JP2013029820A - Heart model - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a heart model in which a tubular medical instrument is inserted as a training of surgical operation or examination, appropriately for simulating the actual surgical operation or examination.SOLUTION: A heart model H in which a catheter C can be inserted comprises a heart model body HM including at least regions corresponding to the interventricular septum and the interatrial septum of the real heart, a first region R1 corresponding to a predetermined portion of the real heart excepting the interventricular septum and the interatrial septum, and a second region R2 corresponding to a portion of which the responsiveness to contact pressure in bringing the catheter into contact with an inner surface is higher than that of the predetermined portion, in the real heart. The second region R2 is mounted to the heart model body HM at a position different from the first region R1, and a strength of the second region R2 with respect to the contact pressure is lower than a strength of the first region R1.

Description

  The present invention relates to a heart model used for surgery or examination training, and more particularly to a heart model in which a tubular medical instrument such as a catheter can be inserted.

  The operation and examination of the heart using a tubular medical instrument such as a catheter is already well known. For example, as an examination of the heart using a catheter, a catheter with an electrode attached to the tip is contacted with each part of the myocardial tissue to diagnose a stimulus transmission path in the heart and identify an origin of arrhythmia Yes. In addition, as a heart operation using a catheter, a high frequency is passed between the electrode at the tip of the catheter and a counter electrode attached to the patient's back, and the electrode is brought into contact with the site specified as the origin of arrhythmia, Treatment of arrhythmia is performed by cauterizing the myocardial tissue of the site.

  By the way, as a training for a trainee or the like to actually perform the above-described operation or examination on a human body, a training may be performed using an artificial heart model. The above heart model is formed of, for example, a resin material, and in particular, a flexible material such as silicon rubber may be used for the purpose of approaching the actual human heart (for example, see Patent Document 1). Patent Document 1 discloses a heart model composed of an internal casting that mimics the myocardium and an outer shell corresponding to the epicardium. Both of the two parts in the heart model are silicon. It is made of a flexible member such as rubber. As a result, it is possible to provide a heart model having elasticity similar to that of an actual human heart.

JP-T-2004-508589

  By the way, in the actual human heart, the physical characteristics are different between the parts of the myocardial tissue, and the above physical characteristics are reproduced in order to realize a heart model with higher reality (reproducibility). There is a need. In particular, when a tubular medical instrument such as a catheter is inserted into the heart and brought into contact with the inner surface in actual surgery or examination, the responsiveness to the contact pressure differs between the various parts of the heart, and the difference in the responsiveness. There is a need for the development of a heart model that can be used for training.

  Therefore, the present invention has been made in view of the above problems, and its purpose is to perform an actual operation or examination on a heart model into which a tubular medical instrument such as a catheter is inserted as an operation or examination training. It is to provide an appropriate heart model for simulation.

According to the heart model of the present invention, the subject is a heart model that is used for training of surgery or examination, and in which a tubular medical device can be inserted, and the actual ventricular septum and A heart model body including at least a region corresponding to the atrial septum; a first region attached to the heart model body and corresponding to a predetermined portion of the actual heart excluding the ventricular septum and the atrial septum; It is attached to the heart model body at a position different from the first region, and the responsiveness to the contact pressure when the tubular medical device contacts the inner surface of the actual heart is a predetermined part of the actual heart And a second region corresponding to a higher part, and the strength of the second region with respect to the contact pressure is smaller than the strength of the first region.
In such a heart model, since the first region and the second region exist as regions having different behaviors against the contact pressure when the tubular medical device is contacted to the inner surface, contact according to the contact part It is possible to simulate (reproduce) an actual operation or examination that requires adjustment of the pressure well. In particular, in the present invention, by setting a portion of the actual heart that is more responsive to the contact pressure in the second region and making the strength of the second region smaller than the first region, It is possible to satisfactorily simulate the response when the tubular medical device is brought into contact with the inner surface of the portion of the heart corresponding to the second region.
That is, the heart model of the present invention reproduces well the difference in response to contact pressure when a tubular medical device such as a catheter contacts the inner surface in each part of the heart. It is suitable as a training model used for simulating an actual operation or examination performed by being inserted inside.

In the above heart model, the first region is integrated with the heart model body, and the second region is detachably attached to the integrated heart model body and the first region. It is more preferable that the second region can be replaced with a new one, and the hardness of the second region is smaller than the hardness of the first region.
With such a configuration, it is possible to accurately represent the difference in responsiveness to the contact pressure when the tubular medical device is brought into contact with the difference in hardness between the first region and the second region. Moreover, a reusable heart model is realized by exchanging the deteriorated second region.

In the above heart model, each of the first region and the second region is detachably attached to the heart model body, and the first region is formed in the heart model body. A first engaging portion that engages with the first engaged portion, and the first engaging portion is attached to the heart model body by engaging with the first engaged portion; The contact pressure of a magnitude that releases the engagement state between the engagement portion and the first engaged portion acts on the inner surface, so that the heart model main body is removed, and the second region is A second engaging portion that engages with a second engaged portion formed in the heart model main body, and the second engaging portion engages with the second engaged portion; And the engagement state between the second engagement portion and the second engaged portion is released. When the contact pressure acts on the inner surface, the contact pressure is released from the heart model body, and the contact pressure is released to release the engagement state between the second engagement portion and the second engaged portion. It is even more preferable that the height is smaller than the magnitude of the contact pressure that releases the engaged state between the first engaging portion and the first engaged portion.
With such a configuration, the engagement force between each engagement portion and the engaged portion (that is, the magnitude of the contact pressure for releasing the engagement state between the engagement portion and the engaged portion) is set in the first region and By making it differ between 2nd area | regions, it becomes possible to express correctly the difference of the response with respect to the contact pressure at the time of making a tubular medical device contact.

Further, in the above heart model, among the actual hearts, the first response corresponding to a part having a higher responsiveness to the contact pressure than a predetermined part of the actual heart and lower than a corresponding part of the second region. It is good also as having 3 area | regions, and the said intensity | strength of this 3rd area | region is smaller than the said intensity | strength of the said 1st area | region, and larger than the said intensity | strength of the said 2nd area | region.
In such a configuration, a third region is added in addition to the first region and the second region described above, reflecting the difference in responsiveness to the contact pressure when the tubular medical device is brought into contact with the inner surface. As a result, it is necessary to finely adjust the contact pressure according to the contact site, and it is possible to better simulate an actual operation or examination.

