WO1989012470A1

WO1989012470A1 - Subsaturated transdermal delivery device

Info

Publication number: WO1989012470A1
Application number: PCT/US1989/002561
Authority: WO
Inventors: James L. Osborne; Melinda Nelson; David James Enscore; Su Il Yum; Robert M. Gale; Patricia S. Campbell
Original assignee: Alza Corporation
Priority date: 1988-06-14
Filing date: 1989-06-13
Publication date: 1989-12-28
Also published as: NZ229515A; NO302065B1; NO905270L; KR900701328A; DK297690D0; JPH04500322A; PT90820A; AU3852189A; DK297690A; ATE161734T1; JP2933337B2; FI104700B; FI906155A0; EP0427741B1; CA1338700C; DK175805B1; DE68928533T2; EP0427741A1; NO905270D0; IE81102B1

Abstract

Subsaturated, rate controlled delivery devices (1) for delivering an agent (5). The initial equilibrated concentration of the agent in the agent reservoir (3) and the adhesive (5) is below saturation. The initial loading of the agent in reservoir (3) is sufficient to prevent the activity of the agent in the reservoir (3) from decreasing by more than about 75 % and preferably no more than about 25 % during the predetermined period of administration. The thicknesses of the adhesive (5), rate controlling membrane (4) and reservoir (3) layers are selected so that at least 50 % and, preferably at least 75 % of the initial equilibrated agent loading is in the reservoir layer (3). The devices (1) are usable to deliver agents which are liquid at body temperatures such as benzotropine, secoverine, nicotine, arecoline, polyethylene glycol monolaurate, glycerol monolaurate, glycerol monooleate and ethanol, for example.

Description

SUBSATURATED TRANSDE MAL DELIVERY DEVICE

This invention relates to transdermal delivery devices intended to deliver biologically active agents through skin at substantially constant rates for extended periods of time and more particularly to such devices in which the active agent to be delivered is present in the device at a concentration below saturation.

BACKGROUND OF THE INVENTION Transdermal delivery devices for the delivery of a wide variety of biologically active agents have been known for sometime and representative systems are disclosed in U.S. Patents 3,598,122, 3,598,123, 3,742,951, 4,031,894, 4,060,084, 4,144,317, 4,201,211 and 4,379,454 which are incorporated herein by reference. Such devices generally comprise an impermeable backing, a drug or active agent reservoir, a rate controlling membrane and a contact adhesive layer which can be laminated or heat sealed together to produce a transdermal delivery device. Although subsaturated systems are known, see patent 4,379,454, for example, it is generally desirable that the agent reservoir comprise the agent to be delivered in a suitable carrier at a concentration above the saturation concentration in the carrier. This is done to maintain a unit activity source of the agent so that the delivery rate of the agent will remain substantially constant over the intended administration period; the amount of agent originally present over saturation being the depot or reservoir for the dose of agent ultimately delivered. If the concentration of the agent drops below unit activity during the delivery period, the rate of agent delivery will also tend to decrease. It is also generally desirable to minimize the residual agent in the device after use and, to accomplish this, devices normally utilize a carrier, which has a limited solubility for the agent to be delivered. Although such typical devices have been found useful for the delivery of a wide variety of agents, we have encountered significant problems in producing devices intended to deliver an agent which is capable of dissolving or plasticizing medically acceptable contact adhesives. Such agents are usually, but not always, oily, nonpolar materials, liquid at ambient temperatures, and are either solvents for medically acceptable contact adhesives or are highly soluble therein and cause such adhesives to loose their adhesiveness. In the latter case, the agent, may not actually solvate the adhesive but instead plasticize the adhesive and cause it to swell, loose its cohesiveness and adhesiveness, and degrade its other physical properties. As used herein, an agent is a "solvent" for medically acceptable adhesives, and such adhesives are "soluble" in such agents if the agent either dissolves or plasticizes such adhesives as described above. Agents which are such solvents may be drugs, permeation enhancers or other transdermally deliverable substances. Representatives of such agents are drugs such as benztropine base, an anticholinergic useful in the treatment of Parkinsonis , the antispasmolytic drugs secoverine and dexsecoverine, nicotine, useful in the withdrawal from smoking, and arecoline, a cholinergic and anthel intic agent. Representative permeation enhancers include polyethylene glycol monolaurate (PGML), glycerol monolaurate (GML), and glycerol mono.oleate (GMO) and ethanol. Although ethanol is not an oily, nonpolar liquid, it is an example of a material which, in high concentrations, can act as solvent for certain medically acceptable contact adhesives.

