CA2145631C - Two-phase matrix for sustained release drug delivery device - Google Patents
Two-phase matrix for sustained release drug delivery device Download PDFInfo
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- CA2145631C CA2145631C CA002145631A CA2145631A CA2145631C CA 2145631 C CA2145631 C CA 2145631C CA 002145631 A CA002145631 A CA 002145631A CA 2145631 A CA2145631 A CA 2145631A CA 2145631 C CA2145631 C CA 2145631C
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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
- A61K9/7053—Transdermal patches of the drug-in-adhesive type, i.e. comprising drug in the skin-adhesive layer the adhesive comprising macromolecular compounds obtained by reactions only involving carbon to carbon unsaturated bonds, e.g. polyvinyl, polyisobutylene, polystyrene
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- 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
- A61K31/33—Heterocyclic compounds
- A61K31/38—Heterocyclic compounds having sulfur as a ring hetero atom
-
- 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
- A61K31/33—Heterocyclic compounds
- A61K31/395—Heterocyclic compounds having nitrogen as a ring hetero atom, e.g. guanethidine or rifamycins
- A61K31/55—Heterocyclic compounds having nitrogen as a ring hetero atom, e.g. guanethidine or rifamycins having seven-membered rings, e.g. azelastine, pentylenetetrazole
-
- 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
- A61K9/14—Particulate form, e.g. powders, Processes for size reducing of pure drugs or the resulting products, Pure drug nanoparticles
- A61K9/141—Intimate drug-carrier mixtures characterised by the carrier, e.g. ordered mixtures, adsorbates, solid solutions, eutectica, co-dried, co-solubilised, co-kneaded, co-milled, co-ground products, co-precipitates, co-evaporates, co-extrudates, co-melts; Drug nanoparticles with adsorbed surface modifiers
- A61K9/143—Intimate drug-carrier mixtures characterised by the carrier, e.g. ordered mixtures, adsorbates, solid solutions, eutectica, co-dried, co-solubilised, co-kneaded, co-milled, co-ground products, co-precipitates, co-evaporates, co-extrudates, co-melts; Drug nanoparticles with adsorbed surface modifiers with inorganic compounds
-
- 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
- A61K9/7053—Transdermal patches of the drug-in-adhesive type, i.e. comprising drug in the skin-adhesive layer the adhesive comprising macromolecular compounds obtained by reactions only involving carbon to carbon unsaturated bonds, e.g. polyvinyl, polyisobutylene, polystyrene
- A61K9/7061—Polyacrylates
-
- 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
Abstract
A two-phase hydrophilic drug-containing matrix for use in transdermal drug delivery patches (10) in which one phase is a continuous hydrophobic polymer phase which optionally includes a hydrophobic solvent that acts as a skin permeation enhancer and the other phase is a dispersed particulate hydrated inorganic silicate in whose absorbed aqueous phase the drug is dissolved.
A simple transdermal patch structure (10) contains a backing layer (11), a matrix layer (12) and a release liner layer (13) as com-ponents.
A simple transdermal patch structure (10) contains a backing layer (11), a matrix layer (12) and a release liner layer (13) as com-ponents.
Description
~ - PCT/US93/09510 _. '. ,: g- ~- , .
-1= = ...
TWO-PHASE MATRIX FOR SUSTAINED RELEASE
DRUG DELIVERY DEVICE
Descri tp ion Technical Field The present invention is in the field of controlled or sustained release drug formulations and relates specifically to a two-phase drug-containing matrix that may be used as a component in a transdermal patch. -$ackg~round _ _ In general there are two types of transdermal 2o patch designs: a "reservoir" type and a matrix" type.
In the reservoir type the drug, typically in fluid form, is contained within a walled reservoir whose basal surface is permeable to the drug. In the matrix type the -drug is dispersed in a polymer layer, typically an adhesive, and the matrix directly contacts the skin Both types of device also typically include a backing layer and an inner release liner layer that is removed prior to use.
The present invention concerns a matrix-type 3o device in which the matrix includes a particulate hydrated hydrophilic material that contains the drug and defines at least a portion of the basal surface area of ' the matrix.
WO 94/07468 - P~./US93/0951(~' Several prior patents describe two-phase matrixes used in transdermal drug devices, but all are distinct from the matrixes of the present invention.
U.S. 4,568,232 describes a matrix for a transdermal patch which comprises.a water-insoluble adhesive, drug that is soluble in the adhesive, and a water-swellable polymer. The inclusion of the water-swellable polymer is alleged to increase the release rate of drug from the matrix.
EPA 0391172 describes a transdermal patch having a matrix composed of a water-insoluble material that contains islands of a solid solution of drug in a water-soluble/swellable polymer and an underlayer that controls the amount of water vapor passing from the skin to the matrix. The matrix is said to be activated by water vapor from the skin.
U.S. 4,559,222 describes a transdermal matrix-type patch in which the matrix is composed of a mixture of mineral oil,~polyisobutylene (an adhesive), and colloidal silicon dioxide. The addition of the silicon dioxide allegedly affects the flow characteristics of the mineral oil-polyisobutylene mix.
U.S. 5,071,657 describes a transdermal patch matrix of a drug-containing gel that is dispersed in a cross-linked silicone polymer. This matrix is apparently not adhesive as the patent teaches the use of a separate peripheral adhesive layer to affix the patch to the skin.
EPA 0452837A2 describes an adhesive matrix composed of a hydrophobic polymer, a hydrophilic drug, a hydrophilic swellable polymer, water, and a permeation enhancer. The water is said to act as a solubilizer for the drug and the hydrophilic swellable polymer acts to facilitate the mixing of the ingredients and improve the ' stability of the matrix.
-:
2~~~~~~ -. PCT/LJS93/09510 -3- - = -The invention provides a novel matrix composed of a continuous hydrophobic domain and a dispersed particulate hydrated silicate domain which may be used to administer hydrophilic drugs in a sustained manner. The invention permits hydrophilic drugs to be effectively dispersed in a hydrophobic phase, maintains separation of the drug from the hydrophobic phase so that potential interaction between the two is reduced, and provides enhanced release of hydrophilic drugs from matrixes l0 composed of a continuous hydrophobic domain.
n1 ~r~ osure of the In-vention One aspect of the invention is a sustained-release drug formulation comprising a matrix of:
(a) a continuous hydrophobic polymer phase;
-- (b) a particulate phase dispersed in the -continuous polymer phase comprised of: -(i) a hydrated inorganic silicate;
(ii) a water-solubilizable drug at least partly dissolvQd in the aqueous phase of (i); and (c) a dispersing agent for dispersing (b) in (a) . -wherein the particulate phase defines at least a portion of the surface area of the matrix and provides a diffusion pathway for .the drug in the matrix. -Another aspect of the invention is a transdermal patch comprising a laminated composite of:
(a) a backing layer; and -(b) a layer of the above-described matrix wherein the continuous hydrophobic polymer phase is a pressure sensitive adhesive.
Still another aspect of the invention is a matrix of (a) a continuous hydrophobic polymer phase;
-WO 94/07468 _ ~ ~ ~ '- _ . .~ ~~/US93/09510 (b) a particulate phase dispersed in the continuous polymer phase comprised af:
w a hydrated inorganic silicate and an aqueous phase; and (c) a dispersing agent for dispersing (b) in (a) wherein the particulate phase defines at least a portion of the surface area of the matrix and provides a diffusion pathway in the matrix for an active ingredient that can be water-solubilized.
