JP5290103B2 - Biological model for training - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a biological model for training, which can be approximated to the physical property of an actual narrow segment in the training aiming at the improvement of operator's skills by using the biological model for training. <P>SOLUTION: The biological model 1 for training includes a right coronary artery 4 consisting of a tubular body having a reduced diameter portion 44 wherein the diameter of the tubular body is reduced in the longitudinal course and imitating a tubular tissue, and a reinforcing member 7 provided on the outer circumferential side of the reduced diameter portion 44 to reinforce the reduced diameter portion 44. The reduced diameter portion 44 and the reinforcing member 7 constitute a pseudo-lesion part 21 imitating a narrow segment occurring in a tubular tissue. The pseudo-lesion part 21 is used in dilation training for conducting dilation of the narrow segment. <P>COPYRIGHT: (C)2011,JPO&amp;INPIT

Description

  The present invention relates to a biological model for training.

  As one of the percutaneous coronary angioplasty, for example, PTCA (Percutaneous Transluminal Coronary Angioplasty) is known.

  In this PTCA technique, when the transfemoral artery method is applied, the blood flow in the blood vessel is recovered through the following procedure. That is, I.I. First, insert a sheath catheter into the femoral artery, then insert a guide catheter guide wire into the femoral artery, and advance the guide catheter along the guide catheter guide wire with its tip advanced to the vicinity of the coronary artery entrance. The tip is located at the coronary ostium. II. Next, the guide wire for the guide catheter is removed, the guide wire for the balloon catheter is inserted into the guide catheter, the guide wire for the balloon catheter is projected from the distal end of the guide catheter, and a stenotic site (lesion) occurring in the coronary artery Advance to a position beyond (part). III. Next, the balloon catheter is advanced to the stenosis site via the balloon catheter guide wire, and after the balloon portion is positioned at the stenosis site, the balloon is inflated to widen the stenosis site, that is, the blood vessel wall and re-open the blood passage. Form and restore blood flow.

  As described above, in order to position the balloon catheter at the stenosis site, there are complicated steps, and the operator is required to have a very advanced technique.

  Therefore, in recent years, in addition to surgery for patients, development of a biological model used for training for improving an operator's technique is required.

  As such a living body model, for example, Patent Document 1 proposes a method of manufacturing a tube model using a tube such as a blood vessel or a lymph vessel.

  That is, in Patent Document 1, first, a cavity region of the subject is extracted based on the tomographic image data of the subject obtained by an image diagnostic apparatus such as a CT scanner or an MRI scanner, and corresponds to the cavity region. Laminate the lumen model. Next, the three-dimensional model molding material is cured in a state where the periphery of the lumen model is surrounded by the three-dimensional model molding material, and then the lumen model is removed to form a tube model (three-dimensional model).

  In the three-dimensional model having such a configuration, silicone rubber, polyurethane elastomer, or the like is used as the three-dimensional model molding material, and the tube model is formed by approximating the physical properties of blood vessels and lymph vessels. Since this three-dimensional model is formed so as to surround the lumen model, the stenosis site, which is a lesion site, is also formed integrally with the tube, and exhibits the same physical properties as the tube, that is, elasticity. It will be. However, for example, a stenosis site formed in a blood vessel is mainly composed of plaques (deposits) on which cholesterol is deposited, so that its physical properties are significantly different from those of blood vessels.

  Therefore, in the three-dimensional model described in Patent Document 1, it is not possible to carry out training corresponding to the physical properties of the actual plaque generated in the stenosis site, and the state of the plaque after the balloon is inflated at the stenosis site cannot be confirmed. There is a problem that it is impossible to know how the blood flow path is reconstructed.

Japanese Patent No. 361568

  The object of the present invention is to train the living body model for training by approximating the physical properties of the actual stenosis when performing training for improving the skill of the surgeon using the living body model for training. It is to provide a biological model for training.

Such an object is achieved by the present invention of the following (1) to ( 10 ).
(1) A pseudo-tubular tissue that is formed of a tubular body, has a reduced diameter portion that is reduced in diameter in the longitudinal direction, and imitates a tubular tissue;
A reinforcing member made of a plastically deformable material including at least one of silicone clay, rubber clay, resin clay and oil clay, which is provided on the outer peripheral side of the reduced diameter portion and reinforces the reduced diameter portion; With
The reduced diameter portion and the reinforcing member constitute a pseudo stenosis portion simulating a stenosis portion generated in a tubular tissue, and the pseudo stenosis portion is used for expansion training for expanding the stenosis portion. Biological model for training.

  (2) The training biological model according to (1), wherein the pseudo-stenosis part is plastically deformed so as not to return to the shape before expansion when the expansion training is performed.

(3) The living body model for training according to the above ( 1 ), wherein the reduced diameter portion is made of a plastically deformable material.

(4) The training biological model according to (1) or (2) , wherein the reduced diameter portion is made of an elastic material.

(5) The training biological model according to any one of (1) to ( 3 ), wherein at least the reduced diameter portion of the pseudo tubular tissue is made of a thermoplastic resin.

(6) the the reduced diameter portion, the internal diameter of the reduced diameter portion at one end or both ends (1) to the tapered portion gradually increases toward the end portion side is formed from the inner side (5 ) The biological model for training according to any one of the above.

( 7 ) The living body model for training according to any one of (1) to ( 6 ), wherein the reinforcing member has a ring shape along a circumferential direction of the reduced diameter portion.

( 8 ) The living body model for training according to any one of (1) to ( 7 ), further including a restricting member that is installed on an outer peripheral side of the reinforcing member and restricts the deformation when the reinforcing member is deformed.

( 9 ) The living body model for training according to ( 8 ), wherein the restriction member is a ring-shaped band made of a plastically deformable material or an elastic material.

( 10 ) Any one of the above (1) to ( 9 ), wherein one or more medical instruments are inserted through the pseudo-tubular tissue to reach the pseudo-stenosis, and then the expansion training is performed. Biological model for training described in 1.

  In the training biological model of the present invention, the medical instrument is preferably a balloon catheter and / or stent used for percutaneous coronary angioplasty.

  According to the present invention, the pseudo-stenosis part approximated to the physical property of the stenosis part generated in the tubular tissue can be disposed at any position and in any size (shape). Therefore, since the training corresponding to various patient pathologies can be performed using the biological model for training provided with this pseudo-stenosis, the surgeon learns a higher level of technology at a place other than the operation performed on the patient. be able to.

