WO2005082405A1 - たんぱく性薬物の注射用徐放性微粒子製剤およびその製造法 - Google Patents
たんぱく性薬物の注射用徐放性微粒子製剤およびその製造法 Download PDFInfo
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- WO2005082405A1 WO2005082405A1 PCT/JP2005/001095 JP2005001095W WO2005082405A1 WO 2005082405 A1 WO2005082405 A1 WO 2005082405A1 JP 2005001095 W JP2005001095 W JP 2005001095W WO 2005082405 A1 WO2005082405 A1 WO 2005082405A1
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- Prior art keywords
- protein drug
- sustained
- injection
- release
- polylactic acid
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- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K47/00—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient
- A61K47/02—Inorganic compounds
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K47/00—Medicinal preparations characterised by the non-active ingredients used, e.g. carriers or inert additives; Targeting or modifying agents chemically bound to the active ingredient
- A61K47/30—Macromolecular organic or inorganic compounds, e.g. inorganic polyphosphates
- A61K47/34—Macromolecular compounds obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds, e.g. polyesters, polyamino acids, polysiloxanes, polyphosphazines, copolymers of polyalkylene glycol or poloxamers
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K9/00—Medicinal preparations characterised by special physical form
- A61K9/08—Solutions
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
- A61K9/00—Medicinal preparations characterised by special physical form
- A61K9/48—Preparations in capsules, e.g. of gelatin, of chocolate
- A61K9/50—Microcapsules having a gas, liquid or semi-solid filling; Solid microparticles or pellets surrounded by a distinct coating layer, e.g. coated microspheres, coated drug crystals
- A61K9/5005—Wall or coating material
- A61K9/5021—Organic macromolecular compounds
- A61K9/5031—Organic macromolecular compounds obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds, e.g. polyethylene glycol, poly(lactide-co-glycolide)
Definitions
- the present invention relates to a sustained-release particulate preparation for injection of a proteinaceous drug and its production method.
- the present invention relates to a sustained-release microparticle preparation for injection of a protein drug, which is based on microparticles of porous apatite or a derivative thereof which slowly disappear in a living body, and a method for producing the same.
- a long-term sustained-release injectable preparation of a protein drug has been studied on the basis of polylactic acid / glycolic acid (PLGA) in many cases (for example, Patent Documents 1, 2, See Non-Patent Documents 1, 2, and 3).
- sustained-release microcapsules based on PLGA containing human growth hormone (hGH) have been used for actual treatment in the United States (see, for example, Non-Patent Document 4).
- PLGA is a biodegradable base which is gradually hydrolyzed in the body and gradually disappears, and is preferred as a base for injections and has properties.
- a sustained release formulation using PLGA use an organic solvent that dissolves it.
- many protein drugs are water-soluble, and an organic solvent solution and an aqueous solution are used to produce a sustained release microparticle preparation using PLGA.
- Patent Document 1 JP-A-10-231252
- Patent Document 2 U.S. Patent 5,656,297
- Non-Patent Document 1 0 ⁇ . Johnson et al: Nature Medicine, 2: 795-799, (1996)
- Non-Patent Document 2 M. Takenaga et al: J. Pharmacy Pharmacology, 54: 1189-1194,
- Non-Patent Document 3 S. Takada et al: J. Controlled Release, 88: 229-242, (2003)
- Non-Patent Document 4 NDA 21-075
- Non-Patent Document 5 J. Guicheux et al: J. Biomedical Materials Research, 34: 165-170, (1997)
- Non-Patent Document 6 H. Gautier et al: J. Biomedical Materials Research, 40: 606-613, (1998)
- a sustained-release preparation for injection of a protein drug a material having a biodegradable function that disappears from the body at the end of drug release after administration must be selected.
- simultaneous use of an organic solvent immiscible with water and an aqueous solution must be avoided to avoid denaturation of a protein drug.
- the drug content in the microparticle preparation is not at least 5% or more, the dosage of the preparation will be too large and it will be difficult to administer with a fine needle, and in many cases it will be repeated. Because of administration, it is preferable to use a fine needle.Also, the sustained release period must be a microparticle preparation for at least 3 days or more, preferably 1 week or more. There was a problem that the release had to be minimized.
