Patent Application
20210178138
The present invention relates to the field of medical technology. More specifically, it relates to an implantable sustained-release microneedle patch and a preparation method therefor.
Transdermal drug delivery preparations are a dosage form by which drugs are administered through skin, which can avoid the interference of the gastrointestinal environment with the drug effect and the “first pass effect” of the liver, maintain a constant optimal plasma-drug concentration or physiological effect, prolong the effective acting time, and reduce the dosage frequency. The drugs can be administrated by patients on their own, and the patient compliance is good. However, the stratum corneum in the outer layer of the skin will hinder the absorption of drugs, and the drugs are not easy to penetrate into the body, resulting in very limited choices of drugs. In recent years, microneedle technology has received widespread attention. It is one of physical penetration enhancement methods using transdermal drug delivery, which can achieve painless and precise drug delivery.
Traditional microneedles made of metal, glass, and silicon materials will inevitably be broken and left in the skin during use due to the properties of their materials, causing damage to the human body. In recent years, the emerging polymer microneedles use materials including water-soluble polymer that can be absorbed by the skin, biocompatible polymer, and biodegradable polymer materials, greatly reducing the risk of use; furthermore, polymer microneedles are advantageous in low production cost, simple manufacturing process, mass production, and environmental friendliness, and microneedle manufacturing can achieve controlled release of drugs by selecting water-soluble polymer materials or biodegradable polymer materials having different physical and chemical properties.
In recent years, many scientific researchers have devoted themselves to using polylactic acid-based degradable polymer materials to make polymer microneedles that are biocompatible, naturally degradable, and easy to prepare.
Chinese patent (CN104888343 A) discloses a polymer solid microneedle and a batched preparation method therefor. The material described in this invention is a biodegradable water-insoluble polymer material. The preparation method used is to place polymer material particles on a microneedle mold, heat the particles in a closed heating device until the particles melt, and use the preparation device to implement press molding of the melt while the melt is hot. However, the microneedle prepared in this patent cannot load drugs, and the microneedle only plays a role in pretreating the skin and destroying the skin stratum corneum barrier during use.
International patent (WO2007/030477) discloses a solid drug solution perforator containing drug particles and/or drug-adsorbed or loaded particles with an associated drug reservoir (SSPP system). In order to deliver drugs, the SSPP system comprises an active drug ingredient in a particulate form or a drug adsorbed on a particle surface in a matrix material that dissolves upon contact with a patient's body. The inert particles are poly(lactic-co-glycolic acid) (PLGA) or aluminum hydroxide and aluminum phosphate. The microneedle made by this method can be loaded with protein and vaccine drugs. However, in this method, the drug barely has a sustained-release effect since it is adsorbed on the PLGA inert particles.
Literature 1 (Pharmaceutical Research. 2006 May; 23(5):1008-19.) proposes a method for preparing a microneedle by using poly(lactic-co-glycolic acid) (PLGA) as a material of a microneedle support. The method achieves controlled release of drugs by loading into the microneedle the drugs or microspheres of polylactic acid or sodium carboxymethyl cellulose loaded with the drugs. However, in this method, since the matrix material of the body of the microneedle is PLGA, the user needs to apply it for a long time until the material PLGA of the support is completely degraded.
Literature 2 (Biomed Microdevices. 2007 April; 9(2):223-34) proposes a method for preparing a porous multi-layered biodegradable microneedle by using PLA, PGA or PLGA microspheres. The method is to prepare a porous or multi-layered microneedle by injecting microspheres made of a biodegradable polymer material into a mold and using extrusion and ultrasonic welding or thermal welding technology. In the microneedle manufacturing, the microspheres need to be prepared by spray drying technology or by emulsification at first, and thus the process is complicated. Compared with a single microneedle, the porous multi-layered microneedle is weaker and easier to break, and is difficult to be effectively demolded from the mold.
In summary, from the current point of view, taking polylactic acid microneedles as an example, the manufacturing of microneedles can be divided into two categories: one is to first make polylactic acid-based biodegradable polymer materials and drugs into microspheres, then add them into a microneedle mold, and then heat, melt, and cool them to form a microneedle with a certain mechanical strength, such microneedle can be loaded with drugs, but it needs to make microspheres at first to form the microneedle, the operation is cumbersome and the cost is high; the other is to directly add polylactic acid powder into a microneedle mold, and then heat, melt (above 200° C.) and then cool them to form a microneedle, but this manufacturing method is difficult to load drugs.
