant useful for the formation of the dissolved drug are the triblock copolymers of ethylene oxide / propylene oxide / ethylene oxide, also known as poloxamers. In this class of surfactants, the ethylene oxide hydrophilic ends of the surfactant molecule and the hydrophobic middle block of propylene oxide of the surfactant molecule serve to dissolve and suspend the drug in the hydrogel that can be pumped. These surfactants are solid at room temperature. Other useful surfactants which are solid at room temperature include sorbitan monopalmitate, sorbitan monostearate, glycerol monostearate and polyoxyethylene stearate (autoemulsifier), polyoxyethylene lanolin 40 sorbitol derivative, polyoxyethylene 75 sorbitol lanolin derivative, beeswax derivative of polyoxyethylene 6 sorbitol, polyoxyethylene 20 sorbitol beeswax derivative, polyoxyethylene 20 sorbitol lanonyla derivative, polyoxyethylene 50 sorbitol lanolin derivative, polyoxyethylene 23 lauryl ether, polyoxyethylene 23 -lauryl ether 23, polyoxyethylene 2-cetyl ether with butylated hydroxyanisole; cetyl polyoxyethylene 10 ether, polyoxyethylene cetyl ether 20, polyoxyethylene 2 stearyl ether, polyoxyethylene 10 stearyl ether, polyoxyethylene 20 stearyl ether, polyoxyethylene 21 stearyl ether, polyoxyethylene oleoyl ether 20, polyoxyethylene stearate 40, polyoxyethylene stearate 50, polyoxyethylene 100 stearate, sorbitan monopalmitate, sorbitan monostearate, sorbitan tristearate, polyoxyethylene 4 sorbitan monostearate, polyoxyethylene sorbitan tristearate 20, phospholipids and fatty acid derivatives of phospholipids such as lecithins, monoglycerides and monoesters of propylene glycol, as monoglyceride of hydrogenated palm oil, monoglyceride of hydrogenated soybean oil, hydrogenated palm stearin monoglyceride, hydrogenated vegetable monoglyceride, hydrogenated cottonseed oil monoglyceride, refined palm oil monoglyceride, partially hydrogenated soybean oil monoglyceride, cottonseed oil monoglyceride, sunflower oil monoglyceride, monoglyceride of canola oil, succinylated monoglycerides, acetylated monoglyceride, acetylated hydrogenated vegetable oil monoglyceride, acetylated hydrogenated coconut oil monoglyceride, acetylated hydrogenated soybean oil monoglyceride, glycerol monostearate, monoglycerides with hydrogenated soybean oil, monoglycerides with hydrogenated oil, hydrogenated palm, succinylated monoglycerides and monoglycerides, rapeseed oil and monoglycerides, cottonseed oils, and monoglycerides, monoglycerides with silicon dioxide of sodium stearyl lactylate, monoester of propylene glycol, diglycerides, triglyceride acids, sugar ester surfactants and the like. Any of the above surfactants may also include optional added preservatives, such as citric acid and butylated hydroxyanisole. In addition, any hydrocarbon chain in the surfactant molecules can be saturated or unsaturated, hydrogenated or non-hydrogenated. A particularly preferred family of surfactants are poloxamer surfactants, which are triblock copolymers a: b: a of ethylene oxide: propylene oxide: ethylene oxide. The "a" and "b" represent the average number of monomer units for each of the blocks of the polymer chain. These surfactants are commercially available from BASF Corporation of Mount Olive, New Jersey, in a variety of different molecular weights and with different values of "a" and "b" blocks. For example, Lutrol® F127 has a molecular weight scale of 9.840 to 14.600, where "a" is about 101 and "b" is about 56, Lutrol F87 represents a molecular weight of 6.840 to 8.830, where "a "is 64 and" b "is 37, Lutrol F108 represents an average molecular weight of 12,700 to 17,400, where" a "is 141 and" b "is 44, as well as Lutrol F68 represents an average molecular weight of 7,680 to 9,510, wherein "a" has a value of about 80 and "b" has a value of about 27. Other particularly preferred surfactants are "sugar ester surfactants, which are sugar esters of fatty acids. Such sugar ester surfactants include sugar fatty acid monoesters, sugar fatty acid diesters, triesters, tetraesters, or mixtures thereof, although mono and diesters are most preferred, preferably the fatty acid monoester. of sugar comprises a fatty acid having 6 to 24 carbon atoms, which may be linear or branched, or saturated or unsaturated C6 to C24 fatty acids. The acid grades of C6 to C24 include C6, 7 >; 8, Ug, 0, 11, L > 12, 13, U 4, U15, 16, C17, 18, 19, G 0, L 21, G22, 23 and 24 on any subscale or combination. Preferably, these esters are selected from stearates, behenates, cocoates, arachidonatos, palmitates, .. myristates, laurates, carprates, oleates, laurates and their mixtures. Preferably, the sugar fatty acid monoester- comprises at least one saccharide unit, such as sucrose, maltose, glucose, fructose, mannose, galactose, arabinose, xylose, lactose, sorbitol, trehalose or methyl glucose. Disaccharide esters such as sucrose esters are more preferred and include sucrose cocoate, sucrose mono-octanoate, sucrose monodecanoate, sucrose mono or dilaurate, sucrose monomyristate, sucrose mono- or dipalmitate, sucrose mono- and distearate, mono, sucrose di-trioleate, sucrose mono or dilinoleate, sucrose polyesters, such as sucrose pentaoleate, hexaoleate, heptaoleate orocto-oleate and mixed esters, such as sucrose stearate / palmitate. Particularly preferred examples of these sugar ester surfactants include those sold by Croda Inc. of Parsippany, NJ, under the names Crodesta F10, F50, F160 and F110 denoting various mixtures of mono, di and mono / diester which comprise sucrose stearates, manufactured using a method that controls the degree of esterification, as described in the US Patent No. 3,480,616. These preferred sugar ester surfactants provide the added benefit of facilitating tabletting and granulation without smearing. The ester surfactants. of sugar may also provide better compatibility with sugar-based therapeutics, as exemplified by topiramate. Also those sold by the company Mitsubishi can be used, with the name esters Ryoto Sugars, for example with reference B370 corresponding to sucrose behenate formed of 20% of monoester and 80% of di, tri and polyester. The stearate / mono and dipalmitate of sucrose sold by the company Goldschmidt under the name "Tegosoft PSE" can also be used. You can also use a mixture of these different products. The sugar ester may also be present mixed with another compound not derived from sugar; and a preferred example includes the mixture of sorbitan stearate and sucrose cocoate sold under the name "Arlateme 2121" by the ICI company. Other sugar esters include, for example, glucose trioleate, di, tri, tetra or galactose pentaoleate, di, tri or tetralinoleate of arabinose or di, tri or tetralinoleate of xylose, or mixtures thereof. Other sugar esters of fatty acids include methylglucose esters including methylgluous distearate and polyglycerol-3 sold by the company Goldschmidt, under the name of Tegocare 450. Maltose or glucose monoesters can also be included, such as methyl O-hexadecanoyl -6-D-glucoside and O-hexadecanoyl-6-D-maltose. Some other sugar ester surfactants include oxyethylenated fatty acid and sugar esters which include oxyethylenated derivatives, such as methyl glucose sesquistearate PEG-20, sold under the name "Glucamate SSE20", by the company Amerchol. A surfactant resource that includes solid surfactants and their properties is available from McCutcheon's Deterqents and Emulsifiers, International Edition 1979 and McCutcheon's Deterqents and Emulsifiers, North American Edition 1979. Other sources of information on the properties of solid surfactants include BASF Technical Bulletin Pluronic & Tetronic Surfactants 1999 and General Characteristics of Surfactants from ICI Americas Bulletin 0-1 10/80 5M, as well as Eastman Food Emulsifiers Bulletin ZM-1 K October 1993. One of the characteristics of the surfactants tabulated in these references is the equilibrium value hydrophilic lipophilic (HLB, for its acronym in English). This value represents the relative hydrophilicity and relative hydrophobicity of a surfactant molecule. In general, the higher the HLB value, the greater the hydrophilicity of the surfactant, while the lower the HLB value, the greater the hydrophobicity. For Lutrol® molecules, for example, the fraction of ethylene oxide represents the hydrophilic portion, while the propylene oxide fraction represents the hydrophobic fraction. The HLB values of the Lutrol F127, F87, F108 and F68 are, respectively, 22.0, 24.0, 27.0 and 29.0. Preferred sugar ester surfactants provide HLB values on the scale from about 3 to about 15. The most preferred sugar ester surfactant, Crodesta F160, is characterized as having an HLB value of 14.5. Surfactants generally have few cohesive properties and, therefore, do not compress into such hard and durable tablets. Additionally, surfactants have the physical form of liquid, pastes or wax solids at standard temperatures and conditions that are unsuitable for oral pharmaceutical tablet dosage forms. Surprisingly, it has been found that the aforementioned surfactants function in the present invention by increasing the solubility and potential bioavailability of the low solubility drugs administered in high doses. The surfactant 33 may be a surfactant or a mixture of surfactants. The surfactants are selected such that they have values that promote dissolution and solubility of the drug. A surfactant with high HLB can be mixed with a surfactant with low HLB, to achieve a net HLB value that is between them, if a particular drug requires an intermediate HLB value. The surfactant 33 is selected depending on the drug being administered, so that the appropriate degree of HLB is used. The present invention involves a method for adapting the suitable solid surfactant or mixture of surfactants with a particular active pharmaceutical agent, to produce the solubilizing center or Center S of the present invention. The method involves preparing aqueous solutions of surfactants that range in a scale of HLB values and a scale of concentrations. Then, the pharmaceutical agent is added in excess to the surfactant solutions and the saturated solubility of active pharmaceutical agent is then measured by a suitable analytical method such as ultraviolet spectroscopy, chromatographic methods or gravimetric analysis. Then, the solubility values are plotted as a function of HLB and as a function of the concentration of the surfactant. The maximum point of solubility generated in the graphs in the different levels of concentrations, reveals the solid surfactant or mixture of surfactants for use in the S Center of the present invention. In those delivery systems that are with more than one drug layer, a ratio of drug concentration gradient between the two or more drug layers is generally in the range of 1.0 to 2.0. When combined with the application of the surfactant in a certain drug to the proportion of surfactant, this ratio can be used to achieve an acceptable upward release rate profile as intended. The ratio of drug to surfactant is generally within the range from about 0.5: 1 to about 2.0: 1 in the drug layers, to achieve a functional release rate profile. A whole series of processing techniques can be used to promote the uniformity of mixing between the drug and the surfactant 33 in the drug layer 30. In a method, each of the drug and the surfactant are micronized to a nominal particle size of less than about 200 microns. Standard micronization procedures such as jet grinding, crixing, ball milling and the like can be used. Alternatively, the drug and the surfactant can be dissolved in a common solvent to produce the mixture at the molecular level and co-dried to form a uniform dough. The resulting mass can be crushed and sifted to produce a free flowing powder. The free flowing powder can be granulated with wet mass sifting or fluid bed granulation with the structural polymer vehicle, to form the drug granulation of the present invention. Alternatively, the drug 31 and the surfactant 33 can be fused together at an elevated temperature to encapsulate the drug in the surfactant and subsequently be cooled to room temperature. The resulting solid can be crushed, sized and granulated with the structural polymer vehicle. In another manufacturing process, the drug and the surfactant can be dissolved in a common solvent or mixture of solvents and spray dried to form a coprecipitate that is incorporated with the structural polymer by standard granulation processing by fluid bed processing or sieving. of wet mass. In still another manufacture, the drug and the surfactant can be dissolved in a common solvent or mixture of solvents, wherein the drug / surfactant solution is sprayed into the structural polymer carrier directly in a fluid bed granulation process. The amount of structural polymer vehicle 32 and surfactant 33 formulated within the drug layer 30 should be selected and appropriately controlled. The excessive structural polymeric vehicle 32 creates a hydrated layer of drug that is too viscous to be administered from the dosage form through the outlet 60, while the small vehicle 32 does not achieve sufficient functional viscosity to control administration. Insufficient levels of structural polymer vehicle 32 also create manufacturing problems because the tablet, lacking sufficient integrity, lacks the ability to withstand grinding and degradation by abrasion or physical impact. Similarly, too much surfactant 33 creates structural instability of the center of the tablet, while too little does not provide sufficient solubilization of the drug layer 30 to allow it to form a suspension or solution that can be administered. The amount of structural polymer vehicle 32 in drug layer 30 should be from 1% to 80% by weight, preferably from 1% to 50%, most preferably from 5% to 50% and, most preferably, from 10% to 40%. In a particular embodiment, the amount of structural polymer is between 5% and 15% by weight of the composition. The amount of surfactant 33 in the dosage form should be from 1% to 50% and, preferably, from 5% to 40%. Low drug doses will require amounts of structural polymeric vehicle at the higher scales, while higher drug doses will require doses of structural polymeric vehicle at the lower scales. The dosage form 30 may further comprise the lubricant 34 represented by a horizontal wavy line in Figure 2 and Figure 3. The lubricant is used during manufacture of the tablet to prevent adhesion to punched walls or punched faces. Typical lubricants include magnesium stearate, sodium stearate, stearic acid, calcium stearate, magnesium oleate, oleic acid, potassium oleate, caprylic acid, sodium stearyl fumarate and magnesium palmitate or mixtures of such lubricants. The amount of lubricant present in the therapeutic composition is 0.01 to 20 mg. The drug layer 30 may additionally comprise a therapeutically acceptable vinyl polymer binder 36 represented by small circles in Figure 2 and Figure 3. The vinyl polymer comprises an average molecular weight of 5., 000 to 350,000, represented by a member selected from the group consisting of poly-n-vinylamide, poly-n-vinylacetamide, poly (vinylpyrrolidone), also known as poly-n-vinylpyrrolidone, poly-n-vinylcaprolactone, poly-n -vinyl-5-metii-2-pyrrolidone and poly-n-vinylpyrrolidone copolymers, with a member selected from the group consisting of vinyl acetate, vinyl alcohol, vinyl chloride, vinyl fluoride, vinyl butyrate, vinyl laureate. and vinyl stearate. The dosage form 10 and the therapeutic composition comprise from 0.01 to 40 mg of the binder or vinyl polymer which serves as the binder. Representatives of other binders include hydroxypropylcellulose, hydroxypropylmethylcellulose, acacia, starch and gelatin. - - - The drug layer 30 will be a dry composition formed by compression of the vehicle, the surfactant and the central drug composition as one layer and the push composition as the other layer in contacting relationship. The drug layer 30 is formed as a mixture containing a therapeutic agent, a carrier and the surfactant which, upon contact with biological fluids in the environment of use, provides a paste, solution or suspension of the compound that could be delivered by the action of the push layer. The drug layer can be formed from particles by spraying which produces the size of the drug and the size of the accompanying polymer used in the manufacture of the drug layer, typically as a center containing the compound, of - conformity with the mode and manner of the invention. The medium for producing particles includes granulation, spray drying, sifting, lyophilization, crushing, grinding, jet grinding, micronization and chopping to produce the desired particle size in microns. The process can be carried out by size reduction equipment, such as a micropulverizing mill, a fluid energy grinding mill, a grinding mill, a roller mill, a hammer mill, a grinding mill, a chiselling mill, a grinding mill of balls, a vibrating ball mill, an impact pulverizer mill, a centrifugal sprayer, a coarse shredder and a fine shredder. The size of the particular can be ensured by monitoring, including a grill screen, a flat screen, a vibrating screen, a rotating screen, a vibrating screen, an oscillating screen and an oscillating screen. Methods and equipment for the preparation of vehicle and drug particles are described in Pharmaceutical Sciences, Remington, 17th Ed., Pp. 1585-1594 (1985); Chemical Enqineers Handbook, Perry, 6th Ed., Pp. 21-13 to 21-19 (1984); Journal of Pharmaceutical Sciences, Parrot, Vol. 61, No. 6, pp. 813-829 (1974); and Chemical Enqineer, Hixon, pp. 94-103 (1990). The drug layer 30 may additionally comprise disintegrants. The disintegrants can be selected from starches, clays, celluloses, algines and gums, as well as cross-linked starches, celluloses and polymers. Representatives of the disintegrants include corn starch, potato starch, croscarmellose, crospovidone, sodium starch glycolate, Veegum HV, methylcellulose, agar, bentonite, carboxymethylcellulose, alginic acid, guar gum, low substitution hydroxypropylcellulose, microcrystalline cellulose and the like. . The therapeutic agent can be provided in the drug layer in amounts from 1 μg to 750 mg per dosage form, preferably from 1 mg to 500 mg per dosage form, or from 10 mg to 250 mg. In other preferred embodiments, the therapeutic agent is provided in an amount of from 10 mg to 400 mg per dosage form, or from 25 to 400 mg per dosage form, depending on the therapeutic agent and the required dosage level that must be maintained. throughout the administration period, ie the time between consecutive administrations of the dosage forms. More typically, loading the compound into the dosage forms will provide compound doses to the subject that range between 20 mg and 350 mg and, more frequently, between 40 mg and 200 mg per day. In general, if a total drug dose greater than 200 mg per day is required, multiple units of the dosage form may necessarily be administered at the same time, to provide the required amount of drug. As a representative compound of the compounds having therapeutic activity described herein, the immediate release of topiramate is generally administered for the treatment of epilepsy with an initial dose of about 25 to 50 mg per day. This regime continues over a period of one week. Then, the dose administered to the patient is titrated ascending every week, with increments of 25 to 50 mg per day, depending on the tolerability until an effective dose is achieved. It has been determined that the effective dose scale-for this indication is generally about 400 mg / day. As a representative compound of the compounds having therapeutic activity described herein, phenytoin immediate deliberation is generally administered at an initial dose of approximately 100 mg, administered in two or four doses, per day. It has been determined that the effective dose scale is generally 200 mg / day to 400 mg / day. The observation of tolerability and the need to achieve an additional clinical effect on the starting dose often causes the dose to increase to a regimen of 200 mg three times a day.