Still another aspect of the invention is a process for preparing the above described sustained release drug formulation which comprises:
(1) solubilizing on water-solubilizable drug in a liquid aqueous medium;
(2) combining the solubilized drug with the aqueous medium with a hydrated inorganic silicate source;
(3) dispersing the product of step (2) with a hydrophobic polymer and optionally a surfactant to form a 2o dispersion; and optionally (4) applying the dispersion of step (3) to a backing; and (5) removing excess liquid aqueous medium.
Brief Description of the Drawing The drawing is a cross-sectional view (not to scale) of a transdermal patch that includes the matrix formulation of the invention.
As used herein with respect to the continuous phase, the term "hydrophobic°' intends that the material is less than 20$ by weight soluble in water at 32°C, over 24 hr.
21456~~
-5- ~ - ~- . F-_. r_ , _, , ;> - . _ As used herein, the term 'substantially ~ _ insoluble' intends a solubility of less than about 1% by weight, more usually less than about 0.5% by weight.
As used herein the term "continuous" intends a phase that is interconnected and not separated into distinct domains, segments, or particles.
As used herein with respect to the drug, the terms 'hydrophilic" and "water soluble" are intended to be synonymous and to denote that the drug has a water solubility of at least about 0.1 mg/L, preferably at least about 1 mg/L at 32C. -The term "hydrated" intends that the dispersed particulate material comprises all or a portion of its total absorptive capacity of absorbed aqueous phase (i.e.
water and/or other polar solvent). -The term "sustained release" intends a formulation that is capable of releasing a therapeutically effective amount of drug over a time period of one to seven days. __ 2o The material that constitutes the continuous -phase or hydrophobic domain of the matrix is a hydrophobic polymer that is capable of being mixed with the other components of the matrix and formed into a layer or film. When the matrix is used as the drug-containing matrix of a transdermal patch, the hydrophobic polymer preferably has pressure-sensitive adhesive properties that permit the matrix to adhere to living human skin for a sustained period of time, i.e., usually at least about one to seven days. Because the polymer is hydrophobic, the drug is substantially insoluble and immiscible in the polymer. Specific examples of polymers that may be used as the continuous hydrophobic phase of the matrix are polysiloxanes, polyisobutylene, solvent-based hydrophobic polyacrylates, polyurethanes, ' 35 plasticized ethylene-vinyl acetate copolymers, low W~ 94/07468 ~ . - ~ - ~ -. PCT/US93/09510~' . .4 -6_ ~14~~3~.
molecular weight polyether block amide copolymers, styrene-butadiene polymers, and vinyl acetate-based adhesives. The hydrophobic polymer will normally constitute about 30~ to 95~.by weight of the matrix, more usually 40~ to SO$ by weight. Other hydrophobic materials such as solvents or permeation enhancers may be , included in the hydrophobic domain of the matrix.
Examples of such materials are fatty acids (oleic and stearic acid), isopropyl myristate (IPM), fatty acid esters (e. g., propylene glycol monolaurate, polyethylene glycol monolaurate (PEGML), methyl oleate, oleyl oleate), fatty alcohols (e. g., oleyl alcohol), and terpenoids (limonene, menthol, ~-pinene, and geraniol).
The dispersed inorganic silicate is in the form of particles that are typically in the non-colloidal size range of 0.001 to 0.1 mm (largest dimension), more usually 0.01 to 0.05 mm. In its hydrated form the material will normally contain about 15~ to 600 of its - own weight in absorbed water, more usually look to of its own weight in water (measured at 25°C). Other hydrophilic polar solvents such as ethanol, propylene glycol, low molecular weight (200 to 400 mw) polyethylene glycol, isopropyl alcohol, N-butanediol, m-pyrol and benzyl alcohol may be substituted for water or included in the hydrophilic domain of the matrix. These solvents may be used to increase the solubility of the drug in the absorbed aqueous phase. The hydrated silicate should be stable in the presence of the other components of the matrix and not adversely interact therewith. The loading and particle size of the silicate phase should be such '-that diffusion pathways defined by the aqueous component of the phase be available for the drug to diffuse from within the matrix to the surface ~f the matrix. In other words, there is substantial particle-to-particle contact -in the dispersed phase. The unhydrated silicate will ~~
4~63~
.
WO 94/07 468 ' PGT/US93/09510 a - -~- .._ . - .- . r normally constitute about 2% to 20% by weight of the matrix, more usually 4% to 1o% by weight. The silicate -may be synthetic, purified, or in a natural form (e. g., clay or talcum). Calcium, magnesium and aluminum silicates and mixtures thereof are preferred. Calcium silicates which have high water and oil absorptions (i.e., >400% by weight) are particularly preferred.
The particulate hydrated silicate is dispersed uniformly throughout the matrix and will define a portion of the surface area of the matrix. That portion should be sufficiently great to provide the desired flux of drug from the matrix. When the matrix is adhesive and is intended to adhere to skin, the portion should not be so great as to cause the matrix to lack sufficient adhesiveness to the skin. Usually the portion of the surface area defined by the hydrated silicate will be in the range of about 0.1 to 20%, more usually 0.5 to 10%.
The drugs that may be used in the matrixes of -this invention are hydrophilic and are dissolved in the aqueous component of the hydrated silicate.
Correlatively, the drug is substantially insoluble in the hydrophobic polymer component of the matrix and hence no significant amount of drug is dissolved in that polymer.
The amount of drug present in the matrix will depend upon the amount of aqueous component present in the matrix and the solubility of the drug in that component. It will normally constitute 1% to 20% by weight of the matrix.
The concentration of drug in the aqueous component of the matrix will be at or below saturation.
Examples of hydrophilic drugs that may be used in the matrixes of the invention are, without limitation, nicardipine hydrochloride, methylsalicylic acid, . nitroglycerine, hydrophilic eerotonin 5-HT3 receptor antagonists such as ondansetron (sold under the brand name ZOFRAN) and granisetron, aminotetralins such as WO 94/07468 , ' PGT/US93/09510 _$_ 214 63 ~
S(-)-2-(N-propyl-N-2-thienylethylamine)-5-hydroxytetralin, and those drugs disclosed on pages 4-6 of European Patent Application Pub. No. 0452837A2 (Application No. 91105933.5).
The matrix also contains a dispersing agent which aids in maintaining the particulate phase dispersed in the continuous phase. Anionic,.cationic, amphoteric or nonionic dispersing agents may be used. Preferably, the dispersing agent is a nonionic surfactant. Examples l0 of such dispersing agents are polyethylene-polyoxypropylene glycol copolymers (sold under the Platonic trademark), polyoxyethylene sorbitan esters (sold under the Tween trademark) such as polyoxyethylene sorbitan monolaurate, polyoxyethylene sorbitan monopalmitate, polyoxyethylene sorbitan monostearate, and polyoxyethylene sorbitan monooleates, and sorbitan esters (sold under the Span trademark) such as sorbitan monolaurate, sorbitan monostearate, and sorbitan monooleate. The dispersing agent will normally 2o constitutQ 0.5~ to lOx by weight of the matrix, more usually 3~ to 6~ by weight of the matrix.
