Simulated organ

Abstract

Provided are a simulated organ, a medical procedure training kit, a medical procedure training device, and a method for manufacturing a simulated mucus-covered simulated organ.　The simulated organ includes a simulated blood vessel and a simulated ulcer. At least a part of the outer surface of the simulated blood vessel and at least a part of the simulated ulcer have electroconductivity. The surface resistance value of the part of the simulated blood vessel that has electroconductivity is lower than the volume resistivity of the part of the simulated ulcer that has electroconductivity. The electroconductive part of the simulated ulcer has a volume resistivity of 1×102 to 1×107 Ω･cm.

Description

Mock organs

[0001] The present disclosure relates to a simulated organ, a medical procedure training kit, a medical procedure training device, and a method for manufacturing a simulated mucus-coated simulated organ.

[0002] In recent years, expectations have been rising for minimally invasive surgeries, such as those using endoscopes or laparoscopes, which place less strain on the human body and promise faster recovery, and the number of cases is increasing. For example, endoscopic resection and removal of tumors in the mucosal layer of organs such as the digestive tract (endoscopic mucosal resection and endoscopic submucosal dissection) allows for surgery to be performed with smaller incisions than standard open surgery. Furthermore, endoscopic hemostasis of bleeding in the digestive tract (endoscopic hemostasis) can prevent shock due to bleeding and avoid emergency surgery or death. This reduces the physical burden on patients, shortens hospital stays, and allows for earlier rehabilitation.

[0003] Therefore, there is an increasing demand for surgical training models for doctors and medical students that are compatible with endoscopic and laparoscopic surgeries, and medical training models have been proposed to improve skills and the quality of medical procedures (Patent Documents 1, 2, and 3). Furthermore, there are an increasing number of cases in which surgical energy devices such as electric scalpels are used as instruments.

[0004] JP 2006-116206 A JP 2008-197483 A JP 2015-085017 A

[0005] In training for procedures such as incision and hemostasis using energy devices such as electric scalpels on mucosal tissue of a living body, for example, in a simulated organ that mimics an organ or tissue, a simulated blood vessel is clamped at the tip of the energy device and electricity is passed through it. However, depending on the combination of materials and physical properties of the simulated blood vessel and simulated ulcer, it was not possible to stop bleeding in the simulated blood vessel.

[0006] An object of the present disclosure is to provide a simulated organ that includes a simulated blood vessel and a simulated ulcer and that allows hemostasis treatment to be performed in medical treatment training.

[0007] As a result of examining various means, the inventors have found that the simulated organ is such that at least a part of the outer surface of the simulated blood vessel and at least a part of the simulated ulcer are electrically conductive, the surface resistance of the electrically conductive part of the simulated blood vessel is lower than the volume resistivity of the electrically conductive part of the simulated ulcer, and the volume resistivity of the electrically conductive part of the simulated ulcer is 1.0 × 10 ２ ~1.0 x 10 ７ The inventors have found that hemostasis treatment in a simulated blood vessel can be performed by using a simulated organ with a resistance of Ω·cm, and have thus completed the present invention.

[0008] The present disclosure includes the following aspects: [1] A simulated organ including a simulated blood vessel and a simulated ulcer, wherein at least a portion of the outer surface of the simulated blood vessel and at least a portion of the simulated ulcer are electrically conductive, the surface resistance of the electrically conductive portion of the simulated blood vessel is lower than the volume resistivity of the electrically conductive portion of the simulated ulcer, and the volume resistivity of the electrically conductive portion of the simulated ulcer is 1.0 × 10 ２ ~1.0 x 10 ７ [2] A method for producing a simulated mucus-coated simulated organ, comprising coating at least a portion of the outer surface of a simulated organ including a simulated blood vessel and a simulated ulcer with a simulated mucus composition, wherein at least a portion of the outer surface of the simulated blood vessel and at least a portion of the simulated ulcer are conductive, the surface resistivity of the conductive portion of the simulated blood vessel is lower than the volume resistivity of the conductive portion of the simulated ulcer and higher than the volume resistivity of the simulated mucus composition, and the volume resistivity of the conductive portion of the simulated ulcer is 1.0 x 10 ２ ~1.0 x 10 ７ Ω·cm, and the simulated blood vessel comprises a thermoplastic resin.

[0009] According to the present disclosure, a simulated organ can be provided that includes a simulated blood vessel and a simulated ulcer, and that allows hemostasis treatment to be performed in medical treatment training.

[0010] An embodiment of the present disclosure will be described in detail below. However, the scope of the present disclosure is not limited to the embodiment described herein, and various modifications can be made without departing from the spirit of the present disclosure. Each aspect disclosed in this specification can be combined with any other feature disclosed in this specification. Furthermore, when multiple upper and lower limit values ​​are described for a specific parameter, any of these upper and lower limit values ​​can be combined to form a suitable numerical range. Furthermore, the lower and / or upper limit values ​​of a numerical range described in this disclosure are numerical values ​​within that numerical range and may be replaced with numerical values ​​shown in the examples. The expression "X to Y" indicating a numerical range means "X or more and Y or less." If a specific description described for one embodiment also applies to other embodiments, that description may be omitted in other embodiments.

[0011] [First embodiment (simulated organ)] The simulated organ according to this embodiment is a simulated organ including a simulated blood vessel and a simulated ulcer, in which at least a part of the outer surface of the simulated blood vessel and at least a part of the simulated ulcer are electrically conductive, the surface resistance of the electrically conductive part of the simulated blood vessel is lower than the volume resistivity of the electrically conductive part of the simulated ulcer, and the volume resistivity of the electrically conductive part of the simulated ulcer is 1.0 × 10 ２ ~1.0 x 10 ７ It is a simulated organ with a resistance of Ω·cm.

[0012] <Simulated Blood Vessel> The simulated blood vessel is a tubular structure, at least a portion of its outer surface is electrically conductive, and is not limited to a specific area as long as it can supply simulated blood to the treatment surface of a simulated ulcer in medical procedure training using a simulated organ.

[0013] In one embodiment, the simulated blood vessel preferably contains a thermoplastic resin. When the simulated organ is used for medical procedure training using an energy device, the simulated blood vessel contains a thermoplastic resin, which makes it easier to reproduce the behavior of human blood vessels due to heat generated when electricity is applied by the energy device, and makes it easier to stop bleeding.

[0014] (Configuration of simulated blood vessel) The simulated blood vessel may be composed of one layer or multiple layers. That is, the simulated blood vessel may be a tubular single-layer structure composed of a conductive material, or a multi-layer structure including a base layer constituting a tubular structure and a conductive layer made of a conductive material, or a two-layer structure composed of the base layer and the conductive layer. When the simulated blood vessel includes or is composed of a base layer and a conductive layer, it is sufficient that the conductive layer is disposed on at least a portion of the outer surface of the base layer, but the conductive layer may also be disposed on the entire outer surface of the base layer.

[0015] In one embodiment, the diameter (outer diameter) of the simulated blood vessel is 0.5 to 10.0 mm. In another embodiment, the diameter of the simulated blood vessel is preferably 0.7 to 5.0 mm, and more preferably 1.0 to 3.0 mm. By setting the diameter of the base layer to 0.5 mm or more, processing stability during molding and handling during preparation of a simulated organ are improved, and by setting the diameter of the simulated blood vessel to 10.0 mm or less, the reproducibility of human blood vessels is improved, and poor electrical conduction by energy devices can be suppressed. The inner diameter of the simulated blood vessel is preferably 0.3 to 8.0 mm, more preferably 0.3 to 3.6 mm, and even more preferably 0.4 to 2.0 mm.

[0016] In one embodiment, the simulated blood vessel has a thickness of 0.05 to 2.0 mm. The thickness of the simulated blood vessel is preferably 0.05 to 1.0 mm, more preferably 0.1 to 0.7 mm, and even more preferably 0.2 to 0.5 mm. By making the thickness of the simulated blood vessel 2.0 mm or less, thermal conductivity is improved when the simulated blood vessel is held with an energy device, and heat is transferred in a shorter time.

[0017] In one embodiment, when the simulated blood vessel includes a base layer and a conductive layer, the diameter (outer diameter) of the base layer is 0.5 to 10.0 mm. In another embodiment, the diameter of the base layer is preferably 0.7 to 5.0 mm, and more preferably 1.0 to 3.0 mm. By setting the diameter of the base layer to 0.5 mm or more, processing stability during molding and handling during preparation of a simulated organ are improved, and by setting the diameter of the base layer to 10.0 mm or less, the reproducibility of human blood vessels is improved and poor electrical conduction by the energy device can be suppressed. The inner diameter of the base layer is preferably 0.3 to 9.8 mm, more preferably 0.3 to 3.6 mm, and even more preferably 0.4 to 2.0 mm.

[0018] In one embodiment, when the simulated blood vessel includes a base layer and a conductive layer, the thickness of the base layer is 0.05 to 2.0 mm. The thickness of the base layer is preferably 0.05 to 1.0 mm, more preferably 0.1 to 0.7 mm, and even more preferably 0.2 to 0.5 mm. If the thickness of the base layer is 2.0 mm or less, heat is transferred in a short time when the simulated blood vessel is grasped by an energy device, and bleeding can be stopped.

[0019] In one embodiment, when the simulated blood vessel includes a base layer and a conductive layer, the thickness of the conductive layer is 20 nm or more. The thickness of the conductive layer is preferably 20 nm to 2,000 nm, more preferably 50 to 1,000 nm, and even more preferably 150 to 500 nm. By making the thickness of the conductive layer 20 nm or more, sufficiently high conductivity can be exhibited and the smoothness of the surface of the base layer is improved. Therefore, when the simulated organ is used for medical procedure training using an energy device, hemostasis is facilitated when electricity is applied by the energy device.

[0020] For example, when the simulated blood vessel is composed of a base layer and a conductive layer, the thickness of the simulated blood vessel tube is the sum of the thickness of the base layer and the thickness of the conductive layer.

[0021] (Composition of simulated blood vessel) (1) Base layer When the simulated blood vessel includes a base layer and a conductive layer, the base layer preferably includes a thermoplastic resin. The base layer may be molded using only a thermoplastic resin, or may have a single-layer structure molded using a thermoplastic resin composition comprising one type of thermoplastic resin or an alloy of two or more types of thermoplastic resins, or may have a multilayer structure molded using two or more types of thermoplastic resin compositions. When the base layer includes a thermoplastic resin, the simulated blood vessel includes a thermoplastic resin. When a simulated organ is used for medical procedure training using an energy device, the simulated blood vessel includes a thermoplastic resin, which makes it easier to reproduce the behavior of human blood vessels due to heat when electricity is applied by the energy device, and makes it easier to stop bleeding.

[0022] In one embodiment, the substrate layer may include a thermoplastic resin, a thermoplastic resin composition, be formed using only a thermoplastic resin, or be formed using only a thermoplastic resin composition.

[0023] (1-1) Thermoplastic Resin Here, the thermoplastic resin composition mainly contains a thermoplastic resin. Here, "mainly contains" means that the thermoplastic resin composition contains 50% by mass or more of the thermoplastic resin. In another embodiment, the thermoplastic resin composition may contain 70% by mass or more, or 90% by mass or more, or may consist solely of the thermoplastic resin.

[0024] The thermoplastic resin may have a tensile modulus of 0.01 to 50 MPa. In one embodiment, the tensile modulus of the thermoplastic resin may be 0.05 to 30 MPa, or 0.1 to 15 MPa. By setting the tensile modulus to 50 MPa or less, it becomes easier to crush the simulated blood vessel when grasped by the energy device, thereby stopping the bleeding of the simulated blood flowing through the simulated blood vessel. The tensile modulus is calculated from the slope of the initial straight line in the stress-strain curve according to JIS K7127, a tensile test method for plastics, in which a 1.0 mm thick sheet is punched into the shape of a Type 5 test piece, and measured at an environment of 23±1°C using a tensile tester (Shimadzu Corporation, Autograph AG-Xplus) at a tensile speed of 50.0 mm / min.

[0025] The type of thermoplastic resin used in this embodiment is not limited and may be selected from the group consisting of, for example, ethylene-vinyl acetate resins, urethane resins, vinyl chloride resins, and thermoplastic elastomers. In one embodiment, the thermoplastic resin is preferably an ethylene-vinyl acetate resin and / or a thermoplastic elastomer. Using these thermoplastic resins as the material for the base layer tends to improve the flexibility of the simulated blood vessel and / or lower its softening point. These properties make it easier for the simulated blood vessel to reproduce the behavior of blood vessels in a living body. For example, the higher the flexibility of the simulated blood vessel, the easier it is for the lumen of the simulated blood vessel to collapse, similar to that of a human blood vessel when clamped at the tip of an energy device during medical procedure training, making it easier to stop bleeding. Furthermore, the lower the softening point, the easier it is to stop bleeding at low temperatures, similar to that of a human blood vessel. Therefore, when the simulated blood vessel has high flexibility and / or a low softening point, it becomes easier to stop bleeding with fewer electrical current applications.

[0026] In this embodiment, the ethylene-vinyl acetate resin refers to a resin containing an ethylene-vinyl acetate copolymer. It is acceptable for the resin to contain multiple types of ethylene-vinyl acetate copolymers. The ethylene-vinyl acetate copolymer is a copolymer of ethylene and vinyl acetate, but may also contain chlorinated ethylene, vinyl chloride, vinylidene fluoride, or the like. The vinyl acetate content of the ethylene-vinyl acetate resin is preferably 10 to 35% by mass, more preferably 15 to 35% by mass, and even more preferably 20 to 35% by mass. By setting the vinyl acetate content to 10% by mass or more, the flexibility of the simulated blood vessel is improved. Furthermore, by setting the vinyl acetate content to 35% by mass or less, the heat resistance of the resin composition is improved. By setting the vinyl acetate content to 20% by mass or more, the flexibility of the simulated blood vessel is likely to be increased and / or the softening temperature is likely to be lowered.

[0027] For urethane resins, the raw materials are isocyanate and polyol, and the isocyanate is MDI-based, H １２ MDI system, HDI system, TDI system, IPDI system, NDI system, XDI system, H ６Any combination of XDI-based, NBDI-based, and polyols such as polyether-based, polyester-based, and polycarbonate-based may be selected, or a combination of two or more thereof may be used. As these urethane-based resins, thermoplastic polyurethanes are preferably used, and can be selected from those generally available on the market.

[0028] The vinyl chloride resin may be a vinyl chloride homopolymer or a copolymer of vinyl chloride and another comonomer. When polyvinyl chloride is a copolymer, it may be a random copolymer or a graft copolymer. Examples of graft copolymers include those in which vinyl chloride is graft-polymerized onto an ethylene-vinyl acetate copolymer or a thermoplastic urethane polymer as a backbone polymer. The polyvinyl chloride of this embodiment is an extrusion-moldable flexible polyvinyl chloride composition containing additives such as a polymeric plasticizer. Known polymeric plasticizers can be used as the polymeric plasticizer, but preferred examples include ethylene copolymer polymeric plasticizers such as ethylene-vinyl acetate-carbon monoxide copolymer, ethylene-(meth)acrylate-carbon monoxide copolymer, and ethylene-vinyl acetate copolymer with a high vinyl acetate content.

[0029] Thermoplastic elastomers include those having a structure combining a soft polymeric substance and a hard polymeric substance. Specific examples include styrene-based elastomers, hydrogenated styrene-based thermoplastic elastomers, olefin-based elastomers, vinyl chloride-based elastomers, polyamide-based elastomers, polybutadiene-based thermoplastic elastomers, and polyester-based thermoplastic elastomers. These elastomers can be selected from commercially available products. In one embodiment, the thermoplastic elastomer is preferably a styrene-based elastomer, an olefin-based elastomer, and / or a polyester-based thermoplastic elastomer. Using a styrene-based elastomer, an olefin-based elastomer, and / or a polyester-based thermoplastic elastomer as the material for the base layer tends to improve the flexibility of the simulated blood vessel and / or lower the softening point. These properties enable the simulated blood vessel to more easily reproduce the behavior of blood vessels in a living body. For example, the greater the flexibility of the simulated blood vessel, the more easily the lumen of the simulated blood vessel collapses, similar to a human blood vessel when clamped at the tip of an energy device during medical procedure training, making it easier to stop bleeding. Furthermore, the lower the softening point, the easier it is to stop bleeding at low temperatures, similar to human blood vessels. Therefore, when the simulated blood vessel has high flexibility and / or a low softening point, bleeding can be stopped with fewer electrical current applications. The preferred range of the softening point of the simulated blood vessel is as described below in "Properties of the simulated blood vessel."