The push layer 40 comprises a displacement composition in contact layer arrangement with the first component drug layer 30 as illustrated in Figure 3. The push layer 40 comprises the osmopolymer 41 which absorbs an aqueous or biological fluid and is swells to push the drug composition through the outlet means of the device. A polymer having suitable absorption properties can be referred to herein as an osmopolymer. Osmopolymers are hydrophilic polymers with the ability to swell, which interact with water and aqueous biological fluids and swell or expand to a high degree, generally presenting a volume increase of 2 to 50 times. The osmopolymer may be crosslinked or non-crosslinked. The push layer 40 comprises from 20 to 375 mg of osmopolymer 41, represented by the symbols "V" in Figure 3. The osmopolymer 41 in layer 40 has a molecular weight higher than that of osmopolymer 32 in the drug layer. 20. Representatives of fluid-absorbing displacement polymers comprise members selected from poly (alkylene oxide) having an average number-average molecular weight of 1 million to 15 million, represented by poly (ethylene oxide) and poly (alkalicarboxymethylcellulose) with a average molecular weight of 500,000 to 3,500,000, where the alkali is sodium, potassium or lithium. Examples of additional polymers for the formulation of the displacement push composition comprise polymers that form hydrogels, such as Carbopol® acidic carboxypolymer, an acrylic polymer crosslinked with a polyallyl sucrose, also known as carboxypolymethylene, as well as a vinyl carboxypolymer it has a molecular weight from 250,000 to 4,000,000; Cyanamer® polyacrylamide; indenomalic anhydride polymers which can be swollen with cross-linked water; Good-rite® polyacrylic acid having a molecular weight of 80,000 to 200,000; Aqua-Keeps® acrylate polymer polysaccharides composed of condensed glucose units, such as a cross-linked diester polyglucan; and other similar ones. Representative polymers that form hydrogels are known in the prior art in the U.S. Patent. No. 3,865,108, issued to Hartop; Patent of E.U.A. No. 4,002,173, issued to Manning; Patent of E.U.A. No. 4,207,893, issued to Michaels; and in Handbook of Common Polymers, Scott and Roff, Chemical Rubber Co., Cleveland, OH. The push layer 40 comprises from 0 to 75 mg and, in the present, from 5 to 75 mg of an osmotically effective compound, the osmagent 42, is represented by large circles in Figure 3. The osmotically effective compounds are also known as osmagents and as osmotically effective solutes. The osmagents 42 that can be found in the drug layer and the push layer in the dosage form are those that exhibit a gradient of osmotic activity along the wall 20. Suitable osmagents comprise a member selected from the group consisting of of sodium chloride, potassium chloride, lithium chloride, magnesium sulfate, magnesium chloride, potassium sulfate, sodium sulfate, lithium sulfate, potassium hydrogen phosphate, mannitol, urea, inositol, magnesium succinate, tartaric acid , raffinose, sucrose, glucose, lactose, sorbitol, inorganic salts, organic salts and carbohydrates. The push layer 40 may further comprise a therapeutically acceptable vinyl polymer 43 depicted with triangles in Figure 3. The vinyl polymer comprises a molecular weight of average viscosity between 5,000 and 350,000, represented by a member selected from the group consisting of polyn. -vinylamide, poly-n-vinylacetamide, poly (vinylpyrrolidone), also known as poly-n-vinylpyrrolidone, poly-n-vinylcaprolactone, poly-n-vinyl-5-methyl-2-pyrrolidone and copolymers of poly-n-vinylpyrrolidone with a member selected from the group consisting of vinyl acetate, vinyl alcohol, vinyl chloride, vinyl fluoride, vinyl butyrate, vinyl laureate and vinyl stearate. The push layer contains 0.01 to 25 mg of vinyl polymer. The push layer 40 may additionally comprise between 0 and 5 mg of a non-toxic dye or dye 46, identified with vertical wavy lines in Figure 3. The dye 35 includes a Food and Drug Administration Dye (FD &C), as blue dye FD &C No.1, red dye FD &C No. 4, red ferric oxide, yellow ferric oxide, titanium dioxide, carbon black and indigo. The push layer 40 may further comprise the lubricant 44, identified with circles means in Figure 3. Typical lubricants comprise a member selected from the group consisting of sodium stearate, potassium stearate, magnesium stearate, stearic acid, stearate calcium, sodium oleate, calcium palmitate, sodium laurate, sodium ricinoleate and potassium linoleate, as well as mixtures of such lubricants. The amount of lubricant included in the push layer 40 is 0.01 to 10 mg. The push layer 40 may additionally comprise an antioxidant 45, depicted with slanted dashes in Figure 3, to inhibit oxidation of the ingredients comprising the expandable formulation 40. The push layer 40 comprises 0.00 to 5 mg of an antioxidant. Representative antioxidants comprise a member selected from the group consisting of ascorbic acid, ascorbyl palmitate, butylated hydroxyanisole, a mixture of 2 and 3 tertiary-butyl-4-hydroxyanisole, butylated hydroxytoluene, sodium isoascorbate, dehydroguarate acid, potassium sorbate, bisulfate of sodium, sodium metabisulfate, sorbic acid, potassium ascorbate, vitamin E, 4-chloro-2,6-diterciary butylphenol, alpha tocopherol and propylgalate. Figure 4 describes a preferred embodiment of the present invention comprising a drug top cover 50 in the dosage form of Figure 3. The dosage form 10 of Figure 4 comprises an upper cover 50 on the outer surface of the wall 20 of the dosage form 10. The top cover 50 is a therapeutic composition comprising from 1 μg to 200 mg of drug 31 and from 5 to 200 mg of a pharmaceutically acceptable carrier selected from the group consisting of alkyl cellulose, hydroxyalkyl cellulose and hydroxypropyl alkyl cellulose . The top coat is represented by methylcellulose, hydroxyethylcellulose, hydroxybutylcellulose, hydroxypropylceluose, hydroxypropylmethylcellulose, hydroxypropylethylcellulose and hydroxypropylbutylcellulose, polyvinylpyrrolidone / vinyl acetate copolymer, polyvinyl alcohol-polyethylene graft copolymer and the like. The top cover 50 provides therapy immediately, as the top cover 50 dissolves or undergoes dissolution in the presence of gastrointestinal fluid and, concurrently, delivers the drug 31 to the gastrointestinal tract for immediate therapy. The drug 31 in the top cover 50 may be the same as or different from the drug 31 in the drug layer 30. Examples of suitable solvents for manufacturing the components of the dosage form comprise inert or accusatory organic solvents that do not adversely harm the materials used in the system. The solvents broadly include members selected from the group consisting of aqueous solvents, alcohols, ketones, esters, ethers, aliphatic hydrocarbons, halogenated solvents, cycloaliphatics, aromatics, heterocyclic solvents and mixtures thereof. Typical solvents include acetone, diacetone alcohol, methanol, ethanol, isopropyl alcohol, butyl alcohol, methyl acetate, ethyl acetate, isopropyl acetate, n-butyl acetate, methyl isobutyl ketone, methyl propyl ketone, n-hexane, n-heptane, monoethyl ethylene glycol ether, ethylene glycol monoethyl acetate, methylene dichloride, ethylene dichloride, propylene dichloride, carbon tetrachloride nitroethane, nitropropanetrachloroethane, ethyl ether, isopropyl ether, cyclohexane, cyclo-octane, benzene, toluene, naphtha, tetrahydrofuran, diglyme , water, aqueous solvents with content of inorganic salts such as sodium chloride, calcium chloride and the like, as well as mixtures thereof, such as acetone and water, acetone and methanol, acetone and ethyl alcohol, methylene dichloride and methanol, as well as ethylene dichloride and methanol. The wall 20 is formed to be permeable to the passage of a fluid, such as water and biological fluids, and is basically impermeable to the passage of the drug 31, the osmagent, the osmopolymer and the like. As such, it is semipermeable. The selectively semipermeable compositions used to form the wall are basically non-wearing and are basically insoluble in biological fluids during the life of the dosage form. Representative polymers for forming the wall 20 comprise semipermeable homopolymers, semipermeable copolymers and the like. Said materials comprise cellulose esters, cellulose ethers and cellulose ester ethers. Cellulosic polymers have a degree of substitution (DS) of their anhydroglucose unit of more than 0 to 3, including the latter. The degree of substitution (DS) means the average number of hydroxyl groups originally present in the anhydroglucose unit that is replaced by a substitution group or converted to another group. The anhydroglucose unit can be partially or completely substituted with groups such as acyl, alkanol, alkenyl, aroyl, alkyl, alkoxy, halogen, carboalkyl, alkylcarbamate, alkylcarbonate, alkylsulfonate, alkisulphamate, semipermeable polymer forming groups and the like, wherein the organic moieties they contain from one to twelve carbon atoms and preferably from one to eight carbon atoms. The semipermeable compositions generally include a member selected from the group consisting of cellulose acylate, cellulose diacylate, cellulose triacylate, cellulose acetate, cellulose diacetate, cellulose triacetate, mono, di, and cellulose trialkanilate, mono, di, and trialkenylates. , mono, di and triaroylates, as well as other similar ones. Examples of polymers include cellulose acetate having a DS of 1.8 to 2.3 and an acetyl content of 32 to 39.9%; cellulose diacetate having a DS of 1 to 2 and an acetyl content of 21 to 35%; cellulose triacetate having a DS of 2 to 3 and an acetyl content of 34 to 44.8%; and other similar ones. The most specific cellulosic polymers include cellulose propionate having a DS of 1.8 and a propionyl content of 38.5%; cellulose acetate propionate having an acetyl content of 1.5 to 7% and an acetyl content of 39 to 42%; cellulose acetate propionate having an acetyl content of 2.5 to 3%, an average propionyl content of 39.2 to 45% and a hydroxyl content of 2.8 to 5.4%; cellulose acetate butyrate having a DS of 1. 8, an acetyl content of 13 to 15% and a butyryl content of 34 to 39%; cellulose acetate butyrate having an acetyl content of 2 to 29%, a butyryl content of 17 to 53% and a hydroxyl content of 0.5 to I4J%; cellulose triacylonates having a DS of 2.6 to 3, such as cellulose trivalerate, cellulose trilamate, cellulose tripalmitate, cellulose trioctanoate and cellulose tripropionate; cellulose diesters having a DS of 2.2 to 2.6, such as cellulose disuccinate, cellulose dipalmitate, cellulose dioctanoate, cellulose dicaprylate and the like; and mixed cellulose esters, such as cellulose acetate valerate, cellulose acetate succinate, cellulose propionate succinate, cellulose acetate octanoate, cellulose valerate palmitate, cellulose acetate, heptanoate and the like. are known in US Patent No. 4,077,407 and can be synthesized by the methods described in Encvclopedia of Polymer Science and Technology, Vol. 3, pp. 325-354 (1964), Interscience Publishers Inc., New York, NY. additional semipermeable polymers to form the outer wall 20 comprise cellulose acetaldehyde dimethyl acetate; cellulose acetate ethyl carbamate; cellulose acetate methyl carbamate; cellulose dimethylamino acetate; semipermeable polyamide; semipermeable polyurethanes; semipermeable sulfonate polystyrenes; semipermeable polymers selectively cross-linked formed by the co-precipitation of an anion and a cation, as described ibe in the Patents of E.U.A. No. 3,173,876; 3,276,586; 3,541, 005; 3,541, 006 and 3,546,142; semipermeable polymers, as described by Loeb et al., in the U.S. Patent. No. 3,133,132; derivatives of semipermeable polystyrenes; semipermeable poly (sodium styrenesulfonate); semipermeable poly (vinylbenzyltrimethylammonium chloride); and semipermeable polymers having a permeability to fluids of 10"5 to 10" 2 (cc.mil / cmhr.Am), expressed in relation to atmosphere of differences of hydrostatic or osmotic pressure along a semipermeable wall. Polymers are known in the art in the patents of E.U.A. No. 3,845,770; 3,916,899 and 4,160,020; and in Handbook of Common Polymers, Scott and Roff (1971) CRC Press, Cleveland, OH. The wall 20 may optionally be formed as two or more sheets as those described in the U.S. Patent. No. 6,210,712. Wall 20 may also comprise a flow regulating agent. The flow regulating agent is an added compound to help regulate fluid permeability or flow through the wall 20. The flow regulating agent can be a flow enhancing agent or a flow reducing agent. The agent can be preselected to increase or decrease the flow of liquid. Agents that produce a marked increase in fluid permeability, such as water, are often basically hydrophilic, while those that produce a marked reduction for fluids such as water are basically hydrophobic. The amount of regulator in the wall, when incorporated into that site, is generally from about 0.01% to 20% by weight or more. The flow regulating agents may include polyhydric alcohols, polyalkylene glycols, polyalkylene diols, polyesters of alkyl ene glycols and the like. Typical flow enhancers include polyethylene glycol 300, 400, 600, 1500, 4000, 6000 and other similar; low molecular weight glycols, such as polypropylene glycol, polybutylene glycol and polyamylene glycol: polyalkylene diols such as poly (1,3-propanediol), poly (1,4-butanediol), poly (1,6-hexanediol) and the like; aliphatic derivatives such as 1,3-butylene glycol, 1,4-pentamethylene glycol, 1,4-hexamethylene glycol and the like; alkylene triols such as glycerin, 1,3-butanetriol, 1,4-hexanetriol, 1,3,6-hexanetriol and the like; esters such as ethylene glycol dipropionate, ethylene glycol butyrate, butylene glycol dipropionate, glycerol acetate ester and the like. Preferred flow enhancers herein include the group of bifunctional propylene glycol block copolymer polyoxyalkylene derivatives known as Lutroles. Representative flow reducing agents include phthalates substituted with an alkyl or alkoxy, or both with an alkoxy group and alkyl, such as diethyl phthalate, dimethoxyethyl phthalate, dimethyl phthalate and [di (2-ethylhexyl) phthalate] , aryl phthalates such as triphenyl phthalate and butyl benzyl phthalate; vinyl polyacetate, triethyl citrate, Eudragit; insoluble salts such as calcium sulfate, barium sulfate, calcium phosphate and the like; nonsoluble oxides such as titanium oxide; polymers in powder, granule and similar form, such as polystyrene, polymethylmethacrylate, polycarbonate and polysulfone; esters such as esters - citric acid esterified with long chain alkyl groups; fillers basically impermeable to water and inert; resins compatible with cellulose-based wall-forming materials and the like.

