CA1276111C - Transdermal verapamil delivery device - Google Patents
Transdermal verapamil delivery deviceInfo
- Publication number
- CA1276111C CA1276111C CA000512950A CA512950A CA1276111C CA 1276111 C CA1276111 C CA 1276111C CA 000512950 A CA000512950 A CA 000512950A CA 512950 A CA512950 A CA 512950A CA 1276111 C CA1276111 C CA 1276111C
- Authority
- CA
- Canada
- Prior art keywords
- delivery device
- drug delivery
- enhancing agent
- transdermal drug
- recited
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Fee Related
Links
Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K9/00—Medicinal preparations characterised by special physical form
- A61K9/70—Web, sheet or filament bases ; Films; Fibres of the matrix type containing drug
- A61K9/7023—Transdermal patches and similar drug-containing composite devices, e.g. cataplasms
- A61K9/703—Transdermal patches and similar drug-containing composite devices, e.g. cataplasms characterised by shape or structure; Details concerning release liner or backing; Refillable patches; User-activated patches
- A61K9/7038—Transdermal patches of the drug-in-adhesive type, i.e. comprising drug in the skin-adhesive layer
- A61K9/7046—Transdermal patches of the drug-in-adhesive type, i.e. comprising drug in the skin-adhesive layer the adhesive comprising macromolecular compounds
- A61K9/7069—Transdermal patches of the drug-in-adhesive type, i.e. comprising drug in the skin-adhesive layer the adhesive comprising macromolecular compounds obtained otherwise than by reactions only involving carbon to carbon unsaturated bonds, e.g. polysiloxane, polyesters, polyurethane, polyethylene oxide
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K31/00—Medicinal preparations containing organic active ingredients
- A61K31/275—Nitriles; Isonitriles
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K9/00—Medicinal preparations characterised by special physical form
- A61K9/70—Web, sheet or filament bases ; Films; Fibres of the matrix type containing drug
- A61K9/7023—Transdermal patches and similar drug-containing composite devices, e.g. cataplasms
- A61K9/703—Transdermal patches and similar drug-containing composite devices, e.g. cataplasms characterised by shape or structure; Details concerning release liner or backing; Refillable patches; User-activated patches
- A61K9/7084—Transdermal patches having a drug layer or reservoir, and one or more separate drug-free skin-adhesive layers, e.g. between drug reservoir and skin, or surrounding the drug reservoir; Liquid-filled reservoir patches
Abstract
ABSTRACT OF THE DISCLOSURE
A transdermal drug delivery device for administering 5-[(3,4-dimethoxyphenethyl) methylamino]-2-(3,4-dimethoxyphenyl)-2-isopropylvaleronitrile com-prising a permeable matrix of silicone elastomer or other bioacceptable lipophilic polymer material having an effective cardiovascular affecting amount of active drug and an effective drug release promoting amount of a transport enhancing agent dispersed therein. The back of the matrix is covered with an occlusive backing and the face of the matrix is covered with a biocompatible adhesive such as a silicone adhesive also having a transport enhancing agent dispersed therein.
A supply of skin permeation enhancing agent may be provided adjacent the adhesive layer such that the skin of a patient to whom the device is applied is pretreated with permeation enhancing agent.
Particularly preferred skin permeation and transport enhancing agents include N,N-diethyl-m-toluamide, isopropyl myristate and similar compounds.
A transdermal drug delivery device for administering 5-[(3,4-dimethoxyphenethyl) methylamino]-2-(3,4-dimethoxyphenyl)-2-isopropylvaleronitrile com-prising a permeable matrix of silicone elastomer or other bioacceptable lipophilic polymer material having an effective cardiovascular affecting amount of active drug and an effective drug release promoting amount of a transport enhancing agent dispersed therein. The back of the matrix is covered with an occlusive backing and the face of the matrix is covered with a biocompatible adhesive such as a silicone adhesive also having a transport enhancing agent dispersed therein.
A supply of skin permeation enhancing agent may be provided adjacent the adhesive layer such that the skin of a patient to whom the device is applied is pretreated with permeation enhancing agent.
Particularly preferred skin permeation and transport enhancing agents include N,N-diethyl-m-toluamide, isopropyl myristate and similar compounds.
Description
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TRANSDERMAL VERAPAMIL DELIVERY DEVICE
-Background of the Invention Thi~ invention relates to a devioe for transdermal admini~tration of an active pharmaceutical at a ~ustained 9 substantially uniform rate of delivery over an extended period of time. More particularly, the invention relates to a device particularly adapted ~or tran~dermal admini~tration of verapamil.
Treatment of patient~ with pharmaceutically active substance~ i~ commonly carried out by periodically adminstering defined doses of the pharmaceutical to the patient, e.g. either orally or by injection. Such techniques provide a maximum dosage of the pharmaceutical ~ollowing each administration which then eontinually decline~ until the next do~e is admini~tered~ In order to as3ure that an effective dosage of pharmaceutical is present in the body at all times, peak dosages which are much higher than the effective level are needed. Thiq unde~irably increase~
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the amount of pharmaceutical which is consumed and concomitantly increa~es the danger of unde~ired side effects. Moreover, even though qubstantial excess dosages are adminstered, there is always a danger that ~ 5 the concentration of the pharmaceutical may drop below the effective level if adminstration of a ~ubsequent dose 9 delayed or omitted. Further, there is a possibility, particularly with oral administration of pharmaceuticals, that a portion of the pharmaceutically active substance may be metabolized before r,eaching its intended locus of activity. This further increases the excess of pharmaceutical which must be administered in order to assure that an effective concentration i~
maintained.
Techniques also exist for Yustained, low level administration of pharmaceuticals. The technique most commonly utilized is intravenous infusion. This technique, while effective at providing sustained low levels of pharmaceutical, is cumbersome and al~o ~0 requires close supervision by trained medical personnel. Con~equently, intravenous infusion of pharmaceuticals typically requires hospitalizat~on of the patient with attendant expense and inconvenience.
Techniques have also been developed for administering pharmaceuticals at sustained low levels by absorption through the skin. Transdermal delivery devices are now commerically available for nitroglycerin, scopolamine and other pharmaceuticals.
Such devices typically comprise either a pharmaceutical-containing reservoir enclosed by a membrane through which the pharmaceutical can diffuse at a controlled rate or a dispersion of pharmaceutical in a polymer matrix from which the pharmaceutical can diffuse at a controlled rate. The devices are attached either adhesively or otherwise to the skin of a '' .:; ` ' : ' , ' - . . : . . .
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patient, and the pharmaceutical is permitted to diffu3e from the device and permeate through the outer sublayer~ of skin until it iq absorbed into the blood stream in the fine capillary network of the dermi~.
Once absorbed into the blood stream, the pharmaceutical is then oarried throughout the entire body syste~ of the patient.
While such transdermal delivery devices have worked well for some pharmaceutical~, notably nitroglycerine, conventional tran~dermal delivery devices have not proved suitable for other important drugs. Reservoir-type delivery devices are subject to the risk of undersirable dose damping if the rate controlling membrane is inadvertently damaged. The rate of release of some pharmaceutical~ from conventional devices has proved to be too slow to provide an effective dosage of pharmaceutical unless the size of the transdermal delivery patch was excessively large. In some instances it has been difficult to maintain effective contact between the transdermal drug delivery device and the skin of the patient. Attempt~ to solve the problem of maintaining contact by providing an adhesive over the face of the delivery device so that it po~itively adheres to the patient'~ skin have not been fully successful. In some instances, due to the nature of the drug delivery matrix, available adhe~ives have not adhered well to the tranqdermal drug delivery device. Where ~atisfactory adhesion between the drug delivery device and the matrix ha~ been obtained, it has been found that the adhesive act~ aq a barrier and retards transfer o~ the active qub~tance from the drug delivery device to the skin. For some pharmaceutical~, the rate of skin permeation and abqorption is o low that it has not been possible to provide an effective do~age within - . .. .
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a reasonably sized area o~ 3kin.
One drug for which a transdermal delivery device would be desirable i~ 5-[(3,4-dimethoxy-phenethyl) methylamino] 2-(314-dimethoxyphenyl)-2-isopropylvaleronitrile, also known as verapamil. Thi~substance is a well established coronary vasodialator and antiarrythmic agent. A self-supporting polymeric diffusion matrix for su~tained transdermal delivery of verapamil has been propo3ed by Reith et al. (PCT
application No. W083/00091), but this sy~tem is subject to many of the disadvantages discussed above.
Summary of the Invention Accordingly, it iR the object of the present invention to provide a new drug delivery device for sustained uniform admini~tration of a pharmaceutical by the transdermal route.
Another object of the present invention i~ to provide a transdermal drug delivery device which enables sustained maintenance of an effective dosage level using a lesser amount of active ingredient than required for periodic administration either orally or by injection.
A further object of the present invention is to provide a transdermal drug delivery device which is not subject to the danger of dose dampingO
It is also an object of the present invention to provide a transdermal drug delivery device from which the active pharmaceutical is released at an enhanced rate.
A ~till further object of the pre3ent invention is to provide a transdermal drug delivery device in which effective contact between the device and the skin of a patient can be continuously maintained.
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~76 Yet another object oP the present invention is to provide an adhesively attached transdermal drug delivery device in which the adhe~ive layer perrnits a high rate of transfer of active pharmaceutical from the device to the skin of a patient.
Additionally, it is an object of the present inventîon to provide a transdermal drug delivery device which facilitates permeation of the active pharmaceutical through the!~kin of a patient.
It is also an object of the presen,t invention to provide a transdermal drug delivery device which can administer an effective dosage of pharmaceutical while at the same time being conveniently small in size.
These and other objects of the invention are achieved by providing a transdermal drug delivery device comprising a permeable bioacceptable lipophilic polymer matrix having an effective cardiovascular affecting amount of 5-[(3,4-dimethoxyphenethyl) methyl~
amino]-2-(3,~-dimethoxyphenyl)-2-isopropylvaleronitrile and an effectiYe release promoting amount of a transport enhancing agent dispersed therein.
In another aspect of the invention, the objects of thè invention are achieved by providing a transdermal drug delivery device comprising a permeable, polymer matrix having an effective cardiovascular affecting amount of 5-[(3,4-dimethoxyphenethyl) methyl-amino]-2-(3,4-dimethoxyphenyl~-2-isopropylvaleronitrile and an effective release promoting amount of a first transport enhancing agent dispersed therein, and a bioacceptable adhesive layer covering one face of said polymer matrix, said adhesive having an effective transport promoting amount of a second transport enhancing agent dispersed therein.
According to a still further aspect of the present invention, the objects of the invention are - ., : . . -: .. . .
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achieved by providing a transdermal drug delivery device compri~ing a permeable polymer matrix having an effective cardiovascular affecting amount of 5-[(3,4-dimethoxyphenethyl) methylamino]-2-(3,4-dimethoxy-phenyl)-2-isopropylvaleronitrile and an effective release promotlng amount of a transpork enhancing agent dispersed therein, ~aid polymer matrix having one surface di~posable adjacent the skin of a patient, and a supply o~ skin permeation enhancing agent adjacent said one`polymer matrix surface such that when said one surface is disposed adjacent (e.g. in intimate contact with) a patient's skin, the skin is then treated with said skin permeation enhancing agent.
