JP2018189761A - Organ membrane model and organ model coated thereby - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an organ model whose flexibility and resilience are like those of a real organ and which three-dimensionally reproduces membrane tissue coating organ, muscle fiber, blood vessel and the like.SOLUTION: An organ membrane model 100 comprises: a multilayer membrane part 120 having multilayer construction of overlapped or laminated single layer membrane parts 110 formed of gelatinous raw materials and simulating monolayer of a membrane tissue; and a fiber part 130 formed of gelatinous raw materials and simulating a fiber tissue. The fiber part 130 can be formed in the combination of a main structure of a fiber tissue made of gelatinous raw materials as a backing for reproducing form of twist of multiple filaments like the fiber tissue, and a coating body made of gelatinous raw materials coating the surface of the main structure of the fiber tissue to give tensile strength like the fiber tissue.SELECTED DRAWING: Figure 1

Description

  The present invention relates to an organ membrane model and an organ model coated with the organ membrane model. The organ membrane model is a model in which the membrane tissue and fiber structure are reproduced, and also relates to an organ membrane model in which the softness is close to that of an actual organ membrane and the response to an electronic medical device such as an electric knife is close to the actual organ membrane.

  In general, an organ model is used as a tool for performing surgical training. The organ model is molded using a polymer material or the like, and is a model assuming a soft part such as an actual organ. The organ model is known to be formed by a powder sintering additive manufacturing method, an optical modeling method, an injection molding method, a vacuum casting method, a cutting method, or the like. These are widely used for medical research or educational models.

However, organ models produced by these molding methods are models that refer to the shape of the organ, etc., and are often hard plastic molded products, and in many cases do not actually have physical properties like biological tissues. .
An actual human organ is covered with a membrane tissue, in which extremely important tissues such as blood vessels and nerves are arranged, and a muscle fiber structure is present in the membrane. In an actual procedure, it is important to train a procedure to peel the membrane without bleeding while paying attention to these blood vessels and nerves in the affected area.

Thus, as an organ model, it is important not only to simulate the shape of an anatomical organ, but also to reproduce the membrane tissue, blood vessels, nerves, and muscle fiber structures contained in the membrane tissue. Because of their complexity, it is difficult to produce an organ model that reproduces even the membrane tissue in the prior art. For this reason, there are many simplified models in which only a part is reproduced, and there are some models in which membrane tissue and muscle fibers are not reproduced, and only one of arteries and veins is reproduced.
An actual organ is covered with a membrane tissue, and the membrane tissue contains muscle fibers and blood vessels. The inside of the organ contains a lot of body fluid, and is rich in flexibility and elasticity. The reproduction of these membrane tissues and muscle fibers is important in training the procedure.

In the prior art, gel materials such as urethane gels, silicone elastomers, and polyvinyl alcohol aqueous gels are frequently used as organ model materials.
An organ model disclosed in Patent Document 1 (Japanese Patent Application Laid-Open No. 2015-125231) is a training model for a simulated intestinal tract wall, and is provided with a simulated mucosal layer and a simulated muscle layer. However, both the simulated mucosa layer and the simulated muscle layer are simple ones in which two flat sheets are bonded together, and muscle fibers and blood vessels are not reproduced.

  The organ model disclosed in Patent Document 2 (Japanese Patent Laid-Open No. 2015-194708) is a model of the shape of an organ and the like, and the organ tissue and muscle fibers are not reproduced. .

  An organ model disclosed in Patent Document 3 (Japanese Patent Application Laid-Open No. 2015-069054) is a simulator for catheter treatment, and a pseudo blood vessel channel is reproduced by an aqueous gel of silicone elastomer and polyvinyl alcohol. However, since it is a simulator for catheter treatment, relatively thick aorta and vena cava are reproduced, and membrane tissue and muscle tissue as an organ model are not reproduced.

  The organ model disclosed in Patent Document 4 (Japanese Patent Application Laid-Open No. 2014-106400) is also a catheter treatment simulator, in which a coronary artery is reproduced in a pseudo manner by an aqueous gel of polyvinyl alcohol. Relatively thick coronary arteries have been reproduced, but the membrane tissue and muscle fibers as organ models have not been reproduced.

  The organ model disclosed in Patent Document 5 (Japanese Patent Application Laid-Open No. 2014-021174) is an organ model having a space inside such as the heart, and has an outer shell type that is hollow inside by a photocurable resin. A support resin mold consisting of an inner shell mold is made, and an aqueous gel of urethane gel, silicone elastomer, and polyvinyl alcohol is poured into the mold to form an organ model with a space inside, but the tissue itself is a single layer. Even the membrane tissues and muscle fibers as organ models have not been reproduced.

  The organ model disclosed in Patent Document 6 (Japanese Patent Application Laid-Open No. 2010-277003) is a massive organ model used for practicing a procedure in an operation such as incision or cutting suture of a human body, and is simulated by an aqueous gel of polyvinyl alcohol. A lump has been reproduced. However, the organ model has a solid outer shape, and the membrane model and muscle fibers as the organ model are not reproduced.