In the above heart model, the first region is a region corresponding to the left ventricle and the right ventricle in the actual heart, and the second region is equivalent to the right atrium in the actual heart. The third region may be a region corresponding to the left atrium of the actual heart.
Alternatively, in the above heart model, the heart model body is a region corresponding to a ventricular septum, an atrial septum, a left ventricle, and a right ventricle in the actual heart, and the second region is the actual heart The first region is a region corresponding to the junction with the pulmonary vein in the left atrium and the posterior myocardial wall, and the first region is a junction with the pulmonary vein in the left atrium of the actual heart. The region may correspond to a region other than the region and the rear myocardial wall.
Alternatively, in the above heart model, the heart model body is a region corresponding to a ventricular septum, a left ventricle, and a right ventricle of the actual heart, and the second region is a portion of the actual heart. The region corresponding to the foveal fossa in the atrial septum, and the first region may be a region corresponding to a portion other than the foveal fossa in the atrial septum of the actual heart. .
As described above, by setting, as the second region, a part of the heart that is particularly important in surgery or examination, particularly a part that requires careful attention when the tubular medical device is brought into contact with the inner surface, A more suitable heart model for training of surgery or examination will be realized.

Further, in the above heart model, the heart model is installed in a human body model body having a tubular member corresponding to a femoral vein connected to the heart model to form a human body model together with the human body model body, The tubular medical device is a catheter having an electrode for identifying or cauterizing the origin of arrhythmia, and it is more preferable that the catheter is inserted into the heart model through the tubular member.
In such a configuration, the catheter is inserted into the heart model through a tubular member corresponding to the femoral vein, as in the case of actual surgery and examination using a catheter for arrhythmia examination and treatment. The reality of the used surgical or examination training will be improved.

In the heart model of the present invention, the first region and the second region exist as regions having different behavior with respect to the contact pressure when a tubular medical device such as a catheter is contacted to the inner surface. It is possible to satisfactorily simulate (reproduce) an actual operation or examination that requires adjustment of the contact pressure according to the condition. In particular, in the present invention, by setting a portion of the actual heart that is more responsive to the contact pressure in the second region and making the strength of the second region smaller than the first region, It is possible to satisfactorily simulate the response when the tubular medical device is brought into contact with the inner surface of the portion of the heart corresponding to the second region.
That is, the heart model of the present invention reproduces well the difference in response to contact pressure when a tubular medical device such as a catheter contacts the inner surface in each part of the heart. The heart model is suitable as a training model used for simulating an actual operation or examination performed by being inserted inside.

It is a figure which shows the insertion route of the catheter C in a surgery or test | inspection. 2A and 2B are schematic external views of the human body model J. FIG. It is an external view of the heart model H (the 1). It is an external view of the heart model H (the 2). It is an external view of the heart model H (the 3). It is an external view of the heart model H (the 4). It is an external view of the heart model H (the 5). It is an external view of the heart model H (the 6). 2 is a schematic cross-sectional view of a heart model H. FIG. It is explanatory drawing about the structure which makes 2nd area | region R2 or 3rd area | region R3 detachable with respect to the heart model main body HM and 1st area | region R1. It is a figure which shows the flow of the process which manufactures each part of the heart model H. It is explanatory drawing about the process which manufactures each part of the heart model H (the 1). It is explanatory drawing about the process which manufactures each part of the heart model H (the 2). It is a figure which shows the heart model H which concerns on a 2nd modification. It is a schematic cross section of heart model H concerning the 3rd modification.

  Hereinafter, a heart model H according to an embodiment (this embodiment) of the present invention will be described with reference to the drawings. The embodiment described below is merely an example for facilitating the understanding of the present invention, and does not limit the present invention. That is, the present invention can be changed and improved without departing from the gist thereof, and the present invention includes the equivalents thereof.

FIG. 1 is a diagram showing an insertion route of the catheter C in the operation or examination. 2A and 2B are schematic external views of the human body model J. Specifically, the human body model J is divided into a ventral part (FIG. 2A) and a dorsal part (FIG. 2B). 3 to 8 are external views of the heart model H, showing a front view, a rear view, a right side view, a left side view, a plan view, and a bottom view, respectively. FIG. 9 is a schematic cross-sectional view of the heart model H. FIG. 10 is an explanatory diagram of a configuration in which the second region R2 or the third region R3 is detachable from the heart model body HM and the first region R1. FIG. 11 is a diagram illustrating a flow of a process for manufacturing each part of the heart model H. 12 and 13 are explanatory diagrams of a process for manufacturing each part of the heart model H. FIG. Specifically, FIG. 12 is a diagram showing a manufacturing process of the first region R1 and the heart model body HM described later, and FIG. 13 shows a manufacturing process of the second region R2 or the third region R3 described later. FIG. FIG. 14 is a diagram showing a heart model H according to a second modification, and corresponds to FIG. FIG. 15 is a schematic cross-sectional view of a heart model H according to the third modification, and corresponds to FIG.
Note that the members shown in FIGS. 12 and 13 are simplified for the sake of illustration, and are slightly different in shape and dimensions from the actual ones.

  The heart model H is a model imitating an actual human heart, and is used for training of surgery or examination, and a catheter C as a tubular medical instrument can be inserted therein. Training is a general term for training, practice, practical tests, and the like performed as a pre-stage for performing actual surgery or examination.

  In particular, the heart model H according to the present embodiment is used as training for surgery or examination using a catheter C having an electrode at the tip. That is, in the heart model H according to the present embodiment, the catheter C with the electrode attached to the distal end portion is inserted as in the actual operation or examination.

  Here, the operation using the catheter C to which the electrode is attached means that a high frequency is passed between the electrode at the tip of the catheter and a counter electrode attached to the back of the patient, and the electrode is brought into contact with the origin of arrhythmia, This is an operation (so-called catheter ablation) in which the myocardial tissue in the region is cauterized to treat arrhythmia. The examination using the catheter C to which the electrode is attached refers to diagnosis of the stimulation transmission path in the heart by bringing the catheter C to which the electrode is attached at the tip into contact with each part of the myocardial tissue, and specifies the origin part of the arrhythmia. Test (electrophysiological catheter test). As described above, inside the heart model H according to the present embodiment, the catheter C in which the electrode for identifying or cauterizing the origin part of the arrhythmia is attached is inserted.

  By the way, in the above-described operation or examination, as shown in FIG. 1, the catheter C is percutaneously inserted into the femoral vein of the human body and pushed into the heart through the femoral vein. On the other hand, in surgery or examination training using the heart model H according to the present embodiment, the catheter C is inserted into the heart model H in the same procedure as described above.

  More specifically, the heart model H according to this embodiment is installed in the hollow human body model main body JH shown in FIGS. 2A and 2B and forms the human body model J together with the human body model main body JH. Here, the human body model main body JH is a portion excluding the heart model H in the human body model J used in training using the catheter C having the electrode at the tip, as shown in FIGS. 2A and 2B. This is a hollow member made of a transparent material that mimics the portion from the thigh to the neck of the human body. Furthermore, the human body model main body JH according to the present embodiment can be disassembled into an abdominal part and a dorsal part, and a rubber tube T as a tubular member imitating a blood vessel is set therein.

