Heart model device

Abstract

To provide a heart model device capable of causing a combined movement of expansion / contraction and twisting of a heart model.SOLUTION: A heart model device is provided, comprising an expandable / contractible heart model simulating a heart, and a driving mechanism connected to the heart model and configured to move a surface of the heart model either inward or outward.SELECTED DRAWING: Figure 1

Description

Technical Field

[0001] The present disclosure relates to a heart model device.

Background Art

[0002] For minimally invasive treatment and examination of heart diseases, medical devices such as guidewires and catheters are used. Patent Documents 1 to 3 disclose training devices that enable an operator such as a doctor to simulate procedures using these medical devices. The devices described in Patent Documents 1 to 3 include a simulated heart body, and by supplying water or air into the simulated heart body, the simulated heart body is caused to perform expansion and contraction operations that simulate pulsation. Hereinafter, the expansion and contraction operations are also simply referred to as "expansion / contraction operations". The simulated heart body is also referred to as a "heart model".

Prior Art Documents

Patent Documents

[0003]

Patent Document 1

Patent Document 2

Patent Document 3

Summary of the Invention

Problems to be Solved by the Invention

[0004] The actual heart is known to perform contraction and relaxation motions accompanied by torsional motion. Torsional motion is also called twisting motion. Therefore, in order to provide a more clinically relevant training environment for the operator, it is preferable for the heart model to perform a combined motion of contraction / relaxation and torsion. In this regard, Patent Documents 1 to 3 have the problem that only the contraction / relaxation motion of the heart model is realized, and no consideration is given to the torsional motion. In other words, in Patent Documents 1 to 3, the movement of the heart model is monotonous, and there is a problem that the movement of the actual heart having a complex motion pattern cannot be simulated at all.

[0005] The present disclosure has been made to solve the above-described problems, and an object thereof is to provide a heart model device capable of causing a heart model to perform a combined motion of contraction / relaxation and torsion.

Means for Solving the Problems

[0006] The present disclosure has been made to solve at least a part of the above-described problems, and can be realized in the following forms.

[0007] (1) According to one aspect of the present disclosure, a heart model device is provided. This heart model device includes a heart model that mimics the heart and is capable of expansion and contraction, and a drive mechanism that is connected to the heart model and moves the surface of the heart model in one direction, either the outer direction or the inner direction of the heart model.

[0008] According to this configuration, the heart model device includes a drive mechanism in addition to a heart model that can expand and contract, in other words, a heart model that can perform contraction / relaxation. Therefore, in addition to the contraction / relaxation motion of the heart model, the drive mechanism can realize the torsional motion of the heart model. That is, according to this configuration, a heart model device capable of causing a heart model to perform a combined motion of contraction / relaxation and torsion can be provided. As a result, it becomes possible to cause the heart model to perform a motion simulating the motion of an actual heart having a complex motion pattern, and a more clinically relevant training environment can be provided for the operator.

[0009] (2) In the heart model device of the above-described form, the drive mechanism may apply a force to the surface of the heart model in a direction intersecting the direction perpendicular to the surface. According to this configuration, since the drive mechanism applies a force to the surface of the heart model in a direction intersecting the direction perpendicular to the surface, compared with the case of applying a force in the perpendicular direction, a three-dimensional twisting motion closer to the actual movement of the heart can be imparted to the heart model.

[0010] (3) In the heart model device of the above-described form, the drive mechanism includes a linear member having a first end and a second end, and a drive device. The first end of the linear member is connected to the heart model, and the second end is connected to the drive device. The drive device may move the surface of the heart model in an outward direction by pulling the linear member. According to this configuration, since the drive device moves the surface of the heart model in an outward direction by pulling the linear member, with a simple configuration, it is possible to move the surface of the heart model, in other words, to realize the twisting motion of the heart model.

[0011] (4) In the heart model device of the above-described form, the heart model has an opening formed at a position to which the aorta model is connected, a heart base portion which is a peripheral portion of the opening, and an apex portion which is a portion farthest from the center of the opening. The first end of the linear member may be fixed between the apex portion and the heart base portion of the heart model. According to this configuration, since the linear member is fixed between the apex portion and the heart base portion of the heart model, a three-dimensional twisting motion closer to the actual movement of the heart can be imparted to the heart model.

[0012] (5) In the heart model device of the above-described form, when the plan view of the heart model is viewed with the heart base portion on the upper side and the apex portion on the lower side, the first end of the linear member may be fixed to the right of an imaginary straight line connecting the center of the opening of the heart base portion of the heart model and the apex portion. By pulling the linear member in the vertically upward direction, when viewing the heart model from the apex to the base, counterclockwise twisting can be caused during the contraction phase of the heart model. To cause the twisting, it is only necessary to pull the linear member in the vertically upward direction, so a heart model device with a simple configuration can be provided.

[0013] (6) In the heart model device of the above form, further, a container containing a liquid is provided, the heart model is disposed in the liquid inside the container, the drive device is disposed outside the container, and the linear member may be drawn out from the inside to the outside of the container. According to this configuration, since the linear member is drawn out from the inside to the outside of the container, leakage of liquid from the container due to the arrangement of the linear member can be suppressed.

[0014] (7) In the heart model device of the above form, the linear member may be formed of an X-ray transmissive material. According to this configuration, since the linear member is formed of an X-ray transmissive material, it can be suppressed that the linear member appears in the X-ray image and hinders the procedure.

[0015] (8) In the heart model device of the above form, the drive mechanism may move the surface of the heart model in synchronization with at least one of the expansion and the contraction of the heart model. According to this configuration, the drive mechanism moves the surface of the heart model in synchronization with at least one of the expansion and the contraction of the heart model. In other words, the drive mechanism twists the surface of the heart model in synchronization with at least one of the expansion and the contraction of the heart model. Therefore, according to this configuration, an operation in which a contraction / expansion operation and a twisting operation, which are close to the movement of an actual heart, are combined in synchronization can be performed on the heart model.

[0016] (9) In the heart model device of the above form, the drive mechanism may move the surface of the heart model after a lapse of a predetermined time from the start of at least one of the expansion and the contraction of the heart model. According to this configuration, it is possible to cause the heart model to perform an operation in which a contraction / expansion operation and a twisting operation, which are closer to the actual movement of the heart, are combined in synchronization.

[0017] The present disclosure can be realized in various aspects, for example, in the form of a heart model device, a human body simulation device including the heart model device, a control method for these devices, and the like.

Brief Description of the Drawings

[0018]

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Embodiments for Carrying Out the Invention

[0019] <First Embodiment> FIG. 1 is an explanatory diagram illustrating the configuration of the heart model device 1. The heart model device 1 of the present embodiment is a device used to simulate treatment and examination procedures using medical devices such as catheters and guidewires. The heart model device 1 includes a cardiovascular model 10, a container 21, a filtration filter 22, a pump 23, a control device 30, a pulsation unit 40, a driving device 50, and a linear member 51.