In a particularly preferred embodiment) the transdermal drug delivery device of the invention comprises a matrix of bioacceptable cross-linked ~ilicone polymer having an effective cardiovascular affecting amount of 5-~(3,4-dimethoxyphenethyl) methyl-amino3-2-(3,4-dimethoxyphenyl)-2-i~opropylvaleronitrile and an effective release promoting amount of a first drug transport enhancing agent such as isopropyl myristate or N,N-diethyl-m-toluamide dispersed therein, ~aid matrix having first and second opposed faces; a layer of bioacceptable silicone adhesive on said first face o~ said matrix, said adhesive having an effectiYe drug transport promoting amount of a second transport enhancing agent dispersed therein, and an occlusive backing covering ~aid second face of ~aid matrix.
In a further preferred embodiment of the transdermal drug delivery device of the invention, an absorbent material impregnated with a 3kin permeation enhancing agent is removably positioned adjacent the adhe~ive ~urface of the drug delivery device ~uch that the impregnated absorbent material can be peeled away prior to use and when peeled away will leave the . ~ , ~ - , : ... . . . . : :
- . ~ . - - .. , _ 7 _ adhesive surface moistened with skin permeation enhancing agent such that when the transdermal drug delivery device i9 applied to the skin of a patient, the skin surface will be moistened with the skin permeation enhancing agent.
Brief Deqcription of the Drawin~s The invention will be described in further detail with reference to the accompanying drawings wherein: , Figure 1 ~s a schematic representation of matrix-type transdermal drug delivery device with a skin permeation enhancing agent reservoir removably disposed adjacent the adhesive layer, and Figure 2 is a schematic repre~entation of a lS microreservoir-type transdermal drug delivery device.
Detailed Description of Preferred Embodiments The polymer matrix in which the active pharmaceutical is dispersed may be formed from any biocompatible polymeric material which exhibits significant lipophilic character. It has been found that release of active drug from the polymer matrix i3 better if the polymeric material of the matrix i~
eqsentially electroneutral with respect to the drug.
That is to say, the polymer matrix must not donate any proton or electron to or receive any proton or electron from the active pharmaceutical, but instead the active pharmaceutical should exi~t essentially in electrically neutral, non-ionic form within the polymer matrix. Use of lipophilic (hydrophobic) polymer materials for the polymeric matrix also facilitate~ application of an adhesive over the surface of the matrix to secure the drug delivery device in continuou~ contact with the skin of a patient. Where hydrophilic polymer matrice~
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are used~ it i~ dif'ficult to obtain ~atisfactory adhesion between the adhesive and the polymer matrix.
Suitable bioacceptable polymers which can be u~ed for preparation of the drug di~per~ing polymer matrix include silicone elastomers with variou~ sub~tituents on the ~ilicon atom~, dialkylsiloxane-ethylene oxide copolymers, dialkylsiloxane-methacrylate copolymers, dialkylsiloxane-polycarbonate copolymers, ethylene-vinyl acetate copolymers (EVA), polyolefins 3uch a~
polyeth~lene or polypropylene, and other polymers with similar lipophilic, electroneutral character. Cros~~
linking silicone rubber materialq such a~ silicone polymers corresponding to the formula:
~ IH3 ~ ~ CH3 t --IH3~ I tC}13 ~m CH3--Si O _ r--P
wherein R i~ alkoxy, alkyl, alkenyl or aryl containing 1 to 7 carbon atom~ and wherein n, m and p are about 100 to 5,000 are particularly preferred a~ polymer matrix material~. Good results have been achieved u~ing matrioies formed o~ cro~s-linked polydimethyl~
siloxanes.
The thickne~ of the polymer matrix may be varied as desired depending inter alia upon the de~ired pharmaceutical dosage and duratior. of treatment.
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Ordinarily suitable matrix thickne~es may range from about 0.005 cm to about 0.5 cm.
An effective drug release promoting amount of a tran~port enhancing agent is de~irably incorporated in the polymer matrix with the active pharmaceutical.
Suitable transport enhancing materials include ~aturated aliphatic acids and derivatives such as myri~tic acid, isopropyl myristate, myristyl alcohol and mono-myristein; unsaturated aliphatic acids and derivativeQ ~uch as oleic acid, propyl oleate, oleyl alcohol and mono-olein; aryl alkyl tertiary amine~
including dialkyl aryl amines ~uch as N 3 N-diethyl-m-toluamide; dialkyl sulfoxides such as dimethyl sulfoxide or decyl methyl sulfoxide; 1-substituted azacycloalkan-2-ones such a3 1-dodecyla~acycloheptan-2-one; dialkyl amide~ Quch as dimethyl or diethylacetoamide and thioglycollates such as calcium thioglycollate. Mixtures of two or more of the foregoing may be u~ed to advantage; for example, mixtures of isopropyl myristate and N,N-diethyl-m-toluamide have been used to good effect.
The transport enhancing agent may be dispersed in the polymer matrix ln amounts ranging from about 2 to about 40 percent by weight. Preferably, the transport enhancing agent will be present in an amount ranging from about 5 to about 3O percent by weight.
Where the polymer matrix i~ disposed in direct contact with the skin of a pati`ent during use, the drug release promoting tran~port agent may also promote skin permeation by the drug.
The active pharmaceutical may be di~persed in the polymeric material prior to cros~linking to form the completed matrix~ Alternatively, a solution or su~pension of the active pharmaceutical in the transport enhancing agent may be disper~ed in the ~ ` '` .
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-- 10 _ polymer matrix prior to cros~linking in which case microre~ervoirs of the drug are formed in the matrix.
Generally, the active drug will be pre~ent in an amount ranging from about 2 to about 50 p~rcent by weight of ~he polymer matrix. Preferably, the amount of active drug will range from about 5 to about 30 weight percent ~ith respect to the polymer matrix. U~e of exces~ively low concentrations of active drug makes it difficult to obtain an acceptably high rate of relea~e of the drug from the polymer matrix and to achieve a ~ubstantially uniform rate of release over an extended period of time. Use of excessively high concentrations of active drug render3 it more di~ficult to control the rate of release of the drug from the matrix.
An occlusive backing material is disposed over one side of the polymer matrix. The backing material should be substantially impermeable to the active drug and any transport enhancer found in the polymer matrix.
Such a backing iq needed to prevent migration of the active ingredient~ from the polymer matrix other than to the skin of a patient to which the matrix is properly attached. Such a backing also facilitates handling of the drug delivery device and inhibitq ~oiling of clothing worn by a patient over the transdermal drug delivery device. Suitable backing materials include metal foil~ such as aluminum foil, polyesters such as polyethylene terephthalate, polyamides such as polycaprolactones, polyolefins such as polyethylene or polypropylene, polyacrylates such as polymethylmethacrylate or acrylamide, polyurethaneq, vinyl polymers and copolymer3 such a~ polyvinyl chloride or polyvinylacetate, polyurethanes, cellophaneq or other similar materials. Multi-layer laminates may also be used. A particularly preferred backing material compriqeq a skin-colored polyester ' ~ - ,' ' ' ' . . ' .
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- ' film/metal foil laminate.
The drug delivery device of the invention may be advantageously Yecured to the skin of a patient by using a bioacceptable pressure-sen~itive adhe~ive of the type used for medical dre~ings. In order to assure continuou3 and reliable contact between the drug-releasing polymer matrix and the patient's ~kin, it is preferred to apply the adhesive layer over at least the entire face of the polymer matrix. Suitable adhe~ive materials include non-toxic and non-irritating hypoallergenic adhesive~ based on polydienes, for example polybutadiene; acrylates, for example copolymers of methylacrylate or methacrylate and methacrylic acid; vinyl resins, for example polyvinyl-acetate, polyvinylalcohol, polyvinylchloride andcopolymers o~ the~e and similar vinyl monomer~; natural gum~, for example guar or acacia; polyurethanes; and other adhe~ive material Silicone rubber adhesives have been found to combine excellent hypoallergenicity, ~0 satisfactory adhesion and good stripability when the patient i~ finished wearing the dressing and are therefore particularly preferred. Good result~ have been achieved u~ing commercially available medical-grade polydimethyl~iloxane adhesive~.
Of course, it is also po~sible tv provide adhe~ive only around the periphery of the drug delivery device of the invention to ~ecure it to the patient or even to omit the adhesive layer entirely and ~ecure the drug delivery device to the patient with any overlying wrap or bandage.
The interpo~ed adhe~ive between the drug-releasing polymer matrix and the ~in of the patient will to ~ome extent impede the tran~fer of the drug from the matrix to the patient. However, it has been found that by incorporating a suitable tran~port - - . : .
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enhancing agent into the adhe~ive, good transfer of the drug from the matrix to the patient may be obtained.
.~ny of the tran~port enhancing agent~ ted above a~
suitable for inclusion in the polymer matrix may also be used in the adhesive. It is not necessary that the same transport enhancing agent be u~ed in the adhe~ive as is used in the polymer matrix. For verapamil, particularly preferred transport enhancing agents include isopropyl myristate, n-decylmethyl~ulfoxide, oleyl alcohol, propyl oleate, 1-dodecylazaGycloheptan-2-one, or N,N-diethyl-m-toluamide. From about 1 to about 30 percent by weight transport enhancing agent may be incorporated into the adhesive. Preferably, the amount of transport enhancing agent will lie in the range from about 5 to about 25 weight percent of the adhesive.
The pH of the adheqive has also been found to affect the tranqfer of the active drug from the drug-releasing matrix to the patient. The pH of the adhesive should be such that the active drug exist~ as ~n electrically neutral species at the lnterfaces between the matrix and adhesive and between the adhesive and the 3kin of the patient. Suitable control of the pH achieves an optimum balance between drug solubility which increases the rate of release of the drug from the polymer matrix and skin hydration which increases the rate of absorption of the drug specie~
through the skin. The optimum pH may vary omewhat with different drugs. For verapamil, the pH should be maintained between about 5 and about 7. It is particularly preferred that the pH of the adhe~ive system in the verapamil transdermal delivery device of the invention be maintained at approximately 6. If desired, a small amount of a buffering agent quch as a disodium hydrogen pho phate/citric acid buffer may be - , ,, , ~
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incorporated into the adhesive and/or polymer matrix to a~sist in maintaining the desired pH value at which the drug molecules exi~t in electrically neutral form.
The adhe~ive layer may be applied to the exposed face of the polymer matrix and the protruding margins of the backing by solvent ca~ting or spraying.
Any suitable solvent may be used such as acetone, methyl ethyl acetate, diethyl ether, etc. Di~per~ion o~ a skin permeation enhancing agent and/or a buffering agent throughout the adhesive may be achieved by dissolving the agent in the adhesive solution prior to applying the adhesive to the polymer matrix. The thickness of the applied adhesive layer may vary.
Suitable thicknesses may range'from about 10 to about 200 microns or more. In order tQ minimize any tendency of the adhesive layer to impede transfer of the pharmaceutical substances from the polymer matrix to a patient's skin, it i~ generally desirable that the adhesive layer be as thin as practicable.
Prior to use of the drug delivery device the adhesive layer may be co~ered by a releasable protective strip. Such a strip may be formed from the same materials used for the backing provided with a conventional release coating, for example, a fluorocarbon or a silicone surface treatment.
It has also been ~ound that ab~orption of the active drug through the skin can be enhanced by pretreating the ~kin with a permeation enhancing agent when the drug delivery device is applied to the skin of the patient. Any of the transport enhancing agents described above may be utilized. Particularly good re~ult~ have been obtained using n-decyl-methylsùlfoxide, 1-dodecylazacycloheptan-~-one, isopropyl myri~tate or N,N-diethyl-m-toluamide.
Pretreatment may be achieved by simply contacting or `. '~ ` ' ' -~ ~ . ' . ' . ' . ' -; . ' , ' ' ` .