Other materials may be included in the semipermeable wall material to impart flexibility and elongation properties to make the wall 20 less brittle and provide tear resistance. Suitable materials include phthalate plasticizers such as dibenzyl phthalate, dihexyl phthalate, butyl octyl phthalate, long-chain phthalates six to eleven carbons, di-isononyl phthalate, di-isodecyl phthalate and the like. Plasticizers include nonphthalates as triacetin, citrate esters as triethyl citrate, dioctyl azelate, epoxidized phthalate, tri-isoctyl trimellitate, tri-isonol trimellitate, sucrose acetate isobutyrate, epoxidized soybean oil and the like. The amount of plasticizer in a wall, when incorporated in that site, is from about 0.01% to 20% by weight or greater. A total cover can conveniently be used to provide the walls of the completed dosage form. In the system of total cover, wall-forming composition for wall 20 is deposited by successive spraying of the composition suitable wall on the center dual layer or single tablet comprising the drug layer to the center of single layer or layer of drug and the push layer for the laminated center, accompanied by capsizing in a rotating pan. A total cover is used due to its availability in the market. Other techniques can be used to cover the compressed center. Once covered, the wall is dried in a forced air oven or in a controlled temperature and humidity oven, to release the dosage form of the solvent (s) used in the manufacture. The drying conditions will be conventionally selected based on the available equipment, the ambient conditions, the solvents, the coatings, the thickness of the cover and the like. Other coating techniques can also be used. For example, the wall or walls of the dosage form can be formed with a technique, using the air suspension method. This method consists of suspending and dumping the compressed single or double layer core in a stream of hot air and the semipermeable wall forming composition, until the wall is applied to the center. The air suspension method is well adapted to independently form the wall of the dosage form. The air suspension process is described in the U.S. Patent. No. 2,799, 241; in J ^ Am. Pharm. Assoc. Vol. 48, pp. 451-459 (1959); and ibid., Vol. 49, pp. 82-84 (1960). The dosage form can also be covered with a Wurster® air suspension cover using, for example, methylene dichloride mixed with methanol as a co-solvent for the wall-forming material. An Aeromatic® air suspension cover can be used using a co-solvent. The dosage forms according to the present invention are manufactured by standard techniques. For example, the dosage form can be manufactured by the wet granulation technique. In the wet granulation technique, the drug, carrier and surfactant are mixed using an organic solvent, such as denatured anhydrous ethanol, as the granulation fluid. The remaining ingredients can be dissolved in a portion of the granulation fluid, such as the solvent described above, and this last prepared solution is added slowly to the drug mixture with continuous mixing in the mixer. The granulation fluid is added until a wet mixture is produced, wherein the wet mass mixture is forced to then pass through a predetermined sieve into baking trays. The mixture is dried for 18 to 24 hours at a temperature of 24 ° C to 35 ° C in a forced air oven. The size of the dry granules is then achieved. Subsequently, magnesium stearate or other suitable lubricant is added to the drug granulation and the granulation is placed in grinding jars and mixed in a grinding jar for up to 10 minutes. The composition is. compress to form a layer, for example, on a Manesty® press or a Korsch LCT press. For a double layer center, the drug-containing layer is compressed and a similarly prepared wet mixture of the push layer composition, if included, is compressed against the layer containing the drug. Intermediate compression generally occurs under a force of approximately 50 to 100 newtons. Final stage compression generally occurs with a force of 3500 Newtons or more, often from 3500 to 5000 Newtons. The centers compressed with a single or double layer are fed in a dry coating press, for example, Kilian® Dry Coating Press and, subsequently, covered with the wall materials described above. A similar procedure is employed for those centers that are manufactured with a pusher layer and more than one drug layer, generally in a Korsch multilayer press. One or more exit ports are drilled at the end of the drug layer of the optional water-soluble dosage form and top covers, which may be colored (e.g., Opadry color coatings) or be transparent (e.g., Opadry Transparent), can be coated on the dosage form, to provide the finished dosage form. In another manufacture, the drug and other ingredients comprising the drug layer are mixed and compressed to form a solid layer. The layer has dimensions corresponding to the internal dimensions of the area that the layer must occupy in the dosage form and also has dimensions corresponding to the second thrust layer, if included, to form a contact arrangement therewith. The drug and other ingredients can also be mixed with a solvent and mixed to form a solid or semi-solid form by conventional methods, such as ball milling, calendering, stirring or roller milling, and then compressed to arrive at a preselected shape. Subsequently, if included, a layer of osmopolymer composition is placed with the drug layer in a similar manner. The layering of the drug formulation and the osmopolymer layer. they can be manufactured by conventional two-layer press techniques.