- the present invention provides a method for producing a biodegradable and sustained-release drug which minimizes the use of an organic solvent during production and avoids the simultaneous use of a water-immiscible organic solvent and an aqueous solution.
- a biodegradable and sustained-release drug which minimizes the use of an organic solvent during production and avoids the simultaneous use of a water-immiscible organic solvent and an aqueous solution.
- release the protein drug contained at an almost constant rate for at least 3 days have a drug content of 5% or more, and have good dispersibility and permeability.
- An object of the present invention is to provide a sustained release fine particle preparation and a method for producing the same. Means for solving the problem
- the inventors of the present invention utilize porous apatite or a derivative thereof in fine particles to prepare a preparation having both in vivo degradability and sustained release functions. Can be obtained without using water and an organic solvent at the same time.
- a sustained release over a longer period can be obtained by coating or adhering the biodegradable polymer compound, and at the same time, the initial excess release is achieved. I found that it could be smaller.
- the porous apatite and the derivative thereof constituting the sustained-release particulate preparation for injection of a protein drug described herein include hydroxyapatite or a part of calcium as a component thereof as zinc. It can be a substituted compound. At this time, the substitution rate of zinc is preferably 1 to 20%. Fine particles of porous apatite and its derivatives can be obtained by a known method. For example, the method described in “Takayama Yamaro” edited by Hiroaki Yanagida, Akio Makishima ⁇ Hideki Aoki: Ceramic Science Series 7 Bioceramics, Gihodo Shuppan Co., Ltd., pp. 7-9, 1984. Is raised.
- the rate of disappearance in the living body varies depending on the ratio of calcium (Ca) and phosphorus (P) constituting hydroxyapatite, and the value of (Ca + Zn) / P is smaller than 1.67. Disappears faster.
- the value of (Ca + Zn) / P is preferably in the range of 1.67 to 1.51.
- the processing temperature is from room temperature to 800 ° C, preferably from 150 to 600 ° C. Further, 150-400 ° C. is more preferable. If it is fired at 800 ° C or higher, it will not disappear in vivo.
- the particle diameter is preferably 50 / m or less on average. However, if the particle size is too small, there is a concern that the encapsulation rate of the protein drug may be reduced. Thus, 0.1 to 50 zm is preferable, 0.530 xm is more preferably used, and 0.5 to 10 ⁇ m is more preferably used.
- the biodegradable polymer compound covering the porous apatite includes polylactic acid (PLA) or polylactic acid 'glycolic acid (PLGA), a block in which PLA and / or PLGA are bonded to polyethylene glycol (PEG). There are copolymers, collagen, polycyanacrylic acid, polyamino acid derivatives, etc.
- PLA polylactic acid
- PLGA polylactic acid 'glycolic acid
- PEG polyethylene glycol
- copolymers collagen, polycyanacrylic acid, polyamino acid derivatives, etc.
- apatite coated with biodegradable polymer aggregates.
- an organic solvent that is immiscible with water Unless completely removed because it is used, denaturation of the protein drug may occur due to heat of water when freeze-drying in the final step.
- This bonding mode may be a compound in which PLA or PLGA is ester-bonded to the hydroxyl groups at both ends of PEG, or a compound in which PEG is ester-bonded to one terminal of PEG.
- the other terminal is preferably protected with an OCH, alkoxy group, etc.
- a functional group such as a ruboxyl group is bonded.
- the ratio of PEG to PLA or PLGA is 20 90% by weight of PEG is preferred, and 25 65% is more preferred by weight.
- the molecular weight of the block copolymer is preferably from 3,000 to 20,000, more preferably from 5,000 to 12,000.
- the amount of the biodegradable polymer used is in the range of 3 to 100% by weight of the apatite derivative, preferably in the range of 5 to 30%.
- Examples of the water-soluble divalent metal compound include zinc chloride, zinc acetate, zinc carbonate, calcium chloride, calcium hydroxide, iron chloride, iron hydroxide, and cobalt chloride.
- zinc chloride is preferably used.
- sodium carbonate or sodium hydrogen carbonate may be used in combination.
