mock chess

Abstract

A method for manufacturing a simulated organ, a medical procedure training kit, a medical procedure training device, and a simulated mucus-coated simulated organ is provided. The mock organ includes mock blood vessels and mock ulcers, wherein at least a portion of the outer surface of the mock blood vessels and at least a portion of the mock ulcers are conductive, the surface resistance value of the conductive portion of the mock blood vessels is lower than the volume resistivity of the conductive portion of the mock ulcers, and the volume resistivity of the conductive portion of the mock ulcers is 1×10² to 1×10⁷ Ω·cm.

Description

Technology Field

[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. Background Technology

[0002] Recently, there has been growing anticipation for minimally invasive surgeries—such as those using endoscopy or laparoscopy—which place less burden on the body and allow for early recovery, leading to an increase in such cases. For instance, by endoscopically resecting or excising tumors located in the internal mucosal layer of organs like the digestive tract (endoscopic mucosal resection and endoscopic submucosal dissection), surgery can be performed with smaller incisions compared to conventional open surgery. Furthermore, by endoscopically controlling bleeding within the digestive tract (endoscopic hemostasis), hemorrhagic shock can be prevented, thereby avoiding the need for emergency surgery or death. Consequently, the physical burden on patients is reduced, hospital stays are shortened, and an early return to society is anticipated.

[0003] As a result, there is a growing demand for procedural practice models for doctors and medical students corresponding to endoscopic or laparoscopic surgeries, and models for medical procedural training have been proposed to improve skills and the quality of medical practice (Patent Documents 1, 2, 3).

[0004] In addition, there is an increasing number of cases where surgical energy devices, such as electric scalpels, are used as instruments. Prior art literature

[0005] Patent Document 1: Japanese Patent Publication No. 2006-116206 Patent Document 2: Japanese Patent Publication No. 2008-197483 Patent Document 3: Japanese Patent Publication No. 2015-085017 The problem to be solved

[0006] As a training exercise for procedures such as incision or hemostasis using an energy device, such as an electric scalpel, on mucosal tissue of a living organism, for example, a mock blood vessel in a mock organ mimicking an organ or tissue was pinched with the tip of the energy device and electric current was applied. However, depending on the combination of materials or physical properties of the mock blood vessel or mock ulcer, hemostasis could not be achieved in the mock blood vessel.

[0007] The present disclosure aims to provide a simulated organ that includes simulated blood vessels and simulated ulcers and can perform hemostatic treatment during medical treatment training.

[0008] As a result of examining various means, the inventors found that the mock organ has at least a portion of the outer surface of the mock blood vessel and at least a portion of the mock ulcer that are conductive, the surface resistance value of the conductive portion of the mock blood vessel is lower than the volume resistivity of the conductive portion of the mock ulcer, and the volume resistivity of the conductive portion of the mock ulcer is 1.0 x 10 2 ~ 1.0X10 7 By using a simulated organ with a diameter of Ω·cm, it was confirmed that hemostatic treatment could be performed on the simulated blood vessel, and the present invention was completed. means of solving the problem

[0009] The present disclosure includes the following aspects.

[0010] [1] As a mock organ including mock blood vessels and mock ulcers,

[0011] At least part of the outer surface of the mock blood vessel and at least part of the mock ulcer are conductive, and

[0012] The surface resistance value of the conductive portion of the mock blood vessel is lower than the volume resistivity of the conductive portion of the mock ulcer, and

[0013] The volume resistivity of the conductive portion of the mock ulcer is 1.0×10 2 ~ 1.0X10 7 A simulated organ with Ω·cm.

[0014] [2] As a method for manufacturing a simulated organ coated with a simulated mucus,

[0015] It includes coating at least a portion of the outer surface of a mock organ, including mock blood vessels and mock ulcers, with a mock mucus composition, and

[0016] At least part of the outer surface of the mock blood vessel and at least part of the mock ulcer are conductive, and

[0017] The surface resistance value of the conductive portion of the mock blood vessel is lower than the volume resistivity of the conductive portion of the mock ulcer, and is also higher than the volume resistivity of the mock mucus composition, and

[0018] The volume resistivity of the conductive portion of the mock ulcer is 1.0×10 2 ~ 1.0X10 7 It is Ω·cm, and

[0019] A method for manufacturing a simulated blood vessel comprising a thermoplastic resin. Effects of the invention

[0020] According to the present disclosure, a simulated organ comprising a simulated blood vessel and a simulated ulcer can be provided, which can perform hemostatic treatment during medical treatment training. Specific details for implementing the invention

[0021] Hereinafter, an embodiment of the present disclosure is described in detail; however, the scope of the present disclosure is not limited to the embodiment described herein, and various modifications are possible without departing from the spirit of the present disclosure. Each aspect disclosed in this specification may be combined with any other feature disclosed in this specification. Furthermore, if multiple upper and lower limits are described for a specific parameter, any upper and lower limit among such upper and lower limits may be combined to form a preferred numerical range. Additionally, the lower and / or upper limits of the numerical range described in this disclosure are numerical values ​​within that range and may be substituted with numerical values ​​described in the embodiments. The expression "X ~ Y" indicating a numerical range means "X or greater and Y or less." Where a specific description described for one embodiment applies to other embodiments, such description may be omitted in other embodiments.

[0022] [First embodiment (simulated organ)]

[0023] The mock organ according to the present embodiment is a mock organ comprising a mock blood vessel and a mock ulcer, wherein at least a portion of the outer surface of the mock blood vessel and at least a portion of the mock ulcer are conductive, the surface resistance value of the conductive portion of the mock blood vessel is lower than the volume resistivity of the conductive portion of the mock ulcer, and the volume resistivity of the conductive portion of the mock ulcer is 1.0 x 10 2 ~ 1.0X10 7 It is a simulated organ with a diameter of Ω·cm.

[0024] Simulated Blood Vessels

[0025] The simulated blood vessel is a tubular structure, and at least part of its outer surface is conductive, and is not particularly limited as long as it is within a range where simulated blood can be supplied to the treatment surface of a simulated ulcer during medical procedure training using the simulated organ.

[0026] In one embodiment, it is preferable that the simulated blood vessel comprises a thermoplastic resin. When the simulated organ is used for medical procedure training using an energy device, the inclusion of a thermoplastic resin in the simulated blood vessel makes it easier to reproduce the behavior of human blood vessels due to heat generated when current is applied by the energy device, and makes hemostasis easier.

[0027] (Composition of mock blood vessels)

[0028] The simulated blood vessel may be composed of a single layer or multiple layers. That is, the simulated blood vessel may be a tubular single-layer structure composed of a conductive material, or a multilayer structure comprising a substrate layer constituting the tubular structure and a conductive layer made of a conductive material, or a two-layer structure composed of the substrate layer and the conductive layer.

[0029] When a simulated blood vessel includes a substrate layer and a conductive layer or is composed of them, the conductive layer may be disposed on at least a portion of the outer surface of the substrate layer, but the conductive layer may also be disposed on the entire outer surface of the substrate layer.

[0030] 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 making the diameter of the substrate layer 0.5 mm or more, processing stability during molding and handling during the manufacture of the simulated organ are improved, and by making the diameter of the simulated blood vessel 10.0 mm or less, the reproducibility of human blood vessels is improved and current failure caused by the energy device can be suppressed.

[0031] 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.

[0032] In one embodiment, the thickness of the simulated blood vessel is 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 gripped by an energy device, and heat is transferred in a shorter time.

[0033] In one embodiment, when the simulated blood vessel includes a substrate layer and a conductive layer, the diameter (outer diameter) of the substrate layer is 0.5 to 10.0 mm. In another embodiment, the diameter of the substrate layer is preferably 0.7 to 5.0 mm, and more preferably 1.0 to 3.0 mm. By making the diameter of the substrate layer 0.5 mm or more, processing stability during molding and handling ease during the manufacture of the simulated organ are improved, and by making the diameter of the substrate layer 10.0 mm or less, the reproducibility of the human blood vessel is improved and current failure caused by the energy device can be suppressed.

[0034] The inner diameter of the substrate 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.

[0035] In one embodiment, when the simulated blood vessel includes a substrate layer and a conductive layer, the thickness of the substrate layer is 0.05 to 2.0 mm. The thickness of the substrate 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.

[0036] If the thickness of the substrate layer is 2.0 mm or less, heat is transferred in a short time when gripped by an energy device, making it possible to stop bleeding.

[0037] In one embodiment, when the simulated blood vessel comprises a substrate 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 2000 nm, more preferably 50 to 1000 nm, and even more preferably 150 to 500 nm.

[0038] By making the thickness of the conductive layer 20 nm or more, sufficiently high conductivity can be achieved, and the smoothness of the substrate surface is also improved. Therefore, when a simulated organ is used for medical procedure training with an energy device, hemostasis is facilitated when current is applied by the energy device.

[0039] For example, if a simulated blood vessel consists of a substrate layer and a conductive layer, the thickness of the tube of the simulated blood vessel is the sum of the thickness of the substrate layer and the thickness of the conductive layer.

[0040] (Composition of simulated blood vessels)

[0041] (1) Base layer

[0042] When the simulated blood vessel comprises a substrate layer and a conductive layer, it is preferable that the substrate layer comprises a thermoplastic resin. The substrate layer may be formed using only a thermoplastic resin, may be a single-layer structure formed using a thermoplastic resin composition alloyed with one type of thermoplastic resin or two or three or more types of thermoplastic resins, or may be a multi-layer structure formed using two or three or more types of thermoplastic resin compositions.

[0043] Since the substrate layer includes a thermoplastic resin, the simulated blood vessel includes a thermoplastic resin. When the simulated organ is used for medical procedure training using an energy device, the inclusion of a thermoplastic resin in the simulated blood vessel makes it easier to reproduce the behavior of human blood vessels caused by heat generated during current application by the energy device, thereby facilitating hemostasis.

[0044] In one embodiment, the substrate layer may include a thermoplastic resin, may include a thermoplastic resin composition, may be molded using only a thermoplastic resin, or may be molded using only a thermoplastic resin composition.

[0045] (1-1) Thermoplastic resin

[0046] Here, the thermoplastic resin composition mainly contains a thermoplastic resin. Here, "mainly contains" means that the thermoplastic resin composition contains 50 mass% or more of the thermoplastic resin. In another embodiment, it may contain 70 mass% or more or 90 mass% or more, or may consist only of the thermoplastic resin.

[0047] 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 making the tensile modulus 50 MPa or less, the simulated blood vessel can be compressed by gripping with an energy device, and the bleeding of the simulated blood flowing through the simulated blood vessel can be easily stopped.

[0048] The tensile modulus is calculated from the slope of the initial straight line in the stress-strain curve by punching a sheet with a thickness of 1.0 mm into the shape of a test specimen type 5 according to the tensile test method for plastics of JIS K7127, using a tensile testing machine (manufactured by Shimadzu, Autograph AG-Xplus) under conditions of a tensile speed of 50.0 mm / min, and according to the tensile test method for plastics of JIS K7127.

[0049] The type of thermoplastic resin used in this embodiment is not limited and can be selected from the group consisting of, for example, ethylene-vinyl acetate resin, urethane resin, vinyl chloride resin, and thermoplastic elastomer.

[0050] In one embodiment, the thermoplastic resin is preferably an ethylene-vinyl acetate-based resin and / or a thermoplastic elastomer. By using these thermoplastic resins as the material for the substrate layer, the flexibility of the simulated blood vessel is easily improved, and / or the softening point is easily lowered. Due to these characteristics, the simulated blood vessel becomes easier to reproduce the behavior of blood vessels in the 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 be compressed, similar to human blood vessels when the simulated blood vessel is squeezed with the tip of an energy device during medical procedure training, and thus hemostasis becomes easier. Additionally, the lower the softening point, the easier it is to hemostasis at low temperatures, similar to human blood vessels. Therefore, when the flexibility of the simulated blood vessel is high and / or the softening point is low, hemostasis becomes easier with fewer current passes.

[0051] In the present embodiment, the ethylene-vinyl acetate-based resin is a resin containing an ethylene-vinyl acetate copolymer. It may contain multiple types of ethylene-vinyl acetate copolymers. The ethylene-vinyl acetate copolymer is a copolymer of ethylene and vinyl acetate, but chlorinated ethylene, vinyl chloride, vinylidene fluoride, etc. may also be copolymerized. The vinyl acetate content of the ethylene-vinyl acetate-based resin is preferably 10 to 35 mass%, more preferably 15 to 35 mass%, and even more preferably 20 to 35 mass%. By making the vinyl acetate content 10 mass% or more, the flexibility of the simulated blood vessel is improved. In addition, by making the vinyl acetate content 35 mass% or less, the heat resistance of the resin composition is improved. By making the vinyl acetate content 20 mass% or more, the flexibility of the simulated blood vessel is likely to increase, and / or the softening temperature is likely to decrease.

[0052] As for urethane-based resins, as a combination of the raw material isocyanate and polyol, the isocyanate is MDI-based, H 12A combination of any one of the MDI, HDI, TDI, IPDI, NDI, XDI, H6XDI, NBDI, polyols, polyethers, polyesters, and polycarbonates may be selected, or multiple types may be combined. As for these urethane resins, thermoplastic polyurethanes are preferably used, and can be selected from those generally available on the market.

