WO1996034061A1 - Materiau polymere, materiau medical et composition polymere liquide - Google Patents
Materiau polymere, materiau medical et composition polymere liquide Download PDFInfo
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- WO1996034061A1 WO1996034061A1 PCT/JP1996/000769 JP9600769W WO9634061A1 WO 1996034061 A1 WO1996034061 A1 WO 1996034061A1 JP 9600769 W JP9600769 W JP 9600769W WO 9634061 A1 WO9634061 A1 WO 9634061A1
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- copolymer
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
- C08L101/00—Compositions of unspecified macromolecular compounds
- C08L101/02—Compositions of unspecified macromolecular compounds characterised by the presence of specified groups, e.g. terminal or pendant functional groups
- C08L101/06—Compositions of unspecified macromolecular compounds characterised by the presence of specified groups, e.g. terminal or pendant functional groups containing oxygen atoms
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
- A61L29/04—Macromolecular materials
- A61L29/049—Mixtures of macromolecular compounds
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
- A61L31/04—Macromolecular materials
- A61L31/041—Mixtures of macromolecular compounds
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08L—COMPOSITIONS OF MACROMOLECULAR COMPOUNDS
- C08L75/00—Compositions of polyureas or polyurethanes; Compositions of derivatives of such polymers
- C08L75/04—Polyurethanes
- C08L75/08—Polyurethanes from polyethers
Definitions
- the present invention relates to a polymer material that is a polymer mixed material that can be used for medical materials, cosmetic materials, paint materials, and the like, a liquid polymer composition as a raw material thereof, and excellent biocompatibility and mechanical properties.
- the present invention relates to a medical material which is a polymer mixture having strength and a polymer composition for a medical material as a raw material thereof.
- the polymer having a phosphorylcholine group is excellent in biocompatibility because it has a structure similar to the phospholipid constituting the cell membrane, and can deactivate complements such as blood coagulation factors.
- biological material non-adsorptive such proteins or cells, antithrombotic, moisture, is this a force s knowledge showing excellent properties as a medical polymer material having a lipid bilayer weaker Joka etc. Al., Journal of Biomedical Materials Research, 24 (1990) 1069-1077, Kazuhiko Ishihara, et. A1, Journal of Biomedical Materials Research, 25 (1991) 1397-1407.
- JP-A-3-39309 discloses a copolymer of 2-methacrylo-inoleoxhetylphosphorinolecoline and a methacrylate ester Is an excellent biocompatible material.
- WO93-012122 discloses a polymer having a phosphorinolecholine group. It is described that when used as a ligating material, it can be used as a material having a biocompatible surface in various bio-related applications.
- WO93-1661117 discloses that a water-soluble cellulose derivative obtained by graft polymerization of 2-methacryloyloxyshethylphosphorinolecoline to water-soluble cellulose is disclosed in It is disclosed that it has both biocompatibility and affinity for cellulose, so that it can be used for biocompatible materials such as blood purification.
- Japanese Patent Application Laid-Open No. Sho 59-433342 discloses a polymer composition comprising a moisture-sensitive material comprising a polymer having a phosphorylcholine group and a thin film material as a water-soluble polymer. It is disclosed that it is useful as a humidity sensor material.
- a polymer composition comprising a polymer having a phosphorylcholine group and a polymer having desirable mechanical and / or physical properties. It is disclosed that it is used as a biomedical material.
- various monomers, homopolymers, copolymers having a phosphorylcholine group, and their production methods are described in, for example, JP-A-54-63025, Japanese Unexamined Patent Application Publication No. Sho 58-154, 591, Japanese Unexamined Patent Publication No. Sho 63-3222, Japanese Unexamined Patent Publication No. Hei 5-110751, Japanese Unexamined Patent Application Publication No. It is conventionally known as described in Japanese Patent Publication No. 57 and W093-01221 Publication.
- the polymer or copolymer having a phosphorylcholine group shows remarkable biocompatibility, when it is used as a medical material, it necessarily has sufficient mechanical properties such as mechanical strength and durability. It cannot be said that. Therefore, it has a phosphorylcholine group as described above.
- copolymerizable monomer is copolymerized with the monomer.
- Attempts have also been made to improve by mixing a hydrophobic polymer having mechanical strength and durability.
- a polymer having a functional group exhibiting remarkable water solubility, such as a phosphorylcholine group unlike the conventional mixing of hydrophobic polymers, which is generally performed in the past, In fact, the results are not sufficiently good.
- segmented polyurethane has excellent mechanical properties and good blood compatibility as compared with other materials (Japanese Patent Application Laid-Open No. 57-139393). No. 2, Japanese Patent No. 683885, U.S. Pat. No. 4,739,904, WO83-06995) are known. I have. Such segmented polyurethanes are widely used as medical materials in blood circuits, artificial hearts, various catheters, medical sensors, etc. Edited by Tetsuzo Kishi, “Artificial Organs” 1994-95, published by Nakayama Shoten). However, if these are used in vivo for a long period of time, they will not always show ideal antithrombotic properties because the materials will deteriorate and calcify based on inflammatory reactions and cell adhesion. It is not a satisfactory state.