Therefore, there is a need to provide a polylactic acid-based implantable sustained-release microneedle which is simple in process and high in safety, and does not need long-term application.
A first objective of the present invention is to provide an implantable sustained-release microneedle, which has sufficient mechanical strength and can implant a polylactic acid-based needle tip into the skin, realizing purposes of convenience, safety, biodegradability, and efficient administration.
The second objective of the present invention is to provide a preparation method for the above-mentioned implantable sustained-release microneedle, which has simple process and low cost.
The third objective of the present invention is to provide a microneedle patch comprising the above-mentioned implantable sustained-release microneedle.
To achieve the above objectives, the present invention adopts the following technical solutions:
The present invention provides an implantable sustained-release microneedle, comprising a needle tip, a needle body, and a base; the needle tip comprises a needle tip center layer and a needle tip outer layer; the needle tip center layer is formed of a matrix comprising a biodegradable water-insoluble polymer material; and the needle tip outer layer, the needle body, and the base are formed of a matrix comprising a water-soluble polymer material.
Further, the biodegradable water-insoluble polymer material includes, but is not limited to, one or more of polylactic acid, poly-L-lactide, poly-DL-lactide, poly(lactic-co-glycolic acid), polyglycolic acid, and polycaprolactone.
In the present invention, the water-soluble polymer material of the needle tip outer layer of the microneedle is connected with the water-soluble polymer material of the needle body of the microneedle, which can enhance the mechanical strength of the microneedle and improve the success rate of the microneedle puncturing the skin. Without the wrapping by the outer layer of the microneedle, since the biodegradable material of the center layer of the microneedle has weak hydrophilicity, and the strength of connection with the water-soluble polymer matrix material of the needle body is low, the microneedle will easily break at the time of puncturing, the success rate of the needle tip entering the skin is relatively low, and the quality of the microneedle puncturing the skin is uncontrollable.
Further, the needle tip center layer comprises at least one active ingredient; preferably, a mass ratio of the biodegradable water-insoluble polymer material to the active ingredient is 0.5:1-1000:1, so as to ensure the mechanical strength and skin penetration of the microneedle.
In a preferred embodiment of the present invention, the needle tip center layer further comprises a pore-forming agent. The pore-forming agent helps intradermal water molecules enter the interior of the matrix of the needle tip center layer, so as to regulate the drug release rate. The pore-forming agent includes, but is not limited to, one or more of sodium chloride, sodium carbonate, sodium bicarbonate, ammonium bicarbonate, trehalose, maltose, polyethyleneglycol, cyclodextrin and its derivatives, polyvinylpyrrolidone (PVP), a low-molecular weight hyaluronic acid and its sodium salt (with a molecular weight of 5-100 kDa), and low-molecular weight cellulose derivatives (with a molecular weight of 5-100 kDa).
Preferably, the pore-forming agent accounts for 0.1%-10% of the total mass of the needle tip center layer.
In a preferred embodiment of the present invention, the needle tip center layer further comprises a protective agent. The protective agent includes, but is not limited to, one or more of polyhydroxy compounds (mannitol, sorbitol, xylitol, polyethyleneglycol, etc.), carbohydrate compounds (trehalose, dextrin, lactose, sucrose, maltose, etc.), serum albumin. polyvinylpyrrolidone, chondroitin sulfate, amino acids (proline, tryptophan, glutamic acid, glycine, etc.)
Preferably, the protective agent accounts for 0.1%-10% of the total mass of the needle tip center layer.
Further, the water-soluble polymer material includes, but is not limited to, one or more of carboxymethyl cellulose, hydroxypropyl methyl cellulose (HPMC), hydroxyethyl cellulose, polyvinyl alcohol and its derivatives, polyvinylpyrrolidone (PVP) and its derivatives, sodium hyaluronate and its derivatives, chondroitin sulfate, chitosan derivatives, polyacrylamide derivatives, polyglutamic acid, polydopamine, pullulan, gelatin, collagen, plant protein, and silk protein.
Preferably, the molecular weight of the water-soluble polymer material is 20-2000 kDa.
Preferably, the needle tip outer layer, the needle body, and the base further comprise low-molecular weight carbohydrates and polyol compounds (specifically, one or more of trehalose, sucrose, maltose, sorbitol, mannitol, xylitol, and glycerol, etc.), so as to accelerate a dissolution rate of the water-soluble polymer material.
Preferably, the needle tip outer layer, the needle body, and the base are the same type of water-soluble polymer material.
