Patent Application
20050226919
The present invention relates to devices for the transdermal delivery of indoline compounds of formula (I) for treating or preventing urinary tract disorders. Moreover, the invention relates to the use of indoline compounds of formula (I) for the preparation of a medicament for transdermal application.
The active ingredient of the device according to the present invention is an indoline compound of formula (I)
wherein
R represents a saturated or unsaturated C2-7 aliphatic acyl group optionally substituted with one or more halogen atoms, a hydroxy group, a C1-6 alkoxy group, a carboxyl group, a C2-7 alkoxycarbonyl group, a 5 to 7-membered cycloalkyl group, a phenyl or naphthyl group; a C2-6 hydroxyalkyl group; an aliphatic acyloxyalkyl group having a C2-7 acyl group and a C1-6 alkyl group; a C1-6 alkyl group substituted with a C1-6 alkoxy group, a carboxyl group, a C2-7 alkoxycarbonyl group, a C2-7 alkoxycarbonyl group substituted with a phenyl or naphthyl group, a carbamoyl group, a mono- or di-(C1-6 alkyl)-substituted carbamoyl group or a cyano group; a benzoyl or naphthoyl group optionally substituted with one or more halogen atoms; a furoyl group or a pyridylcarbonyl group; and
R1 represents a C1-6 alkyl group optionally substituted with one or more halogen atoms, a phenyl or a naphthyl group;
the carbon atom marked “*” represents a carbon atom in (R)-configuration, (S)-configuration or a mixture thereof.
A particularly preferred compound of formula (I) is (-)-(R)-1-(3-hydroxypropyl)-5-[2-[[2-[2-(2,2,2-trifluoroethoxy)phenoxy]ethyl]amino]propyl]indoline-7-carboxamide (KMD 3213) which has the structure as shown below:
The compounds of formula (I) as well as methods for their preparation are disclosed in EP A 600 675. The compounds are said to be useful for the treatment of dysuria. KMD 3213 is disclosed in EP A 600 675 as a particularly preferred embodiment of the compounds of formula (I).
The indoline compounds of formula (I) are α-adrenoceptor antagonists. α-Adrenoceptor antagonist are generally thought to be useful in treating and preventing urinary tract disorders, such as dysuria, benign prostatic hypertrophy (BPH) or prostatic cancer (EP A 799 618 and EP A 799 619).
Furthermore, it is known that KMD 3213 is an α-adrenoceptor subtype specific antagonist, binding specifically to the α1a-receptor (S. Murata, T. Taniguchi, I. Muramatsu, British Journal of Pharmacology (1999) 127, 19-26).
Urinary outlet obstruction in patients with BPH is attributed to a mechanical component which is the urethral impression produced by the hypertrophy prostatic tissue, and a dynamic component related to the tone of urethral and prostatic smooth muscles. Stimulation of α1a-adrenoceptors of urethral and prostatic smooth muscles has been shown to cause bladder outlet obstructions in patients suffering from BPH.
Consequently, KMD 3213 was tested in animal models for its usefulness in the treatment of urinary outlet obstructions in patients with BPH (K. Akiyama, M. Hora, S. Tatemichi, N. Masuda, S. Nakamura, R. Yamagishi, M. Kitazawa, J. Pharmacol. Exp. Thera. (1999) 241, 81-91).
Moreover, it has been postulated that α-adrenoceptor antagonists are capable of preventing and treating urinary tract disorders such as BPH and prostate cancer causally (EP 799 618 and EP 799 619).
The indoline compounds of formula (I) have presently only been suggested for oral or parenteral administration. Other application forms of these compounds were not suggested previously.
In order to provide a reliable treatment for BPH the indoline compounds of formula (I), and particularly KMD 3213, have to be administered in a way that secures
The desired combination of (a), (b) and (c) was previously impossible to achieve as all previously used administration forms of the indoline compounds of formula (I), and in particularly KMD 3213 proved to show certain disadvantages.
Firstly, the bio-availability of those compounds of formula (I) when administered orally is very low (about 20%), and the half-life of compounds such as KMD 3213 is short, i.e. in the range of 4.5 to 10 hours.
Moreover, the relatively low therapeutic index of α-adrenoceptor antagonists such as the indoline compounds of formula (I) requires a constant plasma level without periodic concentration peaks as obtained by oral administration.
