Patent Application
20050226910
The present invention relates to a transdermal delivery system for local anesthetic, immunosuppresive and neurologically effective drugs, as well as for polypeptides and protein-based drugs. More particularly, the present invention relates to a transdermal delivery system for such drugs as granisetron, lidocaine, and cyclosporine in a transdermal drug delivery system (TDDS).
The present invention is a modification of the invention described and claimed in WO 02/09763.
In WO 02/09763 there is described and claimed a transdermal delivery system for analgesic, anti-pyretic and anti-inflammatory drugs comprising an analgesic, anti- pyretic or anti-inflammatory drug in combination with water-miscible tetraglycol and water for dissolving said drug in hydrogel form.
As stated, WO 02/09763 teaches a transdermal delivery system especially useful for non-steroidal-anti-inflammatory drugs.
It has now been found that not only non-steroidal-anti-inflammatory drugs can be effectively transported across the skin by the drug delivery system described in said Specification, but that many other types of active molecules may also be delivered transdermally utilizing a combination of water-miscible tetraglycol and water for dissolving such drugs in hydrogel form and this especially when said transdermal delivery system is in the form of a microemulsion. Thus it has now been discovered that by mixing a drug model and tetraglycol in a microemulsion, in a plain solution as well as in patches or hydrogels containing an ionized polymer, the obtained drug delivery system resulted in an enhanced percutaneous permeation thus increased the drug's potential of curing, healing or improving its therapeutic effect.
Thus according to the present invention there is now provided a transdermal delivery system for local anesthetic, immunosuppresive and neurologically effective drugs, as well as for polypeptides and protein-based drugs comprising a local anesthetic, immunosuppresive or neurologically effective drug, as well as a polypeptide or protein-based drug in combination with water-miscible tetraglycol and water for dissolving said drug in hydrogel form.
In preferred embodiments of the present invention said drug is selected from the group consisting of granisetron, lodocaine, and cyclosporine.
The novel transdermal drug delivery system (TDDS) is preferably applied using a unilayer polymeric patch with adhesive margins, providing an effective and convenient mode of drug delivery.
In principle, transdermal administration of medications has several advantages: elimination of variations in plasma concentration after gastrointestinal absorption, elimination of hepatic first pass metabolism, and avoidance of gastrointestinal intolerance. The dermal administration of drugs may produce less gastrointestinal (GI) adverse reactions as compared with the oral route, as it is assumed that some of the GI adverse effects are due to the local action of the drug (e.g., in stomach). The transdermal route of administration may be of particular significance in infants and in children because of their greater surface area to weight ratio. The epidermis of the full term neonate (but not that of the premature infant) is well developed and similar to that of an older child or adult. But the thinner skin with relatively rich blood supply of the infant and child may affect the pharmacokinetics of drugs administered by transdermal delivery systems, this has obvious therapeutic advantages, but it may have also toxic significance (the majority of cases of percutaneous drug toxicity have occurred in infants: aniline dye, hexachlorophene, iodine, and alcohol poisoning). Transdermal drug absorption can significantly alter drug kinetics depending on a number of factors, such as site of application, thickness and integrity of the stratum corneum epidermis, size of the molecule, permeability of the membrane of the transdermal drug delivery system, state of skin hydration, pH of the drug, drug metabolism by skin flora, lipid solubility, depot of drug in skin, alterations of blood flow in the skin by additives and body temperature.
While topical drug delivery systems have been used for centuries for the treatment of local skin disorders, the use of the skin as a route for systemic drug delivery is of relatively recent origin. Transdermal administration of drugs has been established in adults in relation to nitroglycerine, estrogens, scopolamine, and fentanyl. Although lacking adequate pediatric studies, scopolamine and fentanyl are often used in pediatric patients by this route. There are data on the pharmacokinetics and clinical use of transdermal administration of theophylline in human neonates: after a single application to the skin an hydrogel disc system resulted in therapeutic concentrations of theophylline for up to 3 days in neonates with apnea.