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_ 14 _ wiping the skin with the permeation enhancing agent shortly prior to affixing the drug delivery device to the patient's skin. Alternatively, a re~ervoir of tran~port enhancing agent may be included in the drug delivery device such that the skin i~ moi3tened with the transport enhancing agent as the drug delivery device is applied to the patient.
Typically, permeation of the drug through the stratum corneum ti.e. the outermost layer of the epidermi~) is quite slow. If the strakum. corneum is untreated, it may limit the rate at which the active drug can be administered to the patient. Under such circumstances9 it is often desirable that the rate of drug relea~e from the polymer matrix be slightly greater than the rate of permeation through the stratum corneum so that the surface of the skin will be saturated with the active drug in order to maximize the rate of drug absorption.
If, on the other hand, the skin i~
appropriately treated with a ~kin permeation enhancing agent either by pretreatment or by incorporation of ~ufficient permeation enhancing agent into the adhesive layer, it i~ possible to increase the rate of ~kin permeation to a value which equals or exceed~ the desired rate of tran~fer of active drug to the patient.
Under such circum~tance~, skin permeation i~ no longer the rate-limiting ~tep. Instead, the overall rate of tran~fer of the active drug to the patient is controlled by the rate of relea~e of the drug from the drug delivery device. This i~ particularly de~irable in situations where the rate of skin permeation i~
affected by patient difference~ so that uniform do~ing can be achieved independently of the nature or condition of the patient'~ ~kin.
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The ~ize of the drug delivery device should be large enough to permit easy handling but small enough to facilitate convenient application to ~he patient and to avoid an ob~trusive appearance. Typical ~ize~ may range from about 3 square centimeter~ to about 100 square centimeters, preferably from about 5 square centimeters to about 80 ~quare centimeters. It i~
understood, of course, that the size of the delivery device must be interrelated with the rate of relea3e and ab~orption of the active drug in order,to achieve administration of a desired do~age to the patient.
The desired dosage will vary depending on the individual drug as ~ell as on the size and condition of the patient. For verapamil, suitable dosages may lie in the range from about 1 to about 200 milligrams per day. In mo~t case~, the verapamil dosage will lie in the range from-about 1 to about 100 milligrams per day.
The transdermally absorbed verapamil dosage will generally lie in the range from about 2 to about 20 milligrams per day. Do~ages in the range from about 5 to about 10 milligram~ per day are usually preferred.
The actual do~age which ~hould be admini~tered in any given case can be determined by the pre~cribing phy~ician in accordance with good medical practice. If desired, higher rate~ of admini~tration can be achieved by affixing more than ons transdermal drug delivery device to the patient.
Generally speaking, the matrix will contain some exce~ of drug above the dosage amount to be administered to the patient. Ordinarily the polymer matrix will contain from about 1.5 to about 10 time~
the intended dosage amount, preferably from about 2 to about 5 times the dosage amount of drug which is to be tran~dermally absorbed. The drug may also be incorporated in the form of an active derivative or a . . . . .
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~ ~7 prodrug~
Referring now to the drawings, Figure illustrates a first preferred embodiment of the transdermal drug delivery device of the invention generally designated by reference numeral 1. The device comprises a permeable lipophilic cross-linked polymer matrix 3 having an effective release-promoting amount of a transport enhancing agent di~persed throughout the matrix. Also disper~ed throughout the matrix i9 a pharmaceutically effective amount of a transdermally absorbable drug representated schematically by particles 5. The bac~ of the polymer matrix is covered by an occlusive layer, such as plastic ~ilm/metal foil 7, to prevent los~ of material through the back of the drug delivery device and to protect the device from the environmental conditions.
A layer of bioacceptable pressure-sensitive adhesive 9 is applied to the opposite face of the polymer matrix and extends over the margins 11 of the backing. A
suitable amount o~ tranqport enhancing agent is also dispersed in adhesive layer 9. The outer ~ace of the adhesive is covered by a relea~able cover strip 13 provided with a protruding pull tab 15. In the illustrated embodiment, an absorbent layer 17 is affixed to cover layer 13 between the cover layer and adhesive layer 9. For example, the absorbent layer could comprise an open-celled foam layer which has been heat sealed to the inner surface of the cover layer.
Absorbent layer 17 is impregnated with a permeation enhancing agent in order to facilitate pretreatment of the patient's skln.
In use, tab 15 is firmly grasped and pulled away from adhesive layer 9 to ~eparate the cover 13 and absorbent layer 17 from the rest o~ the drug delivery device. As the ab~orbent layer 17 separates from the ., . , . ~ .
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adhesive layer, a ~hin film of permeation enhancing agent remains on the qurface of the adhe~ive layer.
The exposed adhesive surface is then pre~ed again~t the skin of a patient to be treated wikh the drug S contained in the drug delivery device. The adhesive adheres to the skin and thereby holds the entire surface of the drug delivery device in contact with the patient. As the adhesive is applied to the patient's skin, the skin surface is moistened by the thin ~ilm of transport enhancing agent on the surface of the adhesive, thereby facilitating increa~ed premeation of the active drug through the stratum corneum. If desired, the surface of the patient's skin may be wiped with the transport enhancing agent-containing ab~orbent layer to effect further pretreatment of the skin before the drug delivery device is affixed.
The active drug substance diffuses at a substantially constant rate from the polymer matrix through the thin adhesive layer and permeate~ through the outer layers of skin into the dermis where it is absorbed through the fine capillary network of the papillary layer and enter~ the blood stream. The drug substance is carried by the blood throughout the body of the patient to effect a sy~temic treatment.
Figure 2 is a qchematic representation of an alternative transdermal drug delivery device embodiment generally designated by reference numeral 21.
Disper~ed throughout polymer matrix 23 are micro-reservoirs 24 containing active drug 25 dis~olved or disper~ed in a tran~port-enhancing agent 26. Use of the microreservoir-type matrix ~tructure is particular-ly advantageous where it is desired to incorporate a larger proportion of active drug into the polymer matrix than can be readily disper~ed uniformly throughout the matrix. The back of the polymer matrix . : . , . . . :
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. ' ~ : . ~ . . -' : . , . ',:
:,; ' .' : ' is covered by an occlu~ive backing layer 27, and a biocompatible pre~sure sensitive adhesive layer 29 i~
disposed over the opposite face of the matrix and the margins 31 of the backing layer. The adhe~ive layer i~
in turn covered with a releasable cover layer 33 which iq separated from the device to expoqe the adhe~ive prior to use by pulling on tab 35.
The manner of use of the embodiment of Figure 2 i~ similar to that de cribed above!~or the embodiment of Figure 1. It i~ under~tood,- of courqe, that the embodiment of Figure 2 could also be provided, if desired, with a reservoir of transport enhancing agent between adhesive layer 29 and cover layer 33 in order to effect a permeation-enhancing pretreatment of the patient's skin when the drug delivery device is applied to the patient.
It should be understood~ of course, that the drawing~ are merely schematic representations of drug delivery devices according to the invention in which proportions have been exaggerated for purpose~ of illustration.
Further detail~ of the invention will become apparent from a con~ideration of the following nonlimiting illustrative examples.
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Silioone ela~tomer (Dow Corning Silastic medical-grade 382) wa~ thoroughly mixed with isopropyl myristate using a laboratory agitator at 1,000 rpm for three minutes. Verapamil base wa~ then incorporated into the mixture and mixing was continued for four additional minutes. Then a few drops of ~tannous octanoate crosslinking catalyqt were added and thoroughly mixed for another minute. The mixture waq deaerated under vacuum for five minutes. The deaerated . .
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mixture was pressed into ~heets 0.015 centimeters thick.
Dif~usion of the active pharmaceutical was tested using a Valia-Chien diffusion cell. See P.R.
Keshary and Y.W. Chien, in Drug Develop. and Ind.
Pharm., 10, (6) 883-913 (1984). The freshly excised abdominal skin of female hairless mouse (5 to 7 weeks old), which has been found to approximate the transdermal absorption behavior of human ~kin, was olamped over the receptor cell, and the verapamil-containing polymer matrix was disposed against the stratum corneum of the skin. The receptor compartment was filled with a buffer solution at a pH of 7.4 to simulate the physiologic pH of the dermal fluid. The temperature of the system was controlled at 37C
throughout the experiment. The receptor solution was sampled periodically and analyzed by high pressure liquid liquid chromatography to determine how much of the active drug from the polymer matrix had been absorbed through the skin and the rate o~ skin permeation was calculated.
The rates of skin permeation of verapamil at different loading doses of verapamil and isopropyl myristate are shown in the followir,g table:
Device VerapamilIsopropyl myristate Permeation Number Concentration Concentration Ra~e (weight percent) (weight percent) ,ug/cm -hr . ~ . ._ V~S17 4.2 4.2 13.94 VPS18 8.4 4.2 14.04 VPS19 ~.4 8.4 21.63 VPS21 8.4 ' 8.4 23.34 VPS22 8.4 12.6 39.88 VPS23 12.6 12.6 66.92 . . . ___ . - --. . . ~ ~. . .
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Example 2 Verapamil base and isopropyl myristate were thoroughly mixed using a laboratory agitator at 1,000 rpm for three minute~. The resulting co~~olvent mixture wa~ then incorporated into ~ilicone elastomer (Dow Corning Silastic medical grade 382) and mixed for ~our additional minute~. One drop o~ cataly~t for the ~ilicone elastomer wa~ then added and mixed for another minute. The catalyzed mixkure wa~ deaerated under vacuum for five minutes J and the deaerated ,mixture was pressed into sheets 0.015 centimeters thick to form a microreservoir type polymer matrix.
The rate of skin permeation of verapamil was measured as described above. For a microreservoir-type matrix containing 4.2 weight percent verapamil and 4.2 weight percent i30propyl ~yristate the rate of permeation wa~ found to be 12.04 ,ug/cm2-hr (micrograms per square oentimeter per hour) For a microre~ervoir-type polymer matrix containing 7 weight percent ~0 verapamil and 7 weight percent isopropyl myristate the rate of verapamil ~kin permeation wa~ found to be 13.94 2-hr, Example 3 The procedure of Example 2 wa~ repeated except that 40% polyethylene glycol 400 waq utilized as the co-~olvent instead of isopropyl myristate. For a microreservoir-type polymer matrix containing 4.2 weight percent verapamil and 4.2 weight percent poly-ethylene glycol 400 (40%) the rate of verapamil ~kin permeation wa~ found to be 4.51 microgram~ per square centimeter per hour.
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Example 4 The procedure of Example 2 was repeated except glycerol was utilized as the co-solvent instead of isopropyl myristate. For a microreservoir type polymer matrix containing 9.1 weiyht percent verapamil and 9.1 weight percent glycerol, the rate of verapamil skin permeation was found to be 6.87 micrograms per square centimeter per hour.
Example 5 ~ ~he procedure o~ Example 3 was repea~ed except I-dodecylazacycloheptan-2-one (AZONE'~, Nelson Research and Development) was additionally added as a transport enhancing agent. For a microreservoir type polymer matrix containing 9.2 weight percent verapamil, 9.2 weight percent polyethylene glycol 400 (40~) and 5 weight percent 1-dodecylazacycloheptan-2-one, the rate of verapamil skin permeation was found to be 11.56 micrograms per square centimeter per hour.
Example 6 The procedure of Example 1 was repeated except that a thin layer o~ a pressure~sensitive silicone adhesive (Dow Corning DC355~) was applied to the surface of the polymer matrix and used -to adhere the polymer matrix to the skin. For a matrix-type delivery system containing 4.2 weight percent verapamil and 4.2 weight percent isopropyl myristate the rate of skin permeation was found to decrease to 11.06 micrograms per square centimeter per hour.