  Among the rubber tubes T set in the human body model body JH, there is a rubber tube T corresponding to the femoral vein as shown in FIG. 2B. At the time of the above-described surgery or examination training, a hole is formed in a portion of the outer surface of the human body main body JH located above the rubber tube T corresponding to the femoral vein, and the catheter C corresponds to the femoral vein through this hole. Is inserted into the rubber tube T, and finally inserted into the heart model H through the rubber tube T. As described above, since the catheter C is inserted into the heart model H through the rubber tube T corresponding to the femoral vein, as in the actual operation and examination using the catheter C for the examination and treatment of arrhythmia, the heart model The reality of training of surgery or examination using H is improved.

  When the catheter C reaches the inside of the heart model H, an operator of the catheter C (that is, a training person) operates the catheter C so that the distal end of the catheter C is in contact with the inner surface of the heart model H. As a result, the operator feels at hand when the tip of the catheter C is brought into contact with each part of the heart myocardial tissue, and the degree of application of a delicate force when the tip of the catheter C is brought into contact with a predetermined site. Adjustment and the like can be simulated.

  In the above simulation, it is particularly desirable that the load (contact pressure) applied to the myocardial tissue when the tip of the catheter C is brought into contact with the myocardial tissue of the heart can be accurately reproduced. This is because the responsiveness to the contact pressure when the distal end of the catheter C is contacted varies depending on the myocardial tissue (parts of the heart), and there is a part where a hole is opened or broken with a relatively small contact pressure. Because it exists. For this reason, regarding the heart model H, it is desirable that the behavior with respect to the contact pressure when the distal end of the catheter C is contacted is different in each part.

  The heart model H according to the present embodiment satisfies the above-described requirements, and simulates an actual operation (catheter ablation) or examination (electrophysiological catheter examination) performed by inserting the catheter C into the heart. Therefore, it is suitable as a training model used for this purpose.

  More specifically, the heart model H according to the present embodiment has the outer shape shown in FIGS. 3 to 8, and the heart model H includes the region 3 corresponding to the left ventricle of the actual heart and the right ventricle. A corresponding region 4, a region 5 corresponding to the left atrium, and a region 6 corresponding to the right atrium are provided. Furthermore, in the heart model H, as a part corresponding to a blood vessel connected to the heart, a part 21 corresponding to the inferior vena cava, a part 22 corresponding to the superior vena cava, a part 23 corresponding to the aorta, and a part corresponding to the pulmonary artery 24, a portion 25 corresponding to a pulmonary vein is provided.

  Further, the heart model H according to the present embodiment is a resin molded product that is molded by a manufacturing method described later. Note that the heart model H according to the present embodiment has a translucent hollow body. However, for example, the distal end position of the catheter C inserted into the heart model H can be visually recognized from the outside. In actual surgery or examination, the tip position of the catheter C cannot be confirmed from the outside. However, in surgery or examination training, the tip position of the catheter C can be seen from the outside as in the present embodiment. It is preferable that it is possible to grasp how the tip of the catheter C moves with the operation.

  As shown in FIG. 9, the heart model H according to the present embodiment includes a heart model main body HM and a plurality of regions attached to the heart model main body HM. Some regions have different strengths against the contact pressure when the catheter C contacts the inner surface. More specifically, the heart model H according to the present embodiment includes a first region R1, a second region R2, and a third region R3 that are attached to the heart model body HM at different positions.

  Here, the heart model body HM includes at least regions corresponding to the ventricular septum and the atrial septum of the actual heart. In the heart model H, a first region R1, a second region R2, and a third region R3, which will be described later. It is the part which makes the base for attaching. In other words, the heart model main body HM is a portion excluding the first region R1, the second region R2, and the third region R3 among the portions constituting the heart model H.

  In the present embodiment, the heart model main body HM and the first region R1 are integrally formed as described later, and the integrally formed heart model main body HM and the first region R1 function as a frame in the heart model H. . Then, the remaining region (that is, the second region R2 and the third region R3) is assembled to the heart model body HM and the first region R1 as a frame, thereby completing the heart model H.

  About said 3 area | region R1, R2, R3, the intensity | strength with respect to the contact pressure when the catheter C contact | abuts to an inner surface mutually differs. More specifically, the first region R1 is a region corresponding to a predetermined portion of the actual heart excluding the ventricular septum and the atrial septum, while the second region R2 is the above-described portion of the actual heart. This is a region corresponding to a portion having higher responsiveness to the contact pressure than a corresponding portion of the first region R1 (that is, a predetermined portion of the actual heart). And the intensity | strength with respect to the said contact pressure of 2nd area | region R2 is smaller than the intensity | strength of 1st area | region R1.

  Further, the third region R3 has a higher responsiveness to the contact pressure than the corresponding portion of the first region R1 (that is, the predetermined portion of the actual heart) in the actual heart, and corresponds to the second region R2. This is a region corresponding to a lower part than the part. And the intensity | strength of 3rd area | region R3 is smaller than the intensity | strength of 1st area | region R1, and is larger than the intensity | strength of 2nd area | region R2.

Here, the responsiveness to the contact pressure is a concept indicating the degree of reaction when the contact pressure is received. The higher the responsiveness, the greater the response to the same contact pressure. In other words, it means that the degree of physical or physiological change that occurs when subjected to contact pressure is large.
On the other hand, strength means mechanical strength, and more specifically, is an index indicating the deformation behavior when the catheter C abuts against the inner surface and a contact pressure acts. In the present embodiment, as an example of strength, difficulty in deformation with respect to the contact pressure, in other words, hardness is used. Therefore, in the heart model H according to the present embodiment, the hardness of the second region R2 is smaller than the hardness of the first region R1. That is, the second region R2 is a region richer in elasticity than the first region R1. Further, the hardness of the third region R3 is smaller than the hardness of the first region R1 and larger than the hardness of the second region R2.

  The difference in strength between the regions as described above is caused by the difference in the types of resin materials used for molding the regions. For example, the first region R1 is formed of a thermoplastic resin having flexibility, specifically, silicon rubber having high hardness. The second region R2 is formed of a gel material, and specifically, formed of a material that has high stretchability and is not easily broken. The third region R3 is formed of a thermoplastic resin having flexibility, specifically, silicon rubber having low hardness.

  Here, the correspondence relationship between the above-described regions and the heart model main body HM and the actual heart will be described. As shown in FIG. 9, in this embodiment, the heart model main body HM is located in the ventricular septum of the actual heart. The region 1 corresponds to a region 2 corresponding to the atrial septum. The first region R1 is a region 3 corresponding to the left ventricle and a region 4 corresponding to the right ventricle in the actual heart. The second region R2 is a region 6 corresponding to the right atrium in the actual heart, and the third region R3 is a region 5 corresponding to the left atrium in the actual heart.