  The organ model disclosed in Patent Document 7 (Japanese Patent Application Laid-Open No. 2010-197637) is also a massive organ model used for practicing a procedure in an operation such as incision or cutting suture of a human body, and is simulated by an aqueous gel of polyvinyl alcohol. Although a lump is reproduced, the organ model has a lump shape, and even the membrane tissue and muscle fibers as the organ model are not reproduced.

Japanese Patent Laying-Open No. 2015-125231 Japanese Patent Laid-Open No. 2015-194708 Japanese Patent Laying-Open No. 2015-069054 JP 2014-106400 A JP 2014-021174 A JP 2010-277003 A JP 2010-197637 A

However, the organ model in the above-described prior art is a model that mainly refers to the shape of an organ and the like, and in many cases does not actually have physical properties like a living tissue. Even if the anatomical shape of the organ is reproduced, the membrane tissue that is a problem in the procedure and the blood vessels and nerves in it are not reproduced, or even if it is reproduced, only a part is easily reproduced It was just something.
An actual human organ is covered with a membrane tissue, in which extremely important tissues such as blood vessels and nerves are arranged, and a muscle fiber structure is present in the membrane. In an actual procedure, it is important to train a procedure to peel the membrane without bleeding while paying attention to these blood vessels and nerves in the affected area.

As an organ model, it is important not only to simulate the shape of the organ, but also to reproduce the membrane tissue, blood vessels, nerves, and muscle fiber structures contained in the membrane tissue. However, because they are complex, it has now been considered difficult to produce an organ model that reproduces even the membrane tissue.
Moreover, ideally, the organ model preferably reproduces the same reaction as when a procedure is performed on an actual organ using a medical device such as an electric knife. In particular, incision of an organ whose surface is covered with a membrane requires incision while carefully handling the membrane tissue, muscle fibers, blood vessels, nerves, etc. in it, and their actual reactions are reproduced in a close form. It is preferable.

  Therefore, the present invention uses a medical device such as an electric scalpel as an organ membrane model that reproduces three-dimensionally from membrane tissue, muscle fibers, blood vessels, and the like that are close to the actual organ membrane and have flexibility and elasticity as an organ membrane model. The purpose of this study is to provide an organ membrane model that is similar to the actual reaction. Another object of the present invention is to provide an organ model covered with the organ membrane model.

In order to achieve the above object, an organ membrane model of the present invention is an organ membrane model that simulates a membrane tissue including a fiber tissue, and is a single-layer membrane that simulates a single layer of the membrane tissue formed of a gel material It is characterized by comprising multilayer film parts that have a multilayer structure by overlapping or bonding parts, and fiber parts that simulate the fiber structure formed of a gel material, and the fiber parts are arranged between the multilayer film parts. It is an organ membrane model.
In the above configuration, the main structure of the fiber structure made of a gel-like material used as a base material for reproducing the shape in which the fiber parts are intertwined with a plurality of filaments close to the fiber structure, and the tensile strength close to the fiber structure It is preferable that the surface of the main structure of the fiber structure is formed by a combination of coating bodies made of a gel-like material.
With the above configuration, the organ membrane model has a structure in which the fiber parts are reproduced between the layers of the multilayer membrane parts, and the finish is close to the actual organ membrane, which is necessary for medical training, in the membrane in the affected area. It becomes an organ membrane model that allows you to experience simulations of procedures such as peeling the membrane while paying attention to fiber tissues such as muscle fibers, blood vessels, and nerves.

As a specific material example, the main structure of the fiber part is a sodium alginate gel. In order to form a sodium alginate gel into a fibrous form, an aqueous sodium alginate solution is extruded into a thread form from a syringe into a calcium chloride aqueous solution to form a filamentous body, and the filamentous body is entangled into a fibrous form to form a fibrous alginate gel.
Furthermore, the fibrous alginic acid gel which is the main structure of the fiber part formed by the above method is immersed in an aqueous polyvinyl alcohol solution and crosslinked with a crosslinking agent such as saturated boric acid to make the polyvinyl alcohol gel the surface of the fibrous alginic acid gel. The structure is formed by coating with a coating body.

Next, the organ model coated with the organ membrane of the present invention was formed by pouring a gel material for an organ model such as polyvinyl alcohol in a state where a blood vessel model or a nerve model was placed on an organ model template as necessary. The organ body model is covered with the above organ membrane model.
The organ model with the above structure has a structure in which an organ membrane model that is similar to an actual organ membrane is reproduced and covered with an organ body model that is reproduced as being close to an actual organ. Reproduced as a close organ model.

Next, as a method for forming an organ membrane model according to the present invention, a sodium alginate aqueous solution is extruded into a thread form from a syringe with respect to a mixed aqueous solution of a calcium chloride aqueous solution and a polyvinyl alcohol aqueous solution while creating a filament of an alginate gel. The filamentous body is entangled into a fiber to form a main structure of a fiber part made of a fibrous alginic acid gel (first step).
Furthermore, a cross-linking agent for polyvinyl alcohol around the main structure of the fiber part is added, and the polyvinyl alcohol clinging around the main structure of the fiber part is cross-linked to form a coating around the main structure of the fiber part. Is formed (second step).
On the other hand, a single-layer film part simulating a single layer of a film structure formed of a gel-like material was created, and was created through the first step and the second step when they were overlapped or bonded together A multilayer part having a multilayer structure is formed by sandwiching the fiber part (third step). This completes the organ membrane model.
In addition, an organ model gel is formed by pouring a gel material for an organ model such as polyvinyl alcohol in a state where a blood vessel model or a nerve model is arranged on the organ model template as necessary. A formed organ membrane model can be created by covering with the organ membrane model created through step 3 (fourth step).