[0020] FIG. 2 is an explanatory diagram illustrating the configuration of the cardiovascular model 10. As shown in FIG. 2, the cardiovascular model 10 includes various models that simulate the human cardiovascular system, specifically, a heart model 100, a coronary artery model 111, a large artery model 112, and an artery model 113. Details of each model will be described later. In FIG. 2, a part of the linear member 51 extending from the fixing portion 120 is not shown.

[0021] Returning to FIG. 1, the description will be continued. The container 21 is a substantially rectangular parallelepiped-shaped water tank. As shown in FIG. 1, a fluid W is accommodated inside the container 21. In this state, by disposing the cardiovascular model 10 inside the container 21, the cardiovascular model 10 is in a state of being immersed in the fluid W. Thereby, the cardiovascular model 10 can be in a wet state similar to that of an actual human body. As the fluid W, water, physiological saline, an aqueous solution of an arbitrary compound, etc. can be adopted. The fluid W of the present embodiment is a liquid. The fluid W accommodated in the container 21 is taken into the inside of the large artery model 112 and functions as simulated blood simulating blood. The fluid W is taken into the heart lumen 100i of the heart model 100 via the large artery model 112, and causes the heart model 100 to perform an expansion and contraction operation simulating pulsation. Hereinafter, the expansion and contraction operation will also be referred to as a "scaling operation".

[0022] A lid is provided on the upper part of the container 21. An upper opening 211, which is an opening for communicating the inside and outside of the container 21, is formed in the lid of the container 21. The upper opening 211 is used to draw out the linear member 51 from the inside of the container 21 to the outside. A lower opening 212, which is an opening for communicating the inside and outside of the container 21, is formed in the bottom plate located at the lower part of the container 21. The lower opening 212 is used to connect a connection member 221 for discharging the fluid W to the filtration filter 22. The container 21 can be formed of any material, in addition to a synthetic resin having X-ray permeability and high transparency. Examples of the synthetic resin with high transparency include acrylic resin. The container 21 may further be provided with a wave suppressor for covering the surface of the fluid W. By using the wave suppressor, the undulation occurring on the surface of the fluid W can be suppressed, and the visibility of the circulator model 10 can be improved.

[0023] The filtration filter 22 is connected to the lower opening 212 of the container 21 via the connection member 221. The filtration filter 22 removes impurities in the fluid W by filtering the fluid W passing through the filtration filter 22. Examples of the impurities include, for example, a contrast agent used in a procedure. As the connection member 221, for example, a tubular body such as a hose can be used. The same tubular body can be used for other connection members described later. The pump 23 is connected downstream of the filtration filter 22 and circulates the filtered fluid W at a constant flow rate. As the pump 23, for example, a non-positive displacement centrifugal pump can be used.

[0024] The pulsating unit 40 incorporates a pump different from the pump 23. Examples of the pump incorporated in the pulsating unit 40 include a positive displacement reciprocating pump and a rotary pump operated at a low speed. The pulsating unit 40 functions as a "fluid supply device". The pulsating unit 40 periodically sends out the fluid W to the aortic lumen 112i (FIG. 2) of the aorta model 112. When the pulsating unit 40 sends out the fluid W, the sent-out fluid W is supplied to the heart lumen 100i of the heart model 100 through the aorta model 112, and the heart model 100 expands. When the pulsating unit 40 stops sending out the fluid W, the fluid W is discharged from the heart lumen 100i of the heart model 100, and the heart model 100 contracts. Thus, in the present embodiment, the fluid W discharged from the heart model 100 is sent to the pump 23 through the lower opening 212 and then the connecting member 221. In order to discharge the fluid from the heart model 100, a pump different from the above can also be used. The pump is also called a "fluid discharge device".

[0025] The drive device 50 is a servo motor having an arm 59 that rotates by a certain angle and stops rotating at a predetermined position. The drive device 50 is arranged outside the container 21. The linear member 51 is a long member such as a wire, a rope, or a string. Hereinafter, one end of the linear member 51 is also referred to as the "first end 511", and the other end of the linear member 51 is also referred to as the "second end 512". The second end 512 is the end in the direction opposite to the first end 511. As the material of the linear member 51, for example, at least one of a metal material, a resin material, and a natural fiber can be used. Examples of the metal material include stainless steel and nickel-titanium. Examples of the resin material include an olefin resin and a polyamide resin. Examples of the natural fiber include cotton and hemp. It is preferable to use a resin material having radiation transparency or a natural fiber as the linear member 51.

[0026] The tensile elastic modulus of the linear member 51 is preferably 10 MPa or more. More preferably, the tensile elastic modulus of the linear member 51 is 10 MPa or more and 100 MPa or less. If the tensile elastic modulus of the linear member is less than 10 MPa, the linear member is likely to break when pulling the heart model 100. If it exceeds 100 MPa, it becomes difficult for the linear member to bend. For example, when the second end 512 of the linear member is brought close to the heart model 100, the linear member may push into the heart model 100, easily causing a twist different from that of the actual heart in the heart model 100.

[0027] The linear member 51 used in this embodiment has radiation transparency (X-ray transparency) that allows radiation (X-rays) to pass through. As the linear member 51, a material that has radiation transparency (X-ray transparency), is deformable under bending, and is strong against pulling is used, for example, a solid wire made of nylon (registered trademark).

[0028] The first end 511 of the linear member 51 is connected to the heart model 100 by the fixing portion 120. The second end 512 of the linear member 51 is fixed to the arm 59 of the driving device 50. The heart model 100 is immersed in the fluid W in the container 21. Therefore, for the linear member 51, the first end 511 is immersed in the fluid W of the container 21, drawn upward from the liquid level of the fluid W to the upper part of the container 21, drawn out from the upper opening 211 of the lid of the container 21 to the outside, passes through the outside of the container 21, and the second end 512 is connected to the arm 59 of the driving device 50. In FIG. 1, among the linear member 51, the portion located inside the container 21 is represented by a dashed line, and the portion located outside the container 21 is represented by a solid line. Thus, the linear member 51 of this embodiment is drawn upward from the liquid level of the fluid W to the upper part of the container 21. The linear member 51 may be drawn out from the inside of the container 21 to the outside in a liquid-tight state. In this case, the linear member 51 can be drawn out from the inside of the container 21 to the outside in a liquid-tight state through the wall of the container 21.

[0029] The drive device 50 repeats, by driving periodically, the operation of rotating the arm 59 to pull the linear member 51 and the operation of returning the arm 59 to its original position to return the linear member 51 to its original position. When the drive device 50 pulls the linear member 51, the surface of the heart model 100 is moved in the outward direction of the heart model 100. When the drive device 50 returns the linear member 51 to its original position, the surface of the heart model 100 returns to its original position. Thus, in the present embodiment, the drive device 50 and the linear member 51 function as a "drive mechanism".

[0030] The control device 30 is constituted by, for example, a personal computer, and includes a CPU, a ROM, a RAM, a storage unit, and an input / output interface (not shown). The control device 30 controls the pulsation unit 40, the drive device 50, and the pump 23 (FIG. 1: broken line arrow) by expanding and executing a computer program stored in the ROM in the RAM. As the input / output interface of the control device 30, any device such as a touch panel, a keyboard, an operation button, an operation dial, a foot switch, a microphone, a monitor, an indicator, a speaker, etc. can be adopted.