  Next, the hardness of each region R1, R2, R3 will be specifically described. In the following description, the contact pressure at the time when the hole is opened by the contact of the distal end of the catheter C, that is, perforation force (hereinafter referred to as PF) will be described as an example of the hardness index. To do.

For the region corresponding to the first region R1, that is, the region 3 corresponding to the left ventricle and the region 4 corresponding to the right ventricle of the actual heart, the PF is 14268 g / cm ² (the diameter of the tip of the catheter C is It is about 700 g) when converted to a load when 2.5 mm. The above value corresponds to the upper limit value of the PF of the ventricular wall (left ventricular wall) measured by extracting a healthy heart.

On the other hand, the PF of the region 6 corresponding to the second region R2, that is, the region 6 corresponding to the right atrium in the actual heart is 8153 g / cm ² (the load when the diameter of the tip of the catheter C is 2.5 mm) When converted, it is about 400 g). The above value corresponds to the average value of the atrial wall (left atrial wall and right atrial wall) measured by removing a healthy heart. In addition, the PF of the region corresponding to the third region R3, that is, the region 5 corresponding to the left atrium in the actual heart is 12229 g / cm ² (load when the diameter of the tip of the catheter C is 2.5 mm) This value is approximately 600 g), and this value corresponds to the upper limit value of the PF of the atrial wall (left atrial wall) measured by extracting a healthy heart.

  As described above, the heart model H according to the present embodiment includes the three regions R1, R2, and R3 having different hardnesses. Thereby, the behavior with respect to the contact pressure when the tip of the catheter C inserted into the heart model H is brought into contact with the inner surface is different between the regions, and the catheter C is inserted into the heart. An actual operation or examination can be simulated well. In particular, in the present embodiment, by setting a portion of the actual heart that is more responsive to the contact pressure in the second region R2, and making the intensity of the second region R2 smaller than the first region, It is possible to satisfactorily simulate the response when the catheter C is brought into contact with the inner surface of the part corresponding to the second region R2 in the actual heart.

  That is, the difference in the responsiveness to the contact pressure when the catheter C is contacted is accurately expressed by the difference in strength (hardness in the present embodiment) between the first region R1 and the second region R2. Is possible. As a result, the difference in responsiveness to the contact pressure when the catheter C is in contact with the inner surface in each part of the heart is well reproduced, and an actual operation or examination performed by inserting the catheter C into the heart Can be simulated well, and it becomes possible to experience the responsiveness to the force applied when the catheter C is operated.

  More specifically, the tip of the catheter C inserted into the heart model H is attached to the inner surface of the region corresponding to the first region R1, that is, the region 3 corresponding to the left ventricle and the region 4 corresponding to the right ventricle. In the case of contact, even if a relatively large contact pressure is applied (specifically, as long as it falls below the above-mentioned PF), the region is not deformed and is not broken (a hole is not opened). This reflects the relatively large PF of the ventricular wall in the actual heart.

On the other hand, when the distal end of the catheter C is brought into contact with the inner surface of the region 6 corresponding to the second region R2, that is, the region 6 corresponding to the right atrium, the region is elastically deformed and is not specifically torn. Stretch. This reflects that the atrial wall PF, particularly the right atrial wall PF, is smaller in the actual heart than the ventricular wall PF.
When the heart model H is configured as described above, the operator of the catheter C visually recognizes, for example, that the region 6 corresponding to the right atrium is abnormally deformed during surgery or examination training. It can be noticed that an excessive contact pressure is acting on the inner surface of the region 6 corresponding to the right atrium, and appropriate catheter operation can be learned through this experience.

  Further, in addition to the first region R1 and the second region R2, a third region R3 is added to reflect the difference in responsiveness to the contact pressure when the catheter C is brought into contact with the inner surface, as described above. In addition, the strength of the third region is smaller than the strength of the first region and larger than the strength of the second region. Specifically, in the region set as the third region R3, that is, the region 5 corresponding to the left atrium, an excessively large contact pressure is applied when the distal end of the catheter C is brought into contact with the inner surface thereof. When it acts (specifically, when a contact pressure higher than the above-mentioned PF acts), the region is broken (a hole is opened). Since the third region R3 is provided, it is necessary to finely adjust the contact pressure according to the contact portion of the catheter C in training for surgery or examination. That is, it becomes possible to better simulate an actual operation or examination in a training scene.

Note that the hardness (specifically, PF) of each of the above-described regions R1, R2, and R3 is merely an example, and is not limited to the above values, and the first region R1 and the third region R3. Other values may be used as long as the second region R2 becomes smaller in order. For example, the above value is a value obtained by measuring and measuring a healthy heart, but an average value or a minimum value of PF measured for a healthy heart in a beating state, or after catheter ablation. It is good also as employ | adopting PF measured about the heart. As a reference value, the average value of PF for the atrial wall of the heart in a healthy beating state is 4663 g / cm ² (about 200 g when converted to a load when the diameter of the tip of the catheter C is 2.33 mm). 2346 g / cm ² (about 100 g in terms of load when the diameter of the tip of the catheter C is 2.33 mm). Since the PF after the catheter ablation is reduced by about 23% from the normal value, it becomes 1877 g / cm ² (about 80 g in terms of the load when the diameter of the tip of the catheter C is 2.33 mm).

  Next, assembly of the heart model H according to the present embodiment will be described. In the heart model H according to the present embodiment, the second region R2 and the third region R3 are relative to a frame (hereinafter also simply referred to as a frame) configured by the integrally formed heart model body HM and the first region R1. It is detachably attached. A configuration in which each of the second region R2 and the third region R3 is detachable from the integrated heart model body HM and the first region R1 will be described with reference to FIG.

  Each of the second region R2 and the third region R3 has a pin 8 protruding from the outer edge of the main body portion 7 (specifically, a portion forming the right atrium and the left atrium) as shown in FIG. Yes. This pin 8 corresponds to an engaging portion and extends along the attaching / detaching direction (the direction indicated by the arrow in FIG. 10) of the second region R2 and the third region R3 with respect to the heart model main body HM, and is shown in FIG. Thus, it has the large diameter part 8a located in the front end side, and the small diameter part 8b which adjoins the large diameter part 8a in the back side of the large diameter part 8a, and is slightly smaller in outer diameter than the large diameter part 8a. In the present embodiment, a plurality of pins 8 are provided in each of the second region R2 and the third region R3 along the outer edge of the main body portion 7 with appropriate intervals.