[0030] (2) Conductive Layer When the simulated blood vessel includes a base layer and a conductive layer, the conductive layer is a layer disposed on at least a portion of the outer surface of the base layer and contains a conductive material. In one embodiment of the present disclosure, the conductive material of the conductive layer is not particularly limited, but may be one or more types of conductive polymers, metal materials such as silver, copper, tin oxide, and zinc oxide, or carbon materials such as carbon black, carbon nanotubes, graphite, and diamond-like carbon. In one embodiment, the conductive material may be a conductive polymer or a carbon nanotube.

[0031] In this embodiment, "disposed on at least a portion" means that the conductive layer is disposed so as to have at least an area necessary for use in thermal coagulation using an energy device. In one embodiment, the conductive layer has an area of ​​less than 5%, 5% or more, 10% or more, 30% or more, 50% or more, 70% or more, or 90% or more of the outer surface of the base material layer, and may even be 100%.

[0032] (2-1) Conductive Polymer In one embodiment, the conductive polymer is a π-conjugated conductive polymer. The π-conjugated conductive polymer is not particularly limited as long as it is an organic polymer whose main chain is composed of a π-conjugated system and is effective. Examples include polythiophene-based conductive polymers, polypyrrole-based conductive polymers, polyacetylene-based conductive polymers, polyphenylene-based conductive polymers, polyphenylene vinylene-based conductive polymers, polyaniline-based conductive polymers, polyacene-based conductive polymers, polythiophene vinylene-based conductive polymers, and copolymers thereof. From the viewpoint of stability in air, polypyrrole-based conductive polymers, polythiophene-based conductive polymers, and polyaniline-based conductive polymers are preferred, and from the viewpoint of transparency, polythiophene-based conductive polymers are more preferred.

[0033] Examples of polythiophene-based conductive polymers include polythiophene, poly(3-methylthiophene), poly(3-ethylthiophene), poly(3-propylthiophene), poly(3-butylthiophene), poly(3-hexylthiophene), poly(3-heptylthiophene), poly(3-octylthiophene), poly(3-decylthiophene), poly(3-dodecylthiophene), poly(3-octadecylthiophene), poly(3-bromothiophene), poly(3-chlorothiophene), and poly(3-iodothiophene). thiophene), poly(3-cyanothiophene), poly(3-phenylthiophene), poly(3,4-dimethylthiophene), poly(3,4-dibutylthiophene), poly(3-hydroxythiophene), poly(3-methoxythiophene), poly(3-ethoxythiophene), poly(3-butoxythiophene), poly(3-hexyloxythiophene), poly(3-heptyloxythiophene), poly(3-octyloxythiophene), poly(3-decyloxythiophene), poly(3-dodecyl oxythiophene), poly(3-octadecyloxythiophene), poly(3,4-dihydroxythiophene), poly(3,4-dimethoxythiophene), poly(3,4-diethoxythiophene), poly(3,4-dipropoxythiophene), poly(3,4-dibutoxythiophene), poly(3,4-dihexyloxythiophene), poly(3,4-diheptyloxythiophene), poly(3,4-dioctyloxythiophene), poly(3,4-didecyloxythiophene), poly(3,4-di dodecyloxythiophene), poly(3,4-ethylenedioxythiophene), poly(3,4-propylenedioxythiophene), poly(3,4-butylenedioxythiophene), poly(3-methyl-4-methoxythiophene), poly(3-methyl-4-ethoxythiophene), poly(3-carboxythiophene), poly(3-methyl-4-carboxythiophene), poly(3-methyl-4-carboxyethylthiophene), and poly(3-methyl-4-carboxybutylthiophene).Examples of polypyrrole-based conductive polymers include polypyrrole, poly(N-methylpyrrole), poly(3-methylpyrrole), poly(3-ethylpyrrole), poly(3-n-propylpyrrole), poly(3-butylpyrrole), poly(3-octylpyrrole), poly(3-decylpyrrole), poly(3-dodecylpyrrole), poly(3,4-dimethylpyrrole), poly(3,4-dibutylpyrrole), poly(3-carboxypyrrole), poly(3-methyl-4-carboxypyrrole), poly(3-methyl-4-carboxyethylpyrrole), poly(3-methyl-4-carboxybutylpyrrole), poly(3-hydroxypyrrole), poly(3-methoxypyrrole), poly(3-ethoxypyrrole), poly(3-butoxypyrrole), poly(3-hexyloxypyrrole), and poly(3-methyl-4-hexyloxypyrrole). Examples of polyaniline-based conductive polymers include polyaniline, poly(2-methylaniline), poly(3-isobutylaniline), poly(2-anilinesulfonic acid), and poly(3-anilinesulfonic acid). Among the above-mentioned π-conjugated conductive polymers, poly(3,4-ethylenedioxythiophene) is particularly preferred in terms of conductivity, transparency, and heat resistance. The above-mentioned π-conjugated conductive polymers may be used alone or in combination of two or more types.

[0034] In another embodiment, the conductive polymer further contains a polyanion. A polyanion is a polymer having two or more monomer units having an anionic group in the molecule. The anionic group of this polyanion functions as a dopant for the π-conjugated conductive polymer, improving the conductivity of the π-conjugated conductive polymer. The anionic group of the polyanion is preferably a sulfo group or a carboxy group. Specific examples of such polyanions include polymers having sulfonic acid groups such as polystyrene sulfonic acid, polyvinyl sulfonic acid, polyallyl sulfonic acid, polyacrylic sulfonic acid, polymethacrylic sulfonic acid, poly(2-acrylamido-2-methylpropanesulfonic acid), polyisoprene sulfonic acid, polysulfoethyl methacrylate, poly(4-sulfobutyl methacrylate), and polymethacryloxybenzenesulfonic acid, and polymers having carboxylic acid groups such as polyvinyl carboxylic acid, polystyrene carboxylic acid, polyallyl carboxylic acid, polyacrylic carboxylic acid, polymethacrylic carboxylic acid, poly(2-acrylamido-2-methylpropanecarboxylic acid), polyisoprene carboxylic acid, and polyacrylic acid. These may be homopolymers or copolymers of two or more types. Among these polyanions, polymers having sulfonic acid groups are preferred, and polystyrene sulfonic acid is more preferred, as they can further enhance antistatic properties. The polyanions may be used alone or in combination of two or more types. The weight-average molecular weight of the polyanion is preferably 20,000 or more and 1,000,000 or less, more preferably 100,000 or more and 500,000 or less. The weight-average molecular weight in this specification is a value measured by gel permeation chromatography using polystyrene as the standard substance.

[0035] In a conductive composite containing a π-conjugated conductive polymer and a polyanion, the content of the polyanion is preferably in the range of 1 part by mass to 1,000 parts by mass, more preferably 10 parts by mass to 700 parts by mass, and even more preferably 100 parts by mass to 500 parts by mass, per 100 parts by mass of the π-conjugated conductive polymer. If the content of the polyanion is less than the lower limit, the doping effect on the π-conjugated conductive polymer tends to be weak, resulting in insufficient conductivity and reduced dispersibility of the conductive composite in the dispersion. On the other hand, if the content of the polyanion exceeds the upper limit, the content of the π-conjugated conductive polymer decreases, making it difficult to obtain sufficient conductivity.

[0036] The conductive composite is formed by doping a polyanion by coordinating with a π-conjugated conductive polymer. However, in the polyanion of this embodiment, not all anionic groups are doped into the π-conjugated conductive polymer, and there are excess anionic groups that do not contribute to doping. (2-2) Carbon Nanotubes The carbon nanotubes may be single-walled carbon nanotubes (SWCNTs) or multi-walled carbon nanotubes (MWCNTs), but single-walled carbon nanotubes are preferred. Single-walled carbon nanotubes are suitable because they have high conductivity and / or transparency at low concentrations.

[0037] (2-3) Dispersion Medium In one embodiment, the conductive material can be dispersed in a dispersion liquid using, for example, water, an organic solvent, or a mixture of water and an organic solvent. Examples of organic solvents include ester-based solvents, ether-based solvents, hydrocarbon-based solvents, nitrogen-containing solvents, alcohol-based solvents, ketone-based solvents, and dimethyl sulfoxide. Examples of ester-based solvents include ethyl acetate, propyl acetate, and butyl acetate. Examples of ether-based solvents include diethyl ether, dimethyl ether, ethylene glycol, propylene glycol, propylene glycol dialkyl ether, and diethylene glycol diethyl ether. Examples of hydrocarbon-based solvents include hexane, cyclohexane, pentane, octane, decane, dodecane, benzene, toluene, xylene, ethylbenzene, propylbenzene, and isopropylbenzene. Examples of nitrogen-containing solvents include N-methylpyrrolidone, dimethylacetamide, and dimethylformamide. Examples of alcohol-based solvents include methanol, ethanol, 1-propanol, 2-propanol, 2-methyl-2-propanol, 1-butanol, 2-butanol, 2-methyl-1-propanol, allyl alcohol, propylene glycol monomethyl ether, ethylene glycol monomethyl ether, and glycerin. Examples of ketone-based solvents include diethyl ketone, methyl propyl ketone, methyl butyl ketone, methyl isopropyl ketone, methyl isobutyl ketone, methyl amyl ketone, diisopropyl ketone, methyl ethyl ketone, acetone, and diacetone alcohol. One type of organic solvent may be used alone, or two or more types may be used in combination. Among the dispersion media, at least one solvent selected from the group consisting of water, hydrocarbon solvents, ether solvents, nitrogen-containing solvents, and alcohol-based solvents is preferred. Furthermore, among the above dispersion media, at least one selected from the group consisting of water, ethyl acetate, toluene, N-methylpyrrolidone, glycerin, dimethyl sulfoxide, ethylene glycol, and diethylene glycol diethyl ether is more preferred.

[0038] The content of the conductive material in the dispersion of this embodiment is preferably 0.05% by mass or more and 80% by mass or less, more preferably 0.1% by mass or more and 50% by mass or less, and even more preferably 0.2% by mass or more and 30% by mass or less, relative to the total mass of the dispersion. When the content of the conductive polymer in the dispersion is equal to or greater than the lower limit, a thick conductive layer can be easily formed by a single coating. When the content of the conductive polymer in the dispersion is equal to or less than the upper limit, the dispersibility of the conductive material in the dispersion can be increased.

[0039] (2-4) Transparent Binder Component The dispersion in one embodiment contains a transparent binder component together with the conductive material. The transparent binder component is a transparent compound such as a thermoplastic resin, a thermosetting compound, or a photocurable compound. The thermoplastic resin becomes the binder resin described below as it is. The thermosetting compound and the photocurable compound are each a monomer or oligomer, and the thermosetting compound becomes the binder resin described below when thermally cured, and the photocurable compound becomes the binder resin described below when photocured. A dispersion containing a transparent binder component together with a conductive material can easily form a conductive layer that has transparency, conductivity, and anti-reflection properties.

[0040] Examples of transparent binder components include olefin resins, ethylene-vinyl acetate resins, acrylic resins, polystyrene, styrene-acrylic copolymers, polycarbonates, polyethylene terephthalate, polybutylene terephthalate, polyethylene naphthalate, polyvinyl alcohol, cyclic polyolefins, polyester resins, polyurethane resins, polyimide resins, melamine resins, acrylic compounds having one or more acryloyl groups, and epoxy compounds having two or more epoxy groups. Among the transparent binder components, examples of thermoplastic resins include olefin resins, ethylene-vinyl acetate resins, acrylic resins, polystyrene, styrene-acrylic copolymers, polycarbonates, polyethylene terephthalate, polybutylene terephthalate, polyethylene naphthalate, polyvinyl alcohol, and cyclic polyolefins. Examples of thermosetting compounds among the transparent binder components include acrylic compounds and epoxy compounds. Examples of photocurable compounds include acrylic compounds. Among the transparent binder components, thermoplastic resins that are highly transparent and easy to process are preferred. The transparent binder components may be used alone or in combination. When the transparent binder component is a thermosetting compound, it is preferable to add a thermal polymerization initiator to the conductive particle dispersion liquid, and when the transparent binder component is a photocurable compound, it is preferable to add a photopolymerization initiator to the dispersion liquid.

[0041] The content of the transparent binder component in the dispersion of this embodiment is preferably 0.1% by mass or more and 20% by mass or less, more preferably 1% by mass or more and 15% by mass or less, and even more preferably 2% by mass or more and 10% by mass or less, relative to 100% by mass of the dispersion. When the content of the transparent binder component in the conductive particle dispersion of this embodiment is equal to or greater than the lower limit, the strength of the conductive layer can be improved. When the content of the transparent binder component in the conductive particle dispersion of this embodiment is equal to or less than the upper limit, a decrease in conductivity due to a decrease in the content of the conductive complex can be prevented.

[0042] (Properties of simulated blood vessel) In one embodiment, the surface resistance of the conductive portion of the simulated blood vessel (the portion where the conductive layer is disposed) is 1.0×10 １ Ω ~ 1.0 x 10 ６ The surface resistance is preferably 5.0×10 １ Ω ~ 1.0 x 10 ３ Ω, more preferably 6.0×10 １ Ω ~ 1.0 x 10 ３ The surface resistance of the conductive portion of the simulated blood vessel is 1.0 × 10 １ Ω ~ 1.0 x 10 ６ The simulated ulcer with a resistance of Ω can be prepared by adjusting the arrangement and / or thickness of the conductive layer in the simulated blood vessel as described above, measuring the surface resistance, and confirming whether it falls within the above range. For example, preferably 1.0 × 10 １ Ω ~ 1.0 x 10 ６ Ω, more preferably 5.0×10 １ Ω ~ 1.0 x 10 ３ Ω, more preferably 6.0×10 １ Ω ~ 1.0 x 10 ３ The surface resistance can be prepared using a thermoplastic resin having a resistance of 1.0×10 Ω. In this embodiment, the surface resistance is a value measured using a resistivity meter (for example, Loresta-GP (MCP-T610) manufactured by Nitto Seiko Analytech Co., Ltd.) under conditions of 23±1°C, relative humidity of 50% RH, and an applied voltage of 10 V with an ASP probe. In particular, when the surface resistance of the conductive portion of the simulated blood vessel is 1.0×10 ２ If the voltage is higher, when the simulated organ is used for medical procedure training using an energy device, it becomes easier to reproduce the behavior of human blood vessels when electricity is applied by the energy device, making it easier to stop bleeding.

[0043] The softening point of the simulated blood vessel is preferably 200°C or lower, more preferably 100°C or lower, more preferably 30°C to 70°C, and even more preferably 30°C to 60°C. When the simulated blood vessel has a softening point of 200°C or lower, the simulated blood vessel can more easily reproduce the behavior of human blood vessels by thermal coagulation using an energy device, i.e., the material is more easily deformed. When the simulated blood vessel has a softening point of 200°C or lower, bleeding can be easily stopped at low temperatures. Therefore, when the simulated blood vessel has a softening point of 200°C or lower, bleeding can be easily stopped with fewer electrical current applications. A simulated blood vessel having a softening point of 200°C or lower can be prepared by adjusting the type and / or composition of the thermoplastic resin, measuring the softening point, and confirming that it falls within the above range. For example, the simulated blood vessel can be prepared using a thermoplastic resin having a softening point of preferably 200°C or lower, more preferably 100°C or lower, more preferably 30°C to 70°C, and even more preferably 30°C to 60°C. In this embodiment, the softening point of the simulated blood vessel is measured in accordance with JIS K 7206.

[0044] The simulated blood vessel preferably has a melting point of 50 to 200°C. In one embodiment, the melting point of the simulated blood vessel may be 50 to 150°C or 50 to 120°C. Having a melting point of 50 to 200°C makes it possible to suppress shape changes in the simulated blood vessel due to the influence of temperature, and / or to facilitate material deformation of the simulated blood vessel by thermal coagulation using an energy device, similar to that of human blood vessels. A simulated blood vessel having a melting point of 50 to 200°C can be prepared by adjusting the type and / or composition of the thermoplastic resin, measuring the melting point, and confirming that it falls within the above range. For example, the simulated blood vessel can be prepared using a thermoplastic resin having a melting point of preferably 50 to 200°C, more preferably 50 to 150°C, and even more preferably 50 to 120°C. In this embodiment, the melting point of the simulated blood vessel is measured using a differential scanning calorimeter (DSC; manufactured by METTLER TOLEDO, DSC 3+) in a nitrogen atmosphere at a heating rate of 10°C / min.