[0053] As the vinyl chloride-based resin, a vinyl chloride homopolymer or a copolymer of vinyl chloride and other comonomers may be used. When polyvinyl chloride is a copolymer, it may be a random copolymer or a graft copolymer. As an example of a graft copolymer, for instance, an ethylene-vinyl acetate copolymer or a thermoplastic urethane polymer may be used as the main chain polymer, and vinyl chloride may be graft polymerized thereon. The polyvinyl chloride of the present embodiment represents a soft polyvinyl chloride that is extrusion-moldable and is a composition containing additives such as a polymeric plasticizer. As for the polymeric plasticizer, known polymeric plasticizers may be used, but preferred examples include ethylene copolymer polymeric plasticizers such as an ethylene-vinyl acetate-carbon monoxide copolymer, an ethylene-(meth)acrylic acid ester-carbon monoxide copolymer, and an ethylene-vinyl acetate copolymer with a high vinyl acetate content.

[0054] Thermoplastic elastomers include those having a structure that combines a soft polymer material and a hard polymer material. Specifically, 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. Such elastomers can be selected from those generally available on the market.

[0055] In one embodiment, the thermoplastic elastomer is preferably a styrene-based elastomer, an olefin-based elastomer, and / or a polyester-based thermoplastic elastomer. By using a styrene-based elastomer, an olefin-based elastomer, and / or a polyester-based thermoplastic elastomer as the material of the substrate layer, the flexibility of the simulated blood vessel is easily improved, and / or the softening point is easily lowered. Due to these characteristics, the simulated blood vessel becomes easier to reproduce the behavior of blood vessels in the 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 be compressed, similar to human blood vessels when the simulated blood vessel is pinched with the tip of an energy device during medical procedure training, and thus hemostasis becomes easier. Additionally, the lower the softening point, the easier it is to stop bleeding at low temperatures, similar to human blood vessels. Therefore, when the flexibility of the simulated blood vessel is high and / or the softening point is low, hemostasis becomes easier with fewer current passes. The desirable range of the softening point of the simulated blood vessel is as described in "Properties of the simulated blood vessel" below.

[0056] (2) Conductive layer

[0057] In the case where the simulated blood vessel comprises a substrate layer and a conductive layer, the conductive layer is a layer disposed on at least a portion of the outer surface of the substrate layer and contains a conductive material.

[0058] 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-based materials such as silver, copper, tin oxide, zinc oxide, etc., carbon materials such as carbon black, carbon nanotubes, graphite, diamond-like carbon, etc. In one embodiment, the conductive material may be a conductive polymer or carbon nanotubes.

[0059] In the present embodiment, "arranged in at least a portion" means that the conductive layer is arranged to have an area required for use in a thermal coagulation method by 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 substrate layer, and may be 100%.

[0060] (2-1) Conductive polymer

[0061] In one embodiment, the conductive polymer is a π-conjugated conductive polymer. As for the π-conjugated conductive polymer, it is not particularly limited as long as it is an organic polymer in which the main chain is composed of a π-conjugated system. Examples include polythiophene-based conductive polymers, polypyrrole-based conductive polymers, polyacetylene-based conductive polymers, polyphenylene-based conductive polymers, polyphenylenevinylene-based conductive polymers, polyaniline-based conductive polymers, polyacene-based conductive polymers, polythiophenevinylene-based conductive polymers, and copolymers thereof. From the perspective of stability in air, polypyrrole-based conductive polymers, polythiophene-based conductive polymers, and polyaniline-based conductive polymers are preferred, and from the perspective of transparency, polythiophene-based conductive polymers are more preferred.

[0062] 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), poly(3-iodothiophene), 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-dodecyloxythiophene), 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-didodecyloxythiophene), Poly(3,4-ethylenedioxythiophene), Poly(3,4-propylenedioxythiophene), Poly(3,4-butylenedioxythiophene), Examples include 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).

[0063] 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).

[0064] Examples of polyaniline-based conductive polymers include polyaniline, poly(2-methylaniline), poly(3-isobutylaniline), poly(2-anilinesulfonic acid), and poly(3-anilinesulfonic acid).

[0065] Among the above π-conjugated conductive polymers, poly(3,4-ethylenedioxythiophene) is particularly preferred in terms of conductivity, transparency, and heat resistance.

[0066] The above π-conjugated conductive polymer may be used alone or in combination with two or more types.

[0067] In another embodiment, the conductive polymer further contains a polyanion.

[0068] A polyanion is a polymer having two or more monomer units having anionic groups within the molecule. The anionic groups of this polyanion function as dopants for π-conjugated conductive polymers, thereby improving the conductivity of π-conjugated conductive polymers.

[0069] It is preferable that the anionic group of the polyanion be a sulfo group or a carboxyl group.

[0070] Specific examples of such polyanions include polymers having sulfonic acid groups such as polystyrene sulfonic acid, polyvinyl sulfonic acid, polyallyl sulfonic acid, polyacryl sulfonic acid, polymethacryl sulfonic acid, poly(2-acrylamide-2-methylpropane sulfonic acid), polyisoprene sulfonic acid, polysulfoethyl methacrylate, poly(4-sulfobutyl methacrylate), and polymethacryloxybenzene sulfonic acid, or polymers having carboxylic acid groups such as polyvinyl carboxylic acid, polystyrene carboxylic acid, polyallyl carboxylic acid, polyacryl carboxylic acid, polymethacryl carboxylic acid, poly(2-acrylamide-2-methylpropane carboxylic acid), polyisoprene carboxylic acid, and polyacrylic acid. These may be homopolymers or copolymers of two or more types.

[0071] Among such polyanions, a polymer having a sulfonic acid group is preferred because it can provide higher antistatic properties, and polystyrene sulfonic acid is more preferred.

[0072] The above polyanions may be used as a single type or in combination of two or more types.

[0073] The weight average molecular weight of the polyanion is preferably 20,000 or more and 1,000,000 or less, and more preferably 100,000 or more and 500,000 or less.

[0074] The weight average molecular weight in this specification is a value obtained by measuring by gel permeation chromatography and using polystyrene as the standard material.

[0075] Among the conductive composites containing a π-conjugated conductive polymer and a polyanion, the content ratio of the polyanion is preferably in the range of 1 part by mass or more and 1,000 parts by mass or less per 100 parts by mass of the π-conjugated conductive polymer, more preferably in the range of 10 parts by mass or more and 700 parts by mass or less, and even more preferably in the range of 100 parts by mass or more and 500 parts by mass or less. If the content ratio of the polyanion is below the above lower limit, the doping effect on the π-conjugated conductive polymer tends to weaken, conductivity may be insufficient, and the dispersibility of the conductive composite in the dispersion is reduced. On the other hand, if the content of the polyanion exceeds the above upper limit, the content of the π-conjugated conductive polymer decreases, and it is also difficult to obtain sufficient conductivity.

[0076] The conductive composite is formed by coordinating and doping a polyanion into a π-conjugated conductive polymer.

[0077] However, in the polyanion of the present embodiment, not all anionic groups are doped into the π-conjugated conductive polymer, and there are residual anionic groups that do not contribute to doping.

[0078] (2-2) Carbon nanotubes

[0079] Carbon nanotubes may be single-layer carbon nanotubes (SWCNT) or multilayer carbon nanotubes (MWCNT), but single-layer carbon nanotubes are preferred. Single-layer carbon nanotubes are preferred because they exhibit high conductivity and / or transparency at low concentrations.

[0080] (2-3) Dispersion medium

[0081] In one embodiment, the conductive material may use, for example, water, an organic solvent, a mixture of water and an organic solvent, etc. as a dispersion medium in the dispersion liquid.

[0082] Examples of organic solvents include ester solvents, ether solvents, hydrocarbon solvents, nitrogen atom-containing solvents, alcohol solvents, ketone solvents, dimethyl sulfoxide, etc.

[0083] Examples of ester-based solvents include ethyl acetate, propyl acetate, butyl acetate, etc.

[0084] Examples of ether-based solvents include diethyl ether, dimethyl ether, ethylene glycol, propylene glycol, propylene glycol dialkyl ether, diethylene glycol diethyl ether, etc.

[0085] Examples of hydrocarbon solvents include hexane, cyclohexane, pentane, octane, decane, dodecane, benzene, toluene, xylene, ethylbenzene, propylbenzene, isopropylbenzene, etc.

[0086] Examples of nitrogen atom-containing solvents include N-methylpyrrolidone, dimethylacetamide, dimethylformamide, etc.

[0087] 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, glycerin, etc.

[0088] Examples of ketone-based solvents include diethyl ketone, methylpropyl ketone, methyl butyl ketone, methyl isopropyl ketone, methyl isobutyl ketone, methyl amyl ketone, diisopropyl ketone, methyl ethyl ketone, acetone, diacetone alcohol, etc.

[0089] The above organic solvent may be used as a single type, or two or more types may be used in combination.

[0090] Among the above dispersion media, at least one solvent selected from the group consisting of water, hydrocarbon solvents, ether solvents, nitrogen atom-containing solvents, and alcohol 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.

[0091] In the dispersion of the present embodiment, the content of the conductive material is preferably 0.05 mass% or more and 80 mass% or less with respect to the total mass of the dispersion, more preferably 0.1 mass% or more and 50 mass% or less, and even more preferably 0.2 mass% or more and 30 mass% or less. If the content of the conductive polymer in the dispersion is greater than or equal to the lower limit value above, a conductive layer with thickness can be easily formed in a single coating process. If the content of the conductive polymer in the dispersion is less than or equal to the upper limit value above, the dispersibility of the conductive material in the dispersion can be increased.

[0092] (2-4) Transparent binder component

[0093] In one embodiment, the dispersion contains a transparent binder component together with the conductive material. The transparent binder component is a thermoplastic resin, a thermosetting compound, a photocurable compound, etc., and examples include transparent compounds. The thermoplastic resin becomes the binder resin described below as is. The thermosetting compound and the photocurable compound are each monomers or oligomers, and the thermosetting compound becomes the binder resin described below by thermosetting, and the photocurable compound becomes the binder resin described below by photocuring.

[0094] If the dispersion contains a transparent binder component along with a conductive material, a conductive layer having transparency, conductivity, and anti-reflective properties can be easily formed.

[0095] Examples of transparent binder components include, for instance, 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, epoxy compounds having two or more epoxy groups, etc.

[0096] Examples of thermoplastic resins among the above 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, and cyclic polyolefins.

[0097] Examples of thermosetting compounds among the above transparent binder components include acrylic compounds and epoxy compounds.

[0098] Examples of photocurable compounds include acrylic compounds.

[0099] Among the above transparent binder components, a thermoplastic resin that has high transparency and is easy to process is preferred.

[0100] One type of transparent binder component may be used alone, or two or more types may be used in combination.

[0101] When the transparent binder component is a thermosetting compound, it is preferable to include a thermal polymerization initiator in the conductive particle dispersion, and when the transparent binder component is a photocurable compound, it is preferable to include a photopolymerization initiator in the dispersion.

[0102] In the dispersion of the present embodiment, the content of the transparent binder component is preferably 0.1 mass% or more and 20 mass% or less with respect to 100 mass% of the dispersion, more preferably 1 mass% or more and 15 mass% or less, and even more preferably 2 mass% or more and 10 mass% or less.

[0103] If the content of the transparent binder component in the conductive particle dispersion of the present embodiment is greater than or equal to the lower limit value, the strength of the conductive layer can be improved. If the content of the transparent binder component in the conductive particle dispersion of the present embodiment is less than or equal to the upper limit value, a decrease in conductivity due to a decrease in the content of the conductive composite can be prevented.

[0104] (Properties of simulated blood vessels)

[0105] In one embodiment, the surface resistance value of the conductive portion of the simulated blood vessel (the portion where the conductive layer is disposed) is 1.0 x 10 1 Ω ~ 1.0X10 6 It is Ω. The above surface resistance value is preferably 5.0X10 1 Ω ~ 1.0X10 3 Ω, more preferably 6.0X10 1 Ω ~ 1.0X10 3 It is Ω.

[0106] The surface resistance value of the conductive part of the simulated blood vessel is 1.0×10 1 Ω ~ 1.0X10 6 A mock ulcer with Ω can be prepared as described above by adjusting the arrangement and / or thickness of the conductive layer in the mock blood vessel, measuring the surface resistance value, and verifying whether it falls within the above range. For example, preferably 1.0×10 1 Ω ~ 1.0X10 6 Ω, more preferably 5.0X10 1 Ω ~ 1.0X10 3 Ω, more preferably 6.0X10 1 Ω ~ 1.0X10 3It can be prepared using a thermoplastic resin with Ω.

[0107] In this embodiment, the surface resistance value is a value measured using a resistivity meter (e.g., Loresta-GP (MCP-T610) manufactured by Nitto Seiko Analytech Co., Ltd.) under conditions of 23±1℃ and relative humidity of 50%RH with an applied voltage of 10V using an ASP probe.

[0108] In particular, the surface resistance value of the conductive part of the simulated blood vessel is 1.0×10 2 In higher cases, when a simulated organ is used for medical procedure training with an energy device, it becomes easier to reproduce the behavior of human blood vessels during current application by the energy device, and hemostasis becomes easier.

[0109] It is preferable that the mock blood vessel has a softening point of 200°C or lower, 100°C or lower, 30°C to 70°C, and even more preferable that it is 30°C to 60°C. By having a softening point of 200°C or lower, the mock blood vessel becomes easier to reproduce the behavior of human blood vessels by a thermal coagulation method using an energy device, that is, material deformation becomes easier. By having a softening point of 200°C or lower, hemostasis becomes easier at low temperatures. Therefore, by having a softening point of 200°C or lower, hemostasis becomes easier with fewer current passes.