It is a figure which shows simply the structure of the organ membrane model 100 of this invention, and the organ model 200 to which it is applied. It is a figure which shows simply the structure of the organ membrane model 100 concerning Example 1 of this invention. It is a figure which shows simply a mode that the blood vessel model 210 is produced using a three-dimensional printer. It is a figure which shows a mode that the organ main body model 200 is formed. It is a figure which shows a mode that the completed organ model 200 is taken out from the organ model casting_mold | template 300. FIG. FIG. 10 is a diagram illustrating a production example of an organ membrane model 100 according to Example 4; It is a figure which shows the prototype example which coated the fiber part 130 concerning Example 5. FIG. It is a figure which shows a mode that the film | membrane of the upper layer of the organ membrane model 100 concerning Example 5 was peeled.

  Hereinafter, examples of the organ membrane model of the present invention and an organ model formed by covering with the organ membrane model will be described. The present invention is not limited to these examples.

FIG. 1 is a diagram simply showing a configuration of an organ membrane model 100 according to the present invention and an organ model 200 to which the organ membrane model 100 is applied.
In the example of FIG. 1, a kidney organ model is shown as an example of an organ model.
FIG. 1A is a diagram showing the appearance of the organ model 200. The organ model 200 has a structure in which the surface of the organ body model 220 is covered with the organ membrane model 100.
FIG. 1B shows a longitudinal sectional view of an organ membrane model 100 and an organ model 200 to which the organ membrane model 100 is applied. In FIG. 1B, in addition to the organ body model 220 and the organ membrane model 100 that is the capsule, the renal artery model 210-1 and the renal vein model 210-2 that are the blood vessel model 210 are illustrated. However, other models of the cortex, medulla, kidney cup, renal pelvis, ureter, etc. existing inside the actual kidney body are not shown and are shown as a uniform organ body model 220. Yes.

Hereinafter, each component will be described.
[Organic membrane model 100]
The organ membrane model 100 will be described in detail later.
As shown in FIG. 1, the organ body model 200 is covered with an organ membrane model 100. As shown in FIG. 1B, a part of the organ membrane model 100 will be extracted and described.
FIG. 2 is a diagram simply showing the configuration of the organ membrane model 100 according to the first embodiment of the present invention.
FIG. 2A is a diagram simply showing a configuration example in which a fragment of the organ membrane model 100 is extracted.
FIG. 2 (b) shows a state in which the interleaved fiber part 130 tears into a fibrous shape when the upper monolayer film part 110-1 is peeled off from the lower monolayer film part 110-2. It is the figure shown simply.

As shown in FIG. 2A, the organ membrane model 100 according to Example 1 of the present invention includes a plurality of single-layer parts 110, a multilayer film part 120 formed by multilayering the parts, and a fiber part 130. It has a multilayer structure. That is, the multilayer film part 120 simulates a film-like structure having a multilayer structure in which the single-layer film parts 110 formed of a gel-like material are overlapped or bonded together. A fiber part 130 is inserted between the single-layer film parts 110.
In the configuration example of FIG. 2, the multilayer film part 110 is an example configured by two single-layer film parts 110-1 and 110-2. The multilayer film part 110 is not limited to two, and may be a multilayer structure in which three or more are stacked.

[Single layer film part 110]
First, the single layer film part 110 will be described.
The single-layer membrane part 110 simulates a single layer of a membrane tissue, and its flexibility, elasticity, echo characteristics, and the response of a procedure by a medical electronic device such as an electric knife, If a gel material having a close finish is selected, an ideal single layer film part 110 is formed. In addition, the multilayer film part 120 in which they are stacked is also ideal. For example, it is formed using a thermosetting polyvinyl alcohol gel material.
In this configuration example, the monolayer film part 110 is formed of a mixed polyvinyl alcohol gel material obtained by gelling a blend of two types of polyvinyl alcohol aqueous solutions having an average degree of polymerization of 300 to 3500 and different saponification degrees. To do.

  For example, a polyvinyl alcohol aqueous solution having a saponification degree of 97 mol% to 99 mol% is used as the first saponified polyvinyl alcohol aqueous solution, and a saponification degree of 50% to 80 is used as the second saponified polyvinyl alcohol aqueous solution. As an example, an aqueous polyvinyl alcohol solution having a saponification degree of 72.5 mol% to 74.5 mol% is used. A partially saponified polyvinyl alcohol mixed aqueous solution prepared by mixing these two types of saponified polyvinyl alcohol aqueous solutions at a predetermined ratio to prepare a saponification degree of the whole mixed solution to 50 mol% or more and less than 90 mol%, It can be formed by introducing a curing agent comprising a crosslinking agent and curing.

