Patent Application
20090099502
The present invention relates to a microneedle device having a plurality of microneedles on a substrate, which are capable of piercing a skin for administering a drug through a skin, and a transdermal drug administration apparatus with microneedles.
The method of administering a drug by applying a drug containing patch on the skin, and allowing the drug to penetrate into the skin from the patch, has been conventionally used in general. On the other hand, the method of administering drugs with help of electrical energy, such as iontophoresis (Journal of Pharmaceutical Sciences, Vol. 76, p. 341, 1987) and electroporation (National Publication of International Patent Application No. 03-502416; Proc. Natl. Acad. Sci. USA, Vol. 90, p. 10504-10508, 1993), have been developed as methods of promoting drug uptake through the skin or mucosa. The applications of iontophoresis and electroporation are looked forward to with high expectations, as methods of promoting transdermal or transmucosal drug absorption.
Apart from this, microneedle-equipped devices are known, for instance, from National Publication of International Patent Application No. 2000-512529 (Patent document 1) as devices that increase transdermal flux by mechanically piercing the skin before releasing the transdermal drug. This kind of technology has become of particular interest because in recent years there have been many advances in pain reduction and improvement of transdermal permeability. The device has a sheet with a plurality of openings, a plurality of microblades that are integrated with the sheet and extend downwards from the sheet, and means of holding the device in position on the body surface. In this case, the drug product placed in the drug reservoir is in the form of a viscous gel. Also, the National Publication of International Patent Application No. 2004-501724 (Patent document 2) discloses transdermal delivery means of hormonal substances in which pain reduction and assured delivery of a hormonal substance are achieved by specifying the length of a number of small gauge needles at about 300 μm to 2 mm, and the needle insertion depth as about 250 μm to 2 mm.
There have been further advances in recent years. Japanese Patent Laid-Open No. 2003-238347 (Patent document 3) proposes the installation, on a substrate, of a columnar pile mainly made of saccharides that dissolve and get cleared in the living body. The functional micropile creates passages that reach the horny layer of the skin and enables delivery of the functional substance specifically to the horny layer, through a simple painless procedure, safely, and effectively. Japanese Patent Laid-Open No. 2004-65775 (Patent document 4) discloses a device having needle-like structure elements having a thin film, through which the needle part of the needle-like structure element can penetrate, present on the needle tip part of the needle-like structure element, and an adhesive is applied to the surface of this thin film.
Furthermore, in recent years, various advances have been made in the techniques of coating microneedles. National Publication of International Patent Application No. 2004-504120 (Patent document 5) discloses an interface having microneedles, wherein the skin-piercing member is coated with a reservoir medium, or is itself made of the reservoir medium, as a device for inoculating a vaccine through the skin. It is reported that biodegradable sugars (lactose, raffinose, trehalose, and sucrose), which can easily release the drug contained in them by getting dissolved, are preferable as the reservoir medium. National Publication of International Patent Application No. 2004-528900 (Patent document 6) describes the selection of the coating carrier, for the microprojection array used for transdermal administration of vaccines, etc, from among human albumin, polyglutamic acid, polyasparaginic acid, polyhistidine, pentosan polysulfuric acid, and polyamino acids. This coating carrier also rapidly dissolves when it passes through the skin and thereby releases the useful active substance. WO2005/016440 (Patent document 7) discloses coating carriers containing a polymer such as hydroxymethyl cellulose (HPMC), hydroxypropyl cellulose, dextran, polyvinyl alcohol, and polyethylene oxide. Here, because the coating carrier has fluidity, with a viscosity of 3 to 500 cps, by making some arrangements on the surface of the needles, the needle tips are automatically coated with the coating carrier. It is mentioned that because of this there is no need for a coating operation and a long period of effectiveness can be achieved. However, in this case, as the coating carrier is forced through the skin, it is difficult to control it, and there is some doubt about its practical utility.