On the other hand, parenteral administration may often be undesirable for the patient in view of the higher effort and stress (e.g. fear of injections) and the higher risk involved. Furthermore, intramuscular or subcutaneous injection may cause local irritation of the skin or the underlying tissue. Finally, it is difficult to provide the necessary constant and effective plasma level even by parenteral administration unless constant infusions are applied.
The indoline compounds of formula (I) are relatively large compounds having a molecular mass of about 500 Da or more. KMD 3213 for example has a molecular mass of 495.5 Da. A person skilled in the art generally considers a molecular mass of as high as about 500 Da as being in a range where transdermal application is no longer possible, i.e. compounds having a molecular mass of about 400 Da or more are normally not suitable for transdermal administration.
Reference is made to Pfister (Pfister W. R. “Transdermal and Dermal Therapeutic Systems: Current Status” in the standard textbook of Ghosh, T. K., Pfister, W. R., Yum S. I. (eds) “Transdermal and Topical Drug Delivery Systems”, Chapter 2, Interpharm Press, Buffalo Grove, Ill. 1997, pp 33-112). On page 48 thereof it is stated: “In general the desirable physicochemical, biopharmaceutical and pharmacokinetic attributes of a candidate for passive TDD include the following: . . . Low molecular weight, (i.e. less than 400 daltons) . . . ”
Moreover, it is widely accepted that the MW has a large influence on the drug absorption, e.g Potts and Guy have proposed the following equation for predicting the skin permeability of drugs:
log Kp (cm/sec)=−6.3 +0.71 log Koct−0.0061 MW
(Potts, R. O. and Guy, R. H. (1992) “Predicting skin permeability”. Pharmaceutical Research 9, 663-669). According to this equation, the skin permeability constant Kp has an exponential relationship to the molecular weight (MW) of a given substance.
An even stronger dependence of drug diffusion through the stratum corneum on the molecular weight permeation of a drug has been determined by Anderson & Raykar (J. Invest. Dermatol 93 (1989) 280) who found that the permeability coefficient of a solute across the stratum corneum is inversely proportional to the 4.6th power of its molecular weight.
In view of the above, it has been very surprising that by using a device containing indoline compounds of formula (I) with a molecular size of about 500 Da, such as KMD 3213, the active agent can be administered at a steady state flux rate of about 3 mg per day across human skin for an extended period of time, e.g. for at least 24 hours, preferably for 72 hours, resulting in uniform plasma levels of the active agent.
The flux rate obtained and the corresponding plasma level are sufficient to allow for a reasonable expectation that an effective prevention or treatment of urinary tract disorders such as BPH or prostatic cancer with less side effects can be provided.
It is to be understood that the term “treatment” in the context of this invention is meant to designate causal treatment or alleviation of the symptoms of urinary tract disorders.
The present invention provides a device for transdermal administration of a compound of formula (I) in order to achieve an effect in treating or preventing urinary tract disorders, such as prostatic hypertrophy (BPH), in a mammal including human. Moreover, the invention concerns the use of said compounds of formula (I) for the preparation of a medicament for transdermal administration.
The present invention provides a device for transdermal administration of a compound of formula (I)
wherein
R represents a saturated or unsaturated C2-7 aliphatic acyl group optionally substituted with one or more halogen atoms, a hydroxy group, a C1-6 alkoxy group, a carboxyl group, a C2-7 alkoxycarbonyl group, a 5 to 7-membered cycloalkyl group, a phenyl or naphthyl group; a C2-6 hydroxyalkyl group; an aliphatic acyloxyalkyl group having a C2-7 acyl group and a C1-6 alkyl group; a C1-6 alkyl group substituted with a C1-6 alkoxy group, a carboxyl group, a C2-7 alkoxycarbonyl group, a C2-7 alkoxycarbonyl group substituted with a phenyl or naphthyl group, a carbamoyl group, a mono- or di-(C1-6 alkyl)-substituted carbamoyl group or cyano groups; a benzoyl or naphthoyl group optionally substituted with one or more halogen atoms; a furoyl group or a pyridylcarbonyl group; and
R1 represents a C1-6 alkyl group optionally substituted with one or more halogen atoms, a phenyl or a naphthyl group;
the carbon atom marked “*” represents a carbon atom in (R)-configuration, (S)-configuration or a mixture thereof.