- polymer blends Attempts to modify materials by mixing two or more polymer compounds with different properties are called “polymer blends”, and are generally well performed.
- a hydrophilic polymer compound with a highly hydrophobic polymer compound, or a mixture of a polymer compound with excellent crystallinity and a polymer compound with good amorphous properties When two kinds of polymer compounds having contrasting properties are mixed to form a film, polymer compounds having the same properties are aggregated by molecular motion to cause phase separation. Modification of materials using this phase separation is also a general method of polymer blending, and is a multi-phase structural material that skillfully utilizes the phase separation mechanism of a polymer mixed system that can be compatible with each other. Is also being developed.
- the 2- (methacryloyl) oxy-1,2- (tri) (Methylammonium) A 1: 2 copolymer of ethylphosphoric acid and n-dodecylmethacrylate and a segmented polyurethane are a single dichloromethan. Dissolution is carried out with a solvent or a mixed solvent of ethyl acetate and propan-2-ol.
- the purpose of the present invention is to provide a polymer material and a medical material having both excellent biocompatibility and excellent mechanical properties such as mechanical properties and durability.
- Another object of the present invention is to provide a long-term stable raw material for a polymer material and a medical material having both excellent biocompatibility and mechanical properties such as excellent mechanical properties and durability.
- An object of the present invention is to provide a liquid polymer composition which is a homogeneous solution.
- the present inventors have conducted various studies on a hydrophobic monomer, a hydrophobic polymer to be mixed, a solvent, a mixing method, and the like in order to achieve the above-mentioned purpose, and as a result, a host having a remarkably high polarity has been obtained.
- R 1 R 2 and R 3 are the same or different groups and represent a hydrogen atom or an alkyl group having 1 to 4 carbon atoms
- a mixed material comprising a copolymer A obtained by copolymerizing a monomer composition containing a polymer, and at least one type of water-phobic polymer B other than the copolymer A, wherein the structure of the mixed material is Provided is a polymer material characterized in that a domain of several hundreds // in or less composed of copolymer A exhibits phase separation uniformly distributed in a phase composed of hydrophobic polymer B. .
- hydrophobic polymer B in the polymer material a segment obtained by a polyaddition reaction between dicyclohexylmethanediisosinate and polyetherdiol is used. Selected from the group consisting of polyurethane halides, segmented polyurethans obtained by the polyaddition reaction of diphenylmethanediisocyanate with polyetherdiol, and mixtures thereof.
- Demented polyurethan sementated polyurethan obtained by polyaddition reaction of diphenylmethanthocyanate and polyetherdiol, and the power of a mixture thereof
- a liquid polymer composition containing a hydrogen chloride solvent and a mixed solvent of a lower alcohol solvent and having a concentration of 60% or less is provided.
- an alkyl (meta) acrylate having 1 to 4 carbon atoms having a side chain represented by the general formula (1) and a branched alkyl (meth) having 5 to 15 carbon atoms
- a monomer composition containing a hydrophobic monomer selected from the group consisting of atalylate, alicyclic alkyl (meth) atalylate and a mixture thereof.
- a mixed material containing a copolymer A and one or more kinds of hydrophobic polymers B other than the copolymer A, wherein the mixed material is a hydrophobic polymer B and is a hexahedral hexylmethandisilane.
- the mixed material comprises a segmented polyurethan obtained by the polyaddition reaction of polyether diol and polyether diol, and the structure of the mixed material is a domain of several hundred m or less made of copolymer A. Indicates phase separation uniformly distributed in the phase composed of hydrophobic polymer B. Medical material is provided, wherein a call that.
- a liquid polymer composition as a raw material of the medical material, wherein the alkyl (meth) alkyl having 1 to 4 carbon atoms and having a side chain represented by the general formula (1) is provided.
- the structure of the mixed material, which contains the urea shows phase separation in which a domain of several hundred jum or less composed of the copolymer A is uniformly distributed in the phase composed of the hydrophobic polymer B.
- a medical material is provided, characterized in that:
- a liquid polymer composition as a raw material of the medical material, wherein the alkyl (meth) alkyl having 1 to 4 carbon atoms and having a side chain represented by the general formula (1) is provided.
- One or more types of hydrophobic polymers other than copolymer A containing segment topopolyurethane obtained by the polyaddition reaction of diphenylmethane succinate with polyetherdiol.
- a liquid component for medical materials that contains coalesced B and a mixed solvent consisting of a halogenated hydrocarbon solvent and a lower alcohol solvent and has a turbidity of 60% or less.
- a child composition is provided.
- Fig. 1 is a graph showing the stress-strain curve of the uniform film of the polymer composition measured in the example or the SPU-1 single film / non-uniform film of the comparative example.
- FIG. 2 is a graph showing a stress-strain curve of a uniform film of the polymer composition measured in the example or a non-uniform film of the comparative example.