  As described above, the range of the average degree of polymerization in the gel material forming the single-layer film part 110 is 300 to 3500, but the lower limit thereof needs to consider the moldability that the material can be molded as a biological tissue model. . In other words, in order to produce a biological tissue model for surgical practice, structural strength must be obtained to such an extent that it can be solidified and firmly molded. For this purpose, the degree of polymerization of the molecules must be large to some extent, and the average degree of polymerization is preferably 300 or more, more preferably 1000 or more. On the other hand, the upper limit needs to consider that the material can retain elasticity as a biological tissue model. As the degree of polymerization increases, the molding becomes harder. However, it is not preferable that the degree of polymerization becomes so hard that the elasticity is lost. Therefore, it is necessary to suppress the degree of polymerization of molecules to some extent from the viewpoint of imparting appropriate elasticity, and the average degree of polymerization is preferably 3500 or less, and more preferably 2500 or less.

  The first saponified polyvinyl alcohol aqueous solution is a polyvinyl alcohol aqueous solution having a high saponification degree among the two types of polyvinyl alcohol aqueous solutions having the saponification degree. For example, a completely saponified polyvinyl alcohol aqueous solution is used. In general, there are no commercially available saponified polyvinyl alcohols with a saponification degree of 100 mol%. In fact, even those having a saponification degree of 97 mol% to 99 mol% are called fully saponified polyvinyl alcohol. ing. Also in the present invention, a polyvinyl alcohol aqueous solution having a saponification degree of 97 mol% to 99 mol% can be used as the first saponified polyvinyl alcohol aqueous solution.

  On the other hand, the second saponified polyvinyl alcohol aqueous solution is a polyvinyl alcohol aqueous solution having a low saponification degree among the two types of polyvinyl alcohol aqueous solutions having the saponification degree. For example, an aqueous polyvinyl alcohol solution having a saponification degree of 50% to 80 mol% can be used. As an example, an aqueous polyvinyl alcohol solution having a saponification degree of about 72.5 mol% to 74.5 mol% is suitable.

  Although it is the blend amount of the 1st saponified polyvinyl alcohol aqueous solution and the 2nd saponified polyvinyl alcohol aqueous solution, as above-mentioned, the average polymerization degree in the partially saponified polyvinyl alcohol mixed aqueous solution obtained by blending, an average saponification degree In addition, it is necessary to blend so that the average concentration of polyvinyl alcohol falls within the range described above.

  For example, as the first saponified polyvinyl alcohol aqueous solution, a polyvinyl alcohol aqueous solution having a saponification degree of 97 mol% to 99 mol% is used, and as the second saponified polyvinyl alcohol aqueous solution, the saponification degree is 72.5 mol. % To 74.5 mol% of the polyvinyl alcohol aqueous solution, the mixing ratio of the first saponified polyvinyl alcohol aqueous solution and the second saponified polyvinyl alcohol aqueous solution is in the range of 7: 3 to 4: 6. When blended, the partially saponified polyvinyl having an average degree of polymerization of 300 to 3500, a degree of saponification of 50 mol% or more and less than 90 mol%, and a concentration of contained polyvinyl alcohol of about 1 wt% to 30 wt%. It becomes an alcohol mixed aqueous solution.

As a result of many years of research, the inventor has blended two types of polyvinyl alcohol aqueous solution in such a range as a single-layer film part 110, and then cured by introducing a curing agent. We have determined that the resilience and echo characteristics, as well as the response of procedures using medical electronic devices such as electric scalpels, are similar to those of actual organs.
Reasons for blending two types of polyvinyl alcohol having different saponification degrees without making the saponification degree of polyvinyl alcohol uniform are as follows.

The first reason is to facilitate adjustment of the saponification degree as a whole of the partially saponified polyvinyl alcohol mixed aqueous solution.
Since the biological tissue model to be manufactured has different hardness depending on the part, it is preferable that the elasticity and the like to be hardened and reproduced in the manufacturing process can be freely adjusted. Here, factors that determine the elasticity of the molded product include the average degree of polymerization of polyvinyl alcohol, the degree of saponification of polyvinyl alcohol, the concentration of polyvinyl alcohol in the polyvinyl alcohol mixed aqueous solution, the amount of water reduced by cooling treatment and thawing heat treatment, etc. However, since the average degree of polymerization of polyvinyl alcohol is determined at the time of raw material procurement, it is not easy to change. Here, it is relatively easy to adjust the blend of two types of polyvinyl alcohol having different saponification degrees. Therefore, the average saponification degree and the concentration of polyvinyl alcohol as a whole of the partially saponified polyvinyl alcohol mixed aqueous solution are adjusted by using two kinds of polyvinyl alcohols having different saponification degrees.

The second reason is to reproduce the elasticity variation as a living tissue in the living tissue model to be manufactured.
The tissue model to be manufactured varies in hardness depending on the part, but there is a variation in elasticity unique to the living body even if the contents are the same part. For example, the contents of the liver, pancreas, and their membrane tissues are not completely uniform, and it is considered that the portion with relatively large elasticity and the portion with relatively small elasticity are slightly mixed. Here, when two types of polyvinyl alcohols with different degrees of saponification are blended and cured with a crosslinking agent or coagulant, the physical properties indicated by the average degree of saponification appear as a whole. Can reproduce a biological tissue that naturally produces subtle variations. Therefore, by using two types of polyvinyl alcohols having different saponification degrees, the average saponification degree of the whole aqueous solution of partially saponified polyvinyl alcohol is adjusted, but dispersion due to blending is ensured.