Regardless of the initial concentration of the agent in the reservoir and adhesive layers, the devices will equilibrate upon standing. Thus, if the agent is a solvent for the adhesive layer, we have found that substantial quantities migrate from the reservoir through the rate controlling membrane and into the adhesive layer prior to use. The migration will continue until the thermodynamic activity of the agent in the adhesive equals the activity of the agent in the reservoir. Thus, a substantial amount of agent can migrate into the adhesive layer and will be released onto the skin in an uncontrolled manner before the rate controlling membrane can exert any effect on the agent remaining in the reservoir. Also, high concentrations of agent in the adhesive layer and in direct contact with the skin may cause irritation or produce undesirably high plasma levels during the initial period after application to the skin and prior to depletion of the initial loading of agent in the contact adhesive layer. In addition to the deleterious effects on a patient that may be caused by high concentrations of agent in the adhesive, certain adhesives tend to lose their adhesive properties when they are dissolved or plasticized by the agent being delivered.

According to our invention we have provided a rate controlled, subsaturated transdermal delivery device having an in-line adhesive which delivers an agent which is a solvent for the in-line adhesive and which exhibits improved release characteristics. In certain embodiments of our invention a substantially constant release rate over a substantial portion of a predetermined administration period can be obtained. The device utilizes a subsaturated reservoir containing a sufficient amount of agent to prevent the activity from decreasing by more than about 75% and preferably no more than about 25% during the predetermined delivery period. The device is also preferably designed such that no mαre.-than, and preferably substantially less than, half of the total agent loading in the device is in the adhesive and rate controlling membrane layers after equilibration and prior to use. Preferred embodiments of our invention are rate-controlled drug delivery devices having in-line adhesives for the controlled delivery of drugs which are solvent for the in-line adhesive such as the smoke cessation aid, nicotine, the anticholinergic, benztropine, and the tertiary amine secoverine, l-cyclohexyl-4-C[ethyl (p-methoxy- alpha-methylphenylethyl) aminoj-butazone, an anti-spasmodic agent described in U.S. Patents 3,996,245 and 4,125,623 which are incorporated herein by reference. The active, (d) isomer of secoverine is hereinafter referred to as "dexsecoverine".

Other preferred embodiments can be used to deliver drugs in connection with permeation enhancers such as ethanol, PGML, GML and GMO for example. Attempts to produce transdermal delivery devices for these agents and enhancers by following the aforementioned teachings of the prior art were unsuccessful based on a combination of the above considerations. It is also expected that similar problems will be encountered with respect to other agents which are solvents for medical adhesives and this invention will have utility with such other agents. It is accordingly an object of this invention to provide a rate controlled transdermal delivery device having an in-line adhesive and a subsaturated agent reservoir which device exhibits improved agent release rate characteristics. It is another object of this invention to provide a transdermal delivery device for the delivery of agents which are solvents (as defined herein) for in-line adhesives.

It is another object of this invention to improve the delivery characteristics of a rate-controlled, transdermal delivery device utilizing a subsaturated agent reservoir.