[0110] A simulated blood vessel with a softening point of 200°C or lower can be prepared by adjusting the type and / or formulation of the thermoplastic resin, measuring the softening point, and confirming whether it falls within the above range. For example, it can be prepared using a thermoplastic resin that preferably has a softening point of 200°C or lower, more preferably 100°C or lower, more preferably 3070°C, and even more preferably 3060°C.

[0111] In this embodiment, the softening point of the simulated blood vessel is measured in accordance with JIS K 7206.

[0112] It is preferable that the mock blood vessel has a melting point of 50 to 200°C. In one embodiment, the melting point of the mock blood vessel may be 50 to 150°C, or 50 to 120°C.

[0113] By having a melting point of 50 to 200°C, it is possible to suppress changes in the shape of the simulated blood vessel due to temperature influences, and / or the material deformation of the simulated blood vessel by thermal coagulation using an energy device becomes as easy as that of human blood vessels.

[0114] A simulated blood vessel with a melting point of 50 to 200°C can be prepared by adjusting the type and / or formulation of the thermoplastic resin, measuring the melting point, and confirming whether it falls within the above range. For example, it can be prepared using a thermoplastic resin that preferably has a melting point of 50 to 200°C, more preferably 50 to 150°C, and even more preferably 50 to 120°C.

[0115] 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+) under a nitrogen atmosphere at a heating rate of 10℃ / min.

[0116] In one embodiment, the water contact angle on the surface of the substrate layer of the simulated blood vessel is 45° or less. In another embodiment, the water contact angle on the surface of the substrate layer is preferably 30° or less, and more preferably 20° or less. By making the water contact angle on the surface of the substrate layer 45° or less, the occurrence of defects such as bounce or pinholes, or detachment from the substrate layer, of the coating composition forming the conductive layer containing the π-conjugated conductive polymer component is suppressed.

[0117] In accordance with JIS K 6768, 1 μL of water (pure water) was dropped onto the surface of the primer layer using the automatic contact angle measuring device OCA20 manufactured by Eiko Seiki Co., Ltd., and the contact angle measured after 30 seconds was defined as the contact angle in this embodiment. In addition, the contact angle can be measured using a sample processed into a resin sheet with a thickness of 1.0 mm, which is press-molded at 160 to 200°C from the thermoplastic resin composition that is the material of the substrate layer.

[0118] (Method for manufacturing mock blood vessels)

[0119] A substrate layer can be manufactured by extruding a thermoplastic resin or a thermoplastic resin composition. In another embodiment, the substrate layer can be manufactured by molding, injection molding, or compression molding.

[0120] A simulated blood vessel having a conductive layer disposed on the surface of a substrate layer is manufactured by immersing the substrate layer in a dispersion in which a conductive polymer is dispersed in a dispersion medium.

[0121] In another embodiment, it may be manufactured by coating a conductive polymer dispersion on the outer surface of the substrate layer.

[0122] Before coating with the conductive polymer dispersion, the substrate layer may be subjected to corona discharge treatment, plasma discharge treatment, flame treatment, etc., to form hydrophilic groups (hydroxyl groups, carbonyl groups, etc.) on the surface of the substrate layer. If the substrate layer is hydrophilized, the adhesion of the conductive layer can be further improved.

[0123] Mock ulcer

[0124] In one embodiment, the mock ulcer comprises a conductive material. The conductive material is, for example, a conductive gel.

[0125] In one embodiment, the conductive gel may be a conductive resin composition or other conductive gel as exemplified in "Example 3" below.

[0126] (Composition of a mock ulcer)

[0127] In this specification, the term "ulcer" includes tissues containing a site (ulcer) requiring treatment in the body of an animal, and non-limiting examples of such tissues include at least some tissues among organs such as the digestive system, urinary system, reproductive system, and respiratory system. Here, examples of the digestive system include the oral cavity, pharynx, esophagus, stomach, duodenum, small intestine, large intestine, rectum, anus, etc.; examples of the urinary system include the ureter, bladder, urethra, etc.; examples of the reproductive system include the fallopian tube, uterus, vagina, vas deferens, penis, urethra, etc.; and examples of the respiratory system include the nasal cavity, trachea, bronchi, etc., but are not limited thereto.

[0128] A mock ulcer is a molded product that mimics tissue and / or organ containing a site (ulcer) that requires treatment.

[0129] Mock ulcers may be colored to a color similar to that of living tissues and organs.

[0130] (Composition of mock ulcer)

[0131] 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 may be preferably 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, etc. contain any chloride to provide conductivity when a simulated organ is used for medical procedure training with an energy device.

[0132] The tensile breaking elongation of the conductive gel is preferably 50 to 4000%, more preferably 100 to 4000%, and even more preferably 300 to 4000%. By setting the tensile breaking elongation to 50 to 4000%, a soft texture similar to that of an actual organ can be achieved.

[0133] The tensile fracture elongation can be obtained by measuring the fracture point elongation when a conductive gel, adjusted to a thickness of 1 mm, a width of 10 mm, and a length of 80 mm, is fixed with a chuck gap of 20 mm using a tensile testing machine manufactured by Shimadzu Corporation (model number: AUTOGRAPH AG-X plus) and subjected to a tensile test at a tensile speed of 50 mm / min at 23±2℃.

[0134] The above measurement method is based on JIS K 7161-1:2014 with the sample size and other factors modified.

[0135] 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 overlapping sample sheets of the conductive gel with a thickness of 5.0 mm and under conditions of 23±1℃ in accordance with the durometer hardness test method for plastics of JIS K7215.

[0136] In addition, the conductive gel may be formulated with other resins, elastomers, rubber, plasticizers, fillers or stabilizers, anti-aging agents, light resistance enhancers, UV absorbers, softeners, lubricants, processing aids, colorants, anti-fogging agents, anti-blocking agents, crystallization nucleating agents, foaming agents, etc., as needed. To manufacture the conductive gel, a known suitable blending method may be used. For example, melt mixing can be performed using a heated stirrer, a single-screw or twin-screw extruder, a Banbury-type mixer, a Plastomill, a Conider, a heated roll, etc. Before mixing, each raw material may be uniformly mixed using a Henschel mixer, a ribbon blender, a Super mixer, a tumbler, etc. Although there are no particular restrictions on the melt mixing temperature, it is generally 100 to 300°C, preferably 150 to 250°C. As molding methods for various compositions, known molding methods such as mold forming, vacuum forming, injection molding, blow molding, and extrusion molding may be used.

[0137] (Example 1 of conductive gel (conductive resin composition))

[0138] In one embodiment, the conductive resin composition contains 100 parts by mass of component (A) a hydrogenated styrene-based thermoplastic elastomer and 100 to 1000 parts by mass of component (B) an oil, additionally 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.

[0139] ( Component (A): Hydrogenated styrene-based thermoplastic elastomer)

[0140] In one embodiment, the hydrogenated styrene-based thermoplastic elastomer is a hydrogenated aromatic vinyl-conjugated diene block copolymer composed of a block polymerization unit (X) derived from aromatic vinyl and a block polymerization unit (Y) derived from conjugated diene.

[0141] The form of an aromatic vinyl-conjugated diene block copolymer with such a composition is, for example, X(YX) n or (XY) n It is represented as [n is an integer greater than or equal to 1]. Among these, X(YX) n A type of XYX form is preferred, particularly an XYX form. As for the XYX form, one or more copolymers selected from the group consisting of polystyrene-polybutadiene-polystyrene block copolymer, polystyrene-polyisoprene-polystyrene block copolymer, and polystyrene-polyisoprene·butadiene-polystyrene block copolymer are preferred.

[0142] In such an aromatic vinyl-conjugated diene block copolymer, the aromatic vinyl block unit (X), which is a hard segment, exists as a crosslinking point for the conjugated diene rubber block unit (Y) to form a pseudo-crosslink (domain). The conjugated diene rubber block unit (Y) existing between these aromatic vinyl block units (X) is a soft segment and has rubber elasticity.

[0143] Examples of aromatic vinyls forming block polymerization 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.

[0144] Examples of conjugated dienes forming a block polymerization unit (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 (copolymerization of butadiene and isoprene) are preferred. One or more conjugated dienes among these may also be used in combination. The conjugated diene block polymerization unit (Y) formed by a butadiene and isoprene copolymerization unit may be any one of a random copolymerization unit, a block copolymerization unit, or a tapered copolymerization unit of butadiene and isoprene.

[0145] In the aromatic vinyl-conjugated diene block copolymer as described above, it is preferable that the content of the aromatic vinyl block polymerization unit (X) be 5 mass% or more and 50 mass% or less, and more preferable that it be 20 mass% or more and 40 mass% or less. The content of the aromatic vinyl unit can be measured by conventional methods such as infrared spectroscopy and NMR spectroscopy.

[0146] In one embodiment, the melt flow rate (MFR) (temperature 230°C, load 2.16 kg) of component (A) 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 under conditions of a temperature of 230°C and a load of 2.16 kg in accordance with JIS K7210. By making the MFR 1 g / 10 min or less, it is easy to bleed out when oil is added, and the decrease in mechanical strength can be suppressed. The MFR can be measured, for example, in accordance with JIS K7210.

[0147] The aromatic vinyl-conjugated diene block copolymer described above can be manufactured by various methods. Examples of manufacturing methods include: (1) a method of sequentially polymerizing an aromatic vinyl followed by a conjugated diene using an alkyl lithium compound such as n-butyllithium as an initiator; (2) a method of polymerizing an aromatic vinyl followed by a conjugated diene using an alkyl lithium compound as an initiator and coupling the results with a coupling agent; and (3) a method of sequentially polymerizing a conjugated diene followed by an aromatic vinyl using a lithium compound as an initiator.

[0148] It is preferable that the hydrogenated styrene-based thermoplastic elastomer be obtained by hydrogenating an aromatic vinyl-conjugated diene block copolymer as described above by a known method, and the hydrogenation rate is 90 mol% or more. This hydrogenation rate is the value when the total amount of carbon-carbon double bonds in the conjugated diene block polymerization unit (Y) is 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 specifically, examples include SEPTON (manufactured by Kuraray Corporation), Kraton (manufactured by Shell Chemicals Corporation), Kraton G (manufactured by Shell Chemicals Corporation), and Toughtec (manufactured by Asahi Kasei Corporation) (all product names).

[0149] The hydrogenation rate is measured by known methods such as nuclear magnetic resonance (NMR) spectral analysis.

[0150] SEEPS is preferred as a hydrogenated styrene-based thermoplastic elastomer. The shape of the hydrogenated styrene-based thermoplastic elastomer is preferred to be powder or amorphous (crumb) form from the perspective of oil absorption before mixing.

[0151] ( Ingredient (B): Oil)

[0152] Examples of oils are not particularly limited but include paraffinic process oils, naphthenic process oils, aromatic process oils, mineral oils such as liquid paraffin, silicone oils, castor oil, linseed oil, olefinic waxes, and mineral waxes. Among these, paraffinic and / or naphthenic process oils 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 Co., Ltd.).

[0153] Oils are used, for example, to soften resin compositions and to adjust the elastic modulus or hardness of simulated organs. One or more of the above oils may also be used in combination.

[0154] It is desirable to pre-absorb oil into the hydrogenated styrene-based thermoplastic elastomer for workability.

[0155] The oil content is preferably 100 to 1000 parts by mass per 100 parts by mass of component (A), 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. The oil content is adjusted within the above range according to the actual model organ and lesion. By making the oil content 100 parts by mass or more per 100 parts by mass of component (A), the lack of softness is suppressed, and by making it 1000 parts by mass or less, the hydrogenated styrene-based thermoplastic elastomer is prevented from failing to sufficiently absorb oil and thus unable to form a compound.

[0156] ( Component (C): Polymer antistatic agent)

[0157] In one embodiment, the polymer antistatic agent is not particularly limited, but preferably refers to a copolymer of a hydrophobic polymer and a hydrophilic polymer, and more preferably refers to a copolymer having one or more hydrophobic polymer blocks and one or more hydrophilic polymer blocks. Hydrophilicity means having a functional group or polarity that forms hydrogen bonds between molecules, and hydrophobicity means being non-hydrophilic. Here, the bonding method of each block may be a block copolymer in which a hydrophobic polymer block and a hydrophilic polymer block are connected linearly, or a graft copolymer in which a graft chain is connected as a branched chain to one of the polymer chains, but a block copolymer is more preferred.

[0158] More specifically, examples include polyethers that are block copolymerized with hydrophilic groups (nonionic types such as polyetheresteramides, ethylene oxide-epichlorohydrins, and polyetheresters; anionic types such as polystyrenesulfonic acids; cationic types such as quaternary ammonium-containing poly(meth)acrylates, etc.). Among these, a diblock copolymer having a structure in which a polyethylene glycol block and a polypropylene glycol block, or a polyether block and a polyolefin block are bonded through at least one type of bond selected from ester bonds, amide bonds, ether bonds, urethane bonds, and imide bonds, or a block copolymer having a structure in which they are repeatedly alternately bonded, may be used, and as an example thereof, a volume resistivity of 10 5 ~ 10 11 Examples include block copolymers having a structure in which polyether blocks and polyolefin blocks, which are hydrophilic blocks with an Ω·cm ratio, are repeatedly and alternately bonded. It is preferable that the number average molecular weight (Mn) of the block copolymer be 500 to 60,000.