[0031] As shown in FIG. 2, the heart model 100 of the circulatory model 10 has an outer shape that simulates the outer shape of the human heart. Inside the heart model 100, a heart lumen 100i, which is a space capable of accommodating the fluid W, is formed. That is, the heart model 100 is a hollow organ model. The heart lumen 100i communicates with the aortic lumen 112i of the aortic model 112 through an opening 100c formed at a position corresponding to the heart base 100a. Through this opening 100c, the fluid W supplied from the aortic model 112 can be supplied into the heart model 100. In the heart model 100, a through hole communicating the heart lumen 100i with the outside may be formed at a position corresponding to the heart apex 100b. The heart model 100 has an opening 100c formed at the position where the aortic model 112 is connected, a heart base 100a which is a part of the periphery of the opening 100c, and a heart apex 100b which is the part farthest from the center of the opening 100c.

[0032] The coronary artery model 111 is a tubular blood vessel model that simulates the coronary arteries of the human body and is formed on the outer surface of the heart model 100. The coronary artery model 111 includes a tubular right coronary artery model 111R that simulates the right coronary artery and a tubular left coronary artery model 111L that simulates the left coronary artery. The proximal end of the coronary artery model 111 is connected to the distal end of the aorta model 112. In other words, the proximal ends of the left and right coronary artery models 111R and 111L are connected to the distal end of the aorta model 112. Inside the coronary artery model 111, a coronary artery lumen 111i, which is a space through which fluid W can flow, is formed. In other words, inside the left and right coronary artery models 111R and 111L, a coronary artery lumen 111i, which is a space through which fluid W can flow, is formed. The coronary artery lumen 111i communicates with the aortic lumen 112i of the aorta model 112 through an opening formed at a position corresponding to the connection portion between the coronary artery model 111 and the aorta model 112. At the distal end of the coronary artery model 111, a tip opening 111o that communicates the coronary artery lumen 111i with the outside is provided. In other words, at the distal ends of the left and right coronary artery models 111R and 111L, a tip opening 111o that communicates the coronary artery lumen 111i with the outside is provided.

[0033] The aorta model 112 is a tubular blood vessel model that simulates the aorta of the human body. In the illustrated example, the aorta of the human body is specifically the ascending aorta, the aortic arch, the descending aorta, and the abdominal aorta. The distal end of the aorta model 112 is connected to the heart model 100 and the coronary artery model 111. Inside the aorta model 112, an aortic lumen 112i, which is a space through which fluid W can flow, is formed. At an arbitrary position of the aorta model 112 (in the illustrated example, the abdominal aorta portion), a first connection member 41 is connected in a state where the lumen 41i of the first connection member 41 communicates with the aortic lumen 112i. Through this first connection member 41, the fluid W sent out from the pulsating portion 40 flows into the aortic lumen 112i of the aorta model 112.

[0034] The arterial model 113 is a tubular blood vessel model that simulates the outer shape of the arteries leading to the human head. In the illustrated example, the arteries leading to the human head are the brachiocephalic artery, the left common carotid artery, and the left subclavian artery. The proximal end of the arterial model 113 is connected to a position corresponding to the aortic arch of the aortic model 112. Inside the arterial model 113, an arterial lumen 113i, which is a space through which the liquid W can flow, is formed. At the distal end of the arterial model 113, a tip opening 113o that communicates the arterial lumen 113i with the outside is provided. Usually, a plug for suppressing the discharge of the fluid W from the tip opening 113o is attached to the tip opening 113o. A valve may be attached to the tip opening 113o instead of the plug. When simulating a procedure using the heart model device 1, the operator removes the plug of the tip opening 113o only when the operator intends to insert and remove a medical device from the arterial model 113. As shown in FIG. 2, the arterial model 113 includes a brachiocephalic artery model, a left common carotid artery model, and a left subclavian artery model, each individually connected to the aortic model 112, and the arterial model 113 is a general term for these.

[0035] The heart model 100, the coronary artery model 111, the aortic model 112, the arterial model 113, and the first connecting member 41 can be formed of well-known materials in addition to a synthetic resin of a soft material having X-ray permeability. Examples of the synthetic resin of a soft material having X-ray permeability include silicone. The first connecting member 41 may be formed of a synthetic resin having X-ray permeability and higher rigidity than silicone. The heart model 100, the coronary artery model 111, the aortic model 112, the arterial model 113, and the first connecting member 41 may be formed of the same material or different materials.

[0036] With reference to FIGS. 1 and 2, the expansion of the heart model 100 and the operation of contraction will be described. When the pulsating unit 40 sends out the fluid W, the sent fluid W is supplied to the heart lumen 100i of the heart model 100 through the aorta model 112, and the heart model 100 is caused to perform an expansion operation. In the present embodiment, the "expansion operation of the heart model 100" means that the surface of the heart model 100 moves in the outward direction as the heart model 100 expands. When the pulsating unit 40 stops sending out the fluid W, the fluid W is discharged from the tip opening 111o of the coronary artery model 111, so that the amount of the fluid W in the heart lumen 100i of the heart model 100 decreases, and the heart model 100 can be caused to perform a contraction operation. The "contraction operation of the heart model 100" means that the surface of the heart model 100 moves in the inward direction as the heart model 100 shrinks. When a through hole is provided at a position corresponding to the apex 100b of the heart model 100, the fluid W is also directly discharged from the through hole of the heart model 100, so that the heart model 100 can be contracted more quickly. To promote the contraction operation of the heart model 100, the fluid W may be sucked from the container 21.

[0037] FIG. 3 is a diagram for explaining the configuration of the linear member 51 and the fixing portion 120. The linear member 51 is fixed to the surface of the heart model 100 by the fixing portion 120. The fixing portion 120 has the first end portion 511 of the linear member 51 fixed thereto. The fixing portion 120 has flat portions at both ends and a concave portion in the center. The fixing portion 120 is fitted into a through hole 1003 that penetrates the outer surface 1001 and the inner surface 1002 of the heart model 100. As shown in the figure, the flat portions are brought into contact with the outer surface 1001 and the inner surface 1002, and the wall of the heart model 100 is sandwiched from both sides of the heart model 100. The wall of the heart model 100 is also called the "myocardial wall". The fixing portion 120 is preferably formed of a resin material having X-ray permeability (radiation permeability) that allows X-rays (radiation) to pass through so as not to interfere with the procedure. The fixing portion 120 may be formed of an arbitrary adhesive such as an epoxy-based adhesive. The linear member 51 may be directly fixed to the surface of the heart model 100 using, for example, an adhesive without using the fixing portion 120. The linear member 51 may be fixed by being tied to the heart model 100 without using the fixing portion 120. In these cases, the heart model 100 may not have the through hole 1003.