Further, the needle tip has a conical shape or a polygonal conical shape, preferably, the needle tip has a conical shape; the density of the needle tip of the microneedle is: 25-1000 needle bodies and needle tips per square centimeter of the base; the height of the needle tip and the needle body is 0.3-2 mm; the angle of the needle tip is 10-60°; and the thickness of the base is 10-300 μm. The height of the needle tip center layer is not greater than two-thirds of the height of the needle tip and the needle body.
The present invention further provides a preparation method for the above-mentioned implantable sustained-release microneedle, comprising the following steps:
1) mixing a biodegradable water-insoluble polymer material with a part of an organic solvent, adding or not adding a pore-forming agent, adding or not adding a protective agent, to prepare a needle tip center layer matrix material solution; mixing an active ingredient with the remaining organic solvent to prepare a drug solution; mixing the drug solution with the needle tip center layer matrix material solution to obtain a needle tip center layer injection molding liquid;
alternatively,
mixing the biodegradable water-insoluble polymer material with the organic solvent, adding or not adding the pore-forming agent, adding or not adding the protective agent, adding the active ingredient, and mixing uniformly to obtain the needle tip center layer injection molding liquid;
2) mixing the water-soluble polymer material with water, adding or not adding low-molecular weight carbohydrates or polyol compounds, and mixing uniformly to obtain a needle tip outer layer injection molding liquid; mixing the water-soluble polymer material with water, adding or not adding the low-molecular weight carbohydrates or the polyol compounds, and mixing uniformly to obtain a needle body and base injection molding liquid;
3) injecting the needle tip outer layer injection molding liquid into a microneedle mold, and drying to prepare a needle tip outer layer; injecting the needle tip center layer injection molding liquid into the microneedle mold, heating to remove the organic solvent, and cooling; injecting the needle body and base injection molding liquid into the microneedle mold to prepare a needle body and a base, drying, and demolding to obtain the implantable sustained-release microneedle.
Further, the organic solvent includes, but is not limited to, acetone, ethylacetate, chloroform, dichloro or N-methylpyrrolidone; preferably, the organic solvent is N-methylpyrrolidone.
Further, the mass concentration of the biodegradable water-insoluble polymer material in the needle tip center layer injection molding liquid is 5-30%; the mass concentration of the water-soluble polymer material in the needle tip outer layer injection molding liquid is 0.5-10%; the mass concentration of the water-soluble polymer material in the needle body and base injection molding liquid is 10-50% and the mass ratio of the biodegradable water-insoluble polymer material to the active ingredient is 0.5:1-1000:1.
Further, in said step 3), the needle tip center layer injection molding liquid, the needle tip outer layer injection molding liquid, or the needle body and base injection molding liquid are added to the microneedle mold by means of a pressurization method or a vacuum method, so as to avoid the formation of air bubbles in the needle during manufacturing. If the pressurization method is adopted, then the applied pressure is 0.2-0.6 MPa, and the pressurization time is 1-20 min. If the vacuum method is adopted, then the vacuum degree is 0.05-0.1 MPa, and the vacuuming time is 3-20 min.
Preferably, the drying time after the needle tip outer layer injection molding liquid is injected into the microneedle mold is 1-10 min.
Preferably, the heating temperature after the needle tip center layer injection molding liquid is injected into the microneedle mold is 30-85° C., and the heating time is 1-24 h, so as to volatilize the organic solvent and ensure that the microneedle has sufficient mechanical strength and skin puncturing ability after cooling.
Preferably, the drying condition after the needle body and base injection molding liquid is injected into the microneedle mold is drying for 0.5-6 hours under 25-30° C. and 10-35% humidity.
The present invention further provides an implantable sustained-release microneedle patch comprising the above-mentioned implantable sustained-release microneedle and a backing; preferably, the backing is a pressure-sensitive adhesive backing or a silicone backing or a hydrocolloid backing.
The preparation method for the above-mentioned implantable sustained-release microneedle patch is to, based on preparing the implantable sustained-release microneedle, further paste the backing on the backside of the dried base and then demould to obtain the implantable sustained-release microneedle patch.
The implantable sustained-release microneedle patch described in the present invention can be applied in fields of disease treatment and prevention, health care, and cosmetology.
The term “active ingredient” refers to a substance used for diagnosis, treatment, prevention, cosmetic or health care purposes that is delivered through the microneedle or the microneedle patch of the present invention in a transdermal manner and has the efficacy of acting on animals or humans. According to the present invention, the active ingredient includes, but is not limited to, pharmaceutical active ingredients, vaccine active ingredients, cosmetic active ingredients, health care product active ingredients, etc., which are specifically selected according to actual needs.