[0159] In addition, commercially available copolymers include, for example, Sanyo Chemical Industry's product names "Pellestat (registered trademark)", "Pellestat 300", "Pellestat 230", "Pellestat NC6321", "Pellestat NC6322", "Pellestat NC7350", "Pellestat HC250", etc.), "Peletron (registered trademark)", "Peletron PVH", "Peletron PVL", "Peletron HS", "Peletron LMP-FS", etc.), Sanko Chemical Industry's product names "Sankonol (registered trademark)", "Sankonol TBX-65", etc.), Mitsui-DuPont's product name "Entira (registered trademark) AS", Arkema's product name "Pebax (registered trademark)", Lubrizol's product name "Statrite (registered trademark)", Examples include "IonPhasE (registered trademark) IPE (registered trademark) U2" manufactured by IonPhasE, "Pluronic (registered trademark) L-31" and "Pluronic (registered trademark) L-41" manufactured by ADEKA Co., Ltd., and "Alcox (registered trademark) EP1010N" and "Alcox (registered trademark) CP-A1H" manufactured by Meisei Chemical Industry Co., Ltd., and these may be used individually or in combination.

[0160] In addition, polyolefin blocks, polyisobutylene blocks, and volume resistivity of 1.0×10 5 ~ 1.0X10 11 A block polymer in which a hydrophilic polymer block with an Ω·cm length is bonded through at least one type of bond selected from the group consisting of ester bonds, amide bonds, ether bonds, imide bonds, and urethane bonds can be used as the copolymer of the present embodiment.

[0161] In addition, a block polymer or polyolefin block having a hydrophobic polymer block not having polyethers, a hydrophilic polymer block, and an aromatic ring-containing hydrophobic polyether block as constituent units, and a volume resistivity of 10 5 ~ 10 11A block polymer characterized by having a structure in which hydrophilic polymer blocks with a length of Ω·cm are repeatedly and alternately bonded, or a block polymer having at least one hydrophobic polymer block selected from the group consisting of polyamide, polyolefin, and polyamideimide, a hydrophilic polymer block, and an aromatic ring-containing hydrophobic polyether block as constituent units, may also be used.

[0162] The number average molecular weight (Mn) and weight average molecular weight (Mw) of the copolymer can be measured using gel permeation chromatography (GPC) with polystyrene as a reference material.

[0163] The content of the polymer antistatic agent is preferably 5 parts by mass or more and less than 100 parts by mass per 100 parts by mass of component (A), more preferably 8 parts by mass or more and less than 80 parts by mass, and even more preferably 10 parts by mass or more and less than 60 parts by mass. The content of the polymer antistatic agent contributes to the volume resistivity and tensile fracture elongation.

[0164] ( Component (D): Ionic liquid)

[0165] Examples of ionic liquids include those composed of cations and anions, although they are not particularly limited. In one embodiment, the ionic liquid does not contain a solvent such as water or ethylene glycol.

[0166] Examples of cations include amidinium cations, pyridinium cations, pyrazolium cations, and guanidinium cations.

[0167] Examples of amidinium cations include imidazolinium cation, imidazolium cation, tetrahydropyrimidinium cation, dihydropyrimidinium cation, etc.

[0168] As imidazolinium cations, 1,2,3,4-tetramethylimidazolinium cation, 1,3,4-trimethyl-2-ethylimidazolinium cation, 1,3-dimethylimidazolinium cation, 1,3-dimethyl-2,4-diethylimidazolinium cation, 1,2-dimethyl-3,4-diethylimidazolinium cation, 1-methyl-2,3,4-triethylimidazolinium cation, 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, Examples include 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.

[0169] 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-ethylimidazolium 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-dimethylimidazolium cation, 4-cyano-1,2,3-trimethylimidazolium cation, 3-Cyanomethyl-1,2-Dimethylimidazolium cation, 2-Cyanomethyl-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 Examples include cations, 4-hydroxymethyl-1,2,3-trimethylimidazolium cations and 2-hydroxyethyl-1,3-dimethylimidazolium cations.

[0170] As tetrahydropyrimidinium cations, 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, Examples include 3-methoxymethyl-1,2-dimethyl-1,4,5,6-tetrahydropyrimidinium cation, 4-formyl-1,2,3-trimethyl-1,4,5,6-tetrahydropyrimidinium cation, 3-formylmethyl-1,2-dimethyl-1,4,5,6-tetrahydropyrimidinium cation, 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.

[0171] As dihydropyrimidinium cations, 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, and 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, 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 Examples include cations, 3-hydroxyethyl-1,2-dimethyl-1,6-dihydropyrimidinium cations, 4-hydroxymethyl-1,2,3-trimethyl-1,4-dihydropyrimidinium cations, and 2-hydroxyethyl-1,3-dimethyl-1,4-hydropyrimidinium cations.

[0172] Examples of pyridinium cations include 3-methyl-1-propylpyridinium cation, 1-propyl-3-methylpyridinium cation, 1-butyl-3-methylpyridinium cation, 1-butyl-4-methylpyridinium cation, 1-butyl-3,4-dimethylpyridinium cation, and 1-butyl-3,5-dimethylpyridinium cation.

[0173] Examples of pyrazolium cations include 1,2-dimethylpyrazolium cation, 1-methyl-2-propylpyrazolium cation, 1-n-butyl-2-methylpyrazolium cation, and 1-n-butyl-2-ethylpyrazolium cation.

[0174] Examples of guanidinium cations include guanidinium cations having an imidazolinium skeleton, guanidinium cations having an imidazolinium skeleton, guanidinium cations having a tetrahydropyrimidinium skeleton, and guanidinium cations having a dihydropyrimidinium skeleton.

[0175] 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, 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-1,3-dimethylimidazolinium cation, 2-dimethylamino-3-formylmethyl-1-methylimidazolinium cation, 2-dimethylamino-3-hydroxyethyl-1-methylimidazolinium cation and Examples include 2-dimethylamino-4-hydroxymethyl-1,3-dimethylimidazolinium cations.

[0176] 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-dimethylamino-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 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, Examples include 2-dimethylamino-3-acetylmethyl-1-methylimidazolium cation, 2-dimethylamino-4-methylcarboxymethyl-1,3-dimethylimidazolium cation, 2-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.

[0177] 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-diethylamino-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-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,Examples include 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.

[0178] 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, 2-diethylamino-1-methyl-3,4-diethyl-1,4-dihydropyrimidinium cation, 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 cation, 1,6-dihydro-1,2-dimethyl-2H-imido[1,2a]pyrimidinium cation, 1,6,7,8-tetrahydro-1,2-dimethyl-2H-pyrimidido[1,2a]pyrimidinium cation, 1,6-dihydro-1,2-dimethyl-2H-pyrimidido[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-1,4-dihydropyrimidinium cation, 2-dimethylamino-4-formyl-1,3-dimethyl-1,4,5,Examples include 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.

[0179] Examples of anions include anions obtained by removing a proton from an acid, as exemplified below. Anions may be a mixture of two or more types.

[0180] Carboxylic acids can be used as anions, specifically 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, and behenic acid, etc.), carboxylic acids containing fluorine atoms (trifluoroacetic acid, etc.) and unsaturated monocarboxylic acids (acrylic acid, methacrylic acid, and oleic acid, etc.)] and aromatic monocarboxylic acids (benzoic acid, cinnamic acid, and naphthoic acid, etc.)}, polycarboxylic acids (2 to 4-valent polycarboxylic acids) {aliphatic polycarboxylic acids [saturated polycarboxylic acids (oxalic acid, malonic acid, succinic acid, glutaric acid, adipic acid, pimelic acid, Suberic acid, azelaic acid, and sebacic acid, etc.); unsaturated polycarboxylic acids (maleic acid, fumaric acid, and itaconic acid, etc.); aromatic polycarboxylic acids [phthalic acid, isophthalic acid, terephthalic acid, trimellitic acid, and pyromellitic acid, etc.]; aliphatic oxycarboxylic acids [glycolic acid, lactic acid, and tartaric acid, etc.]; aromatic oxycarboxylic acids [salicylic acid and 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]hepta-2-en-2,3-dicarboxylic acid and bicyclo[2,2,1]hepta-2,5-diene-2,3-dicarboxylic acid], etc. can be mentioned.

[0181] Sulfonic acids can be used as anions, specifically alkanesulfonic acids having 1 to 30 carbon atoms (methanesulfonic acid, ethanesulfonic acid, butanesulfonic acid, octanesulfonic acid, and dodecanesulfonic acid, etc.); and alkylbenzenesulfonic acids having 7 to 30 carbon atoms (octylbenzenesulfonic acid and dodecylbenzenesulfonic acid, etc.).

[0182] Inorganic acids can be used as anions, specifically hydrofluoric acid, hydrochloric acid, sulfuric acid, phosphoric acid, HClO4, HBF4, HPF6, HAsF6, and HSbF6.

[0183] As an anion, a halogen atom-containing alkyl group-substituted inorganic acid (alkyl group having 1 to 30 carbon atoms) can be used, and specifically, HBF n (CF3) 4-n (n is an integer from 0 to 3), HPF n (CF3) 6-n (n is an integer from 0 to 5), examples include 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.

[0184] As an anion, sulfonylimides containing halogen atoms (1 to 30 carbon atoms) can be used, specifically, bis(fluoromethylsulfonyl)imide, bis(trifluoromethanesulfonyl)imide, and bis(fluorosulfonyl)imide.

[0185] As an anion, sulfonylmethanes containing halogen atoms (3 to 30 carbon atoms) can be used, specifically tris(trifluoromethylsulfonylmethane) and the like.

[0186] Halogen-containing carboxylic acid amides (2 to 30 carbon atoms) can be used as anions, and specifically, examples include bis(trifluoroaceto)amide.

[0187] Nitrile-containing imides can be used as anions, specifically HN(CN)2, etc.

[0188] Nitrile-containing methanes can be used as anions, specifically HC(CN)3, etc.

[0189] Alkylenes containing halogen atoms having 1 to 30 carbon atoms can be used as anions, specifically HN(CF3)2, etc.

[0190] Cyanic acid can be used as an anion, specifically thiocyanic acid, etc.

[0191] In addition, commercially available ionic liquids may be used. Examples of commercially available ionic liquids include CIL312 (N-butyl-3-methylpyridinium bistrifluoromethanesulfonylimide, manufactured by Japan Carit Co.), Aminoion AS100 (manufactured by Japan Emulsifier Co.), Aminoion AS300 (manufactured by Japan Emulsifier Co.), FC-4400 (tri-n-butylmethylammonium bistrifluoromethanesulfonimide, manufactured by 3M), and Hisycholine (dodecyl tributylphosphonium chloride, manufactured by Japan Chemical Industry Co.).

[0192] The synthesis method for ionic liquids is not particularly limited as long as the desired ionic liquid can be obtained, but examples include the halide method, hydroxide method, acid ester method, complex formation method, and neutralization method described in “Ionic Liquids - The Cutting Edge and Future of Development -” [Hiroyuki Ono, published in 2003, CMC Publishing].

[0193] The content of the ionic liquid is preferably 50 to 250 parts by mass per 100 parts by mass of component (A), more preferably 50 to 240 parts by mass, and even more preferably 70 to 210 parts by mass. The content of the ionic liquid contributes to the tensile fracture elongation, and by making the content of the ionic liquid 50 parts by mass or more per 100 parts by mass of component (A), it contributes to suppressing the increase in volume resistivity, and by making it 250 parts by mass or less, it is possible to suppress the ion liquid from the material from bleeding out.

[0194] ( Mass ratio of component (D) to component (C)

[0195] 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 making the mass ratio of component (D) to component (C) 2.7 or higher, the increase in volume resistivity can be suppressed, and by making it 10 or lower, the decrease in tensile fracture elongation can be suppressed.

[0196] (Example 2 of conductive gel (resin composition))

[0197] In one embodiment, the conductive resin composition comprises a polyvinyl alcohol-based resin. In this case, in one embodiment, the conductive resin composition comprises a 2 to 10 mass% aqueous solution of a polyvinyl alcohol-based resin (A) and an organic titanium compound (B). The mass ratio of component (A) to component (B) is 70:30 to 90:10.

[0198] In one embodiment, the conductive resin composition preferably comprises a 5 to 10 mass% aqueous solution of component (A) a polyvinyl alcohol-based resin and a component (B) an organic titanium compound. It is preferable that the mass ratio of component (A) to component (B) is 70:30 to 90:10.

[0199] In one embodiment, the conductive resin composition preferably comprises a 5 to 10 mass% aqueous solution of component (A) a polyvinyl alcohol-based resin and a component (B) an organic titanium compound. It is more preferable that the mass ratio of component (A) to component (B) is 80:20 to 90:10.

[0200] In one embodiment, the conductive resin composition preferably comprises a 5 mass% aqueous solution of component (A) a polyvinyl alcohol-based resin and a component (B) an organic titanium compound. It is more preferable that the mass ratio of component (A) to component (B) is 85:15.

[0201] It comprises a 2 to 10 mass% aqueous solution of a polyvinyl alcohol-based resin (A) and an organic titanium compound (B). By having a mass ratio of component (A) to component (B) of 70:30 to 90:10, it is easy to obtain a gel.

[0202] In addition, by including a 5 mass% aqueous solution of component (A) a polyvinyl alcohol-based resin and component (B) an organic titanium compound, and / or by the mass ratio of component (A) to component (B) being 85:15, it is easy to obtain a flexible gel.

[0203] ( Component (A): Aqueous solution of polyvinyl alcohol-based resin)

[0204] Polyvinyl alcohol-based resins may be, for example, polyvinyl alcohol resins or modified polyvinyl alcohol resins. Examples of modified polyvinyl alcohol include those obtained by saponifying a copolymer of a vinyl ester monomer and a monomer copolymerizable therewith, or those obtained by modifying unmodified polyvinyl alcohol, such as acetoacetyl-modified PVA. Among the polyvinyl alcohol-based resin materials described above, it is preferable to use polyvinyl alcohol resin.