The device of the present invention is particularly useful in treating or preventing urinary tract disorders, such as benign prostatic hypertrophy (BPH) in mammals.
The term “mammals” as used herein is to be understood to mean mammalian animals including humans.
In one embodiment of the invention the device for transdermal administration may comprise a racemic mixture of compounds of formula I.
In another, more preferred embodiment of the present invention the device for transdermal administration comprises a compound of formula (I) which is essentially in its R-isomeric form or in its S-isomeric form.
The term “essentially” as used in the present invention is intended to mean at least 95%, preferably at least 97%, more preferably at least 98% and even more preferable at least 99%. In other words, a compound that is essentially in its R-isomeric form is in an amount of at least 95% in its R-isomeric form and in an amount of less than 5% in the corresponding S-isomeric form.
In a preferred embodiment of the invention, the device for transdermal administration comprises a compound of formula (I) which is (-)-(R)-1-(3-hydroxypropyl)-5-[2-[[2-[2-(2,2,2-trifluoroethoxy)phenoxy]amino]propyl]-indoline-7-carboxamide (KMD 3213).
For achieving an effect in treating or preventing urinary tract disorders the compounds of formula (I) preferably have to be administered through mammalian skin in a steady state flux rate of at least 0.5 mg per day. More preferred are steady state flux rates of at least 1 mg/day, even more preferred are flux rates of 1-5 mg/day and especially preferred are flux rates of 2-4 mg/day.
As shown in Examples 1 and 2 (see further below) with the devices provided by the present invention, steady state flux rates of KMD 3213 through human skin of 2.9 mg/day and through mouse skin of 2.7 mg/day could be achieved.
As shown in
A preferred embodiment of the present invention is therefore a device for the transdermal administration characterized in that it allows for the administration of a compound of formula (I) through human and/or animal skin in a steady state flux rate of at least 0.5 mg/day, more preferred at least 1 mg/day, even more preferred 1-5 mg/day and in particular preferred 2-4 mg/day.
The device of the present invention may be applied to the patient's skin for at least 24 hours, preferably for 48 or 72 hours or even 7 days.
In order to achieve the desired flux rate it is important to have a sufficient concentration of dissolved drug incorporated in the device. In a preferred embodiment of the present invention the device comprises at least one layer wherein the drug is dissolved in a concentration of at least 1% (w/w), for example 1-25% (w/w), preferably about 1 to 10% (w/w), most preferably 3-7% (w/w) and particularly preferred 4-6% (w/w).
Said device of the present invention comprises transdermal therapeutic systems (TTS), such as patches or systems wherein the release of the compounds is controlled by electric or osmotic means, e.g. iontophoretic or osmotic devices which are known to the skilled artisan.
In a preferred embodiment the device of the present invention is a patch.
In general, there are two types of designs for patches: a “reservoir” type and a “matrix” type.
In the reservoir type the drug, which is typically in the form of a fluid, is contained within a walled reservoir whose basal surface is permeable to the drug. The reservoir type of TTS may contain several additional layers such as a backing layer, a semi-permeable membrane which controls the drug release rate, an adhesive layer and a removable protective film.
In the matrix type the drug is dispersed in a polymer layer.
The systems of the matrix type in their simplest version comprise a one phase (monolayer) matrix. They consist of a backing layer, a self adhesive matrix containing the active agent and a protective film which is removed prior to use.
More complicated versions comprise multi-layer matrices, wherein the drug may be contained in one or more non-adhesive polymer layers.
The TTS according to the present invention is preferably a matrix system. More preferably it is a one phase (monolayer) matrix system.
Usually the adhesive will be a pressure sensitive adhesive (PSA) or a mixture of such adhesives and will form a matrix in which the active ingredient and the other components of the TTS are incorporated.
Moreover, the adhesive should preferably be pharmaceutically acceptable in a sense that it is biocompatible, non-sensitising and non-irritating to the skin. Particularly advantageous adhesives for use in the present invention should further meet the following requirements:
Although different types of pressure sensitive adhesives may be used in the present invention, it is preferred to use adhesives showing dissolution parameters which are similar to those of the compounds of formula (I). Such a preferred pressure sensitive adhesive for use in the device of the present invention can be an adhesive of the polyacrylate type.