~ ExamPle 7 The procedure of Example 6 was repeated except 5% 1-dodecylazacycloheptan-2-one transport enhancing agent was intimately blended into the adhesive polymer :
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solution before application to the polymer matrixO The resulting verapamil skin permeation data i3 3hown in the ~ollowing table:
Dellvery Yerapamil Isopropyl Myri~- Permeation Device Concentratlon tate Concentratlon R~te Number (welght percent) (weight percent) ~g/cm -hr ~ . _ _ . . . .. __ VPS17c 4.2 4.2 18~58 VPStBc 8~4 4.2 17.82 VPS19c 8.4 8.4 20.09 __ . .. _ ~.. _ Example 8 The procedure of Example 1 wa~ repeated except polyethylene glycol 400 (40%) and 5% 1-dodecylazacyclo-heptane-2-one were utilized as the transfer enhancing agent instead o~ isopropyl myristate. The re~ulting matrix-type delivery device containing 4.2 weight percent verapamil showed a permeation rate of 9.13 microgram~ per square centimeter per hour. A similar delivery system containing 9.2 weight peroent verapamil yielded a permeation rate of 11.56 microgram~ per ~quare centimeter per hour.
Example 9 The procedure of Example 8 was repeated except the skin outer surface was pretreated with 1-dodecyl-azacycloheptan-2-one prior to application of the drug delivery matrix by placing an absorbent pad impregnated ~0 with 1-dodecylazacycloheptan-2-one on- the 3kin for about 15 to 30 seconds where the drug delivery device is sub~equently applied. The verapamil permeation rate for the matrix type device containing 4.2 weight percent verapamil increa~ed to 11.48 micrograms per square centimeter per hour while that for the device . - -. . , . : , .
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containing 9.2 weight percent verapamil increa~ed to 17.26 microgram~ per square centimeter per hour.
Example 10 The procedure of Example 1 was repeatsd except that the skin was pretreated with i~opropyl myristate prior to application of the drug delivery matrix by plaoing an isopropyl myri~tate impregnated absorbent pad on the skin for about 15 to 30 seconds where by drug delivery device is subsequently applied. The resulting skin permeation rate~ are liqted in the following table:
Delivery Verapamil Enhancer Concen- Permeation Device Concentration tration (weight Ra~e Number (weight percent)percent) ~g/cm -hr .,.. _ _ I ~
VPS18e 4.2 8.4 45.00 VPS19e 8.4 8.4 58057 VPS22d 8.4 12.6 58 68 VPS23d 12.6 12.6 112 38 VPS25d 12.6 ~ _ 41.62 . .
Example 11 The prooedure of Example 6 wa~ repeated except i~opropyl myri~tate tran~port enhancing agent was intimately blended with the adhe3ive prior to application of adhesive to the drug-containing polymer matrix. The permeation rate~ achieved with the re~ulting drug delivery device~ are summarized in the ~ollowing table:
- ." ' , ', . ' ' '. ',:, . ".' ' ~ ' . ' - - -: . . : ~ ., .: - .: ~
- 24 ~
Delivery Verapamil Enhan~er Enhancer Permeatlon Devi~e Concentration Conc~n~ratlon Concentration Ra~e Number ~ ~wei~ht (wei~ht percent) Adh~slve 1 ~g/c~ -hr ¦ percent) _(wel~ht percent)l VPS21b 8.4 8.4 10 32.40 VPS21c 8.4 8 4 20 39.79 VPS23a 12.6 12 6 5 30.52 ~PS23b 12.6 12.6 10 43.61 ~PS23c 12.6 12.6 20 71.38 _ _ _ Example 12 The procedure of Example 1 was repeated except N,N-diethyl-m-toluamide (DEET) was utilized a9 the transport enhancing agent instead of isopropyl myristate. The verapamil skin permeation rate achieved are listed in the following table:
Delivery Verapamil Enhancer Concen- Permeation Device Concentration tration (weight Ra~e Number (weight percent) percent) ~g/cm --hr . _ _ VPS24 8.4 8.4 98.39 YPS45 10 20 180.25 VPS46 5 20 200.~2 VPS47 10 30 284.25 ~PS48 20 20 121.96 _ Example 13 The procedure o~ Example 1 was repeated except propyl oleate wa3 u3ed as the transport enhancing agent instead of isopropyl myristate. The verapamil skin permeation rate achieved by a polymer matrix containing - 10 weight peroent verapamil and 10 weight percent propyl oleate was 20.27 micrograms per ~quare centimeter per hour.
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Example 14 The procedure of Ex~mple 13 wa~ repeated except oleyl alcohol was utilized as the transport enhancing agent instead of propyl oleate. The verapamil skin permeation rate achieved by a polymer matrix containing 10 weight percent verapamil and 10 weight percent oleyl alcohol wa~ 36.26 microgram~ per ~quare centimeter per hour.
~;
Example 15 The procedure of Example 14 wa~ repeated except n-decylmethylsulfoxide (DMS) was used as the transport enhancing agent instead of oleyl alcohol. The verapamil skin permeation rate achieved by a polymer matrix containing 10 weight percent verapamil and 10 weight percent DMS waq 105.28 microgram~ per square centimeter per hour.
Example 16 The procedure of Example 1 was repeated except mixtures of isopropylmyristate (IPM) and N,N-diethyl-m-toluamide (DEET) were utilized as the tran~portenhancing agent. The re~ulting skin permeation rate~
are li~ted in the ~ollowing table:
Delivery Verapamil Enhancer Concen- Permeation Device Concentration tration (weight Ra~e Number (weight percent) percent) ~g/cm -hr IPM DEET
VPS39 10 10 10 139.55 VP540 10 15 164.04 , :
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Exam~le 17 A matrix-type transdermal drug delivery device is prepared by intimately blending equal weights of verapamil and N,N-diethyl-m-toluamide after which the mixture is uniformly dispersed in a bioacceptable silicone elastomer. Crosslinking catalyst is then added to the elastomer, th~ catalyzed mixture i~
deaerated, and the deaerated mixture is pressed into thin sheets 0.015 centimeters thick. The resulting sheets are cut into 5 centimeter diameter circles.
One face of each circle is covered with an occlusive backing comprising an aluminum foil/polyester film laminate (3M Company, SCOTCHPAK'~ 1006). A
bioacceptable, amine-resistant silicone adhesive (Dow Corniny X7-2920) containing 20 weight percent N,N-diethyl-m-toluamide intimately blended therewith is applied to the opposite face of the polymer matrix.
The adhesive surface is then covered with a removable polyethylene film having an absorbent open-celled foam layer heat sealed to its inner face and saturated with N,N-diethyl-m-toluamide.
ExamPle 18 Equal amounts of verapamil base and isopropyl myristate were thoroughly mixed using a laboratory agitator at 1000 r.p.m. for three minutes. The resulting co-solvent mixLure was then incorporated into a silicone elastomer (Dow Corning Silastic medical-grade 382~ and mixed for four additional minutes. One drop of catalyst for the silicone elastomer was then added and mixed for another minute. The catalyzed mixture was deaerated under vacuum for five minutes, and the deaerated mixture was pressed into sheets 0.015 centimeters thick to form a microreservolr-type polymer matrix containing 13 weight percent verapamil base and 13 weight percent isopropyl myristate transport --.
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enhancing agent. The sheets were cut into 20 square centimeter patches, and the back of each patch was adhered to the center of an occlusive metal foil backing sheet (3M Company) wlth a ~ilicone adhesive (Dow Corning DC 355). The front surface of each patch was covered with a thin layer of silicone adhesive (Dow Corning DC 355) into which 20 weight percent isopropyl myri~tate tran~port enhancing agent had been incorporated. Prior to use of the device, the exposed adhesive surfaces on the face of the polymer matrix and the margins of the backing sheet were temporarily covered with a protective release liner.
In use1 the release liner was stripped away, and from two to four patches were applied to the chest areas of healthy male volunteers 21 to 40 years of age.
In some ca~es the patient's skin was pretreated by contact with an absorbent pad saturated with isopropyl myristate for a few seconds prior to applying the patches. Patches were removed after 24 hours.
Effective transdermal administration of verapamil was confirmed by monitoring the heart rate, blood pressure, respiration and ECG of each patient and by withdrawing and analyzing blood samples ju~t prior to application of the patches and periodically over 48 hours after application of the patches.
The foregoing description and examples have been set forth merely to illustrate the invention and are not intended to be limiting. Since modifications of the deqcribed embodiments incorporating the spirit and substance of the invention may occur to persons skilled in the art~ the scope of the invention is to be limited solely with respect to the appended claims and equivalentq .
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TRANSDERMAL VERAPAMIL DELIVERY DEVICE
-Background of the Invention Thi~ invention relates to a devioe for transdermal admini~tration of an active pharmaceutical at a ~ustained 9 substantially uniform rate of delivery over an extended period of time. More particularly, the invention relates to a device particularly adapted ~or tran~dermal admini~tration of verapamil.
Treatment of patient~ with pharmaceutically active substance~ i~ commonly carried out by periodically adminstering defined doses of the pharmaceutical to the patient, e.g. either orally or by injection. Such techniques provide a maximum dosage of the pharmaceutical ~ollowing each administration which then eontinually decline~ until the next do~e is admini~tered~ In order to as3ure that an effective dosage of pharmaceutical is present in the body at all times, peak dosages which are much higher than the effective level are needed. Thiq unde~irably increase~
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the amount of pharmaceutical which is consumed and concomitantly increa~es the danger of unde~ired side effects. Moreover, even though qubstantial excess dosages are adminstered, there is always a danger that ~ 5 the concentration of the pharmaceutical may drop below the effective level if adminstration of a ~ubsequent dose 9 delayed or omitted. Further, there is a possibility, particularly with oral administration of pharmaceuticals, that a portion of the pharmaceutically active substance may be metabolized before r,eaching its intended locus of activity. This further increases the excess of pharmaceutical which must be administered in order to assure that an effective concentration i~
maintained.
Techniques also exist for Yustained, low level administration of pharmaceuticals. The technique most commonly utilized is intravenous infusion. This technique, while effective at providing sustained low levels of pharmaceutical, is cumbersome and al~o ~0 requires close supervision by trained medical personnel. Con~equently, intravenous infusion of pharmaceuticals typically requires hospitalizat~on of the patient with attendant expense and inconvenience.
Techniques have also been developed for administering pharmaceuticals at sustained low levels by absorption through the skin. Transdermal delivery devices are now commerically available for nitroglycerin, scopolamine and other pharmaceuticals.
Such devices typically comprise either a pharmaceutical-containing reservoir enclosed by a membrane through which the pharmaceutical can diffuse at a controlled rate or a dispersion of pharmaceutical in a polymer matrix from which the pharmaceutical can diffuse at a controlled rate. The devices are attached either adhesively or otherwise to the skin of a '' .:; ` ' : ' , ' - . . : . . .
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patient, and the pharmaceutical is permitted to diffu3e from the device and permeate through the outer sublayer~ of skin until it iq absorbed into the blood stream in the fine capillary network of the dermi~.
Once absorbed into the blood stream, the pharmaceutical is then oarried throughout the entire body syste~ of the patient.