- the polymer material and the medical material of the present invention comprise a specific copolymer A obtained by copolymerizing a monomer composition containing a monomer having a specific side chain and a hydrophobic monomer as a composition; A mixed material containing at least one type of hydrophobic polymer B other than the copolymer A, wherein the structure of the mixed material is not more than several hundreds / xm of the copolymer A, preferably 100 / m or less, particularly preferably from 0.01 to 50 ⁇ , exhibiting phase separation in which the domain is uniformly distributed in the phase comprising the hydrophobic polymer.
- the uniformly distributed phase separation means that the copolymer ⁇ and the hydrophobic polymer ⁇ exhibit phase separation, and the mixed material is formed by the mechanical properties of the hydrophobic polymer B.
- the copolymer A of a specific size is added to the hydrophobic polymer B phase. This means that the domains are scattered.
- the liquid polymer composition of the present invention which is used as a raw material for such a polymer material or a medical material, conventionally has a very high hydrophilicity.
- a polymer having a phosphorylcholine group which is used only in a highly water-soluble solvent such as water or lower alcohol, is used as a mixture with a hydrophobic polymer.
- a combination of A and the hydrophobic polymer B is specified, and a specific solvent is selected, so that a uniform liquid state for producing the polymer material or the medical material of the present invention is obtained. It was possible to do.
- the uniform liquid state is defined as turbidity (100 in a state where light is completely shielded, 100% in a cell containing only a solvent (an empty cell in a molten state without using a solvent)).
- the homogeneity is 60% or less, preferably 50% or less. The fact that it shows sex. Therefore, such a liquid polymer composition does not separate even if it is kept in a liquid state, and can be stored for a long time.
- the raw materials of the polymer material of the present invention other than those specified in the liquid polymer composition of the present invention may be those in the above-mentioned uniform liquid state.
- it can be appropriately prepared by selecting a combination of the copolymer A and the hydrophobic polymer B and the type of the solvent, or by setting the solvent to a molten state without a solvent.
- the (co) polymer having such a group and another polymer are converted into a uniform liquid state because of the remarkable water solubility of the phosphoric acid group. It is a solution to what has been considered difficult to do, and removes or drys the solvent from such a homogeneous liquid state of the raw material. It has been found that the mixed material in the solid state is a novel material having the above-mentioned specific structure and having both mechanical strength and biocompatibility.
- the above-mentioned specific structure is formed by evaporating the solvent by drying the liquid polymer composition of the present invention, for example, in a hydrophobic environment of the hydrophobic polymer B.
- copolymer A having a very water-soluble phosphorylcholine group it becomes difficult for the copolymer A having a very water-soluble phosphorylcholine group to maintain a uniformly dissolved state, and it gradually aggregates in the solidified birch, and W / It is considered to stabilize the system by phase separation like O-type emulsification.
- the monomer having a specific side chain as an essential component in the monomer composition for preparing the copolymer A is represented by the following general formula (1)
- R 1 , R 2 and R 3 are the same or different groups and represent a hydrogen atom or an alkyl group having 1 to 4 carbon atoms
- This monomer is a monomer having a polymerizable double bond and a side chain represented by the above general formula (1) in the molecule, for example, 2 — (methacryloyl (Roxy) 2ch — (Trimethinorea monmonio) Etylphosphate, 3 — (Metacryloyloxy) Propyl 1 2 ′ — (Trimethinorea monmonio) Echinorehosufate.
- the content ratio of the structural unit of the monomer having a side chain represented by the general formula (1) is slightly reduced in order to sufficiently impart biocompatibility to the obtained material.
- the total amount is preferably at least 1 mol%, more preferably at least 10 mol%, particularly preferably from 10 to 70 mol%.
- the hydrophobic monomer as an essential component of the monomer composition for preparing the copolymer A when preparing a raw material of a polymer material, has a phase with a hydrophobic polymer B described later. It shows the effect of enhancing the solubility.
- the hydrophobic monomer is a monomer having low solubility in water and copolymerizable with the monomer having a side chain represented by the general formula (1). Specifically, for example, styrene derivatives such as styrene, methylstyrene, and methinolestyrene;
- Alicyclic alkyl (meta) acrylates such as (meta) acrylate, and carbon number 5 to 15 such as 2-ethylhexyl (meta) acrylate Branched alkyl (meta) acrylates; glycidinole (meta) acrylate, (meta) acrylate Alkyl (meth) acrylates having a reactive functional group such as tilttrimethoxysilane; 2— (meta) acryloyloxyethylbutylbutyl urethane, 2— (me (T) acryloyloxy shetilbenzilurethane, 2 — (meta) acryloyloxy shelylphenyl urethane, etc.
- (Meth) acrylates ethyl vinyl ether, butyl vinyl ether, vinyl acetate, vinyl chloride, vinylidene chloride, ethylene, propylene, isobutylene, getylfumarate, getylma Rates and so on.
- a branched alkyl (meta-meta) having 5 to 15 carbon atoms may be used depending on the hydrophobic polymer B described later.
- A) a hydrophobic monomer selected from the group consisting of acrylates, aliphatic alkyl (meta) acrylates and mixtures thereof, or alkyls having urethane linkages Use the accredit rate.