The method of coating the microneedles of the needle structures with the drug or coating agent as described above has been mostly used for administering only small quantities of substances like vaccines because the quantity of drug that can be administered is limited to very small amounts. Particularly in the case of low molecular weight active compounds that generally do not show their action unless a significant amount is administered into the living body, the conventional type of coating carrier assumes a dissolved state after passing through the skin. So, the useful drug is released in one go and an effective level of the drug's effect cannot be sustained for a long time. For this reason, the coating technique was considered unsuitable for use with low molecular weight compounds.
Patent document 1: National Publication of International Patent Application No. 2000-512529
Patent document 2: National Publication of International Patent Application No. 2004-501724
Patent document 3: Japanese Patent Laid-Open No. 2003-238347
Patent document 4: Japanese Patent Laid-Open No. 2004-65775
Patent document 5: National Publication of International Patent Application No. 2004-504120
Patent document 6: National Publication of International Patent Application No. 2004-528900
Patent document 7: WO2005/016440
The purpose of the present invention is, therefore, to provide a microneedle device having a coating, which is effective even with a low molecular weight active compound and can sustain the effect of the drug for a long period of time, and a transdermal drug administration apparatus with microneedles.
To achieve the aforesaid purpose, various water-soluble polymers were examined for use as coating carrier for microneedles. As a result, it was found that polyvinyl alcohols, among them, particularly those with hydrolysis degree 94.5 mol % or more, had superior coating property, and better skin permeability of the drug, compared to other water-soluble polymers, which led to the completion of the present invention.
Besides this, the coating carrier with polyvinyl alcohol with hydrolysis degree 94.5 mol % or more, once fixed to the target material, does not dissolve even in an aqueous solvent, and retains its film shape. Therefore, it became clear that clearly unlike hitherto known soluble drug-releasing coating carriers, the new coating carrier functions not only as the drug carrier but also acts as the drug permeation route through a microneedle interface (microneedle device).
In short, the microneedle device of the present invention comprises a plurality of microneedles on a substrate, which are capable of piercing a skin, and the surface of the microneedles and/or the substrate is partly or entirely coated in fixed state with a coating carrier containing polyvinyl alcohol. The coating carrier preferably maintains fixed state, without completely dissolving even after the transdermal application, and the polyvinyl alcohol preferably has a hydrolysis degree of 94.5 mol % or more. The coating carrier can contain a drug.
The transdermal drug administration apparatus with microneedles of the present invention has a microneedle device comprising a plurality of microneedles on a substrate, which are capable of piercing a skin, and the surface of the microneedles and/or the substrate is partly or entirely coated in fixed state with a coating carrier containing a polyvinyl alcohol and a drug. The apparatus can further comprise a dissolving solution reservoir containing a drug solution or a dissolving solution for drug dissolution above the microneedle device.
Further, the transdermal drug administration apparatus with microneedles of the present invention has a microneedle device comprising a plurality of microneedles on a substrate, which are capable of piercing a skin, and a drug retainer retaining a drug and arranged above the microneedle device, and the surface of the microneedles and/or the substrate is partly or entirely coated in fixed state with a coating carrier containing polyvinyl alcohol. The apparatus can further comprise a dissolving solution reservoir containing a drug solution or a dissolving solution for drug dissolution above the drug retainer. The apparatus can further comprise an electrode for supplying electrical energy from the outside, or a sonic transducer for supplying sonic vibration energy from the outside. The polyvinyl alcohol preferably has a hydrolysis degree of 94.5 mol % or more.
A method of coating a microneedle device of the present invention comprising a plurality of microneedles on a substrate, which are capable of piercing a skin, comprises the steps of coating the surface of the microneedles and/or the substrate partly or entirely with a coating carrier containing polyvinyl alcohol, and drying and fixing the coating carrier thereto. The coating carrier can contain a drug. Also, it is preferable that, before fixing coating carrier, the polyvinyl alcohol has a viscosity of 1 to 60,000 cps, and a mean degree of polymerization of 200 to 3500.