These and other objects of the invention will be readily apparent from the following description with reference to the accompanying drawings wherein:

Figure 1 is a cross section through an embodiment of the trans- dermal delivery devices according to this invention;

Figure 2 is a cross section through another embodiment of a

'^"'fI transdermal delivery device according to this invention;

Figures 3, 5 ,6 and 7 are p ots of in vitro release rates directly into a sink at 32#C (Figιμ^v3) or 35#C (Figs 5,6 & 7) vs. time for embodiments of this invention; and

Figure 4 compares plots of its in vitro release rates at 32#C directly into a sink vs. time with the in vitro flux at 32#C through human cadaver skin into a sink vs. time obtained from an embodiment of this invention.

DESCRIPTION OF THE INVENTION

Referring now to Figures 1 and 2 (like reference numerals referring to common elements), transdermal delivery devices 1 and 10 according to this invention are shown. Devices 1 and 10 are formed of an impermeable backing 2, an agent reservoir 3, an agent release rate controlling membrane 4, a contact adhesive 5 permeable to the agent, and a release liner 6 adapted to be removed from the adhesive layer prior to application to the skin of the subject to whom the agent is to be administered. As noted above, the agent to be delivered is a solvent for the adhesive forming the adhesive layer 5. In this regard, the reservoir may contain more than one agent according to this invention provided that at least one of the agents is a solvent for the adhesive. Typically, one of the agents could be a drug and another agent could be a permeation enhancer or another drug, for example. The embodiments of Figures 1 and 2 differ in that the agent reservoir 3 of the embodiment of Figure 1 is less viscous than the reservoir 3 of Figure 2 such that the impermeable backing 2 is bonded at its periphery to the rate controlling membrane 4 to form a pouch fully enclosing reservoir 3 to prevent it from flowing or oozing. In the embodiment of Figure 2 the reservoir 3 has sufficient viscosity to maintain its structural integrity without a peripheral or circumferential seal. Although Figures 1 and 2 relate to laminated devices, other arrangements of the adhesive, reservoir and rate controlling membranes are usable and include, for example, an adhesive having microcapsules of the agent within a rate controlling membrane dispersed therethrough as shown in aforemen¬ tioned patent No. 3,598,123.

According to this invention, transdermal delivery devices 1 and 10 are intended to be applied to a patient for a predetermined administration period, typically from about 1-7 days. During the administration period it would be desirable to control the amount of agent that is released from the device so that the agent can be administered to the patient in a predetermined and controlled manner. The in vitro agent release rate or flux from a transdermal delivery device directly into an infinite sink as a function of time can be considered to consist of two phases, a first, initial "transient" phase, and a second, subsequent "steady-state" delivery phase. During the initial transient phase, the agent is released at a high rate as a result of the initial loading of the agent in the adhesive and rate controlling membrane layers 5 and 4, respectively. This initial pulse release decreases relatively rapidly as a function of t^{*1 2} until the initial loading of agent in the adhesive layer is depleted and the "steady-state" phase in which agent is being delivered from reservoir 3 commences. t_ss shown in Figure 5 and 6 represents the time at which the initial transient phase ends and the steady state delivery phase commences. The variation of release rate with time during the steady-state phase depends on the structure of the device. Simple monoliths of the prior art exhibit a theoretical variation of release rate as a function of t^{'1 2}, whereas prior art devices having unit activity reservoirs and release rate-controlling membranes exhibit theoretical release rates that vary with t°, i . e. , they remain constant. Devices according to this invention exhibit a theoretical release rate which varies as a function of tⁿ where - = n ^* 0 and preferred embodiments exhibit in vitro release rates which approach those obtained from zero order devices. According to preferred embodiments of this invention, the steady-state in vitro release rate can be maintained substantially constant from the termination of the initial transient phase until the expiration of the predetermined administration period. As used herein, the in vitro agent delivery rate is considered to be

"substantially constant" if the steady-state rate does not vary more than about ±50%, and preferably no more than ±25%, during the steady state administration period.

