JP2008020654A - Blood vessel motion simulator - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a blood vessel motion simulator capable of simulating, with comparatively simple configuration, behavior of a blood vessel resulting from biomechanical load, and useful for durability evaluation of a stent, objective evaluation of anastomotic technique and the like taking the behavior into account. <P>SOLUTION: The blood vessel motion simulator 10 is constituted of: an elastic simulated blood vessel 31 in which a liquid is filled; a first and a second supporting members 32 and 33 for supporting both end portions of the simulated blood vessel 31 in the extending direction and for operating both of the end portions so as to approach/move away from each other; and a linear motor 14 for operating the first and the second supporting members 32 and 33. The blood vessel motion simulator 10 extends and contracts the simulated blood vessel 31 in the extending direction by making both of the end portions approach/move away from each other by driving the linear motor 14. <P>COPYRIGHT: (C)2008,JPO&INPIT

Description

  The present invention relates to a vascular motion simulator, and more specifically, can simulate the behavior of a blood vessel caused by biomechanical load, and evaluates a durability test of a stent in consideration of the behavior and a technique evaluation during blood vessel anastomosis training. The present invention relates to a vascular motion simulator that can be used in the field.

  As a medical instrument used for treatment of a blood vessel stenosis, a metal net-like cylinder called a stent is known. Since this stent is placed in the stenosis site in the blood vessel for a long time and continuously expands the stenosis site, the stent is placed in the blood vessel when performing the durability test of the stent. Is important to consider. However, such a durability test cannot be actually performed by the human body, and must be performed by a mechanical device that simulates the characteristics of the human body.

  By the way, as an apparatus for evaluating the performance of a stent, a stent performance evaluation simulator disclosed in Patent Document 1 and a stent mechanical property measuring apparatus disclosed in Patent Document 2 are known.

  The stent performance evaluation simulator of Patent Document 1 has a circuit configuration that simulates coronary circulation, a closed-loop liquid channel, a pump that applies a pulsatile flow to the liquid circulating in the liquid channel, and a fluid A branch pipe branching in the middle of the flow path and a flexible tube provided in the middle of the branch pipe are provided. A stent to be evaluated is placed in the flexible tube, and the stent is exposed to a liquid to which pulsatile flow is applied. Therefore, with this simulator, it is possible to examine the durability of the stent under conditions close to blood pulsation conditions during actual use.

On the other hand, the stent mechanical property measuring apparatus of Patent Document 2 directly evaluates the performance of a stent from a mechanical viewpoint by directly pulling one end of the stent and deriving a correlation between a load acting on the stent and a pulling length. It is a device to do.
JP 2000-342692 A JP 2005-278828 A

  By the way, when a stent is placed in the superficial femoral artery (SFA), which is a blood vessel that passes through the femoral muscle canal of the human body, the superficial femoral artery is a blood vessel having a dynamic element, and therefore, the movement of the blood vessel is larger than in other parts. Thus, a large load is easily applied to the stent placed in the blood vessel. Therefore, when a stent is placed in the superficial femoral artery, damage over time is more likely to occur compared to other sites. Specifically, the superficial femoral artery is subjected to biomechanical loads such as bending, twisting, compression and tension due to external forces and blood pressure fluctuations due to leg movements, etc., and the use environment of the stent more than other blood vessel sites Becomes worse. Therefore, when evaluating the durability of the stent, it is necessary to include the case where the stent is placed in the superficial femoral artery having a different usage environment from other sites.

  However, in the stent performance evaluation simulator and the stent mechanical property measurement apparatus, as described above, it is not possible to simulate the blood vessel behavior due to the biomechanical load peculiar to the superficial femoral artery. When the stent is placed in the femoral artery, the durability of the stent cannot be accurately evaluated.

  In addition, coronary stents placed in coronary arteries have been reported to be damaged when placed in patients, and development of a system that can predict durability in an environment simulating biomechanical loads is required. ing.