[0045] In one embodiment, the water contact angle on the surface of the base layer of the simulated blood vessel is 45° or less. In another embodiment, the water contact angle on the surface of the base layer is preferably 30° or less, and more preferably 20° or less. By setting the water contact angle on the surface of the base layer to 45° or less, defects such as cissing and pinholes, and detachment from the base layer of the coating composition forming the conductive layer containing a π-conjugated conductive polymer component are suppressed. In accordance with JIS K 6768, 1 μL of water (pure water) was dropped on the surface of the primer layer using an automatic contact angle measuring device OCA20 manufactured by Eiko Seiki Co., Ltd., and the contact angle measured 30 seconds later was defined as the contact angle in this embodiment. Note that the contact angle can be measured using a specimen prepared by press-molding the thermoplastic resin composition, which is the material for the base layer, at 160 to 200°C into a resin sheet having a thickness of 1.0 mm.

[0046] (Method for manufacturing a simulated blood vessel) The base layer can be manufactured by extrusion molding of a thermoplastic resin or a thermoplastic resin composition. In another embodiment, the base layer can be manufactured by cast molding, injection molding, or compression molding. A simulated blood vessel having a conductive layer disposed on the surface of the base layer is manufactured by immersing the base layer in a dispersion liquid in which a conductive polymer is dispersed in a dispersion medium. In another embodiment, the simulated blood vessel may be manufactured by coating the outer surface of the base layer with a conductive polymer dispersion. Before coating the conductive polymer dispersion, the base layer may be subjected to corona discharge treatment, plasma discharge treatment, flame treatment, or the like to form hydrophilic groups (hydroxyl groups, carbonyl groups, etc.) on the surface of the base layer. If the base layer has been subjected to a hydrophilization treatment, the adhesiveness of the conductive layer can be further improved.

[0047] <Simulated Ulcer> In one embodiment, the simulated ulcer comprises a conductive material, such as a conductive gel.

[0048] In one embodiment, the conductive gel may be a conductive resin composition or other conductive gels, such as those exemplified in "Example 3" below.

[0049] (Configuration of simulated ulcer) As used herein, the term "ulcer" encompasses tissues that include a site (ulcer) in an animal's living body that requires treatment. Non-limiting examples of such tissues include at least a portion of tissues in organs such as the digestive, urinary, reproductive, and respiratory organs. Examples of digestive organs include the oral cavity, pharynx, esophagus, stomach, duodenum, small intestine, large intestine, rectum, and anus. Examples of urinary organs include the ureter, bladder, and urethra. Examples of reproductive organs include the fallopian tube, uterus, vagina, vas deferens, penis, and urethra. Examples of respiratory organs include, but are not limited to, the nasal cavity, trachea, and bronchi. The simulated ulcer is a molded article that simulates tissue and / or organs that include a site (ulcer) that requires treatment.

[0050] The simulated ulcer may be colored to resemble the color of living tissue and organs.

[0051] (Composition of simulated ulcer) When the conductive gel is a conductive resin composition, the type of conductive resin contained in the conductive resin composition is not limited, and for example, a conductive resin selected from the group consisting of hydrogenated styrene-based thermoplastic elastomers and polyvinyl alcohol-based resins can be suitably used. Other conductive gels include, for example, gels containing konjac, agar, gelatin, carrageenan, and / or cellulose derivatives, as described in "Example 3" below. Konjac, agar, gelatin, carrageenan, and / or cellulose derivatives contain an optional chloride to provide conductivity when the simulated organ is used for medical procedure training using an energy device.

[0052] The tensile elongation at break of the conductive gel is preferably 50 to 4000%, more preferably 100 to 4000%, and even more preferably 300 to 4000%. A tensile elongation at break of 50 to 4000% allows for a soft texture similar to that of an actual organ. The tensile elongation at break can be determined by measuring the elongation at break when a conductive gel adjusted to a thickness of 1 mm, a width of 10 mm, and a length of 80 mm is chucked with a 20 mm chuck distance using a tensile tester (model number: AUTOGRAPH AG-X plus) manufactured by Shimadzu Corporation and pulled at a tensile speed of 50 mm / min at 23±2°C. The above measurement method was based on JIS K 7161-1:2014, with the sample size and other factors modified.

[0053] The E hardness of the conductive gel is preferably less than 30, and more preferably 3 to 25. The E hardness can be measured, for example, by stacking sample sheets of conductive gel with a thickness of 5.0 mm and measuring them at 23±1°C in accordance with the JIS K7215 Durometer Hardness Testing Method for Plastics.

[0054] The conductive gel may contain other resins, elastomers, rubbers, plasticizers, fillers, stabilizers, antioxidants, light resistance improvers, UV absorbers, softeners, lubricants, processing aids, colorants, antifogging agents, antiblocking agents, crystal nucleating agents, foaming agents, etc., as needed. To produce the conductive gel, any suitable known blending method can be used. For example, heat mixing can be performed using a heated mixer, or melt mixing can be performed using a single-screw or twin-screw extruder, a Banbury mixer, a plastomill, a co-kneader, or a heated roll. Prior to mixing, the raw materials may be uniformly mixed using a Henschel mixer, ribbon blender, super mixer, tumbler, or the like. The melt mixing temperature is not particularly limited, but is generally 100 to 300°C, preferably 150 to 250°C. Various compositions can be molded using known molding methods such as cast molding, vacuum molding, injection molding, blow molding, and extrusion molding.

[0055] (Example 1 of Conductive Gel (Conductive Resin Composition)) In one embodiment, the conductive resin composition contains 100 parts by mass of component (A) a hydrogenated styrene-based thermoplastic elastomer, and 100 to 1,000 parts by mass of component (B) an oil, and further contains component (C) a copolymer of a hydrophobic polymer and a hydrophilic polymer, and component (D) an ionic liquid, wherein the mass ratio of component (D) to component (C) is 2.7 to 10.

[0056] (Component (A): Hydrogenated Styrenic Thermoplastic Elastomer) In one embodiment, the hydrogenated styrene thermoplastic elastomer is a hydrogenated product of an aromatic vinyl-conjugated diene block copolymer comprising block polymerized units (X) derived from an aromatic vinyl and block polymerized units (Y) derived from a conjugated diene.

[0057] The aromatic vinyl-conjugated diene block copolymer having such a structure has the following structure: X(YX) ｎ or (XY) ｎ [n is an integer of 1 or more]. Among these, X(YX) ｎ Those in the form of X-Y-X are preferred, and those in the form of X-Y-X are particularly preferred. As those in the form of X-Y-X, one or more copolymers selected from the group consisting of polystyrene-polybutadiene-polystyrene block copolymers, polystyrene-polyisoprene-polystyrene block copolymers, and polystyrene-polyisoprene-butadiene-polystyrene block copolymers are preferred.

[0058] In such an aromatic vinyl-conjugated diene block copolymer, the aromatic vinyl block units (X), which are hard segments, exist as crosslinking points for the conjugated diene rubber block units (Y), forming pseudo-crosslinks (domains). The conjugated diene rubber block units (Y), which exist between the aromatic vinyl block units (X), are soft segments and have rubber elasticity.

[0059] Examples of aromatic vinyls forming the block polymerized units (X) include styrene, α-methylstyrene, 3-methylstyrene, p-methylstyrene, 4-propylstyrene, 4-dodecylstyrene, 4-cyclohexylstyrene, 2-ethyl-4-benzylstyrene, 4-(phenylbutyl)styrene, 1-vinylnaphthalene, 2-vinylnaphthalene, etc. Among these, styrene is preferred.

[0060] Examples of conjugated dienes that form the block polymerized units (Y) include butadiene, isoprene, pentadiene, 2,3-dimethylbutadiene, and combinations thereof. Among these, one or more conjugated dienes selected from the group consisting of butadiene, isoprene, and a combination of butadiene and isoprene (butadiene-isoprene copolymerization) are preferred. One or more conjugated dienes among these can also be used in combination. The conjugated diene block polymerized units (Y) consisting of butadiene-isoprene copolymerized units may be any of random copolymerized units, block copolymerized units, and tapered copolymerized units of butadiene and isoprene.

[0061] In the aromatic vinyl-conjugated diene block copolymer, the content of the aromatic vinyl block polymerization unit (X) is preferably 5% by mass or more and 50% by mass or less, and more preferably 20% by mass or more and 40% by mass or less. The content of the aromatic vinyl unit can be measured by a conventional method such as infrared spectroscopy or NMR spectroscopy.

[0062] In one embodiment, the melt flow rate (MFR) of component (A) (temperature 230°C, load 2.16 kg) is 1 g / 10 min or less, preferably 0.1 g / 10 min or less. MFR (temperature 230°C, load 2.16 kg) refers to the MFR measured in accordance with JIS K7210 under conditions of a temperature of 230°C and a load of 2.16 kg. By setting the MFR to 1 g / 10 min or less, bleeding out when oil is added is facilitated and a decrease in mechanical strength can be suppressed. MFR can be measured, for example, in accordance with JIS K7210.

[0063] The aromatic vinyl-conjugated diene block copolymer as described above can be produced by various methods, including (1) a method in which an aromatic vinyl and then a conjugated diene are sequentially polymerized using an alkyllithium compound such as n-butyllithium as an initiator, (2) a method in which an aromatic vinyl and then a conjugated diene are polymerized using an alkyllithium compound as an initiator, and then the polymerized products are coupled with a coupling agent, and (3) a method in which a conjugated diene and then an aromatic vinyl are sequentially polymerized using a lithium compound as an initiator.

[0064] The hydrogenated styrene-based thermoplastic elastomer is preferably a product obtained by hydrogenating the above-mentioned aromatic vinyl-conjugated diene block copolymer by a known method, and has a hydrogenation rate of 90 mol% or more. This hydrogenation rate is a value when the total amount of carbon-carbon double bonds in the conjugated diene block polymerized units (Y) is taken as 100 mol%. Examples of such hydrogenated styrene-based thermoplastic elastomers include polystyrene-poly(ethylene / propylene) block (SEP), polystyrene-poly(ethylene / propylene) block-polystyrene (SEPS), polystyrene-poly(ethylene / butylene) block-polystyrene (SEBS), and polystyrene-poly(ethylene-ethylene / propylene) block-polystyrene (SEEPS). More specific examples include SEPTON (manufactured by Kuraray Co., Ltd.), Kraton (manufactured by Shell Chemical Co., Ltd.), Kraton G (manufactured by Shell Chemical Co., Ltd.), and Tuftec (manufactured by Asahi Kasei Corporation) (all trade names).

[0065] The hydrogenation rate is measured by a known method such as nuclear magnetic resonance spectroscopy (NMR).

[0066] As the hydrogenated styrene-based thermoplastic elastomer, SEEPS is preferred. The shape of the hydrogenated styrene-based thermoplastic elastomer is preferably powder or amorphous (crumb) from the viewpoint of oil absorption before kneading.

[0067] (Component (B): Oil) The oil is not particularly limited, but examples thereof include paraffinic process oil, naphthenic process oil, aromatic process oil, mineral oil such as liquid paraffin, silicone oil, castor oil, linseed oil, olefin wax, mineral wax, etc. Among these, paraffinic and / or naphthenic process oil are preferred. Examples of process oils include the Diana Process Oil Series (manufactured by Idemitsu Kosan Co., Ltd.) and JOMO Process P (manufactured by Japan Energy Corporation). The oil is used, for example, to soften the resin composition and adjust the elastic modulus and hardness of the simulated organ. One or more of the above oils can also be used in combination. From the viewpoint of workability, it is preferable that the oil be absorbed into a hydrogenated styrene-based thermoplastic elastomer in advance.

[0068] The oil content is preferably 100 to 1,000 parts by mass, more preferably 100 to 700 parts by mass, even more preferably 100 to 600 parts by mass, and most preferably 200 to 500 parts by mass, per 100 parts by mass of component (A). The oil content is adjusted within the above range depending on the actual site and lesion of the organ being modeled. By setting the oil content to 100 parts by mass or more per 100 parts by mass of component (A), insufficient softness can be prevented, and by setting the oil content to 1,000 parts by mass or less, it is possible to prevent the hydrogenated styrene-based thermoplastic elastomer from being unable to occlude the oil, resulting in inability to compound.

[0069] (Component (C): Polymeric Antistatic Agent) In one embodiment, the polymeric antistatic agent is not particularly limited, but is preferably a copolymer of a hydrophobic polymer and a hydrophilic polymer, more preferably a copolymer having one or more hydrophobic polymer blocks and one or more hydrophilic polymer blocks. "Hydrophilic" means having a functional group that forms hydrogen bonds between molecules or polarity, and "hydrophobic" means being non-hydrophilic. Here, the bonding mode of each block may be a block copolymer in which a hydrophobic polymer block and a hydrophilic polymer block are linearly connected, or a graft copolymer in which a graft chain is connected as a branch chain to one of the polymer chains, but a block copolymer is more preferred.

[0070] More specifically, examples of such polyethers include those having hydrophilic groups and being block copolymerized (non-ionic types such as polyetheresteramides, ethylene oxide-epichlorohydrins, and polyetheresters, anionic types such as polystyrenesulfonic acids, and cationic types such as quaternary ammonium-containing poly(meth)acrylates). Among these, diblock copolymers having a structure in which a polyethylene glycol block and a polypropylene glycol block, or a polyether block and a polyolefin block are bonded via at least one bond selected from an ester bond, an amide bond, an ether bond, a urethane bond, and an imide bond, and block copolymers having a structure in which these blocks are bonded alternately and repeatedly can be used. Examples of such copolymers include those having a volume resistivity of 10 ５ ~10 １１ Examples of suitable block copolymers include those having a structure in which polyether blocks, which are hydrophilic blocks with a resistance of Ω cm, and polyolefin blocks are repeatedly and alternately bonded. The number average molecular weight (Mn) of such block copolymers is preferably 500 to 60,000.

[0071] Commercially available copolymers include, for example, "Pelestat (registered trademark)" (such as "Pelestat 300," "Pelestat 230," "Pelestat NC6321," "Pelestat NC6322," "Pelestat NC7350," and "Pelestat HC250") and "Pelestat (registered trademark)" (such as "Pelestat PVH," "Pelestat PVL," "Pelestat HS," and "Pelestat LMP-FS") manufactured by Sanyo Chemical Industries, Ltd.; "Sankonol (registered trademark)" (such as "Sankonol TBX-65") manufactured by Sanko Chemical Industries, Ltd.; and "Pelestat (registered trademark)" (such as "Pelestat PVH," "Pelestat PVL," "Pelestat HS," and "Pelestat LMP-FS") manufactured by Mitsui DuPont Co., Ltd. Examples of such a polymer include "Entira (registered trademark) AS" manufactured by Arkema, "Pebax (registered trademark)" manufactured by The Lubrizol Corporation, "Stat-Rite (registered trademark)" manufactured by IonPhasE, "IonPhasE (registered trademark) IPE (registered trademark) U2" manufactured by IonPhasE, "Pluronic (registered trademark) L-31" and "Pluronic (registered trademark) L-41" manufactured by Adeka Corporation, and "Alkox (registered trademark) EP1010N" and "Alkox (registered trademark) CP-A1H" manufactured by Meisei Chemical Industry Co., Ltd., and these may be used alone or in combination.

[0072] In addition, a polyolefin block, a polyisobutylene block, and a polymer having a volume resistivity of 1.0×10 ５ ~1.0 x 10 １１ A block polymer in which a block of a hydrophilic polymer having a resistance of Ω cm is bonded to the block of a hydrophilic polymer through at least one bond selected from the group consisting of an ester bond, an amide bond, an ether bond, an imide bond, and a urethane bond can be used as the copolymer of this embodiment.

[0073] In addition, a block polymer having a hydrophobic polymer block without polyether, a hydrophilic polymer block, and an aromatic ring-containing hydrophobic polyether block as a constituent unit, and a polyolefin block and a polymer having a volume resistivity of 10 ５ ~10 １１Alternatively, a block polymer having a structure in which blocks of a hydrophilic polymer having a resistance of Ω cm are repeatedly and alternately bonded, or a block polymer having as constituent units a block of at least one hydrophobic polymer selected from the group consisting of polyamide, polyolefin, and polyamideimide, a block of a hydrophilic polymer, and a block of an aromatic ring-containing hydrophobic polyether, can be used.

[0074] The number average molecular weight (Mn) and weight average molecular weight (Mw) of the copolymer can be measured by gel permeation chromatography (GPC) using polystyrene as a standard substance.

[0075] The content of the polymeric antistatic agent is preferably 5 parts by mass or more but less than 100 parts by mass, more preferably 8 parts by mass or more but less than 80 parts by mass, and even more preferably 10 parts by mass or more but less than 60 parts by mass, relative to 100 parts by mass of component (A). The content of the polymeric antistatic agent contributes to the volume resistivity and the tensile elongation at break.