As used herein, the term "agent" is used in its broadest sense to mean any material which is to be delivered into the body of a human or animal to produce a beneficial, therapeutic or other intended effect, such as permeation enhancement, for example, and is not limited tσ drugs and pharmaceutical products. The maximum allowable concentration of the agent in the adhesive will be determined by such factors as the agent concentration at which the adhesive properties are impaired, the agent concentration at which irritation problems or unacceptably high initial transdermal agent fluxes, for example, are observed. When such undesirable effects occur, it is necessary that the initial activity of the agent in the adhesive be at a lower level. Because the device will equilibrate on standing, the activity (but not necessarily the concentration) of the agent in the adhesive will ultimately be the same as the activity of the agent in the reservoir layer.

Transdermal delivery devices, according to our invention, have the following characteristics:

1. The devices utilize an in-line adhesive to maintain the device on the skin;

2. The agent to be delivered is a solvent for the in-line adhesive;

3. The initial equilibrated concentration of the agent in the reservoir 3 and the adhesive 5 is below saturation, expressed alter¬ natively, the activity is less than 1.0; 4. The reservoir 3 comprises the agent dissolved in a diluent with respect to which rate controlling membrane 4 is substantially impermeable;

5. In preferred embodiments the initial loading of the agent in reservoir 3 is sufficient to prevent the activity of the agent in the reservoir from decreasing by more than about 75% and preferably no more than about 25% during the predetermined period of administration; and

6. In preferred embodiments the thicknesses of the adhesive, rate controlling membrane and reservoir layers are selected so that at least 50% and, preferably at least 75% of the initial equilibrated agent loading is in the reservoir layer.

To design a system according to our invention, the permeability of skin to the agent to be delivered, the amount of agent required to saturate the agent binding sites in the skin, the maximum activity of agent in the adhesive layer that can be tolerated without loss of adhesive properties and without producing undesirable initial drug pulses, skin irritation or undesirable sensations would be determined by suitable in vitro and in vivo tests. Having determined the maximum allowable activity of agent in the adhesive; a somewhat lower initial activity would typically be employed to provide for a factor of safety. In some instances, such as in the initial administration of the agent or where intermittent, as opposed to continuous, delivery periods are prescribed, the initial loading of agent in the adhesive layer 5 and rate controlling membrane 4 may correspond approximately to the amount of agent needed to saturate the agent binding sites in the skin below the delivery device.

In preferred embodiments the equilibrated agent loading in the reservoir layer 3 is selected to be sufficient to enable the total dose of agent delivered during the predetermined administration period to be delivered while maintaining the decrease in activity of the agent in the non-permeating solvent forming reservoir 3 within the limits noted above. The total loading of agent in each layer of the device can be readily varied without changing the activity simply by increasing or decreasing the thickness of the adhesive layer 5 and/or reservoir layer 3, and also by appropriate selection of the total surface area of the device through which agent is delivered. Because the rate controlling membrane can only act as a release rate limiting element on agent which is in the reservoir; the reservoir thickness should be selected, with respect to the thicknesses of the rate controlling membrane and the adhesive layers, such that at least half, and preferably substantially more, of the initial equilibrated agent loading is in the reservoir.

The rate-controlling membrane 4 would be selected such that the flux of the agent through the membrane into an infinite sink is pre¬ ferably no greater than the in vitro flux of the agent through skin (which would produce about 50% device control) and preferably substantially less. If the skin flux is greater than the membrane flux by a factor of about 2.4, for example, approximately 70% of the rate control is obtained from the device. Suitable materials from which the various layers of the device according to this invention can be made are known to the art and many are described in the aforementioned U.S. patents.

Having thus generally described our invention, the following description and examples will illustrate how variations of the above described parameters affect the administration of the agent. Device according to our invention can be used for the transdermal administration of nicotine to skin or mucosa. The following calculations can be used to estimate the characteristics required for such a transdermal nicotine delivery device.

Studies with nicotine releasing gum (Nicorette\), have determined that the target blood level of nicotine for reducing the urge to smoke is approximately 12-15 nanograms/ml and that the clearance of nicotine from the body occurs at about 18 ml/min-kg. In order to deliver adequate amounts of nicotine from a reasonably sized system, the target steady-state in vivo delivery rates are within the range of 250-4000 lg/hr with a typical rate being about 1000 lg/hr. This range can be readily achieved according to our invention in a rate controlled device having a size in the range of about 5-50 cm² and typically about 15-20 cm². A one day delivery period can readily be obtained from subsaturated devices of this invention, and administration periods of at least 8-10 hours and up to about 3 days can be attained by varying the thickness of the reservoir.