It is a schematic diagram which shows the artery (a heart is included) in a human body whole body. It is a whole photograph of what applied the artery shown in Drawing 1 to a solid model. It is a mimetic diagram showing an embodiment (the 1st embodiment) when the living body model for training of the present invention is arranged in the right coronary artery. It is a figure which shows the procedure of performing the training (expansion training) of PTCA operation with respect to the biological model for training arrange | positioned in the right coronary artery. It is a longitudinal cross-sectional view which shows in order the state when performing the training of PTCA surgery with respect to the biological model for training (1st Embodiment) of this invention. It is a figure for demonstrating the method to manufacture the biological model for training shown in FIG. It is a figure for demonstrating the connection method with respect to the biological model for training of this invention. It is a figure for demonstrating the connection method with respect to the biological model for training of this invention. It is a longitudinal cross-sectional view which shows in order the state at the time of performing the training of PTCA technique with respect to the biological model for training (2nd Embodiment) of this invention. It is a longitudinal cross-sectional view which shows the biological model for training (3rd Embodiment) of this invention. It is a longitudinal cross-sectional view which shows the biological model for training (4th Embodiment) of this invention. It is a schematic diagram which shows embodiment (5th Embodiment) when the biological model for training of this invention is arrange | positioned in the left coronary artery. It is a longitudinal cross-sectional view which shows the biological model for training (5th Embodiment) of this invention. It is a figure for showing the frequent occurrence site of a lesion where the living body model for training of the present invention is arranged. It is a figure which shows the test method which tests the material characteristic of pseudo-tubular tissue. It is a graph which shows the material characteristic (change with time of stress) of the pseudo-tubular structure | tissue tested by the test method shown in FIG.

Hereinafter, a living body model for training of the present invention is explained in detail based on a suitable embodiment shown in an accompanying drawing.
FIG. 1 is a schematic diagram showing arteries (including the heart) in the whole human body, FIG. 2 is an overall photograph of the arteries shown in FIG. 1 applied to a three-dimensional model, and FIG. FIG. 4 is a schematic diagram showing an embodiment (first embodiment) when placed in the coronary artery, and FIG. 4 shows a procedure for performing PTCA surgery training (expansion training) on a training biological model placed in the right coronary artery. FIGS. 5 and 5 are longitudinal cross-sectional views sequentially showing the state when PTCA training is performed on the living body model for training of the present invention (first embodiment), and FIG. 6 is the living body for training shown in FIG. FIGS. 7 and 8 are diagrams for explaining a method for manufacturing a model, FIG. 7 and FIG. 8 are diagrams for explaining a connection method to the biological model for training of the present invention, and FIG. 9 is a biological model for training of the present invention ( PTCA training is being performed for the second embodiment) FIG. 10 is a longitudinal sectional view showing a biological model for training of the present invention (third embodiment), and FIG. 11 is a biological model for training of the present invention (fourth embodiment). FIG. 12 is a schematic diagram showing an embodiment (fifth embodiment) when the training biological model of the present invention is placed in the left coronary artery, and FIG. 13 is a training biological model of the present invention. Fig. 14 is a longitudinal sectional view showing (fifth embodiment), Fig. 14 is a diagram for showing a site where a lesion is likely to be placed on which the living body model for training of the present invention is arranged, and Fig. 15 is a graph showing material properties of the pseudo-tubular tissue. FIG. 16 is a graph showing the material properties (stress change with time) of the pseudo-tubular tissue tested by the test method shown in FIG. In the following description, the upper side in FIGS. 1 to 14 is referred to as “upper” and the lower side is referred to as “lower”. 3, 12, and 14 also illustrate the shape of the heart so that the shape and position of the coronary artery can be easily understood.

  The three-dimensional model shown in FIG. 2 is artificially manufactured by reproducing the various tubular tissues of a human living body including tubular tissues such as blood vessels (arteries, veins), lymphatic vessels, bile ducts, ureters, and oviducts. It is a thing. Using this three-dimensional model, a medical device such as a balloon catheter is made to reach the pseudo-lesioned part (pseudo-stenosis part), and then the pseudo-lesioned part is expanded to secure a flow path, or the expanded pseudo-lesioned part is stented Training for detention is carried out. In the following, when a pseudo-lesioned part simulating a lesion (stenosis) generated in the artery is arranged (provided) in a pseudo-tubular tissue (simulating a tubular tissue) formed corresponding to the shape of the artery Will be described as an example.

  Arteries (including the heart) in the whole human body have a shape as shown in the schematic diagram of FIG. A three-dimensional model corresponding to the shape of the artery is manufactured as follows based on, for example, the description of Japanese Patent No. 3613568.

  First, tomographic image data of a cavity (blood flow path) provided in an artery is obtained using an image diagnostic apparatus such as a CT scanner or an MRI scanner, and then based on the tomographic image data corresponding to the lumen of the artery. Then, a lumen model that forms the shape of the lumen of the artery is layered.

  Next, after hardening the three-dimensional model molding material in a state in which the periphery of the lumen model is surrounded by the three-dimensional model molding material, the lumen model is removed, and the shape of the artery as shown in the whole photograph of FIG. An arterial model (three-dimensional model) corresponding to is formed.

  By placing a pseudo-lesioned part at an arbitrary position such as a coronary artery, a cerebral artery, a carotid artery, a renal artery, a brachial artery, etc. After the medical instrument is positioned at the pseudo-lesioned portion (stenosis model), expansion training for securing the flow path can be performed by expanding the pseudo-lesioned portion. In the present embodiment, the living body model 1 for training is configured such that a pseudo-lesioned part (pseudo-stenosis part) 21 is disposed on a coronary artery (pseudo-tubular tissue) 10 included in an arterial model.

  The coronary artery 10 includes a left coronary artery 3 and a right coronary artery 4 that branch left and right in the Valsalva sinus of the aorta 5.

  The right coronary artery 4 exits from the upper part of the right coronary sinus, which is one of the Valsalva sinus, and is covered with the right atrial appendage and travels between the right atrium and the pulmonary artery, and sharp edges along the right interventricular groove A blood vessel that feeds the rear wall of the left ventricle and the lower side of the septum is derived from the posterior interventricular groove through the part 41 and toward the descending descending branch 42.

  In the right coronary artery 4, the upper half of the right coronary artery 4 from the entrance to the sharp edge 41 is called Segment1 (# 1: Proxy), and the lower half is called Segment2 (# 2: Middle). The process from the sharp edge 41 to the branch at the descending descending branch 42 is referred to as Segment 3 (# 3: distal). Further, the branch and subsequent branches of the rear descending branch 42 are referred to as Segment 4, and this Segment 4 is divided into three parts, # 4AV, # 4PD, and # 4PL.

  The left coronary artery 3 branches leftward from the upper part of the left coronary sinus, which is one of the Valsalva sinus, and branches into a left anterior descending branch 31 and a left convoluted branch 32 that enter the anterior chamber groove.

  A portion from the aorta 5 to the branch to the left anterior descending branch 31 and the left rotating branch 32 is referred to as a left main trunk 33 (Segment 5). The left front descending branch 31 is subdivided into Segments 6 to 10, and the main trunk of the left front descending branch 31 is Segment 6 (# 6: Proximal), Segment 7 (# 7: Middle), Segment 8 (# 8: (segment 9), segment 9 (# 9: first diagonal branch) branches from between segment 6 and segment 7, and segment 10 (# 10: second diagonal branch) from between segment 7 and segment 8. Branched. Further, the left circumflex branch 32 is subdivided into Segments 11 to 15, and the main trunk of the left convolution branch 32 is classified into two segments, Segment 11 (# 11: Proximal) and Segment 13 (# 13: distal). Segment 12 (# 12: obtuse marginal branch: OM) branches off from the connection part of Segment 11 and Segment 13.