  By the way, when a doctor or medical student performs anastomosis technique training by anastomosing an artificial blood vessel for training that has already been sold, the postoperative state of the actual patient is compared with the obtained artificial blood vessel after anastomosis. There is no device that can reproduce the same behavioral state. Therefore, it is not possible to confirm the state of the anastomosis site over time while giving the behavior due to biomechanical load to the artificial blood vessel obtained by the anastomosis technique training, and the objective of the anastomosis technique considering the behavior of the blood vessel Evaluation cannot be performed.

  The present invention has been devised by paying attention to such a problem, and its purpose is to simulate the behavior of a blood vessel caused by a biomechanical load with a relatively simple configuration. It is an object of the present invention to provide a vascular motion simulator useful for evaluating the durability of a stent in consideration of the above and objective evaluation of an anastomosis technique.

(1) In order to achieve the above object, the present invention supports a simulated blood vessel filled with a liquid and both end portions in the extending direction of the simulated blood vessel, and operates so that the both end portions can be separated and approached. Support means, and drive means for operating the support means,
The simulated blood vessel is made of an elastic body extending in a substantially linear shape,
By driving the driving means, the both end portions are separated and approached to expand and contract the simulated blood vessel in its extending direction.

  (2) Further, it is preferable to adopt a configuration in which temperature control means for controlling the temperature around the simulated blood vessel to a predetermined temperature is further provided.

  (3) Further, it is possible to adopt a configuration further including a fluid pressure adjusting means for adjusting the fluid pressure in the simulated blood vessel.

  (4) Moreover, the said support means is good to support the said simulated blood vessel so that attachment or detachment is possible.

  (5) Furthermore, the support means may be provided so as to support a plurality of simulated blood vessels, and the operation may be performed simultaneously on the simulated blood vessels.

  (6) Moreover, it is good to employ | adopt the structure that the stent is arrange | positioned inside the said simulated blood vessel and the restraint part which restrict | limits the deformation | transformation of the said stent is provided in the inner surface side of this stent.

  (7) Furthermore, it is preferable to further include a gas concentration adjusting means for adjusting the gas concentration around the simulated blood vessel.

  In the claims and the specification, the “simulated blood vessel” is used as a concept including an animal blood vessel in addition to a blood vessel artificially created using a predetermined artificial material and / or biological material. .

  According to the configuration of the above (1), it is possible to simulate the expansion / contraction operation of the behavior of the blood vessel caused by the biomechanical load applied to the blood vessel in which the stent such as the peripheral artery such as the superficial femoral artery or the coronary artery is placed. . Furthermore, since the simulated blood vessel expands and contracts in the extending direction while the simulated blood vessel is filled with liquid while both end portions of the simulated blood vessel are spaced apart from each other, the hydraulic pressure in the simulated blood vessel is And the pulsation state similar to that in the actual blood vessel can be created in the simulated blood vessel. Therefore, in order to generate the pulsation state, it is not necessary to adopt a circulation circuit configuration simulating a living body, and the blood pressure fluctuation in the blood vessel and the accompanying expansion / contraction displacement in the radial direction of the blood vessel are simulated with a simple device configuration. can do. In general, according to the present invention, the behavior of a blood vessel due to a biomechanical load can be simulated with a simple configuration, and the durability evaluation of the stent and the objective evaluation of the anastomosis technique considering the behavior are performed in a short time. It becomes possible.

  With the configuration (2), the temperature around the simulated blood vessel can be maintained at about the body temperature, the test can be performed in almost the same state as the living body, and the durability test of the shape memory alloy stent is performed. It is useful in such cases.

  With the configuration (3), the mean pressure and pulse pressure in the simulated blood vessel can be freely adjusted, and the pressure state according to the disease state and the target blood vessel site can be simulated.

  With the configuration of (4), it is possible to selectively support the simulated blood vessel having various diameters, lengths, and shapes on the support means, and evaluate the durability of the stent in consideration of the target blood vessel region and individual differences. And objective evaluation of anastomosis techniques.

  With the configuration (5), it is possible to simultaneously test different types of evaluation objects such as stents, and the durability and the like of each evaluation object can be compared and evaluated in a short time. In addition, it becomes possible to simultaneously perform a comparative test under the same conditions on the evaluation objects that have undergone different anastomosis procedures.