The compressed centers can then be covered with the semipermeable wall material as described above. - Another manufacturing process that can be used comprises mixing the powder ingredients for each layer in a fluid bed granulator. After the powdered ingredients are dry mixed in the granulator, a granulation fluid, for example, poly (vinylpyrrolidone) in water, is sprayed into the powders. The coated powders are then dried in the granulator. This procedure granulates all the ingredients that are present in that site while adding the granulation fluid. After the granules are dried, a lubricant, such as stearic acid or magnesium stearate, is mixed in the granulation using a mixer, for example, V mixer or box mixer.

The granules are then compressed in the manner described above. The outlet 60 is provided in each of the dosage forms. The outlet 60 cooperates with the compressed center for the uniform release of drug from the dosage form. The exit can be provided during the manufacture of the dosage form or during the administration of the drug by the dosage form in a fluid use environment. The outlet 60 may include an orifice that is formed or can be formed from a substance or polymer that wears, dissolves or is leached from the outer wall, to thereby form an exit orifice. The substance or polymer may include, for example, a poly (lactic acid) or a poly (glycolic) acid that can be worn on the semipermeable wall; a gelatinous filament; a poly (vinyl) alcohol that can be removed in water; a compound that can be leached, such as a fluid-removable pore former, selected from the group consisting of inorganic and organic salt, oxide and carbohydrates. The outlet or a plurality of outlets may be formed by leaching a member selected from the group consisting of sorbitol, lactose, fructose, glucose, mannose, galactose, talose, sodium chloride, potassium chloride, sodium citrate and mannitol, to provide an orifice output pore size uniform release. The outlet can have any shape, such as round, triangular, square, elliptical and the like for the uniform measured dose release of a drug from the dosage form. The dosage form can be made with one or more outlets in a separation ratio or one or more surfaces of the dosage form. Perforation, including laser and mechanical drilling, through the semi-permeable wall can be used to form the exit orifice. Said outlets and equipment for forming said outlets are described in the U.S. Patent. No. 3,916,899, by Theeuwes and Higuchi, and in the U.S. Patent. No. 4,088,864, by Theeuwes et al. In the present description it is preferred to use a single outlet orifice.

The release of the present invention provides an effective therapy for 24 hours. This dosage form releases drug 31 for approximately 16 to 24 hours after administration with an optional immediate release drug top coat administration and a controlled drug release that continues thereafter, until the center ceases to release drug. The representative dosage forms had T70 values of more than 10 hours and released topiramate for a continuous period of time of more than about 16 hours. Approximately within the next 2 hours after the administration, each of the different dosage forms were releasing topiramate from the center at a uniform upward rate or of the order of zero uniform, depending on the composition of the drug layer and the layers of push, which continued for a prolonged period of about 8 to 14 hours or more. After the prolonged period of administration, the drug continues to be administered for several more hours, until the dosage form is spent or is expelled from the Gl tract. In a double-layer embodiment of the once-a-day dosage forms according to the present invention, the dosage forms have a T70 of about 15 to 18 hours and, preferably, of about 17 hours and provided release of topiramate during a continuous period of time of at least about 24 hours. Approximately within the next 2 hours after administration, topiramate is released at a rate of release that continues for a prolonged period of time. After this extended period of uniform release rates, the drug release continues for several more hours until the dosage form is terminated. The dosage forms of this invention exhibit a sustained release of drug over a continuous period of time including a prolonged time in which the drug is released at a uniform rate of release determined in a standard release rate assay as described in the present. The method is put into practice with dosage forms which are adapted to release the compound at different rates of release between about 1% / hr to about 12% / hr for a prolonged period of at least about 12 hours, preferably 14 hours or more. It is preferred to practice the above methods by orally administering a dosage form to a subject once a day for therapeutic treatment. Preferred methods for the manufacture of the dosage forms of the present invention are generally described in the examples that follow. All percentages are percentages by weight, unless otherwise indicated.

Description of Examples of the Invention The following examples are illustrative of the present invention and should not be construed as limiting the scope of the invention in any way, since these examples and other equivalents thereof will be apparent to the person skilled in the art. in light of the "present description, drawings and appended claims.

EXAMPLE 1 Method for practicing the invention - - - A drug layer of the present invention was prepared in the following manner. Aqueous solutions of five surfactants were prepared. The selected surfactants were four grades of ethylene oxide / propylene oxide / ethylene oxide (grades Lutrol F127, F87, F108 and F68) stearate PEG-40 (Myrj 52). The solutions were made at concentrations of 1.5 and 15 percent by weight. The solutions of aqueous surfactant mixtures were cooled as necessary: to promote the complete dissolution of the surfactant prior to the drug solubility studies. Each surfactant had a different HLB value and ranged on a scale of 16.9 to 29 units of HLB. The aqueous surfactant solutions were then equilibrated at a constant temperature in a water bath at a temperature of 37 ° C. Subsequently, the pure topiramate drug was added slowly with stirring in increments of about 10 mg to the surfactant solutions, until no more dissolved drug was present. A control sample of drug dissolved in deionized water without surfactant was included for comparison purposes. The resulting saturated solutions of the drug were filtered through 0.8 micron filters and analyzed for drug concentration by refractive index chromatography. The resulting solubility values were plotted as a function of both the concentration of the surfactant and the hydrophilic-lipophilic equilibrium value of each surfactant. Figure 6 was made from the solubility values obtained and HLB data for each surfactant used. This method reveals three things. With respect to Figure 6, the solubility of topiramate in water is increased for each surfactant. The solubility of the drug is higher in the presence of each surfactant, compared to the control, where the solubility in the deionized water without surfactant was 13.0 mg / ml. Second, a high concentration of surfactant is more effective in solubilizing the drug than a low concentration. Third, the most effective HLB values to increase the solubility of this drug are found at the lower end, on the scale of 16.9 to 22. Each of the three concentrations of surfactant forms the maximum solubility of topiramate with an HLB that includes this scale of HLB values. Therefore, Lutrol F127 or Lutrol F127 mixed with Myrj 52, which has a HLB value of 16.9, is a preferred surfactant for topiramate in the present invention. After this finding, a central drug composition of the present invention was prepared. First, 55 grams of topiramate, 30 grams of Lutrol F127 granular, 11.5 grams of. Ethylene polyoxide (PEO) N80 and 3 grams of polyvinylpyrrolidone (PVP) 2932 were passed through a # 40 mesh sieve and the composition was mixed dry to achieve a uniform mixture, where the PVP It acts as a binder and the PEO acts as the vehicle. The molecular weight of the ethylene polyoxide was 200,000 grams per mole, while the molecular weight of the polyvinylpyrrolidone was about 10,000. The polyoxyethylene serves as carrier and structural polymer 32. The polyvinylpyrrolidone serves as the binder of the drug layer 36. The dried mixture was then moistened with anhydrous ethyl alcohol SDA 3A and stirred to form a uniformly moistened mass. The wet mass was then passed through a 20 mesh sieve, forming wet trickles. The threads were air-dried under ambient conditions overnight, then passed through a # 20 mesh sieve, forming free-flowing granules. Finally, 0.5 grams of magnesium stearate lubricant drug layer 34 were passed through a # 60 mesh sieve on the granules and mixed in the grains. This shaped the granulation of the drug layer composition.A granulation of expandable composition was prepared in a similar manner. First, 89 grams of ethylene polyoxide, 303.7 grams of sodium chloride and 3 grams of hydroxypropyl methylcellulose E5, were passed through a # 40 mesh sieve and mixed dry. The ethylene polyoxide had a molecular weight of about 7,000,000, while the hydroxypropyl methylcellulose had a molecular weight of about 11, 300. The ethylene polyoxide served as the osmopolymeric thrust layer 41 and the hydroxypropyl methylcellulose provided the binder for the thrust layer 43. Subsequently, the dry mixture was wetted with anhydrous ethyl alcohol SDA 3A and mixed to form a uniform wet mass. The dough was passed through a # 20 mesh sieve, forming hilillos that were dried with air during "" the night. Subsequently, the trickles were again passed through a # 20 mesh sieve, forming free-flowing granules. Finally, 0.5 grams of magnesium stearate of less than # 60 mesh magnesium stearate, the lubricant of the thrust layer 44, was emptied into the mixture. This shaped the granulation of the expandable composition. A portion of the granulation of the central drug composition weighing 182 mg was filled into a punched cavity with a diameter of 0.476 centimeters and tamed lightly with a 0.476 centimeter round biconvex tablet tool. Then, 60 mg of the expandable composition granulation was filled into the die and compressed and laminated into the drug layer using a force of 0.5 tons with a Carver press. Six of these double layer tablets were compressed. Subsequently, the tablets were covered with three layers. First, a solution was prepared by dissolving 57 grams of hydroxyethyl cellulose 250L and 3 grams of polyethylene glycol in 940 grams of deionized water. The hydroxyethyl cellulose had a molecular weight of about 90,000, while the polyethylene glycol had a molecular weight of 3,350. This formed a softening cover solution to provide a smooth coatable surface for subsequent coatings. The six active tablets were mixed in a bed of tablets of placebo tablets weighing 0.5 kg. The bed of tablets was covered with this softening cover solution in an Aeromatic coater. The solution was applied in a stream of dry, hot air, until about 4 mg of cover weight was accumulated in each active tablet. The coating solution was continuously stirred during the coating process. The resulting softener coat produced a smooth tablet substrate and rounded the corners of the tablets. This softener cover is optional and is especially useful for rounding the corners of the tablets, where the surfaces of the tablets have remnants of the compression process. The resulting soft tablets were dried in a forced air oven at 40 ° C overnight. The following coating solution was prepared by dissolving 269.5 grams of ethyl cellulose 100 cps, 196.0 grams of hydroxypropyl cellulose EFX and 24.5 grams of Myrj 52 in 6510 grams of anhydrous ethanol SDA3A with stirring and heating. The ethyl cellulose had a molecular weight of about 220,000, while the hydroxypropyl cellulose had a molecular weight of about 80,000. The solution was allowed to stand at room temperature for several days. This formed the membrane sublayer solution. The above soft tablets were mixed on a bed of placebo tablets weighing 1.2 kg and the resulting mixed bed was loaded into a full Vector LDCS cover adapted with a full cover with a pan to apply covers with a diameter of 35.56. The membrane sublayer solution was then sprayed onto a bed of tablets in the coater in a stream of hot air. The coating solution was continuously stirred during the procedure. The solution was applied in this manner until approximately 5.5 mils (or thousandths of an inch) of cover were accumulated in each drug tablet. So, 175 grams of cellulose acetate 398-10 and 75 grams of Lutrol F68 were dissolved in 4,750 grams of acetone with heating and stirring. The cellulose acetate had an average acetyl content of about 39.8 weight percent and a molecular weight of about 40,000. This shaped the upper membrane cover solution. This upper membrane cover solution was applied to the bed of placebo centers and active in the LDCS total cover until 5 mils of membrane top cover were accumulated in each drug tablet. The three cover layers formed the wall 20 of the present invention. An administration port 60 was drilled mechanically through the three cover layers on the side of the drug layer of the tablets, using a drill and drill bit 40 mil in diameter. The systems were then dried in a forced air oven at a temperature of 40 ° C to remove residual processing solvents. The six resulting systems were tested in relation to drug release in deionized water at a temperature of 37 ° C by sampling every 2 hours for 24 hours. The drug release was monitored with refractive index chromatography. The resulting drug release rate is shown in Figure 7. Drug 31 was administered according to an upward release rate for 12 to 14 hours. The time to administer 90% of the 100 mg dose was approximately 18 hours. The cumulative administration in 24 hours was 97.5%. The membranes were intact throughout the administration rhythm. The systems were small enough to be easily swallowed by a patient, even with the high drug loading of 55% present in drug layer 30. Similar systems were formulated with expandable push layers with 55% drug in the drug layer. drug, but without the solubilizing surfactant, in an attempt to implement the prior art technology. However, said prior art systems were not operative. These formulations representing the prior art did not solubilize the drug and produced layers of drug that could not be pumped. The membranes of these systems are split open in situ during in vitro tests, emptying the bolus of the drug in an uncontrolled manner, due to the stress induced within the membrane by the swelling pressure generated by the expanding thrust layer which pushed against the composition of insoluble drug mass through the narrow port of 40 thousand.