- the amount used varies depending on the protein drug to be enclosed, but generally, the range of 2 to 100% by weight of the porous apatite is preferably used. A more preferred range is 2-30%.
- a protein drug it is applied to compounds having a molecular weight of 5,000 or more.
- human growth hormone hepatocyte growth factor (HGF), fibroblast growth factor (FGF), IGF_1, EGF, NK4, VEGF, NGF, BDNF, BMP, adiponectin, interferons (INF-a), interleukins (IL-2, IL-4, IL-5, etc.), EPO, G-CSF, insulin, ANP, TNF-H, and antibodies.
- HGF hepatocyte growth factor
- FGF fibroblast growth factor
- IGF_1 fibroblast growth factor
- EGF fibroblast growth factor
- VEGF vascular endonectin
- NGF hepatocyte growth factor
- BDNF fibroblast growth factor
- BMP adiponectin
- interferons INF-a
- interleukins IL-2, IL-4, IL-5, etc.
- EPO EPO
- G-CSF insulin
- ANP
- the method for producing a sustained-release microparticle preparation for injection of a protein drug of the present invention generally comprises the following operations. Fine particles of porous apatite or a derivative thereof are dispersed in an aqueous solution of a proteinaceous drug and stirred to sufficiently infiltrate the aqueous solution into the apatite. After that, remove the aqueous solution that cannot be completely infiltrated by centrifugation or the like. Add an aqueous solution of a divalent metal compound and stir to infiltrate the aqueous solution. Thereafter, filtration, vacuum drying or lyophilization is performed to obtain a powder containing the protein drug.
- This powder is dispersed in an aqueous solution or suspension of a biodegradable polymer, or an aqueous solution or suspension of a biodegradable polymer containing a water-miscible solvent (for example, acetone or ethanol). After stirring, if necessary, a stabilizer or the like is added and freeze-dried or vacuum-dried to produce a powder.
- this powder is dispersed in an appropriate dispersion medium and injected subcutaneously or intramuscularly.
- the particle size of the finally obtained sustained release microparticle preparation may be passed through an injection needle used for ordinary administration. In fact, the smaller the needle diameter, the less fear there is for the patient.
- the sustained-release microparticle preparation that satisfies these conditions is 0.5 to 50 zm. Further, the sustained release period of the proteinaceous drug varies depending on the activity of the drug and the like, but generally, the sustained release for one week or more is preferable.
- the microparticle preparation obtained by the present invention provides a sustained release of the protein drug for at least 3 days or more, and the initial excessive release is a microparticle preparation having a very small protein drug content of up to 30%. I found what I could get.
- the obtained preparation was passed through a 25G injection needle. In addition, it can be finally prepared into a powdered microparticle preparation by freeze-drying, and the encapsulated protein drug is very stable.
- a confirmation test of in vivo disappearance was performed using two types of zinc-substituted hydroxyapatite (average particle size 8 / im) having different firing temperatures.
- Five male SD rats (6 weeks old) were used per group.
- the drug was administered to the right and left subcutaneous regions in the center of the back. After administration (3 hours, 1, 5, 10, 15, 20 days), remnants of the administration site were removed over time, and the wet weight and calcium content were measured (Tables 1 and 2).
- the mixture was centrifuged again at 3,000 rpm for 3 minutes, and 2.7 mL (zinc chloride 400 / imol) of 20.4 mg / mL zinc chloride (Wako Pure Chemical, Osaka) 7 solution was added to the obtained precipitate, followed by stirring with a touch mixer. Thereafter, freeze-drying was performed.
- PLA-PEG-PLA-Y001 (PEG ratio 65.4%, molecular weight 14,600) was dissolved in acetone to a concentration of 20%, and the acetone solution and water were mixed at a ratio of 1: 4, and the polymer-containing acetone was dissolved.
- a water mixture was prepared. 500 parts of the polymer-containing acetone-water mixture was added to the obtained freeze-dried powder, stirred well with a touch mixer, and then freeze-dried.
- a formulation without polymer solution treatment was also prepared.
- the hGH content in the obtained hGH microparticle preparation was quantified using a micro BCA protein assay kit (Pierce).