An alternate embodiment of this invention would be a system capable of providing nicotine delivery for 16 hours to be applied each day upon waking, worn all day, and removed and discarded just prior to sleep. This would be repeated for as long as nicotine delivery is desired.

Total nicotine loading in a transdermal delivery device of this invention is preferably at least about 50 mg with the equilibrated concentration of nicotine in the reservoir composition being within the range of 5-50 wt%, corresponding to an activity within the range of 0.05-0.50. Reaction of the skin to nicotine is flux dependent

_'"'l and to minimize skin reaction and it is preferred to maintain the flux below about 200 lg/cm²-hr and preferab;] Vbelow 120 lg/cm²-hr in the steady state phase. Typically the fljux will be in the range of about 30 to 70 lg/cm²-hr. ^'<

The equilibrated nicotine loading in the reservoir layer is preferably selected to be sufficient to enable the total dose of nicotine delivered during the predetermined administration period to be delivered while maintaining the decrease in activity of the nicotine in the reservoir the limits noted above. The total loading of nicotine in each layer of the device can be readily varied without changing the activity, simply by increasing or decreasing the thickness of the adhesive layer and/or reservoir layer and also by appropriate selection of the total surface area of the device through which nicotine is delivered. Because the rate controlling membrane can only act as a release rate limiting element on the nicotine which is in the reservoir, the reservoir thickness should be selected with respect to the thicknesses of the rate controlling membrane and the adhesive layers, such that at least half, and preferably substantially more, of the initial equilibrated nicotine loading is in the reservoir.

The preferred embodiments of this invention utilize an anhydrous reservoir formed of natural or synthetic rubbers or polymers as known to the art. When an ethylene/vinyl acetate copolymer (EVA) is selected it has a preferably VA content in the range of about 28-60% by wt.

The rate controlling membrane may be of a dense polymer film that has the requisite permeability to nicotine. The membrane material would be selected such that the flux of the nicotine through the membrane into a sink is preferably no greater than the in in vitro flux of nicotine across skin (which would produce about 50% system control) and preferably substantially less. The fractional control of nicotine delivered across skin (x) from the rate controlled transdermal therapeutic system of this invention is given by the following relationship: v - J / J net system which can be determined from the following equation:

Jnet 'Jsystem = [ Jsystem Λlskin] + 1 ]

Thus, if the skin flux is greater than the membrane or system flux by a factor of about 2.4, for example, the fractional control of nicotine flux from the system would be:

Jnet ^jsystem = [ (1/2.4) + 1 ] ^_1 = 0.7

Therefore, approximately 70% of the rate control is obtained from the system. The flux of nicotine through skin varies somewhat from individual to individual and from body site to body site but generally appears to be in the range of about 400-800 lg/cm²/hr. Preferably the rate controlling membrane is substantially impermeable to the diluent in which the nicotine in the reservoir is dissolved, although a low permeability to the diluent may not abversely affect the operation of the device. Examples of the types of polymer films that may be used to make the membrane 16 are disclosed in U.S. Pat. Nos. 3,797,494 and 4,031,894, both of which are incorporated herein by reference. Particularly suitable materials for use with the mixture are (EVA), low density polyethylene (LDPE) and high density polyethylene (HDPE). The composition and thickness of the adhesive layer is selected so as not to constitute a significant permeation barrier to the passage of nicotine. The adhesive material is selected from known materials having a high permeability to nicotine which is also such that it is compatible with nicotine at the activity chosen for the system. Amine resistant silicone adhesives are particularly suitable. These compounds may be modified with silicone oil to obtain the desired tack.