EXAMPLE 2 A central drug composition of 9.0 grams of micronized Lutrol F127 was mixed dry with 16.5 grams of topiramate. Topiramate had a nominal particle size of 80 microns. Subsequently, 3.45 grams of Poliox N80 and 0.9 grams of polyvinylpyrrolidone were sieved through a mesh of less than 40 and mixed in the mixture. Then, 5 grams of anhydrous ethanol were added slowly with stirring to form a wet mass. The wet mass was passed through a # 16 mesh sieve and dried with air overnight at room temperature. The resulting dry strings were again passed through a # 16 mesh sieve. Then, 150 mg of magnesium stearate was passed through a # 60 mesh sieve onto the dried granules and mixed in the granules. The concentration of surfactant in this drug composition granulation was 30 percent by weight. The granulation of the expandable thrust layer was prepared by passing 63.67 grams of Polyox, 303.3 grams of sodium chloride and 5 grams of hydroxypropyl methyl cellulose through a # 40 mesh sieve and mixing dry to form a uniform mixture. Then, 1.0 grams of ferric oxide red was passed through a # 60 mesh sieve to the mix. The resulting mixture was wet kneaded by slowly adding SDA3A anhydrous ethyl alcohol with agitation, to form a moist mass in a uniform manner. This mass was then passed through a # 20 mesh sieve, producing yarns that were dried at a temperature of 40 ° C in forced air at night. The dried strings were passed through a # 16 mesh sieve to form free-flowing granules. Finally, 25 mg of magnesium stearate and 8 mg of butylated hydroxytoluene were sieved through a # 80 mesh sieve to form the granules and mixed. A portion of the central granulation composition of the drug with a weight of 182 mg was filled into a round die of 0.476 centimeters in diameter and compressed slightly with concave punches of 0.476 centimeters. Subsequently, 60 mg of the granulation of the push layer was added to the drug layer and the two layers were laminated with a force of 800 kilograms force. Six tablets were made. Tablets were covered as described in Example 1 with 5 mg of softener cover, 5.4 mils of the sublayer membrane and 5J mils of the top cover membrane. An outlet port of 40 mils in diameter was drilled through the three layers of deck and the systems were dried overnight at a temperature of 40 ° C in forced air. The resulting systems were tested as described in Example 1. The release profile of topiramate is shown in Figure 8. The systems released 99% of the drug over a period of 24 hours. The rate of release is gently ascending over time during the first 14 hours where 76% of the drug is released. The system released approximately 90% of the drug for 19 hours. The final system is of the same size as is convenient and feasible for patients who need to swallow it as described in Example 1.

EXAMPLE 3 The systems were made as described in Example 2, although the surfactant 33 comprised a mixture of two surfactant solubilizers. The central granulation composition of the drug was made according to the procedures of Example 2, except that the surfactant consisted of 15 weight percent of micronized Lutrol F 127 and 15 weight percent of Myrj 52 was replaced by 30 percent in weight of micronized Lutron F127. The heavy average HLB value of the two surfactants produced an HLB value of 19.5 which is the midpoint between the two HLB values of the individual surfactants. The rate of administration of the resulting systems is shown in Figure 11. The system was administered essentially at a rate of the order of zero between 4 hours and 14 hours. The systems released 88% of the dose for 24 hours.

EXAMPLE 4 Systems were developed as described in Example 3, although with a greater weight of the expandable thrust layer. The expandable push layer weighed 90 mg substituted by 60 mg of weight of the systems in Example 3. The rate of administration of the resulting systems is shown in Figure 10. The system was administered at an upward rate of release for approximately 12 hours. hours, then the rhythm became descending. The amount of drug administered during 24 hours was 93% EXAMPLE 5 Capsule configured in the form of a tablet, see Figure 5.

EXAMPLE 6 A drug composition, drug layer 30, was formed consisting of 30% by weight drug topiramate, 56% by weight of Lutrol F127 surfactant, 10% by weight of Polyox N-80 vehicle and 3% by weight of PVP2932 and 2% by weight of stearic acid by wet granulation with ethanol anhydride. A thrust composition consisting of 63.37% by weight of Polyox 303 (7,000,000 molecular weight), 30% by weight of NaCl, 5% by weight of HPMC E5, 1% by weight ferric oxide, 0.5% by weight of stearate Mg and 0.08% by weight of BHT was granulated wet with anhydrous ethanol. Tablets with 333 mg of the central drug composition (100 mg topiramate) and 133 mg of push composition were compressed using a tool to form compressed tablets of 0.714 centimeters. The total weight of the tablet (capsule-shaped) is 466 mg. The systems were covered, punctured and dried according to "the procedures described in Example 1. The systems were punctured and drug release was tested, producing a rate of release of the order of zero when administering the drug at a stable rate of approximately 5.8 mg per hour for approximately 16 hours.

EXAMPLE 7 100 mg system in three layers of topiramate with capsule form An adapted, designed dosage form formed as an osmotic drug delivery device is made in the following manner, starting with a first layer of the drug composition. First, 3000 g of topiramate, 2520 g of ethylene polyoxide with an average molecular weight of 200,000 and 3630 g of poloxamer 407 (Lutrol F127) having an average molecular weight of 12,000 were added to a bowl of bed granulator. fluid. Next, two separate binding solutions, the poloxamer binder solution and the polyvinylpyrrolidone identified as K29-32 having an average molecular weight of 40,000 of the binder solution, were prepared by dissolving 540 g of the same poloxamer 407 (Lutrol F127) in 4860 g of water and 495 g of the same polyvinyl pyrrolidone in 2805 of water, respectively. The dry materials are granulated in a fluid bed, first by rolling them with 2700 g of the poloxamer binder solution and followed by the spraying of 2000 g of the polyvinyl pyrrolidone binder solution. The granulation is then dried in the granulator until an acceptable moisture content is reached and is sized by passing it through a mesh sieve 7. The granulation is then transferred to a mixer and mixed with 5 g of butylated hydroxytoluene as a antioxidant and is lubricated with 200 g of stearic acid and 75 g of magnesium stearate. Next, a second layer of drug composition is prepared in the following manner: 4000 g of topiramate, 213 g of ethylene polyoxide with average molecular weight of 200,000, 4840 g of poloxamer 407 (Lutrol F127) having an average molecular weight of 12,000 and 10 g of ferric oxide, black are added to a bowl of the fluid bed granulator. Next, two separate binding solutions, the poloxamer binder solution and the polyvinylpyrrolidone identified as IL29-32 having an average molecular weight of 40,000 of the binder solution were prepared by dissolving 720 g of the same poloxamer 407 in 6480 g of water and 495 g. g of the same polyvinyl pyrrolidone in 2805 of water, respectively. The dry materials are granulated in a fluid bed by first spraying 3600 g of the poloxamer binder solution and then spraying 2000 g of the polyvinyl pyrrolidone binder solution. The wet granulation is then dried in the granulator until an acceptable moisture content is reached, and is sized by passing it through a 7 ~ mesh sieve. Next, the granulation is transferred to a mixer and mixed with 2 g of butylated hydroxytoluene as an antioxidant and lubricated with 200 g of stearic acid and 75 g of magnesium stearate. Next, a push composition was prepared in the following manner: first, a binder solution was prepared. 7.5 kg of polyvinylpyrrolidone identified as K29-32 having an average molecular weight of 40,000 in 50.2 kg of water was dissolved. Then, 37.5 kg of sodium chloride and 0.5 kg of ferric oxide are sized using a Quadro Comil with a 21 mesh sieve. Then, sifted materials and 80.4 kg of ethylene polyoxide (approximately 7,000,000 molecular weight) were added to a bowl of the fluid bed granulator. The dry materials are fluidized and mixed while 48.1 kg of the binder solution is sprayed from 3 nozzles onto the powder. The granulation is dried in the fluid bed chamber until an acceptable moisture level is achieved. The coated granules are sized using a Fluid Air mill with a mesh sieve 7. The granulation is transferred to a carrier vessel, mixed with 63 g of butylated hydroxytoluene and lubricated with 310 g stearic acid. Next, the topiramate drug compositions (first drug layer and second drug layer) and the push composition are compressed into three layer tablets in a Korsch multi-layer press. First, 120 mg of the first layer of topiramate drug composition is added to the die cavity and pre-compressed, then 160 mg of the second topiramate drug composition layer is added to the die cavity and are previously compressed once more, and finally, the thrust composition is aggregated to achieve the total system weight of 480 mg and the layers are pressed in a three layer configuration with a deep concave capsule shape 0.635 centimeters in diameter. The three-layer configurations are covered with a two-layer polymer membrane laminate, in which the first cover layer is an already rigid water-permeable laminate and the second cover layer is a semi-permeable membrane laminate. The first laminated composition membrane comprises 55% ethylcellulose, 45% hydroxypropyl cellulose and 5% polyoxyl 40 stearate (PEG 40 stearate or Myrj 52S). The composition that forms the membrane dissolves in 100% ethyl alcohol to achieve a solids solution at 7%. The composition forming the membrane is sprayed on and around the cover having a total cover measuring 10 kg until approximately 45 mg of membrane is applied to each tablet. Next, the three-layer configurations covered with the first membrane laminate are covered with the semi-permeable membrane. The membrane forming the composition comprises 70% cellulose acetate having 39.8% acetyl content and 30% poloxamer 188 (Lutrol F68). The membrane that forms the composition is dissolved in 100% acetone solvent to achieve a 5% solids solution. The membrane that forms the composition is sprayed on and around the three-layer configurations in a total cover until approximately 35 mg of membrane has been applied to each tablet.