  On the other hand, a fitting hole 9 for fitting the pin 8 is formed on the frame side. The fitting hole 9 corresponds to an engaged portion, and includes an opening 9a, a bottom portion 9b, and a connecting portion 9c existing between the opening 9a and the bottom portion 9b. The inner diameter of the bottom portion 9 b corresponds to the outer diameter of the large diameter portion 8 a of the pin 8, and the inner diameter of the connecting portion 9 c corresponds to the outer diameter of the small diameter portion 8 b of the pin 8.

  The fitting hole 9 having the above-described shape is a mounting surface to which each of the second region R2 and the third region R3 of the frame is attached (that is, the second region R2 and the heart region HM and the first region R1). (Bonding surface with each of the third regions R3). In the present embodiment, the same number of fitting holes 9 as the pins 8 formed in each of the second region R2 and the third region R3 are located on the mounting surface at positions corresponding to the pins 8, respectively. Is formed.

  In the configuration described above, each of the second region R2 and the third region R3 approaches the frame along the attaching / detaching direction, and each pin 8 is fitted into the corresponding fitting hole 9, thereby To the frame, that is, the integrated heart model body HM and the first region R1. Here, the fact that each pin 8 is fitted into the corresponding fitting hole 9 means that each pin 8 is engaged with the corresponding fitting hole 9. Such an engaged state is maintained unless a force of a predetermined magnitude or more is applied in the direction of removing the second region R2 and the third region R3 from the frame.

  More specifically, even if some force acts in the direction of removing from the frame for each of the second region R2 and the third region R3, the large-diameter portion 8a of the pin 8 is connected to the bottom portion 9b of the fitting hole 9. Since it is latched by the level | step difference formed in the boundary position with the connection part 9c, the engagement state of the pin 8 and the fitting hole 9 is maintained (that is, each of 2nd area | region R2 and 3rd area | region R3 is). Will not be removed from the frame). On the other hand, when a force exceeding the locking force for the large-diameter portion 8a of the pin 8 is applied to each of the second region R2 and the third region R3 in the direction of removal from the frame, the pin 8 and the fitting hole 9 The engagement state is released, and each of the second region R2 and the third region R3 is detached from the frame.

  As described above, in the heart model H according to the present embodiment, each of the second region R2 and the third region R3 is detachable from the integrated heart model body HM and the first region R1. For example, when the second region R2 is aged or damaged due to the use of the heart model H, the second region R2 can be replaced with a new second region R2. Also, in the third region R3, when a hole is opened or damaged in the third region R3, the third region R3 can be replaced with a new third region R3. Thus, by replacing the deteriorated second region R2 with a new second region R2, or replacing the damaged third region R3 with a new third region R3, a reusable heart model H is obtained. It will be realized.

  In addition, for example, a case assumed as training using a configuration in which each of the second region R2 and the third region R3 is detachable from the integrated heart model body HM and the first region R1. Accordingly, the characteristics of the second region R2 and the third region R3 can be switched. More specifically, the second region R2 and the third region R3 having different intensities can be replaced by training for operating a healthy heart and training for operating a heart having a disease. In addition, depending on the situation using the heart model H, such as the heart of a child and adult, the heart of a man and a woman, and when the trainee uses it for surgical training or for a doctor examination Thus, the second region R2 and the third region R3 having different strengths may be replaced.

Next, a method for manufacturing the heart model H according to the present embodiment will be described with reference to FIGS.
As shown in FIG. 11, the process of manufacturing the heart model H starts from a step of obtaining two-dimensional tomographic image data (hereinafter referred to as CT data) of the heart by performing tomography such as CT scan on the human body. (S001). By reconstructing CT data from two-dimensional data to three-dimensional data by image processing, it becomes possible to specify the outer and inner surfaces of the heart. Here, the space located inside the inner surface of the heart is an internal space that defines each part of the heart (ventricle, atrium, aorta, vena cava, pulmonary artery, pulmonary vein, etc.), and there is no space between the inner surface and the outer surface. A space occupied by the myocardium and corresponds to a portion for specifying the shape of the heart.

  After obtaining the CT data, based on the CT data, the heart model main body HM and the outer shape 11 and the inner shape 12 of the first region R1 shown in FIG. 12 are manufactured (S002). Here, as described above, the heart model main body HM corresponds to the ventricular septum and the atrial septum, and the first region R1 corresponds to the left ventricle and the right ventricle. The outer shape 11 is a solid body whose outer shape is defined by the outer surface of the heart, and the inner shape 12 is a solid body whose outer shape is defined by the inner surface of the heart. The outer shape body 11 and the inner shape body 12 are manufactured separately, and specifically, are manufactured using a known stereolithography method based on the acquired CT data.

  After obtaining the outer shape 11 and the inner shape 12, the basic die 13 is created using the outer shape 11 (S003). The basic mold 13 forms an outer frame (split mold) when the heart model main body HM and the first region R1 are molded. The basic mold 13 is placed in the mold F with the outer shape 11 placed inside the mold F. Created by filling rubber. That is, the basic die 13 is a frame-like body having a cavity 13 a having the same shape as the outer shape of the outer body 11.

  As will be described later, since the core 15 is accurately positioned at a predetermined position and set in the cavity 13a, the core 15 is set in advance in the outer body 11. It is desirable that a positioning projection used at the time is formed. By forming such a protrusion, a positioning part (not shown) for positioning the core 15 is formed at a position corresponding to the protrusion on the basic mold 13 created from the outer body 11, and this positioning part is used. Thus, the core 15 can be accurately set in the cavity 13a. As the protrusions formed in advance on the outer shape 11 described above, a portion formed corresponding to a portion where a part of the inner surface of the heart protrudes, for example, in a connection portion with an artery or vein in the outer shape 11. It is desirable to use the corresponding part.

  Next, the core mold 14 is created using the inner shape 12 (S004). The core mold 14 forms an outer frame (split mold) when the core 15 having the same outer shape as the inner shape 12 is formed, and the rubber is formed with the inner shape 12 in the mold F. Created by filling. That is, the core mold 14 is a frame-like body having a cavity 14 a having the same shape as the outer shape of the inner shape body 12.

  After the core mold 14 is formed, the core 15 is formed by injecting a low melting point metal into the cavity 14a of the core mold 14 (S005). Thereafter, the created core 15 is set at a predetermined position in the cavity 13a of the basic mold 13 (S006). At this time, as described above, a positioning portion for positioning the core 15 is formed in the cavity 13a of the basic die 13 in advance, and the core 15 is accurately positioned using the positioning portion. It is possible.

  After setting the core 15 in the cavity 13a of the basic mold 13, a predetermined resin material is injected into the gap (gate) between the inner surface of the cavity 13a and the outer surface of the core 15 (S007). . When the heart model main body HM and the first region R1 are molded, a thermoplastic resin (silicon rubber) having a high hardness is injected as described above. Thereby, the resin molded product 16 including the core 15 and having the same outer shape as the cavity 13a of the basic mold 13 is formed.

