JP2007333782A - Control method of simulated heart - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To reproduce the operation approximate to the actual pulsating state of a heart. <P>SOLUTION: In controlling a simulated heart 1 internally formed with an atrium section 2 and ventricle section 3 corresponding to the atrium and ventricle, a pressurization and evacuation period for switching pressurization and evacuation for the atrium section 2 and the ventricle section 3 is determined and the atrium section 2 and the ventricle section 3 are pressurized according to the pressurization and evacuation period, meanwhile, in evacuating the atrium section 2 and the ventricle section 3, and pressurizing the atrium section 2 and the ventricle section 3, the air in the atrium section 2 and ventricle section 3 corresponding to the excess component is released to the outside when the internal pressure of the atrium section 2 and the ventricle section 3 exceeds the specified value. <P>COPYRIGHT: (C)2008,JPO&INPIT

Description

  The present invention relates to a method for controlling a simulated heart, and more particularly, to a method for controlling a simulated heart suitable for training of teaching materials and surgical techniques related to the heart.

  In recent years, in coronary artery bypass surgery (hereinafter referred to as “CABG”), an off-pump coronary artery anastomosis in which the blood flow of the coronary artery at the anastomosis is temporarily blocked and the bypass blood vessel is anastomosed has been established. This off-pump coronary artery anastomosis can be performed if the patient can withstand general anesthesia and incision of the sternum, and the advantage of avoiding the risk in CABG performed using a heart-lung machine. There is.

There has been proposed a simulator for surgical training capable of training the vascular anastomosis surgical technique in such an off-pump coronary artery anastomosis in an environment close to the clinical experience before accumulating the clinical experience (for example, Patent Document 1). reference). Such a simulator for surgical training includes a rotation driving means, a crank mechanism coupled to the rotation driving means, a swinging means that operates following the crank mechanism, and a simulated heart attached to the swinging means. Using a swinging simulated heart, it is possible to learn vascular anastomosis surgical techniques.
JP 2005-202267 A

  However, in the conventional surgical training simulator as described above, the pulsating state of the heart is reproduced by oscillating the simulated heart by the oscillating means that operates following the crank mechanism. There is a problem that it is not possible to reproduce the feeling that blood is circulating inside.

  The present invention has been made in view of such conventional problems, and an object of the present invention is to provide a method for controlling a simulated heart that can reproduce an operation approximating an actual heart beat state.

  In order to achieve the above object, a simulated heart control method according to the present invention is a simulated heart control method in which spaces corresponding to the atrium and ventricle are formed, and switches between pressurization and decompression of the space. A step of determining a pressure increasing / decreasing cycle, a step of pressurizing the space according to the pressure increasing / decreasing cycle, a step of depressurizing the space according to the pressure increasing / decreasing cycle, and an internal pressure of the space when pressurizing the space. And a step of discharging the air in the space corresponding to the excess when the value exceeds a certain value to the outside.

  According to the method for controlling the simulated heart, it is possible to reproduce an action approximating the pulsating state of the actual heart by pressurizing and depressurizing the space in the simulated heart in accordance with the determined pressure increase / decrease cycle. It becomes. In particular, by preparing a number of pressure increasing / decreasing periods for the space in the simulated heart, it is possible to reproduce motions corresponding to various pulsation states with the simulated heart. In this case, if the internal pressure of the space in the simulated heart exceeds a certain value, the internal pressure of the space is adjusted. Therefore, when the motion corresponding to various pulsation states is reproduced with the simulated heart, the maximum expansion is achieved. Since the capacity of the space at the time of being performed can be maintained constant, it is possible to reproduce the motion approximated by the actual heart beat state.

  The simulated heart control method may include a step of receiving an instruction for specifying a pulsation state reproduced by the simulated heart, and the pressurization / decompression period may be determined according to the instruction. In this case, since the operation in the simulated heart can be controlled in accordance with the received instruction, the operation according to the desired pulsation state of the operator can be reproduced in the simulated heart.

  In the simulated heart control method, it is conceivable to switch between pressurization and decompression of the space by controlling the open / close state of the open / close control member arranged on the path to the space in the simulated heart. In this case, it is possible to easily control the pressurization and decompression of the space simply by controlling the open / close state of the open / close control member arranged on the path connected to the space.

  For example, the open / close state of the open / close control member may be adjusted according to the pulsation state reproduced by the simulated heart. In this way, by adjusting the open / close state of the open / close control member in accordance with the reproduced pulsation state, it is possible to reproduce with the simulated heart an operation that approximates the actual pulsation state of the heart.

  Further, in the above simulated heart control method, a stretchable mesh body disposed around the space in the simulated heart regulates the expansion of the space at the time of pressurization and the space at the time of decompression. You may make it assist shrinkage | contraction. In this case, it is possible to prevent the simulated heart from aging over time by repeatedly expanding and contracting the space in the simulated heart.

  Further, in the simulated heart control method, adjustment of a reference value for releasing the air in the space to the outside during pressurization may be accepted. In this case, it is possible to adjust the reference value when air is discharged from the space in the simulated heart to the outside, and it is possible to adjust the capacity of the space when expanded to the maximum. As a result, it is possible to reproduce the motion according to the actual heart beat state with individual differences.

  The simulated heart control method according to the present invention is a simulated heart control method in which a first space corresponding to the atrium and a second space corresponding to the ventricle are formed. Determining a pressurizing / depressurizing cycle for switching between pressurization and depressurization of the second space, pressurizing the first space according to the pressurizing / depressurizing cycle, and depressurizing the first space according to the pressurizing / depressing cycle. A step, a step of pressurizing the second space in accordance with the pressurization / decompression cycle, a step of depressurizing the second space in accordance with the pressurization / decompression cycle, and a step of pressurizing the first and second spaces. And a step of releasing the air in the first and second spaces corresponding to the excess when the internal pressure in the first and second spaces exceeds a certain value.