<< First Embodiment >>
The training biological model 1 according to the first embodiment shown in FIGS. 4 and 5 includes a right coronary artery 4 (Segment 2) of the coronary artery 10 and connection portions 11 provided at both ends of the right coronary artery 4, respectively. Yes. In the right coronary artery 4, the end portion of the Segment 2 is connected to the Segment 1 and the Segment 3 via the respective connection portions 11. In this case, each connection part 11 is preferably configured to be detachable from Segment 1 and Segment 3.

  In addition, PTCA surgery training is performed on the pseudo-lesioned portion 21 disposed in the right coronary artery 4. Such training is performed according to the following procedure.

  [1] First, a sheath catheter (not shown) is inserted into the femoral artery, then a guide catheter guide wire (not shown) is inserted into the femoral artery, and the distal end is advanced to the vicinity of the entrance of the right coronary artery 4 Then, the guide catheter 61 is advanced along the guide wire for the guide catheter, and the distal end thereof is positioned at the entrance of the right coronary artery 4 (see FIG. 4A).

  [2] Next, the guide catheter guide wire 62 is removed, the balloon catheter guide wire 62 is inserted into the guide catheter 61, the balloon catheter guide wire 62 projects from the distal end of the guide catheter 61, and the right coronary artery 4. The guide wire 62 for the balloon catheter is advanced to a position beyond the pseudo-lesioned portion 21 disposed in (see FIG. 4B).

  [3] Next, the distal end portion of the balloon catheter 63 inserted from the proximal end (femoral artery) side of the balloon catheter guide wire 62 is projected from the distal end of the guide catheter 61, and further along the balloon catheter guide wire 62. The balloon 64 is inflated by injecting a balloon inflation fluid into the balloon 64 from the proximal end side of the balloon catheter 63 after the balloon 64 of the balloon catheter 63 is positioned at the pseudo-lesioned portion 21 (see FIG. 4 (c).) Thereby, the pseudo-lesioned part 21 is pushed and expanded.

  [4] Next, the balloon inflation fluid is discharged from the proximal end side of the balloon catheter 63, and the balloon 64 is deflated as shown in FIG. Thereafter, the balloon catheter guide wire 62, balloon catheter 63, guide catheter 61 and sheath catheter are removed from the femoral artery side. Thereby, a blood flow path is formed in the pseudo-lesioned part 21.

  As shown in FIG. 5 (a), the right coronary artery 4 is constituted by a tubular body having a lumen portion 43. In the middle of the right coronary artery 4 in the longitudinal direction, a reduced diameter portion 44 whose inner diameter and outer diameter are reduced is formed. Thereby, a concave portion 451 is formed in the outer peripheral portion 45 of the right coronary artery 4. In the recess 451, the reinforcing member 7 that reinforces the reduced diameter portion 44 is disposed (contained). In the training biological model 1, the pseudo-lesioned portion 21 is configured by the reduced diameter portion 44 of the right coronary artery 4 and the reinforcing member 7. Then, extension training (PTCA training) can be performed on the pseudo-lesioned part 21.

In the right coronary artery 4, the inner diameter φd ₁ and the outer diameter φd ₂ are constant along the longitudinal direction except for the portion where the reduced diameter portion 44 is formed. Such right coronary artery 4 is preferably one that satisfies the relationship of the ratio _d 2 / _{d 1} is 1.01 to 2, the ratio _d 2 / _{d 1} is the one that satisfies the 1.01 to 1.2 the relationship More preferred. Furthermore, it is preferable to set the inner diameter φd ₁ of the right coronary artery 4 (Segment 2) to about 0.5 to 10 mm and the outer diameter φd ₂ to about 0.51 to 12.0 mm.

The minimum inner diameter φd ₃ of the reduced diameter portion 44 is not particularly limited, but it is preferable to set φd ₃ so that (φd ₁ −φd ₃ ) / φd ₁ is 50 to 100%. By setting within the above range the minimum inner diameter .phi.d ₃ of reduced diameter portion 44, it is possible to reliably drills suitable for actual stenosis of the stenosis, the surgeon improved technique is achieved in precisely. Further, the minimum inner diameter .phi.d ₃ is preferably about 0.1 to 2.0 mm, and more preferably about 0.3 to 1.0 mm.

  Further, the length of the reduced diameter portion 44 is not particularly limited, but is preferably about 1 to 100 mm, and more preferably about 5 to 50 mm. By setting the length of the reduced diameter portion 44 within such a range, it is possible to carry out training more suitable for the size of the actual lesion site (stenosis site).

  At both ends of the reduced diameter portion 44, inclined surfaces (tapered surfaces (tapered portions)) 441 whose inner surfaces are inclined, that is, whose inner diameter gradually increases from the inner side toward the end side, are formed. . Accordingly, in the step [3], when the balloon 64 reaches the pseudo-lesioned part 21, the balloon catheter 63 can be placed along the inclined surface 441 of the reduced diameter part 44 (pseudo-lesioned part 21). The operation can be performed easily and reliably. The inclined surface 441 is not particularly limited, but is preferably inclined at an angle of about 15 to 65 ° with respect to the central axis of the right coronary artery 4 and is inclined at an angle of about 22 to 55 °. Is more preferable. Thereby, the training more suitable for the shape of the actual stenosis part can be implemented reliably. Further, in the configuration shown in FIG. 5, the inclined surface 441 is formed on both ends of the reduced diameter portion 44, but is not limited thereto, and may be formed only on one end side of the reduced diameter portion 44, for example. . When the inclined surface 441 is formed only on one end side of the reduced diameter portion 44, the inclined surface 441 is formed on the side where the balloon catheter 63 is inserted (the upper side in FIGS. 3 and 4). Is preferred.

  As shown in FIG. 5A, the reinforcing member 7 is disposed on the outer peripheral side of the reduced diameter portion 44 of the right coronary artery 4. The reinforcing member 7 reinforces the reduced-diameter portion 44 and has a characteristic similar to that of the actual lesion portion (stiffness (force against the radial force when the balloon 64 of the balloon catheter 63 is expanded) as a whole. )). For example, if the reinforcing member 7 is omitted and the pseudo-lesioned part 21 is composed of only the reduced diameter part 44, if the extension training is performed, the pseudo-lesioned part 21 is easily expanded by the amount of the reinforcing member 7 being omitted. There is a risk of overdoing it. For this reason, extension training does not approximate actual extension. However, in the training biological model 1, since the reduced diameter portion 44 is reinforced by the amount of the reinforcing member 7, the pseudo-lesioned portion 21 has characteristics approximating to the actual lesioned portion. It approximates the actual extension.