According to the present invention, by coating microneedles with a coating carrier containing polyvinyl alcohol, in transdermal administration of the physiologically active substance (drug) using the microneedle device, we can obtain a microneedle device, which shows good skin permeability and sustainability of the drug effect of low molecular weight physiologically active substances (drugs), achievements hitherto considered difficult, and a transdermal drug administration apparatus with microneedles.
In the present invention, the surface of the microneedles 6 and/or the substrate 8 is partly or entirely (including the inner surfaces of the openings 7) coated in fixed state with a coating carrier containing polyvinyl alcohol. Here, the microneedle device of the present invention is not limited to those used for drug administration. However, in this example, the drug can be contained in the coating carrier. Also, the drug can be supplied to the microneedle device by some other means than including the drug in the coating carrier. The coating 1 is positioned, for instance, on the surface of each microneedle 6 as shown in
A microneedle (the needle part) has a microstructure, and its size (height) is preferably 50 μm to 1000 μm, more preferably 50 μm to 500 μm. Here, “microneedle” means a pointed structure, and in a broad sense, it means a needle-shaped structure or a structure including a needle-shaped structure, but it is not limited to a simple needle shape. Also, in some structures, the tip may not be pointed. So, microneedles are not restricted to those with sharp tips only. The substrate is a platform for supporting the microneedles (needle parts), and there are no particular limitations on its shape. The material of the microneedles can be silicon, silicon dioxide, ceramics, metals (stainless steel, titanium, nickel, molybdenum, chromium, cobalt, etc), and plastics, polylactic acid, polyglycolic acid, and their copolymers, etc. Examples of methods of producing microneedles include wet etching process or dry etching process of a silicon substrate, precision machining (electrical discharge machining, laser machining, dicing, etc) of metals and plastics, machine cutting, extrusion molding, emboss processing, etc. The microneedles and substrates can be shaped in an integrated manner using these methods of processing. The microneedles can be hollow. The microneedles may be made hollow by secondary processing, such as laser machining, after they are prepared.
The coating carrier used on the microneedles in the present invention contains polyvinyl alcohol of hydrolysis degree of 78 to 100 mol %. In particular, those with a hydrolysis degree of 94.5 mol % or more are preferable, especially those that are fully saponified grades, i.e., with a high hydrolysis degree are more preferable. For instance, in the case of PVA117 (KURARAY CO., LTD.), fully saponified grades have a hydrolysis degree 97 mol % or more. Preferably, the polyvinyl alcohol has a mean degree of polymerization of 200 to 3500, more preferably 1000 to 2000. When the mean degree of polymerization is less than 500, the amount of permeation tends to decrease.
The content of polyvinyl alcohol in the coating carrier is 1 to 20 wt. %, 3 to 8 wt. % being particularly preferable. To prevent dripping, the coating carrier is required to have a viscosity of about 1 to 60,000 cps, more preferably 30 to 30,000 cps, most preferably 100 to 20,000 cps.
The mean thickness of the coating is less than 50 μm, most preferably less than 25 μm, 0.1 to 10 μm for example. The thickness of the coating is generally the mean thickness of the coating measured on the surface of the microneedles after drying. In general, the thickness of the coating can be increased by applying more than one coat of the coating carrier, and drying between successive coats. The coating is made by applying the coating carrier on the surface of the microneedles by a known method, and drying. Also, the coating can be applied on the inner surfaces of hollow needle structures of the microneedles, and the lower surface, side surfaces, and upper surface of the microneedle substrate, and the inner surfaces of the openings made on the substrate.