[0038] As shown in FIG. 3, the linear member 51 extends in a direction D0 that intersects the direction DV perpendicular to the surface 1001 of the heart model 100. As described above, when the driving device 50 pulls the linear member 51, the surface of the heart model 100 is moved in the outer direction of the heart model 100. Therefore, when the linear member 51 shown in FIG. 3 is pulled by the driving device 50, a tensile force (force) is applied to the surface 1001 of the heart model 100 in the direction D0 that intersects the direction DV perpendicular to the surface 1001 of the heart model 100. The direction D0 shown in FIG. 3 is merely an example, and the direction in which the linear member 51 is pulled out may be arbitrarily determined.

[0039] Figures 4 and 5 are diagrams for explaining the fixing position of the linear member 51. Figure 4 is a plan view of the heart model 100. Figure 5 is a 17-segment model of the heart model 100. The 17-segment model of the heart model 100 is a model in which the myocardium is divided into 17 segments. In Figure 4, among the heart model 100, the direction D1 from the apex 100b to the base 100a is represented by a white arrow, and the connection part JO between the coronary artery model 111 and the aorta model 112 is represented by a broken-line round frame. In Figure 4, among the heart model 100, the central part AT that is located between the base 100a and the apex 100b and faces the upper side in the vertical direction in the container 21 is surrounded by a two-dot chain line frame.

[0040] In the present embodiment, the first end 511 of the linear member 51 is connected to an arbitrary position within the region A1 indicated by the diagonal hatching. In other words, the fixing portion 120 is arranged at an arbitrary position within the region A1 indicated by the diagonal hatching. The region A1 is a region corresponding to the 7th segment (papillary muscle anterior wall), the 11th segment (papillary muscle inferior wall), and the 12th segment (papillary muscle anterior lateral wall) of the 17-segment model among the heart model 100. In Figure 4, a virtual straight line L1 connecting the center of the opening 100c of the heart model 100 and the apex 100b is drawn. The 5th segment (basal inferior wall), the 6th segment (basal anterior lateral wall), the 11th segment (papillary muscle inferior wall), and the 12th segment (papillary muscle anterior lateral wall) of the 17-segment model correspond to the right side of the virtual straight line L1.

[0041] No. 7 is, as shown in FIG. 4, a portion of the surface of the heart model 100 that includes the above-described central portion AT and the vicinity of the central portion AT. Nos. 11 and 12 are, as shown in FIG. 4, a central portion between the heart base 100a and the heart apex 100b on the surface of the heart model 100, and correspond to a region where the left coronary artery model 111L is formed. In other words, Nos. 11 and 12 are portions corresponding to the right side of the heart model 100 when the heart model 100 is arranged with the aorta model 112 directed vertically downward (FIG. 1) and viewed from the heart apex 100b to the heart base 100a along the arrow D1. Further in other words, Nos. 11 and 12 are portions corresponding to the heart apex 100b side of the heart model 100 rather than the connection portion JO between the coronary artery model 111 and the aorta model 112. Further in other words, Nos. 11 and 12 are portions located on the side surface of the heart model 100 in a state where the heart model 100 is arranged with the aorta model 112 directed vertically downward (FIG. 1).

[0042] It is known that the heart of an actual human body twists counterclockwise during systole and clockwise during diastole when represented by the 17-segment model shown in FIG. 5. In the present embodiment, by fixing the first end portion 511 of the linear member 51 to the region A1, when the linear member 51 is pulled, the surface of the heart model 100 can be twisted counterclockwise ACW.

[0043] In FIG. 4, for the sake of illustration, the coronary artery model 111, specifically, the left and right coronary artery models 111R, L are described in a simplified manner. Actually, the coronary artery model 111 includes a plurality of fine blood vessels branched from relatively thick blood vessels. For this reason, the "region where the coronary artery model 111 is formed" means a region surrounded by the two outermost blood vessels among the plurality of blood vessels branched from one blood vessel extending from the connection portion JO. Specifically, in the case of the left coronary artery model 111L, it means a region surrounded by the blood vessel extending most anteriorly to the papillary muscle and the blood vessel extending most inferiorly to the papillary muscle among the plurality of blood vessels branched from one left main trunk portion extending from the connection portion JO. These points are the same for FIGS. 7 and 9 described later.

[0044] FIG. 6 is a diagram for explaining the operation timing of the drive device 50. The upper part of FIG. 6 shows a timing chart of the supply and stop of the fluid W in the fluid supply device. The transition of the chart from "stop" to "supply" indicates the timing when the pump of the pulsating unit 40 is turned on. The transition of the chart from "supply" to "stop" indicates the timing when the pump of the pulsating unit 40 is turned off. Let the period of the supply / stop of the fluid W by the fluid supply device (in other words, the period of the pump ON / OFF of the pulsating unit 40) be Pn.

[0045] The middle part of FIG. 6 shows the state transition of the heart model 100 due to the supply of the fluid W from the fluid supply device. The state of the heart model 100 means the state of whether the heart model 100 is in an expanded state or a contracted state. As shown in the figure, when the supply of the fluid W from the fluid supply device starts, the heart model 100 gradually becomes in an expanded state, and when the supply of the fluid W from the fluid supply device stops, the heart model 100 gradually becomes in a contracted state. As shown in the middle part of FIG. 6, the timing when the supply of the fluid by the fluid supply device starts, in other words, the timing when the pump of the pulsating unit 40 is turned on, coincides with the timing when the heart model 100 is most contracted. The timing when the supply of the fluid by the fluid supply device stops, in other words, the timing when the pump of the pulsating unit 40 is turned off, coincides with the timing when the heart model 100 is most expanded. Here, "coincides" means allowing a time lag due to a control error.

[0046] The lower part of FIG. 6 shows a drive timing chart of the drive device 50. The transition of the chart from "return" to "pull" indicates that the drive device 50 performs an operation of pulling the linear member 51 by the movement of the arm 59 of the drive device 50 in a direction away from the container 21. The transition of the chart from "pull" to "return" indicates that the drive device 50 performs an operation of returning (loosening) the linear member 51 by the movement of the arm 59 of the drive device 50 in a direction approaching the container 21. In the part where the "return" state is maintained, the drive device 50 is not operating.

[0047] As shown in the lower part of FIG. 6, the drive device 50 (drive mechanism) of the present embodiment pulls the linear member 51 for a period of t1 hours after a lapse of Pre(n+1) hours from the contraction of the heart model 100, and then repeats the operation of returning the linear member 51 for a period of t2 hours. That is, the drive device 50 of the present embodiment moves the surface of the heart model 100 by pulling the linear member 51 in synchronization with the "contraction" of the heart model 100. As a result, the heart model 100 twists counterclockwise during systole and twists. As described above, the contraction of the heart model 100 coincides with the timing at which the supply of fluid by the fluid supply device is started (the timing at which the pump of the pulsating unit 40 is turned on). Therefore, it can be said that the drive device 50 of the present embodiment moves the surface of the heart model 100 by pulling the linear member 51 after a lapse of a predetermined time from the start of the supply of fluid by the fluid supply device.

