Article Useful for Administration of Pharmacologically-Active Substances Transdermally, Orally, or by Means of Implant

1. Field of the Invention

This invention relates broadly to articles of manufacture for administration of pharmacologically-active substances, transdermally, orally and by means of implant (e.g., subdermal implant). The devices consist essentially of a vinyl chloride polymer or copolymer of vinyl chloride containing a majority of vinyl chloride monomeric units and a small amount of other vinyl monomeric units, e.g., vinyl acetate, and intimately dispersed therewith at least one of said pharmacologically-active agents and a plasticizer. Examples of pharmacologically-active agents are isosorbide dinitrate, nicotine, indomethacin, clonidine, glyceryl trinitrate, guanfacine and prostaglandin. Contemplated within the scope of this invention are devices for the controlled release and transdermal administration of such pharmacologically-active agents as nitroglycerine (e.g. in the treatment of conditions, e.g., angina pectoris).

2. The Prior Art

Many prior art articles of manufacture have been disclosed for controlled release delivery of various drugs including transdermal delivery of nitroglycerin. In general, however, available commercial devices and indeed devices published in the prior art are limited with respect to rate of delivery of pharmacologically-active substance.

Canadian Pat. No. 930,668 discloses a bandage for administering drugs comprised of a backing member, a pressure sensitive adhesive, and at least one reservoir disposed between the backing member and pressure sensitive adhesive. The reservoir is comprised of a systemically active drug formulation confined within a wall member, the wall member being formed from a drug release rate controlling material. The reservoir can be in the form of discrete microcapsules or distinct reservoir compartments or layers. The reservoir can also be in the form of walled containers having one or more interior drug-containing chambers, as well as solid matrixes having a systemically active drug distributed therethrough. The Canadian patent discloses a wide variety of materials which can be used to form the reservoir. Among the materials mentioned are silicone rubbers, hydrophilic polymers of monoesters of an olefinic acid, polyvinylalcohol, polyvinylacetate, plasticized polyvinylchloride, plasticized nylon, collagen, modified collagen, gelatin, and waxes such as polyethylene wax, oxidized polyethylene wax, hydrogenated castor oil and the like, with the silicone rubbers being preferred. The Canadian patent does to contain any examples showing the use of plasticized polyvinyl chloride, and does not show the use of a PVC plastisol.

Similarly, Zaffaroni, U.S. Pat. No. 3,921,636 issued on Nov. 25, 1975 discloses a drug delivery device for administering a drug at a controlled rate for a prolonged period of time comprising a plurality of reservoirs containing drug distributed through a matrix. The reservoirs and the matrix are formed of materials permeable to passage of the drug. The rate of drug permeation from the reservoir is lower than the rate of permeation through the matrix so that release from the reservoir is the drug release rate controlling step. Thus, Example 6, at column 15, lines 5-30 of U.S. Pat. No. 3,921,636 relates to a polyvinyl chloride resin containing plasticizer and prednisolone disodium phosphate thusly:

"A drug delivery device for the controlled, oral administration of water-soluble prednisolone is prepared as follows: first, a plurality of drug reservoirs comprising porous, discrete particles of polymerized poly(vinyl chloride) of about 100 microns diameter are prepared by mixing 100 g of suspension grade poly(vinyl chloride) resin with 50 g of octyl diphenyl phosphate and 10 g of predinisolone disodium phosphate at room temperature into a sticky, wet mass. Next, the temperature of the mixture is raised to 80.degree. C. for about 3 to 7 minutes, while stirring, to form dry, free flowing, discrete drug reservoirs. The reservoirs are uniformly dispersed through a matrix by mixing 50 g of reservoirs containing the prednisolone with 140 g of polydimethylsiloxane, 10 g of silicone oil, and 0.5 g of stannous octoate. After mixing the ingredients, the mixture is charged into pill molds and allowed to cure for 30 minutes. Oral administration of the resulting device yields a controlled essentially constant rate of release of prednisolone phosphate to the gastrointenstinal tract to give a more uniform blood level of premisolone over a longer period of time than is achieved when prednisolone alcohol is administered by standard prior art pills."