  With the configuration (6), when the stent is placed in an actual blood vessel, it is possible to create a state where the stent is restrained by the intima of the blood vessel, and the durability of the stent in a state closer to the in vivo environment. Evaluation can be made.

  According to the configuration of (7), when a simulated blood vessel made of silicone or the like is used, gas exchange is performed between the inside and outside of the simulated blood vessel. Therefore, by adjusting the gas concentration outside the simulated blood vessel, By changing the pH, the pH of the liquid in the simulated blood vessel can be adjusted. Thereby, for example, when the liquid in the simulated blood vessel is changed to strongly acidic or strongly alkaline with respect to the evaluation object such as a stent accommodated in the simulated blood vessel, the corrosion state of the evaluation object over time, etc. Can be investigated.

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

  FIG. 1 shows a schematic front view of a blood vessel motion simulator according to the present embodiment, and FIG. 2 shows a schematic plan view of the blood vessel motion simulator. In these drawings, the vascular motion simulator 10 simulates a tension / compression operation in the axial direction of the superficial femoral artery, that is, an expansion / contraction operation and an expansion / contraction operation in the vascular diameter direction accompanying blood pressure fluctuations in the superficial femoral artery. This device can be used mainly for durability evaluation of the stent S placed in the superficial femoral artery.

  The blood vessel motion simulator 10 includes a box-shaped case 11, a simulation unit 12 provided inside the case 11, a linear motor 14 provided outside the case 11 and serving as a driving unit for operating the simulation unit 12, The temperature sensor 17 and the heater 18 provided inside the case 11, and the heater control device 19 provided outside the case 11 and controlling the operation of the heater 18 based on the measured value of the temperature sensor 17. ing.

  The case 11 has a substantially rectangular base 21 as an installation surface, a peripheral wall 22 that rises along the periphery of the base 21, and a space that is disposed on the upper end side of the peripheral wall 22 and is surrounded by the peripheral wall 22. And a top wall 23 that closes from above.

  The simulation unit 12 is connected to the drive plate 26 fixed to the tip of the shaft 25 of the linear motor 14 and extending in the vertical direction in FIG. , And first and second lines 28 and 29 provided toward the right in FIG.

  The first and second lines 28 and 29 are arranged so as to be substantially symmetric in the vertical direction in FIG. 2, and have substantially the same configuration except for the direction of the arrangement. Therefore, for the second line 29 located on the upper side in FIG. 2, the same reference numerals are used for the same or equivalent components as the first line 28 located on the lower side in the figure, and the description is omitted or simplified. To do.

  The first line 28 is fixed to the drive plate 26 and the first holding member 32 that holds the left end portion of the simulated blood vessel 31 in FIG. And a second holding member 33 that holds the right end portion of the simulated blood vessel 31 in FIG. 1, and supports the second holding member 33, and is substantially L-shaped in a side view arranged upright with respect to the base 21. The upright plate 35 is provided.

  A stent S to be evaluated is accommodated inside the simulated blood vessel 31. The simulated blood vessel 31 is not particularly limited, but is formed of an elastic body made of silicone, latex, or the like having elasticity similar to that of a human blood vessel. As shown in FIG. It is provided in a shape extending substantially linearly in the direction. Further, as the simulated blood vessel 31, an animal blood vessel chemically treated with glutaraldehyde or the like may be used.

  The first holding member 32 is provided in a stepped columnar shape. As shown in FIG. 3, the first holding member 32 has a large-diameter base 38 attached to the drive plate 26 and a right end center in the figure. Consecutive small-diameter side projections 39 are formed. The protrusion 39 is set to have an outer diameter that is the same or smaller than the inner diameter of the simulated blood vessel 31 and is fitted into the simulated blood vessel 31 from one end side (left end side in FIG. 3) of the simulated blood vessel 31 in the extending direction. It can be put in. In the state where the projection 39 is fitted in the simulated blood vessel 31, the left end portion of the simulated blood vessel 31 in the drawing is clamped from the outside so that the simulated blood vessel 31 does not fall off from the first holding member 32. It can be tightened with. At this time, the inflow of air from the open portion of the simulated blood vessel 31 on the left end side in the figure is blocked.