- copolymer A containing organic proportion of the structural unit of the hydrophobic monomer, 3 0-9 0 molar 0/0 favored arbitrariness.
- the copolymer A and the hydrophobic polymer B described later are in the uniform liquid state described above.
- a combination in which the constitutional units of each monomer are randomly and uniformly distributed is preferable.
- a combination of (meta) acrylates with high polymerizability and easy control is optimal.
- the monomer composition for preparing the copolymer A includes:
- other monomers that can be polymerized with the monomer having a side chain represented by the general formula (1) can be used as a comonomer.
- aqueous solutions of (meth) acrylic acid, (meth) acrylinoleic acid amide, 2—hydroxyxethyl (meta) acrylate, N-vinylpyrrolidone, etc. can be cited.
- the content ratio of the constituent units of such other monomers in the copolymer A is preferably 10 mol% or less.
- the copolymer A can be produced by subjecting the monomer composition to a conventional polymerization method such as solution polymerization, suspension polymerization, emulsion polymerization or bulk polymerization using a polymerization initiator.
- the molecular weight of copolymer A is preferably in the range of 300 to 700,000 in terms of number average molecular weight, and takes into consideration the properties as a polymer compound and the solubility in a solvent. And the range of 5,000 to 4,000 is more preferred.
- the obtained copolymer A include 2 — (methacryloyloxy) ethyl — 2 ′ — (trimethylammonio) ethyl phosphate and cyclo Copolymer with hexylmethacrylate, 2 — (methacryloyloxy) ethyl 1 2 ′ — (trimethylammonio) ethylethyl phosphate and 2-ethylethyl Copolymer with sylmethacrylate, 2— (methacryloylnorexoxy) echinole 2,1 (trimethylammonio) ethynolephosfet and n—butyl methacrylate 2-(methacryloyloxy), ethyl 2 -'- (trimethylammonio) copolymer with n-dodecylmethacrylate , 2 — (Metacrylo Ioki ) Echiru 2 '- (g Li (Metacrylo
- the copolymer A used for the medical material of the present invention includes an alkyl (meta) acrylate having 1 to 4 carbon atoms having a side chain represented by the general formula (1), and 5 to 1 carbon atoms. And a monomer containing a hydrophobic monomer selected from the group consisting of branched alkyl (meth) acrylates, alicyclic alkyl (meth) acrylates, and mixtures thereof.
- the hydrophobic polymer B used for the polymer material of the present invention and the raw material thereof has extremely low solubility in water, and imparts mechanical properties such as mechanical strength and durability to the obtained polymer material. You can do it. Then, when the liquid polymer composition is formed into a liquid polymer composition by the combination with the copolymer A, the liquid state becomes the uniform liquid state described above, and the material becomes a solid state. Thus, the specific structure described above can be formed.
- segmented polypolyurethane polychlorinated butyl, polypropylene, polystyrene, polyethylene, ABS resin, polymer Chilpentene, polystyrene-butadiene block copolymer, polymethyl methacrylate, polymethyl siloxane, polyethylene terephthalate, polyethyl methacrylate Rear linolephone, porinolephone, polyetherimide, polycarbonate, polybutylene terephthalate, polyacetar, nylon, Polymer materials such as nylon-ABS copolymer, polysulfone-thermoplastic polyester copolymer, polytetrafluoroethylene, cellulose, natural rubber, collagen, etc.
- Heparin-immobilized or sustained-release material examples thereof include polymeric materials for medical materials and the like in which a physiologically active substance such as a prostaglandin-immobilized or sustained-release material is immobilized.
- the molecular weight of the hydrophobic polymer B is in the range of 300 to 700,000 in number average molecular weight. Is preferred but not limited to this.
- segmented polyurethane as the hydrophobic polymer B, blood circuits, artificial hearts, various force tables, sensors for medical materials, cell culture equipment
- Segmented polyurethane is defined as a polyaddition reaction between an excess of diisocyanates or polyisocyanates and a polyether or polyester diol, A group of polymers obtained by polyaddition of a diol or a diamine as a chain extender.
- the isocyanates include diphenylmethane disocyanate and dihexyl hexylmethane disocyanate
- the diols include polyesterdiol and polyetherdiol.
- the chain extender include ethylenediamine, 4,4'-methylenedianiline, water, propylenediamine, butanediol and the like.
- the hydrophobic polymer B used for the medical material of the present invention and the liquid polymer composition as a raw material thereof is the copolymer A, wherein the copolymer A has 1 to 4 carbon atoms having a side chain represented by the general formula (1).
- the copolymer A has a side chain represented by the general formula (1) and has an alkyl (meth) acrylate having 1 to 4 carbon atoms, and a urethane bond which is a hydrophobic monomer.
- the mixing ratio of the copolymer A and the hydrophobic polymer B is such that the copolymer A and the hydrophobic polymer B 0.5 to 95 weight of the copolymer AO. /.
- the hydrophobic polymer B is preferably in the range of 99.5 to 5% by weight, particularly the copolymer Al to 30 weight%. %, Hydrophobic polymer B 99 to 70% by weight is preferred.