While such transdermal delivery devices have worked well for some pharmaceutical~, notably nitroglycerine, conventional tran~dermal delivery devices have not proved suitable for other important drugs. Reservoir-type delivery devices are subject to the risk of undersirable dose damping if the rate controlling membrane is inadvertently damaged. The rate of release of some pharmaceutical~ from conventional devices has proved to be too slow to provide an effective dosage of pharmaceutical unless the size of the transdermal delivery patch was excessively large. In some instances it has been difficult to maintain effective contact between the transdermal drug delivery device and the skin of the patient. Attempt~ to solve the problem of maintaining contact by providing an adhesive over the face of the delivery device so that it po~itively adheres to the patient'~ skin have not been fully successful. In some instances, due to the nature of the drug delivery matrix, available adhe~ives have not adhered well to the tranqdermal drug delivery device. Where ~atisfactory adhesion between the drug delivery device and the matrix ha~ been obtained, it has been found that the adhesive act~ aq a barrier and retards transfer o~ the active qub~tance from the drug delivery device to the skin. For some pharmaceutical~, the rate of skin permeation and abqorption is o low that it has not been possible to provide an effective do~age within - . .. .
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a reasonably sized area o~ 3kin.
One drug for which a transdermal delivery device would be desirable i~ 5-[(3,4-dimethoxy-phenethyl) methylamino] 2-(314-dimethoxyphenyl)-2-isopropylvaleronitrile, also known as verapamil. Thi~substance is a well established coronary vasodialator and antiarrythmic agent. A self-supporting polymeric diffusion matrix for su~tained transdermal delivery of verapamil has been propo3ed by Reith et al. (PCT
application No. W083/00091), but this sy~tem is subject to many of the disadvantages discussed above.
Summary of the Invention Accordingly, it iR the object of the present invention to provide a new drug delivery device for sustained uniform admini~tration of a pharmaceutical by the transdermal route.
Another object of the present invention i~ to provide a transdermal drug delivery device which enables sustained maintenance of an effective dosage level using a lesser amount of active ingredient than required for periodic administration either orally or by injection.
A further object of the present invention is to provide a transdermal drug delivery device which is not subject to the danger of dose dampingO
It is also an object of the present invention to provide a transdermal drug delivery device from which the active pharmaceutical is released at an enhanced rate.
A ~till further object of the pre3ent invention is to provide a transdermal drug delivery device in which effective contact between the device and the skin of a patient can be continuously maintained.
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~76 Yet another object oP the present invention is to provide an adhesively attached transdermal drug delivery device in which the adhe~ive layer perrnits a high rate of transfer of active pharmaceutical from the device to the skin of a patient.
Additionally, it is an object of the present inventîon to provide a transdermal drug delivery device which facilitates permeation of the active pharmaceutical through the!~kin of a patient.
It is also an object of the presen,t invention to provide a transdermal drug delivery device which can administer an effective dosage of pharmaceutical while at the same time being conveniently small in size.
These and other objects of the invention are achieved by providing a transdermal drug delivery device comprising a permeable bioacceptable lipophilic polymer matrix having an effective cardiovascular affecting amount of 5-[(3,4-dimethoxyphenethyl) methyl~
amino]-2-(3,~-dimethoxyphenyl)-2-isopropylvaleronitrile and an effectiYe release promoting amount of a transport enhancing agent dispersed therein.
In another aspect of the invention, the objects of thè invention are achieved by providing a transdermal drug delivery device comprising a permeable, polymer matrix having an effective cardiovascular affecting amount of 5-[(3,4-dimethoxyphenethyl) methyl-amino]-2-(3,4-dimethoxyphenyl~-2-isopropylvaleronitrile and an effective release promoting amount of a first transport enhancing agent dispersed therein, and a bioacceptable adhesive layer covering one face of said polymer matrix, said adhesive having an effective transport promoting amount of a second transport enhancing agent dispersed therein.
According to a still further aspect of the present invention, the objects of the invention are - ., : . . -: .. . .
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achieved by providing a transdermal drug delivery device compri~ing a permeable polymer matrix having an effective cardiovascular affecting amount of 5-[(3,4-dimethoxyphenethyl) methylamino]-2-(3,4-dimethoxy-phenyl)-2-isopropylvaleronitrile and an effective release promotlng amount of a transpork enhancing agent dispersed therein, ~aid polymer matrix having one surface di~posable adjacent the skin of a patient, and a supply o~ skin permeation enhancing agent adjacent said one`polymer matrix surface such that when said one surface is disposed adjacent (e.g. in intimate contact with) a patient's skin, the skin is then treated with said skin permeation enhancing agent.
In a particularly preferred embodiment) the transdermal drug delivery device of the invention comprises a matrix of bioacceptable cross-linked ~ilicone polymer having an effective cardiovascular affecting amount of 5-~(3,4-dimethoxyphenethyl) methyl-amino3-2-(3,4-dimethoxyphenyl)-2-i~opropylvaleronitrile and an effective release promoting amount of a first drug transport enhancing agent such as isopropyl myristate or N,N-diethyl-m-toluamide dispersed therein, ~aid matrix having first and second opposed faces; a layer of bioacceptable silicone adhesive on said first face o~ said matrix, said adhesive having an effectiYe drug transport promoting amount of a second transport enhancing agent dispersed therein, and an occlusive backing covering ~aid second face of ~aid matrix.
In a further preferred embodiment of the transdermal drug delivery device of the invention, an absorbent material impregnated with a 3kin permeation enhancing agent is removably positioned adjacent the adhe~ive ~urface of the drug delivery device ~uch that the impregnated absorbent material can be peeled away prior to use and when peeled away will leave the . ~ , ~ - , : ... . . . . : :
- . ~ . - - .. , _ 7 _ adhesive surface moistened with skin permeation enhancing agent such that when the transdermal drug delivery device i9 applied to the skin of a patient, the skin surface will be moistened with the skin permeation enhancing agent.
Brief Deqcription of the Drawin~s The invention will be described in further detail with reference to the accompanying drawings wherein: , Figure 1 ~s a schematic representation of matrix-type transdermal drug delivery device with a skin permeation enhancing agent reservoir removably disposed adjacent the adhesive layer, and Figure 2 is a schematic repre~entation of a lS microreservoir-type transdermal drug delivery device.
Detailed Description of Preferred Embodiments The polymer matrix in which the active pharmaceutical is dispersed may be formed from any biocompatible polymeric material which exhibits significant lipophilic character. It has been found that release of active drug from the polymer matrix i3 better if the polymeric material of the matrix i~
eqsentially electroneutral with respect to the drug.
That is to say, the polymer matrix must not donate any proton or electron to or receive any proton or electron from the active pharmaceutical, but instead the active pharmaceutical should exi~t essentially in electrically neutral, non-ionic form within the polymer matrix. Use of lipophilic (hydrophobic) polymer materials for the polymeric matrix also facilitate~ application of an adhesive over the surface of the matrix to secure the drug delivery device in continuou~ contact with the skin of a patient. Where hydrophilic polymer matrice~
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are used~ it i~ dif'ficult to obtain ~atisfactory adhesion between the adhesive and the polymer matrix.
Suitable bioacceptable polymers which can be u~ed for preparation of the drug di~per~ing polymer matrix include silicone elastomers with variou~ sub~tituents on the ~ilicon atom~, dialkylsiloxane-ethylene oxide copolymers, dialkylsiloxane-methacrylate copolymers, dialkylsiloxane-polycarbonate copolymers, ethylene-vinyl acetate copolymers (EVA), polyolefins 3uch a~
polyeth~lene or polypropylene, and other polymers with similar lipophilic, electroneutral character. Cros~~
linking silicone rubber materialq such a~ silicone polymers corresponding to the formula:
~ IH3 ~ ~ CH3 t --IH3~ I tC}13 ~m CH3--Si O _ r--P
wherein R i~ alkoxy, alkyl, alkenyl or aryl containing 1 to 7 carbon atom~ and wherein n, m and p are about 100 to 5,000 are particularly preferred a~ polymer matrix material~. Good results have been achieved u~ing matrioies formed o~ cro~s-linked polydimethyl~
siloxanes.
The thickne~ of the polymer matrix may be varied as desired depending inter alia upon the de~ired pharmaceutical dosage and duratior. of treatment.
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Ordinarily suitable matrix thickne~es may range from about 0.005 cm to about 0.5 cm.
An effective drug release promoting amount of a tran~port enhancing agent is de~irably incorporated in the polymer matrix with the active pharmaceutical.
Suitable transport enhancing materials include ~aturated aliphatic acids and derivatives such as myri~tic acid, isopropyl myristate, myristyl alcohol and mono-myristein; unsaturated aliphatic acids and derivativeQ ~uch as oleic acid, propyl oleate, oleyl alcohol and mono-olein; aryl alkyl tertiary amine~
including dialkyl aryl amines ~uch as N 3 N-diethyl-m-toluamide; dialkyl sulfoxides such as dimethyl sulfoxide or decyl methyl sulfoxide; 1-substituted azacycloalkan-2-ones such a3 1-dodecyla~acycloheptan-2-one; dialkyl amide~ Quch as dimethyl or diethylacetoamide and thioglycollates such as calcium thioglycollate. Mixtures of two or more of the foregoing may be u~ed to advantage; for example, mixtures of isopropyl myristate and N,N-diethyl-m-toluamide have been used to good effect.
The transport enhancing agent may be dispersed in the polymer matrix ln amounts ranging from about 2 to about 40 percent by weight. Preferably, the transport enhancing agent will be present in an amount ranging from about 5 to about 3O percent by weight.
Where the polymer matrix i~ disposed in direct contact with the skin of a pati`ent during use, the drug release promoting tran~port agent may also promote skin permeation by the drug.
The active pharmaceutical may be di~persed in the polymeric material prior to cros~linking to form the completed matrix~ Alternatively, a solution or su~pension of the active pharmaceutical in the transport enhancing agent may be disper~ed in the ~ ` '` .
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-- 10 _ polymer matrix prior to cros~linking in which case microre~ervoirs of the drug are formed in the matrix.
Generally, the active drug will be pre~ent in an amount ranging from about 2 to about 50 p~rcent by weight of ~he polymer matrix. Preferably, the amount of active drug will range from about 5 to about 30 weight percent ~ith respect to the polymer matrix. U~e of exces~ively low concentrations of active drug makes it difficult to obtain an acceptably high rate of relea~e of the drug from the polymer matrix and to achieve a ~ubstantially uniform rate of release over an extended period of time. Use of excessively high concentrations of active drug render3 it more di~ficult to control the rate of release of the drug from the matrix.
An occlusive backing material is disposed over one side of the polymer matrix. The backing material should be substantially impermeable to the active drug and any transport enhancer found in the polymer matrix.
Such a backing iq needed to prevent migration of the active ingredient~ from the polymer matrix other than to the skin of a patient to which the matrix is properly attached. Such a backing also facilitates handling of the drug delivery device and inhibitq ~oiling of clothing worn by a patient over the transdermal drug delivery device. Suitable backing materials include metal foil~ such as aluminum foil, polyesters such as polyethylene terephthalate, polyamides such as polycaprolactones, polyolefins such as polyethylene or polypropylene, polyacrylates such as polymethylmethacrylate or acrylamide, polyurethaneq, vinyl polymers and copolymer3 such a~ polyvinyl chloride or polyvinylacetate, polyurethanes, cellophaneq or other similar materials. Multi-layer laminates may also be used. A particularly preferred backing material compriqeq a skin-colored polyester ' ~ - ,' ' ' ' . . ' .
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- ' film/metal foil laminate.
The drug delivery device of the invention may be advantageously Yecured to the skin of a patient by using a bioacceptable pressure-sen~itive adhe~ive of the type used for medical dre~ings. In order to assure continuou3 and reliable contact between the drug-releasing polymer matrix and the patient's ~kin, it is preferred to apply the adhesive layer over at least the entire face of the polymer matrix. Suitable adhe~ive materials include non-toxic and non-irritating hypoallergenic adhesive~ based on polydienes, for example polybutadiene; acrylates, for example copolymers of methylacrylate or methacrylate and methacrylic acid; vinyl resins, for example polyvinyl-acetate, polyvinylalcohol, polyvinylchloride andcopolymers o~ the~e and similar vinyl monomer~; natural gum~, for example guar or acacia; polyurethanes; and other adhe~ive material Silicone rubber adhesives have been found to combine excellent hypoallergenicity, ~0 satisfactory adhesion and good stripability when the patient i~ finished wearing the dressing and are therefore particularly preferred. Good result~ have been achieved u~ing commercially available medical-grade polydimethyl~iloxane adhesive~.