The matrixes of the invention may be prepared by dissolving the drug in water and optionally other hydrophilic polar solvents and contacting the hydrophilic particulate material with the resulting solution to permit the aqueous solution to be absorbed by the particulate material. This mixture will typically have the texture of a paste. The hydrophobic components of the matrix and the dispersing agent, preferably in admixture, are added to the pasta with vigorous mixing to form a viscous dispersion. This dispersion may be formed into appropriate shapes and excess solvent removed therefrom. When the matrix is to be part of a ' transdermal or transbuccal patch, the hydrophobic domain will normally possess pressure sensitive_adhesive -g-properties and the matrix will be cast as a layer or film onto a backing layer. Materials for forming backing layers are wolf-known in the transdermal patch art and era amply exemplified in the transdermal patch patent literature. Typically, the patch will include a basal refease liner layer that is removed prior to use to expose the matrix. A simple and typical transdermal patch structure, generally duignated 1o, is shown in Figure 1 wherein 11 designates the backing layer, 1Z the 1o matrix layer, and 13 the release liner layer.
In addition to being use!ul as a component in transdermal or buccal patches, the matrixu o! the invention may be formed into tablets !or oral administration of the drugs or into inserts or implants for releasing drug into body cavities or within tissues.
The invention is further illustrated by the following examples. These examples are not intended to limit the invention in any manner. Unleas indicatsd otherwise, percentages are by weight.
~.,~i'31i A matrix compost o! 4~ o! the hydrophilic drug (R)-(-)-N-(1-Methyl-1-(3-aethylbensyl)hsxahydro-i»-l, 4-dialspin-6-yl)-iH-inda$ole-3-carboxaside dihydrochloride, 10~ propylene glycol ~nolaurate (PGI~.), ZOi propylene Qlvcol (PG). Z0= distilled watsr, 7~ calciua silicate powder (Micro-Cel E'r"') and 2~ non-ionic surfactant (Pluronic L-121T") in a polydimethylsiloxane adhesive (Dow Corning) 3o Silicone Z9Z0) was prepared by dissolving tb~ drug in the PG and water, mixing the solution with the caloium silicate po~rdar to form a pasts, and vigorously mixing the paste with a sixtuse o! the adhuive, PGML and surfactant to lora~a viscous dispersion.
WO 94/07468 PCd'/US93/09510 - The dispersion was cast onto a 25 micron thick polyester film (silicone-coated Melinex 329 from ICI) to a thickness of 250 microns using a Gardener knife and the composite was dried in an oven at 70°C for 3o min to remove excess solvent. After cooling, the composite was laminated onto a 75 micron thick polyester backing (3M, 1022) .
For comparison purposes, the drug was formulated in various single phase matrixes and formed into laminated composites as above.
Skin Flux Testinc Human epidermis was obtained from the full thickness skin which was frozen prior to being separated.
Separation of the skin at the dermal/epidermal junction was achieved by immersing the skin in water at 60°C for two minutes, and then teasing off the dermis. The heat separated epidermis was stored at 20°C pending use.
Vertically alis~ned diffusion cells with a 2o diffusional area of 0.71 cm2 and a receiver fluid of 8.0 ml were used. A pH 5.0 phosphate buffer was chosen as a receiver fluid to ensure an infinite sink condition being maintained because this buffer solution exhibited reasonable solubility for the drug. Skin flux studies were conducted for a period of 30 hours.
A 1 3/4 cm diameter section of separated epidermis was punched and mounted in the diffusion cell with the stratum corneum facing the donor compartment.
The laminated composites wars punched out in 1 3/4 cm diameter circles. After peeling from the releasing side of polyester film, the drug matrix wa: then mounted between two compartments of the diffusion cell.
After a designated time period has elapsed, a 1 ml sample was taken from the receiver compartment with a micropipette from a given diffusion cell. An equivalent ' amount o! receiver solution was added in the receiver chamber to maintain a constant volume. Dilution o! the receiver medium was taken into account when processing.
the permeation data. Table 1 below reports the results 0! these skin flux teats. Flux is reported as the average llux over 30 hrs.
~inQle phase Comn,~j~~, 28 drug in Silicone 2920 adhssive 0 28 drug in Moratik 6071 adhesive 0 2~ drug in Gelva 7882 adhesive o 28 drug, 108 PGI~~, 108 s-Pyrol 0.5 in Silicone 2920 adhesive 28 drug, 108 PGI~, -108,m~8ys~ol 0 in Morstik 607TM adhesive 48 ~g~ 208 PGHL, ~08 m~Fyrol 0.8 in ICraton 36~617? adhesive Two-Phases 4% drug, 10% PGML, 20% PG 17 .1 20% Dist. water, 7% Micro-Cel ETM
2% Pluronic L-121TM in Silicone 2920 adhesive 1 Morstik 607TM is an acrylate adhesive.
2 Gelva788TM is an acrylate adhesive 3 Kraton 36-6172TM is a styrene-butadiene copolymer adhesive J~s aho~wn in Tabls 1, the skin llux o! the drug lrom the two-phase matrix o! the invention was vastly greater than the skin llux from any o! the comparison single-phase utrixu tested.
~~4~63~. ~ _ _ _ ~xamples 2-6 'These examples illustrate variations of the two-phase matrix formulation of Example 1 in which the proportions of the components differ. These matrixes were prepared and tested as in Example 1. Table 2 below provides details of the compositions of these matrixes and the results of the skin flux~tests on them.
Fable~2 BDcin Bluz ~aampls ~lo. pormul:fii~a (~g/cm2/hs) ' 2 4$ drug, 10$ PGPqL, 30$ PG 15.7 20$ Dist. water, 7$ Micro-Cel E, 3$ Platonic L-121 in silicone 2920 3 4$ drug, 15$ PGl~L, 20$ PG, 9.1 10$ Dist. water, 7$ Micro-Cel E, 3$ Platonic L-121 in Silicone 2920 4 6$ drug, 6$PGML, 30$ PG, 20.4 20$ Dist. water, 7$ Micro-Cel E, 3$ Platonic L-121 in Silicone 2920 5 6$ drug, 6$ PGML, 50% PG, 23.9 20$ Dist. water, 8$ Micro-Cel ~, 3% Platonic L-121 in Silicone 2920 6 5$ drug, 12$ PGI~~, 30$ pG~ 25.7 .
26$ Dist. water, 8$ lKicro-Cel E, 3$ Platonic L-121 in Silicone 2920 Exaa~les 7=g _ _ . _ These examples illustrate two-phase matrix formulations similar to those of Examples of 1-6 but using a different silicone adhesive (Dow Corning 4201).
The matrixes were prepared and tested as in Example 1.
Table 3 below provides details of the compositions of these matrixes and the results of the skin flux tests on ~~, sxia tlu~c ~aapie ~lo. Porsniation 7 4; drug, 15; PGl~, 20~ PG 12.0 10% Dist. water, 7% Micro-Cel ETM, 3% Pluronic L-121' in Silicone 4201 8 2~ dzvg, 5~ PGML, 20~ PG, 5.4 15% Dist. water, 2% Micro-Cel-ET"', 3% Tween~ in Silicon Examples 9-12 These examples illustrate matrixes similar to that of Example 1 in which the hydropbobic solvent was dittarant than PGML. The matrix tormulation consisted of 4~ drug, 20; PG, 15i distillsd water, 7; calcium silicate 2% TweenTM 80 surfactant and the indicated % of hydrophobic solvent in polydimethylsiloxane adhesive (Dow Corning 4201). The matrixes were prepared and tested as in Example 1. Table 4 below provides details on the composition and amount o! the hydrophobic solvent and the results of the skin tlux tests.