Next, the curing agent will be described.
As the curing agent, either a coagulant or a crosslinking agent may be used for curing, or both the coagulant and the crosslinking agent may be used as a curing agent for curing. .
As the coagulant, dipotassium hydrogen citrate, sodium nitrite, zinc nitrate, (NH4) 2SO4, Na2SO4, K2SO4, ZnSO4, CuSO4, FeSO4, MgSO4, Al2 (SO4) 3, KAl (SO4) 2, NH4NO3 Any of KNO3, NaCl, KCl, Na2PO4, K2CrO4, H3BO3, or a combination thereof.
The crosslinking agent is boric acid, phosphonic acid, phosphoric acid, chromic acid, or any of these compounds, or a combination thereof.
The concentration of the curing agent is 2 to 30% by weight, or 20 ° C. saturated concentration. Specifically, the amount is determined in consideration of an amount sufficient to coagulate or crosslink the partially saponified polyvinyl alcohol mixed aqueous solution.

Next, optional additives for the partially saponified polyvinyl alcohol mixed aqueous solution will be described. As one of the additives, a metal hydrosol can be raised. By adding the metal hydrosol, it is possible to improve the structural strength of the molded product and to reproduce the diversity of each minute part.
Examples of the metal hydrosol include a fine particle silica hydrosol, a titanina hydrosol, an alumina hydrosol, and a zirconia hydrosol. It can be prepared by containing 3 wt% to 30 wt%, more preferably 4 wt% to 10 wt% of the metal hydrosol with respect to the mixed aqueous solution of partially saponified polyvinyl alcohol obtained above.
In the configuration using only the coagulant as the curing agent, it can also be used as an alkali agent for gelling the metal hydrosol.

[Multilayer film part 120]
The multilayer film part 120 is formed by multilayering by stacking a plurality of single-layer film parts 110. In the multilayer film part 120, the fiber part 130 is interposed between the single-layer film part 110 and the single-layer film part 110.
As for the adhesion between the single-layer film parts 110, the single-layer film part 110 originally has some adhesiveness, and the fiber part 130 interposed between them also has adhesiveness, so If the single-layer film parts 110 are pressure-bonded, the multilayer film part 120 has a stable structure.

[Fiber parts 130]
Next, the fiber part 130 will be described.
The fiber part 130 simulates a muscle fiber structure formed of a gel material.
In the organ membrane, the membrane tissue and the muscle tissue are connected with the blood vessel interposed therebetween, and the muscle tissue is split between the internal muscle tissue and the membrane tissue where the membrane tissue is peeled off, and becomes a fibrous form. In the organ membrane model 100 of the present invention, a fiber part 130 that simulates this muscle tissue is created.
The fiber part 130 includes a main structure of a fiber structure made of a gel-like material serving as a base material for reproducing a shape in which a plurality of filaments are intertwined so as to have a structure close to a fiber structure.

The material of the main structure of the fiber part 130 is preferably a material that can easily simulate a fibrous structure. For example, a thread obtained by extruding a sodium alginate aqueous solution into a calcium chloride aqueous solution with a syringe is formed into fibers. There is a fibrous alginate gel formed.
Furthermore, the surface of the main structure of the fiber structure can be coated with a coating body. That is, the tensile strength close to that of an actual fiber structure is reproduced by providing a coating body so as to coat the surface of the main structure having a fiber structure in which a plurality of filaments are intertwined. For example, as a material of the coating body, there is a polyvinyl alcohol gel formed by crosslinking a polyvinyl alcohol aqueous solution with a crosslinking agent.

In the example shown in FIG. 2, the main structure 131 of the fiber part 130 is formed of a fibrous alginate gel, and the coating body 132 is formed by coating the surface with a polyvinyl alcohol gel obtained by crosslinking a polyvinyl alcohol aqueous solution with a crosslinking agent. Will be.
FIG. 2B is a diagram illustrating a state where the single-layer film part 110 is peeled off from the multilayer film 120. It can be seen that the internal fiber part 130 inserted between the single-layer film parts 110 is split into fibers.
The configuration example of the organ membrane model 100 has been described above.

[Vessel model 210]
The blood vessel model 210 will be described.
The blood vessel model 210 simulates blood vessels related to an organ, particularly important blood vessels such as arteries and veins. Since organs use a large amount of blood for activity, arteries and veins often pass. The handling of blood vessels such as arteries and veins is important in the procedure. It is important to reproduce the arteries and veins that go to the organ as training.

  The blood vessel model 210 also has flexibility and elasticity as a human tissue. Therefore, the ideal blood vessel model 210 can be formed if a gel material is selected that has flexibility, elasticity, echo characteristics, and the response of the procedure performed by a medical electronic device such as an electric knife close to that of an actual blood vessel. The For example, it is formed of polyurethane gel or the like.