[0205] The lower limit of the average degree of polymerization of the polyvinyl alcohol-based resin is preferably 1000, more preferably 1300, and even more preferably 1600. Meanwhile, the upper limit of the average degree of polymerization of the polyvinyl alcohol-based resin is preferably 4000, and more preferably 3300. The average degree of polymerization 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 degree of polymerization is a value obtained by the method specified in JIS K 6726 (1994). By making the average degree of polymerization of the polyvinyl alcohol-based resin 1000 or higher, desirable strength and orientation can be obtained. Meanwhile, by making the average degree of polymerization of the polyvinyl alcohol-based resin 4000 or less, the solubility in water is sufficient, and the formation of a resin layer containing the polyvinyl alcohol-based resin can be facilitated.

[0206] The lower limit of the degree of saponification of the polyvinyl alcohol resin is preferably 70 mol%, more preferably 80 mol%, and even more preferably 85 mol%. Meanwhile, the upper limit of the degree of saponification of the polyvinyl alcohol resin is preferably 100 mol%, more preferably 95 mol%, and even more preferably 90 mol%. The degree of saponification 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%.

[0207] (Component (B): Organic titanium compound)

[0208] The organotitanium compound is not limited to any specific type and may be a crosslinking agent that reacts with hydroxyl or carboxyl groups. Additionally, it is desirable that the organotitanium compound be water-soluble, not undergo any degradation due to dissociation or other factors in water, and not lose its reactivity in aqueous solution.

[0209] The organic titanium compound used preferably has at least one ligand selected from triethanolamine, acetylacetone, citric acid, lactic acid, malic acid, tartaric acid, and glycolic acid, and also has at least two ligands coordinated per titanium atom.

[0210] Specific examples of organic titanium compounds are preferably selected from titanium lactate (including titanium lactate ammonium salt), diisopropoxytitanium bis(triethanol aminate), and titanium peroxocitrate.

[0211] (Example of conductive gel 3)

[0212] In one embodiment, the conductive gel may be a gel comprising konjac, agar, gelatin, carrageenan and / or cellulose derivatives, etc.

[0213] Konjac, agar, gelatin, carrageenan, cellulose derivatives, etc., as conductive materials included in this embodiment can be gelled by processing these materials according to methods known to those skilled in the art.

[0214] For example, konjac can be produced by grating the main ingredient, konjac potato, with a grater or mixer, mixing in a coagulant, molding, and boiling in hot water to make gelled konjac.

[0215] In addition, for example, agar can be produced by using seaweed of the family Gracilaria and red algae as the main raw materials, filtering the boiled solution in a paste state by boiling it in hot water, and then solidifying it at about 40°C or lower.

[0216] For example, gelatin can be produced by pre-treating main raw materials such as cow bones, cowhide, or pigskin with an inorganic acid or lime, then heat-treating to extract the gelatin liquid, filtering it, and gelling it by cooling. Alternatively, the gelatin liquid can be obtained by undergoing extraction, concentration, and drying processes to produce a dried powder, and then gelling it again.

[0217] The gel preferably has a water content of 20 to 98 mass%, more preferably 25 to 80 mass%, and even more preferably 30 to 70 mass%.

[0218] It is preferable that the gel contains a chloride. The chloride may be, for example, NaCl, CaCl2, FeCl3, or a combination thereof.

[0219] The chloride content relative to the total weight of the gel is preferably in the range of 0.5 to 10 weight%, and more preferably in the range of 1 to 10 weight%. This is because if the amount of metal chloride is excessive, chloride crystals are likely to form.

[0220] (Properties of a mock ulcer)

[0221] The simulated ulcer corresponds to energy devices used for medical skills training, has excellent preservation, and can realize a texture similar to that of a real organ.

[0222] The volume resistivity of the conductive portion of the mock ulcer is preferably 1.0 x 10 2 ~ 1.0X10 7 It is Ω·cm, and more preferably 1.0×10 2 Ω·cm or more 1X10 7 Less than Ω·cm, and more preferably 1.0×10 2 ~ 1.0X10 6 It is Ω·cm, and more preferably 1.0×10 2 ~ 5.0X10 5 It is Ω·cm.

[0223] In particular, the volume resistivity is 1.0×10 7 By making it Ω·cm or less, when a simulated organ is used for medical procedure training with an energy device, it becomes easier to reproduce the behavior of an ulcer in vivo and easier to perform incision procedures.

[0224] The volume resistivity of the conductive part is 1.0 x 10 2 ~ 1.0X10 7 A mock ulcer with a value of Ω·cm can be prepared by adjusting the type and / or composition of the conductive material as described above, measuring the volume resistivity, and verifying whether it falls within the above range. For example, preferably 1.0×10 2 ~ 1.0X10 7 Ω·cm, more preferably 1.0×10 2 Ω·cm or more 1.0×10⁻⁶ 7 Less than Ω·cm, and more preferably 1.0×10 2 ~ 1.0X10 6 Ω·cm, more preferably 1.0×10 2 ~ 5.0X10 5 It can be prepared using a conductive material with a conductivity of Ω·cm.

[0225] As described in the "Simulated Organ" below, it is preferable that the softening point of the simulated ulcer be a temperature higher than the softening point 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 less than 30°C.

[0226] A mock ulcer with 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 verifying whether it falls within the above range. For example, it can be prepared using a conductive material with a softening point of 200°C or lower, 100°C or lower, 30°C, or less than 30°C.

[0227] In this embodiment, the softening point of the mock ulcer is determined by measuring the temperature when the indenter penetrates 30% of the thickness of the test specimen using a TA Instruments viscoelasticity measuring device RSA-G2, with a heating rate of 5℃ / min, an indenter diameter of 10 mm, and an indentation load of 1.0 N, on a test specimen of a conductive resin composition adjusted to a diameter of 30 mm and a thickness of 2 mm.

[0228] As described in the "Simulated Organ" below, it is preferable that the melting point of the simulated ulcer be 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.

[0229] A mock 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 verifying whether it falls within the above range. For example, it can be prepared using a conductive material with a temperature of 50 to 200°C, 50 to 150°C, more preferably 50 to 120°C, or less than 50°C.

[0230] In this embodiment, the melting point of the mock ulcer is measured by the method described in "mock blood vessel".

[0231] (Method for manufacturing a mock ulcer)

[0232] The shape of the simulated ulcer may have any shape selected from, for example, circular, elliptical, polygonal, or irregular.

[0233] A mock ulcer can be formed by known molding methods, and it can be formed integrally or divided. For example, when removing the inner die, an incision may be made in the resin molded body and the inner die may be removed through it, such as when using an inner die (core) and an outer die and molding material into the space between them. In this case, the incision may be bonded to complete the mock ulcer. Additionally, a mock ulcer may be formed using a male die and a female die, such as by heat press molding or vacuum press molding, or a mock ulcer may be completed by separately molding multiple tissue parts, such as by injection molding, and then bonding them together.

[0234] The mock ulcer may be colored using additives such as coloring agents (e.g., pigments, dyes), fragrances, antioxidants, and antimicrobial agents, to the extent that the purpose is not compromised. In order to approximate the mock ulcer to the tissue of the living organism, it is desirable to color it with a color similar to that of the organ of the living organism using a coloring agent.

[0235] <Mock mucus composition>

[0236] The mock mucus composition is a composition for covering at least a portion of the outer surface of a mock organ, in one embodiment, in a mock organ comprising the mock blood vessel and mock ulcer.

[0237] (Composition of the simulated mucus composition)

[0238] In one embodiment, the simulated mucus composition has a volume resistivity of 1.0 to 1.0 x 10 6 It is Ω·cm. Within this range, the components and composition are not limited.

[0239] Examples of components include, for instance, water, sodium chloride, magnesium chloride, potassium chloride, sodium hydroxide, sodium dihydrogen phosphate, sodium phosphate, glycerin, propylene glycol, methyl parahydroxybenzoate, ethyl parahydroxybenzoate, propyl parahydroxybenzoate, butyl parahydroxybenzoate, low molecular weight compounds, hydrogenated castor oil, absorbent polymers such as 12-hydroxystearic acid, gluconodelta lactone, sodium polyacrylate, 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), water-soluble polymers such as hypromellose, methylcellulose, polyacrylic acid, polymethacrylic acid, and hydroxyethylcellulose, and may include one or more of these. In addition, the mock mucus composition may further include one or more electrolytes, carbon nanomaterials, conductive polymers, conductive materials such as metal fillers, preservatives, fragrances, dyes, narcotic ingredients, pH adjusters, dispersants, thickeners (including thixotropic agents, anti-settling agents, and anti-sagging agents), surfactants, antioxidants, etc.

[0240] As a more specific example, the mock mucus composition may be an aqueous sodium chloride solution, a glycerin solution, an aqueous sodium polyacrylate solution, or distilled water.

[0241] In one embodiment, the simulated mucus composition is preferably an aqueous sodium chloride solution, a glycerin solution, and an aqueous sodium polyacrylate solution. Since the simulated mucus composition is an aqueous sodium chloride solution, a glycerin solution, and an aqueous sodium polyacrylate solution, when the simulated organ is used for medical procedure training with an energy device, bubbles are more likely to be generated in the simulated mucus composition by the application of current. That is, the simulated mucus composition is more likely to reproduce the behavior of mucus (continuous bubble generation) during the treatment of mucosal tissue of a living organism using an energy device. For example, the continuous bubble generation may be continuous bubble generation caused by the boiling of water.

[0242] For example, if the mock mucus composition is an aqueous sodium chloride solution, it can be prepared by adding sodium chloride to distilled water and stirring. At this time, 5.0×10 -7 By using an aqueous solution of ~4.0 M, the volume resistivity is 1.0 ~ 1X10 6 It can be done in Ω·cm.

[0243] For example, if the mock mucus composition is a glycerin solution, Hoyu Medical Co.'s Lubricating Jelly J-5G 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 an aqueous solution of 0.5 to 100 mass% (wt%), the volume resistivity is 3×10 2 ~ 1x10 6 It can be done in Ω·cm.

[0244] For example, if the mock mucus composition is an aqueous solution of sodium polyacrylate, it can be prepared by using Aron (registered trademark) A-20L manufactured by Doagosei Co., Ltd. without dilution, or by adding distilled water to Aron A-20L and stirring. In this case, by making the concentration of Aron A-20L in distilled water an aqueous solution of 1 to 100 mass% (wt%), the volume resistivity is 1 to 1X10 6 Ω·cm, and viscosity at 25°C measured by the measurement method specified in JIS Z8803, 1.0 ~ 1.0×10 5 It can be in mPa·s. The sodium polyacrylate aqueous solution can be, for example, 10 wt% at a concentration of 20L of Aaron A in distilled water, or 100 wt%.

[0245] 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 x 10 5 Ω·cm, and viscosity at 25°C measured by the measurement method specified in JIS Z8803 is 1.0 ~ 1.0×10 5Within the range of mPa·s, it can be used as a simulated mucus composition of the present embodiment regardless of its component composition. Examples of such medical lubricating jellies include Boston Scientific’s sterile lubricating jelly (catalog number SLT-612-10) and Fujifilm Healthcare’s ultrasound examination jelly ECHO JELLY MORE (registered trademark).

[0246] In one embodiment, the thickness of the mock mucus composition applied to the mock 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.

[0247] Since the thickness of the mock mucus composition applied to the mock organ is in the range of 0.01 to 3.0 mm, the mock mucus composition in the mock organ in this embodiment makes it easier to reproduce the behavior of mucus (continuous bubble generation) during treatment of the mucosal tissue of a living organism using an energy device.

[0248] (Properties of the simulated mucus composition)

[0249] In one embodiment, the simulated mucus composition has a volume resistivity of 1.0 to 1.0 x 10 6 It is Ω·cm. The volume resistivity is 1.0 ~ 1.0×10 6 Since it is Ω·cm, when a simulated organ is used for medical skill training with an energy device, bubbles are prone to forming in the simulated mucus composition due to current flow.

[0250] In one embodiment, the volume resistivity of the mock mucus composition is 1.0 x 10 1 ~ 1.0X10 3 It is desirable that it be Ω·cm, and 4.0X10 1 ~ 1.0X10 3It is more desirable that it be Ω·cm, and 4.0X10 1 ~ 3.0X10 2 It is more preferable that it be Ω·cm. The volume resistivity of the simulated mucus composition is 1.0×10⁻¹⁰ 1 ~ 1.0X10 3 Since it is Ω·cm, bubbles are more likely to form in the simulated mucus composition with fewer current passes. This is behavior similar to that of mucus in living organisms.

[0251] The volume resistivity is 1.0 ~ 1.0×10 6 A simulated mucus composition in the Ω·cm range can be prepared by adjusting the components included in the composition and the content of each component, and by measuring the volume resistivity and viscosity to confirm whether they fall within the above range.

[0252] Here, the volume resistivity can be calculated at a measurement temperature of 25℃ by measuring the AC impedance.

[0253] Specifically, a sample for measurement was placed in a liquid measurement cell with a diameter of 13 mm and a thickness of 5 mm, and the metal terminals installed at both ends of the cell in contact with the sample for measurement were connected to the terminals of an AC impedance measuring device (Solartron SI 1287, manufactured by Toyo Technica Co., Ltd., frequency response analyzer 1252A). Using a small environmental tester (manufactured by Espec Co., Ltd., model number: SU-241), the resistivity of the cell was measured under an environment of 25°C, and the volume resistivity could be calculated by dividing the obtained result by the thickness of 5 mm.