- the prepared hGH microparticle preparation was suspended in 0.5% CMC_Na, 5% mannitol, and 0.1% Tween 80, and administered subcutaneously at the back of male SD rats at lOIU / kg (1 IU: 0.35 mg).
- PLA-PEG-PLA-Y004 (PEG ratio 32%, molecular weight 8,200) is dissolved in acetone to a concentration of 20%, and the acetone solution and water are mixed at a ratio of 1: 4 to contain the polymer.
- a mixture of acetone and water was prepared. 500 parts of the polymer-containing acetone-water mixture was added to the obtained freeze-dried powder, and the mixture was stirred well with a touch mixer and then freeze-dried.
- the hGH content in the obtained hGH microparticle preparation was quantified using a micro BCA protein assay kit (Pierce).
- the prepared hGH microparticle preparation was suspended in 0.5% CMC_Na, 5% mannitol, 0.1% Tween 80, and Male SD rats immunosuppressed by crolimus (Fujisawa Pharmaceutical, Osaka) were administered subcutaneously at 30 IU / kg (1 IU: 0.35 mg) to the back of male SD rats. Tacrolimus was administered subcutaneously at a dose of 0.4 mg / rat 3 days before administration of the formulation and 0.2 mg / rat every 3 days after the administration of the formulation.
- a derivative of HAp calcined at 400 ° C in which a part of calcium is replaced by zinc (HAp-Zn-0.5; zinc is 0.5 mol for 9.5 mol of calcium) is mixed with 150 mg of interferon a (IFN-hi) solution (2.86 mg / 525 L), and then water was added to make a final volume of 2 mL. After stirring for 5 minutes, centrifugation was performed at 3,000 rpm for 3 minutes. 15 mL of water was added to the obtained precipitate, and the mixture was stirred for 1 minute.
- IFN-hi interferon a
- HAp-IFN-a sample 2.5 mg was precisely weighed, 0.25 mL of PBS (physiological saline phosphate buffer) diluted 1/10 was added thereto, and the mixture was stirred at 37 ° C. The supernatant was collected over time by centrifugation at 3000 ⁇ m 3 min, and the amount of IFN-released into the supernatant was quantified using the Human Interferon Alpha (Hu IFN-a) ELISA Kit (PBL Biomedical Laboratories). Table 6 shows the results. The release of IFN-H into the 1/10 diluted PBS was significantly suppressed in the formulation treated with the polymer solution, compared to the strength of the control solution that was not treated with the polymer solution and the formulation prepared with the solution. .
- PBS physiological saline phosphate buffer
- PLA-PEG-PLA-Y004 PEG ratio 32%, molecular weight 8,200
- a mixture of acetone and water was prepared. 500 / L of this polymer-containing acetone-water mixture was added to the obtained freeze-dried powder, and the mixture was thoroughly stirred with a touch mixer and freeze-dried.
- a preparation without polymer solution treatment was also prepared.
- the hGH content in the obtained preparation was quantified using a micro BCA protein assay kit (Pierce).