The beneficial effects of the present invention are as follows:
In the microneedle or the microneedle patch of the present invention, a biodegradable water-insoluble polymer material is used to make the needle tip center layer of the mnicroneedle, and a water-soluble polymer material is used to make the needle body, the base, and the needle tip outer layer, so as to form a microneedle having a needle tip center layer insoluble in water. After acting on the skin, the water-soluble material of the needle tip outer layer and the needle body absorbs the moisture within the skin, so that the needle body and the base are quickly separated from the needle tip within 0.5-1 h; and after the base of the patch is removed, the needle tip of the microneedle will be completely left in skin, and thus weeks of long-term in vivo release of a drug can be ensured without a user sticking the microneedle patch for a long time. Such microneedle patches are not limited by the manufacturing area, and the drug load can be greatly increased by extending the area, which is suitable for long-term intradermal release of various drugs. In addition, the preparation process for the microneedle or the microneedle patch of the present invention avoids the cumbersome process such as encapsulating the drug in the microsphere liposome, but uses a low-toxic organic solvent such as N-methylpyrrolidone to dissolve biodegradable polylactic acid-based polymer materials, the process cost is reduced, and the process is similar to conventional manufacturing methods for a dissolvable microneedle or a microneedle patch, the operation is simple and fast, high temperature melting is not required, and the applicable drug range is wide.
The specific embodiments of the present invention will be described in further details below with reference to the accompanying drawings.
In order to explain the present invention more clearly, the present invention will be further described below in conjunction with preferred examples and accompanying drawings. Similar components in the accompanying drawings are denoted by the same reference numerals. Those skilled in the art should understand that the content described in detail below is illustrative rather than restrictive, and should not limit the protection scope of the present invention.
1. 0.05 g of polyvinyl alcohol with a molecular weight of 200 kDa was taken and weighed, 4.95 ml of water was added, the resulting solution was placed and heated under 85° C. for 1 hour, a polyvinyl alcohol aqueous solution with a mass fraction of 1% was prepared as a needle tip outer layer injection molding liquid; and 3.5 g of polyvinyl alcohol with a molecular weight of 20 kDa was taken and weighed. 6.5 ml of water was added, the resulting solution was placed and heated under 85° C. for 2 hours, a polyvinyl alcohol aqueous solution with a mass fraction of 30% was prepared as a needle body and base injection molding liquid.
2. 0.3 g of PLGA (80/20) with a molecular weight of 20 kDa was taken and weighed, and 0.7 ml of N-methylpyrrolidone was added, to prepare a PLGA solution with a mass fraction of 30%: 50 mg of etonogestrel (ENG) was taken and weighed, and 1 ml of N-methylpyrrolidone was added, to prepare a 50 mg/ml etonogestrel solution; the above-mentioned etonogestrel solution and the above-mentioned PLGA solution were mixed uniformly in a certain ratio to prepare solutions containing PLGA:ENG at solid content ratios of 60:40 and 75:25, respectively, as the needle tip center layer injection molding liquid.
3. 10 μl of the above-mentioned needle tip outer layer injection molding liquid was added into a mold, the needle tip outer layer injection molding liquid was forced into pinholes of the microneedle mold by means of vacuuming, the excess solution on the mold was removed, and the mold was placed under 25° C. and 20% humidity to dry for 10 minutes; the above-mentioned needle tip center layer injection molding liquid was added into the above-mentioned microneedle mold, the needle tip center layer injection molding liquid was forced into the pinholes of the above-mentioned microneedle mold by means of vacuuming, the excess solution on the mold was removed, and the mold was heated under 80° C. for 2 hours; 150 μl of the above-mentioned base injection molding liquid was added to the above-mentioned cooled microneedle mold and vacuumed to avoid the formation of air bubbles; the above-mentioned microneedle mold was placed under 25° C. and 10% humidity to dry for 6 hours.
4. A pressure-sensitive adhesive backing was pasted on a backside of the base of the dried microneedle, and the microneedle patch was demoulded.
The prepared microneedle patch is as shown in
5. The microneedle patch was applied to a surface of pigskin, the patch was peeled off at different time points, and a dissolution situation of the needle tip of the microneedle patch was observed under a microscope. As shown in
6. In vitro transdermal experiment: the microneedle patch was applied to the surface of pigskin, as for a transdermal cup, a medium of a receiving solution in the cup was a 30% PEG400-10% ethanol-PBS buffer solution, samples were taken at a predetermined time point in a full sampling manner, and an equal volume of the receiving medium was complemented immediately after each sampling.