The physiologically active substance (drug) used in the present invention is a low molecular weight compound, with no particular limitation. Low molecular weight means roughly of molecular weight 1000 or less. Compounds with molecular weight 100 to 800 are particularly suitable. There is no particular limitation on the type of drug, other than the low molecular weight. Examples include hypnotics and sedatives (flurazepam hydrochloride, rilmazafon hydrochloride, phenobarbital, amobarbital, etc), antipyretic, anti-inflammatory and analgesic agents (butorphanol tartrate, perisoxal citrate, acetaminophen, mefenamic acid, diclofenac sodium, aspirin, alclofenac, ketorpofen, flurbiprofen, naproxen, piroxicam, pentazosin, indomethacin, glycol salicylate, aminopirin, loxoprofen, etc), steroidal antiinflammatory agents (hydrocortisone, prednisolone, dexamethasone, betamethasone, etc), analeptic stimulants (methamphetamine hydrochloride, methylphenidate hydrochloride, etc), psychotropic drugs (imipramine hydrochloride, diazepam, sertraline hydrochloride, fulvoxamine maleate, paroxetine hydrochloride, citalopram hydrobromide, fuloxetine hydrochloride, alprazolam, haloperidol, clomipramine, amitriptilin, decipramine, amoxapine, maprotylin, mianserin, setiptilin, trazadone, lofepramine, milnaciplan, duroxetine, venlafaxine, chlorpromazine hydrochloride, thioridazine, diazepam, meprobamate, etizolam, etc), hormone formulations (estradiol, estriol, progesterone, norethisterone acetate, metelonon acetate, testosterone, etc), local anesthetics (lidocaine hydrochloride, procaine hydrochloride, tetracaine hydrochloride, dibucaine hydrochloride, propitocaine hydrochloride, etc), urological drugs (oxybutynine hydrochloride, tamsulosin hydrochloride, propiverin hydrochloride, etc), skeletal muscle relaxants (tizanidine hydrochloride, eperisone hydrochloride, pridinol mesylate, suxamethonium hydrochloride, etc), reproductive system drugs (ritodrine hydrochloride, meluadrine tartrate), antiepileptic drugs (sodium valproate, clonazepam, carbamazepine, etc), autonomous nervous system drugs (carpronium chloride, neostigmine bromide, bethanechol chloride, etc), anti-Parkinson drugs (pergolide mesylate, bromocriptine mesylate, trihexiphenidyl hydrochloride, amantazine hydrochloride, ropinirole hydrochloride, talipexol hydrochloride, cabergoline, droxidopa, piperiden, selegiline hydrochloride, etc), diuretics (hydroflumethiazide, furosemide, etc), respiration promoters (lobeline hydrochloride, dimorpholamine, naloxone hydrochloride, etc), antimigraine drugs (dihydroergotamine mesylate, sumatriptan, ergotamine tartrate, flunaridine hydrochloride, cyproheptadine hydrochloride, etc), antihistamines (clemastine fumarate, diphenhydramine tannate, chlorphenylamine maleate, diphenylpyraline hydrochloride, promethazine, etc), bronchodilators (tolubuterol hydrochloride, procaterol hydrochloride, salbutamol sulfate, clenbuterol hydrochloride, fenoterol hydrobromide, terbutaline sulfate, isoprenaline sulfate, formoterol fumarate, etc), cardiac stimulants (isoprenaline hydrochloride, dopamine hydrochloride, etc), coronary vasodilators (diltiazem hydrochloride, verapamyl hydrochloride, isosorbide nitrate, nitroglycerin, nicorandil, etc), peripheral vasodilators (nicametate citrate, trazoline hydrochloride, etc), antismoking drugs (nicotine, etc), circulatory organ agents (flunarizine hydrochloride, nicardipine hydrochloride, nitrendipine, nisoldipine, felodipine, amlodipine besylate, nifedipine, nilvadipine, manidipine hydrochloride, benedipine hydrochloride, enalapril maleate, temocapril hydrochloride, alacepril, imidapril hydrochloride, cilazapril, lisinopril, captopril, trandolapril, perindopril erbumine, atenolol, bisoprolol fumarate, metoprolol tartrate, betaxolol hydrochloride, arotinolol hydrochloride, celiprolol