[0076] (Component (D): Ionic Liquid) The ionic liquid is not particularly limited, but examples thereof include those composed of a cation and an anion. In one embodiment, the ionic liquid does not contain a solvent such as water or ethylene glycol.

[0077] Examples of the cation include an amidinium cation, a pyridinium cation, a pyrazolium cation, and a guanidinium cation.

[0078] Examples of the amidinium cation include an imidazolinium cation, an imidazolium cation, a tetrahydropyrimidinium cation, a dihydropyrimidinium cation, etc. Examples of the imidazolinium cation include a 1,2,3,4-tetramethylimidazolinium cation, a 1,3,4-trimethyl-2-ethylimidazolinium cation, a 1,3-dimethylimidazolinium cation, a 1,3-dimethyl-2,4-diethylimidazolinium cation, a 1,2-dimethyl-3,4-diethylimidazolinium cation, a 1-methyl-2,3,4-triethylimidazolinium cation, a 1,2,3,4 -tetraethylimidazolinium cation, 1,2,3-trimethylimidazolinium cation, 1,3-dimethyl-2-ethylimidazolinium cation, 1-ethyl-2,3-dimethylimidazolinium cation, 1,2,3-triethylimidazolinium cation, 4-cyano-1,2,3-trimethylimidazolinium cation, 3-cyanomethyl-1,2-dimethylimidazolinium cation, 2-cyanomethyl-1, 3-dimethylimidazolinium cation, 4-acetyl-1,2,3-trimethylimidazolinium cation, 3-acetylmethyl-1,2-dimethylimidazolinium cation, 4-methylcarboxymethyl-1,2,3-trimethylimidazolinium cation, 3-methylcarboxymethyl-1,2-dimethylimidazolinium cation, 4-methoxy-1,2,3-trimethylimidazolinium cation, 3-methoxymethyl-1,2-dimethylimidazolinium cation, 4-formyl-1,2,3-trimethylimidazolinium cation, 3-formylmethyl-1,2-dimethylimidazolinium cation, 3-hydroxyethyl-1,2-dimethylimidazolinium cation, 4-hydroxymethyl-1,2,3-trimethylimidazolinium cation and 2-hydroxyethyl-1,3-dimethylimidazolinium cation.

[0079] Examples of imidazolium cations include 1,3-dimethylimidazolium cation, 1,3-diethylimidazolium cation, 1-ethyl-3-methylimidazolium cation, 1,2,3-trimethylimidazolium cation, 1,2,3,4-tetramethylimidazolium cation, 1,3-dimethyl-2-ethylimidazolium cation, 1,2-dimethyl-3-ethyl-imidazolium cation, 1,2,3-triethylimidazolium cation, 1,2,3,4-tetraethylimidazolium cation, 1,3-dimethyl-2-phenylimidazolium cation, 1,3-dimethyl-2-benzylimidazolium cation, 1-benzyl-2,3-dimethyl-imidazolium cation, 4-cyano-1,2,3-trimethylimidazolium cation, 3-cyanomethyl-1,2-dimethylimidazolium cation, 2-cyanomethyl Examples thereof include 2-hydroxyethyl-1,3-dimethylimidazolium cation, 4-acetyl-1,2,3-trimethylimidazolium cation, 3-acetylmethyl-1,2-dimethylimidazolium cation, 4-methylcarboxymethyl-1,2,3-trimethylimidazolium cation, 3-methylcarboxymethyl-1,2-dimethylimidazolium cation, 4-methoxy-1,2,3-trimethylimidazolium cation, 3-methoxymethyl-1,2-dimethylimidazolium cation, 4-formyl-1,2,3-trimethylimidazolium cation, 3-formylmethyl-1,2-dimethylimidazolium cation, 3-hydroxyethyl-1,2-dimethylimidazolium cation, 4-hydroxymethyl-1,2,3-trimethylimidazolium cation, and 2-hydroxyethyl-1,3-dimethylimidazolium cation.

[0080] Examples of tetrahydropyrimidinium cations include 1,3-dimethyl-1,4,5,6-tetrahydropyrimidinium cation, 1,2,3-trimethyl-1,4,5,6-tetrahydropyrimidinium cation, 1,2,3,4-tetramethyl-1,4,5,6-tetrahydropyrimidinium cation, 1,2,3,5-tetramethyl-1,4,5,6-tetrahydropyrimidinium cation, 8-methyl-1,8-diazabicyclo[5,4,0]-7-undecenium cation, 5-methyl-1,5- Diazabicyclo[4,3,0]-5-nonenium cation, 4-cyano-1,2,3-trimethyl-1,4,5,6-tetrahydropyrimidinium cation, 3-cyanomethyl-1,2-dimethyl-1,4,5,6-tetrahydropyrimidinium cation, 2-cyanomethyl-1,3-dimethyl-1,4,5,6-tetrahydropyrimidinium cation, 4-acetyl-1,2,3-trimethyl-1,4,5,6-tetrahydropyrimidinium cation, 3-acetylmethyl-1,2-dimethyl-1,4 ,5,6-tetrahydropyrimidinium cation, 4-methylcarboxymethyl-1,2,3-trimethyl-1,4,5,6-tetrahydropyrimidinium cation, 3-methylcarboxymethyl-1,2-dimethyl-1,4,5,6-tetrahydropyrimidinium cation, 4-methoxy-1,2,3-trimethyl-1,4,5,6-tetrahydropyrimidinium cation, 3-methoxymethyl-1,2-dimethyl-1,4,5,6-tetrahydropyrimidinium cation, 4-formyl-1,2,3 3-hydroxyethyl-1,2-dimethyl-1,4,5,6-tetrahydropyrimidinium cation, 4-hydroxymethyl-1,2,3-trimethyl-1,4,5,6-tetrahydropyrimidinium cation, and 2-hydroxyethyl-1,3-dimethyl-1,4,5,6-tetrahydropyrimidinium cation.

[0081] Examples of dihydropyrimidinium cations include 1,2,3-trimethyl-1,4-dihydropyrimidinium cation, 1,2,3,4-tetramethyl-1,4-dihydropyrimidinium cation, 1,2,3,5-tetramethyl-1,6-dihydropyrimidinium cation, 8-methyl-1,8-diazabicyclo[5,4,0]-7,9-undecadienium cation, 5-methyl-1,5-diazabicyclo[4,3,0]-5,7 -nonadienium cation, 4-cyano-1,2,3-trimethyl-1,6-dihydropyrimidinium cation, 3-cyanomethyl-1,2-dimethyl-1,4-dihydropyrimidinium cation, 2-cyanomethyl-1,3-dimethyl-1,4-dihydropyrimidinium cation, 4-acetyl-1,2,3-trimethyl-1,6-dihydropyrimidinium cation, 3-acetylmethyl-1,2-dimethyl-1,4-dihydropyrimidinium cation pyrimidinium cation, 4-methylcarboxymethyl-1,2,3-trimethyl-1,4-dihydropyrimidinium cation, 3-methylcarboxymethyl-1,2-dimethyl-1,4-dihydropyrimidinium cation, 4-methoxy-1,2,3-trimethyl-1,6-dihydropyrimidinium cation, 3-methoxymethyl-1,2-dimethyl-1,4-dihydropyrimidinium cation, 4-formyl-1,2,3-trimethyl-1,6-dihydropyrimidinium cation, 3-formylmethyl-1,2-dimethyl-1,6-dihydropyrimidinium cation, 3-hydroxyethyl-1,2-dimethyl-1,6-dihydropyrimidinium cation, 4-hydroxymethyl-1,2,3-trimethyl-1,4-dihydropyrimidinium cation and 2-hydroxyethyl-1,3-dimethyl-1,4-hydropyrimidinium cation.

[0082] Examples of the pyridinium cation include a 3-methyl-1-propylpyridinium cation, a 1-propyl-3-methylpyridinium cation, a 1-butyl-3-methylpyridinium cation, a 1-butyl-4-methylpyridinium cation, a 1-butyl-3,4-dimethylpyridinium cation, and a 1-butyl-3,5-dimethylpyridinium cation.

[0083] Examples of the pyrazolium cation include a 1,2-dimethylpyrazolium cation, a 1-methyl-2-propylpyrazolium cation, a 1-n-butyl-2-methylpyrazolium cation, and a 1-n-butyl-2-ethylpyrazolium cation.

[0084] Examples of the guanidinium cation include a guanidinium cation having an imidazolinium skeleton, a guanidinium cation having an imidazolium skeleton, a guanidinium cation having a tetrahydropyrimidinium skeleton, and a guanidinium cation having a dihydropyrimidinium skeleton.

[0085] Examples of guanidinium cations having an imidazolinium skeleton include 2-dimethylamino-1,3,4-trimethylimidazolinium cation, 2-diethylamino-1,3,4-trimethylimidazolinium cation, 2-diethylamino-1,3-dimethyl-4-ethylimidazolinium cation, 2-dimethylamino-1-methyl-3,4-diethylimidazolinium cation, 2-diethylamino-1-methyl-3,4-diethylimidazolinium cation, 2-diethylamino-1,3 ,4-tetraethylimidazolinium cation, 2-dimethylamino-1,3-dimethylimidazolinium cation, 2-diethylamino-1,3-dimethylimidazolinium cation, 2-dimethylamino-1-ethyl-3-methylimidazolinium cation, 2-diethylamino-1,3-diethylimidazolinium cation, 1,5,6,7-tetrahydro-1,2-dimethyl-2H-imido[1,2a]imidazolinium cation, 1,5-dihydro-1,2-dimethyl-2H-imido [1,2a]imidazolinium cation, 1,5,6,7-tetrahydro-1,2-dimethyl-2H-pyrimido[1,2a]imidazolinium cation, 1,5-dihydro-1,2-dimethyl-2H-pyrimido[1,2a]imidazolinium cation, 2-dimethylamino-4-cyano-1,3-dimethylimidazolinium cation, 2-dimethylamino-3-cyanomethyl-1-methylimidazolinium cation, 2-dimethylamino-4-acetyl-1,3-dimethylimidazolinium cation on, 2-dimethylamino-3-acetylmethyl-1-methylimidazolinium cation, 2-dimethylamino-4-methylcarboxymethyl-1,3-dimethylimidazolinium cation, 2-dimethylamino-3-methylcarboxymethyl-1-methylimidazolinium cation, 2-dimethylamino-4-methoxy-1,3-dimethylimidazolinium cation, 2-dimethylamino-3-methoxymethyl-1-methylimidazolinium cation, 2-dimethylamino-4-formyl-1,Examples include 3-dimethylimidazolinium cation, 2-dimethylamino-3-formylmethyl-1-methylimidazolinium cation, 2-dimethylamino-3-hydroxyethyl-1-methylimidazolinium cation, and 2-dimethylamino-4-hydroxymethyl-1,3-dimethylimidazolinium cation.

[0086] Examples of guanidinium cations having an imidazolium skeleton include 2-dimethylamino-1,3,4-trimethylimidazolium cation, 2-diethylamino-1,3,4-trimethylimidazolium cation, 2-diethylamino-1,3-dimethyl-4-ethylimidazolium cation, 2-dimethylamino-1-methyl-3,4-diethylimidazolium cation, 2-diethylamino-1-methyl-3,4-diethylimidazolium cation, 2-diethylamino-1,3,4-tetraethylimidazolium cation, 2-dimethylamino -1,3-dimethylimidazolium cation, 2-diethylamino-1,3-dimethylimidazolium cation, 2-dimethylamino-1-ethyl-3-methylimidazolium cation, 2-diethylamino-1,3-diethylimidazolium cation, 1,5,6,7-tetrahydro-1,2-dimethyl-2H-imido[1,2a]imidazolium cation, 1,5-dihydro-1,2-dimethyl-2H-imido[1,2a]imidazolium cation, 1,5,6,7-tetrahydro-1,2-dimethyl-2H-pyrimido[1,2a]imidazolium ium cation, 1,5-dihydro-1,2-dimethyl-2H-pyrimido[1,2a]imidazolium cation, 2-dimethylamino-4-cyano-1,3-dimethylimidazolium cation, 2-dimethylamino-3-cyanomethyl-1-methylimidazolium cation, 2-dimethylamino-4-acetyl-1,3-dimethylimidazolinium cation, 2-dimethylamino-3-acetylmethyl-1-methylimidazolium cation, 2-dimethylamino-4-methylcarboxymethyl-1,3-dimethylimidazolium cation, 2-dimethylamino-4-methylcarboxymethyl-1,3-dimethylimidazolium cation, dimethylamino-3-methylcarboxymethyl-1-methylimidazolium cation, 2-dimethylamino-4-methoxy-1,3-dimethylimidazolium cation, 2-dimethylamino-3-methoxymethyl-1-methylimidazolium cation, 2-dimethylamino-4-formyl-1,3-dimethylimidazolium cation, 2-dimethylamino-3-formylmethyl-1-methylimidazolium cation, 2-dimethylamino-3-hydroxyethyl-1-methylimidazolium cation and 2-dimethylamino-4-hydroxymethyl-1,3-dimethylimidazolium cation, etc.

[0087] Examples of guanidinium cations having a tetrahydropyrimidinium skeleton include 2-dimethylamino-1,3,4-trimethyl-1,4,5,6-tetrahydropyrimidinium cation, 2-diethylamino-1,3,4-trimethyl-1,4,5,6-tetrahydropyrimidinium cation, 2-diethylamino-1,3-dimethyl-4-ethyl-1,4,5,6-tetrahydropyrimidinium cation, 2-dimethylamino-1-methyl-3,4-diethyl-1,4,5,6-tetrahydropyrimidinium cation, 2-diethyl Amino-1-methyl-3,4-diethyl-1,4,5,6-tetrahydropyrimidinium cation, 2-diethylamino-1,3,4-tetraethyl-1,4,5,6-tetrahydropyrimidinium cation, 2-dimethylamino-1,3-dimethyl-1,4,5,6-tetrahydropyrimidinium cation, 2-diethylamino-1,3-dimethyl-1,4,5,6-tetrahydropyrimidinium cation, 2-dimethylamino-1-ethyl-3-methyl-1,4,5,6-tetrahydropyrimidinium cation, 2-diethylamino 1,3-diethyl-1,4,5,6-tetrahydropyrimidinium cation, 1,3,4,6,7,8-hexahydro-1,2-dimethyl-2H-imido[1,2a]pyrimidinium cation, 1,3,4,6-tetrahydro-1,2-dimethyl-2H-imido[1,2a]pyrimidinium cation, 1,3,4,6,7,8-hexahydro-1,2-dimethyl-2H-pyrimido[1,2a]pyrimidinium, 1,3,4,6-tetrahydro-1,2-dimethyl-2H-pyrimido[1,2a]pyrimidinium cation, 2-dimethyl 2-dimethylamino-4-cyano-1,3-dimethyl-1,4,5,6-tetrahydropyrimidinium cation, 2-dimethylamino-3-cyanomethyl-1-methyl-1,4,5,6-tetrahydropyrimidinium cation, 2-dimethylamino-4-acetyl-1,3-dimethyl-1,4,5,6-tetrahydropyrimidinium cation, 2-dimethylamino-3-acetylmethyl-1-methyl-1,4,5,6-tetrahydropyrimidinium cation, 2-dimethylamino-4-methylcarboxymethyl-1,3-dimethyl-1,4,5,6-tetrahydropyrimidinium cation, 2-dimethylamino-3-methylcarboxymethyl-1-methyl-1,4,5,6-tetrahydropyrimidinium cation, 2-dimethylamino-4-methoxy-1,3-dimethyl-1,4,5,6-tetrahydropyrimidinium cation, 2-dimethylamino-3-methoxymethyl-1-methyl-1,4,5,6-tetrahydropyrimidinium cation, 2-dimethylamino-4-formyl-1,3-dimethyl-1,4,5,6-tetrahydropyrimidinium cation, 2-dimethylamino-3-formylmethyl-1-methyl-1,4,5,6-tetrahydropyrimidinium cation, 2-dimethylamino-3-hydroxyethyl-1-methyl-1,4,5,6-tetrahydropyrimidinium cation, and 2-dimethylamino-4-hydroxymethyl-1,3-dimethyl-1,4,5,6-tetrahydropyrimidinium cation.