In this example, etonogestrel can be replaced by other active ingredients of small molecular compounds having thermal stability at 80° C., which include, but are not limited to ethinyl estradiol, levonorgestrel, norgestrel, gestodene, desogonolone, desogestrel, artemisinin derivatives, paclitaxel derivatives and other active ingredients, and the obtained microneedle patch has a similar sustained-release effect.
The polyvinyl alcohol in the needle tip outer layer injection molding liquid and the needle body and base injection molding liquid of the this example can be replaced by carboxymethyl cellulose, hydroxypropyl methyl cellulose, hydroxyethyl cellulose, polyvinyl alcohol derivatives, polyvinylpyrrolidone and its derivatives, sodium hyaluronate and its derivatives, chondroitin sulfate, chitosan derivatives, polyacrylamide derivatives, polyglutamic acid, polydopamine, pullulan, gelatin, collagen, and silk protein, and the obtained microneedle patch has a similar sustained-release effect.
In the needle tip center layer injection molding liquid of this example, a pore-forming agent such as 0.1-5% sodium chloride, 0.1-5% sodium carbonate, 0.1-3% sodium bicarbonate, 0.1-3% ammonium bicarbonate, 1-10% trehalose, 1-10% maltose, 1-10% cyclodextrin and its derivatives, 1-5% polyvinylpyrrolidone, 1-5% sodium hyaluronate, and 1-5% carboxymethyl cellulose can be further added, and the obtained microneedle patch can be sustained-released for 5-20 days.
1. 0.05 g of sodium carboxymethyl cellulose with a molecular weight of 200 kDa was taken and weighed, and 9.95 ml of water was added, to prepare a sodium carboxymethyl cellulose aqueous solution with a mass fraction of 0.5% as the needle tip outer layer injection molding liquid, 2.5 g of sodium carboxymethyl cellulose with a molecular weight of 200 kDa was taken and weighed, and 7.5 ml of water was added, to prepare a sodium carboxymethyl cellulose aqueous solution with a mass fraction of 25% as the needle body and base injection molding liquid.
2. 0.2 g of polylactic acid (PLA) with a molecular weight of 10 kDa was taken and weighed, and 0.6 ml of N-methylpyrrolidone was added, to prepare a PLA solution with a mass fraction of 20%; 10 mg of a fat-soluble simulated drug red fluorescent dye was taken and weighed, and 1 ml of N-methylpyrrolidone was added, to prepare a red fluorescent dye solution with a mass fraction of 10 mg/mL; 0.5 ml of the red fluorescent dye solution was mixed uniformly with 0.5 ml of the PLA solution, to prepare a 10% PLA solution containing 5 mg/ml of the red fluorescent dye as the needle tip center layer injection molding liquid.
3. 20 μl of the needle tip outer layer injection molding liquid was added into a mold, the needle tip outer layer injection molding liquid was forced into pinholes of the microneedle mold by means of pressurization, the excess solution on the mold was removed, and the mold was placed under 25° C. and 30% humidity to dry for 10 minutes; the above-mentioned needle tip center layer injection molding liquid was added into the above-mentioned microneedle mold, the needle tip center layer injection molding liquid was forced into the pinholes of the above-mentioned microneedle mold by means of vacuuming, the excess solution on the mold was removed, and the mold was heated under 80° C. for 2 hours; 150 μl of the above-mentioned needle body and base injection molding liquid was added to the above-mentioned cooled microneedle mold and vacuumed to avoid the formation of air bubbles; the above-mentioned microneedle mold was placed under 25° C. and 30% humidity to dry for 0.5 hours.
4. A pressure-sensitive adhesive backing was pasted on a backside of the base of the dried microneedle, and the microneedle patch was demoulded.
The prepared microneedle patch is as shown in
If the microneedle is applied to pigskin and peeled off from the base within 30 minutes, it can be sustained-released for one month.
In this example, the red fluorescent dye can be replaced by other active ingredients of small molecular compounds with a heat resistance of 80° C., and the obtained microneedle patch has a similar sustained-release effect.
1. 0.25 g of carboxymethyl cellulose with a molecular weight of 40 kDa was taken and weighed, and 4.75 ml of water was added, to prepare a carboxymethyl cellulose aqueous solution with a mass fraction of 5% as the needle tip outer layer injection molding liquid; 3 g of polyvinyl alcohol with a molecular weight of 70 kDa was taken and weighed, 7 ml of water was added, and the resulting solution was heated under 85° C. for 2 hours, to prepare a polyvinyl alcohol aqueous solution with a mass fraction of 30% as a needle body and base injection molding liquid.