Many drugs are practically insoluble in water or slightly soluble even in their ionized form. Therefore, dissolution of active agents in topical and transdermal preparations usually requires incorporation of an alcohol. However, the use of solvents like alcohols in topical preparations may lead to precipitation of the drug on the skin upon evaporation of the solvent once spread over the skin area. In situations in which the application area is occluded, such as in transdermal patches, alcohol presence may cause a skin irritation and inflammatory conditions.
The present invention obviates this problem since it enables the preparation of transdermal delivery systems for drugs usually requiring alcohol for the dissolution thereof, utilizing water-miscible tetraglycol instead of the standard alcohols used heretofor.
Thus, the present invention also provides a transdermal delivery system for an alcohol-miscible drug comprising an alcohol-miscible local anesthetic, immunosuppresive or neurologically effective drug, as well as a polypeptide or protein- based drug in combination with water-miscible tetraglycol and water for dissolving said drug in hydrogel form wherein said transdermal delivery system is in the form of a microemulsion.
Another aspect of the present invention comprises the method of preparing transdermal drug delivery systems. This method includes preparation of ‘easy-to-make’ patches containing the drug, tetraglycol and other ingredients, which adhere spontaneously to the skin surface. The manufacturing method of transdermal patches of the present invention is unique by the virtue of the guar-based polymer to solidify the drug-containing liquid within few minutes to a patch at any desired size, shape and thickness. The manufacturing of the composition can be designed in such a way that once the polymer is dispersed in a liquid mixture containing the drug in a tetraglycol- containing microemulsion, the mixture is molded to a patch—a process that takes few minutes at the best case to several hours at the worst. The obtained patch is self- adhesive to the skin surface, requiring only a covering sheet with adhesive margins to occlude the system from any kind of evaporation or contamination during treatment.
It should be defined, that by the term “comprising” as used in the present invention is meant that various other inactive ingredients, compatible drugs and medicaments can be employed in the compositions as long as the critical tetraglycol or ionized polymers are present in the compositions and are used in the manner disclosed.
All percentages herein are by weight unless otherwise specified.
As stated hereinbefore, the transdermal delivery systems of the present invention comprise an effective amount of:
In addition, the transdermal systems of the present invention preferably include further components as follows:
Further preferred components include:
Preferred compositions according to the present invention are pharmaceutically accepted and easy-to-apply skin-adhesive systems containing NSAIDs as active ingredients. More particularly, these systems composed of tetraglycol (glycofurol, tetrahydrofurfuryl alcohol polyethyleneglycol ether) (TG) and an ionized polymer such as hydroxypropyl guar hydroxypropyltrimonium chloride (guar-based polymer, GP), which assist in dissolving or solubilizing the active materials in a hydrogel form, and facilitate their penetration through the lipophilic strata of the skin.
While the invention will now be described in connection with certain preferred embodiments in the following examples and with reference to the accompanying figures so that aspects thereof may be more fully understood and appreciated, it is not intended to limit the invention to these particular embodiments. On the contrary, it is intended to cover all alternatives, modifications and equivalents as may be included within the scope of the invention as defined by the appended claims. Thus, the following examples which include preferred embodiments will serve to illustrate the practice of this invention, it being understood that the particulars shown are by way of example and for purposes of illustrative discussion of preferred embodiments of the present invention only and are presented in the cause of providing what is believed to be the most useful and readily understood description of formulation procedures as well as of the principles and conceptual aspects of the invention.
In the drawings:
a and 6b are graphical representations of the concentrations of cyclosporine found in the epidermal (A) and dermal (B) layers and
This example is a study performed in vitro using porcine ear skin as described below:
Diffusion cells: The permeability of granisetron through porcine skin was measured in-vitro with a Franz diffusion cell system. The diffusion area was 1.767 cm2 (15 mm diameter orifice), and the receptor compartment volumes varied between 1.1 to 12 ml. The solutions on the receiver side were stirred by externally driven, teflon- coated magnetic bars.