Furthermore, as is well known, polyvinyl chloride (PVC) is never used alone, but is always mixed with other ingredients before being processed. Polyvinyl chloride appeared initially to be an unpromising resin because of its thermal instability and high rigidity. PVC, however, was then discovered to form a rubber-like material when dissolved hot in high boiling solvents known as plasticizers and cooled to room temperature. PVC is now available in a number of different physical forms and types, and its manufacture depends on the form desired. Thus, PVC is available as a vinyl latex, a dispersion resin, or a general purpose resin. PVC latexes are true colloidal dispersions of submicrometer particles in water, stabilized by a surfactant system, and need plasticizers in order to form a continuous film. The PVC in vinyl latex is manufactured by emulsion polymerization.

Dispersion resins are produced by emulsion polymerization and are mixed with plasticizers to form a colloidal dispersion. Such dispersions are known as plastisols and are easily handled and readily pourable. When heated to a temperature of about 148.degree. to 177.degree. C., the plastisol is transformed to a homogeneous melt which, upon cooling to below 50.degree. C., results in a tough flexible product. The PVC resins made by emulsion polymerization are hard spheres of particle size between about 0.05 and 20 microns, such as between 1 and 20 microns. They do not have the ability to absorb plasticizers. Therefore, a mixture containing, for exmaple, 30% plasticizer and 70 PVC resin, produces a flowable liquid, known a plastisol.

General purpose PVC resins are made by mass and suspensin polymerization process, and comprise the largest amount of PVC resins produced, such as at least 80% of all PVC resins, and are used chiefly to make so-called 100% vinyl products by a variety of molding and extrusion techniques. Resins intended for flexible applications should have good uptake of plasticizer in a dry blending operation and contain more than 25% of a plasticizer system. PVC compounds that contain less than 25% plasticizers are referred to as semirigid compounds: The PVC resins manufactured by suspension and bulk polymerization are 50 to 200, such as 100 to 150 microns in diameter, and are like sponges They are capable of absorbing large amounts of plasticizers, so that even 50% plasticizer, 50% PVC resin composition would result in a non-flowing, solid material.

It is an object of the present invention to provide an article of manufacture which offers enhanced delivery capability of pharmacologically-active agents over prior commercial devices (transdermal devices, articles used to orally administer pharmacologically-active agents and subdermal implants used to administer subdermally pharmacologically-active agents) by providing an article capable of efficaciously administering pharmacologically-active agents such as isosorbide dinitrate, nicotine, indomethacin, clonidine, glyceryl trinitrate, guanfacine, and prostaglandin directly from a plastisol resin layer in which the pharmacologically-active agent is incorporated in relatively high concentrations, e.g , from 0.5 up to 35%.

This invention also enables the administration of a pharmacologically-active agent, such as isosorbide dimitrate, nicotine, indomethacin, clonidine, glyceryl trinitrate, guanfacine, and prostaglandin to be achieved through an article of manufacture, e.g., a transdermal delivery device requiring contact with a relatively smaller area of a patient's tissue, such as the epidermis in the case of a transdermal delivery device.

Thus, this invention is directed to an article of manufacture incorporating a polyvinyl chloride resin plastisol monolayer for administration of pharmacologically-active agents transdermally, orally or by means of subdermal implant to a patient requiring treatment for a condition such as, for example, angina pectoris (in the case of the use of such materials as nitroglycerin). In particular, it has been found that pharmacologically-active agents such as isosorbide dinitrate, nicontine, indomethacin, clonidine, glyceryl trinitrate, guanfacine and prostaglandin can be homogeneously dispersed in high concentrations in a plastisol of an emulsion polymerized polyvinyl chloride resin and plasticizer; the composition is fused into a solid layer and the layer is applied onto the tissue of a patient (either transdermally, orally or subdermally) whereby the pharmacologically-active agent is absorbed either (i) through the patient's skin or (ii) through the patient's internal membranes or (iii) directly ionto the circulation system.

A preferred embodiment comprises a multilayer adhesive bandage device incorporating a plastisol monolayer containing homogeneously dispoersed pharmacologically-active agents, e.g., isosorbide dinitrate, nicotine, indomethacin, clonidine, glyceryl trinitrate, guanfacine and prostaglandin .

FIG. 1 is a cross-sectional view of a preferred pharmacologically-active agent delivery device in accordance with this invention.

FIG. 2 is a plan view of a strip of material in accordance with this invention viewed from the surface which is applied to the patient's skin.

FIG. 3 is a plan view of material in accordance with this invention viewed from the surface away from the surface which is applied to the patient's skin.