2. 0.4 g of PLGA (75/25) with a molecular weight of 10 kDa was taken and weighed, and 0.6 ml of N-methylpyrrolidone was added, to prepare a PLGA solution with a mass fraction of 30%; 5 mg of interferon a-2b was taken and weighed and dissolved in 1 ml of sterile water for injection, 10 mg of zinc hydroxide subjected to micronization and sterilization was added, the resulting solution was vortex-mixed for 10 minutes to form a zinc salt-containing interferon a-2b solution; the zinc salt-containing interferon a-2b solution was added to the above-mentioned 30% PLGA solution and stirred to form a drug-loaded sol system as the needle tip center layer injection molding liquid.
3. 20 μl of the above-mentioned needle tip outer layer injection molding liquid was added into a mold, the needle tip outer layer injection molding liquid was forced into pinholes of the microneedle mold by means of pressurization, the excess solution on the mold was removed, and the mold was placed under 25° C. and 30% humidity to dry for 10 minutes: the above-mentioned needle tip center layer injection molding liquid was added into the above-mentioned microneedle mold, the needle tip center layer injection molding liquid was forced into the pinholes of the above-mentioned microneedle mold by means of vacuuming, the excess solution on the mold was removed, and the mold was heated under 30° C. for 24 hours: 200 μl of the above-mentioned needle body and base injection molding liquid was added to the above-mentioned cooled microneedle mold and vacuumed to avoid the formation of air bubbles; the above-mentioned microneedle mold was placed under 25° C. and 10% humidity to dry for 6 hours.
4. A pressure-sensitive adhesive backing was pasted on a backside of the base of the dried microneedle, and the microneedle patch was demoulded.
The prepared microneedle patch is as shown in
If the microneedle patch is applied to pigskin, the base can be completely peeled off within 1 hour, and the microneedle patch can be sustained-released for 4 weeks according to in vitro transdermal results.
In this example, the interferon a-2b can be replaced by other types of interferons, and can also be replaced by other proteins and polypeptides or hydrophilic small molecules, such as insulin, growth hormones, cytokines, nerve growth factors, amino acids, etc. The obtained needle patch has a similar sustained-release effect.
The carboxymethyl cellulose in the needle tip outer layer injection molding liquid and the polyvinyl alcohol in the needle body and base injection molding liquid of the this example can be replaced by carboxymethyl cellulose, hydroxypropyl methyl cellulose, hydroxyethyl cellulose, polyvinyl alcohol derivatives, polyvinylpyrrolidone and its derivatives, sodium hyaluronate and its derivatives, chondroitin sulfate, chitosan derivatives, polyacrylamide derivatives, polyglutamic acid, polydopamine, pullulan, gelatin, collagen, and silk protein, and the obtained microneedle patch has a similar sustained-release effect.
In the needle tip center layer injection molding liquid of this example, a pore-forming agent such as 0.1-5% sodium chloride, 0.1-5% sodium carbonate, 0.1-3% sodium bicarbonate. 0.1-3% ammonium bicarbonate. 1-10% trehalose, 1-10% maltose, 1-10% cyclodextrin and its derivatives, 1-5% polyvinylpyrrolidone, 1-5% sodium hyaluronate, and 1-5% carboxymethyl cellulose can be added, and the sustained-release time of the obtained microneedle patch ranges between 5-20 days.
A protective agent can be added to the needle tip center layer injection molding liquid of this example, such as one or more of 1-10% polyhydroxy compounds (such as 1% glycerin, 3% butylene glycol, 1-5% xylitol, 1-10% mannitol), 1-10% carbohydrate compounds (1-10% trehalose, 1-5% sucrose), 0.1-5% serum albumin, 1-10% polyvinylpyrrolidone, and 1-10% amino acids, and the sustained-release time of the obtained microneedle patch ranges between 5-20 days.
In the carboxymethyl cellulose in the needle tip outer layer injection molding liquid and the needle body and base injection molding liquid of this example, low-molecular weight carbohydrates and polyol compounds, specifically 1-10% trehalose. 1-5% sucrose, 1-10% sorbitol. 5-10% mannitol, 5-10% xylitol, 0.1-3% glycerol or the like can further be added to accelerate a dissolution rate of the water-soluble polymer materials, and the sustained-release effect of the obtained microneedle patch is similar to this example.