Skin preparation: Full-thickness porcine skin was excised from fresh ears of slaughtered white pigs (breeding of Landres and Large White, locally grown in Kibbutz Lahav, Israel). Skin sections (about 2×2 cm) were cut and subcutaneous fat was removed from the skin sections with a scalpel. Transepidermal water loss measurements (TEWL, Dermalab® Cortex Technology, Hadsund, Denemark) was performed and only those pieces that the TEWL levels were within specification (<10 g/m2 h) were mounted in the diffusion cells.
Permeation study: 0.200 mg specimens of three granisetron preparations [5% aqueous solution, 5% in tetraglycol-containing microemulsion, and 5% granisetron in a same microemulsion gelled with ionized polymer—see Table 1 below] were applied on the skin. The receiver solutions (PBS, pH 7.4) were sampled at predetermined time intervals, and the cells were replenished to their marked volumes with fresh buffer solution. Samples were kept at −20° C. until analyzed by HPLC.
Calculations: As a result of a large volume sampling from the receiver solution and replacing with equal volumes, the solution is constantly diluted. Taking this into account, cumulative drug permeation (Qt) is calculated from the following equation:
where Ct is the drug concentration of the receiver solution at each sampling time, Ci is the drug concentration of the i-th sample, and Vr and Vs are volumes of the receiver solution and the sample, respectively. Data were expressed as the cumulative granisetron permeation per unit of skin surface area, Qt/S (S=1.767 cm2).
Results:
GRN = granisetron
Chremophor RH40 = polyoxyl 40 hydrogenated castor oil USP24/NF19 (PEG-40 hydrogenated castor oil) [Manufacturer: BASF, Germany].
Arlacel 186 = glyceryl oleate [Manufacturer: Uniqema, UK].
Jaguar C-162 = guar-based polymer (Guar gum, 2-hydroxypropyl 2-hydroxy-3-(trimethylammonio)propyl ether chloride;
CTFA/INCI name: Hydroxypropyl guar hydroxypropyltrimonium chloride) [Manufacturer: Rhone-Poulenc, France].
This example includes experiments that were performed in vitro using excised rat skin and in vivo in rats as described below:
In vitro: The diffusion testing, skin preparation, permeation and calculations were performed exactly as described for granisetron, except that the skin was taken from the abdominal side of Sprague-Dawley rats. The rats (around 500 g) were killed by aspiration of ethyl ether vapors and the abdominal hair was then trimmed off with a hair clipper. Sections of full-thickness abdominal skin were excised from the fresh carcasses of the animals. Subcutaneous fat was removed with a scalpel, and the skin sections were mounted in the diffusion cells. The skin was placed with the stratum corneum facing up on the receiver chambers, and then the donor chambers were clamped in place. The excess skin was trimmed off and the receiver chamber, defined as the side facing the dermis, was filled with phosphate buffer (4 mM, pH=7.4).
In vivo: The in-vivo skin penetration was evaluated in anesthetized rats. Anesthetized (15 mg/kg pentobarbital sodium i.p.) rats (Sprague-Dawley, 250-300 g) were placed on their back, the abdominal hair was trimmed off, and the skin was washed gently with distilled water. Drug-containing preparations were applied on a restricted skin, surface (4.9 cm2). Blood samples were taken from the tail vein into heparanized tubes at t=0, 1, 2, 3, 4, 5, and 6 hours from the time of drug application. In a separated study 18 anesthetized rats were applied with (a) 2.5% lidocaine base in tetraglycol-containing microemulsion gelled with guar-based ionized polymer [n=9], and (b) a commercial product known as EMLA 5% cream (Astra) containing 2.5% lidocaine (as base) and 2.5% prilocaine [n=9]. After 15, 30 and 60 minutes of in vivo study (3 animals were designated for each time and for each group), the products were removed from the animals and they were killed by aspiration of ethyl ether. The drug-exposed skin areas were swabbed 3-4 times with 3 layers of gauze pads, washed for 30 seconds with running water, wiped carefully and harvested from the animals. The excised skin sections were rinsed with phosphate buffer (pH=7.4), and heat-separated (60° C., 60 seconds) to its epidermal and dermal layers. Each layer was cut to small pieces and inserted in 2-ml vials. The tissue in each vial was extracted by ethyl alcohol. Each extraction was performed by incubation in a 40° C. shaking water bath (150 rpm) for 1 hour. The extracts were injected into the HPLC system.