The blood vessel model 210 has a complicated shape, and it is difficult to integrally mold the organ body model 220 and the blood vessel model 210 at the same time. Therefore, the blood vessel model 210 is manufactured in advance separately from the organ body model 220, and after the created blood vessel model 210 is placed on the mold for the organ body model 220, the gel material for the organ body model 220 is poured to heat it. In addition, it can be molded by integrating them.
FIG. 3 is a diagram simply showing how the blood vessel model 210 is manufactured using a three-dimensional printer. As shown in FIG. 3A, the blood vessel model 210 can be formed of a gel material using a three-dimensional printer. For example, a solid is formed using an ultraviolet curable material. Here, a material mainly composed of an ultraviolet curable polyurethane gel is a three-dimensional printer capable of three-dimensional modeling by ultraviolet irradiation. Such 3D printers can be procured in the market.
As shown in FIG. 3B, the blood vessel model 210 is arranged at a predetermined position with respect to the organ model template 300 on which the organ membrane model 100 is spread.

[Organ body model 220]
Next, the organ body model 220 will be described.
The organ body model 220 is a model of the kidney body, and the actual organ and its flexibility, elasticity, echo characteristics, and the response of the procedure by a medical electronic device such as an electric knife are close to the actual organ. If the gel material to be selected is selected, an ideal organ body model 220 is formed. For example, a thermosetting polyvinyl alcohol gel material (PVA gel material) is used.

In this configuration example, the organ body model 220 is formed of a mixed polyvinyl alcohol gel material obtained by gelling a mixture of two types of polyvinyl alcohol aqueous solutions having an average polymerization degree of 300 to 3500 and different saponification degrees. .
For example, a polyvinyl alcohol aqueous solution having a saponification degree of 97 mol% to 99 mol% is used as the first saponified polyvinyl alcohol aqueous solution, and a saponification degree of 50% to 80 is used as the second saponified polyvinyl alcohol aqueous solution. As an example, an aqueous polyvinyl alcohol solution having a saponification degree of 72.5 mol% to 74.5 mol% is used. A partially saponified polyvinyl alcohol mixed aqueous solution prepared by mixing these two types of saponified polyvinyl alcohol aqueous solutions at a predetermined ratio to prepare a saponification degree of the whole mixed solution to 50 mol% or more and less than 90 mol%, It can be formed by introducing a curing agent comprising a crosslinking agent and curing.
The average polymerization degree is in the range of 300 to 3500, the first polyvinyl alcohol aqueous solution having a saponification degree of 97 mol% to 99 mol% and a saponification degree of 50% to 80 mol%. Since there are many points similar to the method of forming the single-layer part 110 of the organ membrane model 100 with respect to the point of blending and curing the second aqueous polyvinyl alcohol solution of the degree, explanation here is omitted.
FIG. 4 is a diagram showing how the organ body model 200 is formed.
As shown in FIG. 4A, the above-described polymer gel is injected into the organ model template 300 via a gel injection device.
Thereafter, as shown in FIG. 4B, the organ model 200 is completed by heating at a predetermined temperature for a predetermined time to be thermoset.
As shown in FIG. 5, the completed organ model 200 is taken out from the organ model template 300.

The above is the description of the components of the organ membrane model 100 and the organ model 200 including the organ membrane model 100 and the manufacturing method thereof.
Next, an organ membrane model 100 was actually made as shown below.

[Prototype 1 of single layer film model 110]
In order to simulate the tissue film and finish the single-layer film model 110, a tensile strength that does not break is necessary. Since the strength of PVA alone is weak, an attempt was made to improve the strength by combining two types of gels.

[Materials used]
PVA-117 aqueous solution (15wt%) 95.0g
Sodium polyacrylate aqueous solution (5wt%) 5.0g
Silica sol (Snowtex ZL) 2.6g
Tripotassium citrate aqueous solution (1M) 12mL
Aqueous sodium hydroxide (1M) 4.0mL
Trisodium borate aqueous solution (0.5M)
Ocher pigment 0.3g

[Production method]
95 g of 15 wt% PVA-117 aqueous solution and 5.0 g of 5 wt% sodium polyacrylate aqueous solution were mixed and stirred while heating to 80 ° C. The mixed solution was cooled to room temperature, and 2.6 g of silica sol was added and stirred. Then, 12 mL of 1M tripotassium citrate aqueous solution was added dropwise with stirring. Thereafter, 4.0 mL of 1M aqueous sodium hydroxide solution was added dropwise, 0.3 g of ocher pigment was added, stirred, vacuum degassed, poured into a mold, and frozen overnight. After thawing in a refrigerator, it was immersed in a 0.5M trisodium borate aqueous solution for 1 minute.

[result]
The strength seemed to be sufficiently higher than that of the actual organ membrane, but it was harder to stretch than the actual organ membrane and the extensibility was small.

[Trial production of single layer film model 2]
In the trial production 1 of the single-layer membrane part 110 shown in Example 1, it was difficult to stretch as compared with the actual organ membrane, so that the degree of cross-linking is reduced in order to reproduce the extensibility close to the actual organ membrane. . In the manufacturing process of Example 1, the treatment with the trisodium borate aqueous solution is eliminated, and the film is changed to stretch.
That is, when treated with a trisodium borate aqueous solution, the degree of crosslinking increases and the elongation is small even when pulled. The treatment of the aqueous sodium hydroxide solution and the trisodium borate aqueous solution was eliminated, and the membrane was changed so that the film was stretched while suppressing the degree of crosslinking.