1. 1 g of chondroitin sulfate with a molecular weight of 40 kDa is taken and weighed, and 9 ml of water was added, to prepare a chondroitin sulfate aqueous solution with a mass fraction of 10% as the needle tip outer layer injection molding liquid: 4 g of chondroitin sulfate with a molecular weight of 40 kDa was taken and weighed, and 6 ml of water was added, to prepare a chondroitin sulfate aqueous solution with a mass fraction of 40% as the needle body and base injection molding liquid.
2. N-methylpyrrolidone was used as a solvent to prepare solutions containing 5%, 15%, and 30% PLGA, respectively, and 10 mg of granisetron hydrochloride was added to the above-mentioned solutions to prepare needle tip center layer injection molding liquids containing PLGA: granisetron hydrochloride in mass ratios of 1:2, 1.5:1, and 3:1.
3. 20 μl of the above-mentioned needle tip outer layer injection molding liquid was added into a mold, the needle tip outer layer injection molding liquid was forced into pinholes of the microneedle mold by means of pressurization, the excess solution on the mold was removed, and the mold was placed under 25° C. and 30% humidity to dry for 15 minutes; the above-mentioned needle tip center layer injection molding liquid was added into the above-mentioned microneedle mold, the needle tip center layer injection molding liquid was forced into the pinholes of the above-mentioned microneedle mold by means of vacuuming, the excess solution on the mold was removed, and the mold was heated under 60° C. for 4 hours; 150 μl of the above-mentioned needle body and base injection molding liquid was added to the above-mentioned cooled microneedle mold and vacuumed to avoid the formation of air bubbles; the above-mentioned microneedle mold was placed under 25° C. and 35% humidity to dry for 1 hour.
4. A pressure-sensitive adhesive backing was pasted on a backside of the base of the dried microneedle, and the microneedle patch was demoulded.
The prepared microneedle patch is as shown in
If the microneedle patch is applied to pigskin, it can be separated from the needle tip after 30 minutes, and the sustained-release time of the drug is respectively 14 days, 18 days, and 21 days, according to in vitro transdermal results. As the content of PLGA increases, the sustained-release time extends.
In this example, granisetron hydrochloride can also be replaced by leuprolide acetate, octreotide acetate, amlodipine besylate/ketoprofen, cyclosporine, diclofenac sodium controlled release, everolimus, methylphenidate, clarithromycin, mycophenolic acid, griseofulvin, mabilone, tacrolimus and other drugs, and the obtained microneedle patch has a similar sustained-release effect.
1. 0.05 g of polyvinyl alcohol with a molecular weight of 50 kDa was taken and weighed. 4.95 ml of water was added, the resulting solution was placed and heated under 85° C. for 1 hour, a polyvinyl alcohol aqueous solution with a mass fraction of 1% was prepared as a needle tip outer layer injection molding liquid; and 3.5 g of polyvinyl alcohol with a molecular weight of 50 kDa was taken and weighed. 6.5 ml of water was added, the resulting solution was placed and heated under 85° C. for 2 hours, a polyvinyl alcohol aqueous solution with a mass fraction of 35% was prepared as a needle body and base injection molding liquid.
2. 3 g of PLGA (80/20) with a molecular weight of 20 kDa was taken and weighed, 7 ml of N-methylpyrrolidone was added, and then 0.03 g of PVP K30 was added, to prepare a PLGA solution containing PVP K30; 50 mg of vinpocetine was taken and weighed, and 1 ml of N-methylpyrrolidone was added, to prepare a 50 mg/ml vinpocetine solution; 1 ml of the vinpocetine solution was mixed with 1 ml of the PLGA solution containing PVP K30 to prepare a needle tip center layer injection molding solution containing vinpocetine.
3. 10 μl of the above-mentioned needle tip outer layer injection molding liquid was added into a mold, the needle tip outer layer injection molding liquid was forced into pinholes of the microneedle mold by means of vacuuming, the excess solution on the mold was removed, and the mold was placed under 25° C. and 20% humidity to dry for 10 minutes; the above-mentioned needle tip center layer injection molding liquid was added into the above-mentioned microneedle mold, the needle tip center layer injection molding liquid was forced into the pinholes of the above-mentioned microneedle mold by means of vacuuming, the excess solution on the mold was removed, and the mold was heated under 70° C. for 3 hours; 150 μl of the above-mentioned needle body and base injection molding liquid was added to the above-mentioned cooled microneedle mold and vacuumed to avoid the formation of air bubbles; the above-mentioned microneedle mold was placed under 25° C. and 10% humidity to dry for 6 hours.