  Thereafter, the resin molded product 16 is taken out from the basic mold 13 and the low melting point metal constituting the core 15 contained in the resin molded product 16 is melted (S008). Thereby, the resin molded product 16 is formed with a hollow body having a predetermined thickness, that is, the heart model body HM and the first region R1. The heart model main body HM and the first region R1 are integrally formed by a series of steps described above.

  When the heart model main body HM and the first region R1 are molded, as described above, the pin 8 is attached to the joint surface of the second region R2 and the third region R3 of the heart model main body HM and the first region R1. It is necessary to form a fitting hole 9 for fitting. For this reason, when injecting the thermoplastic resin into the cavity 13a of the basic mold 13, in addition to the core 15, the hole forming body 17 (see FIG. 12) for forming the fitting hole 9 is made of a low melting point metal. It is created and set at a predetermined position (a position corresponding to the position where the fitting hole 9 is formed) of the cavity 13a of the basic mold 13. Thereafter, the resin molded product 16 is taken out from the basic mold 13 and melted by melting the low melting point metal constituting the core 15 contained in the resin molded product 16 and the low melting point metal constituting the hole forming body 17. The heart model main body HM and the first region R1 having the joint hole 9 at a predetermined position are formed.

  On the other hand, as shown in FIG. 13, the second region R2 and the third region R3 are also formed by a procedure substantially similar to the steps S001 to S008 described above. Here, when forming 2nd area | region R2 and 3rd area | region R3, it is necessary to form the above-mentioned pin 8 which protrudes from the main-body part 7. FIG. For this reason, when creating the basic mold 13, together with the outer body 11, the mold member F with the cylindrical member 18 (see FIG. 13) having the same outer shape as the pin 8 is placed in the mold frame F. Fill the inside with rubber. That is, in the case of molding each of the second region R2 and the third region R3, the basic mold 13 includes a cavity 13a having the same shape as the outer shape of the outer body 11, and a pin forming hole 13b having the same shape as the outer shape of the pin 8. , Will come to have. By injecting the resin material into the basic mold 13, the second region R2 and the third region R3 having the pins 8 at predetermined positions are molded.

  The integrated heart model main body HM and the first region R1 (that is, the frame) and the second region R2 and the third region R3 formed as the fragment members are respectively formed by the procedure as described above. Then, by fitting each of the pins 8 provided in the second region R2 and the third region R3 into the fitting hole 9 formed in the frame, the second region R2 and the third region with respect to the frame. R3 is assembled. When such assembly is completed, the heart model H according to the present embodiment is completed.

  The replacement second region R2 and third region R3 (that is, the new second region R2 and third region R3) are also formed by the same procedure as the above-described procedures S001 to S008.

<< About the heart model H according to the first modification >>
In the embodiment described above (hereinafter referred to as the present example), the heart model body HM and the first region R1 are integrated, and the second heart model HM and the first region R1 are integrated with each other. The region R2 and the third region R3 are detachably attached. However, the present invention is not limited to this, and a configuration in which the first region R1 is detachably attached to the heart model body HM is also conceivable.
Furthermore, in this example, the strength of each of the regions R1, R2, and R3 is defined by hardness (easiness of tearing, easiness of elongation). However, the present invention is not limited to this. It may be specified by an indicator.

  Hereinafter, a configuration in which the first region R1 is detachably attached to the heart model main body HM will be described as a first modification of the heart model H. Hereinafter, the heart model H including only the first region R1 and the second region R2 will be described as a specific example, but the description of the configuration common to this example will be omitted.

  In the heart model H according to the first modification, the first region R1 and the second region R2 are detachably attached to the heart model body HM, respectively. That is, in the first modified example, unlike the present example, the first region R1 is separate from the heart model main body HM, and the heart model main body HM and the first region R1 are individually molded. Molded with In the heart model H according to the first modification, the first region R1 is a region 3 corresponding to the left ventricle and a region 4 corresponding to the right ventricle in the actual heart. The second region R2 is a region 5 corresponding to the left atrium and a region 6 corresponding to the right atrium in the actual heart.

  And the above-mentioned pin 8 is formed in the 1st field R1 and 2nd field R2 side so that the 1st field R1 and 2nd field R2 can be attached detachably with respect to heart model main part HM, The aforementioned fitting hole 9 is formed on the heart model main body HM side.

  Here, the pin 8 provided in the first region R1 corresponds to the first engaging portion, and the pin provided in the first region R1 among the plurality of fitting holes 9 provided in the heart model body HM. The fitting hole 9 into which 8 is fitted (that is, the fitting hole 9 corresponding to the pin 8 corresponding to the first engaging portion) corresponds to the first engaged portion. The first region R1 is attached to the heart model main body HM by engaging the pin 8 provided in the first region R1 with the fitting hole 9 corresponding to the pin 8.

  Similarly, the pin 8 provided in the second region R2 corresponds to the second engaging portion, and among the plurality of fitting holes 9 provided in the heart model body HM, the pin provided in the second region R2 The fitting hole 9 into which 8 is fitted (that is, the fitting hole 9 corresponding to the pin 8 corresponding to the second engaging portion) corresponds to the second engaged portion. Then, the second region R2 is attached to the heart model main body HM when the pin 8 provided in the second region R2 is engaged and engaged with the fitting hole 9 corresponding to the pin 8.

  On the other hand, in surgery or examination training using the catheter C, when the tip of the catheter C is brought into contact with the inner surface of the heart model H, if the contact portion is the inner surface of the first region R1, the first region The contact pressure of such a magnitude that the engagement state between the pin 8 provided in R1 and the fitting hole 9 is released (in other words, the pin 8 is fitted into the pin 8 provided in the first region R1. When the contact pressure (extracted from the fitting hole 9) is applied, the first region R1 comes out of the heart model body HM.

  Similarly, when the contact portion of the distal end of the catheter C is the inner surface of the second region R2, the size of the engagement between the pin 8 provided in the second region R2 and the fitting hole 9 is released. When the contact pressure acts, the second region R2 comes out of the heart model body HM.

  In the first modified example, the magnitude of the contact pressure for releasing the engagement state between the pin 8 provided in the second region R2 and the fitting hole 9 is the same as that of the pin 8 provided in the first region R1. It is smaller than the magnitude of the contact pressure for releasing the engaged state with the fitting hole 9. That is, also in the first modified example, the first region R1 and the second region R2 have different strengths against the contact pressure when the catheter C contacts the inner surface, and the strength of the second region R2 However, it is smaller than the strength of the first region R1.