[0048] The Pre(n+1) time as the predetermined time is a time determined in consideration of the period Pn, and can be determined, for example, by the following formula (1). Pre(n+1)=Pn×A×R ···(1) In formula (1), n is a natural number indicating the number of processing cycles, A is an arbitrary constant, and R is a random number determined for each processing cycle. The constant A is a constant for taking into account the delay time between the start of the supply of fluid by the fluid supply device and the expansion of the heart model 100, and can be, for example, any value smaller than 1.0. The random number R can be, for example, a random number in the range greater than 0.6 and less than 1.4. By changing the Pre(n+1) time for each processing cycle using the random number R, the drive device 50 of the present embodiment can realize an irregular expansion and contraction operation close to the actual movement of the heart. The calculation of the Pre(n+1) time for each processing cycle using formula (1) may be omitted. In this case, the process may be performed using a predetermined constant Pre time.

[0049] The operation times t1 and t2 are times determined in consideration of the period Pn, and can be determined, for example, by the following formulas (2) and (3). t1=Pn×B ···(2) t2=Pn×C ···(3) In equations (2) and (3), B is an arbitrary constant, and C is an arbitrary constant. The constants B and C can be, for example, any value less than 1.0. In this embodiment, the value of constant B = the value of constant C. The constants B and C may have different values.

[0050] As described above, in addition to the heart model 100 that can expand and contract, that is, the heart model 100 that can expand and contract, the heart model device 1 of the first embodiment includes a drive mechanism (drive device 50, linear member 51). Therefore, in addition to the expansion and contraction operation of the heart model 100, the drive mechanism (drive device 50, linear member 51) can realize the twisting operation of the heart model 100. That is, according to this embodiment, a heart model device 1 capable of causing the heart model 100 to perform an operation combining expansion / contraction and twisting can be provided. As a result, it becomes possible to cause the heart model 100 to perform an operation simulating the movement of an actual heart having a complex motion pattern, and a training environment closer to clinical practice can be provided for the operator.

[0051] In the heart model device 1 of the first embodiment, since the drive mechanism (drive device 50, linear member 51) applies a force in a direction D0 that intersects the direction DV perpendicular to the surface 1001 of the heart model 100, compared with the case of applying a force in the perpendicular direction DV, a three-dimensional twisting operation closer to the movement of an actual heart can be caused for the heart model 100.

[0052] In the heart model device 1 of the first embodiment, since the drive device 50 moves the surface of the heart model 100 outward by pulling the linear member 51, with a simple configuration, the surface of the heart model 100 can be moved, that is, the twisting operation of the heart model 100 can be realized.

[0053] In the heart model device 1 of the first embodiment, if the linear member 51 is fixed to the region (No. 11, No. 12) where the left coronary artery model 111L is formed on the surface of the heart model 100, compared with the case where it is fixed to the region without the left coronary artery model 111L, a three-dimensional twisting motion closer to the movement of the actual heart can be imparted to the heart model 100.

[0054] In the heart model device 1 of the first embodiment, in a state where the heart model 100 is arranged with the aortic model 112 facing vertically downward, when looking at the heart base 100a from the heart apex 100b of the heart model 100, since the linear member 51 is fixed to the right side of the heart apex 100b, the twist during the contraction phase of the heart can be reproduced by twisting the heart model 100 counterclockwise. In the heart model device 1 of the first embodiment, since the linear member 51 is fixed closer to the heart apex 100b side than the connection portion JO between the coronary artery model 111 and the aortic model 112 in the heart model 100, the linear member 51 can be fixed while avoiding the connection portion JO between the coronary artery model 111 and the aortic model 112 where the configuration of the blood vessel model is complex and twisting is less likely to occur.

[0055] In the heart model device 1 of the first embodiment, the linear member 51 is fixed between the heart apex 100b and the heart base 100a of the heart model 100. In other words, the linear member 51 is fixed to the intermediate portion between the heart apex 100b and the heart base 100a. Therefore, a three-dimensional twisting motion closer to the movement of the actual heart can be further imparted to the heart model 100. Since a drive device 50 with a small driving force can be used, a heart model device 1 with a simple configuration can be realized.

[0056] In the heart model device 1 according to the first embodiment, when the plan view of the heart model 100 (FIG. 2) is viewed with the heart base portion 100a on the upper side and the heart apex portion 100b on the lower side, the first end portion 511 of the linear member 51 may be fixed to the right side of the virtual straight line L1 connecting the center of the opening 100c of the heart base portion 100a of the heart model 100 and the heart apex portion 100b. If this is done, by pulling the linear member 51 in the vertically upward direction or a direction intersecting the vertically upward direction (the direction on the front side of the paper surface in FIG. 2), when the heart model 100 is viewed from the heart apex portion 100b toward the heart base portion 100a, a counterclockwise twist can be generated during the contraction period of the heart model 100. In order to generate the twist, since the linear member 51 may be pulled in the vertically upward direction, a heart model device 1 with a simple configuration can be provided.

[0057] In the heart model device 1 according to the first embodiment, since the linear member 51 is drawn out from the inside of the container 21 to the outside, leakage of the liquid from the container 21 due to the arrangement of the linear member 51 can be suppressed (FIG. 1). As the drive device 50, a drive device 50 having a simple configuration without waterproof measures can be used, so that a heart model device 1 with a simple configuration can be realized. The linear member 51 is drawn out in a direction D0 intersecting the direction DV perpendicular to the surface 1001 of the heart model 100 (FIG. 3). Therefore, by driving the drive device 50, a force can be naturally applied in the direction D0 intersecting the direction DV perpendicular to the surface 1001 of the heart model 100. As a result, a three-dimensional twisting motion similar to the actual motion of the heart can be imparted to the heart model 100. Since the linear member 51 is formed of an X-ray transmissive material, it is possible to suppress the linear member 51 from being reflected in the X-ray image and interfering with the procedure.

[0058] In the heart model device 1 according to the first embodiment, the drive mechanism, specifically the drive device 50, moves the surface of the heart model 100 in synchronization with at least one of the expansion and contraction of the heart model 100. In other words, the drive mechanism twists the surface of the heart model 100 in synchronization with at least one of the expansion and contraction of the heart model 100. Therefore, according to the heart model device 1, it is possible to cause the heart model 100 to perform an operation in which the expansion and contraction operations and the twisting operation, which are similar to the actual movement of the heart, are combined in synchronization.

[0059] In the heart model device 1 according to the first embodiment, the drive mechanism, specifically the drive device 50, moves the surface of the heart model 100 after a lapse of a predetermined time from the start of at least one of the expansion and contraction of the heart model 100. Therefore, it is possible to cause the heart model 100 to perform an operation in which the expansion and contraction operations and the twisting operation, which are more similar to the actual movement of the heart, are combined in synchronization.