  According to the above simulated heart control method, the first and second spaces in the simulated heart are pressurized and depressurized according to the determined pressure increase / decrease cycle, and the operation approximates the pulsation state of the actual heart. Can be reproduced. In particular, by preparing a large number of pressure increasing / decreasing periods for the first and second spaces in the simulated heart, it is possible to reproduce operations corresponding to various pulsation states with the simulated heart. In this case, when the internal pressures of the first and second spaces in the simulated heart exceed a certain value, the internal pressures of the first and second spaces are adjusted, so that operations corresponding to various pulsation states are performed. Since the volume of the first space and the second space when expanded to the maximum can be kept constant when reproducing with a simulated heart, the motion approximated by the actual pulsation state of the heart can be reproduced. Is possible.

  According to the present invention, the internal pressure of the space is adjusted when pressurizing and depressurizing the space in the simulated heart according to the determined pressurization cycle. It is possible to provide a method for controlling a simulated heart that can reproduce an action approximate to a state.

  Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings.

  FIG. 1 is a schematic diagram showing a simulated heart 1 used in a simulated heart device according to an embodiment of the present invention. Note that FIG. 1 shows a state in which a part of the space formed inside the simulated heart 1 is exposed. Further, in FIG. 1, parts attached to the simulated heart 1 are omitted.

  As shown in FIG. 1, four spaces A to D are formed inside the simulated heart 1. These spaces A to D correspond to the left and right atria and the left and right ventricles in the actual heart. Here, the space A and the space B correspond to the right atrium and the left atrium, respectively. In the present simulated heart 1, unlike an actual heart, the space A and the space B communicate with each other in the vicinity of the center of the space B. In the following, these space A and space B are referred to as the atrial part 2. On the other hand, the space C and the space D correspond to the right ventricle and the left ventricle, respectively. In the present simulated heart 1, unlike an actual heart, the space C and the space D communicate with each other near the center of the space C. Hereinafter, these spaces C and D will be referred to as the ventricular portion 3.

  The simulated heart 1 according to the present embodiment reproduces an operation that approximates the pulsating state of the actual heart by applying pressure and decompression to the atrial part 2 and the ventricular part 3. In particular, by controlling the pressurization and depressurization timings for the atrial part 2 and the ventricular part 3, the motions that approximate various heartbeat states are reproduced. In the following, for convenience of explanation, pressurization of air to the atrial part 2 and ventricular part 3 will be referred to as “inspiration” as appropriate, and decompression to the atrial part 2 and ventricular part 3 will be referred to as “exhaust” as appropriate. To do.

  An intake / exhaust port 4 is provided in the upper part of the atrial part 2, and an intake / exhaust port 5 is provided in the upper part of the ventricle part 3. Intake and exhaust to and from the atrium 2 and ventricle 3 are performed through the intake and exhaust ports 4 and 5, respectively. Inhalation and exhaust to the space B in the atrial part 2 are performed via the communication holes 6A formed in the inner walls of the space A and the space B. Intake and exhaust to and from the space C in the ventricle portion 3 are performed through communication holes 6B formed in the inner walls of the space C and the space D. The intake / exhaust port 4 and the intake / exhaust port 5 are provided with a backflow prevention sleeve which will be described later.

  When the simulated heart 1 according to the present embodiment is manufactured, a predetermined gel substance is dissolved in a hard urethane mold (hereinafter referred to as “urethane mold”) prepared in advance for manufacturing the simulated heart 1. Inject. Then, after defoaming the injected gel-like substance with a defoamer and cooling and stabilizing for a certain period of time, the gel-like substance is taken out from this urethane mold, so that the main body part of the simulated heart 1 shown in FIG. Manufactured. The simulated heart 1 used in the simulated heart device according to the present embodiment is completed by attaching a backflow prevention sleeve, which will be described later, to the main body of the simulated heart 1 manufactured in this way.

  More specifically, as the urethane mold, an outer mold for forming the outer shape of the main body of the simulated heart 1 and a middle mold for forming the atrial section 2 and the ventricular section 3 in the simulated heart 1 are prepared. . Then, the outer mold is assembled with the middle mold held at a fixed position. In addition, the predetermined gel-like substance described above is, for example, SEBS powder obtained by pulverizing powder made of thermoplastic elastomer (manufactured by Kraton Polymer Japan Co., Ltd .: Kraton (registered trademark) G: G1654X) into extremely fine particles. It is produced by adding a certain percentage of lubricating oil (Idemitsu Kosan Co., Ltd .: liquid paraffin, Daphne oil CP, 12N) and stirring for 8 hours. At this time, the ratio between the SEBS powder and the lubricating oil is set to a ratio of 1: 6.5. Such a predetermined gel-like substance is heated to 180 ° C. to dissolve and injected into the assembled outer mold. Then, after defoaming with a defoaming machine and cooling and stabilizing for 8 hours, the body part of the simulated heart 1 is taken out from the outer mold, and the middle mold is taken out from the body part, whereby the simulated heart 1 shown in FIG. The main body is manufactured. A backflow prevention sleeve, which will be described later, is attached to the main body of the simulated heart 1 manufactured in this way.

  In the present embodiment, since the gel substance constituting the surface portion of the simulated heart 1 is generated by adding lubricating oil to a powdery body composed of thermoplastic elastomer, the lubricating oil for the thermoplastic elastomer is added. By changing the ratio, the elasticity imparted to the simulated heart 1 can be changed. As a result, it is possible to give the simulated heart 1 a feeling that approximates the actual heart having individual differences.