4. A pressure-sensitive adhesive backing was pasted on a backside of the base of the dried microneedle, and the microneedle patch was demoulded.
The prepared microneedle patch is as shown in
If the microneedle patch is applied to pigskin, the base can be completely peeled off within 30 minutes, and the microneedle patch can be sustained-released for 3 weeks.
Polylactic acid-based sustained-release microneedle patches comprising a pore-forming agent were prepared respectively according to the preparation method of Example 5. The specific formulations are shown in Table 1.
The preparation methods of Examples 18-28 are as shown in Example 1, and the specific parameters of each component in Examples 18-28 are shown in Table 2.
The preparation methods of Examples 29-35 are as shown in Example 3, and the specific parameters of each component in Examples 26-35 are shown in Table 3.
Examples 29-35 are also applicable to the preparation of other microneedle patches for macromolecular drugs or vaccines.
1. 0.05 g of sodium hyaluronate with a molecular weight of 50 kDa was taken and weighed, 4.95 ml of water was added, the resulting solution was placed and heated under 85° C. for 1 hour, to prepare a sodium hyaluronate aqueous solution with a mass fraction of 1% as a needle tip outer layer injection molding liquid. 3.5 g of polyvinyl alcohol with a molecular weight of 50 kDa and 0.35 g of trehalose were taken and weighed, 6.5 ml of water was added, the resulting solution was placed and heated under 85° C. for 2 hours, a polyvinyl alcohol-trehalose aqueous solution with a mass fraction of 35% was prepared as a needle body and base injection molding liquid.
2. 0.3 g of PLGA (75/25) with a molecular weight of 20 kDa was taken and weighed, and 0.7 ml of N-methylpyrrolidone was added, to prepare a 30% PLGA solution; 20 mg of asiaticoside was dispersed in the above-mentioned 30% PLGA solution, and the resulting solution was used as the needle tip center layer injection molding liquid.
3. 10 μl of the above-mentioned needle tip outer layer injection molding liquid was added into a mold, the needle tip outer layer injection molding liquid was forced into pinholes of the microneedle mold by means of vacuuming, the excess solution on the mold was removed, and the mold was placed under 25° C. and 20% humidity to dry for 10 minutes: the above-mentioned PLGA solution containing asiaticoside was added into the above-mentioned microneedle mold, the needle tip center layer injection molding liquid was forced into the pinholes of the above-mentioned microneedle mold by means of vacuuming, the excess solution on the mold was removed, and the mold was heated under 60° C. for 1 hour; 150 μl of the above-mentioned needle body and base injection molding liquid was added to the above-mentioned cooled microneedle mold and vacuumed to avoid the formation of air bubbles; the above-mentioned microneedle mold was placed under 25° C. and 10% humidity to dry for 6 hours.
4. A pressure-sensitive adhesive backing was pasted on a backside of the base of the dried microneedle, and the microneedle patch was demoulded.
The prepared microneedle patch is as shown in
If the microneedle patch is applied to pigskin, the base can be completely peeled off within 50 minutes, and the microneedle patch can be sustained-released for 15 days.
The preparation methods of Examples 37-42 are as shown in Example 36, and the specific parameters of each component are shown in Table 6.
The microneedle patch prepared in Examples 1-42 (except Example 17) was applied to fresh pigskin, pressed with fingers for 1 min, and dyed with 1% concentration of trypan blue for 20 min, the excess trypan blue was wiped off with a cotton swab, and then whether there were pinholes on the skin was observed. As shown in
The microneedle patch prepared in Examples 1-42 (except Example 17) was applied to fresh pigskin, pressed with fingers for 1 min, and the microneedle patch was kept on the skin for 1 hour, then an intradermal implantation situation of the needle tip was observed under a fluorescence microscope.
It will be obvious that the above-mentioned examples of the present invention are merely examples to clearly illustrate the present invention, and are not intended to limit the embodiments of the present invention. For those of ordinary skill in the art, other different forms of variations or changes may also be made on the basis of the above description. It is not possible to list all the embodiments here. Any obvious variations or changes derived from the technical solutions of the present invention are still within the protection scope of the present invention.
| Number | Date | Country | Kind |
|---|---|---|---|
| 201811011984.8 | Aug 2018 | CN | national |
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/CN2019/103332 | 8/29/2019 | WO | 00 |