  The shape of the reinforcing member 7 is a ring shape along the circumferential direction of the reduced diameter portion 44. As a result, the entire reduced diameter portion 44 can be covered from the outside, and therefore the degree of reinforcement of the reduced diameter portion 44 is uniform along the circumferential direction. Further, it is possible to uniformly expand along the circumferential direction when the balloon is expanded, and further, since the reinforcing member 7 is prevented from falling off, there is an advantage that reliable expansion training can be performed.

The reinforcing member 7 preferably has a maximum thickness t _max of 0.1 to 5 mm, more preferably 0.25 to 4 mm.

  In such a pseudo-lesioned part 21, at least one of the reduced diameter part 44 and the reinforcing member 7 constituting the pseudo-lesioned part 21 is made of a plastically deformable material. That is, in the pseudo-lesioned portion 21, when the reduced diameter portion 44 and the reinforcing member 7 are each made of a plastically deformable material (hereinafter referred to as “first constituent material form”), the reduced diameter portion When 44 is made of a plastically deformable material and the reinforcing member 7 is made of an elastic material (this case is hereinafter referred to as “second constituent material form”), the reinforcing member 7 is a plastically deformable material. And the reduced diameter portion 44 is made of an elastic material (this case is hereinafter referred to as “third constituent material form”). And in any case of the 1st-3rd structural material form, the pseudo-lesioned part 21 will be plastically deformed.

<First constituent material form>
The entire right coronary artery 4 including the reduced diameter portion 44 is made of a plastically deformable material, and the material is not particularly limited, and polyethylene, polypropylene, ethylene / vinyl acetate copolymer, nylon elastomer, soft Examples thereof include thermoplastic resins such as polyvinyl chloride and ethylene / propylene copolymers, and one or more of them can be used in combination. Of these thermoplastic resins, it is particularly preferable to use polyethylene. In this case, a resin in which different densities, that is, crystallinity, such as low density polyethylene and high density polyethylene are mixed can also be used. The right coronary artery 4 is not limited to a material that is entirely made of a plastically deformable material. For example, the reduced diameter portion 44 is made of a plastically deformable material, and portions other than the reduced diameter portion 44 are formed. It may be composed of an elastic material.

  Further, the hardness of the right coronary artery 4 made of polyethylene is preferably 20 to 80 in Shore A (as defined in JIS K6253), and more preferably 25 to 35. The breaking strength is preferably 5 to 30 MPa, and more preferably 8 to 12 MPa. The elongation at break is preferably about 100 to 600%, more preferably about 100 to 200%.

  By using such polyethylene, the right coronary artery 4 can be reliably plastically deformed. Thereby, when expansion training is performed in combination with the reinforcing member 7, the reduced diameter portion 44 and the reinforcing member 7 are deformed collectively, and the deformed state (expanded state) is reliably maintained (FIG. 5B). reference). Moreover, when manufacturing the right coronary artery 4, the tubular body (tube) 40 used as the base material of the right coronary artery 4 can be shape | molded by extrusion molding. Then, after the tubular body is formed, the diameter-reduced portion 44 having a desired size can be manufactured by processing the tubular body (for example, heating or compression) (see FIG. 6).

  In addition, the plastically deformable material constituting the right coronary artery 4, that is, the thermoplastic resin has a material characteristic that the stress relaxation rate is preferably 20 to 60%, more preferably 20 to 30%.

  Here, the “stress relaxation rate” is obtained (defined) by testing the tubular body 40 at room temperature by the test method shown in FIG.

  First, as shown in FIG. 15A, the tubular body 40 is made into a strip 403, and one end (left side in the figure) of the strip 403 is fixed to become a fixed end 401, and the other end (right side in the figure) is It is a free end 402. Further, the strip 403 at this time has an overall length L.

Next, from the state shown in FIG. 15A, the free end 402 of the strip 403 is pulled to the right side (longitudinal direction) in the figure at a predetermined speed (tensile speed) (see FIG. 15B). The conditions at this time are pulled so that the total length becomes 2 L in one minute. The initial tensile stress when the total length becomes 2 L is defined as f ₀ (see FIG. 16).

Next, the speed (pulling speed) is set to zero from the state shown in FIG. Then, the tensile stress after 5 minutes of the velocity to zero and f _t (see FIG. 15 (c)).

Therefore, it is assumed that can represent a "stress relaxation ratio" in _{((f 0 -f t) /} f 0) × 100.

  When the stress relaxation rate is within such a numerical range, the pseudo-lesioned portion 21 (the reduced diameter portion 44) is more reliably deformed during expansion training, and thus approximates to an actual human artery. It will be a thing. Thereby, when extended training is performed, the same feeling as if the training is performing an actual procedure (PTCA technique) is obtained. The magnitude of the stress relaxation rate can be adjusted, for example, by appropriately selecting a constituent material or changing the molecular weight or molecular structure (crystallinity).

  Further, the tensile elastic modulus in the circumferential direction of the right coronary artery 4 is preferably 0.5 to 50 MPa, and more preferably 0.5 to 5.0 MPa.

  The reinforcing member 7 is made of a plastically deformable material, which is preferably different from the constituent material of the right coronary artery 4. Specific examples include silicone clay, rubber clay, resin clay, and oil clay, and one or more of these can be used in combination.

  Among the above, for example, as silicone clay, as silicone rubber, polyorganosiloxane having a viscosity of about 5000 to 200,000 cSt (25 ° C.) and polyorganosiloxane having a viscosity of 1 million cSt (25 ° C.) or more are weighted. 100 parts by weight mixed at a ratio of 80:20 to 40:60, 20 combined with one or more of quartz powder, diatomaceous earth, magnesium silicate, calcium carbonate, talc, mica powder, etc. as inorganic filler 20 ˜100 parts by weight, and others containing 10 parts by weight as liquid paraffin if necessary. In addition, the silicone clay having such a structure is prepared by using the above-mentioned silicone rubber, inorganic filler, and liquid paraffin as necessary, and using a kneader used for ordinary rubber kneading such as a roll and a kneader. Can be obtained by uniformly kneading.

  In addition, although the average particle diameter of an inorganic filler is not specifically limited, It is preferable that it is about 0.1-50 micrometers, and it is more preferable that it is about 0.5-30 micrometers. If the average particle size is less than 0.1 μm, the silicone clay may be too hard or the viscosity may be poor depending on the type of the inorganic filler. On the other hand, if the average particle size exceeds 50 μm, depending on the type of the inorganic filler, it may be difficult to obtain stretched physical properties. When the blending amount of the inorganic filler is too small, it is difficult to obtain a preferable clay-like material, and when it is too large, there is a possibility that it becomes too hard.

  Further, liquid paraffin has a function of improving the viscosity of clay, but if this content is excessively increased, it may bleed and adhere to the hand.

  Examples of the rubber clay include those containing natural rubber or butyl rubber instead of the silicone rubber.