Next, a 40 mil (1 mm) exit passage is perforated with a laser beam through the two-layer membrane laminate to connect the drug layer to the exterior of the dosing system.

The residual solvent is removed by drying for 72 hours at a temperature of 40 ° C and humidity. Then the colored cover is placed on the perforated and dried systems. The upper color cover is a suspension of 12% Opadry solids in water. The suspension of the colored top cover is sprayed on the three layer systems until a average weight cover of approximately 25 mg per system. Then, the upper color cover systems are covered with a transparent cover. The transparent cover is a solution of 5% solids of Opadry in water. The solution-transparent cover is sprayed over the centers covered with color until it achieves an average wet weight of approximately 10 mg per system. The dosage form produced by this manufacturing system is designed to deliver 100 mg of topiramate in an ascending manner at a given controller rate of administration - from the center containing the first drug layer of 30% topiramate, the 25.2% of ethylene polyoxide having 200,000 molecular weight, 39% of poloxamer 407 (Lutrol F127), the 3% of polyvinylpyrrolidone having 40,000 molecular weight, 0.05% of butylated hydroxytoluene, 2% of stearic acid and 0.75% magnesium stearate, and the second drug layer of 40% topiramate, 2.13% ethylene polyoxide having 200,000 molecular weight, 52% poloxamer 407 (Lutrol F127), 3% polyvinylpyrrolidone having 40,000 of molecular weight, 0.1% of black ferric oxide, 0.05% of butylated hydroxytoluene, 2% of stearic acid and 0.75% of magnesium stearate. The thrust composition comprises 64.3% ethylene oxide comprising 7,000,000 molecular weight, 30% sodium chloride, 5% polyvinylpyrrolidone having an average molecular weight of 40,000, 0.4% ferric oxide, 0.05% butylated hydroxytoluene and 0.25% stearic acid. The two-layer membrane laminate, in which the first membrane layer comprises 55% ethylcellulose, 45% hydroxypropyl cellulose and 5% polyoxyl 40 stearate (PEG 40 stearate or Myrj 52S), and the second membrane laminate is a semi-permeable wall comprising 80% cellulose acetate, 39.8% acetyl content and 20% poloxamer 188 (Lutrol F68). The dosage form comprises a passage of 40 mils (1 mm) in diameter formed on the drug end of the delivery system. The final dosage form contains a colored top cover and transparent top cover and the time to achieve 90% release of drugs in an ascending fashion is approximately 12-14 hours. A representative release profile is shown in Figure 13.

EXAMPLE 8 12.5 mg system in three layers of capsid-shaped topiramate A dosage form adapted, designed and formed as an osmotic drug delivery device is manufactured in the following manner, starting with the first drug layer. First, add 4 g of topiramate, 40 g of ethylene polyoxide with average molecular weight of 200,000, 4 g of poloxamer 407 (Lutrol F127) having an average molecular weight of 12,000 and 1.5 g of polyvinylpyrrolidone identified as K29- 32 which has an average molecular weight of 40,000 to a mixing vessel or bowl. Next, the dry materials are mixed for 60 seconds. Then, 16 mL of denatured anhydride alcohol are slowly added to the mixed materials with continuous mixing for about 2 minutes. Then, the freshly prepared wet granulation is allowed to dry at room temperature for approximately 16 hours, and it is passed through a 16 mesh sieve. Next, the granulation is transferred to a suitable container, mixed and lubricated with 0.5 g of stearic acid. Next, the second drug layer is prepared in the following manner: 6 g of topiramate, 35.95 g of ethylene polyoxide with average molecular weight of 200,000, 6 g of poloxamer 407 (Lutrol F127) having an average molecular weight of 12,000 , 1.5 g of polyvinylpyrrolidone identified as K29-32 having an average molecular weight of 40,000 and 0.05 g of ferric oxide are added to a vessel or mixing bowl. Next, the dry materials are mixed for 60 seconds. Then, 16 mL of the denatured anhydride alcohol is slowly added to the mixed materials with continuous mixing for about 2 minutes. Next, the freshly prepared wet granulation is allowed to dry at room temperature for approximately 16 hours, and is passed through a 16 mesh sieve. The granulation is then transferred to a suitable container, mixed and lubricated with 0.5 g of stearic acid. Next, a push composition is prepared in the following manner: first, a binder solution is prepared. 7.5 kg of polyvinylpyrrolidone identified as K29-32 having an average molecular weight of 40,000 was dissolved in 50.2 kg of water. Then, 37.5 kg of sodium chloride and 0.5 kg of ferric oxide are sized using a Quadro Comil with a 21 mesh sieve. Then, sifted materials and 80.4 kg of Ethylene Polyoxide (approximately 7,000,000 molecular weight) are added to a bowl of the fluid bed granulator. The dry materials are fluidized and mixed while 48.1 kg of binder solution is sprayed from 3 nozzles onto the powder. The granulation is dried in the fluid bed chamber to an acceptable moisture level. The coated granules are sized using a Fluid Air mill with a 7-mesh sieve. The granulation is transferred to a carrier vessel, mixed with 63 g of butylated hydroxytoluene and lubricated with 310 g of stearic acid. Next, the topiramate drug compositions (first drug layer and second drug layer) and the push composition are compressed into three layer tablets in the Carver Tablet Press. First, 56 mg of the first layer of topiramate drug composition is added to the die cavity and is precompressed, then, 67 mg of the second topiramate drug composition layer is added to the die cavity and previously compressed one more time, and finally, the thrust composition is added to achieve the total system with a weight of 211 mg and the layers are pressed in a three layer configuration of deep concave capsule of 0.476 centimeters in diameter. The three-layer configurations are covered with a polymeric membrane laminate in which the first cover layer is an already rigid water-permeable laminate and the second cover layer is a semi-permeable membrane laminate. The cover is elaborated in a casserole to elaborate coverings of 10 kg of measure by means of the load of tip of topiramate of the systems of three layers of topiramate with tablets of placebo. The first composition of the membrane laminate comprises 55% ethylcellulose, 45% hydroxypropyl cellulose and 5% polyoxyl 40 stearate (PEG 40 stearate or Myrj 52S). The membrane that forms the composition dissolves in 100% ethyl alcohol to make a 7% solids solution. The membrane forming the composition is sprayed on and around the three layer configuration in a pan to apply covers until approximately 30 mg of membrane is applied to each tablet. Next, the three-layer configurations covered with the first membrane laminate are covered with the semi-permeable membrane. The membrane forming the composition comprises 80% cellulose acetate having 39.8% acetyl content and 20% poloxamer 188 (Lutrol F68). The composition that forms the membrane is dissolved in 100% acetone solvent to make a 5% solids solution. The membrane forming the composition is sprayed onto and around the three layer compositions a casserole to apply covers until a total of about 25 mg of membrane is applied to each tablet. Then, a 30 mil (0.76 mm) exit passage is perforated with a laser beam through the membrane laminate to connect the drug layer to the exterior of the dosing system. The residual solvent is removed by drying for 72 hours at a temperature of 40 ° C and room humidity. Then the perforated and dry systems are covered with a colored cover. The color cover is a suspension of 12% Opadry solids in water. The colored top cover is sprayed over the three layer systems until an average wet cover system of approximately 15 mg per system is achieved. The dosage form produced by this means of manufacture is designed to deliver 12.5 mg of topiramate in an ascending form at a controlled rate determined from the center containing the first drug layer of 8% topiramate, 80% ethylene polyoxide having 200,000 molecular weight, 8% poloxamer 407 (Lutrol F127), 3% polyvinylpyrrolidone having 40,000 molecular weight and -1% stearic acid, and the second drug layer 12% topiramate, 71.9% polyoxide of ethylene having 200,000 molecular weight, 12% of poloxamer 407 (Lutrol F127), 3% of polyvinylpyrrolidone having 40,000 molecular weight, 0.1% of ferric oxide and 1% of stearic acid. The thrust composition comprises 64.3% ethylene polyoxide comprising 7,000,000 molecular weight, 30% sodium chloride, 5% polyvinylpyrrolidone having an average molecular weight of 40,000, 0.4% ferric oxide, 0.05 % butylated hydroxytoluene and 0.25% stearic acid. The two-layer membrane laminate in which the first membrane layer is comprised of 55% ethylcellulose, 45% hydroxypropyl cellulose and 5% polyoxyl 40 stearate (PEG 40 stearate or Myrj 52S), and the second Membrane laminate is a semipermeable wall, which is comprised of 80% cellulose acetate of 39.8% acetyl content and 20% poloxamer 188 (Lutrol F68). The dosage form comprises a passage of 30 mils (0.J6 mm) in diameter located on the drug side of the delivery system. The final dosage form could contain a colored top cover and a transparent top cover and the time to achieve 90% of the drug release in an ascending form is approximately 16 hours.

EXAMPLE 9 Double layer 100 mg system in the form of a topiramate capsule An adapted dosage form designed and formed as an osmotic drug delivery device is manufactured in the following manner: firstly, 2880 g of topiramate, 958 g of ethylene polyoxide with average molecular weight of 200,000 and 4980 g are added. of poioxamer 407 (Lutrol F127) having an average molecular weight of 12,000 to a bowl of the fluid bed granulator. Next, two separate binding solutions, the plyoxamer binder solution and the polyvinylpyrrolidone identified as K29-32 having an average molecular weight of 40,000 binder solution are prepared by dissolving 500 g of the same poloxamer 407 (Lutrol F127) in 4500 g of water and 750 g of the same polyvinyl pyrrolidone in 4250 of water, respectively. The dry materials are granulated in a fluid bed by first spraying 3780 g of the poloxamer binder solution and followed by the spraying of 3333 g of the polyvinyl pyrrolidone binder solution. Then, the wet granulation is dried in the granulator until an acceptable moisture content is reached, and it is dimensioned using a 7 mesh sieve to pass it. Next, the granulation is transferred to a mixer and is mixed with 2 g of butylated hydroxytoluene as an antioxidant and is lubricated with 200 g of stearic acid and 100 g of magnesium stearate. Next, a pusher composition is prepared in the following manner: first, a binder solution is prepared. 7.5 kg of polyvinylpyrrolidone identified as K29-32 having an average molecular weight of 40,000 is dissolved in 50.2 kg of water. Then, 37.5 kg of sodium chloride and 0.5 kg of ferric oxide are dimensioned using a Quadro Comil with a 21 mesh sieve. Then, the sifted materials and 80.4 kg of Ethylene Polyoxide (approximately 7,000,000 molecular weight) are added to a bowl fluid bed granulator. The dry materials are fluidized and mixed while 48.1 kg of binder solution is sprayed from 3 nozzles onto the powder. The granulation is dried in the fluid bed chamber to an acceptable moisture level. The coated granules are sized using a Fluid Air Mill with a mesh sieve 7. The granulation is transferred to a carrier vessel, mixed with 63 g of butylated hydroxytoluene and lubricated with 310 g of stearic acid. Next, the topiramate drug composition and the push composition are compressed into two-layer tablets in a Korsch multi-layer press. First, 278 mg of the topiramate composition is added to the die cavity and pre-compressed, then, the push composition is added to achieve the total system weight of 463 mg and the layers are pressed to a two-layer configuration deep concave shaped capsule of 0.59 centimeters in diameter. The two-layer configurations with two-layer polymeric membrane laminate covers wherein the first cover layer is an already rigid water-permeable laminate and the second cover layer is a semi-permeable membrane laminate. The first membrane laminate composition comprises 55% ethylcellulose, 45% hydroxypropylcellulose and 5% polyoxyl stearate 40 (PEG 40 stearate or Myrj 52S). The membrane that forms the composition dissolves in 100% ethyl alcohol to make a 7% solids solution. The membrane that forms the composition is sprayed on and around the configurations in a total cover until approximately 38 mg of membrane is applied to each of the tablets. Next, the three-layer configurations covered with the first membrane laminate are covered with the semi-permeable membrane. The membrane forming the composition comprises 80% cellulose acetate having 39.8% acetyl content and 20% poloxamer 188 (Lutrol F68). The membrane that forms the composition is dissolved in 100% acetone solvent to make a 5% solids solution. The membrane that forms the composition is sprayed onto and around the configurations in a total cover until "approximately 30 mg of membrane is applied to each of the tablets., a 45 mil (1.14 mm) exit passage is perforated with laser beam through the two layer membrane laminate to connect the drug layer to the exterior of the dosing system.