  Further, the strength in the first modification is the magnitude of the contact pressure required to release the engagement state between the pin 8 and the fitting hole 9, and is provided in the second region R2 as described above. The contact pressure for releasing the engaged state between the pin 8 and the fitting hole 9 is the contact pressure for releasing the engaged state between the pin 8 and the fitting hole 9 provided in the first region R1. It is smaller than the size of. As a result, the engagement force between each engagement portion and the engaged portion (that is, the magnitude of the contact pressure for releasing the engagement state between the engagement portion and the engaged portion) is set to the first region R1 and the second region. By making the difference between the regions R2, the heart model H in which the difference in responsiveness to the contact pressure when the catheter C is brought into contact with the inner surface is accurately expressed.

  In addition, about the magnitude | size of the contact pressure required to cancel the engagement state of the pin 8 and the fitting hole 9, it can adjust by changing the shape of the pin 8 or the fitting hole 9, etc., For example, it may be set with the same value as the hardness (specifically, PF) described in this example. In the first modification, the pin 8 and the fitting hole 9 are given as an example of the engaging portion and the engaged portion. However, the present invention is not limited to this, and the first region R1 or the second region R2 is not limited thereto. As long as they are engaged with each other for assembling to the heart model main body HM, they can be used as the engaging portion and the engaged portion without limitation.

<< About the heart model H according to the second modification >>
In this example and the first modification described above, a plurality of regions (that is, the first region R1 to the third region R3) attached to the heart model body HM are regions corresponding to the ventricle and the atrium of the actual heart. It was supposed to be. That is, in the embodiment described above, the region corresponding to the atrium / ventricle partitioned by the myocardium and the septum in the actual heart is attached to the heart model body HM. However, the present invention is not limited to this. For example, the first region R1 and the second region R2 attached to the heart model body HM are regions corresponding to predetermined portions (regions of interest) in the atria and ventricles, respectively. It is good as well.

  A heart model H shown in FIG. 14 will be described as a specific example of the above contents (hereinafter, a second modification).

  In the heart model H according to the second modification, the heart model body HM is a region corresponding to the ventricular septum, the atrial septum, the left ventricle, and the right ventricle in the actual heart. On the other hand, the second region is a region 5b corresponding to the junction with the pulmonary vein in the left atrium and a region 5c corresponding to the myocardial wall on the back side of the left atrium in the actual heart. Of the actual heart, this is a region 5a corresponding to a portion other than the junction with the pulmonary vein and the posterior myocardial wall (hereinafter referred to as the left atrial body) in the left atrium. The region 5b corresponding to the junction with the pulmonary vein in the left atrium and the region 5c corresponding to the myocardial wall behind the left atrium are detachably attached to the region 5a corresponding to the left atrial body. ing.

  Here, in the left atrium, the joint portion with the pulmonary vein and the posterior myocardial wall correspond to the above-mentioned region of interest, specifically, the portion to be cauterized in actual surgery, and the distal end of the catheter C This is a part that requires a greater degree of caution in the operation of abutting. Therefore, in the above configuration, the region corresponding to the region of interest, that is, the region 5b corresponding to the junction with the pulmonary vein in the left atrium and the region 5c corresponding to the myocardial wall on the back side of the left atrium In order to increase the responsiveness to the contact pressure when the tip of the catheter C is contacted, the region corresponding to the region of interest may be the second region R2 having a smaller strength against the contact pressure. . As described above, a part of the heart that is particularly important in surgery or examination, particularly a part (part of interest) that requires careful attention when the catheter C is brought into contact with the inner surface is set as the second region R2. By doing so, a more suitable heart model H is realized as a heart model for training of surgery or examination.

When the region corresponding to the region of interest is set as the second region R2, the PF as the strength of the second region R2 is, for example, 1408 g / cm ² (the diameter of the tip of the catheter C is 2.33 mm). In terms of the load in the case, it is preferably about 60 g). Such a value corresponds to a general contact pressure when catheter ablation is performed as an arrhythmia treatment. The PF is more preferably 235 to 704 g / cm ² (about 10 to 30 g in terms of load when the diameter of the tip of the catheter C is 2.33 mm). This value is safe in avoiding pops (water vapor explosion phenomenon that occurs when the temperature of the deep part of the myocardium suddenly rises while water is sprayed from the tip of the catheter C and the tip electrode is cooled) during catheter ablation. This corresponds to the contact pressure at which catheter ablation can be performed.

<< About the heart model H according to the third modification >>
In the second modification described above, the region of interest in the left atrium is the junction with the pulmonary vein and the posterior myocardial wall. However, the present invention is not limited to this. It is good. For example, as shown in FIG. 15, a region 26 corresponding to the foveal fossa formed in the septum of the right atrium and the left atrium (hatched portion in FIG. 15, hereinafter also referred to as the atrial septum). A configuration in which the region of interest is a region of interest (hereinafter, a third modified example) is also conceivable.

  The foveal fossa is a part where a hole is formed by a Brocken blow technique (a technique of making a hole with a needle attached to the tip of the catheter C) in actual surgery. In consideration of such circumstances, in the heart model H according to the third modified example, the region 26 corresponding to the foveal fossa is set as the second region R2 having a lower strength against the contact pressure, and the oval circle in the atrial septum A region corresponding to a portion other than the fovea is a first region R1, and the other region is a heart model body HM. In the third modified example, the region 26 corresponding to the foveal fossa is made of a material that opens a hole with a predetermined puncture force (a force required to open a hole using a blocken blow needle). The puncture force is preferably set to be about 2 to 3N.

  In surgical training using the heart model H, a hole is formed in the region 26 corresponding to the foveal fossa as in actual surgery. For this reason, it is preferable that the region 26 corresponding to the foveal fossa can be exchanged, and can be easily exchanged by, for example, peeling it off and replacing it with a new one when it is torn.

<< About the heart model H according to the fourth modification >>
In the embodiments described above, the strength against the contact pressure when the distal end of the catheter C is in contact with the inner surface is difficult to deform (hardness) with respect to the contact pressure, and the engagement portion and the engaged portion. The contact pressure is such that the engagement state with the joint portion (the engagement state between the pin 8 and the fitting hole 9 in the above embodiment) is released. However, the present invention is not limited to this, and other indices such as yield point, elastic modulus, plasticity, fracture energy, and tensile strength may be used as the strength against the contact pressure.

  As an example of using an index other than the hardness and the engaged state as the strength against the contact pressure (hereinafter referred to as a fourth modified example), a heart model H in which a region 5 corresponding to the left atrium is formed of a material having a high elastic modulus. Is mentioned. In the heart model H according to the fourth modified example, when a contact pressure acts on the region 5 corresponding to the left atrium, the heart model H extends without breaking. That is, in the fourth modified example, the elastic modulus, in other words, the tensile breaking strength is used as the strength against the contact pressure, and the heart model H so that the region 5 corresponding to the left atrium is higher in elasticity than the other regions. Is configured. That is, in the fourth modified example, the region 5 corresponding to the left atrium corresponds to the second region R2, and the other regions (regions corresponding to the right atrium, the left ventricle, and the right ventricle) correspond to the first region R1. .