  In general, the resin clay includes clay composed mainly of starch and / or flour and a vinyl acetate emulsion adhesive. Examples of the starch and cereal flour include corn starch, potato starch, wheat starch, rice starch, tapioca starch and sweet potato starch, and wheat flour, corn flour, rice flour and buckwheat flour, respectively. Examples of the vinyl acetate emulsion adhesive include a vinyl acetate resin emulsion, an ethylene-vinyl acetate copolymer emulsion, and an acrylic-vinyl acetate copolymer emulsion.

  In addition, it is preferable that these compounding quantities are about 100-150 weight part of vinyl acetate emulsion adhesives with respect to 100 weight part of starch and flour. In addition to these materials, the resin clay may contain inorganic powder, wax, soap and the like. Examples of the inorganic powder include quartz, kaolin, zeolite, diatomaceous earth, talc, bentonite, borax, and rock powder, and one or more of these can be used in combination. Examples of the wax include beeswax. Examples of the soap include fatty acid salt soap. However, as for these, it is preferable that the compounding quantity is all less than 10 weight part.

  As the oil clay, a mixture of an inorganic filler such as clay, calcium carbonate, sericite clay, soap and an oil component is usually used. More specifically, liquid paraffin and / or microcrystalline wax is contained as an oil component in an amount of about 15 to 45 parts by weight with respect to 100 parts by weight of the inorganic filler, and the soap includes alkali metal soap, alkaline earth metal soap, aluminum soap. Of these, those containing about 0.2 to 15 parts by weight of one or a combination of two or more of them, and further containing about 0.2 to 10 parts by weight of glycerin are preferably used.

  In addition, as a specific example of the above-mentioned silicone clay, transparent clay (manufactured by Nisshin Associates) is mentioned, and as a specific example of resin clay, excellent (manufactured by Nisshin Associates) is mentioned.

  Further, the compression elastic modulus of the constituent material of the reinforcing member 7 is preferably about 0.001 to 0.5 MPa, and more preferably about 0.01 to 0.3 MPa. By setting the physical property value of the reinforcing member 7 within the above range, the pseudo-lesioned portion 21 is plastically deformed in a state in which the physical property is more approximate to the actual lesioned portion, and higher quality training is performed. Can be implemented.

  By configuring the reinforcing member 7 with such a material, the reinforcing member 7 can be deformed following the deformation when the reduced diameter portion 44 is deformed (see FIG. 5B).

  In addition, the right coronary artery 4 and the reinforcing member 7 are each deformed by dilatation training. However, the reinforcing member 7 is more difficult to return than the right coronary artery 4 after the deformation. As a result, the pseudo-lesioned part 21 is maintained in its deformed state as a whole. That is, the pseudo-lesioned part 21 is plastically deformed to the extent that it does not return to the shape before the expansion due to the expansion when the expansion training is performed. This is almost the same phenomenon as when the stenosis is deformed and the state is maintained even when PTCA is performed on the stenosis that actually occurs in the human right coronary artery. Therefore, the trainer can perform training close to the actual procedure.

  The training biological model 1 having the above-described configuration can be manufactured, for example, as follows. Here, an example of a method for manufacturing the biological training model 1 will be described.

  First, as shown in FIG. 6A, a tubular body 40 as a base material that becomes the right coronary artery 4 is prepared. The tubular body 40 is made of polyethylene and has heat shrinkability.

  Next, as shown in FIG. 6B, for example, hot air of 80 to 120 degrees is applied to the lesion formation region 20 of the tubular body 40 (right coronary artery 4) using a heat gun 100 such as a hair dryer. The affected part formation region 20 is heated by applying. Then, heating is stopped when the diameter of the lesioned part forming region 20 is reduced to a desired size. Thereby, the right coronary artery 4 in which the pseudo lesioned part 21 is formed is obtained. Note that the degree of stenosis of the pseudo-lesioned portion 21 can be appropriately changed depending on the heating time and temperature.

  Next, as shown in FIG.6 (c), the reinforcement member 7 comprised with the clay is prepared. The reinforcing member 7 has a “C” shape in cross section in advance. The reduced diameter portion 44 of the right coronary artery 4 is inserted into the reinforcing member 7 through the defect portion 71 of the reinforcing member 7.

  Next, the reinforcing member 7 is deformed along the recess 451 and positioned in the recess 451. Moreover, the defect | deletion part 71 is filled by making the reinforcement member 7 deform | transform (it lose | disappears). Thereby, the living body model 1 for training of the state shown in FIG.6 (d) is obtained.

  When forming the reduced diameter portion 44, a soldering iron can be used instead of the heat gun 100.

  Moreover, when forming the reduced diameter part 44, it can replace with the method of heating the tubular body 40, and the method of pulling the tubular body 40 along the longitudinal direction can be used.

  Further, when the reduced diameter portion 44 is formed, a regulating member that regulates the degree of the reduced diameter may be used. Examples of the restricting member include those that have a rod shape and can be inserted into the tubular body 40 and used.

<Second constituent material form>
In the second constituent material form, the right coronary artery 4 (the reduced diameter portion 44) is made of a plastically deformable material (thermoplastic resin) as described above. On the other hand, the reinforcing member 7 is made of an elastic material.

  The elastic material constituting the reinforcing member 7 is not particularly limited. For example, a polystyrene-poly (ethylene / propylene) block copolymer, a polystyrene-poly (ethylene / propylene) block-polystyrene copolymer, polystyrene- Poly (ethylene / butylene) block-polystyrene copolymer, mixture of one or more copolymers selected from the group consisting of polystyrene-poly (ethylene-ethylene / propylene) block-polystyrene copolymer And a polymer containing a softening agent that softens the polymer.

  Specific examples of the copolymer include, for example, the Septon series (manufactured by Kuraray Plastics, thermoplastic elastomer), Espolex SB series (manufactured by Sumitomo Chemical Co., Ltd.), and the like.

  As the softener, process oil is particularly preferably used, and the process oil is not particularly limited, and any of paraffinic, naphthenic and aromatic types may be used, and one of these may be used. Alternatively, two or more kinds can be used in combination. Moreover, as a specific example of process oil, Diana process oil series (made by Idemitsu Kosan), JOMO process P (made by Japan Energy) etc. are mentioned, for example.

  The weight ratio of the copolymer to the softening agent is preferably about 1: 3 to 1:10, and more preferably about 1: 5 to 1: 7.

  Furthermore, the reinforcing member 7 that is elastically deformed may be added with other additives as needed in addition to the above-described constituent materials. Examples of such additives include preventing aging of the pseudo-lesioned portion 21. Anti-aging agent (antioxidant) and the like.

  The anti-aging agent is not particularly limited, and examples thereof include amine-based or phenol-based anti-aging agents. Examples of the amine-based anti-aging agent include N-isopropyl-N′-phenyl-p-phenylenediamine, N- ( 1,3-dimethylbutyl) -N′-phenyl-p-phenylenediamine, amine derivatives such as 6-ethoxy-2,2,4-trimethyl-1,2-dihydroquinoline, and phenolic aging The inhibitors include 2,6-di-tert-butyl-p-cresol, 2,5-di-tert-amylhydroquinone, 2,5-di-tert-butyl-hydroquinone, 4,4'-butylidene-bis (3-methyl-6-tert-butylphenol), 2,2′-methylene-bis (4-methyl-6-tert-butylphenol) and the like.