- the copolymer A content is less than 0.5% by weight, biocompatibility derived from the side chain represented by the general formula (1) tends to be difficult to develop, and when the content exceeds 95% by weight, the hydrophobic polymer is used. It is not preferable because the mechanical strength, durability and the like derived from B tend to hardly develop.
- a mixture containing the copolymer A and at least one other hydrophobic polymer B other than the copolymer A is mixed with the above-mentioned homogeneous liquid state (solvent-based). (A dissolved state or a heated molten state), and thereafter, a method of obtaining a solid state of a desired shape or the like by cooling and solidifying or evaporating and removing the solvent.
- solvent-based homogeneous liquid state
- the copolymer A having a highly polar phosphorylcholine group should be a material that exhibits strong specific interaction by associating strongly in a hydrophobic environment. Can be done.
- the solvent used is, of course, compatible with each polymer, but is preferably a low-molecular compound that can be easily removed by evaporation to facilitate coating and film formation. It may be a mixed solvent.
- the selection of a solvent with good compatibility is determined by searching for the optimal combination that approximates the solubility parameter of the polymer constituting the polymer material and the solubility parameter of the solvent. Can be carried out.
- a specific polymer material of the present invention that is, a copolymer A of a monomer having a side chain represented by the above general formula (1) and a hydrophobic monomer, and dicyclohexylmethazinediocyanine Segmentation of polyolefin obtained by the polyaddition reaction between polyetherdiol and polyetherdiol, and the polyaddition reaction of polyetherdiol with polyphenoldiol.
- hydrophobic polymers B other than the copolymer A containing the segmented polyurethan selected from the group consisting of the segmented polyurethan and the mixture thereof In the case of a polymer material which is a mixed material containing, or a liquid polymer composition as a raw material of the medical material of the present invention, the solvent is a specific copolymer A which constitutes these.
- Solubility (++) dissolving, (+) dissolving by ultrasonic irradiation for 5 minutes, (soil) swelling,
- ultrasonic irradiation can be performed to further increase the uniformity, and is made of a copolymer A formed when the material (solid state) is formed.
- the size of the domain can be made smaller and the distribution of the domain can be made more uniform.
- a probe type ultrasonic generator or a commercially available ultrasonic cleaner can be used for ultrasonic irradiation.
- the irradiation time should be at least 5 minutes.
- turbidity can be obtained by using a commonly used mechanical device such as a kneader, a Banbury mixer, a roll, and various molding machines.
- the melting may be performed so as to be 60% or less, preferably 50% or less.
- the amount of the solvent used is not particularly limited as long as the copolymer A and the hydrophobic polymer B can be dissolved to form the above-mentioned uniform liquid state, and may be appropriately selected. can do.
- the polymer material and the medical material of the present invention are prepared by forming a uniform liquid state material such as the liquid polymer composition of the present invention into a desired material, or forming a film on the surface of the material. Desired function for material Can be given. In the case of coating on the surface of a material, by selecting a material having a structure similar to that of the material as the hydrophobic polymer B, the adhesion, durability and the like are remarkably improved. be able to.
- the polymer material of the present invention has excellent physical properties such as biocompatibility and mechanical strength, it can be used for medical devices such as blood circuits, artificial hearts, various catheters, sensors for medical materials, and cell culture equipment. It can be widely used for application materials and coating materials.
- the polymer material of the present invention comprises a copolymer A obtained by copolymerizing a monomer composition containing a monomer having a side chain represented by the general formula (1) and a hydrophobic monomer. Since it has a hydrophobic polymer B other than the polymer A in a specific structure, it has excellent biocompatibility and hydrophobicity caused by the monomer having the following chain represented by the general formula (1). It has both physical properties such as the practical mechanical strength of the polymer B. In addition, since a domain of a specific size composed of copolymer A shows phase separation uniformly distributed in the phase composed of hydrophobic polymer B, it has both biocompatibility and mechanical properties. It is useful as a medical material.
- segmented polyurethane as the hydrophobic polymer B, especially when durability is required, flexibility is required, and mechanical deformation is required. It can solve the problem of peeling due to lack of adhesion to the substrate, even when used for medical materials in the blood circulation system, which is easily affected.
- blood circuits, artificial hearts, various catheters, sensors for medical materials First, it is useful for various medical materials such as cell culture equipment.
- CHMA Roeki Shirume data click Li rate
- EHMA abbreviated 2 - Kishirume data to Echiru click Li rate
- MPC the monomer composition of CHMA or EHMA the (3 0 Z 7 0) (mol 0/0), the concentration of 1 Moruno l Azobisisobutyronitrile as a polymerization initiator so as to have a concentration of 5 millimoles Z-litre.
- Solution polymerization was carried out at the polymerization time shown in FIG.
- Synthesis Examples 1 and 2 are homopolymers of CHMA and EHMA, respectively (abbreviated as PC and PE, respectively).
- the copolymers of Synthesis Examples 3 and 4 were identified by IR spectroscopy.