  The second holding member 33 includes a cylindrical base 43 fixed to the upright plate 35, a cylindrical protrusion 44 that extends to the left in FIG. The injection path 49 and the pressure sensor 50 are embedded inward from the inside.

  The base 43 is provided with a hole 52 that is open on the left end side in FIG. 3, and the inlet of the injection path 49 and the measurement part of the pressure sensor 50 are arranged on the inner peripheral surface of the hole 52. ing.

  The protrusion 44 is set to have an outer diameter that is the same or smaller than the inner diameter of the simulated blood vessel 31, and enters the simulated blood vessel 31 from the other end side in the extending direction of the simulated blood vessel 31 (right end side in FIG. 3). It can be inserted. Even in a state in which the projection 44 is fitted in the simulated blood vessel 31, the simulated blood vessel 31 is clamped by the drop-off preventing clamp member 54, as in the left part of FIG. Further, the protrusion 44 is open at the left end side in FIG. 3 and is connected to the hole 52 of the base portion 43 at the right end side. For this reason, in a state where the simulated blood vessel 31 is attached to the first and second holding members 32 and 33, the internal space of the simulated blood vessel 31, the internal space of the protrusion 44 in the second holding member 33, and the hole 52. Will be connected to each other. In this state, the open portion of the simulated blood vessel 31 on the left end side in FIG. 3 is closed by the protrusion 39, and the injection passage 49 connected to the hole 52 is always filled with liquid. It has become. For this reason, the liquid filled in each internal space of the simulated blood vessel 31 and the protrusion 44 and the hole 52 is in a non-atmospheric state, so long as the simulated blood vessel 31 is not removed from the first and second holding members 32 and 33. Therefore, the blood does not flow out of the simulated blood vessel 31.

  The injection path 49 is provided so that a liquid having the same quality as blood can be injected into the hole 52 by a pump or a syringe (not shown). Therefore, in a state in which the simulated blood vessel 31 is attached to the first and second holding members 32 and 33, the liquid injected into the hole 52 passes through the internal space of the protrusion 44 connected to the hole 52 and simulates it. The blood vessel 31 is filled. In this state, the inside of the simulated blood vessel 31 is not in contact with the atmosphere, and is simulated as an intravascular environment in which no air exists.

  The liquid filled in the simulated blood vessel 31 is not particularly limited, but phosphate buffer solution (PBS) or serum from animals or the like is used. By using the phosphate buffer solution, the stent S can be accommodated in the simulated blood vessel 31 in an environment close to the pH environment in the living body, and corrosion of the metal stent S with time is prevented. In addition, as long as there is no problem in the durability test of the stent S, it can be replaced with another liquid.

  The pressure sensor 50 is provided so as to be able to measure the liquid pressure of the liquid filled in the simulated blood vessel 31, and the amount of liquid injected from the injection path 49 is adjusted by the measured value of the liquid pressure. The adjustment here may be performed manually by the operator by visually checking the measured value of the hydraulic pressure, or by injecting the liquid from the injection path 49 via a predetermined hydraulic pressure control device (not shown). The amount may be controlled automatically. In the latter case, the injection path 49, the pressure sensor 50, and the fluid pressure control device constitute fluid pressure adjusting means for adjusting fluid pressure in the simulated blood vessel 31. Note that a stopper (not shown) is provided at the attachment portion of the pressure sensor 50, and by opening the stopper, air can be vented when the liquid is injected into the simulated blood vessel 31.

    The linear motor 14 is not particularly limited, and a voice coil motor is employed. The motor 14 drives the shaft 25 so as to repeatedly move in the left-right direction in FIG. 1 at a predetermined timing. Accordingly, the first holding member 32 supported by the drive plate 26 connected to the shaft 25 repeatedly operates in the left-right direction (arrow direction) in FIG. On the other hand, since the second holding member 33 is supported by the upright plate 35 fixedly arranged, the first holding member 32 is connected to the second holding member 33 connected via the simulated blood vessel 31. On the other hand, it operates so as to repeatedly separate and approach in the left-right direction in FIG. Accordingly, the first and second holding members 32 and 33 constitute support means that operate so as to allow the simulated blood vessel 31 to be separated and approachable at both ends in the extending direction of the simulated blood vessel 31 and detachably support the simulated blood vessel 31.