  The pseudo-lesioned portion 21 made of such a constituent material is substantially maintained in a deformed state as in the case of the first constituent material form. It is reduced as compared with that of the constituent material form, that is, it is slightly easier to return to the shape before expansion.

  In the pseudo-lesioned part 21, the hardness can be changed by appropriately selecting the constituent material. As a result, pseudo-lesioned portions 21 approximated to various stenotic objects having different hardnesses are obtained, and expansion training corresponding to the pseudo-lesioned portions 21, that is, from when the expansion force is relatively small to when the expansion force is relatively large. Can be performed reliably.

<Third constituent material form>
In the third constituent material form, the reinforcing member 7 is made of a plastically deformable material (clay) as described above. On the other hand, the right coronary artery 4 (the reduced diameter portion 44) is made of an elastic material.

  The elastic material constituting the right coronary artery 4 is not particularly limited, and examples thereof include natural rubber, isoprene rubber, butadiene rubber, styrene-butadiene rubber, nitrile rubber, chloroprene rubber, butyl rubber, acrylic rubber, ethylene-propylene rubber, hydrin rubber, Various rubber materials (especially those vulcanized) such as urethane rubber, silicone rubber, fluoro rubber, styrene, polyolefin, polyvinyl chloride, polyurethane, polyester, polyamide, polybutadiene, trans polyisoprene Various thermoplastic elastomers such as those based on fluorocarbons, fluororubbers, and chlorinated polyethylenes can be used, and one or more of these can be used in combination.

  The pseudo-lesioned portion 21 made of such a constituent material is substantially maintained in a deformed state as in the case of the first constituent material form. It is reduced from that of the constituent material form.

  Even in the third constituent material form, the hardness can be changed by appropriately selecting the constituent material of the pseudo-lesioned portion 21. Thereby, the pseudo-lesioned part 21 approximated to various narrowed objects with different hardness is obtained.

  Next, the state of the living body model 1 for training when the PTCA surgery is performed using the living body model 1 (three-dimensional model) for training will be described in detail.

  When PTCA training is performed using the training biological model 1, the reduced diameter portion 44 is pressed outward by the inflated balloon 64 in the step [3] shown in FIG. The reinforcing member 7 is also pressed outward through the reduced diameter portion 44. Thereby, the reduced diameter portion 44 and the reinforcing member 7 are expanded and deformed collectively.

  Then, after removing the balloon catheter guide wire 62 and the balloon catheter 63 from the pseudo-lesioned part 21 in the step [4] shown in FIG. 4D, the pseudo-lesioned part 21 is plastically deformed as described above. Therefore, the expanded and deformed state, that is, the shape expanded by the balloon 64 is maintained without returning to the shape before expansion. This is almost the same phenomenon as when the right coronary artery and stenosis are expanded when PTCA is performed on a stenosis that actually occurs in the human right coronary artery.

  Thus, by using the biological training model 1, the training biological model 1 approximates the physical properties of the actual lesion when performing training aimed at improving the skill of the surgeon. Therefore, it is possible to reliably perform training in accordance with the actual technique.

  Further, since the expansion of the balloon 64 in the step [3] can be practiced while observing visually or by an X-ray contrast image, and the degree of expansion of the pseudo-lesioned portion 21 can be confirmed, from this viewpoint, Higher quality training can be implemented.

  As shown in FIG. 5C, the stent 81 is applied to the pseudo-lesion 21 after the blood flow is restored by the step [4], that is, the pseudo-lesion 21 after the PTCA operation is performed. By indwelling, restenosis of the pseudo-lesioned portion 21 can be more reliably suppressed. The training biological model 1 can also be used for training of treatment in which such a stent 81 is placed, and if the training biological model 1 is used for such training, it is evaluated whether restenosis is suitably suppressed. It can be implemented more reliably.

  Further, as described above, the connecting portions 11 are provided at both ends of the right coronary artery 4 as the Segment 2 in order to allow the right coronary artery 4 to be detachable at both ends (see FIG. 3). That is, Segment 2 is configured such that one end is connected to Segment 1 and the other end is connected to Segment 3 by connection 11, thereby being detachable from right coronary artery 4.

  Such a connection part 11 may be of any structure as long as it is detachable at the segment 2 part and can connect each end part to be connected liquid-tightly. The connection form as shown in FIG. Since each connection part 11 is the same structure as each other, only one (Segment 1 side) connection part 11 will be described below.

<First connection configuration>
As shown in FIG. 7, the connector 12 has a through-hole 14 penetrating in the axial direction (longitudinal direction) at the center thereof, and a main body 13 whose overall shape is substantially cylindrical, and the longitudinal direction of the main body 13. And a flange 15 provided at substantially the center.

  The main body 13 has a reduced diameter portion whose outer diameter is reduced at both ends, and the outer diameter of the reduced diameter portion is set to be smaller than the inner diameter of the right coronary artery 4 and is closer to the flange 15 than the reduced diameter portion. In (inner side), the outer diameter is set larger than the inner diameter of the right coronary artery 4.

  When the right coronary artery 4 is inserted from the distal end (cut surface) of the right coronary artery 4 toward the flange 15 with respect to the connector 12 having such a configuration, the inner diameter of the right coronary artery 4 is increased. Thereby, since the outer peripheral surface of the main body 13 and the inner peripheral surface of the right coronary artery 4 are in close contact with each other, the ends of the right coronary artery 4 are fluid-tightly connected by the connector 12.

  Although it does not specifically limit as a constituent material of the connection tool 12, Various resin materials are used suitably, Specifically, polyethylene, a polypropylene, an ethylene-propylene copolymer, ethylene-vinyl acetate copolymer (EVA), etc. Polyolefin, polyvinyl chloride, polyvinylidene chloride, polystyrene, polyamide, polyimide, polyamideimide, polycarbonate, poly- (4-methylpentene-1), ionomer, acrylic resin, polymethyl methacrylate, acrylonitrile-butadiene-styrene copolymer Polymer (ABS resin), acrylonitrile-styrene copolymer (AS resin), butadiene-styrene copolymer, polyethylene terephthalate (PET), polybutylene terephthalate (PBT), polycyclohexane terephthalate (PCT) Polyester, polyether, polyetherketone (PEK), polyetheretherketone (PEEK), polyetherimide, polyacetal (POM), polyphenylene oxide, modified polyphenylene oxide, polysulfone, polyethersulfone, polyphenylenesulfide, polyarylate And various resin materials such as aromatic polyester (liquid crystal polymer), polytetrafluoroethylene, and polyvinylidene fluoride, and one or more of them can be used in combination.