[0088] Examples of guanidinium cations having a dihydropyrimidinium skeleton include 2-dimethylamino-1,3,4-trimethyl-1,4-dihydropyrimidinium cation, 2-diethylamino-1,3,4-trimethyl-1,6-dihydropyrimidinium cation, 2-diethylamino-1,3-dimethyl-4-ethyl-1,6-dihydropyrimidinium cation, 2-dimethylamino-1-methyl-3,4-diethyl-1,4-dihydropyrimidinium cation, and 2-diethylamino-1-methyl-3,4-diethyl-1,4-dihydropyrimidinium cation. Thione, 2-diethylamino-1,3,4-tetraethyl-1,6-dihydropyrimidinium cation, 2-dimethylamino-1,3-dimethyl-1,4-dihydropyrimidinium cation, 2-diethylamino-1,3-dimethyl-1,4-dihydropyrimidinium cation, 2-dimethylamino-1-ethyl-3-methyl-1,4-dihydropyrimidinium cation, 2-diethylamino-1,3-diethyl-1,6-dihydropyrimidinium cation, 1,6,7,8-tetrahydro-1,2-dimethyl-2H-imido[1,2a]pyrimidinium Cations, 1,6-dihydro-1,2-dimethyl-2H-imido[1,2a]pyrimidinium cation, 1,6,7,8-tetrahydro-1,2-dimethyl-2H-pyrimido[1,2a]pyrimidinium cation, 1,6-dihydro-1,2-dimethyl-2H-pyrimido[1,2a]pyrimidinium cation, 2-dimethylamino-4-cyano-1,3-dimethyl-1,4-dihydropyrimidinium cation, 2-dimethylamino-3-cyanomethyl-1-methyl-1,6-dihydropyrimidinium cation, 2-dimethylamino-4-acetyl-1,3 -dimethyl-1,4-dihydropyrimidinium cation, 2-dimethylamino-3-acetylmethyl-1-methyl-1,4-dihydropyrimidinium cation, 2-dimethylamino-4-methylcarboxymethyl-1,3-dimethyl-1,4-dihydropyrimidinium cation, 2-dimethylamino-3-methylcarboxymethyl-1-methyl-1,4-dihydropyrimidinium cation, 2-dimethylamino-4-methoxy-1,3-dimethyl-1,6-dihydropyrimidinium cation, 2-dimethylamino-3-methoxymethyl-1-methyl-1,Examples include 4-dihydropyrimidinium cation, 2-dimethylamino-4-formyl-1,3-dimethyl-1,4,5,6-tetrahydropyrimidinium cation, 2-dimethylamino-3-formylmethyl-1-methyl-1,4,5,6-tetrahydropyrimidinium cation, 2-dimethylamino-3-hydroxyethyl-1-methyl-1,4,5,6-tetrahydropyrimidinium cation, and 2-dimethylamino-4-hydroxymethyl-1,3-dimethyl-1,4-dihydropyrimidinium cation.

[0089] Examples of the anion include anions obtained by removing a proton from the following acids. The anion may be a mixture of two or more kinds.

[0090] Carboxylic acids can be used as the anion, and specific examples thereof include monocarboxylic acids {aliphatic monocarboxylic acids having 1 to 30 carbon atoms [saturated monocarboxylic acids (formic acid, acetic acid, propionic acid, butyric acid, isobutyric acid, valeric acid, caproic acid, enanthic acid, caprylic acid, pelargonic acid, lauric acid, myristic acid, stearic acid, behenic acid, etc.), fluorine atom-containing carboxylic acids (trifluoroacetic acid, etc.), unsaturated monocarboxylic acids (acrylic acid, methacrylic acid, oleic acid, etc.)], and aromatic monocarboxylic acids (benzoic acid, cinnamic acid, naphthoic acid, etc.)}, polycarboxylic acids (divalent to tetravalent polycarboxylic acids) {aliphatic polycarboxylic acids [saturated polycarboxylic acids (oxalic acid, malonic acid, succinic acid, glutaric acid, adipic acid, pimelic acid, suberic acid, benzoic acid, cinnamic acid, naphthoic acid, etc.)], and aromatic monocarboxylic acids (benzoic acid, cinnamic acid, naphthoic acid, etc.)}. unsaturated polycarboxylic acids (maleic acid, fumaric acid, itaconic acid, etc.); aromatic polycarboxylic acids (phthalic acid, isophthalic acid, terephthalic acid, trimellitic acid, pyromellitic acid, etc.); aliphatic oxycarboxylic acids (glycolic acid, lactic acid, tartaric acid, etc.); aromatic oxycarboxylic acids (salicylic acid, mandelic acid, etc.); sulfur atom-containing polycarboxylic acids (thiodipropionic acid, etc.); other polycarboxylic acids (cyclobutene-1,2-dicarboxylic acid, cyclopentene-1,2-dicarboxylic acid, furan-2,3-dicarboxylic acid, bicyclo[2,2,1]hept-2-ene-2,3-dicarboxylic acid, bicyclo[2,2,1]hepta-2,5-diene-2,3-dicarboxylic acid, etc.).

[0091] As the anion, a sulfonic acid can be used, and specific examples thereof include alkanesulfonic acids having 1 to 30 carbon atoms (methanesulfonic acid, ethanesulfonic acid, butanesulfonic acid, octanesulfonic acid, dodecanesulfonic acid, etc.); and alkylbenzenesulfonic acids having 7 to 30 carbon atoms (octylbenzenesulfonic acid, dodecylbenzenesulfonic acid, etc.).

[0092] As the anion, inorganic acids can be used, specifically, hydrofluoric acid, hydrochloric acid, sulfuric acid, phosphoric acid, HClO ４ , H.B.F. ４ , HPF ６ , HAsF ６ , and HSbF ６ etc.

[0093] As the anion, a halogen atom-containing alkyl group-substituted inorganic acid (the alkyl group has 1 to 30 carbon atoms) can be used, specifically, HBF ｎ (CF ３ ) ４－ｎ (n is an integer from 0 to 3), HPF ｎ (CF ３ ) ６－ｎ (n is an integer of 0 to 5), trifluoromethanesulfonic acid, pentafluoroethanesulfonic acid, heptafluoropropanesulfonic acid, trichloromethanesulfonic acid, pentachloropropanesulfonic acid, heptachlorobutanesulfonic acid, tris(pentafluoroethyl)trifluorophosphate, trifluoroacetic acid, pentafluoropropionic acid, pentafluorobutanoic acid, trichloroacetic acid, pentachloropropionic acid, and heptachlorobutanoic acid.

[0094] As the anion, a halogen atom-containing sulfonylimide (having 1 to 30 carbon atoms) can be used, and specific examples thereof include bis(fluoromethylsulfonyl)imide, bis(trifluoromethanesulfonyl)imide, and bis(fluorosulfonyl)imide.

[0095] As the anion, a halogen atom-containing sulfonyl methide (having 3 to 30 carbon atoms) can be used, and specific examples thereof include tris(trifluoromethylsulfonyl)methide.

[0096] As the anion, a halogen atom-containing carboxylic acid amide (having 2 to 30 carbon atoms) can be used, and specific examples thereof include bis(trifluoroacet)amide.

[0097] As the anion, a nitrile group-containing imide can be used, specifically, HN(CN) ２ etc.

[0098] As the anion, a nitrile group-containing methide can be used, specifically, HC(CN) ３ etc.

[0099] As the anion, a halogen atom-containing alkylamine having 1 to 30 carbon atoms can be used, specifically, HN(CF ３ ) ２ etc.

[0100] As the anion, cyanic acid can be used, and specific examples include thiocyanic acid.

[0101] Alternatively, commercially available ionic liquids may be used, such as CIL312 (N-butyl-3-methylpyridinium bistrifluoromethanesulfonylimide, manufactured by Nippon Carlit Co., Ltd.), Aminoion AS100 (manufactured by Nippon Nyukazai Co., Ltd.), Aminoion AS300 (manufactured by Nippon Nyukazai Co., Ltd.), FC-4400 (tri-n-butylmethylammonium bistrifluoromethanesulfonimide, manufactured by 3M Co., Ltd.), and Hishicolin (dodecyltributylphosphonium chloride, manufactured by Nippon Chemical Industry Co., Ltd.).

[0102] The method for synthesizing an ionic liquid is not particularly limited as long as the desired ionic liquid can be obtained. Examples of the method include the halide method, hydroxide method, acid ester method, complex formation method, and neutralization method described in "Ionic Liquids - The Frontline and Future of Development" [Hiroyuki Ohno, published in 2003 by CMC Publishing].

[0103] The content of the ionic liquid is preferably 50 to 250 parts by mass, more preferably 50 to 240 parts by mass, and even more preferably 70 to 210 parts by mass, per 100 parts by mass of component (A). The content of the ionic liquid contributes to the tensile elongation at break, and by setting the content of the ionic liquid to 50 parts by mass or more per 100 parts by mass of component (A), it contributes to suppressing an increase in volume resistivity, and by setting the content to 250 parts by mass or less, it is possible to suppress bleeding of the ionic liquid from the material.

[0104] (Mass Ratio of Component (D) to Component (C)) The mass ratio of component (D) to component (C) in the conductive resin composition is 2.7 to 10. In one embodiment, it is preferably 3.0 to 9.5, more preferably 3.0 to 9.0, and even more preferably 3.0 to 7.0. By setting the mass ratio of component (D) to component (C) to 2.7 or more, an increase in volume resistivity can be suppressed, and by setting it to 10 or less, a decrease in tensile elongation at break can be suppressed.

[0105] (Example 2 of Conductive Gel (Resin Composition)) In one embodiment, the conductive resin composition contains a polyvinyl alcohol-based resin. In that case, in one embodiment, the conductive resin composition contains component (A) a 2 to 10 mass % aqueous solution of a polyvinyl alcohol-based resin, and component (B) an organotitanium compound. The mass ratio of component (A) to component (B) is 70:30 to 90:10. In one embodiment, the conductive resin composition preferably contains component (A) a 5 to 10 mass % aqueous solution of a polyvinyl alcohol-based resin, and component (B) an organotitanium compound. The mass ratio of component (A) to component (B) is preferably 70:30 to 90:10. In one embodiment, the conductive resin composition preferably contains component (A) a 5 to 10 mass % aqueous solution of a polyvinyl alcohol-based resin, and component (B) an organotitanium compound. The mass ratio of component (A) to component (B) is more preferably 80:20 to 90:10. In one embodiment, the conductive resin composition preferably contains component (A) a 5% by mass aqueous solution of a polyvinyl alcohol-based resin and component (B) an organotitanium compound. The mass ratio of component (A) to component (B) is more preferably 85:15. The conductive resin composition contains component (A) a 2 to 10% by mass aqueous solution of a polyvinyl alcohol-based resin and component (B) an organotitanium compound. A mass ratio of component (A) to component (B) of 70:30 to 90:10 facilitates the preparation of a gel. Furthermore, a flexible gel is easily obtained by containing component (A) a 5% by mass aqueous solution of a polyvinyl alcohol-based resin and component (B) an organotitanium compound, and / or by a mass ratio of component (A) to component (B) of 85:15.

[0106] (Component (A): Aqueous Solution of Polyvinyl Alcohol Resin) The polyvinyl alcohol resin may be, for example, a polyvinyl alcohol resin or a modified polyvinyl alcohol resin. Examples of modified polyvinyl alcohol include those obtained by saponifying a copolymer of a vinyl ester monomer and a monomer copolymerizable therewith, and those obtained by modifying unmodified polyvinyl alcohol, such as acetoacetyl-modified PVA. Among the above-mentioned polyvinyl alcohol resin materials, it is preferable to use a polyvinyl alcohol resin.

[0107] The lower limit of the average polymerization degree of the polyvinyl alcohol-based resin is preferably 1000, more preferably 1300, and even more preferably 1600. Meanwhile, the upper limit of the average polymerization degree of the polyvinyl alcohol-based resin is preferably 4000, more preferably 3300. The average polymerization degree of the polyvinyl alcohol-based resin is preferably 1000 to 4000, more preferably 1300 to 3500, and even more preferably 1600 to 3300. Here, the average polymerization degree is a value determined by the method defined in JIS K 6726 (1994). By setting the average polymerization degree of the polyvinyl alcohol-based resin to 1000 or more, favorable strength and orientation can be obtained. Meanwhile, by setting the average polymerization degree of the polyvinyl alcohol-based resin to 4000 or less, sufficient solubility in water can be achieved, facilitating the formation of a resin layer containing the polyvinyl alcohol-based resin.

[0108] The lower limit of the saponification degree of the polyvinyl alcohol resin is preferably 70 mol%, more preferably 80 mol%, and even more preferably 85 mol%. On the other hand, the upper limit of the saponification degree of the polyvinyl alcohol resin is preferably 100 mol%, more preferably 95 mol%, and even more preferably 90 mol%. The saponification degree of the polyvinyl alcohol resin is preferably 70 to 100 mol%, more preferably 80 to 100 mol%, and even more preferably 85 to 95 mol%.

[0109] (Component (B): Organotitanium Compound) The organotitanium compound is not limited, and may be any compound that reacts with hydroxyl groups or carboxyl groups (crosslinking agent). Furthermore, it is preferable that the organotitanium compound is water-soluble, does not undergo denaturation due to dissociation in water, and does not lose its reactivity in aqueous solution. The organotitanium compound used preferably has a ligand that is at least one selected from triethanolamine, acetylacetone, citric acid, lactic acid, malic acid, tartaric acid, and glycolic acid, and has two or more ligands coordinated per titanium atom. Specific examples of the organotitanium compound include titanium lactate (including titanium lactate ammonium salt), diisopropoxytitanium bis(triethanolaminate), and titanium peroxocitrate.

[0110] (Example 3 of Conductive Gel) In one embodiment, the conductive gel may be a gel containing konjac, agar, gelatin, carrageenan, and / or a cellulose derivative. Konjac, agar, gelatin, carrageenan, cellulose derivatives, and the like, which are the conductive materials included in this embodiment, can be gelled by processing these materials according to methods well known to those skilled in the art. For example, gelled konjac can be produced by crushing the main ingredient, konjac root, using a grater or mixer, kneading with a coagulant, molding, and boiling in hot water. Furthermore, for example, gelled agar can be produced by boiling seaweed from the Agaraceae family and seaweed from the Red Algae family in hot water, filtering the resulting paste, and then solidifying it at approximately 40°C or below. For example, gelatin can be prepared by pretreating a main raw material such as cattle bone, cattle hide, or pigskin with an inorganic acid or lime, followed by heating to extract a gelatin solution, filtering the solution, and then cooling to form a gel. Alternatively, the gelatin solution can be subjected to an extraction step, a concentration step, and a drying step to form a dry powder or the like, and then gelled again.

[0111] The gel preferably has a water content of 20 to 98% by mass, more preferably 25 to 80% by mass, and even more preferably 30 to 70% by mass.

[0112] The gel preferably contains chlorides, such as NaCl, CaCl ２ , FeCl ３ The chloride content of the gel is preferably in the range of 0.5 to 10 wt %, more preferably in the range of 1 to 10 wt %, based on the total weight of the gel. If the amount of metal chloride is too high, chloride crystals are likely to form.

[0113] (Properties of the simulated ulcer) The simulated ulcer is compatible with energy devices used in medical technique training, has excellent preservation properties, and can realize a texture similar to that of an actual organ.

[0114] The volume resistivity of the conductive portion of the simulated ulcer is preferably 1.0×10 ２ ~1.0 x 10 ７ Ω cm, and more preferably 1.0×10 ２ Ω・cm or more 1×10 ７ Ω cm, and more preferably less than 1.0 × 10 ２ ~1.0 x 10 ６ Ω cm, and more preferably 1.0×10 ２ ~5.0 x 10 ５ In particular, the volume resistivity is 1.0 × 10 ７ By setting the volume resistivity to Ω cm or less, when the simulated organ is used for medical procedure training using an energy device, it becomes easier to reproduce the behavior of an ulcer in a living body, and incision treatment becomes easier. ２ ~1.0 x 10 ７ The simulated ulcer having a resistivity of Ω cm can be prepared by adjusting the type and / or composition of the conductive material, measuring the volume resistivity, and confirming whether it falls within the above range. For example, preferably, ２ ~1.0 x 10 ７ Ω cm, more preferably 1.0×10 ２ Ω・cm or more 1.0×10 ７ Ω cm, and more preferably less than 1.0 × 10 ２ ~1.0 x 10 ６ Ω cm, more preferably 1.0×10 ２ ~5.0 x 10 ５It can be prepared using a conductive material with a resistance of Ω·cm.