  The heater control device 19 controls the operation of the heater 18 so as to keep the temperature in the case 11 including the simulated blood vessel 31 at about the human body temperature (37 ° C.) based on the measurement value of the temperature sensor 17. Accordingly, the temperature sensor 17, the heater 18, and the heater control device 19 constitute a temperature control unit that controls the temperature around the simulated blood vessel 31 to a predetermined temperature. By providing this temperature control means, the test can be performed in the same state as the temperature environment in the body, which is useful when a stent S made of a shape memory alloy or the like whose properties change due to temperature changes is an evaluation target. In the case where only the stent S that does not significantly affect the temperature change is evaluated, the temperature control means can be omitted.

  Next, the flow of durability evaluation of the stent S using the blood vessel motion simulator 10 will be described.

  First, the stent S to be evaluated is inserted into the simulated blood vessel 31, and both end portions in the extending direction of the simulated blood vessel 31 are attached to the first and second holding members 32 and 33 to obtain the state shown in FIG. In this state, liquid is injected into the hole 52 from the injection path 49, and the simulated blood vessel 31 is filled with the liquid while the air is drawn from the stopper (not shown) of the attachment portion of the pressure sensor 50, and a desired state is obtained. Then, the liquid injection from the injection path 49 is stopped. Next, the linear motor 14 is driven at a predetermined frequency, and the first holding member 32 is repeatedly separated and approached in the left-right direction in FIG. 1 with respect to the second holding member 33. Here, when the first holding member 32 moves in the direction approaching the second holding member 33, the linear separation distance between the first and second holding members 32, 33 decreases, and accordingly, The connected simulated blood vessel 31 is elastically deformed in a compressing direction along the axis. And conversely, when the first holding member 32 moves in the direction away from the second holding member 33, the linear separation distance between the first and second holding members 32, 33 increases, and accordingly, The simulated blood vessel 31 is elastically deformed in a pulling direction along the axis. These series of operations are repeatedly performed, that is, the first and second holding members 32 and 33 are repeatedly separated and approached so that the expansion / contraction operation in the extending direction of the simulated blood vessel 31 is repeatedly performed. At this time, the outer diameter of the simulated blood vessel 31 also expands and contracts due to its elasticity.

  Along with the expansion and contraction operation of the simulated blood vessel 31, the volume inside the simulated blood vessel 31 changes, and accordingly, the internal fluid pressure fluctuates. For this reason, a pulse pressure is generated in the liquid in the simulated blood vessel 31 by repeatedly performing the expansion and contraction operation. According to the experiments by the present inventors, when the simulated blood vessel 31 made of silicone having an inner diameter of 6 mm is used and the stroke of the linear motor 14 is 6.5 mm and driven at a frequency of 40 Hz, the length of the simulated blood vessel 31 is natural. The expansion and contraction operation is repeatedly performed in a range extending about 6.5 mm from the length, and a pulse pressure with a pressure difference of 20 to 30 mmHg can be generated in accordance with the drive frequency of the linear motor 14.

  After being left for a predetermined time in the above state, the driving of the linear motor 14 is stopped, and the stent S is taken out from the simulated blood vessel 31. In addition to observing the damaged state of the surface of the stent S using a microscope (not shown), the metal component that has flowed into the solution by using the stent S over time is measured. The durability of the stent S is quantitatively evaluated, such as by performing a qualitative analysis of elements.

  Therefore, according to such an embodiment, with a very simple configuration, the durability test of the stent S placed in the superficial femoral artery can be performed in a state close to that when actually placed in the living body. In particular, as the simulated blood vessel 31 expands and contracts, a pulse pressure can be generated in the simulated blood vessel 31, and the pulse pressure is taken into account without adopting a large-scale circulation circuit configuration that simulates the blood circulation state of the living body. It is possible to simulate the blood vessel behavior.