[Materials used]
PVA-117 aqueous solution (15wt%) 95.0g
Sodium polyacrylate aqueous solution (5wt%) 5.0g
Silica sol (Snowtex ZL) 2.6g
Tripotassium citrate aqueous solution (1M) 12mL
Aqueous sodium hydroxide (1M) 4.0mL
Trisodium borate aqueous solution (0.5M)
Ocher pigment 0.3g

[Production method]
95 g of PVA-117 (15 wt%) aqueous solution and 5.0 g of 5 wt% sodium polyacrylate aqueous solution were mixed and stirred while heating to 80 ° C. The mixed solution was cooled to room temperature, and 2.6 g of silica sol was added and stirred. Then, 12 mL of 1M tripotassium citrate aqueous solution was added dropwise with stirring. Thereafter, 0.3 g of an ocher pigment was added, stirred, vacuum degassed, poured into a mold and frozen overnight. Thawed in the refrigerator. In addition, the immersion process to 0.5M trisodium borate aqueous solution is not performed after thawing.

[result]
The strength was sufficiently higher than that of the actual organ membrane, and the extensibility close to that of the actual organ membrane was obtained. Since the treatment with trisodium borate was not performed, the incision with an electric knife was good.

[Prototype 1 of multilayer film model 1]
[Production method]
As a trial production 1 of the multilayer film model 120, a trial production was performed with a configuration in which the fiber part 130 was not inserted.
A multilayer film model 120 was manufactured by simply press-bonding the single-layer film part 110 made of PVA-117 created in Example 2 as a main component and multilayering it.
[result]
When the single-layer film parts 110 of the prototype multilayer film model 120 were peeled apart, a fibrous structure was not reproduced between the peeled surfaces.

[Prototype 1 of fiber part 130, prototype 2 of multilayer film model 120 interpolated therewith]
A fiber part 130 according to Example 4 is manufactured as a prototype. A fibrous alginic acid gel formed by entwining a filamentous body obtained by extruding a sodium alginate aqueous solution into a calcium chloride aqueous solution into a thread by a syringe is obtained.

(1) Single layer film part 110
[Materials used]
PVA-117 (15wt%) aqueous solution 300g
Silica sol (Snowtex ZL) 8g
94 mL of tripotassium citrate aqueous solution (1M)
Red pigment 0.3g
[Production method]
After adding 8 g of silica sol to 300 g of PVA-117 (15 wt%) aqueous solution and stirring, 94 mL of 1 M tripotassium citrate aqueous solution was added dropwise with a burette while stirring. Thereafter, 0.3 g of a red pigment was added, stirred, vacuum degassed, poured into a mold and frozen overnight. Thawed in the refrigerator. In addition, the immersion process to 0.5M trisodium borate aqueous solution is not performed after thawing.

(2) Fiber parts 130 (main structure only)
[Materials used]
Sodium alginate aqueous solution (1wt%)
Calcium chloride aqueous solution (1M)
[Production method]
A 1 wt% aqueous sodium alginate solution was placed in a syringe and extruded into a 1 M aqueous calcium hydroxide solution to prepare a fibrous alginate gel (the inner diameter of the needle used was 0.6 mm).

FIG. 6 is a diagram illustrating a production example of the organ membrane model 100 according to the fourth embodiment.
FIG. 6A is a prototype example of the fiber part 130. It can be seen that the structure in which the fiber parts 130 made of the fibrous alginate gel are intertwined in a fibrous form can be reproduced.

(3) Multilayer film model 120
[Production method]
Two single layer film parts 110 of the prepared PVA thin film were thawed and applied with the same PVA material as an adhesive (the remainder of PVA obtained in the process of creating the single layer film part 110 was used). The produced fiber part 130, which is an alginate fiber, was placed between the single layer film parts 110 to be multilayered to form a multilayer film part 120, which was frozen overnight while being sandwiched from above and below.

[result]
When the single-layer film parts 110 of the multilayer film model 120 according to the prototype Example 4 were peeled apart, the fiber parts 130 between the peeled surfaces were peeled into fibers. For the time being, the appearance of the muscle fiber tissue peeling off could be reproduced.
However, the fiber part 130 formed only with the main structure of the alginate gel may be easily broken and broken.
FIG. 6B is a diagram illustrating a state where the single-layer film part 110 of the multilayer film model 120 according to the fourth example is peeled off and peeled off. The fiber part 130 formed of only the alginate gel is pulled and the other part is broken and the others are broken and broken.

Although it was confirmed from the results of Example 4 that the alginate gel is a suitable material for simulating muscle fibers, the fiber part 130 of only the main structure of the alginate gel melts and easily breaks. I found out there was a fear. It is possible to increase the structural strength by cross-linking and gelling other elastic gel materials such as PVA. For example, as a method of simply mixing and gelling to improve the structural strength, there is a method of gelling a sodium alginate / PVA-117 mixed solution, but the width of the produced fiber part 130 becomes thick (with a diameter of about 1 mm), there is a possibility that the applicable range of the fiber part 130 of the organ membrane model 100 is limited.
Therefore, in Example 5, a structure in which the surface of the main structure alginate gel was coated with a PVA gel coating was fabricated. If the surface of the main structure alginate gel is coated with PVA gel, the tensile strength is improved.

(1) Single layer film part 110
The single layer film part 110 is the same as that manufactured in the fourth embodiment.