hydrochloride, carvedilol, carteolol hydrochloride, bevantolol hydrochloride, valsartan, candesartan, cilexetil, losartan potassium, clonidine hydrochloride, etc), antiarrhythmic drugs (propranolol hydrochloride, alprenolol hydrochloride, procainamide hydrochloride, mexiletine hydrochloride, nadolol, disopyramid, etc), antineoplastic agents (cyclophosphamide, fluorouracil, tegafur, procarbazine hydrochloride, ranimustine, irinothecan hydrochloride, fluridine, etc), antilipidemia drugs (pravastatin, simvastatin, bezafibrate, probucol, etc), hypoglycemic agents (glibenclamide, chlorpropamide, tolubutamide, glymidine sodium, glybzole, buformin hydrochloride, etc), peptic ulcer drugs (proglumide, cetraxate hydrochloride, spizofurone, cimetidine, glycopyrronium bromide), choleretic drugs (ursodesoxycholic acid, osalmid, etc), eneterokinetic agents (domperidone, cisapride, etc), drugs for hepatic diseases (thiopronin, etc), antiallergy drugs (ketotifen fumarate, azelastine hydrochloride, etc), antiviral drugs (acyclovir, etc), antivertigo agents (betahistine mesylate, difenidol hydrochloride, etc), antibiotics (cephaloridin, cephdinyl, cephpodoxime proxetil, cefachlor, clarithromycin, erythromycin, methyl erythromycin, kanamycin sulfate, cycloserine, tetracycline, benzylpenicillin potassium, propicillin potassium, cloxacillin sodium, ampicillin sodium, bacampicillin hydrochloride, carbenicillin sodium, chloramphenicol, etc), anti-addiction drugs (cyanamide, etc), appetite suppressants (mazindol, etc), chemotherapy drugs (isoniazid, ethionamide, pyrazinamide, etc), blood coagulation accelerators (ticlopidine hydrochloride, warfarin potassium), anti-Alzheimer drugs (physostigmine, donepezyl hydrochloride, tacrin, arecoline, xanomelin, etc), serotonin receptor antagonist antinausea drugs (ondansetron hydrochloride, granisetron hydrochloride, ramosetron hydrochloride, azasetron hydrochloride, etc), gout drugs (colchicine, probenecid, sulfinpyrazone, etc), and narcotic analgesics (fentanyl citrate, morphine sulfate, morphine hydrochloride, codeine phosphate, cocaine hydrochloride, pethidine hydrochloride, etc). As long as the molecular weight is about 1000, physiologically active substances like vaccines, low molecular weight peptides, sugars, nucleic acids, etc also can be used.
These drugs can be used singly or in combinations of two or more, and drugs in the form of inorganic and organic salts are both naturally included, as long as they are pharmaceutically permissible. Although basically the drug can be included in the coating carrier, this need not be so. Instead, it can be supplied via the through-holes (openings) made on the microneedle substrate.
The liquid composition used for coating the microneedles is prepared by mixing the biocompatible carrier, the useful active substance to be delivered, and any coating adjuvant in some cases, with a volatile fluid. There is no particular limitation on the volatile fluid, but water, dimethylsulfoxide, dimethylformamide, ethanol, isopropyl alcohol and their mixtures can be used. Water is most preferable among these. The liquid coating solution or suspension can typically have 0.1 to 60 wt. % of the beneficial, low molecular weight, physiologically active substance concentration, the preferable concentration being 1 to 30 wt. %, more preferably 3 to 20 wt. %. “Fixed” here means that the coating carrier is almost uniformly attached to the object to be coated. Immediately after the coating, coating carrier is fixed under the dry state by a known method like air drying, vacuum drying, freeze-drying, or their combinations. But it need not remain to be fixed under the dry state after the transdermal administration because it might have a water content that is at equilibrium with the surroundings, or it may retain an organic solvent, etc.