FIG. 4 is an enlarged sectional schematic view of a specific embodiment of the invention; a transdermal device for controlled release of a pharmacologically-active agent from a plastisol monolayer through a membrane transdermally.

FIG. 5 is an enlarged sectional schematic view of another embodiment of the invention where there is no membrane separating the plastisol monolayer from the epidermis and whereby pharmacologically-active agent is transported from the plastisol transdermally into the patient.

FIG. 6 is a perspective view of a roll of material in accordance with this invention.

FIG. 7 is a graph of tensile strength (PSI) versus percent resin containing either of isosorbide dinitrate, nicotine, indomethacin, clonidine, glyceryl trinitrate or guanfacine, specifically as described herein in the description of Examples VIII-XIII, infra.

FIG. 8 is graph showing release rate of pharmacologically-active agent (in micrograms per square centimeter per hour) versus percent resin, individually, for isosorbide dinitrate, nicotine, indomethacin, clonidine, glyceryl trinitrate or guanfacine specifically in relationship to Examples XIV-XIX, infra.

FIG. 9 is a graph of plasma concentration (picograms per milliliter) versus time detected in a human subject during the clinical study concerning the composition of matter consisting of polyvinyl chloride resin, dioctyl adipate plasticizer and prostaglandin as specifically set forth in Example XX, infra.

FIG. 10 is a graph showing the effective decrease in diastolic blood pressure of the human subject observed during the period of patch application as specifically set forth in Example XX.

FIG. 11 is a graph of delivery of nitroglycerine versus time resulting from the use of the formulation of Example XXI.

FIG. 12 is the infrared spectrum of ADMEX.RTM. 760 as used in Examples II-XIX.

The invention is described herein with respect to preferred embodiments including transdermal devices containing various pharmacologically-active agents including, but not limited to, indomethacin having the structure: ##STR1## guanfacine having the structure: ##STR2## clonidine having the structure: ##STR3## nicotine having the structure: ##STR4## isosorbide dinitrate having the structure: ##STR5## glyceryl trinitrate and prostaglandin (e.g., methyl (.+-.) -[11a, 5z and 5E), 13E, 16R (and 16S)]-16-ethenyl-11,16 dihydroxy-9-oxoprosta-5, 13-dien-1-oate. It will be understood that other embodiments may be employed within the spirit and scope of this invention.

The articles of our invention are useful for transdermal, oral and subdermal administration of pharmacologically-active substances and comprise a solid vinyl plastisol layer (consisting essentially of polyvinyl chloride and a plasticizer) for contacting a patient's skin or other membrane. The vinyl plastisol layer contains from about 20 up to about 70% by weight of a polyvinyl chloride resin which consists essentially of a vinyl chloride polymer containing, predominantly or completely repeating vinyl chloride monomeric units and in an amount of less than about 10% other repeating vinyl units, e.g., repeating vinyl acetate units; from about 20% up to about 70% by weight of the composition of one or more plasticizers; from about 0.5 up to about 35% by weight of the total composition of a pharmacologically-active substance, such as isosorbide dinitrate, nicotine, indomethacin, clonidine, glyceryl trinitrate, guanfacine or prostaglandin and optionally other excipients, such as materials which will accelerate transdermal penetration as exemplified hereinafter. As one example of the use of a pharmacologically-active substance, nitroglycerin can be present in an amount of about 20-35%.

It has now been found that the release rate of an active agent, which is uniformly dispersed in the vinyl plastisol layer, is critically dependent upon the proportion of the PVC resin in the composition; and the release follows a bell shaped curve (FIG. 8), the maximum occurring in the range of 30 to 50% PVC content. This is an unexpected finding, which has not hitherto been known. Such a release behavior permits tailoring of release rates of an agent from the matrix.

The reservoir layers of this invention are relatively weak and less than 1500 psi, (FIG. 7), highly flexible and soft materials. In contrast, the flexible vinyl films of commerce are considerably stronger materials exhibiting tensile strengths of the order of 1,500 to 5,000 psi. The polyvinyl chloride resin content of the commercially useful and available flexible vinyl films ranges from 50 to 75%. Such materials do not have adequate drug permeating characteristics to serve as suitable drug delivery reservoirs.

Referring to FIG. 1, the device 1 includes a solid plastisol monolayer 2 which is composed of or comprises resin, plasticizer and a pharmacologically-active agent as set forth supra.