[0254] In one embodiment, the simulated mucus composition has a viscosity at 25°C of 1.0 to 1.0 x 10, measured by the measurement method specified in JIS Z8803. 5 It is desirable that the viscosity be mPa·s. By having such viscosity, the applicability to the mock organ is likely to be good. Applicability refers to the characteristic that when the mock mucus composition is applied to the mock organ, there is no excessive viscosity (stickiness), and it is easy to remain on the surface of the mock organ after application.

[0255] Viscosity can be measured using a rheometer (Anton Paar MCR-92) according to the measurement method specified in JIS Z8803, with a jig of 50 mm diameter cone plate, a measurement temperature of 25℃, and a shear rate of 10 / s.

[0256] If the mock mucus composition is an aqueous sodium chloride solution, 5.0×10 -7 ~ By using a 4 M aqueous sodium chloride solution, the viscosity at 25°C measured by the measurement method specified in JIS Z8803 is 1.0 ~ 1.0×10 5 It can be done in mPa·s.

[0257] When the mock mucus composition is a glycerin solution, by making the concentration of lubricating jelly J-5G in distilled water an aqueous solution of 1 to 100 mass% (wt%), the viscosity at 25°C measured by the measurement method specified in JIS Z8803 is 1.0 to 8.0 x 10 4 It can be done in mPa·s.

[0258] The viscosity of the simulated mucus composition at 25°C, measured by the measurement method specified in JIS Z8803, is 1.0 ~ 1.0×10 5 mPa·s and 1.0×10 2 ~ 5.0X10 4 It is desirable that it be mPa·s, and 1.0×10 3 ~ 5.0X10 4 It is more desirable that it be mPa·s, and 5.0X10 3 ~ 5.0X10 4 It is more desirable that it be mPa·s. 5.0X10 3 ~ 5.0X10 4 In the case of mPa·s, 9.0×10 3 ~ 8.0X10 4 It can be mPa·s, and 9.0X10 3 ~ 2.6 x 10 4 It could be mPa·s.

[0259] The volume resistivity of the simulated mucus composition and the range of viscosity at 25°C measured by the measurement method specified in JIS Z8803 are as described above, and the ranges of volume resistivity and viscosity can be combined arbitrarily.

[0260] The volume resistivity of the simulated mucus composition is 1.0 ~ 1.0×10 6 That is in the range of Ω·cm and / or the viscosity at 25°C measured by the measurement method specified in JIS Z8803 of the mock mucus composition is 1.0 ~ 1.0×10 5 By being in the mPa·s range, the risk of deformation or problems caused by the current flow and heating of energy devices that have been used in conventional medical procedure training can be reduced.

[0261] Mock Chess

[0262] The mock organ comprises mock blood vessels and mock ulcers. In one embodiment, the mock organ further comprises a mock mucus composition (in this case, referred to as "mock mucus composition coated mock organ").

[0263] In this specification, "simulated organ" includes not only the entire organ but also a part of the organ's tissue that mimics it.

[0264] The simulated organ is not limited to any model that imitates the organ of any animal species; for example, it may be a simulated organ of any animal species, such as mammals including humans, birds, reptiles, amphibians, and fish, and a person skilled in the art may appropriately select one according to the training needs of medical procedures.

[0265] In one embodiment, the mock organ is a mock organ for use as a mock mucus-coated mock organ in which at least a portion of its outer surface is coated with a mock mucus composition.

[0266] (Composition and properties of simulated chess)

[0267] In one embodiment, the mock organ is a structure in which a mock blood vessel penetrates in the thickness direction at any part of the mock ulcer. Such a mock organ can be manufactured by penetrating a mock blood vessel at any part of the mock ulcer.

[0268] In the mock organ, at least a portion of the outer surface of the mock blood vessel and at least a portion of the mock ulcer are conductive, the surface resistance of the conductive portion of the mock blood vessel is lower than the volume resistivity of the conductive portion of the mock ulcer, and the volume resistivity of the conductive portion of the mock ulcer is 1.0 x 10 2 ~ 1.0X10 7 It is Ω·cm.

[0269] In one embodiment, the simulated blood vessel comprises a thermoplastic resin.

[0270] Since the surface resistance of the conductive part of the mock blood vessel is lower than the volume resistivity of the conductive part of the mock ulcer, when the mock organ is used for medical procedure training with an energy device, the mock blood vessel becomes easier to heat up than the mock ulcer due to current flow, making it easier to perform hemostatic treatment on the mock blood vessel.

[0271] The surface resistance value of the mock blood vessel and the volume resistivity of the mock ulcer can be adjusted as described in the "mock blood vessel" and "mock ulcer" above.

[0272] The preferred range of surface resistance values ​​of the mock blood vessel and the preferred range of volume resistivity of the mock ulcer are as described in the "mock blood vessel" and "mock ulcer" above.

[0273] In one embodiment, it is preferable that the softening point of the mock blood vessel is lower than the softening point of the mock ulcer.

[0274] For example, as described above, by adjusting the softening point of the thermoplastic resin in the substrate layer of the mock blood vessel, the softening point of the mock blood vessel can be adjusted to the same desired range as the thermoplastic resin.

[0275] Since the softening point of the mock blood vessel is lower than the softening point of the mock ulcer, it becomes difficult for the mock ulcer to melt before or during hemostasis in the mock blood vessel.

[0276] In one embodiment, it is preferable that the melting point of the mock blood vessel is lower than the melting point of the mock ulcer.

[0277] For example, as described above, by adjusting the melting point of the thermoplastic resin in the substrate layer of the mock blood vessel, the melting point of the mock blood vessel can be adjusted to the same desired range as the thermoplastic resin.

[0278] Since the melting point of the mock blood vessel is lower than the melting point of the mock ulcer, it becomes difficult for the mock ulcer to melt before or during hemostasis in the mock blood vessel.

[0279] In one embodiment, the mock organ may be used as a mock mucus-coated mock organ in which at least a portion of the outer surface of the mock organ is coated with a mock mucus composition. In this case, it is preferable that the surface resistance value of the conductive portion of the mock blood vessel is higher than the volume resistivity of the mock mucus composition.

[0280] In one embodiment, at least a portion of the outer surface of the mock organ is coated with a mock mucus composition, and it is preferable that the surface resistance value of the conductive portion of the mock blood vessel is higher than the volume resistivity of the mock mucus composition.

[0281] In the case where at least a portion of the outer surface of the simulated organ is coated with a simulated mucus composition, the coated portion, the coating method, etc. are as described in the fifth embodiment.

[0282] Since the surface resistance of the conductive portion of the mock blood vessel is higher than the volume resistivity of the mock mucus composition covering at least a portion of the outer surface of the mock organ, when the mock organ is used for medical procedure training with an energy device and energized, the mock mucus composition heats up before the mock blood vessel, and the mock mucus composition is prone to generating bubbles before the hemostasis timing of the mock blood vessel.

[0283] In medical procedures performed in vivo, the continuous generation of bubbles resulting from the heating of mucus covering mucosal tissue is used as one of the criteria for electrical conduction and hemostasis by electrical conduction. Therefore, since the surface resistance value of the conductive part 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, it becomes easier to more accurately reproduce the behavior of mucus (continuous bubble generation) and hemostasis in medical procedures performed in vivo when training with the simulated organ.

[0284] Here, if the surface resistance value of the conductive portion of the mock blood vessel is higher than the volume resistivity of the mock mucus composition covering at least a portion of the outer surface of the mock organ, then the volume resistivity of the mock mucus composition < the surface resistance value of the conductive portion of the mock blood vessel < the volume resistivity of the conductive portion of the mock ulcer.

[0285] In this case, when a simulated organ is used for medical procedure training with an energy device, the simulated mucus composition is prone to heating first, then the simulated blood vessel, and finally the simulated ulcer due to the application of electricity. Consequently, the simulated mucus composition is prone to generating bubbles before the hemostasis timing of the simulated blood vessel, and furthermore, melting of the simulated ulcer is difficult to occur before or during hemostasis in the simulated blood vessel.

[0286] In one embodiment, the surface resistance value of the conductive portion of the mock blood vessel in the mock organ is 1.0 x 10 1~ 1.0X10 6 It is Ω, and the volume resistivity of the conductive part of the mock ulcer is 1.0×10 2 ~ 1.0X10 7 It can be Ω·cm.

[0287] The surface resistance value of the conductive part of the mock blood vessel in the mock organ and the volume resistivity of the conductive part of the mock ulcer may be a combination of any one of the ranges of surface resistance values ​​described in "mock blood vessel" and any one of the ranges of volume resistivity described in "mock ulcer".

[0288] In one embodiment, the surface resistance value of the conductive portion of the mock blood vessel in the mock organ is 1.0 x 10 1 ~ 1.0X10 6 The volume resistivity of the conductive portion of the mock ulcer is Ω, and the volume resistivity is 1.0×10 2 ~ 1.0X10 7 The volume resistivity of the mock mucus composition is Ω·cm and is 1.0 ~ 1.0×10 6 It may be Ω·cm. The surface resistance value of the conductive part of the mock blood vessel in the mock organ, the volume resistivity of the conductive part of the mock ulcer, and the volume resistivity of the mock mucus composition may be a combination of any one of the ranges of surface resistance values ​​described in "mock blood vessel," any one of the ranges of volume resistivity described in "mock ulcer," and any one of the ranges of volume resistivity described in "mock mucus composition."

[0289] In one embodiment, the simulated organ may be connected to a device capable of supplying simulated blood to the simulated blood vessels.

[0290] For example, a simulated blood vessel is a pathway for supplying simulated blood to a surface mimicking the mucosal tissue of a simulated ulcer during hemostasis practice, and may also penetrate the simulated ulcer of a simulated organ. Any device capable of supplying simulated blood may be used, for example, a tubular pump or a syringe.

[0291] (Uses of mock chess)

[0292] In one embodiment, the simulated organ is a simulated organ used for medical skills training.

[0293] Here, "medical skills training" refers to training for improving the skills of doctors or medical students and the quality of medical practice, and includes, for example, medical skills training performed under endoscopic observation or medical skills training performed under ultrasound observation.

[0294] In one embodiment, the medical procedure is the treatment of mucosal tissue, etc. (e.g., ulcer) using an energy device. Examples of energy devices include high-frequency hemostatic forceps, electric scalpels, ultrasonic scalpels, heat probes, microwave scalpels, laser scalpels, etc.

[0295] As a desirable example of a medical procedure, a treatment including incision and / or hemostasis of mucosal tissue using an energy device may be exemplified, and more specifically, endoscopic mucosal resection, endoscopic submucosal dissection, endoscopic hemostasis may be exemplified.

[0296] 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.

[0297] [Second Embodiment (Medical Skill Training Kit)]

[0298] The kit according to the present embodiment is a medical procedure training kit comprising a simulated organ and a simulated mucus composition according to the first embodiment.

[0299] In one embodiment, the surface resistance value of the conductive portion of the simulated blood vessel in the kit is higher than the volume resistivity of the simulated mucus composition.

[0300] "Medical skills training" is as described in the first embodiment.

[0301] (Mock Chess)

[0302] In this embodiment, the simulated organ is a simulated organ of any one of the modes described in the first embodiment.

[0303] A medical procedure training kit comprises a simulated mucus composition. As described in the first embodiment, a simulated organ may be provided as a kit with at least a portion of its outer surface coated with the simulated mucus composition. Alternatively, the simulated mucus composition may be provided separately from the simulated organ, and may be provided for use by a user, etc., to apply the simulated mucus composition appropriately to the simulated organ prior to medical procedure training.

[0304] In addition to mock organs and mock mucus compositions, the kit may include one or more devices, medical instruments, medical treatment consumables, etc., necessary for medical procedure training. For example, it may include energy devices used in medical treatment, recording cameras, computers, forceps, clips, cotton swabs for hemostasis, sponges, mock blood, pumps or syringes for supplying mock blood, etc.

[0305] (Mock mucus composition)

[0306] In this embodiment, the mock mucus composition is a mock mucus composition of any one of the embodiments described in the first embodiment.

[0307] [Third Embodiment (Medical Skill Training Device)]

[0308] The device according to the present embodiment is a medical procedural training device having a simulated organ according to the first embodiment and one or more other types of simulated organs.

[0309] Here, the device according to the present embodiment may include a plurality of the simulated organs of 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 reproduce a living organism. Additionally, the device may be a device including one or more types of simulated organs, such as a part of a human body model or an animal model equipped with various organs regardless of the presence or absence of simulated blood vessels or simulated ulcers.

[0310] The device according to the present embodiment can be used for medical skills training. "Medical skills training" is as described in the first embodiment.

[0311] [Fourth Embodiment (Medical Skill Training Method)]

[0312] The method according to the present embodiment is a medical procedural training method using a simulated organ according to the first embodiment, a kit according to the second embodiment, and / or a device according to the third embodiment.

[0313] "Medical skills training" is as described in the first embodiment.

[0314] (Medical Skills Training Methods)

[0315] For example, in the treatment of mucosal tissue in vivo, the tip of an energy device is brought into contact with the mucosal tissue and current is applied to incise and / or stop the mucosal tissue.

[0316] In the medical procedural training method according to the present embodiment, just like in actual biological treatment, the tip of the energy device may be brought into contact with a surface (mucosa) coated with a simulated mucus composition of a simulated mucus-coated simulated organ and current may be applied.