EXAMPLE 1 Transdermal delivery devices for the controlled delivery of nicotine were prepared utilizing a highly permeable, amine resistant adhesive available from Dow Corning (X7-2920), LDPE as the rate controlling membrane, EVA (40% VA) as the non-diffusible drug reservoir diluent, pigmented medium density polyethylene/aluminized polyester as the impermeable backing member and nicotine base as the source of nicotine. The devices had 4 mil LDPE rate controlling membranes, 6 mil drug reservoirs containing either 20 or 25 weight percent nicotine base and a 2 mil adhesive layer. The in vitro fluxes of drug from these subsaturated transdermal nicotine devices through cadaver skin i to aqueous sink at 35#C were determined and are shown in Table I. Nicotine flux data across skin was obtained from averaging the data generated by devices tested on two different skin donors ,

TABLE I

Drug Flux with Drug Flux with

Time 20 wt% drug 25 wt% drug l (lα/cm²-hr) (lq/cm²-hr

2 87.9 133.2

4 65.8 104.6

6 tss 52.6 85.0

8 47.5 73.2

23.25 33.4 52.8 27.25 27.9 45.2 30.75 23.1 40.3

EXAMPLE II Subsaturated nicotine transdermal delivery devices (1 cm²) were fabricated having a nicotine loading of about 5 lg/cm² comprising a 30 wt% nicotine/70 wt% EVA 40 reservoir composition (0.30 nicotine activity), a 2 mil rate controlling membrane and a 2 mil amine resistant adhesive layer (Dow Corning X7-2920 with 5 wt% silicone fluid). The in vitro release rate at 35#C directly into an aqueous sink is shown in Figure 3. A device according to this example having a surface area of about 20 cm² applied to human subjects on a daily basis, should provide transdermal delivery of nicotine at administration rates sufficient to assist in the cessation of smoking.

The previous examples related to nicotine delivery devices; the following examples illustrate embodiments of this invention for transdermally administering other agents.

Secoverine normally exists as a racemic mixture of d and 1- isomers, the d-isomer, dexsecoverine, being the biologically active ingredient. We have determined that dexsecoverine diffuses through normal skin at substantially the same rate as the racemic mixture and therefore, if dexsecoverine is used as the agent in the reservoir, the agent flux through the skin need be only about one half that which would otherwise be required if racemic secoverine were delivered. EXAMPLE III Transdermal delivery devices for the controlled delivery of dexsecoverine were prepared utilizing Dow Corning DC 355 silicone adhesive as the highly permeable medical adhesive, EVA (9% VA) as the rate controlling membrane, EVA (40% VA) as the non-diffusible drug reservoir diluent, pigmented medium density polyethylene/aluminized polyester as the impermeable backing member and racemic secoverine or dexsecoverine as the source of dexsecoverine. Secoverine and dexsecoverine are extremely soluble (essentially miscible) in the EVA (40% VA) diluent and thus the weight percent concentration in the diluent corresponds approximately to the thermodynamic activity. Secoverine and dexsecoverine are solvents for the adhesive and form solutions therewith at concentrations of 300 mg/cm³ or more. Adverse effects on adhesive properties have been observed when agent concentration reached about 50 mg/cm³.

Thus, according to the preferred dexsecoverine delivering embodiments of this invention, it is desirable to maintain the agent concentration in the adhesive below about 45 mg/cm³ which corresponds to an activity of about 0.15 in the drug reservoir and the adhesive layers. The thicknesses of the adhesive and rate controlling layers in the subsaturated system were selected to provide an initial pulse of about 225 ug/cm² to saturate the agent binding sites in the skin, the contribution to the pulse of each such layer being dependent on the thickness of the layer and the solubility of the agent in each layer. A thicker layer would provide a higher initial pulse and a thinner layer would provide a smaller initial pulse for the same initial activity. One or 1.3 mil LDPE and 2 or 4 mil EVA (9% VA) rate control membranes were utilized in the preferred embodiments and drug reservoirs of approximately 5-20 mils were tested. A 5 mil thickness was sufficient to prevent the activity of the agent in the reservoir 3 from decreasing by more than 30% during a four-day administration period. The in vitro release rates of various subsaturated dexsecoverine systems are compared to the characteristics for unit activity systems in Table II. In Figure 4 the upper group of curves shows the in vitro release rates at 32#C vs. time in hours directly into an aqueous sink and the lower group curves show the flux through cadaver skin at 32#C vs. time in hours into an aqueous sink from racemic secoverine systems and illustrate the effect of varying reservoir thicknesses on in vitro release rates and flux.