2 5 . syatopnobio skis i~lu:
szaaple ~to. solveat (~q/aas/hr) 9 12; PEGl~L, 3! IFli 6.4 10 10; Oleyl Oleata 2.1 11 lob oleic lucid 2. o 3 0 1Z lOi Oleyl 711COho1 9 . 6 g,~ammlws 13=,~
These axa~aples illustrate aatrixas siailar to that o! Example 1 in which the silicates other than W~ 94/07468 P~/US93/09510 Micro-Cel E were used. These matrixes were prepared and tested as in Example 1. Table 5 below provides details of the compositions of these matrixes and the results of the skin flux tests. ' _ __ Table 5 s BD~in Fluz ~campls ~lo. Formulation (~ag/cm2/hrD
13 2$ Drug, 5$ Oleyl Alcohol, 2.1 20$ PG, 15$ Dist. water, 1$
Talc, 3$ Tween 80 in Silicone-4201 14 2$ Drug, 5% Oleyl Alcohol, 1.2 20$ PG, 15$ Dist. water, 1$
Kaolin, 3$ Tween 80 in.
Silicone 4201 Example 15 S(-)-2-(N-propyl-N-2-thienyl~thylamine)-5-hydroxytetralin is a selective D2 agonist for treating 2o Parkinson~s disease. The effective doss for treating Parkinson~s disease is estimated to be in the range of about 1 to 3 ~Cg/kg/hr. Accordingly, for transdermal administration, the target flux of this drug (based on a 2o cm2 delivery area) is estimated to be in the range of .approximately 3-10 ~Cg/cm2/hr.
Skin flux studies of this drug from various liquid formulations showed that fluxes at or above the effective range could be achieved from saturated solutions of the drug in pH 6.0 buffer or PGI~. Similar studies of the flux of this drug from simple matrix systems in which the drug and PGI~ were formulated in various adhesives (silicone, polyisobutylene, or P~iorstik 607 acrylate) did not provide affective flux levels. ' In contrast a series of five two-phase matrix formulations of this drug were prepared in accordance WO 94/07468 PC1"/L'S93/09510 with th~ pressnt invention. Table 6 blow presents the composition of tho~~ matrixes and the results of the flux tests thereon.
Matrix 1 2 3 4 5 6 7 8 Skin Flux (1~9/~2 /~') 11 2 10 5 5 10 4 3 61 6.411 0.13 g 4 10 5 5 10 4 3 59 14.21 0.6 C 4 0 5 5 10 4 6 66 8.661 0.19 D 4 5 5 s 10 4 5 62 15.51 0.19 E 4 10 5 5 10 2 3 61 13.71 1.2 1 - Drug 2 s PG~Ir 3 ~ H~rrsyl alcohol ( ~
4 - l~r 5 ~ D$ 6.0 pho~phat~ buttll' (_~
6 = Micro-CeITM E (%) 7 = Span 60TM Emulsifier (%) 8 = Silicone 4201 Adhesive (%) 1~ indicated, all !iw o! the tvo-phaa~
matrixsa provid~d tlux~s st or above the targt level.
Ha~~d on th~ r~sulta o! Exasple is, two optimised toraulations o! S(-)-Z-(N-propyl-N-Z-thisaylethylamin~)-5-hydroxyt~tralin. Thss~ formulations lacked any PQ~L, b~nzyl alcohol or PG. One contained 4~
drug, 20i phoephat~ butter (pH 6. 0) , 4~ Micro-Cel ETM, 4%
~an 60TM emulsifier, and 4% silicone medical fluid 360 (Dav Corning) in silicone 4Z0i adhe~iw. Th~ ~a~c contained 5% drug, 18% buffer, 5% Micro-Cel ETM, 4% Span 60TM emulsifier, and 4% silicone medical fluid 360 in silicon~ 4201 adhuiw. The flux Irooa thas~ formulations was comparable to those from matrixes B, D, and E of Example 15.
Modifications of the above modes for carrying out the invention that are obvious to those of skill in pharmaceuticals, sustained release formulation, transdermal drug delivery, polymers, pressure sensitive adhesives, and related fields are intended to be within the scope of the following claims.
-1= = ...
TWO-PHASE MATRIX FOR SUSTAINED RELEASE
DRUG DELIVERY DEVICE
Descri tp ion Technical Field The present invention is in the field of controlled or sustained release drug formulations and relates specifically to a two-phase drug-containing matrix that may be used as a component in a transdermal patch. -$ackg~round _ _ In general there are two types of transdermal 2o patch designs: a "reservoir" type and a matrix" type.
In the reservoir type the drug, typically in fluid form, is contained within a walled reservoir whose basal surface is permeable to the drug. In the matrix type the -drug is dispersed in a polymer layer, typically an adhesive, and the matrix directly contacts the skin Both types of device also typically include a backing layer and an inner release liner layer that is removed prior to use.
The present invention concerns a matrix-type 3o device in which the matrix includes a particulate hydrated hydrophilic material that contains the drug and defines at least a portion of the basal surface area of ' the matrix.
WO 94/07468 - P~./US93/0951(~' Several prior patents describe two-phase matrixes used in transdermal drug devices, but all are distinct from the matrixes of the present invention.
U.S. 4,568,232 describes a matrix for a transdermal patch which comprises.a water-insoluble adhesive, drug that is soluble in the adhesive, and a water-swellable polymer. The inclusion of the water-swellable polymer is alleged to increase the release rate of drug from the matrix.
EPA 0391172 describes a transdermal patch having a matrix composed of a water-insoluble material that contains islands of a solid solution of drug in a water-soluble/swellable polymer and an underlayer that controls the amount of water vapor passing from the skin to the matrix. The matrix is said to be activated by water vapor from the skin.
U.S. 4,559,222 describes a transdermal matrix-type patch in which the matrix is composed of a mixture of mineral oil,~polyisobutylene (an adhesive), and colloidal silicon dioxide. The addition of the silicon dioxide allegedly affects the flow characteristics of the mineral oil-polyisobutylene mix.
U.S. 5,071,657 describes a transdermal patch matrix of a drug-containing gel that is dispersed in a cross-linked silicone polymer. This matrix is apparently not adhesive as the patent teaches the use of a separate peripheral adhesive layer to affix the patch to the skin.
EPA 0452837A2 describes an adhesive matrix composed of a hydrophobic polymer, a hydrophilic drug, a hydrophilic swellable polymer, water, and a permeation enhancer. The water is said to act as a solubilizer for the drug and the hydrophilic swellable polymer acts to facilitate the mixing of the ingredients and improve the ' stability of the matrix.
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2~~~~~~ -. PCT/LJS93/09510 -3- - = -The invention provides a novel matrix composed of a continuous hydrophobic domain and a dispersed particulate hydrated silicate domain which may be used to administer hydrophilic drugs in a sustained manner. The invention permits hydrophilic drugs to be effectively dispersed in a hydrophobic phase, maintains separation of the drug from the hydrophobic phase so that potential interaction between the two is reduced, and provides enhanced release of hydrophilic drugs from matrixes l0 composed of a continuous hydrophobic domain.
n1 ~r~ osure of the In-vention One aspect of the invention is a sustained-release drug formulation comprising a matrix of:
(a) a continuous hydrophobic polymer phase;
-- (b) a particulate phase dispersed in the -continuous polymer phase comprised of: -(i) a hydrated inorganic silicate;
(ii) a water-solubilizable drug at least partly dissolvQd in the aqueous phase of (i); and (c) a dispersing agent for dispersing (b) in (a) . -wherein the particulate phase defines at least a portion of the surface area of the matrix and provides a diffusion pathway for .the drug in the matrix. -Another aspect of the invention is a transdermal patch comprising a laminated composite of:
(a) a backing layer; and -(b) a layer of the above-described matrix wherein the continuous hydrophobic polymer phase is a pressure sensitive adhesive.