[0317] More specifically, for example, a mock blood vessel in a mock mucus-coated mock organ, in which a surface mimicking the mucosal surface of a sheet mainly composed of a hydrogenated styrene-based thermoplastic elastomer as exemplified in the first embodiment is coated with a mock mucus composition having a thickness of 0.5 mm, may be pinched with the tip of an electric scalpel (ERBE high-frequency surgical device: VIO-100C, condition: FORCED coagulation mode, output 30W, treatment device: hemostatic forceps FD-410LR) and energized.

[0318] Generally, when an electric current is applied to living mucosal tissue, the mucus covering the membrane heats up, causing vaporization from within the mucus to begin forming bubbles, and the gradual, continuous generation of bubbles becomes observed. In medical procedure training methods using simulated mucus-coated organs, the completion of the electric current may be determined based on the behavior of the mucus—such as the size and number of bubbles generated—that is identical to what is actually observed when the current is applied to the simulated blood vessel being treated.

[0319] In the case of a simulated mucus-coated simulated organ, the simulated blood vessel is clamped with the tip of an energy device and current is applied, so that bubbles are continuously generated in the simulated mucus composition, preferably, the generation of bubbles continues until current is stopped, which can be used as a criterion for the completion of current application.

[0320] The volume resistivity of the simulated mucus composition is 1.0 ~ 1.0 × 10 6 By being in the range of Ω·cm, the simulated mucus composition in the simulated mucus-coated simulated organ becomes easier to reproduce the behavior of mucus during treatment of the mucosal tissue of a living organism using an energy device. In addition, according to the medical procedural training method of the present embodiment, the risk of deformation or problems occurring in the energy device due to the current application and heating of thermoplastic resins, which have been used in conventional medical procedural training, can be reduced.

[0321] In one embodiment, when a simulated mucus-coated simulated organ includes a simulated blood vessel connected to a device capable of supplying simulated blood, the medical skill training method may be a training method for hemostasis simulating bleeding from the simulated blood vessel.

[0322] In the case of such hemostasis training, bleeding in mucosal tissue can be reproduced by supplying simulated blood to simulated blood vessels prior to medical procedure training using an energy device.

[0323] According to the medical skill training method of the present embodiment, the behavior of mucus in a living mucosal tissue during treatment of mucosal tissue using an energy device can be reproduced, and thus it is useful for medical personnel to acquire skills for treating living tissue.

[0324] In one embodiment, the viscosity at 25°C of the mock mucus composition, measured by the measurement method specified in JIS Z8803, is 1.0 to 1.0 x 10 5 It may be in the range of mPa·s. Since the simulated mucus composition has such viscosity, according to the medical procedure training method, it becomes easier to reproduce the behavior of mucus in living mucosal tissue during treatment of mucosal tissue using an energy device. In addition, when the simulated mucus composition is applied to a simulated organ, the applicability is likely to be good.

[0325] In this embodiment, by using a simulated organ according to the first embodiment, a kit according to the second embodiment, and / or a device according to the third embodiment, in a hemostatic training in which a simulated blood vessel is squeezed and energized, for example, with the tip of an energy device, the behavior of mucus in the mucosal tissue of the living body, the behavior of the blood vessel, and / or the state during hemostatic training can be easily reproduced, and the hemostatic training can be performed effectively.

[0326] [Fifth Embodiment (Manufacturing Method)]

[0327] The manufacturing method according to the present embodiment comprises coating at least a portion of the outer surface of a mock organ, comprising a mock blood vessel and a mock ulcer, with a mock mucus composition, wherein at least a portion of the outer surface of the mock blood vessel and at least a portion of the mock ulcer are conductive, the surface resistance value of the conductive portion of the mock blood vessel is lower than the volume resistivity of the conductive portion of the mock ulcer, and the volume resistivity of the conductive portion of the mock ulcer is 1.0 x 10 2 ~ 1.0X10 7 It is a manufacturing method in which the simulated blood vessel contains a thermoplastic resin and is Ω·cm.

[0328] In one embodiment, it is preferable that the surface resistance value of the conductive portion of the mock blood vessel is higher than the volume resistivity of the mock mucus composition.

[0329] In the manufacturing method of the present embodiment, examples and preferred examples of "mock organ," "mock blood vessel," "mock ulcer," and "mock mucus composition," as well as the manufacturing method and materials, are as described in the first embodiment.

[0330] The manufacturing method according to the present embodiment is a method for manufacturing a mock mucus-coated mock organ in which at least a portion of the outer surface of the mock organ described in the first embodiment is coated with a mock mucus composition.

[0331] The manufacturing method according to the present embodiment comprises coating at least a portion of the outer surface of a mock organ, which includes a mock blood vessel and a mock ulcer, with a mock mucus composition. In the mock organ, the portion to be coated is preferably a surface that mimics the mucosal surface of the mucosal tissue of the mock blood vessel and / or mock ulcer. In this case, it is not necessary to coat the entire surface that mimics the mucosal surface of the mucosal tissue, and when the mock mucus-coated mock organ is used for medical procedure training, it is sufficient to coat at least the portion that is contacted by the tip of an energy device and energized.

[0332] 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 performing hemostasis training simulating bleeding from a simulated blood vessel using a simulated organ comprising a simulated blood vessel connected to such a device capable of supplying simulated blood, it is sufficient to at least cover the area around the simulated blood vessel with a simulated mucus composition.

[0333] In one embodiment, the thickness of the mock mucus composition in the process of coating the mock organ, preferably the thickness of the mock mucus composition applied to the mock 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.

[0334] The application of the mock mucus composition to the mock organ can be appropriately performed using a finger or a spatula, etc.

[0335] The timing of the process of coating a mock organ with a mock mucus composition, preferably the timing of the application of the mock mucus composition, should be determined in such a way that the mucus state of the biological mucosal tissue can be reproduced when current is applied by an energy device during medical procedure training.

[0336] A simulated mucus-coated simulated organ manufactured by the method according to the present embodiment can reproduce the behavior of mucus in a living mucosal tissue during treatment of mucosal tissue using an energy device, and is therefore useful for medical procedure training.

[0337] An exemplary embodiment of the present disclosure and a non-limiting list of combinations of exemplary embodiments are disclosed below.

[0338] [1-1] As a mock organ including mock blood vessels and mock ulcers,

[0339] At least part of the outer surface of the mock blood vessel and at least part of the mock ulcer are conductive, and

[0340] The surface resistance value of the conductive portion of the mock blood vessel is lower than the volume resistivity of the conductive portion of the mock ulcer, and

[0341] The volume resistivity of the conductive portion of the mock ulcer is 1.0×10 2 ~ 1.0X10 7 A simulated organ with Ω·cm.

[0342] [1-2] A mock organ described in [1-1], in which the mock blood vessels contain a thermoplastic resin.

[0343] [1-3] A mock organ described in [1-1] or [1-2], which is a mock organ for use as a mock mucus-coated mock organ in which at least a portion of the outer surface of the mock organ is coated with a mock mucus composition.

[0344] [1-4] A simulated organ described in any one of [1-1] to [1-3], wherein the softening point of the simulated blood vessel is 200°C or lower.

[0345] [1-5] The surface resistance of the conductive part of the simulated blood vessel is 1.0×10 1 ~ 1.0X10 6 A simulated organ described in any one of [1-1] to [1-4] that is Ω.

[0346] [1-6] A simulated organ described in any one of [1-3] to [1-5], wherein the surface resistance value of the conductive portion of the simulated blood vessel is higher than the volume resistivity of the simulated mucus composition.

[0347] [1-7] At least a portion of the outer surface of the mock organ is covered with a mock mucus composition, and

[0348] A mock organ described in any one of [1-1] to [1-6], wherein the surface resistance value of the conductive portion of the mock blood vessel is greater than or equal to the volume resistivity of the mock mucus composition.

[0349] [1-8] The volume resistivity of the simulated mucus composition is 1.0 to 1.0×10 6 A simulated organ described in [1-7], with a diameter of Ω·cm.

[0350] [1-9] A simulated blood vessel has a tubular substrate layer and a conductive layer disposed on at least a portion of the outer surface of the substrate layer, and

[0351] A simulated organ described in any one of [1-1] to [1-8], wherein the outer diameter of the substrate layer is 0.5 to 10.0 mm and / or the thickness of the substrate layer is 0.05 to 2.0 mm.

[0352] [1-10] A simulated organ described in any one of [1-1] to [1-9], in which a simulated blood vessel is connected to a device capable of supplying simulated blood into the simulated blood vessel.

[0353] [1-11] A simulated organ used for medical skills training, as described in any one of [1-1] to [1-10].

[0354] [1-12] A simulated organ described in [1-11], the medical procedure being a treatment involving the incision or hemostasis of mucosal tissue using an energy device.

[0355] [1-13] A mock organ and a mock mucus composition as described in any one of [1-1] to [1-12], and

[0356] A medical procedure training kit in which the surface resistance value of the conductive portion of the simulated blood vessel is higher than the volume resistivity of the simulated mucus composition.

[0357] [1-14] The volume resistivity of the mock mucus composition is 1.0 ~ 1.0×10 6 A medical skills training kit described in [1-13], with a diameter of Ω·cm.

[0358] [1-15] A medical skills training device comprising a simulated organ described in any one of [1-1] to [1-14], and one or more other types of simulated organs.

[0359] [2-1] A method for manufacturing a simulated organ coated with a simulated mucus,

[0360] It includes coating at least a portion of the outer surface of a mock organ, including mock blood vessels and mock ulcers, with a mock mucus composition, and

[0361] At least part of the outer surface of the mock blood vessel and at least part of the mock ulcer are conductive, and

[0362] The surface resistance value of the conductive portion of the mock blood vessel is lower than the volume resistivity of the conductive portion of the mock ulcer, and is also higher than the volume resistivity of the mock mucus composition, and

[0363] The volume resistivity of the conductive portion of the mock ulcer is 1.0×10 2 ~ 1.0X10 7 It is Ω·cm, and

[0364] A method for manufacturing a simulated blood vessel comprising a thermoplastic resin.

[0365] [3-1] A medical skills training method using a simulated organ as described in any one of [1-1] ~ [1-12].

[0366] Examples

[0367] The present disclosure is explained more specifically by presenting examples below, but the interpretation of the present disclosure is not limited by these examples.

[0368] The various raw materials and manufacturing methods used in the examples, etc. were as follows.

[0369] (1) Imitation blood vessel

[0370] (1-1) Base layer

[0371] (X1) Ethylene-vinyl acetate resin (EVA): EVAflex EV170, manufactured by Mitsui-Dow Polychemical, softening point 33°C, melting point 62°C

[0372] (X2) Ethylene-vinyl acetate resin (EVA): EVAFEX V5961, manufactured by Mitsui-Dow Polychemical, softening point 74°C, melting point 97°C

[0373] (X3) Polyester-based thermoplastic elastomer: Pelprene (registered trademark) P-55B, manufactured by Toyobo MC, softening point 155°C, melting point 186°C

[0374] (1-2) Challenge layer

[0375] (T1) Polythiophene-based conductive polymer coating (Denatron PT-436, manufactured by Nagase Chemtex Co., Ltd.)

[0376] (T2) A paint made by mixing carbon nanotube dispersion (HW004M, manufactured by KJ Specialty Paper Co., Ltd.), water-based binder (Rikken Bond REO-29M, manufactured by Mikiriken Industry Co., Ltd.), and water in a weight ratio of 70:5:25.

[0377] (Preparation of mock blood vessels)

[0378] Using the materials of (X1) to (X3) above, 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 manufactured by an extrusion molding machine and used as a substrate layer.

[0379] Next, except for the case where the conductive layer was not coated, the above (T1) and (T2) were prepared as conductive layers, and the substrate layer was coated on the surface by immersing it in the paint, and dried at 20°C for 2 hours. A simulated blood vessel having a conductive layer with a thickness of 500 nm was obtained.

[0380] (Surface resistance value of simulated blood vessels)

[0381] The surface resistance value was measured using a Loresta-GP (MCP-T610) manufactured by Nitto Seiko Analytech Co., Ltd. at a voltage of 10V applied with an ASP probe under conditions of 23±1℃ and 50%RH relative humidity.

[0382] The surface resistance (Ω) of the simulated blood vessels prepared using materials (X1) to (X3) was as follows.

[0383] · Mock blood vessel coated with T1 conductive layer: 1.0×10 3

[0384] · Mock blood vessel coated with T2 conductive layer: 6.0X10 1

[0385] · Mock blood vessel without conductive layer: > 1.0X10 7

[0386] (2) Mock ulcer

[0387] (Material 1) Styrene-based

[0388] (A) Hydrogenated styrene-based thermoplastic elastomer

[0389] ·SEEPS (SEPTON 4055, manufactured by Curare) (MFR (temperature 230℃, load 2.16 kg) 0.0g / 10 min (0.0g / 10 min means non-flowing), styrene content 30 mass%, hydrogenation rate 90 mol% or more)

[0390] (B) Oil

[0391] · Paraffin oil (Diana Process Oil PW90, manufactured by Idemitsu Kosan Co., Ltd.)

[0392] (C) Polymer antistatic agent

[0393] · Polyolefin / polyether copolymer (Pelectoron PVL, manufactured by Sanyo Chemical Industry Co., Ltd.) (MFR (measured at 190℃, load 2.16 kg) 8 ~ 15 g / 10 min)

[0394] (D) Ionic liquid

[0395] ·CIL-312 (Manufactured by Carit, Japan)

[0396] (Material 2) Polyvinyl alcohol (PVA)-1

[0397] · Polyvinyl alcohol (PVA) (Povall B-17, manufactured by Denka Co.)