  In consideration of the fact that fat is attached to the actual heart, it is preferable as an embodiment to form a portion corresponding to fat on the surface of the body portion of the simulated heart 1. In this case, a urethane mold (hereinafter referred to as “fat mold”) for forming a portion corresponding to fat in the main body of the simulated heart 1 is prepared separately. Then, the body portion of the simulated heart 1 before extracting the middle mold is attached to the fat mold, a predetermined gel-like substance is injected, and after curing for a certain period of time, it is removed. Thereafter, as described above, the simulated heart 1 in which a portion corresponding to fat is formed is completed by extracting the middle mold and attaching a backflow prevention sleeve described later.

  The predetermined gel-like substance in this case is, for example, SEBS powder obtained by pulverizing a powder composed of thermoplastic elastomer (Clayton Polymer Japan Co., Ltd .: Clayton (registered trademark) G: G1654X) into ultrafine particles, A certain ratio of lubricating oil (Idemitsu Kosan Co., Ltd .: liquid paraffin, Daphne oil CP, 12N) is mixed to form a gel. At this time, the ratio between the SEBS powder and the lubricating oil is set to a ratio of 1: 4.5. And it is produced | generated by adding 80% of a solvent to such a gel-like substance, coloring, and carrying out stable fusion for 24 hours. In addition, as a solvent added to a gel-like substance, toluene, a heptane, etc. are used, for example.

  When manufacturing the simulated heart 1, a net N formed of specific chemical fibers is disposed in the vicinity of the inner walls of the atrial part 2 and the ventricular part 3. Specifically, a net N as a mesh body is disposed so as to cover the inner walls of the atrial part 2 and the ventricular part 3. The net N is formed by weaving or knitting specific chemical fibers (for example, plain weave, jersey weave, and warp knitting). By forming the net N by weaving or knitting specific chemical fibers in this way, it is possible to impart stretchability to the net N.

  As the specific chemical fiber, for example, wooly nylon, polyester, rayon or the like is used. In each chemical fiber, for example, 8, 12, 16, 24, 40 and 70 deniers are used. The net N plays a role of restricting excessive expansion of the atrial part 2 and the ventricular part 3 during the inhaling operation and assisting the contraction of the atrial part 2 and the ventricular part 3 during the exhausting operation. As a result, it is possible to prevent the simulated heart from deteriorating over time by repeating expansion and contraction of the atrial part 2 and the ventricular part 3. In the present embodiment, the case where the net N is formed by twilling 40 denier woolly nylon will be described.

  FIG. 2 is a schematic diagram showing a simulated heart 1 according to the present embodiment. 2 shows a state in which a part of the space formed inside the simulated heart 1 is exposed as in FIG.

  As shown in FIG. 2, the intake / exhaust port 4 provided in the atrial part 2 and the intake / exhaust port 5 provided in the ventricular part 3 prevent backflow of air in the atrial part 2 and the ventricular part 3, respectively. A backflow prevention sleeve 7 and a backflow prevention sleeve 8 are attached. The backflow prevention sleeve 7 and the backflow prevention sleeve 8 ensure the hermeticity in the atrial part 2 and the ventricular part 3. The backflow prevention sleeve 7 holds an intake / exhaust tube 9 and an internal pressure adjusting tube 11. Similarly, the backflow prevention sleeve 8 holds the intake / exhaust tube 10 and the internal pressure adjusting tube 12. The backflow prevention sleeve 7 and the backflow prevention sleeve 8 function as a holding member. In this way, the backflow prevention sleeve 7 and the backflow prevention sleeve 8 hold the intake / exhaust tube 9 and the internal pressure adjustment tube 11 and also have a function of sealing the atrial portion 2 and the ventricular portion 3. The number of parts in 1 can be reduced, and the manufacturing cost can be reduced.

  FIG. 3 is a front view and a bottom view for explaining the configuration of the backflow prevention sleeve 7. Since the backflow prevention sleeve 8 has the same configuration as the backflow prevention sleeve 7, the description thereof is omitted.

  The backflow prevention sleeve 7 is formed of, for example, the same predetermined gel-like substance as the main body portion of the simulated heart 1. As shown in FIG. 3, the backflow prevention sleeve 7 includes a cylindrical portion 7a and a flange portion 7b provided at the lower end portion of the cylindrical portion 7a. The cylindrical portion 7 a holds the intake / exhaust tube 9 and the internal pressure adjusting tube 11 inserted into the backflow prevention sleeve 7. A regulating portion 7c that regulates the positions of one end of the intake / exhaust tube 9 and the internal pressure adjusting tube 11 disposed in the atrial portion 2 is provided on the lower surface portion of the cylindrical portion 7a. The flange portion 7b has a shape that protrudes to the side of the cylindrical portion 7a. The backflow prevention sleeve 7 is prevented from falling off the simulated heart 1 in a state where it is attached to the intake / exhaust port 4.

  As shown in FIG. 2, the intake / exhaust tube 9 passes through the backflow prevention sleeve 7. A connecting portion 9 a that can be connected to a switching valve, which will be described later, is attached to the upper end portion of the intake / exhaust tube 9 protruding from above the backflow prevention sleeve 7. On the other hand, a sealing plug 9b is attached to the lower end portion of the intake / exhaust tube 9 arranged in the atrial portion 2. As for the intake / exhaust tube 10, similarly to the intake / exhaust tube 9, a connecting portion 10 a is attached to the upper end portion, and a sealing plug 10 b is attached to the lower end portion.

  FIG. 4A is an enlarged view for explaining the configuration in the vicinity of the lower end portion of the intake / exhaust tube 9. Since the intake / exhaust tube 10 has the same configuration as the intake / exhaust tube 9, the description thereof is omitted.