Polyacrylates are produced by radical polymerization of (meth)acrylic acid derivatives, wherein other suitable compounds, such as for example vinyl acetate may be used as further monomers. It is to be understood that as used herein the term “polyacrylate” comprises polymers comprising units derived from acrylic acid and/or methacrylic acid as well as copolymers and mixtures thereof.
By selection of suitable monomers, the resulting adhesives may be designed in order to have specific properties, i.e. a favourable dissolving capacity for the active agent, a desired moveability of the active agent in the matrix as well as a desired transfer rate via the skin. The transfer rate is essentially determined by the distribution coefficient and the resorption of the active agent by the skin.
The pressure sensitive adhesive of the polyacrylate type may be a homopolymer and/or copolymer of at least one acrylic and/or methacrylic acid derivative in the form of a solution in an organic solvent (solution type). The polyacrylate type adhesive may be in a crosslinkable or non-crosslinkable form. The crosslinking agent links the polymer chains via reactive groups. This may result in increased cohesion of the adhesive.
Advantageously, the polymer adhesive of the polyacrylate type contains at least one of the following monomers:
Acrylic acid, acrylamide, hexyl acrylate, 2-ethyl-hexyl acrylate, hydroxy ethyl acrylate, octyl acrylate, butyl acrylate, methyl acrylate, glycidyl acrylate, methyl acrylate, methacrylic acid, methacrylamide, hexyl methacrylate, 2-ethyl-hexylamide acrylate, octyl methacrylate, methyl methacrylate, glycidyl methacrylate, vinyl acetate, vinylpyrrolidone, allyl acrylate.
More preferably the polymer adhesives of the acrylate type are cross-linkable adhesives polymerized from a combination of the following monomers:
As the preferred crosslinking agents the following compounds may be mentioned: diphenyl-methan-4-diisocyanate, hexamethylene diisocyanate, isophoron diisocyanate, titanium acetylacetonate, aluminium acetylacetonate, iron acetylacetonate, zinc acetylacetonate, magnesium acetylacetonate, zirconium acetylacetonate, 2-ethyl-1,3-hexanediol-titanate, tetra-iso-octyl-titanate, tetra-nonyl-titanate, polyfunctional propylene imine derivatives, ether derivatives of melamine formaldehyde resins, highly methylated urethane resins, imino melamine resins.
The non-crosslinkable adhesives of the solution type may advantageously be polymerized from a combination of the following monomers:
Moreover, some adhesives may be used in the form of aqueous dispersions (dispersion type). The use of these dispersion type adhesives may involve the further advantage that during coating and drying no flammable or toxic solvents evaporate. Dispersion type adhesives may advantageously be polymerized from a combination of the following monomers:
Suitable polyacrylates for use in the present invention are cross-linked using multivalent metal ions, in order to improve the physical properties of the adhesive or to adapt it to the specific requirements. The metal ions are normally employed in the form of metal chelates which are soluble in organic solvents. Particularly suitable crosslinking agents are aluminium acetyl acetonate and titanium acetyl acetonate.
If the adhesive used according to the present invention is a polyacrylate adhesive, the solvent capacity is generally dependent on the type and amount of free functional groups in the adhesive.
Most preferred adhesives for use in the device of the present invention are polyacrylates with polar groups, especially with free hydroxy- and/or carboxyl groups. Examples of such adhesives are polyacrylates wherein polar monomers such as e.g. hydroxy-ethyl acrylate, hydroxy-ethyl methacrylate, acrylic acid or methacrylic acid in an amount of about 1-10% (w/w), more preferred in an amount of 3-8% (w/w), most preferred in an amount of 4-6% (w/w) are used. Those adhesives are commercially available under the tradename Duro-Tak® (National Starch & Chemicals; Hamburg).
Even more preferred for use in the device of the present invention are adhesives of the polyacrylate type wherein hydroxy-ethyl acrylate and/or hydroxy-ethyl methacrylate monomers are incorporated during polymerization in an amount of 3-8% (w/w), most preferred in an amount of 4-6% (w/w).