A formulation for layer 2 may comprise from about .[.2.]. 20 up to about 70% by weight of the vinyl resin, from about 20 up to about 70% by weight of plasticizer composition, from about 0.5 up to about 35% by weight of pharmacologically-active agent and the remainder being other excipients, such as materials which will enhance skin penetration. We have found that the substance 1-dodecylhexahydro-2H-azepin-2-one (also known as AZONE.RTM. having the structure: ##STR6## acts as both a plasticizer and as an agent which enhances transdermal penetration of pharmacologically-active agents such as isosorbide dinitrate, indomethacin and the like as set forth supra. By the same token, N,N-diethyltoluamide having the structure: ##STR7## acts in the same manner as AZONE.RTM..

Thus, for example, for a device suitable in the treatment of angina pectoris, a specific formulation for layer 2 comprises about 54% polyvinyl chloride (PVC) resin, about 36% dioctyl phthalate (DOP) plasticizer and 10% nitroglycerin. To prepare layer 2, the PVC and DOP are first blended. Due to the explosive character of the drug, dispersion of the nitroglycerin into the resulting PVC/plasticizers plastisol is then carried out under controlled conditions.

The articles of the present invention including the transdermal devices as well as subdermal implants and orally ingested articles of the present invention comprise a polyvinyl chloride plastisol layer in a fused state and a pharmacologically-active agent uniformly dispersed in the fused layer which may be referred to as a reservoir for the pharmacologically-active agent. The polyvinyl chloride reservoir in the reset invention is prepared from polyvinyl chloride resin and a primary plasticizer for the resin.

The polyvinyl chloride resin employed in the practice of the present invention is that which is specifically used in preparing PVC plastisols, namely, PVC resins which are made by the well known emulsion polymerization process, which are hard spheres of particle size between 0.05 and 20 microns, such as between 1 and 20 microns, for example, between 1 and 5 microns, or between 0.05 and 1 micron, and which do not have the ability to absorb plasticizers to any great extent. Instead, the plasticizer wets the resin particles at room temperature and only then very slowly penetrates and solvates the resin. These PVC resins when mixed with plasticizers, such as a mixture of 30% primary plasticizer, 70% PVC resin, give a flowable liquid known as plastisol which can then be fused at, for example, approximately 250.degree. F. for approximately 30 seconds to provide a solid polymer layers. The PVC resin employed in the present invention is in contrast to the general purpose PVC resins which are produced by suspension or bulk polymerization and which are used in calendering and extrusion processes, which are 50 to 200 microns, such as 100 to 150 microns in diameter, and are like sponges. Thus, the genial purpose resins are capable of absorbing large amounts of plasticizers so that even a 50% DOP and 50% PVC resin would result in a non-flowing solid material. The molecular weight of the PVC resins employed in the present invention preferably is a weight average molecular weight between 80,000 and 250,000, such as a weight average molecular weight of 123,000. A suitable polyvinyl chloride resin is one sold by Occidental Chemical Co. under the designation FPC 6338 containing about 96% vinyl chloride monomer units of about 4% vinyl acetate monomer units. Thus, the polyvinyl chloride resin can be a copolymer containing preferably at least 90% by weight vinyl chloride monomer units, such as a copolymer based on vinyl chloride and vinyl acetate.

The polyvinyl chloride resin generally is present in the layer in an amount of 10 to 75 weight percent, preferably 20 to 70 weight percent, based on the total weight of the vinyl plastisol composition.

The primary plasticizer which is employed in the present invention can be dioctylphthalate (DOP), benzylbutylphthalate, tri-2-ethylhexylmalaete, dioctyl adipate, epoxidized soybean oil, polymeric adipate plasticizers, which are polymers of adipic acid with a monomer, such as propylene plycol, and for example can be obtained under the designation Drapex 334F from Witco Chemical Corp., or any other known primary plasticizer for PVC which is biologically acceptable.

The other examples of polyester adipates, glutarates and sebacates are:

polyester adipate (P)P-644;

polyester glutarate (P)P-530;

polyester glutarate (P)P540;

polyester glutarate (P)P-550;

polyester glutarate (P)P-7035;

polyester glutarate (P)P-7035M;

polyester glutarate (P)P-7046;

polyester glutarate (P)P-7092; and

polyester sebacate (P)P-1070

manufactured by the C. P. Hall Co., 7300 S. Central Avenue, Chicago, Ill. 60638. Other preferred plasticizers are those which are known as "phthalate" plasticizers, for example, ADMEX.RTM. 760 which is a high molecular weight (MW=8000) phthalte plasticizer manufactured by the Sherex Division of Nuodex Inc. In general, polyester plasticizers which are polyesters of (i) 1,4-terephthalic acid and/or 1,2-phthalic acid with (ii) ethylene glycol or 1,3-propylene glycol having molecular weights in the range of 4000-10,000 are preferred.