  As shown in FIG. 4A, the sealing plug 9b is attached to the intake / exhaust tube 9 so as to seal the lower end portion of the intake / exhaust tube 9, and sucks and exhausts air from the lower end portion of the intake / exhaust tube 9. It is preventing. A plurality of vent holes 9 c are formed in the vicinity of the lower end portion of the intake / exhaust tube 9 and on the side surface (circumferential surface) of the intake / exhaust tube 9. Intake and exhaust by the intake / exhaust tube 9 is performed through the vent hole 9c. Thus, by performing intake and exhaust through the vent hole 9c formed in the side surface (circumferential surface) of the intake / exhaust tube 9, the atrial portion 2 can be evenly expanded and contracted.

  In the ventricle portion 3, the lower end portion of the intake / exhaust tube 10 is disposed in the space C via the communication hole 6B. The vent hole 10 c is formed in both the portion disposed in the space D and the portion disposed in the space C in the side surface (circumferential surface) portion of the intake / exhaust tube 10. By forming the vent hole 10c in this manner, the ventricle portion 3 can be expanded and contracted equally, as with the atrial portion 2.

  Further, as shown in FIG. 2, the internal pressure adjusting tube 11 passes through the backflow prevention sleeve 7. An internal pressure adjusting valve 11a, which will be described later, is attached to the upper end portion of the internal pressure adjusting tube 11 protruding from above the backflow prevention sleeve 7. On the other hand, an opening plug 11 c is attached to the lower end portion of the internal pressure adjusting tube 11 disposed in the atrial portion 2. As for the internal pressure adjusting tube 12, similarly to the internal pressure adjusting tube 11, an internal pressure adjusting valve 12 a is attached to the upper end portion, and an opening plug 12 c is attached to the lower end portion.

  Here, the internal pressure adjusting valve 11a will be described. When the internal pressure in the atrial part 2 exceeds a certain value, the internal pressure adjusting valve 11a is configured to release air corresponding to the excess to the outside. Thereby, the upper limit value of the internal pressure in the atrial part 2 can be kept constant. The internal pressure adjustment valve 11a is provided with an adjustment knob 11b. The operator is configured to adjust the upper limit value of the internal pressure in the atrial part 2 by operating this adjustment knob. The internal pressure adjusting valve 12a also plays a role of maintaining the upper limit value of the internal pressure in the ventricular portion 3 constant, like the internal pressure adjusting valve 11a.

  FIG. 4B is an enlarged view for explaining the configuration in the vicinity of the lower end portion of the internal pressure adjusting tube 11. Since the internal pressure adjusting tube 12 has the same configuration as the internal pressure adjusting tube 11, the description thereof is omitted.

  As shown in FIG. 4 (b), the opening plug 11 c is attached to the lower end so as to secure the airway of the internal pressure adjusting tube 11. A vent hole 11d is formed in a side surface (circumferential surface) portion of the internal pressure adjusting tube 11 at a position in the vicinity of the opening plug 11c. Release of the air in the atrial part 2 by the internal pressure adjusting tube 11 is performed through the opening plug 11c and the vent hole 11d.

  FIG. 5 is a block diagram for explaining the configuration of the simulated heart device 100 according to the present embodiment.

  As shown in FIG. 5, the simulated heart apparatus 100 includes a pressurizing apparatus A101 that pressurizes the atrial part 2 in the simulated heart 1, a pressurizing apparatus B102 that pressurizes the ventricular part 3, and the atrial part 2 and the ventricular part 3. A decompression device 103 that decompresses, a pressurization tank 104 that is used when pressurizing the ventricle 3, and a decompression tank 105 that is used when decompressing the atrium 2 and the ventricle 3 are provided. For example, the pressurization device A101 and the pressurization device B102 are configured by a compressor or the like, and the decompression device 103 is configured by an oil rotary vacuum pump or the like. In the present embodiment, pressurization by the pressurization device A101 and the pressurization device B102 corresponds to an intake operation in the simulated heart 1, and decompression by the decompression device 103 corresponds to an exhaust operation in the simulated heart 1. is there.

  In the simulated heart device 100 according to the present embodiment, the pressurization tank 104 is not connected to the pressurization device A101, and the pressurization tank 104 is connected only to the pressurization device B102. This is because the difference in capacity between the atrial part 2 and the ventricular part 3 in the simulated heart 1 is taken into consideration. In other words, considering that the ventricular part 3 has a larger capacity than the atrial part 2, the pressurizing tank 104 is connected only to the pressurizing device B102. The decompression device 103 and the decompression tank 105 are shared by the atrial part 2 and the ventricular part 3. Thus, by sharing the decompression device 103 and the decompression tank 105, it is possible to reduce the number of parts constituting the simulated heart device 1.

  Further, the simulated heart device 100 includes a pressure increase / decrease switching unit 106 to which the connection portion 9a of the intake / exhaust tube 9 is connected, a pressure increase / decrease switching unit 107 to which the connection portion 10a of the intake / exhaust tube 10 is connected, and a pressurizing device. An adjustment unit 108 disposed in a tube connecting A101 and the pressure increase / decrease switching unit 106, an adjustment unit 109 disposed in a tube connecting the pressure reduction tank 105 and the pressure increase / decrease switching unit 106, and a pressure reduction tank 105, an adjustment unit 110 disposed in a tube connecting the pressure increase / decrease switching unit 107, an adjustment unit 111 disposed in a tube connecting the pressurization tank 104 and the pressure increase / decrease switching unit 107, and an addition thereof. The pressure reduction switching unit 106, the pressure increase / decrease switching unit 107, the control unit 112 that controls the open / close state of the adjustment units 108 to 111, and the operation unit 113 that receives an operation input from the operator are provided. That.

  In addition to the connecting portion 9 a, a tube connected to the pressurizing apparatus A 101 and a tube connected to the pressure reducing tank 105 are connected to the pressure increasing / decreasing switching portion 106. Under the control of the control unit 112, the pressure increase / decrease switching unit 106 switches the connection destination between the pressurizing apparatus A 101 and the pressure reducing tank 105. Thereby, in cooperation with the adjustment unit 108 and the adjustment unit 109, the intake and exhaust of the atrium 2 are switched.