Still another aspect of the invention is a matrix of (a) a continuous hydrophobic polymer phase;
-WO 94/07468 _ ~ ~ ~ '- _ . .~ ~~/US93/09510 (b) a particulate phase dispersed in the continuous polymer phase comprised af:
w a hydrated inorganic silicate and an aqueous phase; and (c) a dispersing agent for dispersing (b) in (a) wherein the particulate phase defines at least a portion of the surface area of the matrix and provides a diffusion pathway in the matrix for an active ingredient that can be water-solubilized.
Still another aspect of the invention is a process for preparing the above described sustained release drug formulation which comprises:
(1) solubilizing on water-solubilizable drug in a liquid aqueous medium;
(2) combining the solubilized drug with the aqueous medium with a hydrated inorganic silicate source;
(3) dispersing the product of step (2) with a hydrophobic polymer and optionally a surfactant to form a 2o dispersion; and optionally (4) applying the dispersion of step (3) to a backing; and (5) removing excess liquid aqueous medium.
Brief Description of the Drawing The drawing is a cross-sectional view (not to scale) of a transdermal patch that includes the matrix formulation of the invention.
As used herein with respect to the continuous phase, the term "hydrophobic°' intends that the material is less than 20$ by weight soluble in water at 32°C, over 24 hr.
21456~~
-5- ~ - ~- . F-_. r_ , _, , ;> - . _ As used herein, the term 'substantially ~ _ insoluble' intends a solubility of less than about 1% by weight, more usually less than about 0.5% by weight.
As used herein the term "continuous" intends a phase that is interconnected and not separated into distinct domains, segments, or particles.
As used herein with respect to the drug, the terms 'hydrophilic" and "water soluble" are intended to be synonymous and to denote that the drug has a water solubility of at least about 0.1 mg/L, preferably at least about 1 mg/L at 32C. -The term "hydrated" intends that the dispersed particulate material comprises all or a portion of its total absorptive capacity of absorbed aqueous phase (i.e.
water and/or other polar solvent). -The term "sustained release" intends a formulation that is capable of releasing a therapeutically effective amount of drug over a time period of one to seven days. __ 2o The material that constitutes the continuous -phase or hydrophobic domain of the matrix is a hydrophobic polymer that is capable of being mixed with the other components of the matrix and formed into a layer or film. When the matrix is used as the drug-containing matrix of a transdermal patch, the hydrophobic polymer preferably has pressure-sensitive adhesive properties that permit the matrix to adhere to living human skin for a sustained period of time, i.e., usually at least about one to seven days. Because the polymer is hydrophobic, the drug is substantially insoluble and immiscible in the polymer. Specific examples of polymers that may be used as the continuous hydrophobic phase of the matrix are polysiloxanes, polyisobutylene, solvent-based hydrophobic polyacrylates, polyurethanes, ' 35 plasticized ethylene-vinyl acetate copolymers, low W~ 94/07468 ~ . - ~ - ~ -. PCT/US93/09510~' . .4 -6_ ~14~~3~.
molecular weight polyether block amide copolymers, styrene-butadiene polymers, and vinyl acetate-based adhesives. The hydrophobic polymer will normally constitute about 30~ to 95~.by weight of the matrix, more usually 40~ to SO$ by weight. Other hydrophobic materials such as solvents or permeation enhancers may be , included in the hydrophobic domain of the matrix.
Examples of such materials are fatty acids (oleic and stearic acid), isopropyl myristate (IPM), fatty acid esters (e. g., propylene glycol monolaurate, polyethylene glycol monolaurate (PEGML), methyl oleate, oleyl oleate), fatty alcohols (e. g., oleyl alcohol), and terpenoids (limonene, menthol, ~-pinene, and geraniol).
The dispersed inorganic silicate is in the form of particles that are typically in the non-colloidal size range of 0.001 to 0.1 mm (largest dimension), more usually 0.01 to 0.05 mm. In its hydrated form the material will normally contain about 15~ to 600 of its - own weight in absorbed water, more usually look to of its own weight in water (measured at 25°C). Other hydrophilic polar solvents such as ethanol, propylene glycol, low molecular weight (200 to 400 mw) polyethylene glycol, isopropyl alcohol, N-butanediol, m-pyrol and benzyl alcohol may be substituted for water or included in the hydrophilic domain of the matrix. These solvents may be used to increase the solubility of the drug in the absorbed aqueous phase. The hydrated silicate should be stable in the presence of the other components of the matrix and not adversely interact therewith. The loading and particle size of the silicate phase should be such '-that diffusion pathways defined by the aqueous component of the phase be available for the drug to diffuse from within the matrix to the surface ~f the matrix. In other words, there is substantial particle-to-particle contact -in the dispersed phase. The unhydrated silicate will ~~
4~63~
.
WO 94/07 468 ' PGT/US93/09510 a - -~- .._ . - .- . r normally constitute about 2% to 20% by weight of the matrix, more usually 4% to 1o% by weight. The silicate -may be synthetic, purified, or in a natural form (e. g., clay or talcum). Calcium, magnesium and aluminum silicates and mixtures thereof are preferred. Calcium silicates which have high water and oil absorptions (i.e., >400% by weight) are particularly preferred.
The particulate hydrated silicate is dispersed uniformly throughout the matrix and will define a portion of the surface area of the matrix. That portion should be sufficiently great to provide the desired flux of drug from the matrix. When the matrix is adhesive and is intended to adhere to skin, the portion should not be so great as to cause the matrix to lack sufficient adhesiveness to the skin. Usually the portion of the surface area defined by the hydrated silicate will be in the range of about 0.1 to 20%, more usually 0.5 to 10%.
The drugs that may be used in the matrixes of -this invention are hydrophilic and are dissolved in the aqueous component of the hydrated silicate.
Correlatively, the drug is substantially insoluble in the hydrophobic polymer component of the matrix and hence no significant amount of drug is dissolved in that polymer.
The amount of drug present in the matrix will depend upon the amount of aqueous component present in the matrix and the solubility of the drug in that component. It will normally constitute 1% to 20% by weight of the matrix.
The concentration of drug in the aqueous component of the matrix will be at or below saturation.
Examples of hydrophilic drugs that may be used in the matrixes of the invention are, without limitation, nicardipine hydrochloride, methylsalicylic acid, . nitroglycerine, hydrophilic eerotonin 5-HT3 receptor antagonists such as ondansetron (sold under the brand name ZOFRAN) and granisetron, aminotetralins such as WO 94/07468 , ' PGT/US93/09510 _$_ 214 63 ~
S(-)-2-(N-propyl-N-2-thienylethylamine)-5-hydroxytetralin, and those drugs disclosed on pages 4-6 of European Patent Application Pub. No. 0452837A2 (Application No. 91105933.5).
The matrix also contains a dispersing agent which aids in maintaining the particulate phase dispersed in the continuous phase. Anionic,.cationic, amphoteric or nonionic dispersing agents may be used. Preferably, the dispersing agent is a nonionic surfactant. Examples l0 of such dispersing agents are polyethylene-polyoxypropylene glycol copolymers (sold under the Platonic trademark), polyoxyethylene sorbitan esters (sold under the Tween trademark) such as polyoxyethylene sorbitan monolaurate, polyoxyethylene sorbitan monopalmitate, polyoxyethylene sorbitan monostearate, and polyoxyethylene sorbitan monooleates, and sorbitan esters (sold under the Span trademark) such as sorbitan monolaurate, sorbitan monostearate, and sorbitan monooleate. The dispersing agent will normally 2o constitutQ 0.5~ to lOx by weight of the matrix, more usually 3~ to 6~ by weight of the matrix.