TABLE II

Druα Source Dexsecoverine Secoverine

Drug Activity 1.00 0.06 0.15 0.10 0.20 0.20 0.20

Membrane LDPE EVA LDPE EVA LDPE LDPE LDPE (9%VA) (9%VA)

Membrane Thickness (mils) 1.0 4.0 1.0 2.0 1.3 1.3 1.3

Adhesive Thickness (mils) 1.7 1.8 1.7 1.4 1.7 1.7 1.7

Reservoir Thickness (mils) 5 5.0 5.0 5.0 20.0 10.0 5.0

Initial Burst (ug/cm²) : from membrane 170 142 26 118 from adhesive 1325 84 199 109

Total 1495 226 225 227

Avg. Steady State In vitro Release Rate at 32#C (lcg/cm²/hr)

57 3.5 8.2 22 Range (over 24-96 hr) 60-54 7.5-5.5 10-7 24-18

We have determined that to achieve anti-spasmodic activity from the continuous transdermal administration of secoverine, approximately 1 to 10 nanograms/ml of dexsecoverine should be maintained in the plasma. We have also discovered that the permeability of average human skin when exposed to unit activity sources of either secoverine or dexsecoverine appears to be in the range of approximately 20 to 60 ug/cm²/hr. In order to deliver adequate amounts of a drug from a reasonably sized system, a target steady-state in vivo delivery rate of dexsecoverine from 10-40 ug/hr was selected which rate can be readily achieved according to our invention in a rate controlled device of reasonable size of from about 5 to 60 cm². Delivery periods of about 3-5 days can be obtained from subsaturated devices of Table 2, and administration periods up to about 7 days can be attained by increasing the thickness of the reservoir to about 10 mils.

EXAMPLE IV

Subsaturated transdermal delivery devices similar to those of Example III, but intended to deliver benztropine base are fabricated having an agent reservoir diluent of EVA (40% VA), and a 1 mil LDPE rate-controlling membrane. Benztropine base is soluble to about 650 mg/g of EVA (40% VA). 2.5 cm² devices are fabricated using a highly permeable, amine resistant silicone adhesive available from Dow Corning, (X7-2920) or polyisobutylene/mineral oil adhesives, an impermeable backing, and an 8 mil-thick reservoir layer having an initial benzotropine loading of 5, 10, and 20 weight percent equivalent to activities of 0.125, 0.25, and 0.5. The approximate in vitro release rates directly into an aqueous bath at 32-35#C to be obtained from such devices, using 1 mil LDPE rate-controlling membranes, are illustrated in Figure 5. The effect of using a 2-mil LDPE rate-controlling membrane is illustrated in Figure 6.

The permeability of average skin to benztropine is in the range of 70 to 90 ug/cm² hr and systems as described above can deliver benztropine in vivo at therapeutically useful rates of 10 to 40 ug/hr. The size of the device can be selected to provide daily doses of about 0.4 to 4.5 mg for up to 4 days.

EXAMPLE V

Benztropine transdermal delivery devices for use in clinical testing were fabricated as set forth generally in Example IV from a 10% benztropine in 90% EVA 40 reservoir composition into 5 cm² patches using 1.5 mil LDPE rate controlling membranes and 1.8 mil amine resistant adhesive layers. With a 5 mil reservoir layer the devices contained about 5.4 mg of benztropine and are intended for a 24 hour administration period. The in vitro release rate vs. time at 32#C into an aqueous sink is shown in Figure 7. When applied to human subjects on a daily basis, anticholinergically effective transdermal delivery of benztropine can be obtained.