  In addition to the connecting portion 10 a, a tube connected to the pressurizing tank 104 and a tube connected to the depressurizing tank 105 are connected to the pressure increasing / decreasing switching portion 107. Under the control of the control unit 112, the pressure increase / decrease switching unit 107 switches the connection destination between the pressurization tank 104 and the depressurization tank 105. Thereby, in cooperation with the adjustment part 110 and the adjustment part 111, the intake and exhaust with respect to the ventricle part 3 are switched.

  The adjusting unit 108 adjusts the open / closed state of the tube connecting the pressurizing apparatus A101 and the pressurizing / depressurizing switching unit 106 under the control of the control unit 112. When adjusted to the open state, if the pressurization / decompression switching unit 106 sets the connection destination to the pressurization apparatus A101, the atrial unit 2 is pressurized. On the other hand, the adjustment unit 109 adjusts the open / closed state of the tube connecting the depressurization tank 105 and the pressure increase / decrease switching unit 106 under the control of the control unit 112. When adjusted to the open state, if the pressurization / decompression switching unit 106 sets the connection destination to the depressurization tank 105, the atrial unit 2 will be depressurized.

  Similarly, the adjustment unit 110 adjusts the open / close state of the tube connecting the decompression tank 105 and the pressure increase / decrease switching unit 107 under the control of the control unit 112. When adjusted to the open state, if the pressure increase / decrease switching unit 107 sets the connection destination to the pressure reducing tank 105, the ventricular portion 3 is adjusted to be depressurized. On the other hand, the adjustment unit 111 adjusts the open / close state of the tube connecting the pressurization tank 104 and the pressure increase / decrease switching unit 107 under the control of the control unit 112. In the case of being adjusted to the open state, if the pressurization switching unit 107 sets the connection destination to the pressurizing tank 104, the ventricular unit 3 is pressurized.

  For example, as shown in FIG. 5, the control unit 112 includes a CPU and a ROM and a RAM connected to the CPU. The CPU performs overall control of the simulated heart device 100, more specifically, all control necessary for operating the simulated heart 1. Various programs executed by the CPU when operating the simulated heart 1 are written in the ROM. The RAM functions as a work area when the CPU executes a program on the ROM. For example, in the ROM, a program for reproducing operations according to various pulsation states and operations according to symptoms such as arrhythmia and atrial fibrillation by the simulated heart 1 is written.

  The operation unit 113 is connected to the control unit 112 and receives an instruction input from the operator to the simulated heart device 100. For example, an instruction input for specifying the operation of the simulated heart 1 as described above is received. That is, the operator can specify the operation of the simulated heart 1 via the operation unit 113.

  Next, the control when operating the simulated heart 1 in the simulated heart device 100 according to the present embodiment will be described. FIG. 6 is a timing chart showing an example of control when operating the simulated heart 1 in the simulated heart device 100 according to the present embodiment. For convenience of explanation, FIG. 6 shows a case where the simulated heart 1 reproduces an operation corresponding to a pulsation state (25 heartbeats per minute) slower than the normal pulsation state.

  In FIG. 6, control from the time point when the inhalation operation on the atrial portion 2 is started will be described. In the initial state, all of the adjustment units 108 to 111 are adjusted to the closed state. Furthermore, it is assumed that the pressurizing device A101, the pressurizing device B102, and the decompression device 103 are always driven while the simulated heart device 100 is operating. As a result, while the simulated heart device 100 is in operation, the pressurizing tank 104 is always pressurized to a certain value, and the decompression tank 105 is always decompressed to a certain value. .

  In the case of reproducing an action corresponding to a specific pulsation state with the simulated heart 1, the control unit 112 first switches a cycle (increase) between pressurization (inspiratory motion) and decompression (exhaust motion) for the atrial portion 2 and the ventricular portion 3. The decompression cycle is determined. In the control unit 112, the CPU selects the program written in the ROM to determine the pressure increase / decrease cycle. In this case, when the pulsation state to be reproduced is specified from the operation unit 113, the control unit 112 determines the pressure increase / decrease cycle by selecting a program corresponding to the pulsation state. FIG. 6 shows a case where the pressurization / decompression period is determined to be 2400 ms.

  When reproducing the motion corresponding to the pulsation state shown in FIG. 6 with the simulated heart 1, the control unit 112 first adjusts the adjustment unit 108 to the open state and connects the connection destination of the pressure increase / decrease switching unit 106 to the pressurizing device. Set to A101. As a result, the air from the pressurizing apparatus A101 flows into the atrial portion 2 through the intake / exhaust tube 9. That is, the inhalation operation for the atrial part 2 is started. When the operation according to the pulsation state shown in FIG. 6 is reproduced by the simulated heart 1, the control unit 112 continues this inspiration operation for 400 ms. While such an inhalation operation is being performed, the atrial portion 2 gradually expands.

  When the internal pressure in the atrial part 2 is increased to a predetermined value or more during the inhalation operation to the atrial part 2 in this way, the air in the atrial part 2 is adjusted to the internal pressure via the internal pressure adjusting tube 11. Released from the valve 11a. For this reason, the atrial part 2 does not expand beyond a certain level. Further, since the internal pressure adjusting valve 11a does not perform the air release operation until the internal pressure in the atrial portion 2 becomes equal to or higher than a certain value, the intake pressure operation on the atrial portion 2 is not hindered.