The matrixes of the invention may be prepared by dissolving the drug in water and optionally other hydrophilic polar solvents and contacting the hydrophilic particulate material with the resulting solution to permit the aqueous solution to be absorbed by the particulate material. This mixture will typically have the texture of a paste. The hydrophobic components of the matrix and the dispersing agent, preferably in admixture, are added to the pasta with vigorous mixing to form a viscous dispersion. This dispersion may be formed into appropriate shapes and excess solvent removed therefrom. When the matrix is to be part of a ' transdermal or transbuccal patch, the hydrophobic domain will normally possess pressure sensitive_adhesive -g-properties and the matrix will be cast as a layer or film onto a backing layer. Materials for forming backing layers are wolf-known in the transdermal patch art and era amply exemplified in the transdermal patch patent literature. Typically, the patch will include a basal refease liner layer that is removed prior to use to expose the matrix. A simple and typical transdermal patch structure, generally duignated 1o, is shown in Figure 1 wherein 11 designates the backing layer, 1Z the 1o matrix layer, and 13 the release liner layer.
In addition to being use!ul as a component in transdermal or buccal patches, the matrixu o! the invention may be formed into tablets !or oral administration of the drugs or into inserts or implants for releasing drug into body cavities or within tissues.
The invention is further illustrated by the following examples. These examples are not intended to limit the invention in any manner. Unleas indicatsd otherwise, percentages are by weight.
~.,~i'31i A matrix compost o! 4~ o! the hydrophilic drug (R)-(-)-N-(1-Methyl-1-(3-aethylbensyl)hsxahydro-i»-l, 4-dialspin-6-yl)-iH-inda$ole-3-carboxaside dihydrochloride, 10~ propylene glycol ~nolaurate (PGI~.), ZOi propylene Qlvcol (PG). Z0= distilled watsr, 7~ calciua silicate powder (Micro-Cel E'r"') and 2~ non-ionic surfactant (Pluronic L-121T") in a polydimethylsiloxane adhesive (Dow Corning) 3o Silicone Z9Z0) was prepared by dissolving tb~ drug in the PG and water, mixing the solution with the caloium silicate po~rdar to form a pasts, and vigorously mixing the paste with a sixtuse o! the adhuive, PGML and surfactant to lora~a viscous dispersion.
WO 94/07468 PCd'/US93/09510 - The dispersion was cast onto a 25 micron thick polyester film (silicone-coated Melinex 329 from ICI) to a thickness of 250 microns using a Gardener knife and the composite was dried in an oven at 70°C for 3o min to remove excess solvent. After cooling, the composite was laminated onto a 75 micron thick polyester backing (3M, 1022) .
For comparison purposes, the drug was formulated in various single phase matrixes and formed into laminated composites as above.
Skin Flux Testinc Human epidermis was obtained from the full thickness skin which was frozen prior to being separated.
Separation of the skin at the dermal/epidermal junction was achieved by immersing the skin in water at 60°C for two minutes, and then teasing off the dermis. The heat separated epidermis was stored at 20°C pending use.
Vertically alis~ned diffusion cells with a 2o diffusional area of 0.71 cm2 and a receiver fluid of 8.0 ml were used. A pH 5.0 phosphate buffer was chosen as a receiver fluid to ensure an infinite sink condition being maintained because this buffer solution exhibited reasonable solubility for the drug. Skin flux studies were conducted for a period of 30 hours.
A 1 3/4 cm diameter section of separated epidermis was punched and mounted in the diffusion cell with the stratum corneum facing the donor compartment.
The laminated composites wars punched out in 1 3/4 cm diameter circles. After peeling from the releasing side of polyester film, the drug matrix wa: then mounted between two compartments of the diffusion cell.
After a designated time period has elapsed, a 1 ml sample was taken from the receiver compartment with a micropipette from a given diffusion cell. An equivalent ' amount o! receiver solution was added in the receiver chamber to maintain a constant volume. Dilution o! the receiver medium was taken into account when processing.
the permeation data. Table 1 below reports the results 0! these skin flux teats. Flux is reported as the average llux over 30 hrs.
~inQle phase Comn,~j~~, 28 drug in Silicone 2920 adhssive 0 28 drug in Moratik 6071 adhesive 0 2~ drug in Gelva 7882 adhesive o 28 drug, 108 PGI~~, 108 s-Pyrol 0.5 in Silicone 2920 adhesive 28 drug, 108 PGI~, -108,m~8ys~ol 0 in Morstik 607TM adhesive 48 ~g~ 208 PGHL, ~08 m~Fyrol 0.8 in ICraton 36~617? adhesive Two-Phases 4% drug, 10% PGML, 20% PG 17 .1 20% Dist. water, 7% Micro-Cel ETM
2% Pluronic L-121TM in Silicone 2920 adhesive 1 Morstik 607TM is an acrylate adhesive.
2 Gelva788TM is an acrylate adhesive 3 Kraton 36-6172TM is a styrene-butadiene copolymer adhesive J~s aho~wn in Tabls 1, the skin llux o! the drug lrom the two-phase matrix o! the invention was vastly greater than the skin llux from any o! the comparison single-phase utrixu tested.
~~4~63~. ~ _ _ _ ~xamples 2-6 'These examples illustrate variations of the two-phase matrix formulation of Example 1 in which the proportions of the components differ. These matrixes were prepared and tested as in Example 1. Table 2 below provides details of the compositions of these matrixes and the results of the skin flux~tests on them.
Fable~2 BDcin Bluz ~aampls ~lo. pormul:fii~a (~g/cm2/hs) ' 2 4$ drug, 10$ PGPqL, 30$ PG 15.7 20$ Dist. water, 7$ Micro-Cel E, 3$ Platonic L-121 in silicone 2920 3 4$ drug, 15$ PGl~L, 20$ PG, 9.1 10$ Dist. water, 7$ Micro-Cel E, 3$ Platonic L-121 in Silicone 2920 4 6$ drug, 6$PGML, 30$ PG, 20.4 20$ Dist. water, 7$ Micro-Cel E, 3$ Platonic L-121 in Silicone 2920 5 6$ drug, 6$ PGML, 50% PG, 23.9 20$ Dist. water, 8$ Micro-Cel ~, 3% Platonic L-121 in Silicone 2920 6 5$ drug, 12$ PGI~~, 30$ pG~ 25.7 .
26$ Dist. water, 8$ lKicro-Cel E, 3$ Platonic L-121 in Silicone 2920 Exaa~les 7=g _ _ . _ These examples illustrate two-phase matrix formulations similar to those of Examples of 1-6 but using a different silicone adhesive (Dow Corning 4201).
The matrixes were prepared and tested as in Example 1.
Table 3 below provides details of the compositions of these matrixes and the results of the skin flux tests on ~~, sxia tlu~c ~aapie ~lo. Porsniation 7 4; drug, 15; PGl~, 20~ PG 12.0 10% Dist. water, 7% Micro-Cel ETM, 3% Pluronic L-121' in Silicone 4201 8 2~ dzvg, 5~ PGML, 20~ PG, 5.4 15% Dist. water, 2% Micro-Cel-ET"', 3% Tween~ in Silicon Examples 9-12 These examples illustrate matrixes similar to that of Example 1 in which the hydropbobic solvent was dittarant than PGML. The matrix tormulation consisted of 4~ drug, 20; PG, 15i distillsd water, 7; calcium silicate 2% TweenTM 80 surfactant and the indicated % of hydrophobic solvent in polydimethylsiloxane adhesive (Dow Corning 4201). The matrixes were prepared and tested as in Example 1. Table 4 below provides details on the composition and amount o! the hydrophobic solvent and the results of the skin tlux tests.