Of course, it is also po~sible tv provide adhe~ive only around the periphery of the drug delivery device of the invention to ~ecure it to the patient or even to omit the adhesive layer entirely and ~ecure the drug delivery device to the patient with any overlying wrap or bandage.
The interpo~ed adhe~ive between the drug-releasing polymer matrix and the ~in of the patient will to ~ome extent impede the tran~fer of the drug from the matrix to the patient. However, it has been found that by incorporating a suitable tran~port - - . : .
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enhancing agent into the adhe~ive, good transfer of the drug from the matrix to the patient may be obtained.
.~ny of the tran~port enhancing agent~ ted above a~
suitable for inclusion in the polymer matrix may also be used in the adhesive. It is not necessary that the same transport enhancing agent be u~ed in the adhe~ive as is used in the polymer matrix. For verapamil, particularly preferred transport enhancing agents include isopropyl myristate, n-decylmethyl~ulfoxide, oleyl alcohol, propyl oleate, 1-dodecylazaGycloheptan-2-one, or N,N-diethyl-m-toluamide. From about 1 to about 30 percent by weight transport enhancing agent may be incorporated into the adhesive. Preferably, the amount of transport enhancing agent will lie in the range from about 5 to about 25 weight percent of the adhesive.
The pH of the adheqive has also been found to affect the tranqfer of the active drug from the drug-releasing matrix to the patient. The pH of the adhesive should be such that the active drug exist~ as ~n electrically neutral species at the lnterfaces between the matrix and adhesive and between the adhesive and the 3kin of the patient. Suitable control of the pH achieves an optimum balance between drug solubility which increases the rate of release of the drug from the polymer matrix and skin hydration which increases the rate of absorption of the drug specie~
through the skin. The optimum pH may vary omewhat with different drugs. For verapamil, the pH should be maintained between about 5 and about 7. It is particularly preferred that the pH of the adhe~ive system in the verapamil transdermal delivery device of the invention be maintained at approximately 6. If desired, a small amount of a buffering agent quch as a disodium hydrogen pho phate/citric acid buffer may be - , ,, , ~
- . .
.
..
. , ,: .
, . . .
incorporated into the adhesive and/or polymer matrix to a~sist in maintaining the desired pH value at which the drug molecules exi~t in electrically neutral form.
The adhe~ive layer may be applied to the exposed face of the polymer matrix and the protruding margins of the backing by solvent ca~ting or spraying.
Any suitable solvent may be used such as acetone, methyl ethyl acetate, diethyl ether, etc. Di~per~ion o~ a skin permeation enhancing agent and/or a buffering agent throughout the adhesive may be achieved by dissolving the agent in the adhesive solution prior to applying the adhesive to the polymer matrix. The thickness of the applied adhesive layer may vary.
Suitable thicknesses may range'from about 10 to about 200 microns or more. In order tQ minimize any tendency of the adhesive layer to impede transfer of the pharmaceutical substances from the polymer matrix to a patient's skin, it i~ generally desirable that the adhesive layer be as thin as practicable.
Prior to use of the drug delivery device the adhesive layer may be co~ered by a releasable protective strip. Such a strip may be formed from the same materials used for the backing provided with a conventional release coating, for example, a fluorocarbon or a silicone surface treatment.
It has also been ~ound that ab~orption of the active drug through the skin can be enhanced by pretreating the ~kin with a permeation enhancing agent when the drug delivery device is applied to the skin of the patient. Any of the transport enhancing agents described above may be utilized. Particularly good re~ult~ have been obtained using n-decyl-methylsùlfoxide, 1-dodecylazacycloheptan-~-one, isopropyl myri~tate or N,N-diethyl-m-toluamide.
Pretreatment may be achieved by simply contacting or `. '~ ` ' ' -~ ~ . ' . ' . ' . ' -; . ' , ' ' ` .
.:
.
_ 14 _ wiping the skin with the permeation enhancing agent shortly prior to affixing the drug delivery device to the patient's skin. Alternatively, a re~ervoir of tran~port enhancing agent may be included in the drug delivery device such that the skin i~ moi3tened with the transport enhancing agent as the drug delivery device is applied to the patient.
Typically, permeation of the drug through the stratum corneum ti.e. the outermost layer of the epidermi~) is quite slow. If the strakum. corneum is untreated, it may limit the rate at which the active drug can be administered to the patient. Under such circumstances9 it is often desirable that the rate of drug relea~e from the polymer matrix be slightly greater than the rate of permeation through the stratum corneum so that the surface of the skin will be saturated with the active drug in order to maximize the rate of drug absorption.
If, on the other hand, the skin i~
appropriately treated with a ~kin permeation enhancing agent either by pretreatment or by incorporation of ~ufficient permeation enhancing agent into the adhesive layer, it i~ possible to increase the rate of ~kin permeation to a value which equals or exceed~ the desired rate of tran~fer of active drug to the patient.
Under such circum~tance~, skin permeation i~ no longer the rate-limiting ~tep. Instead, the overall rate of tran~fer of the active drug to the patient is controlled by the rate of relea~e of the drug from the drug delivery device. This i~ particularly de~irable in situations where the rate of skin permeation i~
affected by patient difference~ so that uniform do~ing can be achieved independently of the nature or condition of the patient'~ ~kin.
~ - . ., . -- , . . '; . ' . ~ : .
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The ~ize of the drug delivery device should be large enough to permit easy handling but small enough to facilitate convenient application to ~he patient and to avoid an ob~trusive appearance. Typical ~ize~ may range from about 3 square centimeter~ to about 100 square centimeters, preferably from about 5 square centimeters to about 80 ~quare centimeters. It i~
understood, of course, that the size of the delivery device must be interrelated with the rate of relea3e and ab~orption of the active drug in order,to achieve administration of a desired do~age to the patient.
The desired dosage will vary depending on the individual drug as ~ell as on the size and condition of the patient. For verapamil, suitable dosages may lie in the range from about 1 to about 200 milligrams per day. In mo~t case~, the verapamil dosage will lie in the range from-about 1 to about 100 milligrams per day.
The transdermally absorbed verapamil dosage will generally lie in the range from about 2 to about 20 milligrams per day. Do~ages in the range from about 5 to about 10 milligram~ per day are usually preferred.
The actual do~age which ~hould be admini~tered in any given case can be determined by the pre~cribing phy~ician in accordance with good medical practice. If desired, higher rate~ of admini~tration can be achieved by affixing more than ons transdermal drug delivery device to the patient.
Generally speaking, the matrix will contain some exce~ of drug above the dosage amount to be administered to the patient. Ordinarily the polymer matrix will contain from about 1.5 to about 10 time~
the intended dosage amount, preferably from about 2 to about 5 times the dosage amount of drug which is to be tran~dermally absorbed. The drug may also be incorporated in the form of an active derivative or a . . . . .
- - . ~ ~ . , :.
.. . .
~ ~7 prodrug~
Referring now to the drawings, Figure illustrates a first preferred embodiment of the transdermal drug delivery device of the invention generally designated by reference numeral 1. The device comprises a permeable lipophilic cross-linked polymer matrix 3 having an effective release-promoting amount of a transport enhancing agent di~persed throughout the matrix. Also disper~ed throughout the matrix i9 a pharmaceutically effective amount of a transdermally absorbable drug representated schematically by particles 5. The bac~ of the polymer matrix is covered by an occlusive layer, such as plastic ~ilm/metal foil 7, to prevent los~ of material through the back of the drug delivery device and to protect the device from the environmental conditions.
A layer of bioacceptable pressure-sensitive adhesive 9 is applied to the opposite face of the polymer matrix and extends over the margins 11 of the backing. A
suitable amount o~ tranqport enhancing agent is also dispersed in adhesive layer 9. The outer ~ace of the adhesive is covered by a relea~able cover strip 13 provided with a protruding pull tab 15. In the illustrated embodiment, an absorbent layer 17 is affixed to cover layer 13 between the cover layer and adhesive layer 9. For example, the absorbent layer could comprise an open-celled foam layer which has been heat sealed to the inner surface of the cover layer.
Absorbent layer 17 is impregnated with a permeation enhancing agent in order to facilitate pretreatment of the patient's skln.
In use, tab 15 is firmly grasped and pulled away from adhesive layer 9 to ~eparate the cover 13 and absorbent layer 17 from the rest o~ the drug delivery device. As the ab~orbent layer 17 separates from the ., . , . ~ .
.
~ ~7 - 17 ~
adhesive layer, a ~hin film of permeation enhancing agent remains on the qurface of the adhe~ive layer.
The exposed adhesive surface is then pre~ed again~t the skin of a patient to be treated wikh the drug S contained in the drug delivery device. The adhesive adheres to the skin and thereby holds the entire surface of the drug delivery device in contact with the patient. As the adhesive is applied to the patient's skin, the skin surface is moistened by the thin ~ilm of transport enhancing agent on the surface of the adhesive, thereby facilitating increa~ed premeation of the active drug through the stratum corneum. If desired, the surface of the patient's skin may be wiped with the transport enhancing agent-containing ab~orbent layer to effect further pretreatment of the skin before the drug delivery device is affixed.
The active drug substance diffuses at a substantially constant rate from the polymer matrix through the thin adhesive layer and permeate~ through the outer layers of skin into the dermis where it is absorbed through the fine capillary network of the papillary layer and enter~ the blood stream. The drug substance is carried by the blood throughout the body of the patient to effect a sy~temic treatment.
Figure 2 is a qchematic representation of an alternative transdermal drug delivery device embodiment generally designated by reference numeral 21.
Disper~ed throughout polymer matrix 23 are micro-reservoirs 24 containing active drug 25 dis~olved or disper~ed in a tran~port-enhancing agent 26. Use of the microreservoir-type matrix ~tructure is particular-ly advantageous where it is desired to incorporate a larger proportion of active drug into the polymer matrix than can be readily disper~ed uniformly throughout the matrix. The back of the polymer matrix . : . , . . . :
- : ' :: : , , ~ , :- ' .:
. ' ~ : . ~ . . -' : . , . ',:
:,; ' .' : ' is covered by an occlu~ive backing layer 27, and a biocompatible pre~sure sensitive adhesive layer 29 i~
disposed over the opposite face of the matrix and the margins 31 of the backing layer. The adhe~ive layer i~
in turn covered with a releasable cover layer 33 which iq separated from the device to expoqe the adhe~ive prior to use by pulling on tab 35.
The manner of use of the embodiment of Figure 2 i~ similar to that de cribed above!~or the embodiment of Figure 1. It i~ under~tood,- of courqe, that the embodiment of Figure 2 could also be provided, if desired, with a reservoir of transport enhancing agent between adhesive layer 29 and cover layer 33 in order to effect a permeation-enhancing pretreatment of the patient's skin when the drug delivery device is applied to the patient.
It should be understood~ of course, that the drawing~ are merely schematic representations of drug delivery devices according to the invention in which proportions have been exaggerated for purpose~ of illustration.
Further detail~ of the invention will become apparent from a con~ideration of the following nonlimiting illustrative examples.