Having thus generally described our invention and preferred embodiments thereof, it is apparent that various modifications and substitutions will be apparent to workers skilled in the art, which can be made without departing from the scope of our invention which is limited only by the following claims wherein:

Claims

We cl aim:

1. A medical device utilizing an in-line adhesive for 2 the transdermal administration of an agent, said device comprising, in combination: 4 a. an agent reservoir comprising said agent dissolved in a diluent at a concentration less than saturation 6 and at an initial equilibrated agent loading sufficient to prevent the activity of said agent in said diluent from 8 decreasing by more than 75% during said administration period; b. agent release rate controlling means disposed in 10 the path of agent migration from said reservoir to the skin, said rate controlling means being permeable to said agent and 12 substantially impermeable to said diluent; and c. adhesive means disposed in the path of agent

14 migration from said release rate controlling means to the skin, said adhesive being soluble in said agent.

2. The device of claims 1 wherein at least 50% of the 2 initial loading of the agent in the device is in the agent reservoir.

3. The device of claims 1 or 2 wherein said decrease in 2 activity is no greater than about 25%.

4. The device of claim 3, wherein at least 75% of 2 the initial agent loading is in the reservoir.

5. The device of claims 1,2, or 3 wherein said agent is 2 an oily, non-polar material, liquid at body temperature.

6. The device of claim 5 wherein said reservoir

2 contains more than one agent at least one of which is an oily, nonpolar material, liquid at body temperature.

7. The device of claim 1 wherein said agent solubilizes 2 said adhesive.

8. The device of claim 1 wherein said agent plasticizes 2 said adhesive.

9. The device of claim 1 wherein said agent is selected 2 from the group consisting of ethanol, polyethylene glycol monolaurate, glycerol monolaurate, glycerol onooleate, nicotine, arecoliπe, secoverine, dexsecoverine and benztropine.

10. The device of claims 1,2 or 4 when said agent is selected from the group consisting of nicotine, dexsecoverine and benztropine.

11. The device of claim 10 wherein the agent is dexsecoverine and the source of dexsecoverine is substantially free of the 1-isomer. -

12. The device of claim 10 when the agent is dexsecoverine and the source of dexsecoverine is racemic secoverine.

13. The device of claim 10 wherein the diluent for said agent is an ethylene vinyl acetate copolymer.

14. The device of claim 10 wherein said release rate controlling membrane is selected from the group consisting of low density polyethylene, high density polyethylene and ethylene vinyl acetate copolymers.

15. The device of claim 13 wherein said release rate controlling membrane is selected from the group consisting of low density polyethylene, high density polyethylene and ethylene vinyl acetate copolymers.

16. The device of claim 10 wherein wherein the initial equilibrated thermodynamic activity of agent in said reservoir and adhesive layers is no greater than about 0.50.

17. The device of claim 10 wherein said agent is nicotine and the nicotine is administered through human skin at a flux within the range of from about 35-200 lg/cm²/hr for a substantial portion of said administration period.

18. The device of claim 10, wherein the agent is nicotine and nicotine is administered transdermally from said device at an administration rate of approximately 250-4000 lg/hr for a substantial portion of said extended period of time.

19. The device of claim 10 wherein said reservoir contains sufficient agent to administer said agent at said predetermined rate for extended period of time of at least about 8 hours.

20. The device of claim 10 wherein said reservoir comprises 5-50 wt% nicotine and 50-95 wt% ethylene vinyl acetate copolymer having a vinyl acetate content in the range of 28-60%.

21. The device of claim 20 wherein said device contains sufficient nicotine to administer nicotine through human skin at an administered rate of 35-200 lg/cm²-hr for at least about 24 hours.

22. The device of claim 21 wherein said rate controlling means is selected from the group consisting of low density polyethylene, high density polyethylene and ethylene vinyl acetate copolymers.