(2) Fiber part 130 (the surface of the main structure coated with PVA)
[Materials used]
Sodium alginate aqueous solution (1wt%)
Mixed solution of calcium chloride aqueous solution (1M) and PVA-117 (5w%) Saturated boric acid aqueous solution

[Production method]
Prepare a mixed solution (1M) of calcium chloride aqueous solution and PVA-117, and extrude a 1wt% sodium alginate aqueous solution from the syringe into the solution (the inner diameter of the used needle is 0.6mm) to create a fibrous alginate gel. did. In this state, uncrosslinked PVA is clinging around the fibrous alginate gel. PVA-117 contained on the surface was crosslinked by applying a saturated boric acid aqueous solution to the formed fibrous alginate gel.

[result]
FIG. 7 is a diagram illustrating a prototype example in which the fiber part according to Example 5 is coated.
FIG. 7 (a) is an example of manufacturing an alginate gel in which uncrosslinked PVA is wrapped around. In this state, PVA is in an uncrosslinked state.
FIG. 7B is a view showing a state in which PVA-117 is crosslinked by applying a saturated boric acid aqueous solution to an alginate gel in which uncrosslinked PVA is wrapped around.
The surface is slightly foamed due to the crosslinking reaction.
The diameter of the alginate gel coated with the coating body was 0.7 mm. The structure of the fiber part 130 can be reproduced if the alginate gel coated with the crosslinked PVA is entangled in a fibrous form.

(3) Multilayer film model 120
[Production method]
This is an alginate gel fiber in which a single layer film part 110 of a thawed PVA thin film is placed in a mold, and the same PVA-117 is applied as an adhesive, and the single layer film part 110 is coated with a PVA crosslinked body. The fiber part 130 was arrange | positioned, the remaining PVA-117 was poured from the top, and it frozen in the freezer overnight.

[result]
When the single-layer membrane parts 110 of PVA were peeled off, the fiber part 130 did not break and was peeled off into a fibrous form.
FIG. 8 is a diagram illustrating a state where the upper layer film of the organ membrane model 100 according to the fifth example is peeled off.
As shown in FIG. 8, when the single-layer film part 110 that is the upper layer is peeled off, it can be seen that the interleaved fiber part 130 is peeled off into a fibrous shape without breaking.

  In this way, as an organ model, flexibility and elasticity are close to those of an actual organ, and three-dimensional reproduction of membrane tissues, muscle fibers, blood vessels, etc. that cover the organ, and reactions in procedures using medical instruments such as an electric knife Can also produce an organ model close to the actual reaction.

  As mentioned above, although preferred embodiment in the structural example of the organ membrane model of this invention was illustrated and demonstrated, it will be understood that various changes are possible without deviating from the technical scope of this invention. .

  The organ membrane model of the present invention can be widely applied as a training model for procedures for human organs and the like.

DESCRIPTION OF SYMBOLS 100 Organ membrane model 110 Monolayer membrane part 120 Multilayer membrane part 130 Textile part 200 Organ model 210 Blood vessel model 220 Organ body model

Claims (6)

An organ membrane model simulating membrane tissue including fiber tissue,
A multilayer film part having a multilayer structure in which a single-layer film part simulating a single layer of the film structure formed of a gel-like material is overlaid or bonded, and
Provided with fiber parts simulating the fiber structure formed of a gel-like material,
An organ membrane model, wherein the fiber parts are arranged between layers of the multilayer membrane parts.   The fiber part has a main structure of a fiber structure made of a gel-like material serving as a base material for reproducing a shape in which a plurality of filaments close to the fiber structure are intertwined, and a tensile strength close to the fiber structure. 2. The organ membrane model according to claim 1, wherein the organ membrane model is formed in combination with a coating body made of a gel-like material coated on the surface of the main structure of the fibrous tissue.   The main structure of the fiber part is a fibrous alginic acid gel formed by extruding a sodium alginate aqueous solution into a calcium chloride aqueous solution with a syringe and threading the filamentous body into a fibrous shape. The organ membrane model described.   The fiber part has a structure in which the surface of the fibrous alginic acid gel, which is the main structure of the fiber part, is coated with a coating made of polyvinyl alcohol gel formed by crosslinking a polyvinyl alcohol aqueous solution with a crosslinking agent. Item 5. The organ membrane model according to Item 3. An organ membrane model according to any one of claims 1 to 4,
With an organ body model formed by pouring a gel material for an organ model in a state where a blood vessel model is placed on an organ model template as necessary,
An organ model covered with an organ membrane model formed by covering the organ body model with the organ membrane model. A method for forming an organ membrane model according to any one of claims 1 to 4,
Forming the main structure of the fiber part comprising the fibrous alginate gel obtained by extruding a sodium alginate aqueous solution into a thread form from a syringe to a mixed aqueous solution of a calcium chloride aqueous solution and a polyvinyl alcohol aqueous solution, and entangled to form a fiber. Process,
A second step of adding a crosslinking agent to the polyvinyl alcohol to crosslink the polyvinyl alcohol around the main structure of the fiber part to form a coating around the main structure of the fiber part; ,
A third step of forming a multilayer film part having a multilayer structure by sandwiching the fiber parts when a single-layer film part simulating a single layer of a film structure formed of a gel-like material is stacked or bonded, Organ membrane model formation method.