[0115] As described in the "Simulated Organ" section below, the softening point of the simulated ulcer is preferably higher than that of the simulated blood vessel. That is, the softening point of the simulated ulcer may be 200°C or lower, 100°C or lower, 30°C or lower, or lower than 30°C. A simulated ulcer having a softening point of 200°C or lower can be prepared by adjusting the type and / or composition of the conductive material, measuring the softening point, and confirming whether it falls within the above range. For example, the simulated ulcer can be prepared using a conductive material having a softening point of 200°C or lower, 100°C or lower, 30°C, or lower than 30°C. In this embodiment, the softening point of the simulated ulcer is determined by measuring the temperature of a test piece of the conductive resin composition adjusted to a diameter of 30 mm and a thickness of 2 mm using a viscoelasticity measuring device RSA-G2 manufactured by TA Instruments at a temperature rise rate of 5°C / min, an indenter diameter of 10 mm, and an indenter load of 1.0 N, at which the indenter penetrates 30% of the thickness of the test piece.

[0116] As described in the "Simulated Organ" section below, the melting point of the simulated ulcer is preferably higher than the melting point of the simulated blood vessel. That is, the melting point of the simulated blood vessel may be 50 to 200°C, 50 to 150°C, 50 to 120°C, or less than 50°C. A simulated ulcer with a melting point of 50 to 200°C can be prepared by adjusting the type and / or composition of the conductive material, measuring the melting point, and confirming that it falls within the above range. For example, the simulated ulcer can be prepared using a conductive material with a melting point of 50 to 200°C, 50 to 150°C, more preferably 50 to 120°C, or less than 50°C. In this embodiment, the melting point of the simulated ulcer is measured by the method described in the "Simulated Blood Vessel" section.

[0117] (Method for Producing a Simulated Ulcer) The shape of the simulated ulcer can be any shape selected from, for example, circular, elliptical, polygonal, or irregular. The simulated ulcer can be molded by known molding methods, and may be molded as a single unit or in separate pieces. For example, when using an inner mold (core) and an outer mold and pouring a material into the space between them to form a mold, an incision may be made in the resin molded body to remove the inner mold from the space. At this time, the incision may be glued together to complete the simulated ulcer. Alternatively, the simulated ulcer may be molded using a male and female mold by heat press molding, vacuum press molding, or the like, or multiple tissue portions may be molded separately by injection molding or the like and then glued together to complete the simulated ulcer.

[0118] The simulated ulcer may be colored using additives such as coloring agents such as pigments and dyes, fragrances, antioxidants, antibacterial agents, etc., within the scope that does not impair the purpose. In order to make the simulated ulcer resemble living tissue, it is preferable to color it with a coloring agent to a color similar to that of living organs.

[0119] <Simulated Mucus Composition> In one embodiment, the simulated mucus composition is a composition for coating at least a part of the outer surface of the simulated organ including the simulated blood vessel and simulated ulcer.

[0120] (Composition of simulated mucus composition) In one embodiment, the simulated mucus composition has a volume resistivity of 1.0 to 1.0×10 ６ Within this range, the components and composition are not limited.

[0121] Examples of ingredients include water, sodium chloride, magnesium chloride, potassium chloride, sodium hydroxide, sodium dihydrogen phosphate, sodium phosphate, low molecular weight compounds such as water, sodium chloride, magnesium chloride, potassium chloride, sodium hydroxide, sodium dihydrogen phosphate, sodium phosphate, glycerin, propylene glycol, methyl parahydroxybenzoate, ethyl parahydroxybenzoate, propyl parahydroxybenzoate, and butyl parahydroxybenzoate; water-absorbing polymers such as hydrogenated castor oil, 12-hydroxystearic acid, glucono delta-lactone, and sodium polyacrylate; water-soluble polymers such as polyethylene glycol, polypropylene glycol, hyaluronic acid, alginic acid, carrageenan, dextrin, xanthan gum, guar gum, glycosaminoglycan, collagen, water-soluble vinyl polymers (including carboxyvinyl polymers and polyvinyl alcohol), hypromellose, methylcellulose, polyacrylic acid, polymethacrylic acid, and hydroxyethyl cellulose; and the like, and the composition may contain one or more of these. The simulated mucus composition may further contain one or more electrolytes, conductive materials such as carbon nanomaterials, conductive polymers, and metal fillers, preservatives, fragrances, pigments, narcotic ingredients, pH adjusters, dispersants, thickeners (including thixotropic agents, anti-settling agents, and anti-sagging agents), surfactants, antioxidants, etc.

[0122] More specifically, the simulated mucus composition may be a sodium chloride aqueous solution, a glycerin solution, a sodium polyacrylate aqueous solution, or distilled water. In one embodiment, the simulated mucus composition is preferably a sodium chloride aqueous solution, a glycerin solution, or a sodium polyacrylate aqueous solution. When the simulated mucus composition is a sodium chloride aqueous solution, a glycerin solution, or a sodium polyacrylate aqueous solution, bubbles are more likely to be generated in the simulated mucus composition upon application of electricity when the simulated organ is used for medical procedure training using an energy device. In other words, the simulated mucus composition more easily reproduces the behavior (continuous bubble generation) of mucus during treatment of living mucosal tissue using an energy device. For example, the continuous bubble generation may be the continuous bubble generation caused by boiling water.

[0123] For example, when the simulated mucus composition is a sodium chloride aqueous solution, it can be prepared by adding sodium chloride to distilled water and stirring. －７ By making the aqueous solution up to 4.0M, the volume resistivity can be increased to 1.0 to 1×10 ６ It can be Ω·cm.

[0124] For example, when the simulated mucus composition is a glycerin solution, Lubricating Jelly J-5G manufactured by Hoyu Medical Co., Ltd. can be used undiluted, or it can be prepared by adding distilled water to Lubricating Jelly J-5G and stirring. In this case, by making the concentration of Lubricating Jelly J-5G in distilled water 0.5 to 100% by mass (wt%), the volume resistivity can be reduced to 3 × 10 ２ ~1 x 10 ６ It can be Ω·cm.

[0125] For example, when the simulated mucus composition is a sodium polyacrylate aqueous solution, Aron (registered trademark) A-20L manufactured by Toagosei Co., Ltd. can be used undiluted, or it can be prepared by adding distilled water to Aron A-20L and stirring. In this case, by making the concentration of Aron A-20L in distilled water 1 to 100 mass % (wt %), the volume resistivity can be made 1 to 1 × 10 ６ Ω cm, and the viscosity at 25°C measured by the measurement method specified in JIS Z8803 is 1.0 to 1.0 × 10 ５ The sodium polyacrylate aqueous solution may have a concentration of, for example, 10 wt % or 100 wt % in distilled water, such as Aron A-20L.

[0126] In addition, various commercially available medical lubricating jellies and ultrasound examination jellies other than those mentioned above also have a volume resistivity of 1.0 to 1.0 × 10 ５ Ω cm, and the viscosity at 25°C measured by the measurement method specified in JIS Z8803 is 1.0 to 1.0 × 10 ５As long as the viscosity of the lubricating jelly is within the range of 0.05 mPa·s, it can be used as the simulated mucus composition of this embodiment, regardless of its component composition. Examples of such medical lubricating jellies include Boston Scientific sterile lubricating jelly (catalog number SLT-612-10) and ECHO JELLY MORE (registered trademark), a jelly for ultrasound examinations manufactured by Fujifilm Healthcare Co., Ltd.

[0127] In one embodiment, the thickness of the simulated mucus composition applied to the simulated organ is preferably 0.01 to 3.0 mm, more preferably 0.05 to 2.5 mm, and even more preferably 0.05 to 1.0 mm. When the thickness is 0.05 to 1.0 mm, it may be 0.1 mm, 0.5 mm, or 1.0 mm.

[0128] By applying the simulated mucus composition to a simulated organ with a thickness in the range of 0.01 to 3.0 mm, the simulated mucus composition in the simulated organ of this embodiment can easily reproduce the behavior of mucus (continuous generation of bubbles) during treatment of mucosal tissue of a living body using an energy device.

[0129] (Properties of Simulated Mucus Composition) In one embodiment, the simulated mucus composition has a volume resistivity of 1.0 to 1.0×10 ６ Ω cm. Volume resistivity is 1.0 to 1.0 × 10 ６ When the simulated organ is used for medical procedure training using an energy device, the simulated mucus composition is likely to generate bubbles when energized due to the resistivity of the simulated mucus composition being 1.0×10 １ ~1.0 x 10 ３ Preferably, the resistance is 4.0×10 １ ~1.0 x 10 ３ More preferably, it is 4.0×10 １ ~3.0 x 10 ２ The volume resistivity of the simulated mucus composition is more preferably 1.0×10 １ ~1.0 x 10 ３By having a resistance of Ω·cm, bubbles are more likely to be generated in the simulated mucus composition with fewer energization cycles, which is similar to the behavior of mucus in the living body.

[0130] Volume resistivity is 1.0 to 1.0 x 10 ６ A simulated mucus composition having a resistance in the range of Ω cm can be prepared by adjusting the components contained in the composition and the content of each component, measuring the volume resistivity and viscosity, and confirming whether the volume resistivity and viscosity fall within the above range.

[0131] Here, the volume resistivity can be calculated by AC impedance measurement at a measurement temperature of 25°C. Specifically, a measurement sample was placed in a liquid measurement cell with a diameter of 13 mm and a thickness of 5 mm, and metal terminals provided on both ends of the cell in contact with the measurement sample were connected to the terminals of an AC impedance measurement device (Solartron SI 1287, Frequency Response Analyzer 1252A, manufactured by Toyo Corporation). The resistivity of the cell was measured in an environment at a temperature of 25°C using a small environmental tester (manufactured by Espec Corporation, model number: SU-241), and the volume resistivity can be calculated by dividing the obtained result by the thickness of 5 mm.

[0132] In one embodiment, the simulated viscous liquid composition has a viscosity of 1.0 to 1.0 x 10 at 25°C measured by the measurement method specified in JIS Z8803. ５ It is preferable that the viscosity of the simulated mucus composition is 1000 MPa·s. Such a viscosity tends to improve the suitability for application to the simulated organ. The suitability for application means that when the simulated mucus composition is applied to the simulated organ, it is free from excessive viscosity (stickiness) and tends to remain on the surface of the simulated organ after application.

[0133] The viscosity can be measured by the measurement method specified in JIS Z8803 using a rheometer (MCR-92 manufactured by Anton Paar) with a cone plate having a diameter of 50 mm, a measurement temperature of 25° C., and a shear rate of 10 / s.

[0134] When the simulated mucus composition is a sodium chloride aqueous solution, 5.0 × 10 －７ By using a sodium chloride aqueous solution of up to 4M, the viscosity at 25°C measured by the measurement method specified in JIS Z8803 is 1.0 to 1.0 × 10５ The viscosity can be mPa·s.

[0135] When the simulated mucus composition is a glycerin solution, the concentration of Lubricating Jelly J-5G in distilled water is 1 to 100% by mass (wt%), and the viscosity at 25°C measured by the measurement method specified in JIS Z8803 is 1.0 to 8.0 x 10 ４ The viscosity can be mPa·s.

[0136] The viscosity of the simulated viscous liquid composition at 25°C measured by the measurement method specified in JIS Z8803 is 1.0 to 1.0 x 10 ５ mPa s, and 1.0 × 10 ２ ~5.0 x 10 ４ mPa·s, and preferably 1.0×10 ３ ~5.0 x 10 ４ mPa s is more preferable, and 5.0 × 10 ３ ~5.0 x 10 ４ More preferably, the viscosity is 5.0×10 mPa·s. ３ ~5.0 x 10 ４ mPa s, 9.0 × 10 ３ ~8.0 x 10 ４ mPa s, 9.0 × 10 ３ ~2.6 x 10 ４ It may also be mPa·s.

[0137] The ranges of the volume resistivity of the simulated mucus composition and the viscosity at 25°C measured by the measurement method specified in JIS Z8803 are as described above, and any ranges of volume resistivity and viscosity may be combined.

[0138] The volume resistivity of the simulated mucus composition is 1.0 to 1.0 x 10 ６ and / or the viscosity of the simulated viscous liquid composition at 25°C measured by the measurement method specified in JIS Z8803 is 1.0 to 1.0 x 10 ５ By keeping the viscosity in the range of mPa·s, it is possible to reduce the risk of deformation or malfunction due to current application or heating of energy devices that have been used in conventional medical procedure training.

[0139] <Simulated Organ> The simulated organ includes a simulated blood vessel and a simulated ulcer. In one embodiment, the simulated organ further includes a simulated mucus composition (in this case, it is referred to as a "simulated organ coated with a simulated mucus composition").

[0140] In this specification, the term "simulated organ" includes not only the entire organ, but also a partial tissue replica of an organ.

[0141] The simulated organ may be a model that mimics the organ of any animal species, and may be, for example, a simulated organ of any animal species, such as mammals including humans, birds, reptiles, amphibians, or fish, and can be selected appropriately by a person skilled in the art depending on the needs for training in medical procedures.

[0142] In one embodiment, the simulated organ is a simulated organ for use as a mucus-coated simulated organ, at least a portion of its outer surface being coated with a simulated mucus composition.

[0143] (Configuration and Properties of the Simulated Organ) In one embodiment, the simulated organ has a structure in which a simulated blood vessel penetrates a desired site of the simulated ulcer in the thickness direction. Such a simulated organ can be produced by penetrating a desired site of the simulated ulcer with the simulated blood vessel.

[0144] In the simulated organ, at least a part of the outer surface of the simulated blood vessel and at least a part of the simulated ulcer are electrically conductive, the surface resistance of the electrically conductive part of the simulated blood vessel is lower than the volume resistivity of the electrically conductive part of the simulated ulcer, and the volume resistivity of the electrically conductive part of the simulated ulcer is 1.0 × 10 ２ ~1.0 x 10 ７ It is Ω·cm.

[0145] In one embodiment, the simulated blood vessel comprises a thermoplastic resin.

[0146] Because the surface resistivity of the conductive part of the simulated blood vessel is lower than the volume resistivity of the conductive part of the simulated ulcer, when the simulated organ is used for medical procedure training using an energy device, the simulated blood vessel is more likely to heat up than the simulated ulcer when electricity is passed through it, making it easier to perform hemostasis treatment on the simulated blood vessel.

[0147] The surface resistance of the simulated blood vessel and the volume resistivity of the simulated ulcer can be adjusted as described above in the "Simulated Blood Vessel" and "Simulated Ulcer" sections.

[0148] The preferred ranges of the surface resistance of the simulated blood vessel and the preferred ranges of the volume resistivity of the simulated ulcer are as explained above in the "Simulated Blood Vessel" and "Simulated Ulcer" sections.

[0149] In one embodiment, the softening point of the simulated blood vessel is preferably lower than that of the simulated ulcer. For example, as described above, the softening point of the simulated blood vessel can be adjusted to a desired range similar to that of the thermoplastic resin by adjusting the softening point of the thermoplastic resin of the base layer of the simulated blood vessel.

[0150] By setting the softening point of the simulated blood vessel to a temperature lower than that of the simulated ulcer, the simulated ulcer is less likely to melt before or during hemostasis in the simulated blood vessel.

[0151] In one embodiment, the melting point of the simulated blood vessel is preferably lower than the melting point of the simulated ulcer. For example, as described above, the melting point of the simulated blood vessel can be adjusted to a desired range similar to that of the thermoplastic resin by adjusting the melting point of the thermoplastic resin of the base layer of the simulated blood vessel.

[0152] By setting the melting point of the simulated blood vessel lower than that of the simulated ulcer, melting of the simulated ulcer is unlikely to occur before or during hemostasis in the simulated blood vessel.

[0153] In one embodiment, the simulated organ may be used as a simulated mucus-coated simulated organ, in which at least a portion of the outer surface of the simulated organ is coated with a simulated mucus composition. In this case, it is preferable that the surface resistance of the conductive portion of the simulated blood vessel is higher than the volume resistivity of the simulated mucus composition. In one embodiment, at least a portion of the outer surface of the simulated organ is coated with a simulated mucus composition, and it is preferable that the surface resistance of the conductive portion of the simulated blood vessel is higher than the volume resistivity of the simulated mucus composition. When at least a portion of the outer surface of the simulated organ is coated with a simulated mucus composition, the coated portion, coating method, etc. are as described in the fifth embodiment.

[0154] Because the surface resistance of the conductive portion of the simulated blood vessel is higher than the volume resistivity of the simulated mucus composition coating at least a portion of the outer surface of the simulated organ, when the simulated organ is used in medical procedure training using an energy device and electricity is applied, the simulated mucus composition heats up faster than the simulated blood vessel, making it more likely to generate bubbles before the simulated blood vessel achieves hemostasis. In medical procedures in living organisms, treatments are performed using the continuous generation of bubbles caused by heating of the mucus coating the mucosal tissue as one indicator of electricity application and hemostasis due to electricity application. Therefore, because the surface resistance of the conductive portion of the simulated blood vessel is higher than the volume resistivity of the simulated mucus composition coating at least a portion of the outer surface of the simulated organ, it becomes easier to more accurately reproduce the behavior of mucus (continuous generation of bubbles) and hemostasis behavior in medical procedures in living organisms when using a simulated organ for medical procedure training.