Another preferred plasticizer which also acts as a skin penetrating enhancer for pharmacologically-active drugs which are intended for transdermal delivery from devices such as those set forth in FIGS. 1, 5 and 6 is the compound having the structure: ##STR8## known as AZONE.RTM. marketed by the Nelson Research and Development Co. The composition comprising PVC and the compound having the structure: ##STR9## is a novel composition of matter.

Mixtures of known plasticizers can be used. The term "primary plasticizer" as used herein refers to a plasticizer which can be used alone to effect plasticization and is highly compatible with PVC at high concentrations, such as, for example, 150 parts per hundred. Primary plasticizers are contrasted with "secondary plasticizers" which, because of limited compatibility with PVC, cannot be used alone. See, Kirk-Othmer Encyclopedia of Chemical Technology, Volume 23, 3rd Edition, especially pages 913 and 914 for a discussion of primary and secondary plasticizers, which is incorporated by reference herein.

The primary plasticizer generally is present in an amount of 20 to 85 weight percent, preferably 20 to 70% based on the total weight of the vinyl plastisol layer.

The PVC plastisol may optionally contain other additives or "excipients" useful in the practice of this invention, for example, material which enhance skin penetrated of the pharmacologically-active substances (e.g., 1,6-hexanediol and n-decyloleate) and thickeners, e.g., silica (preferably "fumed" silica, for example, AEROSIL.RTM. in an amount of from 1-6% of the layer).

With reference to FIG. 1, the blended plastisol containing for example, PVC, DOP and nitroglycerin is then coated at a rate of about 36 ounces/yd.sup.2 on a backing, and then fused into solid plastisol layer 2. The backing may be a single layer of drug impermeable plastic or other material, but is preferably composed of two layers 3 and 4. Layer 3 may be MYLAR.RTM. (polyester produced from ethylene glycol and phthalic anhydride) about 0.5 mils thick, and layer 4 may be PVC, about 4 mils thick. The backing 3,4 substantially blocks loss of drug from the plastisol layer 2other than in the direction of the surface which, in use, will contact the patient's skin.

The blended plastisol which is coated on the backing can be fused into a homogeneous solid by heating it for a short period, such as 15 to 30 seconds, at a temperature of, for example, 250.degree. to 280.degree. F. The use of a plastisol to form solid layer 2 enables to be formed by using a low temperature for a short period of time and provides conditions which do not affect the stability of the pharmacologically-active agents.

A strip of solid plastisol layer 2 and backing 3,4 is then tonded to a pressure-sensitive adhesive layer 5 which in turn is provided with a non-adhesive backing 6 such as one made of plastic, moisture-proof fabric, aluminum foil, etc.

When not in use, the entire surface intended for skin contact is preferably covered with a release paper 7 or the like which is removed to expose surfaces of the adhesive layer 5 and drug containing plastisol layer 2 for application to the patient's skin.

FIG. 2 shows a plan view of a strip of material 20 during the stage of manufacture at which a strip of the plastisol 2 (backing 3,4 not shown) has been applied to the adhesive tape (backing 6 not shown). For the preferred device for the controlled administration of pharmacologically-active agent e.g., indomethacin, isosorbide dinitrate, nicotine, clonidine, glyceryl trinitrate, guanfacine or prostaglandin, a plastisol strip preferably about one inch (1") in width is applied on a two and one-half inch (21/2") wide pressure-sensitive adhesive strip.

FIG. 3 shows a plan view of a strip of the material 30 in accordance with this invention; spaced lines 31 may be embossed or printed on the surface away from skin contact so that the patient may conveniently measure out and cut off the proper amount of tape device to provide the prescribed daily dosage. For a device for administering the pharmacologically-active agent, e.g., nitroglycerin, for example a segment 1" long cut from the longer tape (resulting in an approximately one square inch (1 sq. in.) of active surface against the the patient's skin) will provide a dosage of about 17 mg/24 hours; this is to be an enhanced rate of delivery compared with commercially available transdermal drug delivery devices and also will provide the patient with a bandage device having a surface area much smaller than found in previously available devices.