  Further, according to the embodiment, a repeated load due to expansion and contraction and blood pressure fluctuation can be applied to the simulated blood vessel 31 in a high-speed cycle, and the durability evaluation of the stent S can be performed in a short time. This has been proved by experiments of the present inventors. Specifically, when the frequency condition of the linear motor 14 is set to 40 Hz, the fatigue state when left in a living body for one year is performed for 10 days. Can do.

  Furthermore, since the first and second holding members 32 and 33 can detachably support the simulated blood vessel 31, the durability test of the stent S can be performed by replacing the simulated blood vessel 31 with various shapes. Specifically, the simulated blood vessel 31 having a different shape or the simulated blood vessel 31 having a different diameter and length, such as a linear simulated blood vessel 31 having substantially the same inner diameter or a tapered simulated blood vessel 31 that is not so, is used as a blood vessel. The operation simulator 10 can be set arbitrarily. Therefore, although the diameter, length, and shape of the blood vessel vary among individuals, the durability test of the stent S considering such individual variation can be easily performed by replacing the simulated blood vessel 31. Further, in this embodiment, the behavior of the blood vessel in consideration of the biomechanical load in the superficial femoral artery is simulated, but other than the peripheral blood vessel, coronary artery blood vessel, aortic blood vessel, etc. It is possible to easily cope with the durability test for these parts. The protrusions 39 and 44 are detachable, and the protrusions 39 and 44 having an outer diameter that is almost the same as the inner diameter of the simulated blood vessel 31 to be fitted can be selectively replaced, thereby allowing various shapes. Even when the simulated blood vessel 31 is replaced, liquid leakage from the fitting portion of the simulated blood vessel 31 can be more effectively prevented.

  The simulation unit 12 includes the first and second lines 28 and 29. However, the present invention is not limited to this, and the line configuration may be 1 or 3 or more. If a plurality of line configurations are used as in the present embodiment, for example, different types of stents S having different materials and performances can be tested simultaneously, and comparative evaluation of these stents S can be performed efficiently.

  Further, before setting the simulated blood vessel 31 to the first and second holding members 32 and 33, a liquid resin made of silicone, latex, or the like on the inner surface side of the stent S inserted into the simulated blood vessel 31 or A restraint portion that restricts deformation of the stent S may be formed by pouring a liquid obtained by mixing powdered sodium or calcium into the liquid resin, adhering it to the inner surface of the stent S, and allowing the liquid to stand and solidify. For example, when liquid silicone is used, as shown in FIG. 4, a silicone layer 74 is formed as the restraining portion. The reason is as follows. That is, the stent S placed in an actual blood vessel is covered with the intima of the blood vessel in about one month and becomes a kind of restraint state. For this reason, it is considered that the influence of the biomechanical load on the stent S also changes due to the restraint of the stent S. Therefore, the durability test of the stent S can be performed in consideration of the actual restraint state of the stent S by forming the restraint portion and placing the stent S in the restraint state. In addition, the thickness of the silicone layer 74 can illustrate about 1/2 of the thickness of the simulated blood vessel 31.

  Furthermore, in the said embodiment, although the structure which made the 1st holding member 32 space apart from the 2nd holding member 33 was illustrated and demonstrated, this invention is not limited to this, The 2nd holding member 33 is 1st. A structure in which the holding member 32 is spaced apart or a structure in which the holding members 32 and 33 are independently operated to be separated from each other may be employed. In short, the first and second holding members 32, 33 are separated and approached, and the biomechanical load can be applied to the simulated blood vessel 31 by changing the separation distance between both ends in the extending direction of the simulated blood vessel 31. Any structure is acceptable.

  Further, it is preferable to provide an outer diameter measuring means capable of measuring the outer diameter change during the operation of the simulated blood vessel 31. As this outer diameter measuring means, a laser displacement sensor (not shown) can be exemplified. In this case, a laser light emitting part and a light receiving part are provided at lateral positions sandwiching the simulated blood vessel 31 so that the laser light crosses the simulated blood vessel 31. Be placed.