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Abstract
Description
Claims
Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
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JP2006510381A JPWO2005082405A1 (ja) | 2004-02-26 | 2005-01-27 | たんぱく性薬物の注射用徐放性微粒子製剤およびその製造法 |
EP05704198A EP1719523A4 (en) | 2004-02-26 | 2005-01-27 | MICROPARTICULAR PROTEIN CARBIDE RETARD PREPARATION FOR INJECTION AND METHOD FOR THE PRODUCTION THEREOF |
CA002557397A CA2557397A1 (en) | 2004-02-26 | 2005-01-27 | Protein drug sustained-release microparticle preparation for injection and process for producing the same |
US10/588,834 US20070259047A1 (en) | 2004-02-26 | 2005-01-27 | Protein Sustained-Release Microparticle Preparation for Injection and Process for Producing the Same |
Applications Claiming Priority (2)
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JP2004-051526 | 2004-02-26 | ||
JP2004051526 | 2004-02-26 |
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WO2005082405A1 true WO2005082405A1 (ja) | 2005-09-09 |
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PCT/JP2005/001095 WO2005082405A1 (ja) | 2004-02-26 | 2005-01-27 | たんぱく性薬物の注射用徐放性微粒子製剤およびその製造法 |
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US (1) | US20070259047A1 (ja) |
EP (1) | EP1719523A4 (ja) |
JP (1) | JPWO2005082405A1 (ja) |
KR (1) | KR20060129394A (ja) |
CN (1) | CN1921880A (ja) |
CA (1) | CA2557397A1 (ja) |
WO (1) | WO2005082405A1 (ja) |
Cited By (6)
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US20070258903A1 (en) * | 2006-05-02 | 2007-11-08 | Kleiner Lothar W | Methods, compositions and devices for treating lesioned sites using bioabsorbable carriers |
JP2009137875A (ja) * | 2007-12-05 | 2009-06-25 | National Institute For Materials Science | エリスロポエチン徐放製剤とその作製方法 |
WO2009093713A1 (ja) * | 2008-01-25 | 2009-07-30 | Ebara Corporation | ペグ修飾ハイドロキシアパタイト及びそれを基材とする医薬とその製造方法 |
WO2013094955A1 (ko) * | 2011-12-19 | 2013-06-27 | 주식회사 삼양바이오팜 | 분산성이 향상된 생분해성 고분자 미립자의 조성물 및 그 제조방법 |
WO2016092928A1 (ja) * | 2014-12-12 | 2016-06-16 | ジーンメディカル株式会社 | 皮下注射用剤 |
WO2016092929A1 (ja) * | 2014-12-12 | 2016-06-16 | ジーンメディカル株式会社 | 皮下注射用剤及び皮下注射用剤を含有する注射器の製造方法 |
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US8652506B2 (en) * | 2008-06-05 | 2014-02-18 | Boston Scientific Scimed, Inc. | Bio-degradable block co-polymers for controlled release |
CN110527007B (zh) * | 2019-09-05 | 2022-11-08 | 大连合元医疗器械有限公司 | 聚(2-氰基丙烯酸)及其制备方法和应用 |
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Cited By (9)
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US20070258903A1 (en) * | 2006-05-02 | 2007-11-08 | Kleiner Lothar W | Methods, compositions and devices for treating lesioned sites using bioabsorbable carriers |
WO2007133382A2 (en) * | 2006-05-02 | 2007-11-22 | Abbott Cardiovascular Systems Inc. | Methods, compositions and devices for treating lesioned sites using bioabsorbable carriers |
WO2007133382A3 (en) * | 2006-05-02 | 2008-01-10 | Abbott Cardiovascular Systems | Methods, compositions and devices for treating lesioned sites using bioabsorbable carriers |
JP2009137875A (ja) * | 2007-12-05 | 2009-06-25 | National Institute For Materials Science | エリスロポエチン徐放製剤とその作製方法 |
WO2009093713A1 (ja) * | 2008-01-25 | 2009-07-30 | Ebara Corporation | ペグ修飾ハイドロキシアパタイト及びそれを基材とする医薬とその製造方法 |
WO2013094955A1 (ko) * | 2011-12-19 | 2013-06-27 | 주식회사 삼양바이오팜 | 분산성이 향상된 생분해성 고분자 미립자의 조성물 및 그 제조방법 |
WO2016092928A1 (ja) * | 2014-12-12 | 2016-06-16 | ジーンメディカル株式会社 | 皮下注射用剤 |
WO2016092929A1 (ja) * | 2014-12-12 | 2016-06-16 | ジーンメディカル株式会社 | 皮下注射用剤及び皮下注射用剤を含有する注射器の製造方法 |
US10918766B2 (en) | 2014-12-12 | 2021-02-16 | Motejo Ltd. | Agent for hypodermic injection |
Also Published As
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CA2557397A1 (en) | 2005-09-09 |
JPWO2005082405A1 (ja) | 2007-10-25 |
EP1719523A4 (en) | 2009-07-15 |
CN1921880A (zh) | 2007-02-28 |
EP1719523A1 (en) | 2006-11-08 |
US20070259047A1 (en) | 2007-11-08 |
KR20060129394A (ko) | 2006-12-15 |
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