[0398] · Organotitanium compound (Orgatics TC-300, manufactured by Matsumoto Fine Chemical)

[0399] (Material 3) Polyvinyl alcohol (PVA)-2

[0400] · Same as Material 2

[0401] (Ingredient 4) Konjac

[0402] · Konjac (Okawasa) (Moisture content 96%)

[0403] (Material 5) Urethane-based

[0404] · Human Skin (Registered Trademark) Gel Concentrate Starter Set (Model No. H0-START, Manufactured by Exil)

[0405] (Preparation of Ingredient 1)

[0406] 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) were added to 100 parts by mass of hydrogenated styrene-based thermoplastic elastomer (A), and then stored for at least 12 hours to allow sufficient penetration. Using a segment mixer (Toyo Seiki Co., Ltd. Labo Plastomil KF70V2 type), the mixture was kneaded at 180°C, a rotation speed of 100 revolutions / min, for 15 minutes.

[0407] Next, the heat press method (180℃, time 5 min, pressure 50 kg / cm² 2 A sample sheet was prepared by ) and prepared with a width of 50 mm, a length of 50 mm, and a thickness of 3 mm.

[0408] (Preparation of Ingredient 2)

[0409] Water at 90°C was added to make the polyvinyl alcohol a 5 wt% aqueous solution, and then stirred with a magnetic stirrer. The polyvinyl alcohol aqueous solution and the organic titanium compound were mixed in a weight ratio of 85:15 and stirred thoroughly. The mixture was placed in a container and heated in an oven at 105°C for 2 hours. The obtained sample was prepared with a width of 50 mm, a length of 50 mm, and a thickness of 10 mm.

[0410] (Preparation of Ingredient 3)

[0411] The prepared material 2 was dried for 8 days in an environment of 23℃ and 50% humidity, and the obtained sample was prepared with a width of 30 mm, a length of 30 mm, and a thickness of 5 mm.

[0412] (Preparation of Ingredient 4)

[0413] Konjac was prepared with a width of 30 mm, a length of 75 mm, and a thickness of 10 mm.

[0414] (Preparation of Ingredient 5)

[0415] The polyol, which is the main component of the gel stock starter set, and the isocyanate, which is the curing agent, were mixed in a weight ratio of 3:1 and stirred with a magnetic stirrer. The mixture was then poured into a container and cured by heating in an oven at 100°C for 2 hours. The obtained sample was prepared with a width of 50 mm, a length of 50 mm, and a thickness of 10 mm.

[0416] (Volumetric resistivity of a simulated ulcer)

[0417] After adjusting a test specimen of a conductive resin composition with a width of 25 mm, a length of 25 mm, and a thickness of 1 mm for more than 24 hours in an environment with a temperature of 23±2℃ and a relative humidity of 50±5%, the volume resistivity was measured after 20 seconds using a resistivity meter Loresta-GP (model number: MCP-T610) manufactured by Mitsubishi Chemical Analytech Co., Ltd., with a PSP probe and a voltage of 10V applied.

[0418] (Softening point of a mock ulcer)

[0419] A test specimen of a conductive resin composition adjusted to a diameter of 30 mm and a thickness of 2 mm was tested using a viscoelasticity measuring device RSA-G2 manufactured by TA Instruments. The temperature was measured when the indenter penetrated 30% of the thickness of the test specimen at a heating rate of 5℃ / min, an indenter diameter of 10 mm, and an indentation load of 1.0 N.

[0420] (Melting point of a mock ulcer)

[0421] The melting point of the mock ulcer was measured using a differential scanning calorimeter (DSC; METTLER TOLEDO, DSC 3+) under a nitrogen atmosphere at a heating rate of 10℃ / min.

[0422] The volume resistivity (Ω·cm) of the simulated ulcers prepared using materials 1 to 5 was as follows.

[0423] · Material 1: Volume resistivity 5.0×10 6 Softening point 130℃, melting point 220℃

[0424] · Material 2: Volume resistivity 3.0×10 2

[0425] · Material 3: Volume resistivity 2.0×10 3

[0426] · Material 4: Volume resistivity 4.0×10 2

[0427] · Material 5: Volume resistivity > 1.0×10 7

[0428] (3) Mock mucus composition

[0429] (N1) 0.9% physiological saline (0.9% sodium chloride aqueous solution)

[0430] (N2) Lubricating Jelly (Lubricating Jelly J-5G, Hoyu Medical Co., Ltd.)

[0431] (N3) Distilled water

[0432] (Volume resistivity of the simulated mucus composition)

[0433] The volume resistivity of the similar mucus composition was calculated at a measurement temperature of 25°C by AC impedance measurement.

[0434] Specifically, a sample for measurement was placed in a liquid measurement cell with a diameter of 13 mm and a thickness of 5 mm, and the metal terminals installed at both ends of the cell in contact with the sample for measurement were connected to the terminals of an AC impedance measuring device (Solartron SI 1287, manufactured by Toyo Technica Co., Ltd., frequency response analyzer 1252A). Using a small environmental tester (manufactured by Espec Co., Ltd., model number: SU-241), the resistivity of the cell was measured under a temperature of 25°C, and the volume resistivity was calculated by dividing the obtained result by the thickness of 5 mm.

[0435] The volume resistivity (Ω·cm) of the simulated mucus compositions of N1 to 3 was as follows.

[0436] ·N1: 4.0X10 1

[0437] ·N2: 3.0X10 2

[0438] ·N3: 1.0X10 6

[0439] [Examples 1–11 and Comparative Examples 1–5]

[0440] As shown in Table 1, a mock blood vessel, a mock ulcer, and a mock mucus composition were combined. Specifically, a mock blood vessel was inserted into the center of the mock ulcer by penetrating it in the thickness direction. Except for the non-application case, the mock mucus composition was applied to the treated surface of the mock blood vessel and mock ulcer to a thickness of 0.5 mm.

[0441] Next, a syringe filled with mock blood was connected to the end of a mock blood vessel protruding opposite to the treatment surface, and the mock blood was supplied to the treatment surface.

[0442] [Evaluation Methods and Results]

[0443] (Stop bleeding)

[0444] Using the ERBE VIO-100C high-frequency surgical device in FORCED coagulation mode with an output of 30W, current was applied for 2 seconds per cycle while gripping the pseudo-ulcer and the distal end of the pseudo-vascular vessel passed through the pseudo-ulcer with the hemostatic forceps FD-410LR. The number of times current was applied until water stopped coming out of the distal end of the pseudo-vascular vessel when water was flowed through it was checked.

[0445] Hemostasis was evaluated as follows.

[0446] · Hemostasis with 1 to 4 pulses: Right

[0447] · Hemostasis with 5 to 10 pulses: Good

[0448] · Hemostasis with 11 to 20 pulses: Possible

[0449] · Inability to stop bleeding with less than 20 pulses: Not possible

[0450] As shown in Table 1, in Examples 1 to 8, hemostasis was "excellent," in Example 9, hemostasis was "good," and in Examples 10 and 11, hemostasis was "possible."

[0451] In addition, in Comparative Examples 1 to 5, hemostasis was "impossible".

[0452] That is, when the surface resistance value of the mock blood vessel < the volume resistivity of the mock ulcer (Examples 1 to 11), hemostasis was "excellent," "good," or "possible."

[0453] In Examples 1 to 8 (hemostasis was "excellent"), the mock blood vessel material was X1, and in Examples 9 to 11 (hemostasis was "good" or "possible"), the mock blood vessel material was X2 or X3.

[0454] That is, in addition to the surface resistance value of the mock blood vessel < the volume resistivity of the mock ulcer, hemostasis was "excellent" when the mock blood vessel material was X1.

[0455] (blowhole)

[0456] Using the ERBE VIO-100C high-frequency surgical device in FORCED coagulation mode with an output of 30W, current was applied for 2 seconds per cycle while gripping the pseudo-ulcer and the pseudo-ulcer together with the FD-410LR hemostatic forceps passed through the pseudo-ulcer. The number of times current was applied until bubbles were generated was recorded.

[0457] Bubble generation was evaluated as follows.

[0458] · Bubble generation after 1 to 4 cycles of current application: Good

[0459] · Bubble generation with 5 to 10 cycles of current: Possible

[0460] · No bubbles are generated even after 11 or more (up to 20) cycles: Not possible

[0461] As shown in Table 1, in Examples 1 to 11, with the exception of the application of a similar mucus composition (Examples 5 and 10), the evaluation of bubble generation was "good" or "possible".

[0462] In addition, in Comparative Example 5, bubble generation was "good," but in the other Comparative Examples (Comparative Examples 1 to 4), the evaluation of bubble generation was "impossible."

[0463] Comparative Example 5 is a mock mucus composition of N2 (volume resistivity of 3.0×10 2 Ω·cm), mock ulcer is material 1 (volume resistivity is 5.0×10 6 It was Ω·cm).

[0464] In Comparative Examples 1 and 2, the mock mucus composition was N2 (volume resistivity 3.0×10⁻¹⁰). 2 (Ω·cm), but the simulated ulcer is material 5 (volume resistivity > 1.0×10 7 It was Ω·cm). In Comparative Example 3, the mock mucus composition was N1 (volume resistivity was 4×10 1 (Ω·cm), but the simulated ulcer is material 5 (volume resistivity > 1.0×10 7 It is Ω·cm). In Comparative Example 4, the mock ulcer is material 1 (volume resistivity is 5.0×10 6 (Ω·cm), but the mock mucus composition was not applied.

[0465] in other words,

[0466] · The volume resistivity of the simulated ulcer is 1.0×10 7 It is less than Ω·cm, and also

[0467] · When any one of the mock mucus compositions N1 to N3 was applied, the evaluation of bubble generation was "good" or "possible".

[0468] Meanwhile, if the mock mucus composition is not applied, or the volume resistivity of the mock ulcer is > 1.0×10 7 In the case of Ω·cm, the evaluation of bubble generation was "impossible".

[0469]

[0470] Industrial applicability

[0471] The simulated organ of the present embodiment includes a simulated blood vessel and a simulated ulcer, and since the surface resistance value of the conductive part of the simulated blood vessel is lower than the volume resistivity of the conductive part of the simulated ulcer, hemostatic treatment can be performed by energizing with an energy device. Therefore, it can be preferably used during medical procedure training using an energy device.

Claims

Claim 1 A mock organ comprising mock blood vessels and mock ulcers, wherein at least a portion of the outer surface of the mock blood vessels and at least a portion of the mock ulcers are conductive, the surface resistance of the conductive portion of the mock blood vessels is lower than the volume resistivity of the conductive portion of the mock ulcers, and the volume resistivity of the conductive portion of the mock ulcers is 1.0 × 10 2 ~ 1.0X10 7 A simulated organ with Ω·cm. Claim 2 In paragraph 1, a mock organ in which the mock blood vessel comprises a thermoplastic resin. Claim 3 A mock organ for use as a mock mucus-coated mock organ, wherein at least a portion of the outer surface of the mock organ is coated with a mock mucus composition in accordance with claim 1 or 2. Claim 4 A mock organ according to claim 1 or 2, wherein the softening point of the mock blood vessel is 200℃ or lower. Claim 5 In claim 1 or 2, the surface resistance value of the conductive part of the simulated blood vessel is 1.0×10 1 ~ 1.0X10 6 Ω-type, mock organ. Claim 6 In paragraph 3, a mock organ in which the surface resistance value of the conductive portion of the mock blood vessel is higher than the volume resistivity of the mock mucus composition. Claim 7 A mock organ according to claim 1, wherein at least a portion of the outer surface of the mock organ is coated with a mock mucus composition, and the surface resistance value of the portion having the conductivity of the mock blood vessel is greater than or equal to the volume resistivity of the mock mucus composition. Claim 8 In claim 7, the volume resistivity of the mock mucus composition is 1.0 to 1.0×10 6 A simulated organ with Ω·cm. Claim 9 A mock organ according to claim 1 or 2, wherein the mock blood vessel has a tubular substrate layer and a conductive layer disposed on at least a portion of the outer surface of the substrate layer, and the outer diameter of the substrate layer is 0.5 to 10.0 mm and / or the thickness of the substrate layer is 0.05 to 2.0 mm. Claim 10 In paragraph 1 or 2, the mock blood vessel is connected to a device capable of supplying mock blood into the mock blood vessel, a mock organ. Claim 11 A simulated organ used for medical procedure training, including incision or hemostasis of mucosal tissue using an energy device, in accordance with claim 1 or 2. Claim 12 A medical procedure training kit comprising a simulated organ according to claim 1 or 2 and a simulated mucus composition, wherein the surface resistance value of the conductive portion of the simulated blood vessel is higher than the volume resistivity of the simulated mucus composition. Claim 13 In paragraph 12, the volume resistivity of the mock mucus composition is 1.0 to 1.0×10 6 A medical skills training kit with a diameter of Ω·cm. Claim 14 A medical skills training device comprising a simulated organ according to paragraph 1 or 2, and one or more other types of simulated organs. Claim 15 A method for manufacturing a mock mucus-coated mock organ, comprising coating at least a portion of the outer surface of a mock organ, including a mock blood vessel and a mock ulcer, with a mock mucus composition, wherein at least a portion of the outer surface of the mock blood vessel and at least a portion of the mock ulcer are conductive, and the surface resistance value of the conductive portion of the mock blood vessel is lower than the volume resistivity of the conductive portion of the mock ulcer and is also higher than the volume resistivity of the mock mucus composition, and the volume resistivity of the conductive portion of the mock ulcer is 1.0 x 10 2 ~ 1.0X10 7 A method of manufacturing in which the simulated blood vessel comprises a thermoplastic resin and is Ω·cm.

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