Other adjuvants known to be used in drug formulations may be added, depending on the solubility and viscosity required in the coating, to the extent that has no harmful effect on the physical integrity of the dried coating.
The microneedle device of the present invention transdermally delivers a physiologically active substance (drug) via the plurality of microneedles coated with a fixed solid or gel-form coating containing a useful physiologically active substance (drug). Various forms can be imagined for the apparatus. For instance, the microneedle substrate can have more than one solution passage (opening). Moreover, it can also have a sheet-shaped reinforcing member having one or more solution passage (openings). Further, a pad portion placed above the microneedle substrate, and a dissolving solution reservoir that contains a dissolving solution for dissolution drug, and is placed above the pad portion, can also be provided. The microneedle interface provided with such a dissolving solution reservoir is disclosed, for instance, in WO03/084595A1. It is also possible for the transdermal drug administration apparatus to be a blister type transdermal drug administration apparatus with microneedles in which the seal of the aforementioned dissolving solution reservoir breaks when the dissolving solution reservoir is pressed, and the dissolving solution is supplied to the pad portion, while at the same time, the microneedles pierce the horny layer of the skin, and thereby the drug dissolved in the dissolving solution is absorbed transdermally. An example of a blister type apparatus will be described hereinafter.
Examples of the present invention are described below in detail. However, the present invention is not limited by the below-given examples. In all these experiments, the microneedles used were made of silicon and had a height of about 250 μm (230 to 270 μm), and a microneedle substrate (1 cm2) with 400 or 841 microneedles/cm2 as a value of standard was used. A piece of foam tape (#9773, 7.84 cm2) of 3M Company was pasted on the back side of the microneedle substrate in such a way that the adhesive layer of the tape would face the skin. The projecting ends of the tape were attached to the skin to bring the microneedle side of the microneedle substrate in close contact with the skin. To start the experiment, the microneedle substrate was placed on the skin and pressure applied (2 kg/patch for 5 seconds) on the substrate with a finger.
Aqueous solutions each containing 5 wt. % of a polymer (polyvinyl alcohol 220, dextrin, chondroitin A, polyethylene glycol, polyvinylpyrrolidone, hydroxypropyl methylcellulose or methylcellulose), and 7 wt. % sodium calcein were prepared as coating carriers. Microneedles (400 pile/patch) were coated all over their surface with 25 μl/patch of one of these coating carriers, and dried for 30 minutes in a drier for fixing.
Skin was then removed from the trunk of a hairless mouse and fitted to a vertical acrylic cell (2.54 cm2) with the dermis side facing the receptor layer, and the whole assembly was placed in a constant temperature chamber set at 37° C. Then, the transdermal drug administration apparatus with microneedles of the present invention was pasted on the horny layer side, and hourly sampling was done for 6 h. Phosphate buffer solution (PBS) was used for the receptor layer. The drug content of the receptor solution at each time of sampling was measured by fluorescence spectrophotometry (Excitation: 485 nm, fluorescence: 538 nm).
Animal species: Hairless mouse (n=3)
Receptor solution: 4 mL PBS (Sampling volume: 200 μl)
Temperature: 37° C.
Area: 2.54 cm2 (The MN substrate itself was 1 cm2)
Aqueous solutions containing 5% by weight of a polyvinyl alcohol (PVA220, PVA203, or PVA117), and 7% by weight of sodium calcein were prepared as coating carriers. Microneedles (800 pile/patch) were coated all over the surface with 30 μl/patch of one of these coating carriers, and dried for 30 minutes in a drier for fixing. Skin permeation test was carried out as in Example 1, with hairless rats (n=3).