Formulations Tested In-Vitro and In-Vivo (See Table 2):
While the in vitro penetration showed quantitative amounts of penetrating drug, the in vivo study failed to show systemic plasma levels that were above the limit of HPLC assay quantitation. To extrapolate the penetration rates of drug quantities across the skin (fuxes), it was necessary, therefore, to monitor the drug in the skin layers.
LID = Lidocaine
Chremophor RH40 = polyoxyl 40 hydrogenated castor oil USP24/NF19 (PEG-40 hydrogenated castor oil) [Manufacturer: BASF, Germany].
Arlacel 186 = glyceryl oleate [Manufacturer: Uniqema, UK].
Jaguar C-162 = guar-based polymer (Guar gum, 2-hydroxypropyl 2-hydroxy-3-(trimethylammonio)propyl ether chloride;
CTFA/INCI name: Hydroxypropyl guar hydroxypropyltrimonium chloride) [Manufacturer: Rhone-Poulenc, France].
This example includes experiments that were performed in vivo in rats as described below:
The in-vivo skin penetration was evaluated in anesthetized rats. Anesthetized (15 mg/kg pentobarbital sodium i.p.) rats (Sprague-Dawley, 250-300 g) were placed on their back, the abdominal hair was trimmed off, and the skin was washed gently with distilled water. Drug-containing preparations were applied on a restricted skin surface (4.9 cm2). After 2 and 4 hours of in vivo study (3 animals were designated for each time and for each group), the products were removed from the animals and they were killed by aspiration of ethyl ether. The drug-exposed skin areas were swabbed 3-4 times with 3 layers of gauze pads, washed for 30 seconds with running water, wiped carefully and harvested from the animals. The excised skin sections were rinsed with phosphate buffer (pH=7.4), and heat-separated (60° C., 60 seconds) to its epidermal and dermal layers. Each layer was cut to small pieces and inserted in 2-ml vials. The tissue in each vial was extracted by ethyl alcohol. Each extraction was performed by incubation in a 40° C. shaking water bath (150 rpm) for 1 hour. The extracts were injected into the HPLC system.
Test Formulations (See Table 3):
Results:
PEG 400 = polyethylene glycol 400 (or polyoxyethylene glycol 400, Macrogol 400)
Jaguar C-162 = guar-based polymer (Guar gum, 2-hydroxypropyl 2-hydroxy-3-(trimethylammonio)propyl ether chloride;
CTFA/INCI name: Hydroxypropyl guar hydroxypropyltrimonium chloride) [Manufacturer: Rhone-Poulenc, France].
It will be evident to those skilled in the art that the invention is not limited to the details of the foregoing illustrative examples and that the present invention may be embodied in other specific forms without departing from the essential attributes thereof, and it is therefore desired that the present embodiments and examples be considered in all respects as illustrative and not restrictive, reference being made to the appended claims, rather than to the foregoing description, and all changes which, come within the meaning and range of equivalency of the claims are therefore intended to be embraced therein.
| Number | Date | Country | Kind |
|---|---|---|---|
| 150334 | Jun 2002 | IL | national |
| Filing Document | Filing Date | Country | Kind | 371c Date |
|---|---|---|---|---|
| PCT/IL03/00513 | 6/16/2003 | WO | 12/15/2004 |