Such an adhesive may be obtained in line with the general procedure described in U.S. Pat. No. 5,498,418 as follows: The adhesive can be obtained by radical polymerisation in a first stage of a mixture consisting of 21 to 40% by weight vinyl acetate, 55 to 70% by weight of an acrylic acid-C2-8-alkyl ester, and 3 to 10% by weight of an acrylic acid-C2-4-hydroxyl acryl ester, with 100% by weight monomers in the mixture, in an organic solvent, whereafter in a second stage a conventional crosslinking agent in an organic solvent and the active ingredient in the quantity required for the intended use of the transdermal device (plaster) is admixed, if necessary in an organic solvent, and finally in a third stage the resulting mixture of the particular acrylate-vinyl acetate copolymer is crosslinked in an additional stage, accompanied by heating and the removal of the organic solvent or mixture of solvents used; the resulting active ingredient is “built into” the adhesive substance in a special manner by the subsequent and additional crosslinkage of the special acrylate-vinyl acetate copolymer. The acrylate-vinyl acetate copolymer has a relative viscosity of 3.0 to 4.2 at 20° C.
Preferably the mixture of monomers contains 2-ethylhexylacrylate and hydroxyethylacrylate in addition to vinyl acetate. Preferably the subsequent crosslinkage of the special acrylate-vinyl acetate copolymer is performed with a titanium acid ester consisting of polybutyl titanate and/or titanium acetylacetonate, more particularly in a quantity of 0.3 to 3% by weight thereof, the percentages by weight being related to the weight of the copolymer.
A process for producing a TTS according to the invention may also include the steps of applying a solution of a copolymer, containing the active ingredient in the required amount for the intended use of the TTS and a conventional crosslinker or mixture thereof, and obtained by the radical polymerisation of a mixture of monomers consisting of 21 to 40% by weight vinyl acetate, 55 to 70% by weight of an acrylic acid-C2-8-alkyl ester and 1 to 10% by weight of an acrylic acid-C2-4-hydroxyalkylester, in the required layer thickness to the protective film of the TTS, and removing the solvent or mixture of solvents by heating, thus effecting an additional crosslinking of the special acrylate-vinyl acetate copolymer.
One embodiment of such a process is characterized in that the acrylate-vinyl acetate copolymer, the active ingredient and the crosslinking agent are initially dissolved in a solvent which contains 20 to 40% by weight of ethanol or an ethanol-methanol mixture, with a solids proportion consisting of 40 to 60% by weight of the mixture of the special acrylate-vinyl acetate copolymer, crosslinking agent and the active ingredient.
A particular working example for the preparation of such a acrylate-vinyl acetate adhesive is disclosed in U.S. Pat. No. 5,498,418, col. 2, line 61 to col. 3, line 10, hereby incorporated by reference.
An especially preferred adhesive for use in the present invention is the commercially available adhesive DuroTak® 387-2287 (National Starch & Chemicals; Hamburg).
For the preparation of the TTS according to the invention, a compound of formula (I), such as KMD 3213, is solved or suspended in ethanol or another suitable organic solvent and subsequently the adhesive is added while stirring.
If the adhesive contains a suitable solvent system, the active agent may be directly added to the adhesive solution. Further auxiliary agents may be added either to the adhesive solution, the solution of the active agent or the adhesive solution containing the active agent.
In one particular preferred embodiment of the present invention the device of the present invention is a one phase matrix, wherein one or more compounds of formula (I) are dissolved in a pressure sensitive adhesive of the acrylate type in an amount of 1-10% (w/w), preferably 3-7% (w/w), and most preferred 4-6% (w/w), and wherein said acrylate preferably contains free polar groups, such as hydroxy groups or carboxy groups, as described further above. If a 7-day patch is desired, higher drug concentrations will generally be required.
The thickness of the adhesive layer may be between 0.01 and 0.30 mm, preferably between 0.02 and 0.20 mm and most preferably between 0.03 and 0.10 mm.
In a further preferred embodiment, the device further includes a solubilizer.
A solubilizer is an additive that inhibits the crystallisation of the active agent during storage of the device. Examples of solubilizers known in the art are, e.g. phthalic acid esters, adipic acid ester, monoglycerides, diglycerides, triglycerides, fatty acids and esters and derivatives thereof, higher alcohols and their derivatives, derivatives of nonylphenol or octylphenol, derivatives of sorbitol or mannitol, non-ionogenic tensides, polyoxyethylene alkyl ethers, derivatives of ricinus oil, sitosterin or polyvinylpyrrolidone.