  When 400 ms elapses from the start of the inhalation operation for the atrial part 2, the control unit 112 adjusts the adjustment unit 108 to the closed state, adjusts the adjustment unit 109 to the open state, and connects the pressure increase / decrease switching unit 106. The tip is switched to the decompression tank 105. Since the decompression tank 105 is decompressed and the atrium 2 is in a higher pressure state than the decompression tank 105, the air in the atrium 2 flows into the decompression tank 105. That is, the exhaust operation for the atrial portion 2 is started. When the operation according to the pulsation state shown in FIG. 6 is reproduced by the simulated heart 1, the control unit 112 continues this exhausting operation for 600 ms. While the exhausting operation is being performed, the atrial portion 2 gradually contracts.

  As described above, when 1000 ms elapses from the start of the inhalation operation with respect to the atrium 2, the control unit 112 adjusts the adjustment unit 109 to the closed state. Thereby, the atrial part 2 transfers to the stop state which stops both intake operation | movement and exhaust operation | movement. When reproducing the motion corresponding to the pulsation state shown in FIG. 6 with the simulated heart 1, the control unit 112 continues this stop state for 1400 ms. At the end of this stop state, the cycle of one heartbeat operation in the atrial portion 2 (AA interval: Atrium-Atrium interval shown in FIG. 6) ends. And the control part 112 transfers to intake operation again. Specifically, when 1400 ms elapses from the start of the stop state, the adjustment unit 108 is adjusted to an open state, and the connection destination of the pressure increase / decrease switching unit 106 is switched to the pressurizing device A101 to start the intake operation ( 2400 ms shown in FIG. Furthermore, when 400 ms elapses from the start of the intake operation, the adjustment unit 108 is adjusted to the closed state, the adjustment unit 109 is adjusted to the open state, and the connection destination of the pressure increase / decrease switching unit 106 is switched to the pressure reduction tank 105. Thus, the exhaust operation is started (2800 ms shown in FIG. 6).

  On the other hand, when 200 ms elapses from the start of the inhalation operation for the atrial part 2, the control part 112 adjusts the adjustment part 111 to the open state and sets the connection destination of the pressure increase / decrease switching part 107 to the pressurization tank 104. Since the pressurization tank 104 is pressurized and the ventricle part 3 is in a lower pressure state than the pressurization tank 104, the air in the pressurization tank 104 flows into the ventricle part 3. That is, the inhalation operation with respect to the ventricle 3 is started. When the operation according to the pulsation state shown in FIG. 6 is reproduced by the simulated heart 1, the control unit 112 continues this inspiration operation for 600 ms. While such an inhalation operation is performed, the ventricular portion 3 gradually expands.

  When the internal pressure in the ventricular part 3 is increased to a predetermined value or more during the inhalation operation to the ventricular part 3 in this way, the air in the ventricular part 3 is adjusted to the internal pressure via the internal pressure adjusting tube 12. Released from the valve 12a. For this reason, the ventricle part 3 does not expand beyond a certain level. Further, since the internal pressure adjusting valve 12a does not perform the air discharging operation until the internal pressure in the ventricular portion 3 becomes a predetermined value or higher, the inspiratory operation with respect to the ventricular portion 3 is not hindered.

  When 600 ms elapses from the start of the inspiratory operation with respect to the ventricular unit 3, the control unit 112 adjusts the adjustment unit 111 to the closed state, adjusts the adjustment unit 110 to the open state, and connects the pressure increase / decrease switching unit 107. The tip is switched to the decompression tank 105. Since the decompression tank 105 is decompressed and the ventricle part 3 is in a higher pressure state than the decompression tank 105, the air in the ventricle part 3 flows into the decompression tank 105. That is, the exhausting operation for the ventricular portion 3 is started. When the operation according to the pulsation state shown in FIG. 6 is reproduced by the simulated heart 1, the control unit 112 continues this exhaust operation for 1200 ms. While such an exhausting operation is performed, the ventricular portion 3 gradually contracts.

  Thus, when 1800 ms elapses from the start of the inspiratory operation with respect to the ventricular portion 3, the control unit 112 adjusts the adjustment unit 110 to the closed state. As a result, the ventricular portion 3 shifts to a stop state in which both the intake operation and the exhaust operation are stopped. When reproducing the motion corresponding to the pulsation state shown in FIG. 6 with the simulated heart 1, the control unit 112 continues this stop state for 600 ms. When this stop state is finished, the cycle of one heartbeat operation in the ventricular portion 3 (VV interval: Ventricular-Ventricular interval shown in FIG. 6) ends. And the control part 112 transfers to intake operation again. Specifically, when 600 ms elapses from the start of the stop state, the adjustment unit 111 is adjusted to an open state, and the connection destination of the pressure increase / decrease switching unit 107 is switched to the pressurization tank 104 to start the intake operation ( (2600 ms shown in FIG. 6). Furthermore, when 600 ms elapses from the start of the intake operation, the adjustment unit 111 is adjusted to the closed state, the adjustment unit 110 is adjusted to the open state, and the connection destination of the pressure increase / decrease switching unit 107 is switched to the pressure reduction tank 105. Thus, the exhaust operation is started (3200 ms shown in FIG. 6).

  When the operation of the simulated heart 1 is controlled in this way, as shown in FIG. 6, after the inspiratory operation on the atrial portion 2 is started, the inspiratory operation on the ventricular portion 3 is started with a delay of 200 ms. In addition, after the exhaust operation for the atrial portion 2 is started, the exhaust operation for the ventricle portion 3 is started with a delay of 400 ms. Thereafter, the intake operation and the exhaust operation for the atrium 2 and the ventricle 3 are repeated at the same cycle. In response to this, expansion and contraction of the atrial part 2 and the ventricular part 3 are repeated. As a result, the simulated heart 1 reproduces an operation that approximates the actual heartbeat state.