<Second connection form>
As shown in FIG. 8, the connection mechanism 16 includes a flange 17 provided at each distal end (cut surface) of the cut right coronary artery 4 and a ring-shaped member (first member) rotatably supported by one right coronary artery 4. 1 ring-shaped member) 18 and a ring-shaped member (second ring-shaped member) 19 fixed to the other right coronary artery 4 so as to contact the flange 17.

  The ring-shaped member 18 has an open portion that opens to the flange 17 side, and a female screw 181 is formed on the inner surface of the open portion.

  In addition, the ring-shaped member 19 has a male screw 191 formed on the outer peripheral surface thereof, and the ring-shaped member 19 is set to a size that can be inserted into an opening formed in the ring-shaped member 18. The ring-shaped member 19 can be inserted (screwed) into the open portion of the ring-shaped member 18.

  In the connection mechanism 16 having such a configuration, with the end surfaces of the two flanges 17 in contact with each other, the female screw 181 and the male screw 191 respectively formed on the ring-shaped members 18 and 19 are screwed together to Since the end surfaces of the flange 17 are in close contact with each other, the end portions of the right coronary artery 4 are fluid-tightly connected by the connection mechanism 16.

  As the constituent material of the various constituent members of the connection mechanism 16, the same constituent materials as those of the connection tool 12 described above are preferably used.

  In addition, although it does not specifically limit as a constituent material of the part except Segment2 of the right coronary artery 4 of the coronary artery 10, For example, the material similar to Segment2 can be used. In addition, for example, silicone elastomer, silicone rubber such as silicone gel, polyurethane elastomer, silicone resin, epoxy resin, thermosetting resin such as phenol resin, polymethyl methacrylate, polyvinyl chloride, polyethylene, etc. A thermoplastic resin etc. are mentioned, Among these, it can use combining 1 type (s) or 2 or more types. Among these, it is particularly preferable to use silicone rubber.

  Specifically, the breaking strength of the coronary artery 10 made of silicone rubber is preferably about 0.5 to 3.0 MPa, and more preferably about 1.0 to 2.0 MPa.

  The breaking elongation of the coronary artery 10 is preferably about 50 to 300%, more preferably about 100 to 200%.

  Furthermore, the Shore A hardness (specified in JIS K6253) of the coronary artery 10 is preferably about 10 to 40, and more preferably about 25 to 35.

  Furthermore, the tensile elastic modulus of the coronary artery 10 is preferably about 0.01 to 5.0 MPa, and more preferably about 0.1 to 3.0 MPa.

  The inner diameter of the coronary artery 10 is not particularly limited, but is preferably set to about 0.5 to 10.0 mm, and more preferably about 1.0 to 5.0 mm.

<< Second Embodiment >>
Here, although the second embodiment will be described, the description will focus on the differences from the above-described embodiment, and the description of the same matters will be omitted.

  The training biological model 1 </ b> A shown in FIG. 9A is configured such that a regulating member 9 is further installed on the outer peripheral side of the reinforcing member 7. The restricting member 9 is a member that restricts (suppresses) the deformation when the reinforcement member 7 is deformed by performing the extension training. Further, the regulating member 9 is constituted by a band, and the band is wound in a ring shape along the outer periphery of the reinforcing member 7. It is preferable that the inner peripheral portion 91 of the regulating member 9 is not fixed to the outer peripheral portion 45 of the right coronary artery 4.

  In the living body model 1A for training in which such a regulating member 9 is installed, when the expansion training is performed, the reinforcing member 7 is pressed toward the outside via the reduced diameter portion 44 and tends to be deformed. The outward deformation is restricted by the restriction member 9 (see FIG. 9B). As a result, the degree of reinforcement with respect to the reduced diameter portion 44 is increased, so that the pseudo lesion portion 21 is obtained that is harder than the pseudo lesion portion 21 of the first embodiment. In addition, since the pseudo-lesioned portion 21 is maintained in the deformed shape, the expansion training using the balloon catheter 63 can be reliably performed in accordance with the actual procedure. Further, placement training of the stent 81 as shown in FIG. 9C can also be performed.

  In addition, since the regulating member 9 is pressed toward the outside via the reinforcing member 7 similarly to the reinforcing member 7, the regulating member 9 extends slightly in the circumferential direction. As a result, a gap 92 is formed between the inner peripheral portion 91 of the regulating member 9 and the outer peripheral portion 45 of the right coronary artery 4, and a part of the reinforcing member 7 can enter the gap 92 (FIG. 9B). reference).

  Moreover, it is preferable that the regulating member 9 is made of a plastically deformable material or an elastic material. The material that can be plastically deformed is not particularly limited, and for example, the materials mentioned as the constituent material of the right coronary artery 4 in the first constituent material form can be used. The elastic material is not particularly limited. For example, the elastic material may be a material as mentioned as the constituent material of the reinforcing member 7 in the second constituent material form or the constituent material of the right coronary artery 4 in the third constituent material form. Such materials can be used. By using such a material, the deformation of the reinforcing member 7 can be reliably regulated.

<< Third Embodiment >>
Here, the third embodiment will be described, but the description will focus on the differences from the above-described embodiment, and the description of the same matters will be omitted.

  In the living body model 1B for training shown in FIG. 10, the reinforcing member 7B is composed of a plurality of (seven in the illustrated configuration) ring-shaped rubber (rubber rubber) 72. Each of the ring-shaped rubbers 72 has an inner diameter in a natural state where no external force is applied, substantially equal to or slightly smaller than the outer diameter of the reduced diameter portion 44. The reinforcing member 7B having such a configuration can adjust the degree of reinforcement with respect to the reduced diameter portion 44 in accordance with the number of ring-shaped rubbers 72 installed.

<< Fourth Embodiment >>
Here, although the fourth embodiment will be described, the description will focus on the differences from the above-described embodiment, and the description of the same matters will be omitted.

  In the living body model 1C for training shown in FIG. 11, the reinforcing member 7C is made of a foamed elastic body (sponge). The reinforcing member 7 </ b> C has a cylindrical shape, and its natural inner diameter is substantially equal to or slightly smaller than the outer diameter of the reduced diameter portion 44. In the reinforcing member 7 </ b> C having such a configuration, since the reinforcing member 7 </ b> C is relatively flexible, the degree of reinforcement with respect to the reduced diameter portion 44 can be suppressed.

<< Fifth Embodiment >>
In the first to fourth embodiments, the training biological model 1 is applied to the right coronary artery 4 side. In the fifth embodiment, the training biological model 1 is applied to the left coronary artery 3 side. It has become a case. Hereinafter, the fifth embodiment will be described with a focus on differences from the first embodiment, and description of similar matters will be omitted.

  That is, in this embodiment (fifth embodiment), as shown in FIG. 12, the segment 6 of the left coronary artery 3 branches into a segment 7 and a segment 9, and a pseudo-lesion 21 is formed in the branch portion (bi-faction) 34. ing. Further, the configuration is the same as that of the first embodiment except that the connection portion 11 is provided in the middle of the Segment 6, the Segment 7, and the Segment 9 via the pseudo lesioned portion 21.