[0060] <Second Embodiment> FIGS. 7 and 8 are diagrams for explaining the fixed position of the linear member 51A according to the second embodiment. In the second embodiment, the arrangement of the first end portion 511 of the linear member 51A is different from that of the first embodiment described above. FIG. 7 is a plan view of the heart model 100A. FIG. 8 is a 17-segment model of the heart model 100A. FIG. 7 shows the direction D1, the connection portion JO, and the central portion AT described in the first embodiment.

[0061] Region A2 is a general term for region A21 on the right coronary artery model 111R side and region A22 on the left coronary artery model 111L side. Region A21 is the region corresponding to segment 2 (basal anterior wall septum), segment 3 (basal inferior wall septum), segment 8 (papillary muscle anterior septum), and segment 9 (papillary muscle inferior septum) of the 17-segment model in the heart model 100A. As shown in FIG. 8, segments 2, 3, 8, and 9 are the portions corresponding to the region where the right coronary artery model 111R is formed on the surface of the heart model 100A. In the figures after FIG. 6, for the sake of illustration convenience, the coronary artery model 111, specifically the left and right coronary artery models 111R and 111L, are described in a simplified manner. Therefore, the "region where the right coronary artery model 111R is formed" means the region surrounded by the blood vessel extending most anteriorly to the papillary muscle wall and the blood vessel extending most inferiorly to the papillary muscle wall among the plurality of blood vessels branched from one right main trunk extending from the connection part JO.

[0062] Region A22 is the region corresponding to segment 5 (basal inferior lateral wall), segment 6 (basal anterior lateral wall), segment 11 (papillary muscle inferior lateral wall), and segment 12 (papillary muscle anterior lateral wall) of the 17-segment model in the heart model 100A. As shown in FIG. 8, segments 5, 6, 11, and 12 are the portions corresponding to the region where the left coronary artery model 111L is formed on the surface of the heart model 100A.

[0063] That is, region A2 is the region on the surface of the heart model 100A where the coronary artery model 111 is formed. In other words, region A2 is the region on the surface of the heart model 100A where the left and right coronary artery models 111R,L are formed. By adjusting the position where the first end 511 of the linear member 51A is connected to the heart model 100A and the direction in which the linear member is pulled, the twisting direction when the heart model 100A is viewed from the apex 100b towards the base 100a can be set to the clockwise (CW) direction or the counterclockwise (ACW) direction. The position where the first end 511 of the linear member 51A is connected to the heart model 100A can also be said to be the position of the fixing portion 120A. Hereinafter, as specific examples of the linear member 51A, the linear members 51a to 51d are exemplified, and as specific examples of the fixing portion 120A, the fixing portions 120a to 120d are exemplified. The linear members 51a and 51b extend in the vertical direction. The linear members 51c and 51d extend in the horizontal direction. For the linear members 51a to 51d and the fixing portions 120a to 120d, any one set with the same alphabet at the end of the reference numeral may be provided on the heart model 100A. A plurality of sets of the linear members 51a to 51d and the fixing portions 120a to 120d are provided on the heart model 100A, and any one of the linear members may be fixed to the driving device 50.

[0064] For example, by fixing the linear member 51a to the fixing portion 120a and pulling this linear member 51a in the upward direction in FIG. 8, the heart model 100A can be twisted in the clockwise direction. By pulling the linear member 51a in the downward direction in FIG. 8, the heart model 100A can be twisted in the counterclockwise direction.

[0065] By fixing the linear member 51b to the fixing portion 120b and pulling this linear member 51b in the upward direction in FIG. 8, the heart model 100A can be twisted in the counterclockwise direction. By pulling the linear member 51b in the downward direction in FIG. 8, the heart model 100A can be twisted in the clockwise direction.

[0066] For example, by fixing the linear member 51c to the fixing portion 120c and pulling the linear member 51c in the rightward direction in FIG. 8, the heart model 100A can be twisted in the clockwise direction. By pulling the linear member 51c in the leftward direction in FIG. 8, the heart model 100A can be twisted in the counterclockwise direction.

[0067] For example, by fixing the linear member 51d to the fixing portion 120d and pulling the linear member 51d in the rightward direction in FIG. 8, the heart model 100A can be twisted in the counterclockwise direction. By pulling the linear member 51d in the leftward direction in FIG. 8, the heart model 100A can be twisted in the clockwise direction.

[0068] In this way, the position where the first end 511 of the linear member 51A is connected to the heart model 100A can be variously changed. In other words, the position where the fixing portion 120A is provided with respect to the heart model 100A can be variously changed. As described above, it may be any position in the region where the coronary artery model 111 is formed. In other words, the position where the first end 511 is connected may be any position in the region where the left and right coronary artery models 111R, L are formed. The heart model device 1 including the heart model 100A of the second embodiment can also achieve the same effects as those of the first embodiment described above.

[0069] <Third Embodiment> FIGS. 9 and 10 are diagrams for explaining the fixing position of the linear member 51B of the third embodiment. In the third embodiment, the arrangement of the first end 511 of the linear member 51B is different from that of the first embodiment described above. In the heart model 100B of the third embodiment, the fixing portion 120B is arranged at an arbitrary position within the region A3 indicated by the oblique hatching. FIG. 9 is a plan view of the heart model 100B. FIG. 10 is a 17-segment model of the heart model 100B. FIG. 9 shows the direction D1, the connection portion JO, and the central portion AT described in the first embodiment.

[0070] Region A3 corresponds to segment 5 (basal inferior wall), segment 6 (basal anterior wall), segment 11 (inferior wall at the level of the papillary muscle), and segment 12 (anterior wall at the level of the papillary muscle) of the 17-segment model in the heart model 100B. Region A3 is a region corresponding to the right side of the virtual straight line L1 connecting the center of the opening 100c of the heart model 100B and the apex 100b. As shown in FIG. 10, segments 5, 6, 11, and 12 correspond to the portions of the surface of the heart model 100B where the left coronary artery model 111L is formed. In other words, segments 5, 6, 11, and 12 are the portions corresponding to the right side of the heart model 100B when the heart model 100B is placed with the aorta model 112 facing vertically downward and viewed from the apex 100b to the base 100a along the arrow D1 (FIG. 1). Further in other words, segments 5, 6, 11, and 12 are the portions corresponding to the side closer to the apex 100b than the connection part JO between the coronary artery model 111 and the aorta model 112 in the heart model 100B. Further in other words, segments 5, 6, 11, and 12 are the portions located on the side surface of the heart model 100 in the state where the heart model 100B is placed with the aorta model 112 facing vertically downward (FIG. 1).

[0071] In the present embodiment, the first end 511 of the linear member 51B is fixed to the region A3 of the heart model 100B. The linear member 51B extends in the vertical direction. By adjusting the position where the linear member 51B is connected to the heart model 100B (i.e., the position of the fixing portion 120B) and the direction of pulling the linear member 51B, the twisting direction of the heart model 100B when viewed from the apex to the base of the heart model 100B can be set in the clockwise (CW) direction or the counterclockwise (ACW) direction. For example, by fixing the linear member 51B to the fixing portion 120B and pulling this linear member 51B in the upward direction in FIG. 10, the heart model 100B can be twisted in the counterclockwise direction. By pulling the linear member 51B in the downward direction in FIG. 10, the heart model 100B can be twisted in the clockwise direction.