~
Silioone ela~tomer (Dow Corning Silastic medical-grade 382) wa~ thoroughly mixed with isopropyl myristate using a laboratory agitator at 1,000 rpm for three minutes. Verapamil base wa~ then incorporated into the mixture and mixing was continued for four additional minutes. Then a few drops of ~tannous octanoate crosslinking catalyqt were added and thoroughly mixed for another minute. The mixture waq deaerated under vacuum for five minutes. The deaerated . .
. - .
. . . ' .~ ~ . ~ , - , .
mixture was pressed into ~heets 0.015 centimeters thick.
Dif~usion of the active pharmaceutical was tested using a Valia-Chien diffusion cell. See P.R.
Keshary and Y.W. Chien, in Drug Develop. and Ind.
Pharm., 10, (6) 883-913 (1984). The freshly excised abdominal skin of female hairless mouse (5 to 7 weeks old), which has been found to approximate the transdermal absorption behavior of human ~kin, was olamped over the receptor cell, and the verapamil-containing polymer matrix was disposed against the stratum corneum of the skin. The receptor compartment was filled with a buffer solution at a pH of 7.4 to simulate the physiologic pH of the dermal fluid. The temperature of the system was controlled at 37C
throughout the experiment. The receptor solution was sampled periodically and analyzed by high pressure liquid liquid chromatography to determine how much of the active drug from the polymer matrix had been absorbed through the skin and the rate o~ skin permeation was calculated.
The rates of skin permeation of verapamil at different loading doses of verapamil and isopropyl myristate are shown in the followir,g table:
Device VerapamilIsopropyl myristate Permeation Number Concentration Concentration Ra~e (weight percent) (weight percent) ,ug/cm -hr . ~ . ._ V~S17 4.2 4.2 13.94 VPS18 8.4 4.2 14.04 VPS19 ~.4 8.4 21.63 VPS21 8.4 ' 8.4 23.34 VPS22 8.4 12.6 39.88 VPS23 12.6 12.6 66.92 . . . ___ . - --. . . ~ ~. . .
' , - . .
:
.
Example 2 Verapamil base and isopropyl myristate were thoroughly mixed using a laboratory agitator at 1,000 rpm for three minute~. The resulting co~~olvent mixture wa~ then incorporated into ~ilicone elastomer (Dow Corning Silastic medical grade 382) and mixed for ~our additional minute~. One drop o~ cataly~t for the ~ilicone elastomer wa~ then added and mixed for another minute. The catalyzed mixkure wa~ deaerated under vacuum for five minutes J and the deaerated ,mixture was pressed into sheets 0.015 centimeters thick to form a microreservoir type polymer matrix.
The rate of skin permeation of verapamil was measured as described above. For a microreservoir-type matrix containing 4.2 weight percent verapamil and 4.2 weight percent i30propyl ~yristate the rate of permeation wa~ found to be 12.04 ,ug/cm2-hr (micrograms per square oentimeter per hour) For a microre~ervoir-type polymer matrix containing 7 weight percent ~0 verapamil and 7 weight percent isopropyl myristate the rate of verapamil ~kin permeation wa~ found to be 13.94 2-hr, Example 3 The procedure of Example 2 wa~ repeated except that 40% polyethylene glycol 400 waq utilized as the co-~olvent instead of isopropyl myristate. For a microreservoir-type polymer matrix containing 4.2 weight percent verapamil and 4.2 weight percent poly-ethylene glycol 400 (40%) the rate of verapamil ~kin permeation wa~ found to be 4.51 microgram~ per square centimeter per hour.
. . . . .
. . .
Example 4 The procedure of Example 2 was repeated except glycerol was utilized as the co-solvent instead of isopropyl myristate. For a microreservoir type polymer matrix containing 9.1 weiyht percent verapamil and 9.1 weight percent glycerol, the rate of verapamil skin permeation was found to be 6.87 micrograms per square centimeter per hour.
Example 5 ~ ~he procedure o~ Example 3 was repea~ed except I-dodecylazacycloheptan-2-one (AZONE'~, Nelson Research and Development) was additionally added as a transport enhancing agent. For a microreservoir type polymer matrix containing 9.2 weight percent verapamil, 9.2 weight percent polyethylene glycol 400 (40~) and 5 weight percent 1-dodecylazacycloheptan-2-one, the rate of verapamil skin permeation was found to be 11.56 micrograms per square centimeter per hour.
Example 6 The procedure of Example 1 was repeated except that a thin layer o~ a pressure~sensitive silicone adhesive (Dow Corning DC355~) was applied to the surface of the polymer matrix and used -to adhere the polymer matrix to the skin. For a matrix-type delivery system containing 4.2 weight percent verapamil and 4.2 weight percent isopropyl myristate the rate of skin permeation was found to decrease to 11.06 micrograms per square centimeter per hour.
~ ExamPle 7 The procedure of Example 6 was repeated except 5% 1-dodecylazacycloheptan-2-one transport enhancing agent was intimately blended into the adhesive polymer :
,..
, . ' , . .' , ~ . ~ ' :
.
~7~
solution before application to the polymer matrixO The resulting verapamil skin permeation data i3 3hown in the ~ollowing table:
Dellvery Yerapamil Isopropyl Myri~- Permeation Device Concentratlon tate Concentratlon R~te Number (welght percent) (weight percent) ~g/cm -hr ~ . _ _ . . . .. __ VPS17c 4.2 4.2 18~58 VPStBc 8~4 4.2 17.82 VPS19c 8.4 8.4 20.09 __ . .. _ ~.. _ Example 8 The procedure of Example 1 wa~ repeated except polyethylene glycol 400 (40%) and 5% 1-dodecylazacyclo-heptane-2-one were utilized as the transfer enhancing agent instead o~ isopropyl myristate. The re~ulting matrix-type delivery device containing 4.2 weight percent verapamil showed a permeation rate of 9.13 microgram~ per square centimeter per hour. A similar delivery system containing 9.2 weight peroent verapamil yielded a permeation rate of 11.56 microgram~ per ~quare centimeter per hour.
Example 9 The procedure of Example 8 was repeated except the skin outer surface was pretreated with 1-dodecyl-azacycloheptan-2-one prior to application of the drug delivery matrix by placing an absorbent pad impregnated ~0 with 1-dodecylazacycloheptan-2-one on- the 3kin for about 15 to 30 seconds where the drug delivery device is sub~equently applied. The verapamil permeation rate for the matrix type device containing 4.2 weight percent verapamil increa~ed to 11.48 micrograms per square centimeter per hour while that for the device . - -. . , . : , .
~7~
containing 9.2 weight percent verapamil increa~ed to 17.26 microgram~ per square centimeter per hour.
Example 10 The procedure of Example 1 was repeatsd except that the skin was pretreated with i~opropyl myristate prior to application of the drug delivery matrix by plaoing an isopropyl myri~tate impregnated absorbent pad on the skin for about 15 to 30 seconds where by drug delivery device is subsequently applied. The resulting skin permeation rate~ are liqted in the following table:
Delivery Verapamil Enhancer Concen- Permeation Device Concentration tration (weight Ra~e Number (weight percent)percent) ~g/cm -hr .,.. _ _ I ~
VPS18e 4.2 8.4 45.00 VPS19e 8.4 8.4 58057 VPS22d 8.4 12.6 58 68 VPS23d 12.6 12.6 112 38 VPS25d 12.6 ~ _ 41.62 . .
Example 11 The prooedure of Example 6 wa~ repeated except i~opropyl myri~tate tran~port enhancing agent was intimately blended with the adhe3ive prior to application of adhesive to the drug-containing polymer matrix. The permeation rate~ achieved with the re~ulting drug delivery device~ are summarized in the ~ollowing table:
- ." ' , ', . ' ' '. ',:, . ".' ' ~ ' . ' - - -: . . : ~ ., .: - .: ~
- 24 ~
Delivery Verapamil Enhan~er Enhancer Permeatlon Devi~e Concentration Conc~n~ratlon Concentration Ra~e Number ~ ~wei~ht (wei~ht percent) Adh~slve 1 ~g/c~ -hr ¦ percent) _(wel~ht percent)l VPS21b 8.4 8.4 10 32.40 VPS21c 8.4 8 4 20 39.79 VPS23a 12.6 12 6 5 30.52 ~PS23b 12.6 12.6 10 43.61 ~PS23c 12.6 12.6 20 71.38 _ _ _ Example 12 The procedure of Example 1 was repeated except N,N-diethyl-m-toluamide (DEET) was utilized a9 the transport enhancing agent instead of isopropyl myristate. The verapamil skin permeation rate achieved are listed in the following table:
Delivery Verapamil Enhancer Concen- Permeation Device Concentration tration (weight Ra~e Number (weight percent) percent) ~g/cm --hr . _ _ VPS24 8.4 8.4 98.39 YPS45 10 20 180.25 VPS46 5 20 200.~2 VPS47 10 30 284.25 ~PS48 20 20 121.96 _ Example 13 The procedure o~ Example 1 was repeated except propyl oleate wa3 u3ed as the transport enhancing agent instead of isopropyl myristate. The verapamil skin permeation rate achieved by a polymer matrix containing - 10 weight peroent verapamil and 10 weight percent propyl oleate was 20.27 micrograms per ~quare centimeter per hour.
" :
- - . : " . ............ . .:, .
- -.
~27~
Example 14 The procedure of Ex~mple 13 wa~ repeated except oleyl alcohol was utilized as the transport enhancing agent instead of propyl oleate. The verapamil skin permeation rate achieved by a polymer matrix containing 10 weight percent verapamil and 10 weight percent oleyl alcohol wa~ 36.26 microgram~ per ~quare centimeter per hour.
~;
Example 15 The procedure of Example 14 wa~ repeated except n-decylmethylsulfoxide (DMS) was used as the transport enhancing agent instead of oleyl alcohol. The verapamil skin permeation rate achieved by a polymer matrix containing 10 weight percent verapamil and 10 weight percent DMS waq 105.28 microgram~ per square centimeter per hour.
Example 16 The procedure of Example 1 was repeated except mixtures of isopropylmyristate (IPM) and N,N-diethyl-m-toluamide (DEET) were utilized as the tran~portenhancing agent. The re~ulting skin permeation rate~
are li~ted in the ~ollowing table:
Delivery Verapamil Enhancer Concen- Permeation Device Concentration tration (weight Ra~e Number (weight percent) percent) ~g/cm -hr IPM DEET
VPS39 10 10 10 139.55 VP540 10 15 164.04 , :
.
- ' ~
, ' ' . - :
Exam~le 17 A matrix-type transdermal drug delivery device is prepared by intimately blending equal weights of verapamil and N,N-diethyl-m-toluamide after which the mixture is uniformly dispersed in a bioacceptable silicone elastomer. Crosslinking catalyst is then added to the elastomer, th~ catalyzed mixture i~
deaerated, and the deaerated mixture is pressed into thin sheets 0.015 centimeters thick. The resulting sheets are cut into 5 centimeter diameter circles.
One face of each circle is covered with an occlusive backing comprising an aluminum foil/polyester film laminate (3M Company, SCOTCHPAK'~ 1006). A
bioacceptable, amine-resistant silicone adhesive (Dow Corniny X7-2920) containing 20 weight percent N,N-diethyl-m-toluamide intimately blended therewith is applied to the opposite face of the polymer matrix.
The adhesive surface is then covered with a removable polyethylene film having an absorbent open-celled foam layer heat sealed to its inner face and saturated with N,N-diethyl-m-toluamide.