  FIG. 6 shows a case where the simulated heart 1 reproduces an action corresponding to a pulsation state slower than a normal pulsation state. However, the simulated heart device 100 according to the present embodiment is not limited to this, and the simulated heart 1 can reproduce an operation according to an arbitrary pulsation state. FIG. 6 shows a case where the inspiratory operation for the ventricular portion 3 is started after a delay time of 200 ms from the inspiratory operation for the atrial portion 2, but such a delay time can also be set arbitrarily. .

  As described above, according to the simulated heart device 100 according to the present embodiment, the control unit 112 controls the pressurization and decompression on the atrial part 2 and the ventricular part 3, thereby approximating the actual pulsating state of the heart. Can be reproduced with the simulated heart 1. In particular, by preparing a large number of pressurization and decompression patterns for the atrial part 2 and the ventricular part 3, it is possible to reproduce operations corresponding to various pulsation states with the simulated heart 1. In this case, when the internal pressures of the atrial part 2 and the ventricular part 3 exceed a certain value, the internal pressures of the atrial part 2 and the ventricular part 3 are adjusted by the internal pressure adjusting valve 11a and the like, so that various pulsation states are supported. When reproducing the motion with the simulated heart 1, the volume of the atrium 2 and the ventricle 3 when expanded to the maximum can be kept constant, so that the motion more closely approximates the actual heartbeat state. It can be reproduced.

  In particular, according to the simulated heart device 100 according to the present embodiment, as described above, the simulated heart 1 performs an operation that approximates the pulsating state of the actual heart. It can be used as a teaching material. In this way, when using the simulated heart 1 as a teaching material, it is possible to reproduce the motion of the heart according to various heart rates and the motion of the heart according to symptoms such as arrhythmia and atrial fibrillation. It is possible to visually grasp the motion of the heart that can be seen only at the time of actual clinical surgery.

  Further, since the simulated heart 1 performs an operation that approximates the pulsating state of the actual heart, it can be used for training of surgical techniques such as vascular anastomosis. In this way, when used for training of surgical techniques, it is possible to train surgical techniques for the heart in various pulsation states and surgical techniques for the heart with symptoms such as arrhythmia and atrial fibrillation. Surgical techniques that can only be learned through clinical surgery can be experienced at the preparatory stage of clinical surgery.

  For example, when performing surgical technique training related to vascular anastomosis, a portion corresponding to a blood vessel may be integrally formed when the simulated heart 1 is manufactured. However, in consideration of the fact that the annular artery in the actual heart is formed on the surface of the heart and there are individual differences in the position, thickness, hardness, etc., artificially manufactured blood vessels (artificial blood vessels) are simulated It is preferable to adhere to the surface of the heart 1. As the artificial blood vessel bonded to the simulated heart 1 according to the present embodiment, for example, an artificial blood vessel formed of the same material as the main body of the simulated heart 1 is preferably employed. As such an artificial blood vessel, the artificial blood vessel of Japanese Patent Application No. 2005-156006 proposed by the present applicant can be considered. When adhering such an artificial blood vessel, the characteristics of the artificial blood vessel itself (for example, thickness, hardness, etc.) can be changed as appropriate, so by using it together with the simulated heart 1 according to the present embodiment, It becomes possible to perform more practical surgical technique training.

  In the simulated heart device 100 according to the present embodiment, the atrial part 2 (space A and space B) corresponding to the atrium and the ventricular part 3 (space C and space corresponding to the ventricle) are provided inside the simulated heart 1. D), and the volume of the ventricular part 3 is larger than that of the atrial part 2. As a result, the simulated heart 1 can reproduce an action approximated by an actual heart having a larger ventricular volume than the atrium.

  Further, in the simulated heart device 100 according to the present embodiment, the atrial portion 2 is divided into a space A corresponding to the left atrium and a space B corresponding to the right atrium, and the space A and the space B are connected to the communication hole 6A. Communicating via Further, the ventricular portion 3 is divided into a space C corresponding to the left ventricle and a space D corresponding to the right ventricle, and the space C and the space D are communicated via the communication hole 6B. As a result, the simulated heart 1 can reproduce the motion approximated to the actual heart having the left and right atria and the left and right ventricles.

  In the simulated heart device 100 according to the present embodiment, an instruction for specifying the pulsation state reproduced by the simulated heart 1 is received via the operation unit 113. As a result, the control unit 112 can control the operation in the simulated heart 1 in accordance with the instruction received by the operation unit 113, so that the operation according to the desired pulsation state of the operator is reproduced in the simulated heart 1. It becomes possible.

  Moreover, in the simulated heart apparatus 100 according to the present embodiment, the control unit 112 controls the open / close state of the pressurization / decompression switching unit 106, the pressurization / decompression switching unit 107, and the adjustment units 108 to 111, thereby controlling the atrial unit 2 and the ventricle. Since the pressurization and depressurization of the unit 3 are controlled, it can be easily approximated to the actual heart pulsation state simply by controlling the open / close state of the pressurization / decompression switching unit 106, the pressurization / decompression switching unit 107, and the adjusting units 108-111. It is possible to reproduce the operation performed by the simulated heart 1.

  Furthermore, in the simulated heart device 100 according to the present embodiment, the adjustment knob 11b is provided in the internal pressure adjustment valve 11a to accept an operator's adjustment instruction. Thereby, the reference value at the time of releasing air to the outside from the atrial part 2 and the ventricular part 3 can be adjusted, and the capacity of the atrial part 2 and the ventricular part 3 when it is expanded to the maximum can be adjusted. It becomes possible. As a result, it is possible to reproduce with the simulated heart 1 an action according to the actual heart beat state having individual differences.

  In addition, this invention is not limited to the said embodiment, It can change and implement variously. In the above-described embodiment, the size, shape, and the like illustrated in the accompanying drawings are not limited to this, and can be appropriately changed within a range in which the effect of the present invention is exhibited. In addition, various modifications can be made without departing from the scope of the object of the present invention.