Preferred solubilizers for use in the device of the present invention are solubilizers which are capable of keeping the compounds of formula (I) in solution if said device is stored for a prolonged period of time.
It is presently considered that preferred solubilizers for inhibiting the precipitation of the compounds of formula (I) are additives having a pKa of about 4.5 to 6.0, more preferred 4.5 to 5.5, even more preferred between 4.8 and 5.1 and particularly preferred about 5.0 such as e.g. carboxylic acids, including particularly fatty acids.
In a preferred embodiment the devices of the present invention thus contain a solubilizer, wherein said solubilizers are carboxylic acids. Most preferred solubilizers are fatty acids having a PKa of 4.8 to 5.1 and at least 10 carbon atoms and which may or may not have one or more double bonds.
In an even more preferred embodiment of the present invention the solubilizer may be chosen from the group comprising lauric acid, linoleic acid, stearic acid, palmitic acid and oleic acid.
A particularly preferred solubilizer for use in the device of the present invention is oleic acid.
The solubilizer is preferably present in an amount of about 50 to 500 mol %, more preferred in an amount of 100 to 400 mol %, even more preferred in an amount of 100 to 300 mol % and particularly preferred in an amount of about 200 mol % based on the active compound.
If for example KMD 3213 is used as the active ingredient, then oleic acid is preferably used in an amount of approximately 50 to 500 mol %, i.e. in an amount of 28 to 280% (w/w) based on the amount of KMD 3213.
The device of the present invention may therefore contain oleic acid in a concentration of about 0.28% to 28% (w/w) in a layer containing 1 to 10% (w/w) KMD 3213. Typically, KMD 3230 may be present in a concentration of 5% (w/w) in the adhesive layer, which may also contain about 5 to 6% (w/w) oleic acid.
The device of the present invention may further comprise a penetration enhancer. Penetration enhancers are additives which enhance the penetration of the active agent through mammalian skin. Examples of penetration enhancers are well known to the skilled artisan and comprise citrate; fatty acids; fatty acid esters; glycerol and esters thereof such as e.g. glycerol monolaurate (GML); alcohols with up to 8 carboxylic atoms, such as ethanol, 1,2-propandiol, dexpanthenol or polyethyleneglycol; mixtures of alcohol and water; vitamin E and derivatives thereof; copolymers of ethylene and vinyl acetate; polyvinylpyrrolidone; copolymers of polyvinylpyrrolidone and vinyl acetate; polypropyleneglycol.
Although the addition of a penetration enhancer may be possibly useful in some embodiments of the invention, it is usually not necessary. As shown in Example (I), flux rates of 2.7 to 2.9 mg KMD 3213 per day were achieved using a one phase matrix type TTS.
In a preferred embodiment the device of the present invention is therefore devoid of any additive that enhances the penetration of the compounds of formula (I) through mammalian skin.
In other embodiments of the invention the device may comprise additional additives such as stabilizers or swellable agents which are well known to the skilled artisan.
In a preferred embodiment of the present invention, the device has a basal surface area of 5 to 50 cm2, particularly of 10 to 20 cm2. It goes without saying that a device having a surface area of, say, 20 cm2 is pharmacologically equivalent to and may be exchanged by two 10 cm2 devices or four 5 cm2 devices having the same drug content per cm2. Thus, the surface areas as indicated herein should be understood to refer to the total surface of all devices simultaneously administered to a patient.
Providing and applying one or several devices according to the invention has the pharmacological advantage over oral therapy that the attending physician can titrate the optimum dose for the individual patient relatively quickly and accurately, e.g. by simply increasing the number or size of devices given to the patient. Thus, the optimum individual dosage can often be determined after a time period of only about 3 weeks with low side effects.
A preferred content of a compound of formula I, such as KMD 3213 in the devices according to the invention is in the range of 0.1 to 2.0 mg/cm2. Still more preferred are 0.20 to 1.0 mg/cm2. If a 7 day patch is desired, higher drug contents will generally be required.
The device used in the present invention is preferably a patch having a continuous adhesive matrix in at least its center portion containing the drug. However, transdermal equivalents to such patches are likewise comprised by the present invention, e.g. an embodiment where the drug is in an inert but non-adhesive matrix in the center portion of the device and is surrounded by an adhesive portion along the edges.