- MTSi 2-methacryloyloxyl tritrimethoxysilane
- n - monomer composition of Dodeshirume data click Li rate (hereinafter DMA hereinafter) (33Z67) (mol%) was dissolved to a molar mass of 1 mol, and azobisisobutyronitrile was used as a polymerization initiator in 5 ml. The solution was dissolved so as to have a molar crispness, and solution polymerization was performed at 60 ° C. for the polymerization time shown in Table 2.
- a monomer composition (3,600,10) (mol 0 /.) Of loyloxy-shelfyl-urethane (hereinafter abbreviated as MBPU) can be converted to 1 mol Z liter.
- Azobisisobutyronitrile as a polymerization initiator was dissolved at a concentration of 5 mmol / litre-noise, and the mixture was dissolved at 60 ° C. The solution polymerization was carried out at the polymerization time shown in Table 1.
- the presence of the phosphorinolecholine group was confirmed by the presence of the P — O— CH 2 bond peak, and the presence of the C-O bond peak at 1730 cm- 1 the presence of the group, 2 8 0 0 ⁇ 3 0 0 0 c m- 1 near one CH 2 - the presence of and this and force et alkyl Le group having a peak one CH 3, 1 5 8 0 cm -1
- the presence of a urethane bond was confirmed by the presence of a peak of one NHCOO— group in each. From the above, it was confirmed that MPC, BMA and MBPU copolymer (hereinafter abbreviated as PMU) were obtained in Synthesis Example 7.
- the number average molecular weight (M n) of the obtained copolymer was determined by connecting a trade name “Asahipak GS-510 column” to a GPC device of TOSOH, and closing the mouth. Polystyrene was used as a standard in the system. Table 2 shows the results.
- the phosphorus concentration was quantified by measuring the absorbance of this solution at 817.8 nm.
- the calibration curve was created using sodium phosphate hydrogen phosphate.
- the copolymer composition was calculated from the amount of copolymer used (6 mg), the phosphorus concentration, and the molecular weight of the MPC unit. Table 2 shows the results.
- Thermedics hereinafter abbreviated as SPU-1), PMC (Synthesis Example 3), PME (Synthesis Example 4), PMES i (Synthesis Example 5), and PMD (Synthesis Example 6) were separately dissolved to 5% by weight.
- a solution was prepared.
- the SPU-1 solution and the PMC solution, the SPU-1 solution and the PME solution, the SPU-1 solution and the PMES i solution, and the SPU-1 solution and the PMD solution were mixed at a weight ratio of 95: 5 and The mixture was mixed at a ratio of 9: 1 and stirred for 30 minutes to form a homogeneous solution, and the turbidity of these solutions was measured by the method described later.
- Example 11 a film was prepared in the same manner as in Example 11 using only the 5 wt% 5 1_1 _ 1 solution to prepare a film, which was used as Comparative Example 115.
- PVA polyurethane film
- PVA 0.58 and 0.05 g of 1 ⁇ , N'-methylbenzenebisacrylinoleamide were stirred and dissolved in 8.5 ml of distilled water.
- An aqueous solution was prepared.
- the obtained aqueous solution was filtered through a glass filter, degassed under reduced pressure, and coated on the film (segmented polyurethane film) prepared in Comparative Example 16-16.
- a thin film was formed. After that, it was irradiated with a 250 W high-pressure mercury lamp for 3 hours to polymerize it, and a polyurethane film whose surface was treated with MPC polymer described in Japanese Patent Publication No. 59-43332 was obtained. .
- a polymer mixture of an MPC homopolymer that does not contain a hydrophobic monomer unit and a water-soluble polymer, polyvinyl alcohol, is coated on a segmented polyurethane. It is the one that was done. Various measurements described later were performed on the film obtained in this manner.
- a polymer membrane described in Japanese Patent Application Publication No. 7-504449 was prepared. That is, 1.1 g of PME (Synthesis Example 4) was mixed with 20 g of SPU-1, 40 g of ethyl acetate, and 40 g of propan-2-ol, and the resulting solution was turbid. The degree was measured by the method described below. At this time, it was visually observed that SPU-1 was slightly swollen and almost undissolved. The solvent is then removed with a rotary evaporator, and the dried material is compressed between the polyethylene terephthalate receiving sheets into a 0.3 mm thick film (10 tons). (Z ft 2 , 100, 10 minutes). Various measurements, which will be described later, were performed on the film thus obtained.
- ultrasonic waves were irradiated for 30 minutes on a scale 6 with a frequency of 20 KHz and an output of 200 W.
- the turbidity of each of the obtained solutions was measured according to the method described later.
- Example 2-2 The mixed homogeneous solution obtained in Example 2-2 was coated on the film (segmented polyurethane film) prepared in Comparative Example 15 to form a thin film. Put this membrane dryer to remove the solvent and 1 ⁇ heat 6 0 £ €. After drying under reduced pressure, polymer containing MPC Polyurethane film surface-treated with the product was obtained. Each measurement described later was performed on the obtained film.