The residual solvent is removed, by drying for 72 hours at a temperature of 40 ° C and room humidity. Next, the drilled and dried systems are covered with an immediate release drug top cover. The top coat of the coated drug is a 13% aqueous solids solution containing 780 g of topiramate, 312 g of copovidone (Kollidone VA 64) and 208 g of hydroxypropyl methylcellulose having an average molecular weight of 11,200. The top cover solution of coated drug is sprayed onto the dry cover centers until an average wet cover weight of approximately 33 mg per system is achieved. Next, the covered drug systems are covered with color. The upper color cover is a suspension of 12% Opadry solids in water. The colored top coat suspension is sprayed onto the drug over the covered systems until an average wet cover weight of approximately 25 mg per system is achieved. Then, the systems covered with color receive a transparent cover. The transparent cover is a solution of 5% solids of Opadry in water. The clear cover solution is sprayed over the centers with colored covers until an average wet cover weight of approximately 25 mg per system is achieved. The dosage form produced by this manufacture is designed to deliver 20 mg of topiramate as an immediate release from a top cover comprised of topiramate at 60% topiramate, 24% copovidone and 16% hydroxypropyl methylcellulose followed by controlled administration of 80 mg of topiramate. mg of topiramate from the center containing 28.8% topiramate, 9.58% of ethylene polyoxide having 200,000 molecular weight, 53.6% of poloxamer 407 (Lutrol F127), 5% of polyvinylpyrrolidone having 40,000 molecular weight, 0.02% of butylated hydroxytoluene, 2% stearic acid and 1% magnesium stearate. The thrust composition comprises 64.3% ethylene polyoxide comprising 7,000,000 molecular weight, 30% sodium chloride, 5% polyvinylpyrrolidone having an average molecular weight of 40,000, 0.4% ferric oxide, 0.05% butylated hydroxytoluene and 0.25% stearic acid. The two-layer membrane laminate includes a first membrane layer comprised of 55% ethylcellulose, 45% hydroxypropyl cellulose and 5% polyoxyl stearate 40 (PEG 40 stearate or Myrj 52S), and the second membrane layer is a semi-permeable wall, which is comprised of 80% cellulose acetate of 39.8% acetyl content and 20% poloxamer 188 (Lutrol F68). The dosage form comprises a passage, 45 mils (1.14 mm) to the center of the drug side. The final dosage form contains a colored top cover and a transparent top cover and has an average release rate of 6 mg topiramate per hour in the form of the order of zero.

EXAMPLE 10 A central drug composition comprising 53.7 grams of topiramate, 29.8 grams of Crodesta F160, 10 grams of ethylene polyoxide N-80 and 6 grams of polyethylene pyrrolidine K90, in which the particles have a size of at least 40 mesh. they were dried mixed for about 30 minutes. The dried mixture was then wetted with 20 grams of anhydrous ethyl alcohol SDA 3A while stirring to form a homogeneous wet mass. The wet mass was passed through a # 20 stainless steel sieve to form strings, and dried under a cap under ambient conditions for about 12 hours (overnight). The dried strings were passed through a # 20 stainless steel sieve to form granules. These dry granules were then lubricated with 0.5 grams of < 60 mesh magnesium stearate using a mixing roller for 3 minutes. This granulation constitutes the drug layer for the systems that exhibit the drug release illustrated in Figures 14A and 14B. The osmotic layer granulation was made using the same procedures, wherein 73.7 grams of ethylene polyoxide 303.2 grams of sodium chloride, 5 grams of polyvinylpyrrolidone K2932, 1 gram of ferric oxide and 0.05 grams of BHT were mixed dry for 30 minutes. The dried mixture was then wetted with 80 grams of anhydrous ethyl alcohol SDA 3A while stirring to form a homogeneous wet mass. The homogenous wet mass was then passed through a # 20 stainless steel mesh sieve to form strings. These yarns were dried for approximately 12 hours under a cap under ambient conditions. The dried threads were then passed through a # 20 stainless steel mesh sieve to form the granules. These dry granules were then lubricated with 0.25 grams of stearic acid by means of a roller mixer for 3 minutes. This granulation constitutes the osmotic (push) layer for the systems illustrated in Figures 14A and 14B. Both the drug and the osmotic layers were used to form a two-layer center using an LCT tool 0.476 centimeters in diameter. The weight of the 182 mg drug layer granulation was introduced into the die first and then, it was compacted slightly, then an osmotic layer granulation weighing 60 mg was introduced and then compressed in a Carver Press press to a compression force of 0.75 tons. This procedure was repeated until a desired amount of test tablets was produced. For the initial trials, 10 tablets were produced. To these tablets, 3 layers of cover were applied. The first cover, a softener cover, provided a smooth surface for successive control rate coatings. For the softener cover, 5 grams of Poloxamer 407 was dissolved in 783 grams of deionized water by agitation. Then 45 grams of hydroxyethylcellulose was introduced into the solution and stirred until a clear solution was obtained. A device was used to apply aeromatic Aeromatic Coater covers for this cover. The 10 active tablets were mixed with placebo tablets (fillers) to provide a cover load of 500 grams. Standard airsoft cover procedures were followed to cover approximately 3 to 4 mg of cover in each active tablet. The active coating tablets were dried in an oven at a temperature of 40 ° C and room humidity for approximately 12 hours. For tablets compressed with tablet production machinery, this softener cover may not be necessary. The second cover was prepared by dissolving 77 grams of ethylcellulose (100cps), 56 grams of EFX hydroxypropylcellulose, and 7 grams of Myrj 52S in 4.527 grams of ethanol type SDA3A ethanol while stirring. Agitation was carried out until a homogeneous solution was achieved. After stirring, the solution was sealed and stored under ambient conditions for about 2 days, before its application. An LDCS vector cover was used for this cover. To achieve a 1.2 kg cover load, the 10 tablets of smooth active covers were mixed with placebo filler tablets and covered with the second cover. The standard total cover procedures were used for the cover procedure with a target cover of approximately 6 mils. For the third coat, 87.5 grams of cellulose acetate 398-10 and 37.5 grams of Lutrol F68 were dissolved in 2.375 grams of acetone with stirring and heating. This cover was applied using the same cover material and standard cover procedure as with the second cover. Then, the active cover tablets were manually drilled to produce an orifice of 40 thousand, and then dried in an oven at a temperature of 40 ° C and room humidity for about 12 hours (overnight). The rate of release of drugs and residues was determined as described in Example 1 from 5 of these tablets at 2 hour intervals for 24 hours. The results shown in Figures 14A and 14B, show that topiramate was administered at a rate of upward release for 12-14 hours. The time to administer 90% of the 100 mg of the dose was approximately 16 hours. Cumulative administration at 24 hours was 99%. The membranes were found intact through the rate of administration.

EXAMPLE 11 Using the same granulation procedure described in Example 10, the following formulation consisting of 50 grams of topiramate, 33.5 grams of Crodesta F-160, 10 grams of N-80 ethylene polyoxide, and 6 grams of polyvinylpyrrolidone K90, were granulated wetted and lubricated with 0.5 grams and magnesium stearate. This constitutes a drug layer with a charge of 33.5% surfactant compared to 29.8% of Example 10. The tablets were made following the procedures and materials described in Example 10. The rate of drug release was determined as described in Example 1. The results, shown in Figures 15A and 15B, showed that topiramate was administered at a rate of upward release for 12-14 hours. The time to administer 90% of the 100 mg dose was approximately 16 hours. Cumulative administration at 24 hours was 99.5%. The membranes remained intact through the rate of administration.

EXAMPLE 12 The tablets were made as described in Examples 10 and 11, although using a drug layer granulation consisting of 38.5% surfactant (Crodesta F160). An osmotic thrust layer composition in the amount of 60 mg was used. The compositions and membrane amounts applied were approximately the same as the counterpart tablets in Examples 10 and 11. The rate of drug release was determined in those tablets according to the same procedures described in Example 1. The results, shown in Figures 16A and 16B show that topiramate was administered at an upward release rate for 14-16 hours. The time for administration of 90% of the 100 mg dose was approximately 17 hours. Cumulative administration at 24 hours was 98.7%. The membranes remained intact through the rate of administration.

EXAMPLE 13 Using standard procedures for fluid bed granulation, 288 grams of topiramate, 536 grams of Crodesta F-160, 95.8 grams of N-80 ethylene polyoxide, and 5 grams of polyvinylpyrrolidone were granulated. This granulation was then lubricated with 2 grams of stearic acid and 1 gram of magnesium stearate. A Glatt fluid bed granulator with capacity (1 kg) was used for this granulation. To test whether this granulation is muddy or not, a tablet production was performed with a multi-layer tablet press (Korsch Multi-Layer Tablet Press). Using the same press and tablet parameters, another tablet production was performed using a counterpart granulation containing Poloxamer 407 as the surfactant. -It was observed that it was presented as muddy in the tablet towers and in the punches it was observed with the granulation that contains Crodesta F160. In contrast, smear was observed with the granulation containing Poloxamer 407. Therefore, the sugar ester surfactant provides an advantage in the formulation of dosage forms with respect to the Poloxamer surfactant and the sugar ester surfactant. Crodesta is another preferred surfactant for topiramate in the present invention.

EXAMPLE 14 The dosage forms were prepared using the procedures set forth in Example 1, using the following compositions: a core composition consisting of a drug layer composed of 50% topiramate, 27% Myrj 52, 11% NaCl, 10.5% Polyox N80, 1% PVPK90 and 0.5% magnesium stearate (200 mg total weight), and a thrust layer composed of 89% polyoxy 303.7% NaCl, 3% of hydroxypropylmethylcellulose E5, 0.5% ferric oxide and 0.5% magnesium stearate (60 mg total weight). The dosage form was covered with a softening cover composed of 4 mg of hydroxyethylcellulose 250L and polyethylene glycol.3350 (95/5 weight ratio).

A sublayer of 5.5 mils of ethylcellulose (100 cps viscosity) / hydroxypropylcellulose EFX / Myrj 52 was applied in a weight proportion of 55/40/5. An upper final cover composed of 4.1 mils of cellulose acetate 398 and Lutrol F 68 (weight ratio of 70/30) was applied.