[0155] Here, when the surface resistivity of the conductive portion of the simulated blood vessel is higher than the volume resistivity of the simulated mucus composition covering at least a portion of the outer surface of the simulated organ, the relationship becomes: volume resistivity of the simulated mucus composition < surface resistivity of the conductive portion of the simulated blood vessel < volume resistivity of the conductive portion of the simulated ulcer. In this case, when the simulated organ is used for medical procedure training using an energy device, the simulated mucus composition is likely to be heated first by electrical current application, then the simulated blood vessel, and finally the simulated ulcer. Therefore, the simulated mucus composition is likely to generate bubbles before hemostasis in the simulated blood vessel, and the simulated ulcer is unlikely to melt before or during hemostasis in the simulated blood vessel.

[0156] In one embodiment, in the simulated organ, the surface resistance value of the conductive portion of the simulated blood vessel is 1.0×10 １ ~1.0 x 10 ６ Ω, and the volume resistivity of the conductive portion of the simulated ulcer is 1.0 × 10 ２ ~1.0 x 10 ７ The surface resistance of the electrically conductive portion of the simulated blood vessel in the simulated organ and the volume resistivity of the electrically conductive portion of the simulated ulcer can be a combination of any of the ranges of surface resistance described in "Simulated Blood Vessel" and any of the ranges of volume resistivity described in "Simulated Ulcer."

[0157] In one embodiment, in the simulated organ, the surface resistance value of the conductive portion of the simulated blood vessel is 1.0×10 １ ~1.0 x 10 ６ Ω, and the volume resistivity of the conductive portion of the simulated ulcer is 1.0 × 10 ２ ~1.0 x 10 ７ Ω cm, and the volume resistivity of the simulated mucus composition is 1.0 to 1.0 × 10 ６ The surface resistance of the conductive portion of the simulated blood vessel in the simulated organ, the volume resistivity of the conductive portion of the simulated ulcer, and the volume resistivity of the simulated mucus composition can be a combination of any of the ranges of surface resistance described in "Simulated Blood Vessel," any of the ranges of volume resistivity described in "Simulated Ulcer," and any of the ranges of volume resistivity described in "Simulated Mucus Composition."

[0158] In one embodiment, the simulated organ may be connected to a device capable of supplying simulated blood to the simulated blood vessel. For example, the simulated blood vessel may be a path for supplying simulated blood to a surface simulating a mucosal tissue of the simulated ulcer in a hemostasis training, and may penetrate the simulated ulcer of the simulated organ. Any device capable of supplying simulated blood may be used, such as a tubular pump or a syringe.

[0159] (Use of simulated organ) In one embodiment, the simulated organ is a simulated organ used for medical procedure training. Here, "medical procedure training" refers to training for improving the skills of doctors and medical students and the quality of medical procedures, and includes, for example, medical procedure training performed under endoscopic observation and medical procedure training performed under ultrasound observation.

[0160] In one embodiment, the medical procedure is a treatment of mucosal tissue (e.g., an ulcer) using an energy device. Examples of energy devices include high-frequency hemostatic forceps, electric scalpels, ultrasonic scalpels, heat probes, microwave scalpels, and laser scalpels. Preferred examples of the medical procedure include treatments involving incision and / or hemostasis of mucosal tissue using an energy device, and more specifically, examples include endoscopic mucosal resection, endoscopic submucosal dissection, and endoscopic hemostasis. In one embodiment, when simulated blood is supplied from a simulated blood vessel in a simulated organ, the medical procedure may be hemostasis, simulating bleeding from the simulated blood vessel.

[0161] [Second embodiment (medical procedure training kit)] The kit according to this embodiment is a medical procedure training kit including the simulated organ according to the first embodiment and a simulated mucus composition. In one embodiment, in the kit, the surface resistance value of the conductive portion of the simulated blood vessel is higher than the volume resistivity of the simulated mucus composition.

[0162] The "medical procedure training" is as described in the first embodiment.

[0163] (Simulated Organ) In this embodiment, the simulated organ is any of the simulated organs described in the first embodiment. The medical procedure training kit includes a simulated mucus composition. As described in the first embodiment, the simulated organ may be provided as a kit with at least a portion of its exterior coated with the simulated mucus composition. Alternatively, the simulated mucus composition may be provided separately from the simulated organ, so that the user, etc., can apply the simulated mucus composition to the simulated organ as appropriate prior to medical procedure training. In addition to the simulated organ and the simulated mucus composition, the kit may also include one or more devices, medical equipment, medical procedure consumables, etc. required for medical procedure training. For example, the kit may include an energy device, a recording camera, a computer, forceps, clips, hemostatic cotton, a sponge, simulated blood, a pump or syringe for supplying simulated blood, etc., used in medical procedures.

[0164] (Simulated mucus composition) In this embodiment, the simulated mucus composition is any of the simulated mucus compositions described in the first embodiment.

[0165] Third Embodiment (Medical Procedure Training Apparatus) The apparatus according to this embodiment is a medical procedure training apparatus that includes the simulated organ according to the first embodiment and one or more other types of simulated organs.

[0166] Here, the device according to this embodiment may include a plurality of simulated organs according to the first embodiment. For example, the device may be a device in which a series of digestive organs, such as the oral cavity, pharynx, esophagus, stomach, duodenum, small intestine, large intestine, rectum, and anus, are connected to replicate a living organism. Furthermore, the device may be a device including one or more types of simulated organs as part of a human or animal model equipped with various organs, with or without simulated blood vessels or ulcers.

[0167] The device according to this embodiment can be used for medical procedure training. "Medical procedure training" is as described in the first embodiment.

[0168] [Fourth embodiment (medical procedure training method)] The method according to this embodiment is a medical procedure training method using the simulated organ according to the first embodiment, the kit according to the second embodiment, and / or the device according to the third embodiment.

[0169] The "medical procedure training" is as described in the first embodiment.

[0170] (Medical procedure training method) For example, in a treatment of mucosal tissue in a living body, the tip of an energy device is brought into contact with the mucosal tissue and electricity is applied to incise and / or stop bleeding of the mucosal tissue. In the medical procedure training method according to this embodiment, the tip of the energy device may be brought into contact with the surface (mucosal surface) of a simulated mucus-coated simulated organ that is coated with the simulated mucus composition, and electricity may be applied, as in a treatment in an actual living body.

[0171] More specifically, for example, the simulated blood vessel in the simulated mucus-coated simulated organ exemplified in the first embodiment, in which the surface simulating the mucosal surface of a sheet containing a hydrogenated styrene-based thermoplastic elastomer as the main component is coated with a 0.5 mm-thick simulated mucus composition, may be clamped at the tip of an electric scalpel (high-frequency surgical device manufactured by Elbe: VIO-100C, conditions: FORCED coagulation mode, output 30 W, treatment tool: hemostatic forceps FD-410LR) and electricity may be applied.

[0172] Generally, when electricity is applied to mucosal tissue of a living body, the mucus covering the mucosa is heated, causing vaporization from within the mucus, which begins to form bubbles, and gradually, continuous bubble generation becomes observable. In a medical procedure training method using a simulated mucus-coated simulated organ, completion of electricity application may be determined based on the behavior of the mucus, such as the size and number of bubbles generated, that are actually observed when electricity application is completed in the simulated blood vessel that is the treatment target of the medical procedure being trained.

[0173] In the case of a simulated mucus-coated simulated organ, the simulated blood vessel is clamped at the tip of the energy device and an electric current is applied. The completion of the electric current application can be determined by the continuous generation of bubbles in the simulated mucus composition, preferably the continuation of bubble generation until the electric current application is stopped.

[0174] The volume resistivity of the simulated mucus composition is 1.0 to 1.0 x 10 ６ By having the resistivity in the Ω cm range, the simulated mucus composition in the simulated mucus-coated simulated organ can easily reproduce the behavior of mucus during treatment of mucosal tissue in a living body using an energy device. Furthermore, the medical procedure training method according to this embodiment can reduce the risk of deformation or malfunction of energy devices caused by current application and heating of thermoplastic resins, which has been used in conventional medical procedure training.

[0175] In one embodiment, when the simulated mucus-coated simulated organ includes a simulated blood vessel connected to a device capable of supplying simulated blood, the medical procedure training method may be a method for training in hemostasis, simulating bleeding from the simulated blood vessel. In such hemostasis training, before medical procedure training using the energy device, simulated blood may be supplied to the simulated blood vessel to reproduce bleeding in mucosal tissue.

[0176] The medical procedure training method of this embodiment can reproduce the behavior of mucus in the mucosal tissue of a living body when treating mucosal tissue using an energy device, and is therefore useful for medical professionals to learn the procedures for treating a living body.

[0177] In one embodiment, the viscosity of the simulated viscous liquid composition at 25°C measured by the measurement method specified in JIS Z8803 is 1.0 to 1.0 x 10 ５The viscosity of the simulated mucus composition may be in the range of mPa·s. When the simulated mucus composition has such a viscosity, the medical procedure training method makes it easier to reproduce the behavior of mucus in living mucosal tissue when treating mucosal tissue using an energy device. Furthermore, when the simulated mucus composition is applied to a simulated organ, the application suitability is likely to be good.

[0178] In this embodiment, by using the simulated organ according to the first embodiment, the kit according to the second embodiment, and / or the device according to the third embodiment, in hemostasis training, for example, in which a simulated blood vessel is clamped at the tip of an energy device and electricity is passed through it, the behavior of mucus in the mucosal tissue of a living body, the behavior of blood vessels, and / or the state during hemostasis can be easily reproduced, allowing hemostasis training to be carried out effectively.

[0179] Fifth Embodiment (Manufacturing Method) The manufacturing method according to this embodiment comprises coating at least a portion of the outer surface of a simulated organ, including a simulated blood vessel and a simulated ulcer, with a simulated mucus composition, wherein at least a portion of the outer surface of the simulated blood vessel and at least a portion of the simulated ulcer are electrically conductive, the surface resistance of the electrically conductive portion of the simulated blood vessel is lower than the volume resistivity of the electrically conductive portion of the simulated ulcer, and the volume resistivity of the electrically conductive portion of the simulated ulcer is 1.0×10 ２ ~1.0 x 10 ７ In one embodiment, the surface resistivity of the conductive portion of the simulated blood vessel is preferably higher than the volume resistivity of the simulated mucus composition.

[0180] In the production method of this embodiment, examples and preferred examples of the "simulated organ," "simulated blood vessel," "simulated ulcer," and "simulated mucus composition," as well as the production method, materials, etc., are as described in Embodiment 1. The production method of this embodiment is a method for producing a simulated mucus-coated simulated organ, as described in Embodiment 1, in which at least a portion of the outer surface of the simulated organ is coated with the simulated mucus composition.

[0181] The manufacturing method according to this embodiment includes coating at least a portion of the outer surface of a simulated organ, including a simulated blood vessel and a simulated ulcer, with a simulated mucus composition. In the simulated organ, the portion to be coated is preferably a surface of the simulated blood vessel and / or the simulated ulcer that simulates the mucosal surface of mucosal tissue. In this case, it is not necessary to coat the entire surface that simulates the mucosal surface of mucosal tissue; it is sufficient to coat at least the portion that comes into contact with the tip of an energy device and through which electricity is applied when the simulated mucus-coated simulated organ is used for medical procedure training. As described in the first embodiment, in one embodiment, the simulated organ may include a device capable of supplying simulated blood. When manufacturing a simulated organ for hemostasis training simulating bleeding from the simulated blood vessel using such a simulated organ including a simulated blood vessel connected to a device capable of supplying simulated blood, it is sufficient to coat at least the periphery of the simulated blood vessel with the simulated mucus composition.

[0182] In one embodiment, the thickness of the simulated mucus composition in the step of coating the simulated organ, preferably the thickness of the simulated mucus composition applied to the simulated organ, is preferably 0.01 to 3.0 mm, more preferably 0.01 to 2.5 mm, and even more preferably 0.05 to 1.0 mm. When the thickness is 0.05 to 1.0 mm, it may be 0.1 mm, 0.5 mm, or 1.0 mm.

[0183] The simulated mucus composition can be applied to the simulated organ appropriately using fingers, a spatula, or the like.

[0184] The timing of the step of coating the simulated organ with the simulated mucus composition, preferably the timing of applying the simulated mucus composition, may be determined so as to reproduce the state of mucus in the mucosal tissue of a living body when electricity is applied using an energy device during medical procedure training.

[0185] The simulated mucus-coated simulated organ produced by the manufacturing method of this embodiment can reproduce the behavior of mucus in living mucosal tissue when treating mucosal tissue with an energy device, and is therefore useful for medical procedure training.

[0186] A non-limiting list of exemplary embodiments and combinations of exemplary embodiments of the present disclosure is disclosed below. [1-1] A simulated organ including a simulated blood vessel and a simulated ulcer, wherein at least a portion of the outer surface of the simulated blood vessel and at least a portion of the simulated ulcer are electrically conductive, the surface resistance of the electrically conductive portion of the simulated blood vessel is lower than the volume resistivity of the electrically conductive portion of the simulated ulcer, and the volume resistivity of the electrically conductive portion of the simulated ulcer is 1.0 x 10 ２ ~1.0 x 10 ７ [1-2] The simulated organ according to [1-1], wherein the simulated blood vessel contains a thermoplastic resin. [1-3] The simulated organ according to [1-1] or [1-2], wherein at least a part of the outer surface of the simulated organ is coated with a simulated mucus composition, for use as a simulated mucus-coated simulated organ. [1-4] The simulated organ according to any one of [1-1] to [1-3], wherein the softening point of the simulated blood vessel is 200°C or lower. [1-5] The surface resistance of the conductive part of the simulated blood vessel is 1.0 x 10 1 ~1.0 x 10 ６ Ω. [1-6] The simulated organ according to any one of [1-3] to [1-5], wherein the surface resistance of the conductive portion of the simulated blood vessel is higher than the volume resistivity of the simulated mucus composition. [1-7] The simulated organ according to any one of [1-1] to [1-6], wherein at least a part of the outer surface of the simulated organ is covered with the simulated mucus composition, and the surface resistance of the conductive portion of the simulated blood vessel is equal to or higher than the volume resistivity of the simulated mucus composition. [1-8] The volume resistivity of the simulated mucus composition is 1.0 to 1.0 x 10 ６The simulated organ according to [1-7], wherein the resistance is Ω·cm. [1-9] The simulated organ according to any one of claims [1-1] to [1-8], wherein the simulated blood vessel has a tubular base layer and a conductive layer disposed on at least a part of the outer surface of the base layer, and wherein the outer diameter of the base layer is 0.5 to 10.0 mm and / or the thickness of the base layer is 0.05 to 2.0 mm. [1-10] The simulated organ according to any one of claims [1-1] to [1-9], wherein the simulated blood vessel is connected to a device capable of supplying simulated blood into the simulated blood vessel. [1-11] The simulated organ according to any one of [1-1] to [1-10], wherein the simulated organ is used for medical procedure training. [1-12] The simulated organ according to [1-11], wherein the medical procedure is a treatment including incision of mucosal tissue or hemostasis using an energy device. [1-13] A kit for medical procedure training, comprising the simulated organ according to any one of [1-1] to [1-12] and a simulated mucus composition, wherein the surface resistance of the conductive portion of the simulated blood vessel is higher than the volume resistivity of the simulated mucus composition. [1-14] The volume resistivity of the simulated mucus composition is 1.0 to 1.0 x 10 ６ [1-15] A medical procedure training kit according to [1-13], having a resistivity of Ω·cm. [1-15] A medical procedure training device comprising the simulated organ according to any one of [1-1] to [1-14] and one or more other types of simulated organs. [2-1] A method for producing a simulated mucus-coated simulated organ, comprising coating at least a portion of the outer surface of a simulated organ including a simulated blood vessel and a simulated ulcer with a simulated mucus composition, wherein at least a portion of the outer surface of the simulated blood vessel and at least a portion of the simulated ulcer are conductive, the surface resistivity of the conductive portion of the simulated blood vessel is lower than the volume resistivity of the conductive portion of the simulated ulcer and higher than the volume resistivity of the simulated mucus composition, and the volume resistivity of the conductive portion of the simulated ulcer is 1.0 x 10 ２ ~1.0 x 10 ７ A manufacturing method, wherein the simulated blood vessel contains a thermoplastic resin. [3-1] A medical procedure training method using the simulated organ according to any one of [1-1] to [1-12].