  When training is performed using the heart model H having the above configuration, for example, when the tip of the catheter C is brought into contact with the inner surface of the region 5 corresponding to the left atrium, The region 5 corresponding to the atrium bulges outward. By observing the deformation, the operator of the catheter C can notice that an excessive contact pressure is acting on the inner surface of the region 5 corresponding to the left atrium in training for surgery or examination, Through this experience, appropriate catheter operation can be learned.

In obtaining the above effect, the tensile rupture strength of the region 5 corresponding to the left atrium may be designed based on the tensile rupture strength of the myocardium in the actual heart. Specifically, in the case of a human heart in the twenties, the tensile strength of myocardium is 14.1 g / mm ^{2 in} the direction along the myocardial fibers and 1/3 of the above value in the direction perpendicular to the myocardial fibers. It becomes the corresponding size, and the maximum elongation is 69.2%. Based on such data, the region 5 corresponding to the left atrium bulged (deformed) when the tip of the catheter C having a tip diameter of 2.33 mm was pressed against the inner surface with a load of 20 to 60 g. It is preferable to set the tensile strength at such a level that it can be visually recognized.

  Further, the tensile strength at break of the myocardium in the human heart varies depending on the age, and about 0.72 for humans in their 50s when the value for humans in their 20s is the standard (1.0). It is about 0.67 for humans in their 60s to 70s. Considering the correlation between the age and the tensile strength of myocardium, and assuming the age of the patient undergoing surgery or examination in surgery or examination training, it corresponds to the left atrium according to that age. It is more preferable to design the tensile breaking strength of the region 5.

  In addition to the method described above, the strength can be expressed by a material whose characteristics change suddenly when the contact pressure rises to a predetermined value (for example, when the elasticity changes depending on the contact pressure). In addition, a material that abnormally extends from a certain value of contact pressure may be used.

1 region corresponding to the ventricular septum, 2 region corresponding to the atrial septum,
3 region corresponding to the left ventricle, 4 region corresponding to the right ventricle,
5 region corresponding to the left atrium, 5a region corresponding to the left atrial body,
5b Area corresponding to the junction with the pulmonary vein,
5c region corresponding to the posterior myocardial wall, 6 region corresponding to the right atrium,
7 body part, 8 pins, 8a large diameter part, 8b small diameter part,
9 fitting hole, 9a opening, 9b bottom part, 9c connecting part,
11 outer shape, 12 inner shape, 13 basic type, 13a cavity,
13b pin formation hole, 14 core type, 14a cavity,
15 core, 16 resin molded product, 17 hole forming body, 18 cylindrical member,
21 part corresponding to the inferior vena cava, 22 part corresponding to the superior vena cava,
23 part corresponding to the aorta, 24 part corresponding to the pulmonary artery,
25 region corresponding to the pulmonary vein, 26 region corresponding to the foveal fossa,
C catheter, F formwork,
H heart model, HM heart model body,
J human body model, JH human body model body,
R1 first region, R2 second region, R3 third region, T rubber tube

Claims (8)

A heart model used for surgery or examination training, in which a tubular medical device can be inserted;
A heart model body including at least a region corresponding to a ventricular septum and an atrial septum of an actual heart;
A first region attached to the heart model body and corresponding to a predetermined portion of the actual heart excluding the ventricular septum and the atrial septum;
It is attached to the heart model body at a position different from the first region, and the responsiveness to the contact pressure when the tubular medical device contacts the inner surface of the actual heart is predetermined for the actual heart. A second region corresponding to a region higher than the region,
A heart model, wherein a strength of the second region with respect to the contact pressure is smaller than the strength of the first region. The first region is integrated with the heart model body,
The second region is detachably attached to the integrated heart model body and the first region, and can be replaced with a new second region.
The heart model according to claim 1, wherein the hardness of the second region is smaller than the hardness of the first region. Each of the first region and the second region is detachably attached to the heart model body,
The first region includes a first engaging portion that engages with a first engaged portion formed in the heart model body, and the first engaging portion engages with the first engaged portion. By this, the contact pressure of a magnitude that is attached to the heart model main body and is disengaged between the first engaging portion and the first engaged portion acts on the inner surface, Coming off the heart model body,
The second region includes a second engaging portion that engages with a second engaged portion formed in the heart model body, and the second engaging portion engages with the second engaged portion. By this, the contact pressure of a magnitude that is attached to the heart model main body and releases the engagement state between the second engagement portion and the second engaged portion acts on the inner surface, Coming off the heart model body,
The magnitude of the contact pressure for releasing the engagement state between the second engagement portion and the second engaged portion is the engagement state between the first engagement portion and the first engaged portion. The heart model according to claim 1, wherein the contact pressure is smaller than a magnitude of the contact pressure for releasing the pressure. Of the actual heart, further comprising a third region corresponding to a portion having a higher responsiveness to the contact pressure than a predetermined portion of the actual heart and lower than a corresponding portion of the second region,
The heart model according to claim 2 or 3, wherein the intensity of the third region is smaller than the intensity of the first region and larger than the intensity of the second region. The first region is a region corresponding to the left ventricle and the right ventricle in the actual heart,
The second region is a region corresponding to the right atrium in the actual heart,
The heart model according to claim 4, wherein the third region is a region corresponding to the left atrium in the actual heart. The heart model body is a region corresponding to the ventricular septum, the atrial septum, the left ventricle, and the right ventricle of the actual heart,
The second region is a region corresponding to the junction with the pulmonary vein in the left atrium and the posterior myocardial wall of the actual heart,
The said 1st area | region is an area | region corresponded to parts other than the junction part with the said pulmonary veins, and the said rear myocardial wall in the left atrium among the said actual hearts. The heart model described in. The heart model body is a region corresponding to the ventricular septum, the left ventricle, and the right ventricle of the actual heart,
The second region is a region corresponding to the foveal fossa in the atrial septum of the actual heart,
4. The heart model according to claim 2, wherein the first region is a region corresponding to a portion other than the foveal fossa in the atrial septum of the actual heart. The heart model is installed in a human body model body having a tubular member corresponding to a femoral vein connected to the heart model to form a human body model together with the human body model body,
The tubular medical device is a catheter having an electrode for identifying or ablating the origin of arrhythmia,
The heart model according to any one of claims 1 to 7, wherein the catheter is inserted into the heart model through the tubular member.

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