- the glass transition temperature (Tg) from the differential scanning calorimeter (DSC) measurement was measured. Specifically, about 10 mg of the obtained polymer film was collected, sealed in an aluminum pan for DSC, and set in a predetermined place. Then, it was cooled to 100 ° C with liquid nitrogen, heated to 300 ° C at a rate of 10 ° C / min, and the calorific value was measured to determine the glass transition temperature (T g). . Table 3 shows the results.
- Comparative Example 11-1-1-4 or Comparative Example 2-1-2-3 the MPC polymer part appeared as agglomerates, probably because the liquid material of the raw materials was not uniformly dissolved. There was no phase separation in the order of several hundred ⁇ or less. In Comparative Examples 1 to 6, no domain could be recognized, probably because the polymers to be mixed were completely dissolved. Comparative Example 17 shows that although the structure of hydrophobic polymer ⁇ ⁇ could be maintained from the glass transition temperature, the polymer mixture coated on the surface was compatible with MPC copolymer. Domain could not be detected.
- XPS X-ray photoelectron spectroscopy
- Polymer films having a thickness of 0.3 mm were prepared, and these films were punched into a circular shape having a diameter of 1.5 cm, immersed in 10 ml of distilled water, and allowed to stand. Three and ten days after immersion in water, 50 ⁇ l of distilled water whose membrane was immersed was collected, and the phosphorus concentration was quantified according to the above-described method for determining the composition of the MPC copolymer. Next, the elution amount (mg Zcm 3 ) of MPC copolymer per membrane unit volume was determined from the phosphorus concentration. Table 4 shows the results.
- a tensile test of a polymer film having a width of about 5 mm, a length of 10 mm, and a thickness of about 0.3 mm was performed under a condition of a tensile speed of 0.2 mm Z.
- the measurement was performed three times for each type of film sample, the average value was obtained, and the Kerr strain curve was obtained.
- the results are shown in Figs. 1 and 2 Shown in Similarly, stress-strain curves were obtained for the SPU-1 single film of Comparative Example 15 and the heterogeneous film in which the MPC copolymer portion was aggregated. The results are also shown in Fig 1 and Fig 2. Further, the same test was attempted on the polymer single films obtained in Synthesis Examples 1 and 2, but it was too soft to withstand the measurement, and an absolute lack of mechanical strength was confirmed.
- the polymer membrane punched out into a circle having a diameter of 1.5 cm was immersed in 1 O ml of a phosphate buffer solution and immersed in it.
- concentration is human blood Serum protein concentration (albumin: 4.5 g ZdI, ⁇ -globulin: 1.6 gZdl, fibrinogen: 0.3 g Zd1) or 1 1 0 concentration at which Arve Mi emissions, gamma -.. Glo Buri down and off Lee Bed Li Roh one Gen-phosphate buffer solution (N a C l 2 4 0 g, KC 1 0 6 g, N a 2 HPO 4 -..
- a polymer film punched to a diameter of 1.5 cm was immersed in a phosphate buffer solution.
- the phosphate buffer solution was removed, and the pre-prepared whole egret blood or platelet-rich plasma (PRP: 3.8% by weight sodium taenoate per 9 ml of egret blood) was prepared.
- PRP platelet-rich plasma
- 1 ml of an aqueous solution of sodium chloride was centrifuged at 75 rpm for 15 minutes.
- 0.7 ml of the mixture was added and allowed to stand.
- Whole blood was brought into contact with the polymer membrane for 60 minutes and 120 minutes, and PRP was brought into contact with the polymer membrane for 60 minutes.
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Description
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Priority Applications (3)
Application Number | Priority Date | Filing Date | Title |
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DE69628162T DE69628162T2 (de) | 1995-04-28 | 1996-03-25 | Polymermaterial, medizinisches material und flüssige polymerzusammensetzung |
EP96906937A EP0823458B1 (en) | 1995-04-28 | 1996-03-25 | Polymeric material, medical material and liquid polymer composition |
US08/945,741 US5977257A (en) | 1995-04-28 | 1996-03-25 | Polymer material, medical material and liquid high molecular composition |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
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JP10592095 | 1995-04-28 | ||
JP7/105920 | 1995-04-28 |
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WO1996034061A1 true WO1996034061A1 (fr) | 1996-10-31 |
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ID=14420308
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PCT/JP1996/000769 WO1996034061A1 (fr) | 1995-04-28 | 1996-03-25 | Materiau polymere, materiau medical et composition polymere liquide |