The device of the present invention may further comprise a backing film, which is a film being impermeable to the active compounds. Such a film may consist of polyester, polyamide, polyethylene, polypropylene, polyurethane, polyvinylchloride or of combinations of the aforementioned materials which may or may not be coated with an aluminium film or with aluminium vapour. The thickness of the backing film may be between 10 and 100 μm, preferably between 20 and 40 μm.
The device of the present invention may further contain a release liner foil, which will be removed immediately prior before the device will be brought into contact with the mammalian skin. The release liner foil may consist of polyester, polyethylene or polypropylene which may or may not be coated with aluminium film or aluminium vapour or fluoropolymers. Typically, the thickness of such a release liner ranges between 20 and 300 μm and preferably between 50 and 100 μm.
The device according to the present invention is prepared by a manufacturing process comprising preparing a drug loaded adhesive, coating, drying or cooling and lamination to get the bulk product, converting the laminate into patch units via cutting and packaging.
In a further aspect, this invention relates to the use of a compound of formula (I), for example KMD 3213, for preparing a medicament for transdermal administration.
Such a medicament may comprise the devices described above as well as ointments, creams, sprays, gels or films, and the like, provided that a steady state flux rate of at least 0.5 mg per day through the mammalian skin is achieved. Even more preferred are steady state flux rates of at least 1 mg/day, e.g. 1 to 5 mg/day or 2 to 4 mg/day.
In a preferred embodiment a compound of formula (I) is used for preparing a medicament, wherein the medicament is a patch of the matrix type, and most preferably a patch of the one phase matrix type.
In a particular preferred embodiment a compound of formula (I) is used for preparing a medicament, which is a one phase matrix type patch, wherein said compound is dissolved in the adhesive layer and wherein the adhesive is a of the polyacrylate type including polar groups.
Said medicament is particularly useful in treating and preventing urinary tract disorders, such as benign prostate hypertrophy and prostatic cancer and/or symptoms associated with these conditions.
In a still further aspect, this invention relates to a method of treating urinary tract disorders, such as benign prostatic hypertrophy (BPH), by applying on a patient in need thereof the device containing a compound of formula (I) as described above.
The invention and the best mode for carrying it out will be explained in more detail in the following non-limiting examples.
A TTS using a polyacrylate based pressure sensitive adhesive was prepared as follows.
1 g of (-)-(R)-1-(3-hydroxypropyl)-5-[2-[[2-[2-(2,2,2-trifluoroethoxy)phenoxy]ethyl]amino]propyl]indoline-7-carboxamide (KMD 3213) was solved in 8 g ethanol, 1 g of oleic acid and 32.1 g of a solution containing 18 g of DuroTak® 387-2287 (in ethylacetate) were added while stirring. The resulting mixture was stirred (350 u/min) approximately one hour until a homogenous dispersion was obtained.
The dispersion was coated onto a polyester release liner (SCOTCHPAK® 1022) with a suitable doctor knife and the solvents were removed in a drying oven at a temperature of 50° C. for about 30 minutes to obtain an adhesive matrix of 76 g/m2 coating weight, which contained 5% (w/w) drug. The dried matrix film was laminated with a polyester type backing foil (SCOTCHPAK® 1109). The individual patches were punched out of the complete laminate to a desired patch size (for example 5 cm2, 10 cm2, 20 cm2, 30 cm2) and sealed into pouches under the flow of nitrogen. The obtained patches were studied using several test methods.
A TTS using a polyacrylate based pressure sensitive adhesive was prepared as follows.
1 g of KMD 3213 was solved in 8 g ethanol, 1.2 g of oleic acid and 31.8 g of a solution containing 17.8 g of DuroTak® 387-2287 (in ethylacetate) were added while stirring. The resulting mixture was stirred (350 u/min) approximately one hour until a homogenous dispersion was obtained.
The dispersion was coated onto a polyester release liner (SCOTCHPAK® 1022) with a suitable doctor knife and the solvents were removed in a drying oven at a temperature of 50° C. for about 30 minutes to obtain an adhesive matrix of 81 g/m2 coating weight, which contained 5% (w/w) drug. The dried matrix film was laminated with a polyester type tacking foil (SCOTCHPAK® 1109). The individual patches were punched out of the complete laminate to a desired patch size (for example 5 cm2, 10 cm2, 20 cm2, 30 cm2) and sealed into pouches under the flow of nitrogen. The obtained patches were studied using several test methods.