PVA220: hydrolysis degree (87 to 89 mol %)
PVA203: hydrolysis degree (87 to 89 mol %)
PVA117: hydrolysis degree (97 mol % or more)
Aqueous solutions containing 5% by weight of a polyvinyl alcohol (PVA105, PVA117, or PVA124), and 7% by weight of sodium calcein were prepared as coating carriers. Microneedles (800 pile/patch) were coated all over the surface with 30 μl/patch of one of these coating carriers, and dried for 30 minutes in a drier for fixing. Skin permeation test was carried out with hairless rats (n=3) as in Example 1.
PVA105: Mean degree of polymerization (N=500)
PVA117: Mean degree of polymerization (N=1700)
PVA124: Mean degree of polymerization (N=2400)
Coating carriers were prepared by dissolving 16 wt. % granisetron hydrochloride in a 5 wt. % aqueous polymer solution. Microneedles (800 pile/patch) were coated all over the surface with 30 μl/patch of the coating carrier, and dried for 12 h at room temperature for fixing. In vivo testing was done with hairless rats, and blood sampled periodically was analyzed quantitatively by HPLC.
Animal species: Hairless rat (n=4)
Volume of blood sampled: 500 μl (plasma: 200 μl)
HPLC measurement (Excitation: 298 nm, fluorescence: 353 nm)
Column: TSKgel ODS-80TsQA 5 μm (4.6×150)
In this experiment, the coating carrier was prepared for the entire surface of microneedles by using only 5 wt. % polyvinyl alcohol (PVA117), and the microneedles (800 pile/patch) were coated all over the surface with 30 μl/patch and dried for 12 h at room temperature for fixing. After piercing the skin with the microneedles, 15 μl of 32 wt. % aqueous solution of granisetron hydrochloride, 30 μl, was applied through the through-holes (openings) on the microneedle substrate. There were two control groups. In one of these, the microneedles were not given any coating and 30 μl of the drug solution alone was applied through the through-holes. In the other control group, an aqueous solution containing 5 wt. % of polyvinyl alcohol and 32 wt. % of granisetron hydrochloride was prepared, as before, as the coating carrier, and the microneedles (800 piles/patch) were coated all over the surface with 15 μl/patch of this coating carrier.
Skin was then removed from the trunk of a hairless rat and fitted to a vertical acrylic cell (2.54 cm2) with the dermis side facing the receptor layer, and the whole assembly was placed in a constant temperature chamber set at 37° C. The transdermal drug administration apparatus with microneedles of the present invention was pasted on the horny layer side, hourly sampling was done up to 24 h. Phosphate buffer solution (PBS) was used for the receptor layer. The drug content of the receptor solution obtained at each time of sampling was measured by HPLC (Excitation: 298 nm, fluorescence: 353 nm).
Animal species: Hairless rat (n=3)
Receptor solution: 4 mL PBS (Sampling volume: 200 μl)
Temperature: 37° C.
Area: 2.54 cm2 (The MN substrate itself was 1 cm2)
Column: TSKgel ODS-80TsQA 5 μm (4.6×150)
A 5 wt. % solution of a polymer (PVP, polyethyleneoxide, hydroxypropyl cellulose, PVA220, hydroxypropyl methyl cellulose, or PVA117) and 7 wt. % solution of sodium calcein, used as a model low molecular weight compound, were prepared and mixed. Fifteen ml of the mixed solution was filled in a Petri dish by the casting method and dried for 1 day at 50° C. to allow a thin film to form. A 2 cm2 piece of this thin film was then cut out and immersed in phosphate buffer solution (PBS) and the model compound released into the PBS solution was measured periodically. This experiment was carried out at 37° C. Table 1 shows the time of dissolution of the polymer and the time taken to reach steady state in Comparative Examples 1 to 5, and in Example 6-1 (PVA117, a fully saponified PVA of hydrolysis degree 97 mol % or more) and Example 6-2 (PVA617, a partially saponified PVA of hydrolysis degree 94.5 to 95.5 mol %).