[0072] Thus, the position where the first end 511 of the linear member 51B is connected to the heart model 100B can be changed in various ways. In other words, the position where the fixing portion 120B is provided with respect to the heart model 100B can be changed in various ways. As described above, it may be any position within the region where the left coronary artery model 111L is formed. The heart model device 1 including the heart model 100B of the third embodiment can also achieve the same effects as those of the first embodiment described above.

[0073] <Fourth Embodiment> FIG. 11 is an explanatory diagram illustrating the configuration of the heart model device 1D of the fourth embodiment. In the fourth embodiment, the configurations of the heart model device 1D and the cardiovascular model 10D are different from those of the first embodiment. The heart model device 1D of the fourth embodiment includes a cardiovascular model 10D instead of the cardiovascular model 10, a control device 30D instead of the control device 30, a pulsation unit 40D instead of the pulsation unit 40, a first connection member 41D instead of the first connection member 41, and further includes a pulsation unit 60 in the configuration described in the first embodiment.

[0074] FIG. 12 is an explanatory diagram illustrating the configuration of the cardiovascular model 10D of the fourth embodiment. The cardiovascular model 10D of the fourth embodiment includes a heart model 100D instead of the heart model 100 and a aorta model 112D instead of the aorta model 112 in the configuration described in the first embodiment. As shown in FIG. 12, the heart lumen 100i of the heart model 100D does not communicate with the aorta lumen 112i of the aorta model 112D. The first connection member 41D connects the pulsation unit 40D and the heart model 100D in a state where the lumen 41i of the first connection member 41D communicates with the heart lumen 100i. Through this first connection member 41D, the fluid W sent out from the pulsation unit 40 directly flows into the heart lumen 100i of the heart model 100D.

[0075] The pulsating unit 40D incorporates a pump different from the pump 23. Examples of the pump incorporated in the pulsating unit 40D include a positive displacement reciprocating pump and a rotary pump operated at a low speed. The pulsating unit 40D periodically repeats the delivery and suction of the fluid W to and from the heart lumen 100i of the heart model 100D. When the pulsating unit 40D delivers the fluid W, the delivered fluid W is supplied to the heart lumen 100i to expand the heart model 100D. When the pulsating unit 40D suctions the fluid W, the fluid W remaining inside the heart lumen 100i is suctioned to contract the heart model 100D. Therefore, in the present embodiment, the pulsating unit 40D functions as a "fluid supply and discharge device".

[0076] The second connection member 61 connects the pulsating unit 60 and the aorta model 112 in a state where the inner cavity 61i of the second connection member 61 communicates with the aorta lumen 112i. Through this second connection member 61, the fluid W delivered from the pulsating unit 60 flows into the aorta lumen 112i of the aorta model 112. The pulsating unit 60 incorporates a pulsating pump different from the pump 23, and simulates the blood flow from the aorta model 112 to the coronary artery model 111 by delivering the fluid W with pulsation to the aorta lumen 112i of the aorta model 112. As the pulsating pump, for example, a positive displacement reciprocating pump or a rotary pump operated at a low speed can be used. In FIG. 12, the fluid W as the simulated blood is represented by diagonal hatching.

[0077] The control device 30D controls the pulsating unit 40D, the drive device 50, the pulsating unit 60, and the pump 23 (FIG. 11: dashed arrow).

[0078] Thus, the configuration of the heart model device 1D can be variously modified. A fluid flow path (Fig. 12: dot hatching) for expanding and contracting the heart model 100D and a simulated blood flow path (Fig. 12: diagonal hatching) flowing through the aorta model 112 and the coronary artery model 111 may be realized separately. Even in the heart model device 1D of the fourth embodiment, the same effects as those of the first embodiment described above can be achieved. According to the heart model device 1D of the fourth embodiment, since the fluid flow path for expanding and contracting the heart model 100D and the simulated blood flow path are separated, the heart model 100D can be expanded and contracted more strongly. Since the fluid W flowing through the simulated blood flow path can be pulsated, a circulatory model 10D closer to the movement in an actual human body can be provided even more.

[0079] <Fifth Embodiment> Fig. 13 is a diagram for explaining the operation timing of the drive device 50 of the fifth embodiment. In the fifth embodiment, the operation timing in the drive device 50E is different from that in the first embodiment. The heart model device 1E of the fifth embodiment includes a drive device 50E instead of the drive device 50 in the configuration described in the first embodiment. The explanation of how to view the chart in Fig. 13 is the same as that in the first embodiment described in Fig. 6.

[0080] The upper part of FIG. 13 (the supply / stop timing chart of the fluid W in the fluid supply device), and the middle part (the state transition of the heart model 100) are the same as those in the first embodiment described in FIG. 6. As shown in the lower part of FIG. 13, the driving device 50E of the present embodiment repeats the operation of pulling the linear member 51 for t1 hours after a lapse of Pre(n + 1) hours from the expansion of the heart model 100, and then returning the linear member 51 for t2 hours. That is, the driving device 50E of the present embodiment moves the surface of the heart model 100 by pulling the linear member 51 in synchronization with the "expansion" of the heart model 100. As described above, the expansion of the heart model 100 coincides with the timing when the supply of the fluid by the fluid supply device is stopped. The timing when the supply of the fluid by the fluid supply device is stopped is synonymous with the timing when the pump of the pulsating unit 40 is turned off. Therefore, it can be said that the driving device 50E of the present embodiment moves the surface of the heart model 100 by pulling the linear member 51 after a lapse of a predetermined time from the stop of the fluid supply by the fluid supply device. The formulas (1) to (3) described in the first embodiment can be used in the fifth embodiment.

[0081] In this way, the operation timing in the driving device 50E can be variously changed, and the driving device 50E may move the surface of the heart model 100 in synchronization with the expansion of the heart model 100. In the fifth embodiment, the operation timing of the driving device 50E in the configuration using the fluid supply device described in the first embodiment has been described. However, the above-described operation timing of the driving device 50E is also applicable to the configuration using the fluid supply and discharge device described in the fourth embodiment. Also in such a heart model device 1E of the fifth embodiment, the same effects as those of the above-described first and fourth embodiments can be achieved.

[0082] <Modification Example of the Present Embodiment> The present disclosure is not limited to the above-described embodiments, and can be implemented in various aspects without departing from the gist thereof. For example, the following modifications are also possible.

[0083] [Modification Example 1] In the above-described first to fifth embodiments, an example of the configuration of the heart model devices 1, 1D, and 1E was shown. However, the configuration of the heart model devices 1, 1D, and 1E can be variously modified. For example, in the heart model device 1, the circulatory model 10 may not be immersed in the fluid W in the container 21. In this case, the container 21 can be omitted. For example, the heart model device 1 may include other medical devices (not shown). Examples of other medical devices include, for example, an FPD device, a CT device, and an MRI device. For example, the heart model device 1 may include other medical devices (not shown). Examples of other medical devices include, for example, a catheter, a monorail guide wire, and a through-wire.