2 5 . syatopnobio skis i~lu:
szaaple ~to. solveat (~q/aas/hr) 9 12; PEGl~L, 3! IFli 6.4 10 10; Oleyl Oleata 2.1 11 lob oleic lucid 2. o 3 0 1Z lOi Oleyl 711COho1 9 . 6 g,~ammlws 13=,~
These axa~aples illustrate aatrixas siailar to that o! Example 1 in which the silicates other than W~ 94/07468 P~/US93/09510 Micro-Cel E were used. These matrixes were prepared and tested as in Example 1. Table 5 below provides details of the compositions of these matrixes and the results of the skin flux tests. ' _ __ Table 5 s BD~in Fluz ~campls ~lo. Formulation (~ag/cm2/hrD
13 2$ Drug, 5$ Oleyl Alcohol, 2.1 20$ PG, 15$ Dist. water, 1$
Talc, 3$ Tween 80 in Silicone-4201 14 2$ Drug, 5% Oleyl Alcohol, 1.2 20$ PG, 15$ Dist. water, 1$
Kaolin, 3$ Tween 80 in.
Silicone 4201 Example 15 S(-)-2-(N-propyl-N-2-thienyl~thylamine)-5-hydroxytetralin is a selective D2 agonist for treating 2o Parkinson~s disease. The effective doss for treating Parkinson~s disease is estimated to be in the range of about 1 to 3 ~Cg/kg/hr. Accordingly, for transdermal administration, the target flux of this drug (based on a 2o cm2 delivery area) is estimated to be in the range of .approximately 3-10 ~Cg/cm2/hr.
Skin flux studies of this drug from various liquid formulations showed that fluxes at or above the effective range could be achieved from saturated solutions of the drug in pH 6.0 buffer or PGI~. Similar studies of the flux of this drug from simple matrix systems in which the drug and PGI~ were formulated in various adhesives (silicone, polyisobutylene, or P~iorstik 607 acrylate) did not provide affective flux levels. ' In contrast a series of five two-phase matrix formulations of this drug were prepared in accordance WO 94/07468 PC1"/L'S93/09510 with th~ pressnt invention. Table 6 blow presents the composition of tho~~ matrixes and the results of the flux tests thereon.
Matrix 1 2 3 4 5 6 7 8 Skin Flux (1~9/~2 /~') 11 2 10 5 5 10 4 3 61 6.411 0.13 g 4 10 5 5 10 4 3 59 14.21 0.6 C 4 0 5 5 10 4 6 66 8.661 0.19 D 4 5 5 s 10 4 5 62 15.51 0.19 E 4 10 5 5 10 2 3 61 13.71 1.2 1 - Drug 2 s PG~Ir 3 ~ H~rrsyl alcohol ( ~
4 - l~r 5 ~ D$ 6.0 pho~phat~ buttll' (_~
6 = Micro-CeITM E (%) 7 = Span 60TM Emulsifier (%) 8 = Silicone 4201 Adhesive (%) 1~ indicated, all !iw o! the tvo-phaa~
matrixsa provid~d tlux~s st or above the targt level.
Ha~~d on th~ r~sulta o! Exasple is, two optimised toraulations o! S(-)-Z-(N-propyl-N-Z-thisaylethylamin~)-5-hydroxyt~tralin. Thss~ formulations lacked any PQ~L, b~nzyl alcohol or PG. One contained 4~
drug, 20i phoephat~ butter (pH 6. 0) , 4~ Micro-Cel ETM, 4%
~an 60TM emulsifier, and 4% silicone medical fluid 360 (Dav Corning) in silicone 4Z0i adhe~iw. Th~ ~a~c contained 5% drug, 18% buffer, 5% Micro-Cel ETM, 4% Span 60TM emulsifier, and 4% silicone medical fluid 360 in silicon~ 4201 adhuiw. The flux Irooa thas~ formulations was comparable to those from matrixes B, D, and E of Example 15.
Modifications of the above modes for carrying out the invention that are obvious to those of skill in pharmaceuticals, sustained release formulation, transdermal drug delivery, polymers, pressure sensitive adhesives, and related fields are intended to be within the scope of the following claims.
Claims (17)
1. A sustained release drug formulation comprising a matrix of:
(a) a continuous hydrophobic polymer phase;
(b) a particulate phase dispersed in the continuous polymer phase comprised of:
(i) a hydrated inorganic silicate;
(ii) a water-solubilizable drug at least partly dissolved in the aqueous phase of (i) and (c) a dispersing agent for dispersing (b) in (a);
wherein the continuous hydrophobic polymer phase is a pressure sensitive adhesive, wherein the inorganic silicate (unhydrated) constitutes 2% to 20% by weight of the matrix, and wherein the particulate phase defines at least a portion of the surface area of the matrix and provides a diffusion pathway for the drug in the matrix.
(a) a continuous hydrophobic polymer phase;
(b) a particulate phase dispersed in the continuous polymer phase comprised of:
(i) a hydrated inorganic silicate;
(ii) a water-solubilizable drug at least partly dissolved in the aqueous phase of (i) and (c) a dispersing agent for dispersing (b) in (a);
wherein the continuous hydrophobic polymer phase is a pressure sensitive adhesive, wherein the inorganic silicate (unhydrated) constitutes 2% to 20% by weight of the matrix, and wherein the particulate phase defines at least a portion of the surface area of the matrix and provides a diffusion pathway for the drug in the matrix.
2. The sustained release drug formulation of claim 1 wherein the drug comprises 1% to 20% by weight of the matrix, the inorganic silicate comprises 2% to 20% by weight of the matrix and the hydrophobic polymer phase comprises 30% to about 95% by weight of the matrix.
3. The sustained release drug formulation of claim 1 wherein the hydrated inorganic silicate contains 15% to 600% of its own weight in absorbed aqueous phase.
4. The sustained release drug formulation of claim 2 wherein the hydrated inorganic silicate contains 100% to 500% of its own weight in absorbed aqueous phase.
5. The sustained release drug formulation of claim 1 wherein the hydrated inorganic silicate is calcium silicate, magnesium silicate, aluminum silicate, or mixtures thereof.
6. The sustained release drug formulation of claims 1, 2, 3, 4 or 5 wherein said surface area portion constitutes 0.1% to 20% of the surface area of the matrix.
7. The sustained release formulation of claim 1 wherein the hydrophobic polymer phase includes a hydrophobic solvent.
8. The sustained release formulation of claim 7 wherein the hydrophobic solvent is a skin permeation enhancer.
9. The sustained release formulation of claims 7 or 8 wherein the hydrophobic solvent is a fatty acid, a fatty acid ester, a fatty alcohol, or a terpenoid.
10. The sustained release drug formulation of claims 1, 2, 3, 4, or 5 wherein the hydrated inorganic silicate includes an absorbed polar solvent that increases the solubility of the drug in water.
11. The sustained release drug formulation of claim 10 wherein the polar solvent is ethanol, propylene glycol, low molecular weight polyethylene glycol, isopropyl alcohol, n-butanediol, m-pyrol, or benzyl alcohol.