  Furthermore, a load cell capable of measuring the tensile force of the simulated blood vessel 31 may be arranged on the second holding member 33 side, and the load acting on the stent S may be obtained by the expansion and contraction of the simulated blood vessel 31.

  Although not shown, it is preferable to further include a gas concentration adjusting means for adjusting the gas concentration around the simulated blood vessel 31. As the gas concentration adjusting means, a gas supply device such as a gas cylinder is provided outside the case 11, and the gas supply device supplies a predetermined gas such as carbon dioxide or oxygen from the gas supply device to the case 11. A configuration for changing the gas concentration can be exemplified. Accordingly, gas exchange is performed between the inside and outside of the simulated blood vessel 31 made of silicone or the like, and the concentration of the gas in the liquid in the simulated blood vessel 31 is changed, so that the pH of the liquid can be adjusted. Therefore, for example, the temporal corrosion state of the stent S can be investigated by changing the liquid in the simulated blood vessel 31 to strong acidity or strong alkalinity. Note that the gas supplied into the case 11 is discharged to the outside of the case 11 through a slight gap provided in the case 11.

  Furthermore, the blood vessel motion simulator 10 can be used for other applications for evaluating the performance of the stent S described above. For example, by using an artificial blood vessel that has been anastomosed by an anastomosis technique training by a doctor or medical student as the simulated blood vessel 31 set in the simulation unit 12, the anastomotic site is made to behave in a state similar to the actual postoperative state. Evaluation becomes possible over time.

  The blood vessel motion simulator 10 can also be used as a device for accommodating a biodegradable absorbable polymer or acellular tissue in a simulated blood vessel 31, and culturing predetermined cells in an accelerated environment using these.

  In addition, the configuration of each part of the apparatus in the present invention is not limited to the illustrated configuration example, and various modifications are possible as long as substantially the same operation is achieved.

1 is a schematic front view of a blood vessel motion simulator according to the present embodiment. FIG. 2 is a schematic plan view of the blood vessel motion simulator. The principal part expanded sectional view which follows the AA line of FIG. The schematic sectional drawing of the simulated blood vessel which concerns on a modification.

Explanation of symbols

10 Blood vessel motion simulator 14 Linear motor (drive means)
17 Temperature sensor (temperature control means)
18 Heater (temperature control means)
19 Heater control device (temperature control means)
31 Simulated blood vessel 32 First holding member (supporting means)
33 Second holding member (supporting means)
49 Injection path (hydraulic pressure adjusting means)
50 Pressure sensor (hydraulic pressure adjusting means)
74 Silicone layer (restraint part)

Claims (7)

A simulated blood vessel filled with liquid, supporting means for supporting both ends of the simulated blood vessel in the extending direction, and operating the both end parts so as to be separated and approachable, and driving means for operating the supporting means Prepared,
The simulated blood vessel is made of an elastic body extending in a substantially linear shape,
A blood vessel motion simulator characterized in that the simulated blood vessel is expanded and contracted in the extending direction when the both end portions are separated and approached by the driving means.   2. The blood vessel motion simulator according to claim 1, further comprising temperature control means for controlling a temperature around the simulated blood vessel to a predetermined temperature.   The blood vessel operation simulator according to claim 1 or 2, further comprising a fluid pressure adjusting means for adjusting fluid pressure in the simulated blood vessel.   4. The blood vessel operation simulator according to claim 1, wherein the support means removably supports the simulated blood vessel.   The vascular motion simulator according to any one of claims 1 to 4, wherein the support means is provided so as to support a plurality of simulated blood vessels, and simultaneously performs the operation on the simulated blood vessels.   The stent is disposed inside the simulated blood vessel, and a restraining portion that restricts deformation of the stent is provided on the inner surface side of the stent. Blood vessel motion simulator.   The blood vessel operation simulator according to claim 1, further comprising a gas concentration adjusting unit that adjusts a gas concentration around the simulated blood vessel.

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