Referring to FIG. 4, the components of embodiment 33 are backing layer 34, a reservoir layer 35 that contains supplies of percutaneous absorption enhancer and pharmacologically-active substance, such as indomethacin, a diffusion membrane layer 36 and a peripheral ring 37 of contact adhesive. The diffusion membrane layer may be composed of a polymer, such as copolymer of ethylene and methyl acrylate with the methyl acrylate being in the range of 2-90% by weight of the polymer, or blends of such copolymer with low density polyethylene, high density polyethylene or linear low density polyethylene. The contact adhesive component of embodiment 33 is in the form of a peripheral ring. Optionally, backing layer 34 may also be a semi-permeable membrane. Neither the pharmacologically-active agent, e.g., isosorbide dinitrate nor enhancer passes through ring 37 and it therefore need not be permeable to those compositions. Optionally, the contact adhesive may be attached directly to the membrane 36, in which case the adhesive is selected so that it is permeable to the active agent. Secondly, the basil surface from which the pharmacologically-active substance and enhancer (e.g., AZONE.RTM. is transferred to the skin is defined by diffusion membrane layer 36. The backing layer is not flat but instead forms a pocket or cavity in which the reservoir layer is held. The outer edge of the backing layer is sealed to the peripheral ring of the contact adhesive as more specifically set forth in U.S. Pat No. 4,379,454 issued on Apr. 12, 1983, the disclosure of which is incorporated herein by reference. Similarly, an article within the contemplation of our invention need not have a matrix as illustrated in FIG. 5 wherein the backing 61 totally surrounds the PVC-plastisol-plasticizer matrix 62 and is firmly in place as with an adhesive on the skin 63.

As shown in FIG. 6, the device of the invention may conveniently be provided in the form of a tape roll 50 from which daily dosage requirements may be clipped by the patient.

The device is capable of application to humans or other animals capable of usefully absorbing drugs through the skin.

Other embodiments of our invention are those useful in, for example, U.S. Pat. Nos. 4,573,996 and 4,573,995 issued on Mar. 4, 1986, the specifications for which are incorporated by reference herein.

A plastisol was formed by mixing 54% of a polyvinyl chloride resin sold under the designation FPC 6338 by Occidental Chemical Corp. and having a particle size between 1 and 5 microns, 36% DPO, and 10% nitroglycerin. The product was coated onto 1 mil polyester (MYLAR) film and cured at 280.degree. F. The final product consisted of 8.8% nitroglycerin, 31.8% DOP, 47.8% FPC 6338, 11.6% polyester. This product can be used for delivery of nitroglycerin percutaneously.

Fused plastisol drug reservoirs having variable PVC: plasticizer ratios were prepared by heating cast films of the drug containing plastisols at 290.degree. F. for 60 seconds. The drugs used were isosorbide dinitrate (ISDN) and nicotine. AZONE.RTM. having the structure: ##STR10## (registered trademark of the Nelson Research and Development Co.) and ADMEX.RTM. 760 (which is a high molecular weight (MW=8000) phthalate plasticizer manufactured by the Sherex Division of Nuodex Inc.) were used as primary plasticizers in the case of the ISDN and the nicotine reservoirs, respectively. The films, thus prepared, were optically transparent. FIG. 12 is the infrared spectrum ADMEX.RTM. of 760.

The stress-strain properties of the films were determined employing standard procedures using Instron Universal Testing Instrument. The ability of the reservoir to release the drug evaluated by measuring the dissololution rate of the drug in fluid medium (receptor phase) when a known surface area of drug reservoir film was exposed to an excess of the receptor at 31.degree. C. The dissolution rate studies were conducted a Franz diffusion cell. The receptor phase for the nicotine study was pH 4.0 citric acid buffer solution (an aqueous solution containing 1.2% citric acid and 1.1% disodium hydrogen phosphate), and that for the ISDN study was an aqueous solution containing 20% polyethylene glycol 400. The dissolution rate of the drug was calculated from the change in concentration of the drug in the receptor phase at different time intervals. The nicotine and ISDN concentrations were determined by ultraviolet spectroscopy and high pressure liquid chromatographic procedures, respectively.