ExamPle 18 Equal amounts of verapamil base and isopropyl myristate were thoroughly mixed using a laboratory agitator at 1000 r.p.m. for three minutes. The resulting co-solvent mixLure was then incorporated into a silicone elastomer (Dow Corning Silastic medical-grade 382~ and mixed for four additional minutes. One drop of catalyst for the silicone elastomer was then added and mixed for another minute. The catalyzed mixture was deaerated under vacuum for five minutes, and the deaerated mixture was pressed into sheets 0.015 centimeters thick to form a microreservolr-type polymer matrix containing 13 weight percent verapamil base and 13 weight percent isopropyl myristate transport --.
.. . . .. . . . .
~7~
enhancing agent. The sheets were cut into 20 square centimeter patches, and the back of each patch was adhered to the center of an occlusive metal foil backing sheet (3M Company) wlth a ~ilicone adhesive (Dow Corning DC 355). The front surface of each patch was covered with a thin layer of silicone adhesive (Dow Corning DC 355) into which 20 weight percent isopropyl myri~tate tran~port enhancing agent had been incorporated. Prior to use of the device, the exposed adhesive surfaces on the face of the polymer matrix and the margins of the backing sheet were temporarily covered with a protective release liner.
In use1 the release liner was stripped away, and from two to four patches were applied to the chest areas of healthy male volunteers 21 to 40 years of age.
In some ca~es the patient's skin was pretreated by contact with an absorbent pad saturated with isopropyl myristate for a few seconds prior to applying the patches. Patches were removed after 24 hours.
Effective transdermal administration of verapamil was confirmed by monitoring the heart rate, blood pressure, respiration and ECG of each patient and by withdrawing and analyzing blood samples ju~t prior to application of the patches and periodically over 48 hours after application of the patches.
The foregoing description and examples have been set forth merely to illustrate the invention and are not intended to be limiting. Since modifications of the deqcribed embodiments incorporating the spirit and substance of the invention may occur to persons skilled in the art~ the scope of the invention is to be limited solely with respect to the appended claims and equivalentq .
.. . . . .
~ .. . . .
- . : .
:
`
Claims (25)
1. A transdermal drug delivery device comprising:
a permeable polymer matrix having an effective cardiovascular affecting amount of 5-[(3,4-dimethoxy-phenethyl) methylamino]-2-(3,4-dimethoxyphenyl)-2-iso-propylvaleronitrile and an effective release promoting amount of a first transport enhancing agent dispersed therein, and a bioacceptable adhesive layer covering one face of said polymer matrix, said adhesive having an effective drug transport promoting amount of a second transport enhancing agent dispersed therein.
a permeable polymer matrix having an effective cardiovascular affecting amount of 5-[(3,4-dimethoxy-phenethyl) methylamino]-2-(3,4-dimethoxyphenyl)-2-iso-propylvaleronitrile and an effective release promoting amount of a first transport enhancing agent dispersed therein, and a bioacceptable adhesive layer covering one face of said polymer matrix, said adhesive having an effective drug transport promoting amount of a second transport enhancing agent dispersed therein.
2. A transdermal drug delivery device as recited in Claim 1, wherein said polymer matrix comprises a silicone elastomer corresponding to the formula:
wherein R represents an alkoxy, alkyl, alkenyl or aryl group containing 1 to 7 carbon atoms and wherein n, m and p are each 100 to 5,000.
wherein R represents an alkoxy, alkyl, alkenyl or aryl group containing 1 to 7 carbon atoms and wherein n, m and p are each 100 to 5,000.
3. A transdermal drug delivery device as recited in Claim 1, wherein said first and second transport enhancing agents are independently selected from the group consisting of lower alkyl esters of saturated and unsaturated fatty acids, mineral oil, dialkylsulfoxides, N,N-dialkylamides, N-alkyl azacyclo ketones, thioglycolate salts, fatty alcohols, saturated and unsaturated fatty acids, glycol monoesters of fatty acids, and fatty acid monoglycerides.
4. A transdermal drug delivery device as recited in Claim 3, wherein said first and second transport enhancing agents are the same.
5. A transdermal drug delivery device as recited in Claim 1, wherein said adhesive has a pH in the range from about 5 to about 7.
6. A transdermal drug delivery device according to Claim 5, wherein the pH of said adhesive is about 6.
7. A transdermal drug delivery device as recited in Claim 1, wherein said adhesive layer comprises from about 1 to about 30 weight percent transport enhancing agent.
8. A transdermal drug delivery device as recited in Claim 7, wherein said adhesive layer comprises from about 5 to about 25 weight percent transport enhancing agent.
9. A transdermal drug delivery device as recited in Claim 1, wherein said second transport enhancing agent comprises isopropyl myristate.
10. A transdermal drug delivery device as recited in Claim 1, wherein said first transport enhancing agent comprises N,N-diethyl-m-toluamide.
11. A transdermal drug delivery device as recited in Claim 1, wherein said adhesive comprises a bioacceptable silicone elastomer.
12. A transdermal drug delivery device comprising a permeable bioacceptable lipophilic polymer matrix having an effective cardiovascular affecting amount of 5-[(3,4-dimethoxy-phenethyl) methylamino]-2-(3,4-dimethoxyphenyl)-2-isopropylvaleronitrile and an effective release promoting amount of a transport enhancing agent dispersed therein.
13. A transdermal drug delivery device as recited in Claim 12 wherein said polymer matrix comprises a silicone elastomer corresponding to the formula:
wherein R represents an alkoxy, alkyl, alkenyl or aryl group containing 1 to 7 carbon atoms and wherein n, m and p are each 100 to 5,000.
wherein R represents an alkoxy, alkyl, alkenyl or aryl group containing 1 to 7 carbon atoms and wherein n, m and p are each 100 to 5,000.
14. A transdermal drug delivery device as recited in Claim 12 wherein said transport enhancing agent is selected from the group consisting of lower alkyl esters of saturated and unsaturated fatty acids, mineral oil, dialkylsulfoxides, N,N-dialkylamides, N-alkyl azacyclo ketones, thioglycolate salts, fatty alcohols, saturated and unsaturated fatty acids, glycol monoesters of fatty acids, and fatty acid mono-glycerides.
15. A transdermal drug delivery device as recited in Claim 14, wherein said transport enhancing agent comprises from about 2 to about 50 weight percent of said polymer matrix.
16. A transdermal drug delivery device as recited in Claim 15, wherein said transport enhancing agent comprises from about 5 to about 30 weight percent of said polymer matrix.
17. A transdermal drug delivery device as recited in Claim 12, wherein said polymer matrix is substantially electroneutral with respect to 5-[3,4-dimethoxyphenethyl)methylamino]-2-(3,4-dimethoxy-phenyl)-2-isopropylvaleronitrile.
18. A unit-dose package comprising a trans-dermal drug delivery device as recited in Claim 12, and means for pretreating the skin of a patient with a skin permeation enhancing agent.
19. A unit-dose package as recited in Claim 18, wherein said skin permeation enhancing agent is selected from the group consisting of lower alkyl esters of saturated and unsaturated fatty acids, mineral oil, dialkylsulfoxides, N,N-dialkylamides, N-alkyl azacyclo ketones, thioglycolate salts, fatty alcohols, saturated and unsaturated fatty acids, glycol monoesters of fatty acids, and fatty acid monoglycerides.
20. A transdermal drug delivery device comprising:
a permeable polymer matrix having an effective cardiovascular affecting amount of 5-[(3,4-dimethoxy-phenethyl) methylamino]-2-(3,4-dimethoxyphenyl)-2-iso-propylvaleronitrile and an effective release promoting amount of a transport enhancing agent dispersed therein, said polymer matrix having one surface disposable adjacent the skin of a patient, and a supply of skin permeation enhancing agent adjacent said one polymer matrix surface such that when said one surface is disposed adjacent a patient 13 skin, the skin is contacted by said skin permeation enhancing agent.
a permeable polymer matrix having an effective cardiovascular affecting amount of 5-[(3,4-dimethoxy-phenethyl) methylamino]-2-(3,4-dimethoxyphenyl)-2-iso-propylvaleronitrile and an effective release promoting amount of a transport enhancing agent dispersed therein, said polymer matrix having one surface disposable adjacent the skin of a patient, and a supply of skin permeation enhancing agent adjacent said one polymer matrix surface such that when said one surface is disposed adjacent a patient 13 skin, the skin is contacted by said skin permeation enhancing agent.
21. A transdermal drug delivery device as recited in Claim 20, wherein an adhesive layer is provided over said one polymer matrix surface to secure the polymer matrix to the skin of a patient.
22. A transdermal drug delivery device as recited in Claim 21, wherein said supply of skin permeation enhancing agent comprises a removable absorbent layer covering said adhesive layer and impregnated with said skin permeation enhancing agent.
23. A transdermal drug delivery device as recited in Claim 20, further comprising an occlusive backing covering the surface of said matrix opposite said surface which is disposable adjacent the skin of a patient.
24. A transdermal drug delivery device as recited in Claim 20 wherein said polymer matrix comprises a silicone elastomer corresponding to the formula:
wherein R represents an alkoxy, alkyl, alkenyl or aryl group containing 1 to 7 carbon atoms and wherein n, m and p are each 100 to 5,000.
wherein R represents an alkoxy, alkyl, alkenyl or aryl group containing 1 to 7 carbon atoms and wherein n, m and p are each 100 to 5,000.
25. A transdermal drug delivery device as recited in Claim 20 wherein said skin permeation enhancing agent is selected from the group consisting of lower alkyl esters of saturated and unsaturated fatty acids, mineral oil, dialkylqulfoxides, N,N-dialkylamides, N-alkyl azacyclo ketones, thioglycolate salts, fatty alcohols, saturated and unsaturated fatty acids, glycol monoesters of fatty acids, and fatty acid monoglycerides.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US751,126 | 1985-07-02 | ||
| US06/751,126 US4690683A (en) | 1985-07-02 | 1985-07-02 | Transdermal varapamil delivery device |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1276111C true CA1276111C (en) | 1990-11-13 |
Family
ID=25020593
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA000512950A Expired - Fee Related CA1276111C (en) | 1985-07-02 | 1986-07-02 | Transdermal verapamil delivery device |
Country Status (7)
| Country | Link |
|---|---|
| US (1) | US4690683A (en) |
| EP (1) | EP0227816A4 (en) |
| JP (1) | JPS63501075A (en) |
| AU (1) | AU586770B2 (en) |
| BR (1) | BR8606754A (en) |
| CA (1) | CA1276111C (en) |
| WO (1) | WO1987000042A1 (en) |
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-
1985
- 1985-07-02 US US06/751,126 patent/US4690683A/en not_active Expired - Fee Related
-
1986
- 1986-06-27 AU AU61245/86A patent/AU586770B2/en not_active Ceased
- 1986-06-27 JP JP61503622A patent/JPS63501075A/en active Pending
- 1986-06-27 EP EP19860904576 patent/EP0227816A4/en not_active Withdrawn
- 1986-06-27 BR BR8606754A patent/BR8606754A/en unknown
- 1986-06-27 WO PCT/US1986/001363 patent/WO1987000042A1/en not_active Application Discontinuation
- 1986-07-02 CA CA000512950A patent/CA1276111C/en not_active Expired - Fee Related
Also Published As
| Publication number | Publication date |
|---|---|
| US4690683A (en) | 1987-09-01 |
| AU6124586A (en) | 1987-01-30 |
| AU586770B2 (en) | 1989-07-20 |
| EP0227816A4 (en) | 1989-06-13 |
| WO1987000042A1 (en) | 1987-01-15 |
| BR8606754A (en) | 1987-10-13 |
| JPS63501075A (en) | 1988-04-21 |
| EP0227816A1 (en) | 1987-07-08 |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| MKLA | Lapsed |