  In the training biological model 1 having such a configuration, usually, first, the balloon catheter guide wire 62 is inserted from the Segment 6 to the Segment 7 side, and the balloon catheter 63 is advanced along the balloon catheter guide wire 62, whereby the balloon catheter 63 is advanced. 64 is made to reach the position of the pseudo-lesioned part 21, and the balloon 64 is further inflated at this position to expand the segment 7 side of the pseudo-lesioned part 21. Next, the balloon catheter guide wire 62 is inserted from the Segment 6 to the Segment 9 side, and the balloon 64 is made to reach the position of the pseudo-lesion 21 in the same manner as described above, and then inflated to expand the Segment 9 side of the pseudo-lesion 21. Thus, training for securing the flow path is performed.

  In the present embodiment, as described above, the connecting portion 11 is provided in the middle of the Segment 6, the Segment 7 and the Segment 9 so that the pseudo lesioned portion 21 can be arranged in the branching portion 34. A part of Segment 6, Segment 7 and Segment 9 including the branching portion 34 is configured to be detachable from the left coronary artery 3 (see FIG. 13).

  Further, the pseudo-lesioned portion 21 described in the present embodiment can be manufactured in substantially the same manner as the pseudo-lesioned portion 21 described in the first embodiment.

  In the first embodiment, the case where the pseudo lesioned part 21 is arranged in the Segment 2 (# 2: Middle) of the right coronary artery 4 will be described. In the fifth embodiment, the pseudo lesioned part 21 is located in the left coronary artery 3. The segment 6 (# 6) is arranged in the branching portion 34 that branches into the Segment 7 (# 7) and the Segment 9 (# 9). However, the position where the pseudo-lesioned portion 21 is arranged is limited to such a position. Instead, the pseudo-lesioned portion 21 may be disposed at a frequently occurring site where coronary artery stenosis or occlusion occurs with high probability, and training corresponding to the frequently occurring site may be performed. In addition, as a frequent occurrence site | part in which such a pseudo-lesioned part 21 is arrange | positioned, the position of-mark shown in FIG.

  As described above, in the training biological model 1, the pseudo-lesioned part 21 that approximates the physical properties of the lesion site can be arranged in any shape at any position in the right coronary artery 4 or the left coronary artery 3. Since the training biomodel 1 can be used to perform training corresponding to various patient pathologies, the surgeon can learn more advanced techniques in a place other than the surgery performed on the patient.

  As mentioned above, although the biological model for training of this invention was demonstrated about embodiment of illustration, this invention is not limited to this, Each part which comprises the biological model for training is arbitrary which can exhibit the same function. It can be replaced with the configuration of Moreover, arbitrary components may be added.

  Moreover, the biological model for training of the present invention may be a combination of any two or more configurations (features) of the above embodiments.

  In addition, the pseudo-tubular tissue has been described as a typical example of a coronary artery (blood vessel), but is not limited thereto. For example, the esophagus, large intestine, small intestine, pancreatic duct, bile duct, ureter, oviduct, trachea, It may mimic the bronchi.

  Further, the pseudo-tubular tissue is not limited to a single-layer structure, and may be a structure in which a plurality of layers are stacked (laminated body).

  Moreover, the shape of the pseudo-tubular tissue may be linear, or a part or the whole may be curved.

  In addition, the pseudo-tubular tissue has the same wall thickness in the above-described embodiment in the portion where the reduced diameter portion is formed and the other portion, but is not limited thereto, for example, the wall thickness May be different from each other.

  The pseudo-tubular tissue may be a single layer or a laminate in which a plurality of layers are laminated.

1, 1A, 1B, 1C Training biological model 10 Coronary artery (pseudo tubular tissue)
DESCRIPTION OF SYMBOLS 11 Connection part 12 Connection tool 13 Main body 14 Through-hole 15 Flange 16 Connection mechanism 17 Flange 18, 19 Ring-shaped member 181 Female screw 191 Male screw 20 Lesion part formation area 21 Pseudo lesion part (pseudo-stenosis part)
3 Left coronary artery 31 Left anterior descending branch 32 Left convolution 33 Left main trunk 34 Bifurcation
4 right coronary artery 40 tubular body 401 fixed end 402 free end 403 strip 41 sharp edge 42 posterior descending branch 43 lumen 44 reduced diameter 441 inclined surface (tapered surface)
45 Peripheral part 451 Concave part 5 Aorta 61 Guide catheter 62 Guide wire for balloon catheter 63 Balloon catheter 64 Balloon 7, 7B, 7C Reinforcement member 71 Defect part 72 Ring-shaped rubber (ring rubber)
81 Stent 9 Restriction member 91 Inner circumference 92 Gap 100 Heat gun f ₀ Initial tensile stress f _t Tensile stress after 5 minutes φd ₁ inner diameter φd ₂ outer diameter φd ₃ minimum inner diameter t _max maximum thickness L, 2L total length

Claims (10)

A pseudo-tubular tissue that is formed of a tubular body, has a reduced diameter portion that is reduced in diameter in the longitudinal direction, and imitates a tubular tissue;
A reinforcing member made of a plastically deformable material including at least one of silicone clay, rubber clay, resin clay and oil clay, which is provided on the outer peripheral side of the reduced diameter portion and reinforces the reduced diameter portion; With
The reduced diameter portion and the reinforcing member constitute a pseudo stenosis portion simulating a stenosis portion generated in a tubular tissue, and the pseudo stenosis portion is used for expansion training for expanding the stenosis portion. Biological model for training.   2. The training biological model according to claim 1, wherein, when the expansion training is performed, the pseudo-stenosis part is plastically deformed to an extent that the expansion does not return to a shape before expansion. 3. The training biological model according to claim 1 , wherein the reduced diameter portion is made of a plastically deformable material. The reduced diameter portion is training for the biological model according to claim 1 or 2 is made of an elastic material. The living model for training according to any one of claims 1 to 3 , wherein at least the reduced diameter portion of the pseudo-tubular tissue is made of a thermoplastic resin. Wherein the reduced diameter portion, according to any one of claims 1 to 5 the inner diameter of the reduced diameter portion at one end or both ends tapered portion gradually increases toward the end portion side is formed from the inner side Biological model for training. The reinforcing member for training the biological model according to any one of claims 1 to 6 the shape is a component of a ring shape along the circumferential direction of the reduced diameter portion. The biological model for training according to any one of claims 1 to 7 , further comprising a regulating member that is installed on an outer peripheral side of the reinforcing member and regulates the deformation when the reinforcing member is deformed. The training biological model according to claim 8 , wherein the restricting member is a ring-shaped band made of a plastically deformable material or an elastic material. One or more medical devices, wherein after reaching the pseudo stenosis by inserting the pseudo-tubular tissue, training a living body according to any one of claims 1 to 9 wherein the extended training is performed model.

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