  For example, in the above embodiment, the four spaces A to D are formed in the simulated heart 1, the pressurizing device A 101, the pressurizing device B 102 and the decompressing device 103, and the pressurizing tank 104 and the decompressing tank 105. It shows about the case where the pressurization and pressure reduction with respect to space AD are performed using. However, the number of spaces formed in the simulated heart 1 and the number of pressurization devices, pressurization tanks and decompression devices, and decompression tanks for pressurizing and depressurizing these spaces can be appropriately changed. . For example, four independent spaces may be formed in the simulated heart 1, and a pressurizing device, a pressurizing tank, a decompressing device, and a decompressing tank dedicated to each space may be prepared. However, it is preferable as an embodiment to determine the number of spaces in the simulated heart 1 and the number of pressurization devices and decompression devices from the viewpoint of miniaturization and weight reduction of the device body.

  In the above embodiment, between the pressurizing device A101 and the pressure increase / decrease switching unit 106, between the pressure reducing tank 105 and the pressure increasing / decreasing switch unit 106, and between the pressure reducing tank 105 and the pressure increasing / decreasing switch unit 107. In addition, a case where an adjustment unit 108, an adjustment unit 109, an adjustment unit 110, and an adjustment unit 111 are disposed between the pressurization tank 104 and the pressure increase / decrease switching unit 107 is shown. However, between the pressurizing device A101 and the pressurization / decompression switching unit 106, between the depressurization tank 105 and the pressurization / decompression switching unit 106, between the depressurization tank 105 and the pressurization / decompression switching unit 107, and between the pressurization tank 104 and the pressurization tank 104. The configuration with the decompression switching unit 107 is not limited to these, and can be changed as appropriate. As long as the intake and exhaust of the atrium 2 and the ventricle 3 can be controlled as in the above embodiment, any configuration may be used.

  The present invention is a method for controlling a simulated heart in which spaces corresponding to the atrium and the ventricle are formed, and determines a pressurization / decompression cycle for switching between pressurization and decompression of the space, and the above-mentioned according to the pressurization / decompression cycle When the space is pressurized and depressurized, and the pressure in the space is increased, if the internal pressure of the space exceeds a certain value, the air in the space corresponding to the excess is released to the outside to actually beat the heart The operation approximates the state, and has industrial applicability.

It is a schematic diagram which shows the simulation heart applied to the control method of the simulation heart which concerns on one embodiment of this invention. It is a schematic diagram which shows the simulated heart which concerns on the said embodiment. It is the front view and bottom view for demonstrating the structure of the backflow prevention sleeve attached to the simulation heart which concerns on the said embodiment. (A) is an enlarged view for demonstrating the structure of the lower end part vicinity of the intake / exhaust tube attached to the simulated heart which concerns on the said embodiment, (b) is the internal pressure attached to the simulated heart which concerns on the said embodiment. It is an enlarged view for demonstrating the structure of the lower end part vicinity of an adjustment tube. It is a block diagram for demonstrating the structure of the simulation heart apparatus which concerns on the said embodiment. FIG. 6 is a timing chart showing an example of control when operating the simulated heart in the simulated heart device according to the embodiment.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 Simulated heart 2 Atrial part 3 Ventricular part 4, 5 Intake / exhaust port 6A, 6B Communication hole 7, 8 Backflow prevention sleeve 9, 10 Intake / exhaust tube 9a, 10a Connecting part 9b, 10b Seal plugs 9c, 10c Vent holes 11, 12 Internal pressure adjusting tubes 11a, 12a Internal pressure adjusting valves 11b, 12b Adjusting knobs 11c, 12c Opening plug 100 Simulated heart device 101 Pressurizing device A
102 Pressurizer B
103 Depressurization Device 104 Pressurizing Tank 105 Depressurizing Tank 106, 107 Pressurization / Decompression Switching Unit 108, 109, 110, 111 Adjustment Unit 112 Control Unit 113 Operation Unit

Claims (7)

  A method for controlling a simulated heart having a space corresponding to an atrium and a ventricle formed therein, the step of determining a pressurization / decompression period for switching between pressurization and decompression of the space, and the space according to the pressurization / decompression period A step of pressurizing, a step of depressurizing the space according to the pressurization cycle, and an air in the space corresponding to the excess when the internal pressure of the space exceeds a certain value when pressurizing the space A method for controlling the simulated heart, comprising the step of:   The method for controlling a simulated heart according to claim 1, further comprising a step of receiving an instruction for specifying a pulsation state reproduced by the simulated heart, and determining the pressurization / decompression period according to the instruction.   3. The simulated heart control method according to claim 1, wherein pressurization and depressurization of the space are switched by controlling an open / close state of an open / close control member arranged on the path to the space.   4. The simulated heart control method according to claim 3, wherein the open / close state of the open / close control member is adjusted according to a pulsation state reproduced by the simulated heart.   The stretchable mesh body disposed around the space restricts expansion of the space during pressurization and assists the shrinkage of the space during decompression. Item 5. The simulated heart control method according to any one of Items 4 to 5.   6. The simulated heart control method according to claim 1, wherein adjustment of a reference value for releasing air in the space to the outside during pressurization is received.   A method for controlling a simulated heart, in which a first space corresponding to an atrium and a second space corresponding to a ventricle are formed in the interior, the pressure increasing / decreasing pressure switching between pressurizing and depressurizing the first and second spaces A step of determining a cycle, a step of pressurizing the first space in accordance with the pressurization / decompression cycle, a step of decompressing the first space in accordance with the pressurization / decompression cycle, and in accordance with the pressurization / decompression cycle A step of pressurizing the second space, a step of depressurizing the second space in accordance with the pressurization cycle, and the first and second spaces when pressurizing the first and second spaces. And a step of discharging the air in the first and second spaces corresponding to the excess when the internal pressure of the gas exceeds a certain value to the outside.

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