12. The sustained release formulation of claims 1 or 2 wherein the drug is (R) - (-)-N- (1-Methyl-4-(3-methylbenzyl)hexahydro-1H-1,4-diazepin-6-yl)-1H-indazole-3-carboxamide dihydrochloride, ondansetron, granisetron, or S(-)-2-(N-propyl-N-2-thienylethylamine)-5-hydroxytetralin.
13. The sustained release drug formulation of claims 2, 3, 4 or 5 wherein the hydrated inorganic silicate is calcium silicate, the hydrophobic polymer is a silicone, the formulation includes propylene glycol and propylene glycol monolaurate, and the drug is (R)-(-)-N-(1-Methyl-4-(3-methylbenzyl)hexahydro-1H-1,4-diazepin-6-yl)-1H-indazole-3-carboxamide dihydrochloride or S-(-)-2-(N-propyl-N-2-thienylethylamine)-5-hydroxytetralin.
14. A transdermal patch comprising a laminated composite of:
(a) a backing layer; and (b) a layer of the formulation of one of the preceding claims 1, 2, 3, 4, 5, 7, 8 or 12 wherein the continuous hydrophobic polymer phase is a pressure sensitive adhesive.
(a) a backing layer; and (b) a layer of the formulation of one of the preceding claims 1, 2, 3, 4, 5, 7, 8 or 12 wherein the continuous hydrophobic polymer phase is a pressure sensitive adhesive.
15. A matrix of:
(a) a continuous hydrophobic polymer phase;
(b) a particulate phase dispersed in the continuous polymer phase comprised of:
a hydrated inorganic silicate and an aqueous phase; and (c) a dispersing agent for dispersing (b) in (a);
wherein continuous hydrophobic polymer phase is a pressure-sensitive adhesive, wherein the inorganic silicate (unhydrated) constitutes 2% to 20% by weight of the matrix, and wherein the particulate phase defines at least a portion of the surface area of the matrix and provides a diffusion pathway in the matrix for an active ingredient that can be water-solubilized.
(a) a continuous hydrophobic polymer phase;
(b) a particulate phase dispersed in the continuous polymer phase comprised of:
a hydrated inorganic silicate and an aqueous phase; and (c) a dispersing agent for dispersing (b) in (a);
wherein continuous hydrophobic polymer phase is a pressure-sensitive adhesive, wherein the inorganic silicate (unhydrated) constitutes 2% to 20% by weight of the matrix, and wherein the particulate phase defines at least a portion of the surface area of the matrix and provides a diffusion pathway in the matrix for an active ingredient that can be water-solubilized.
16. The use of the matrix of claim 15 in the preparation of a sustained release drug formulation.
17. A process for preparing a sustained release drug formulation of claims 1, 2, 3, 4, 5, 7, 8 or 12 which comprises:
(1) solubilizing a water-solubilizable drug in a liquid aqueous medium;
(2) combining the solubilized drug with the aqueous medium with a hydratable inorganic silicate source;
(3) dispersing the product of step (2) with a hydrophobic polymer and optionally a surfactant to form a dispersion; and optionally (4) applying the dispersion of step (3) to a backing; and (5) removing excess liquid aqueous medium.
(1) solubilizing a water-solubilizable drug in a liquid aqueous medium;
(2) combining the solubilized drug with the aqueous medium with a hydratable inorganic silicate source;
(3) dispersing the product of step (2) with a hydrophobic polymer and optionally a surfactant to form a dispersion; and optionally (4) applying the dispersion of step (3) to a backing; and (5) removing excess liquid aqueous medium.
Applications Claiming Priority (5)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US95663592A | 1992-10-05 | 1992-10-05 | |
| US07/956,635 | 1992-10-05 | ||
| US08/056,076 US5989586A (en) | 1992-10-05 | 1993-04-30 | Two-phase matrix for sustained release drug delivery device |
| US08/056,076 | 1993-04-30 | ||
| PCT/US1993/009510 WO1994007468A1 (en) | 1992-10-05 | 1993-10-05 | Two-phase matrix for sustained release drug delivery device |
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| CA2145631A1 CA2145631A1 (en) | 1994-04-14 |
| CA2145631C true CA2145631C (en) | 2004-02-10 |
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| CA002145631A Expired - Lifetime CA2145631C (en) | 1992-10-05 | 1993-10-05 | Two-phase matrix for sustained release drug delivery device |
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| US (2) | US5989586A (en) |
| EP (1) | EP0662822B1 (en) |
| JP (1) | JPH08504757A (en) |
| CN (1) | CN1089469A (en) |
| AT (1) | ATE198420T1 (en) |
| AU (1) | AU5321194A (en) |
| CA (1) | CA2145631C (en) |
| DE (1) | DE69329825T2 (en) |
| DK (1) | DK0662822T3 (en) |
| ES (1) | ES2155073T3 (en) |
| GR (1) | GR3035626T3 (en) |
| PT (1) | PT662822E (en) |
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| US5989586A (en) * | 1992-10-05 | 1999-11-23 | Cygnus, Inc. | Two-phase matrix for sustained release drug delivery device |
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- 1993-10-05 ES ES93923258T patent/ES2155073T3/en not_active Expired - Lifetime
- 1993-10-05 PT PT93923258T patent/PT662822E/en unknown
- 1993-10-05 DK DK93923258T patent/DK0662822T3/en active
- 1993-10-05 WO PCT/US1993/009510 patent/WO1994007468A1/en active IP Right Grant
- 1993-10-05 CA CA002145631A patent/CA2145631C/en not_active Expired - Lifetime
- 1993-10-05 EP EP93923258A patent/EP0662822B1/en not_active Expired - Lifetime
- 1993-10-05 CN CN93118244A patent/CN1089469A/en active Pending
- 1993-10-05 DE DE69329825T patent/DE69329825T2/en not_active Expired - Lifetime
- 1993-10-05 AT AT93923258T patent/ATE198420T1/en not_active IP Right Cessation
- 1993-10-05 AU AU53211/94A patent/AU5321194A/en not_active Abandoned
- 1993-10-05 JP JP6509398A patent/JPH08504757A/en active Pending
- 1993-10-27 TW TW082108949A patent/TW252919B/zh active
-
1995
- 1995-06-07 US US08/474,693 patent/US5840336A/en not_active Expired - Lifetime
-
2001
- 2001-03-23 GR GR20010400471T patent/GR3035626T3/en unknown
Also Published As
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|---|---|
| CA2145631A1 (en) | 1994-04-14 |
| EP0662822A1 (en) | 1995-07-19 |
| DE69329825T2 (en) | 2001-06-13 |
| TW252919B (en) | 1995-08-01 |
| AU5321194A (en) | 1994-04-26 |
| JPH08504757A (en) | 1996-05-21 |
| US5840336A (en) | 1998-11-24 |
| US5989586A (en) | 1999-11-23 |
| CN1089469A (en) | 1994-07-20 |
| EP0662822B1 (en) | 2001-01-03 |
| DE69329825D1 (en) | 2001-02-08 |
| EP0662822A4 (en) | 1996-08-07 |
| GR3035626T3 (en) | 2001-06-29 |
| ATE198420T1 (en) | 2001-01-15 |
| WO1994007468A1 (en) | 1994-04-14 |
| DK0662822T3 (en) | 2001-01-29 |
| PT662822E (en) | 2001-04-30 |
| ES2155073T3 (en) | 2001-05-01 |
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| EEER | Examination request | ||
| MKEX | Expiry |
Effective date: 20131007 |