In the following formulations .[.(A-F.]. (A-E in each of Examples II-VII), the following terms having the following meanings as now given:

In the following examples, the following terms have meanings as given herein:

FIG. 7 shows tensile versus percent resin for each of the above formulations. The curve indicated by reference numeral 70 is the curve for clonidine. The curve indicated by reference numeral 71 is the curve for guanfacine. The curve indicated by reference numeral 72 is the curve for .[.indocin.]. indomethacin. The curve indicated by reference numeral 73 is the curve for nicotine. The curve indicated by reference numeral 74 is the curve for isosorbide dinitrate. The curve indicated by reference numeral 75 is the curve for glyceryl trinitrate.

In the following examples, the following terms have meanins as set forth below:

FIG. 8 is a graph showing release rate in micrograms per square centimeter per hour versus percent resin. The curve indicated by reference numeral 80 is the curve for nicotine. The curve indicated by reference numeral 81 is the curve for clonidine. The curve indicated by reference numeral 82 is the curve for guanfacine. The curve indicated by reference numeral 83 is the curve for isosorbide dinitrate. The curve indicated by reference numeral 84 is the curve for indomethacin. The curve indicated by reference numeral 85 is the curve for glyceryl trinitrate.

I Drug: Prostaglandin (American Cyanamid Co.) Methyl (.+-.)-[11.alpha., 5z (and 5E), 13E, 16R (and 16S)]ethenyl-11,16-dihydroxy-9-oxoprosta-5, 13-dien-11-oate (an analog of Prostaglandin E.sub.2).

II. Pharmacological Activity: Antihypertensive

III. Patch Formula:

IV. Results:

A. The Drug Concentration up to 500 pg/ml was detected in a human subject. (FIG. 9).

B. Effective decrease in diastolic blood pressure of the human subject was observed during the period of patch application (FIG. 10).

The curve indicated by reference numeral 90 shows plasma concentration in picograms per ml versus time in hours. The curve indicated in FIG. 10 by reference numeral 101 shows mean decrease in sitting diastolic blood pressure following administration of the subject patch formula to normal subjects in a cross over study (sample size=15). The units of pressure are mmHg and the units of time are in hours.

Drug: Nitroglycerin (Glyceryl trinitrate)

Pharmacological Activity: Vasodilator

Patch Formulation:

Results

The patch delivered adequate nitroglycerin through skin of human subjects to provide a concentration of 0.1 to 0.2 ng/ml in the blood plasma for a period of 3 days as set forth in FIG. 11. The graph indicated by reference numeral 111 is a graph of delivery of glyceryl trinitrate in nanograms/ml versus time (in hours).

In Vivo Transdermal Delivery of Isosorbide Dinitrate (ISDN)-from Drug Reservoir

I. Patch Formula:

II. Pharmacological Activity: Vasodilator

III. Test Protocol:

Formulations containing 7.5% ISDN, and 0, and 32% AZONE.RTM. respectively were tested in vivo on monkeys. Each formulation was tested on two monkeys for six consecutive days. The patches were firmly placed on the shaved upper innerarm each morning and were left in place for eight hours. For each test condition blood samples of approximately 3-4 ml were withdrawn from an indwelling catheter inserted into the saphenous vein. Blood samples were drawn at 0 (prior to patch application), 4 and 8 hours after dosing. The eight-hour samples was drawn before the patches were removed. The plasma component was immediately separated from the blood by centrifugation at 1200 rpm for 5 minutes, and frozen at -20.degree. C. The samples were then extracted to determine concentrations of ISDN and its metabolites Isosorbide 5-mononitrate (5-ISMN) and Isosorbide 2-Mononitrate (2-ISMN).

Upon removal of the patches, the site of application was washed with dilute alcohol and inspected visually. Any changes in the condition of the skin (such as erythema or edema) was scored according to the Draze Scoring System. This inspection was repeated 30 minutes and again before next patch application.

IV. Results:

The mean plasma ISDN and metabolite results for the patches are shown in Table I. An increase of 300% to 400% in plasma ISDN concentration was observed for patches containing 32% AZONE.RTM..

A maximum of 43.8% ng/ml of plasma ISDN was obtained from 2patches with a total surface area of 12.5 cm.sup.2. However, the data did not suggest that there was a linear increase of plasma level with surface area of patch. In general, doubling the patch surface area more than doubled the plasma level, for ISDN as well as the metabolites.