0.75 g of KMD 3213 was solved in 4 g ethanol, 0.5 g of Kollidon 90F and 15.6 g of a solution containing 8.75 g DuroTak® 387-2287 (in ethylacetate) were added while stirring. The resulting mixture was stirred (700 u/min) approximately one hour until a homogenous dispersion was obtained.
The dispersion was coated onto a polyester release liner (SCOTCHPAK® 1022) with a suitable doctor knife and the solvents were removed in a drying oven at a temperature of 50° C. for about 30 minutes to obtain an adhesive matrix of 90 g/m2 coating weight, which contained 7.5% (w/w) drug. The dried matrix film was laminated with a polyester type tacking foil (SCOTCHPAK® 1109). The individual patches were punched out of the complete laminate to a desired patch size (for example 5 cm2, 10 cm2, 20 cm2, 30 cm2) and sealed into pouches under the flow of nitrogen. The obtained patches were studied using several test methods.
0.5 g of KMD 3213 was solved in 4 g ethanol, 0.5 g of isopropylmyristate and 16.1 g of a solution containing 9 g DuroTak® 387-2287 (in ethylacetate) were added while stirring. The resulting mixture was stirred (700 u/min) approximately one hour until a homogenous dispersion was obtained.
The dispersion was coated onto a polyester release liner (SCOTCHPAK® 1022) with a suitable doctor knife and the solvents were removed in a drying oven at a temperature of 50° C. for about 30 minutes to obtain an adhesive matrix of 55 g/m2 coating weight, which contained 5% (w/w) drug. The dried matrix film was laminated with a polyester type tacking foil (SCOTCHPAK® 1109). The individual patches were punched out of the complete laminate to a desired patch size (for example 5 cm2, 10 cm2, 20 cm2, 30 cm2) and sealed into pouches under the flow of nitrogen. The obtained patches were studied using several test methods.
Drug Release in Vitro (Flux Across Dialysis Membrane):
The assay was performed according to Tanojo et al. (journal of Controlled Release 45 (1997), 41-47).
In this test, the patch showed a high release rate per area unit. Due to a fast depletion of the reservoir the drug release rate was time dependent as expected.
Skin Permeation:
The skin permeation of KMD 3213 was also evaluated on hairless mouse skin and human skin. Human skin penetration assays were performed as described by Tanojo et al. in Journal of Controlled Release 45 (1997), 41-47. The concentration of KMD 3213 was measured by HPLC with a Symetry Shield RP-8, 3.9*150 mm 5 μm column; T=35° C.; eluent: water/acetonitrile/trifluoracetic acid 800/200/1 (v/v/v); dectetion UV at 225 nm; flux rate 1.5 ml/min; injection volume: 100 μl at 23° C.
The flux measurements on hairless mouse skin were conducted using a TTS area of 2.55 cm2 fixed on mouse abdominal and back skin in a horizontal diffusion cell. Immediately thereafter the acceptor chamber of the cell was filled with phosphate buffer solution (0.066 molar) previously adjusted to 32±0.5° C. and pH 6.2, in an air-bubble free state, and the release medium thermostatted to 32±0.5° C. At the time of sampling (after 3, 6, 24 and 48 hours) the release medium is exchanged with fresh medium thermostatted at 32±0.5° C. KMD 3213 was measured with HPLC as explained above.
On hairless mouse skin a steady state skin permeation rate of approximately 2.7 mg/20 cm2 per day was observed. On human skin the steady state flux rate was equivalent to 2.9 mg/20 cm2 per day.
The cumulative permeation rate on human skin of the device produced according to example 1 is shown in
The permeation rates on human or mouse skin of the devices produced according to examples 1 to 4 are shown in table 1.
n.d. = not determined
Stability:
Stability tests of the devices produced according to Examples 1 and 2 revealed that nucleation or crystal growth could not be observed during a storage at 40° C. and 75% relative humidity for at least 3 months.
| Number | Date | Country | Kind |
|---|---|---|---|
| 01121687.6 | Sep 2001 | EP | regional |
| Filing Document | Filing Date | Country | Kind | 371c Date |
|---|---|---|---|---|
| PCT/EP02/10229 | 9/12/2002 | WO | 5/28/2004 |