Finally, a 1 x 40 mils outlet port was drilled in the dosage form. The release profile for this formulation is shown in Figure 9. Topiramate was administered at a rate of release of the order of zero from about 4 hours to 14 hours, and the amount of topiramaine administered over a 24-hour period was 87.7. %. A second dosage form having a central composition consisting of a drug layer composed of 55% topiramate, 30% Myrj 52, 0% NaCl, 11.5% Polyox N80, 3% PVPK2932, was prepared. and 0.5% magnesium stearate (182 mg total weight), and a thrust layer composed of 63.67% Poliox 303, 30% NaCl, 5% hydroxypropylmethylcellulose E5, 1% ferric oxide, 0.5 % magnesium stearate and 0.08% BHT (60 mg total weight). The dosage form was covered with a softening cover composed of 4 mg of hydroxyethylcellulose 250L and polyethylene glycol 3350 (95/5 weight ratio). A sublayer of 5.5 mils of ethylcellulose (100 cps viscosity) / EFX / Myrj 52 hydroxypropyl cellulose was applied in a weight ratio of 55/40/5. A final top cover composed of 3 mils-cellulose acetate 398-10 and Lutrol F 68 (weight ratio 70/30) was applied. Finally, an output port of 1 x 40 mils was drilled in the dosage form. The release profile for this formulation is shown in Figure 12. Topiramate was administered at a release rate of the order of zero from about 2 hours to about 8 to 10 hours, and the amount of topiramate administered over a period of 24 hours. it was 91.0% ..

The invention also relates to a method for administering from 1 μg to 750 mg of therapeutic agent to a patient in need of therapy. The method, in one administration, comprises orally administering to the patient, a therapeutic agent or its salt that is administered from a therapeutic composition, from 5 mg to 500 mg of a structural polymer carrier having from 100,000 to 7 million molecular weight, and from 5 to 600 mg of a surfactant having an HLB identified by drug solubility studies, whose composition provides therapy over a prolonged period of time. The invention provides methods for administering therapeutic agents to a patient, and methods for producing a plasma concentration of therapeutic agents. The method of the invention is provided for orally administering to a patient, a dosage form that is administered at a controlled rate, for a continuous time of up to 24 hours the drug for the intended therapy. The method also comprises orally administering to a patient, a therapeutic dose of therapeutic agent from a single dosage form that administers the agent for 24 hours. Considering that the above specification comprises the described modalities, it should be understood that variations and modifications may be made thereto in accordance with the principles described without departing from the invention.

Claims (60)

1. NOVELTY OF THE INVENTION CLAIMS 1. - A controlled release therapeutic composition, comprising a low solubility therapeutic agent, a structural polymer carrier and a solubilizing surfactant selected from a polyoxyl stearate, poloxamer, sugar ester surfactant, or mixtures thereof.
2. 2. A controlled release therapeutic composition, comprising a low solubility therapeutic agent, a structural polymer carrier and a solubilizing surfactant adapted to release high doses of the therapeutic agent, wherein said surfactant is selected from a polyoxyl stearate, poloxamer, sugar ester surfactant or mixtures thereof.
3. 3. The composition according to claim 2, further characterized in that the therapeutic agent is present in an amount between about 1 μg and 750 mg.
4. 4. The composition according to claim 2, further characterized in that the therapeutic agent is present in an amount of between about 10 mg and about 250 mg. 5. - The composition according to claim 2, further characterized in that the therapeutic agent is present in an amount between about 25 mg and about 400 mg. 6. The composition according to claim 2, further characterized in that the therapeutic agent has an aqueous solubility of less than about 1 μg / ml. 7. The composition according to claim 2, further characterized in that the therapeutic agent has an aqueous solubility that is between about 1 μg / ml and about 100 mg / ml. 8. The composition according to claim 7, further characterized in that the therapeutic agent has an aqueous solubility that is between about 1 μg / ml and about 50 mg / ml. 9. The composition according to claim 2, further characterized in that the amount of structural polymer is between about 1% and 80% by weight of the composition. 10. The composition according to claim 9, further characterized in that the amount of structural polymer is between about 5% and 50% by weight of the composition. 11. - The composition according to claim 10, further characterized in that the amount of structural polymer is between about 5% and 15% by weight of the composition. 12. The composition according to claim 2, further characterized in that the structural polymer is ethylene polyoxide from about 100,000 to 300,000 molecular weight. 13. The composition according to claim 2, further characterized in that the solubilizing surfactant is polyoxyl 40 stearate, polyoxyl 50 stearate, polyoxyl 100 stearate, polyoxyl 12 distearate, polyoxyl 32 distearate, polyoxyl distearate. 150 or mixtures thereof. 14. The composition according to claim 2, further characterized in that the sugar ester surfactant is a sugar fatty acid monoester, a sugar fatty acid diester or mixtures thereof. 15. The composition according to claim 2, further characterized in that the sugar ester surfactant comprises at least one saccharide unit. 16. The composition according to claim 14, further characterized in that the sugar fatty acid monoester, the sugar fatty acid diester, or both, comprise sucrose. 17. - The composition according to claim 2, further characterized in that the solubilizing surfactant is in micronized form having a nominal particle size of less than about 50 microns in diameter. 18. The composition according to claim 2, further characterized in that the therapeutic agent is in micronized form having a nominal particle size of less than about 50 microns in diameter. 19. The composition according to claim 14, further characterized in that the sugar fatty acid monoester, the sugar fatty acid diester, or both, comprise a fatty acid having from 6 to 24 carbon atoms. 20. The composition according to claim 2, further characterized in that the amount of solubilizing surfactant is between about 1% and 50% by weight of the composition. 21. The composition according to claim 12, further characterized in that the amount of solubilizing surfactant is between about 1% and 40% by weight of the composition. 22. The composition according to claim 2, further characterized in that the therapeutic agent is topiramate or salts or derivatives thereof. 23. A composition comprising a therapeutic agent of low solubility, a structural polymer and a solubilizing surfactant adapted to release the therapeutic agent over a prolonged period of time, wherein said surfactant is selected from a polyoxyl stearate, poloxamer , sugar ester surfactant, or mixtures thereof. 24. The composition according to claim 23, further characterized in that the therapeutic agent of low solubility is present in an amount of between about 1 μg and 750 mg. 25. The composition according to claim 24, further characterized in that the therapeutic agent of low solubility is present in an amount of between about 10 mg and about 250 mg. 26. The composition according to claim 25, further characterized in that the therapeutic agent of low solubility is present in an amount of between about 25 mg and about 400 mg. 27. The composition according to claim 23, further characterized in that the therapeutic agent of low solubility has an aqueous solubility that is less than about 1 g / ml. 28. The composition according to claim 23, further characterized in that the therapeutic agent of low solubility has a solubility of between about 1 μg / ml and about 100 mg / ml. 29. The composition according to claim 28, further characterized in that the therapeutic agent of low solubility has a solubility of between about 1 μ / ml and about 50 mg / ml. 30. The composition according to claim 23, further characterized in that the amount of structural polymer is between about 1% and 80%) by weight of the composition. 31. The composition according to claim 30, further characterized in that the amount of structural polymer is between about 5% and 50%) by weight of the composition. 32. The composition according to claim 31, further characterized in that the amount of structural polymer is between about 5% and 15% by weight of the composition. 33. The composition according to claim 23, further characterized in that the structural polymer is polyethylene polyoxide of about 100,000 to 300,000 molecular weight. 34. The composition according to claim 23, further characterized in that the solubilizing surfactant is polyoxyl 40 stearate, polyoxyl 50 stearate, polyoxyl 100 stearate, polyoxyl 12 distearate, polyoxyl 32 distearate, polyoxyl distearate 150 distearate or mixtures thereof. 35. The composition according to claim 23, further characterized in that the sugar ester surfactant is a sugar fatty acid monoester, a sugar fatty acid diester, or mixtures thereof. 36. The composition according to claim 23, further characterized in that the sugar ester surfactant comprises at least one saccharide unit. 37. The composition according to claim 35, further characterized in that the monoester of sugar fatty acid, sugar fatty acid diester, or both, comprise sucrose. 38.- The composition according to claim 35, further characterized in that the monoester of sugar fatty acid, sugar fatty acid diester, or both, comprise a fatty acid having from 6 to 24 carbon atoms. 39.- The composition according to claim 23, further characterized in that the amount of solubilizing surfactant is between about 1% and 50% by weight of the composition. . . 40.- The composition according to claim 39, further characterized in that the amount of solubilizing surfactant is between about 1% and 40% by weight of the composition. 41.- The composition according to Claim 23, further characterized in that the low solubility therapeutic agent is topiramate or salts or derivatives thereof. The composition according to claim 23, further characterized in that the therapeutic agent of low solubility is released for a period of time ranging from about 1 hour to about 24 hours. 43.- A composition comprising a therapeutic agent of low solubility, a structural polymer and a solubilizing surfactant, wherein the composition is a solid and wherein said surfactant is selected from a polyoxyl stearate, poloxamer, ester surfactant of sugar or mixtures thereof. 44.- A controlled release pharmaceutical composition comprising a low solubility therapeutic agent, a structural polymer - and a solubilizing surfactant adapted to increase the solubility of the therapeutic agent, wherein said surfactant is selected from a polyoxyl stearate, poloxamer, sugar ester surfactant or mixtures thereof. 45.- A dosage form for the controlled release of a therapeutic composition comprising a therapeutic agent of low solubility, a structural polymer and a solubilizing surfactant, wherein said surfactant is selected from a polyoxyl stearate, poloxamer, surfactant of sugar ester or mixtures thereof. 46.- The dosage form according to claim 45, further characterized in that the dosage form is a matrix system. 47. The dosage form according to claim 45, further characterized in that the dosage form is an osmotic system. 48. The dosage form according to claim 45, further characterized in that the dosage form is adapted to be administered once a day. 49.- The dosage form according to claim 45, further characterized in that it is adapted to deliver a high dose of the therapeutic agent. 50.- The dosage form in accordance with the Claim 49, further characterized in that the high dose of the therapeutic agent is between about 20% and about 90% by weight of the therapeutic composition. 51.- The dosage form according to claim 50, further characterized in that the high dose of the therapeutic agent is between about 30% and about 40% by weight of the therapeutic composition. 52. The dosage form according to claim 45, further characterized in that the therapeutic agent is selected from topiramate, or salts or derivatives thereof. 53.- A controlled release oral dosage form for once-a-day administration of a therapeutic agent comprising: a. a center which includes: i. a low solubility therapeutic agent; ii. a structural polymer; iii. a solubilizing surfactant; b. a semipermeable membrane that surrounds the center; and c. an exit orifice through the semipermeable membrane, which communicates with the center in such a way as to allow the release of the therapeutic agent to the environment; wherein the dosage form releases the therapeutic agent for a prolonged period of time, and wherein said surfactant is selected from a polyoxyl stearate, poloxamer, sugar ester surfactant, or mixtures thereof. 54.- The controlled release oral dosage form according to claim 53, further characterized in that it is adapted to release the therapeutic agent at a rate of release substantially in the order of zero or at a rate of release basically upward. 55.- The controlled release oral dosage form according to claim 53, further characterized in that it is adapted to release the therapeutic agent with a pulse release profile or a pulse release profile after a delay. 56. - The controlled release dosage form according to claim 54, further characterized in that the dosage form releases the therapeutic agent after a delay. 57.- The controlled release dosage form according to claim 53, further characterized in that the therapeutic agent is topiramate or salts or derivatives thereof. 58.- The use of the dosage form as defined in Claim 53, for preparing a medicament for administering high doses of low solubility therapeutic agents. 59.- The use of the dosage form that is defined in the Claim 53, for preparing a medicament for increasing the bioavailability of a poorly soluble therapeutic agent. 60.- The use claimed in Claim 58 or 59, wherein said therapeutic agent is topiramate or salts or derivatives thereof.