Country Status (5)
Country | Link |
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US (1) | US5977257A (ja) |
EP (1) | EP0823458B1 (ja) |
KR (1) | KR100258305B1 (ja) |
DE (1) | DE69628162T2 (ja) |
WO (1) | WO1996034061A1 (ja) |
Cited By (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5965111A (en) * | 1998-05-01 | 1999-10-12 | The Procter & Gamble Company | Fast drying water-borne nail polish |
US6080414A (en) * | 1998-05-01 | 2000-06-27 | The Proctor & Gamble Company | Long wear nail polish |
US6080413A (en) * | 1998-05-01 | 2000-06-27 | The Procter & Gamble Company | Polyurethane nail polish compositions |
US6123931A (en) * | 1998-05-01 | 2000-09-26 | The Procter & Gamble Company | Polyurethane and polyacryl nail polish compositions |
US6136300A (en) * | 1998-05-01 | 2000-10-24 | The Procter & Gamble Company | Long wear nail polish having adhesion, toughness, and hardness |
US6197316B1 (en) | 1998-05-01 | 2001-03-06 | The Procter & Gamble Company | Nail polish kits |
US6306375B1 (en) | 1998-05-01 | 2001-10-23 | The Procter & Gamble Company | Long wear nail polish having defined surface properties |
Families Citing this family (13)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2000001424A1 (fr) * | 1998-07-07 | 2000-01-13 | Nof Corporation | Preparation et materiau pour pansement, et methode de traitement des plaies |
US6841639B1 (en) * | 1999-05-27 | 2005-01-11 | Biocompatibles Uk Limited | Polymer solutions |
GB9924502D0 (en) * | 1999-10-15 | 1999-12-15 | Biocompatibles Ltd | Polymer blend materials |
US6858673B1 (en) * | 1999-11-09 | 2005-02-22 | Nof Corporation | Composition for hydrogel, hydrogel and use thereof |
AR027348A1 (es) | 2000-02-04 | 2003-03-26 | Novartis Ag | Proceso para recubrir una superficie |
ATE438097T1 (de) * | 2000-08-29 | 2009-08-15 | Kyowa Medex Co Ltd | Gut reproduzierbares agglutinations- immunoassayverfahren und reagenzien |
US6528554B1 (en) * | 2001-02-15 | 2003-03-04 | The University Of Akron | Ultrasound assisted continuous process for making polymer blends and copolymers |
US7560023B2 (en) * | 2002-11-25 | 2009-07-14 | Shiseido Company, Ltd. | Method of modifying surface of material |
CN100463262C (zh) * | 2004-04-06 | 2009-02-18 | 松下电器产业株式会社 | 电极和燃料电池 |
KR101158269B1 (ko) | 2004-06-15 | 2012-06-20 | 시바 홀딩 인코포레이티드 | 중합체 입자 |
US20100300971A1 (en) * | 2005-05-18 | 2010-12-02 | Sequant Ab | Zwitterionic stationary phase as well as method for using and producing said phase |
US7998124B2 (en) * | 2006-05-31 | 2011-08-16 | Kaneka Corporation | Catheter tube and catheter comprising the tube |
EP2258470A4 (en) * | 2008-03-19 | 2012-10-31 | Shiseido Co Ltd | PROCESS FOR PRODUCING AFFINITY PARTICLES, AFFINITY PARTICLES AND CORRESPONDING SEPARATION METHOD |
Citations (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO1994014897A1 (en) * | 1992-12-23 | 1994-07-07 | Biocompatibles Limited | Polymeric blends with zwitterionic groups |
-
1996
- 1996-03-25 DE DE69628162T patent/DE69628162T2/de not_active Expired - Lifetime
- 1996-03-25 US US08/945,741 patent/US5977257A/en not_active Expired - Lifetime
- 1996-03-25 KR KR1019970707659A patent/KR100258305B1/ko not_active IP Right Cessation
- 1996-03-25 EP EP96906937A patent/EP0823458B1/en not_active Expired - Lifetime
- 1996-03-25 WO PCT/JP1996/000769 patent/WO1996034061A1/ja active IP Right Grant
Patent Citations (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO1994014897A1 (en) * | 1992-12-23 | 1994-07-07 | Biocompatibles Limited | Polymeric blends with zwitterionic groups |
Cited By (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5965111A (en) * | 1998-05-01 | 1999-10-12 | The Procter & Gamble Company | Fast drying water-borne nail polish |
US6080414A (en) * | 1998-05-01 | 2000-06-27 | The Proctor & Gamble Company | Long wear nail polish |
US6080413A (en) * | 1998-05-01 | 2000-06-27 | The Procter & Gamble Company | Polyurethane nail polish compositions |
US6123931A (en) * | 1998-05-01 | 2000-09-26 | The Procter & Gamble Company | Polyurethane and polyacryl nail polish compositions |
US6136300A (en) * | 1998-05-01 | 2000-10-24 | The Procter & Gamble Company | Long wear nail polish having adhesion, toughness, and hardness |
US6197316B1 (en) | 1998-05-01 | 2001-03-06 | The Procter & Gamble Company | Nail polish kits |
US6306375B1 (en) | 1998-05-01 | 2001-10-23 | The Procter & Gamble Company | Long wear nail polish having defined surface properties |
Also Published As
Publication number | Publication date |
---|---|
DE69628162T2 (de) | 2004-04-29 |
KR100258305B1 (ko) | 2000-07-15 |
DE69628162D1 (de) | 2003-06-18 |
KR19990008134A (ko) | 1999-01-25 |
EP0823458B1 (en) | 2003-05-14 |
EP0823458A1 (en) | 1998-02-11 |
EP0823458A4 (en) | 1999-06-16 |
US5977257A (en) | 1999-11-02 |
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