[0187] The present disclosure will be explained in more detail below by showing examples, but interpretation of the present disclosure is not limited to these examples.

[0188] The various raw materials and manufacturing methods used in the examples are as follows: (1) Simulated blood vessel (1-1) Base layer (X1) Ethylene-vinyl acetate resin (EVA): Evaflex EV170, manufactured by Dow Mitsui Polychemicals, softening point 33°C, melting point 62°C (X2) Ethylene-vinyl acetate resin (EVA): Evaflex V5961, manufactured by Dow Mitsui Polychemicals, softening point 74°C, melting point 97°C (X3) Polyester thermoplastic elastomer: Pelprene (registered trademark) P-55B, manufactured by Toyobo MC Co., Ltd., softening point 155°C, melting point 186°C

[0189] (1-2) Conductive layer (T1) Polythiophene-based conductive polymer paint (Denatron PT-436, manufactured by Nagase ChemteX Corporation) (T2) Paint obtained by mixing carbon nanotube dispersion (HW004M, manufactured by KJ Specialty Paper Co., Ltd.), water-based binder (Rikenbond REO-29M, manufactured by Miki Riken Kogyo Co., Ltd.), and water in a weight ratio of 70:5:25

[0190] (Preparation of simulated blood vessel) Using the above materials (X1) to (X3), a tubular structure with an inner diameter of 0.5 mm, an outer diameter of 1.0 mm, and a thickness of 0.25 mm was produced using an extrusion molding machine to serve as a base layer. Next, except in cases where a conductive layer was not applied, the above (T1) and (T2) were prepared as conductive layers, and the base layer was immersed in the paint to coat the surface, followed by drying at 20°C for 2 hours. A simulated blood vessel with a conductive layer 500 nm thick was obtained.

[0191] (Surface Resistance of Simulated Blood Vessel) The surface resistance was measured using a Loresta-GP (MCP-T610) manufactured by Nitto Seiko Analytech Co., Ltd., at 23±1° C., a relative humidity of 50% RH, and an applied voltage of 10 V with an ASP probe.

[0192] The surface resistance values ​​(Ω) of the simulated blood vessels prepared using the materials (X1) to (X3) were as follows: Simulated blood vessel coated with the conductive layer of T1: 1.0 × 10 ３ Simulated blood vessel coated with T2 conductive layer: 6.0 x 10 １ Simulated blood vessel without conductive layer: >1.0 x 10 ７

[0193] (2) Simulated ulcer (Material 1) Styrene-based (A) Hydrogenated styrene-based thermoplastic elastomer SEEPS (SEPTON 4055, manufactured by Kuraray Co., Ltd.) (MFR (temperature 230°C, load 2.16 kg) 0.0 g / 10 min (0.0 g / 10 min means no flow), styrene content 30 mass%, hydrogenation rate 90 mol% or more) (B) Oil Paraffin oil (Diana Process Oil PW90, manufactured by Idemitsu Kosan Co., Ltd.) (C) Polymer antistatic agent Polyolefin / polyether copolymer (Pelectron PVL, manufactured by Sanyo Chemical Industries, Ltd.) (MFR (measured at 190°C, load 2.16 kg) 8 to 15 g / 10 min) (D) Ionic liquid CIL-312 (manufactured by Nippon Carlit Co., Ltd.) (Material 2) Polyvinyl alcohol (PVA)-1・Polyvinyl alcohol (PVA) (Poval B-17, manufactured by Denka Co., Ltd.) ・Organic titanium compound (Orgatics TC-300, manufactured by Matsumoto Fine Chemical Co., Ltd.) (Ingredient 3) Polyvinyl alcohol (PVA) system-2 ・Same as ingredient 2 (Ingredient 4) Konjac ・Konjac (manufactured by Okawa Co., Ltd.) (moisture content 96% by weight) (Ingredient 5) Urethane-based ・Ninhada (registered trademark) Gel concentrate starter set (model number H0-START, manufactured by Exseal Co., Ltd.)

[0194] (Preparation of Material 1) 100 parts by mass of hydrogenated styrene-based thermoplastic elastomer (A) were mixed with 500 parts by mass of oil (B), 30 parts by mass of polymer antistatic agent (C), and 100 parts by mass of ionic liquid (D), and then stored for 12 hours or more to allow the mixture to fully soak in. Using a segment mixer (Labo Plastomill KF70V2 manufactured by Toyo Seiki Co., Ltd.), the mixture was kneaded at 180°C, a rotation speed of 100 rpm, and 15 minutes. Next, the mixture was subjected to a heat press method (180°C, 5 minutes, and a pressure of 50 kg / cm). ２ ) A sample sheet was prepared and adjusted to a width of 50 mm, a length of 50 mm, and a thickness of 3 mm.

[0195] (Preparation of Material 2) After adding 90°C water to obtain a 5 wt% aqueous solution of polyvinyl alcohol, the mixture was stirred with a magnetic stirrer. The polyvinyl alcohol aqueous solution and the organotitanium compound were mixed in a weight ratio of 85:15 and stirred well. The mixture was placed in a container and heated in an oven at 105°C for 2 hours. The resulting sample was cut to a width of 50 mm, length of 50 mm, and thickness of 10 mm.

[0196] (Preparation of Material 3) The prepared material 2 was dried for 8 days in an environment of 23°C and 50% humidity, and the obtained sample was prepared to have a width of 30 mm, a length of 30 mm and a thickness of 5 mm.

[0197] (Preparation of Material 4) Konjac was prepared to have a width of 30 mm, a length of 75 mm, and a thickness of 10 mm.

[0198] (Preparation of Material 5) The main component of the gel concentrate starter set, polyol, and the curing agent, isocyanate, were mixed in a weight ratio of 3:1, stirred with a magnetic stirrer, poured into a container, and cured by heating in an oven at 100°C for 2 hours. The resulting sample was cut to a width of 50 mm, a length of 50 mm, and a thickness of 10 mm.

[0199] (Volume Resistivity of Simulated Ulcer) A test piece of the conductive resin composition adjusted to a width of 25 mm, a length of 25 mm, and a thickness of 1 mm was conditioned for 24 hours or more in an environment of a temperature of 23±2°C and a relative humidity of 50±5%, and then the volume resistivity was measured 20 seconds after application of a voltage of 10 V using a PSP probe with a resistivity meter Loresta-GP (model number: MCP-T610) manufactured by Mitsubishi Chemical Analytech Co., Ltd.

[0200] (Softening point of simulated ulcer) A test piece of the conductive resin composition adjusted to a diameter of 30 mm and a thickness of 2 mm was measured using a viscoelasticity measuring device RSA-G2 manufactured by TA Instruments at a temperature rise rate of 5°C / min, with an indenter diameter of 10 mm and an indenter load of 1.0 N, to determine the temperature at which the indenter penetrated 30% of the thickness of the test piece.

[0201] (Melting Point of Simulated Ulcer) The melting point of the simulated ulcer was measured using a differential scanning calorimeter (DSC; DSC 3+, manufactured by METTLER TOLEDO) in a nitrogen atmosphere at a temperature increase rate of 10° C. / min.

[0202] The volume resistivities (Ω cm) of the simulated ulcers prepared using materials 1 to 5 were as follows: Material 1: Volume resistivity 5.0×10 ６ , softening point 130°C, melting point 220°C Material 2: volume resistivity 3.0 x 10 ２ Material 3: Volume resistivity 2.0 x 10 ３ Material 4: Volume resistivity 4.0 × 10 ２Material 5: Volume resistivity > 1.0 × 10 ７

[0203] (3) Simulated mucus composition (N1) 0.9% saline (0.9% aqueous sodium chloride solution) (N2) Lubricating jelly (Lubricating Jelly J-5G, manufactured by Hoyu Medical Co., Ltd.) (N3) Distilled water

[0204] (Volume Resistivity of Simulated Mucus Composition) The volume resistivity of the simulated mucus composition was calculated by AC impedance measurement at a measurement temperature of 25°C. Specifically, a measurement sample was placed in a liquid measurement cell having a diameter of 13 mm and a thickness of 5 mm, and metal terminals provided on both ends of the cell in contact with the measurement sample were connected to the terminals of an AC impedance measurement device (Solartron SI 1287, Frequency Response Analyzer 1252A, manufactured by Toyo Corporation). The resistivity of the cell was measured in an environment at a temperature of 25°C using a small environmental tester (manufactured by Espec Corporation, model number: SU-241), and the obtained result was divided by the thickness of 5 mm to calculate the volume resistivity.

[0205] The volume resistivities (Ω cm) of the simulated mucus compositions N1 to N3 were as follows: N1: 4.0×10 １ N2: 3.0 x 10 ２ N3: 1.0 x 10 ６

[0206] [Examples 1 to 11 and Comparative Examples 1 to 5] As shown in Table 1, a simulated blood vessel, a simulated ulcer, and a simulated mucus composition were combined. Specifically, the simulated blood vessel was inserted into the center of the simulated ulcer, penetrating it in the thickness direction. Except in cases where no application was made, the simulated mucus composition was applied to a thickness of 0.5 mm on the treated surface of the simulated blood vessel and simulated ulcer. Next, a syringe filled with simulated blood was connected to the end of the simulated blood vessel protruding on the opposite side from the treated surface, allowing the simulated blood to be supplied to the treated surface.

[0207] [Evaluation method and results] (Hemostasis) Using a high-frequency surgical device VIO-100C manufactured by Elbe, electricity was applied for 2 seconds each time in forced coagulation mode at an output of 30 W, while the end of the simulated blood vessel passed through the simulated ulcer and the simulated ulcer were both grasped with hemostatic forceps FD-410LR. When water was flowed through the simulated blood vessel, the number of times electricity was applied until water stopped coming out of the end of the simulated blood vessel was counted.

[0208] Hemostasis was evaluated as follows: Hemostasis after 1 to 4 energies: excellent Hemostasis after 5 to 10 energies: good Hemostasis after 11 to 20 energies: fair Hemostasis after 20 energies or less: poor

[0209] As shown in Table 1, hemostasis was "excellent" in Examples 1 to 8, "good" in Example 9, and "fair" in Examples 10 and 11. Hemostasis was "poor" in Comparative Examples 1 to 5. That is, when the surface resistance of the simulated blood vessel was less than the volume resistivity of the simulated ulcer (Examples 1 to 11), hemostasis was "excellent," "good," or "fair."

[0210] In Examples 1 to 8 (excellent hemostasis), the simulated blood vessel material was X1, and in Examples 9 to 11 (good or fair hemostasis), the simulated blood vessel material was X2 or X3. That is, when the surface resistance of the simulated blood vessel was less than the volume resistivity of the simulated ulcer and the simulated blood vessel material was X1, hemostasis was excellent.

[0211] (Air bubbles) Using a high-frequency surgical device VIO-100C manufactured by Elbe, electricity was applied for 2 seconds each time in forced coagulation mode at an output of 30 W, while the pseudo-ulcer and the end of the pseudo-blood vessel passed through the pseudo-ulcer were both grasped with hemostatic forceps FD-410LR. The number of times electricity was applied until air bubbles appeared was counted.

[0212] The generation of bubbles was evaluated as follows: Bubbles generated after 1 to 4 energizations: Good Bubbles generated after 5 to 10 energizations: Fair No bubbles generated after 11 or more energizations (up to 20 energizations): Poor

[0213] As shown in Table 1, in Examples 1 to 11, except for the cases where the pseudo-mucus composition was not applied (Examples 5 and 10), the evaluation of bubble generation was "good" or "fair." In addition, in Comparative Example 5, the evaluation of bubble generation was "good," but in the other Comparative Examples (Comparative Examples 1 to 4), the evaluation of bubble generation was "fail."

[0214] In Comparative Example 5, the simulated viscous liquid composition was N2 (volume resistivity 3.0 × 10 ２ Ω cm), the simulated ulcer was made of material 1 (volume resistivity 5.0 × 10 ６ In Comparative Examples 1 and 2, the simulated viscous liquid composition was N2 (volume resistivity was 3.0 × 10 ２ Ω cm), but the simulated ulcer was made of material 5 (volume resistivity > 1.0 × 10 ７ In Comparative Example 3, the simulated viscous liquid composition was N1 (volume resistivity was 4×10 １ Ω cm), but the simulated ulcer was made of material 5 (volume resistivity > 1.0 × 10 ７ In Comparative Example 4, the simulated ulcer was made of Material 1 (volume resistivity of 5.0 × 10 ６ Ω·cm), but the simulated mucus composition was not applied.

[0215] That is, the volume resistivity of the simulated ulcer is 1.0 x 10 ７ The evaluation of bubble generation was "good" or "fair" when the simulated mucus composition was not applied or the volume resistivity of the simulated ulcer was >1.0 × 10 ７ When the resistance was Ω·cm, the evaluation of bubble generation was "fail."

[0216]

[0217] The simulated organ of this embodiment includes a simulated blood vessel and a simulated ulcer, and the surface resistivity of the conductive portion of the simulated blood vessel is lower than the volume resistivity of the conductive portion of the simulated ulcer, allowing hemostasis treatment by applying current from an energy device. Therefore, the simulated organ can be suitably used in medical procedure training using energy devices.

Claims

1. A simulated organ including a simulated blood vessel and a simulated ulcer, wherein at least a portion of the outer surface of the simulated blood vessel and at least a portion of the simulated ulcer are electrically conductive, the surface resistance of the electrically conductive portion of the simulated blood vessel is lower than the volume resistivity of the electrically conductive portion of the simulated ulcer, and the volume resistivity of the electrically conductive portion of the simulated ulcer is 1.0 x 10 ２ ~1.0 x 10 ７ A simulated organ with a resistance of Ω·cm.

2. The simulated organ according to claim 1, wherein the simulated blood vessel comprises a thermoplastic resin.

3. The simulated organ according to claim 1 or 2, which is a simulated organ for use as a mucus-coated simulated organ, in which at least a portion of the outer surface of the simulated organ is coated with a simulated mucus composition.

4. The simulated organ according to claim 1 or 2, wherein the softening point of the simulated blood vessel is 200°C or lower.

5. The surface resistance of the conductive part of the simulated blood vessel is 1.0 x 10 １ ~1.0 x 10 ６ The simulated organ according to claim 1 or 2, which is an Ω.

6. The simulated organ according to claim 3, wherein the surface resistivity of the conductive portion of the simulated blood vessel is higher than the volume resistivity of the simulated mucus composition.

7. The simulated organ according to claim 1, wherein at least a portion of the outer surface of the simulated organ is coated with a simulated mucus composition, and the surface resistance of the conductive portion of the simulated blood vessel is equal to or greater than the volume resistivity of the simulated mucus composition.

8. The volume resistivity of the simulated mucus composition is 1.0 to 1.0 x 10 ６ The simulated organ according to claim 7, wherein the resistance is Ω·cm.

9. The simulated organ according to claim 1 or 2, wherein the simulated blood vessel has a tubular base layer and a conductive layer disposed on at least a portion of the outer surface of the base layer, and the outer diameter of the base layer is 0.5 to 10.0 mm and / or the thickness of the base layer is 0.05 to 2.0 mm.

10. A simulated organ according to claim 1 or 2, wherein the simulated blood vessel is connected to a device capable of supplying simulated blood into the simulated blood vessel.

11. The simulated organ according to claim 1 or 2, which is used for training in medical procedures including incision of mucosal tissue or hemostasis using an energy device.

12. A medical procedure training kit comprising the simulated organ of claim 1 or 2 and a simulated mucus composition, wherein the surface resistance of the conductive portion of the simulated blood vessel is higher than the volume resistivity of the simulated mucus composition.

13. The volume resistivity of the simulated mucus composition is 1.0 to 1.0 x 10 ６ 13. The medical procedure training kit according to claim 12, wherein the resistance is Ω·cm.

14. A medical technique training device comprising the simulated organ according to claim 1 or 2 and one or more other types of simulated organs.

15. A method for producing a simulated mucus-coated simulated organ, comprising coating at least a portion of the outer surface of a simulated organ including a simulated blood vessel and a simulated ulcer with a simulated mucus composition, wherein at least a portion of the outer surface of the simulated blood vessel and at least a portion of the simulated ulcer are electrically conductive, the surface resistivity of the electrically conductive portion of the simulated blood vessel is lower than the volume resistivity of the electrically conductive portion of the simulated ulcer and higher than the volume resistivity of the simulated mucus composition, and the volume resistivity of the electrically conductive portion of the simulated ulcer is 1.0 x 10 ２ ~1.0 x 10 ７ Ω·cm, and the simulated blood vessel comprises a thermoplastic resin.

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