As shown in Table 1, all the polymers other than PVA117 (Example 6-1) and PVA617 (Example 6-2) dissolved within 10 minutes from the start of soaking, but both PVA617 and PVA117 retained the film shape even after 120 minutes and up to 12 h, although PVA617 showed some swelling. It thus became clear that PVA117 and PVA617 can not only function as drug carriers but also as routes of drug permeation via microneedles.
10 wt. % aqueous solutions of polyvinyl alcohol (PVA117) containing 16 wt. % of a drug (pergolide, pramipexol, or bisoprolol) in its free form or in the form of salt (pergolide mesylate, pramipexol hydrochloride, or bisoprolol fumarate) were prepared as the coating carrier. Microneedles (800 piles/patch) were coated all over their surfaces with 30 μl/patch one of the coating carriers, and dried at room temperature for 12 h for fixing. Skin removed from hairless rats was pierced with microneedles coated with the drug formulations, including those having their free forms, and samples were removed periodically. Phosphate buffer solution (PBS) was used for the receptor layer. The receptor solution sample, sampled at different time points, and acetonitrile were mixed at 1:1 ratio, stirred, centrifuged (15,000 rpm, 5° C., 5 minutes), then the supernatant was recovered, and its drug content measured by HPLC. Table 2 lists the maximum flux of each drug in the free form and the salt form.
Animal species: Hairless rat (n=3)
Sample volume: 1 ml
HPLC measurement
<Pergolide> TSKgel ODS-80TsQA(4.6×150 mm), 223 nm, 40° C.
<Pramipexol> TSKgel ODS-80TsQA(4.6×150 mm), 265 nm, 40° C.
<Bisoprolol> TSKgel ODS-80TsQA(4.6×150 mm), 280 nm, 40° C.
In the case of pergolide, the amount of drug permeation was about 1 μg, a generally low value, for both the salt and the free form, in the skin permeation test. This is because this drug, whether in the free or the salt form, has almost no solubility in water. Therefore, it is assumed that the drug in the polymer did not get dissolved and did not permeate through the skin. Pramipexol and bisoprolol showed higher maximum flux in their salt form than in their free form, in the skin permeation test. Regarding this aspect, it is generally known that in the case of drug products in the form of tape formulations, etc, which do not affect the horny layer, the physicochemical properties of the drug have a major effect on skin permeability. Especially, drugs with a relatively high fat solubility have a higher permeability than highly water-soluble drugs. However, when the device of the present invention was used, the salt-form compound, which is more water-soluble than the highly fat-soluble free form, showed higher skin permeability. These results confirmed that high skin permeability can be expected even with highly water-soluble drugs when used with the device of the present invention, as can be understood from the fact that granisetron hydrochloride showed good skin permeability in examples 4 and 5.
In the experiment (Table 2) with bisoprolol, a low melting point drug that is liquid at room temperature, both the fumarate and the free form showed good skin permeability. It became clear from this result that the state, i.e., whether dissolved or crystalline, rather than the physicochemical properties of the drug, has a major impact in skin permeation performance of drug administered with the device. In other words, it is believed that skin permeability is promoted if the drug maintains its dissolved state, or gets shifted to the dissolved state, at the time of administering the drug formulation. In other words, it became clear that the water-soluble drugs so far considered not applicable in ordinary transdermal formulations have now become applicable, unless the drug has extremely low solubility, like pergolide.
The present invention relates to a microneedle device having, on a substrate, a plurality of microneedles that can pierce the skin for administering a drug through the skin, and a transdermal drug administration apparatus with microneedles. The invention has industrial applicability.
| Number | Date | Country | Kind |
|---|---|---|---|
| 2006-106995 | Apr 2006 | JP | national |
| Filing Document | Filing Date | Country | Kind | 371c Date |
|---|---|---|---|---|
| PCT/JP2007/057737 | 4/6/2007 | WO | 00 | 10/3/2008 |