[0084] [Modification Example 2] In the above-described first to fifth embodiments, an example of the configuration of the circulatory models 10 and 10D was shown. However, the configuration of the circulatory models 10 and 10D can be variously modified. For example, the circulatory model 10 may include other organ models or blood vessel models. Examples of other organ models include, for example, a lung model simulating the outer shape of the human lung, a diaphragm model simulating the outer shape of the human diaphragm, a brain model simulating the outer shape of the human brain, and a muscle model. Examples of blood vessel models include, for example, a lower limb blood vessel model simulating the outer shape of the human lower limb blood vessels. For example, the circulatory model 10 may be configured by omitting at least a part of the above-described blood vessels. Specifically, the circulatory model 10 may be configured by omitting at least a part of the coronary artery model 111, the aorta model 112, and the artery model 113.

[0085] For example, the heart models 100, 100A, 100B, and 100D may be configured to be scalable without using a fluid supply device or a fluid supply and discharge device. For example, the heart lumen 100i of the heart models 100, 100A, 100B, and 100D may be divided into a plurality of spaces simulating the atria and ventricles. In this case, it is preferable that the spaces communicate with each other so that the fluid W fills each space.

[0086] For example, since the linear member 51 is drawn in the direction DV perpendicular to the surfaces of the heart models 100, 100A, 100B, and 100D, the driving device 50 may apply a force in the direction DV perpendicular to the surface of the heart model 100. For example, the first end 511 of the linear member 51 may be fixed to a region different from the region where the coronary artery model 111 is formed among the surfaces of the heart models 100, 100A, 100B, and 100D (for example, numbers 7 and 10 in FIG. 4).

[0087] In the above embodiment, the driving mechanism is constituted by the driving device 50 and the linear member 51. The driving mechanism may be constituted without using the linear member 51. For example, by directly pushing the surface of the heart models 100, 100A, 100B, and 100D inward using the arm 59 of the driving device 50, the surface of the heart model 100 may be moved in the inner direction of the heart model 100. Instead of the arm 59 of the driving device 50, a rod-shaped member may be attached to the driving device 50, and the surface of the heart model 100 may be pushed in by using the rod-shaped member.

[0088] For example, the heart models 100, 100A, 100B, and 100D may be provided with a plurality of fixing portions 120 for fixing the plurality of linear members 51 respectively. By using the plurality of linear members 51, a more complex twisting motion can be realized.

[0089] [Modification 3] The configurations of the heart model devices 1, 1D, and 1E in the above first to fifth embodiments, and the configurations of the above modifications 1 and 2 may be combined as appropriate. For example, in the heart model device 1D described in the fourth embodiment, the fixing positions of the fixing portions 120 in the heart models 100A to 100B described in any of the second and third embodiments may be adopted. For example, in the heart model device 1E described in the fifth embodiment, the fixing positions of the fixing portions 120 in the heart models 100A to 100B described in any of the second and third embodiments may be adopted.

[0090] Based on the above embodiments and modifications, the present aspect has been described. The embodiments of the above-described aspects are for facilitating the understanding of the present aspect and do not limit the present aspect. The present aspect can be changed and improved without departing from its gist and the scope of the claims, and equivalents thereof are included in the present aspect. If its technical features are not described as essential in this specification, they can be appropriately deleted.

Claims

1. A heart model device (1, 1D, 1E), comprising: A heart model (100, 100A, 100B, 100D) that mimics the heart and is capable of expansion and contraction; and A drive mechanism (50, 50E, 51, 51A, 51B) connected to the heart model (100, 100A, 100B, 100D) and configured to move the surface of the heart model (100, 100A, 100B, 100D) in either an outward or inward direction of the heart model (100, 100A, 100B, 100D). The heart model device (1, 1D, 1E).

2. The heart model device (1, 1D, 1E) according to Claim 1, wherein The drive mechanism (50, 50E, 51, 51A, 51B) applies a force to the surface of the heart model (100, 100A, 100B, 100D) in a direction intersecting a direction perpendicular to the surface.

3. The heart model device (1, 1D, 1E) according to Claim 1 or Claim 2, wherein The drive mechanism (50, 50E, 51, 51A, 51B) includes a linear member (51, 51A, 51B) having a first end (511) and a second end (512), and a drive device (50, 50E); The first end (511) of the linear member (51, 51A, 51B) is connected to the heart model (100, 100A, 100B, 100D), and the second end (512) is connected to the drive device (50, 50E); and The drive device (50, 50E) moves the surface of the heart model (100, 100A, 100B, 100D) in an outward direction by pulling the linear member (51, 51A, 51B).

4. The heart model device (1, 1E) according to Claim 3, wherein The heart model (100, 100A, 100B) has an opening (100c) formed at a position where the aorta model (112) is connected, a heart base (100a) that is a peripheral portion of the opening (100c), and a heart apex (100b) that is a portion farthest from the center of the opening (100c); and The first end (511) of the linear member (51, 51A, 51B) is fixed between the heart apex (100b) and the heart base (100a) of the heart model (100, 100A, 100B).

5. The heart model device (1) according to claim 3 or claim 4, wherein the heart model (100B) has an opening (100c) formed at a position where the aortic model (112) is connected, a heart base part (100a) which is a part of the periphery of the opening (100c), and a heart apex part (100b) which is the part farthest from the center of the opening (100c); when a plan view of the heart model (100B) is viewed with the heart base part (100a) on the upper side and the heart apex part (100b) on the lower side, the first end part (511) of the linear member (51B) is fixed to the right side of a virtual straight line connecting the center of the opening (100c) of the heart base part (100a) of the heart model (100B) and the heart apex part (100b), the heart model device (1).

6. The heart model device (1, 1D, 1E) according to any one of claims 3 to 5, wherein it further comprises a container (21) containing a liquid; the heart model (100, 100A, 100B, 100D) is arranged in the liquid inside the container (21); the driving device (50, 50E) is arranged outside the container (21); the linear member (51, 51A, 51B) is drawn out from inside the container (21) to the outside, the heart model device (1, 1D, 1E).

7. The heart model device (1, 1D, 1E) according to any one of claims 3 to 6, wherein the linear member (51, 51A, 51B) is formed of an X-ray transmissive material, the heart model device (1, 1D, 1E).

8. The heart model device (1, 1D, 1E) according to any one of claims 1 to 7, wherein the driving mechanism (50, 50E, 51, 51A, 51B) moves the surface of the heart model (100, 100A, 100B, 100D) in synchronization with at least one of the expansion and the contraction of the heart model (100, 100A, 100B, 100D), the heart model device (1, 1D, 1E).

9. The heart model device (1, 1D, 1E) according to any one of claims 1 to 8, wherein The drive mechanisms (50, 50E, 51, 51A, 51B) move the surface of the heart model (100, 100A, 100B, 100D) after a lapse of a predetermined time from the start of at least one of the expansion and the contraction of the heart model (100, 100A, 100B, 100D), in a heart model device (1, 1D, 1E).

Images