JPH04200565A - Medical means - Google Patents

Abstract

PURPOSE:To obtain the treating means for in vivo disposition which is simple in constitution, and makes sure operation by surely heating a desired point with a simple heating operation by providing a stimulus applying means for starting the exothermic effect for causing the phase transition from a liquid phase to a solid phase on the heat accumulating material provided on the main body of the medical means. CONSTITUTION:This biospacing path expanding means is formed by providing a bag-shaped member 7 packed with the heat accumulating material 8 on the inner side of an outer layer part 5 consisting of a shape memory resin of a stent 4 and mounting the member on a balloon 2 and, therefore, the pressure by injecting liquid and expanding the balloon 2 is added to the material 8 in the bag-shaped member 7. The material 8 causes the phase change from the liquid phase to the solid phase by the change in this pressure and generates heat by releasing the latent heat at the time of this phase change. The temp. of the outer layer part 5 consisting of the shape memory resin raises in this way and the outer layer part 5 softens. The generation of the heat in the inner layer part 6 stops when the phase transition from the liquid phase to the solid phase of the material 8 ends completely. The stent 4 attains the same temp. as the bodily temp. The outer layer part 5 consisting of the shape memory resin is cooled and is cured to maintain the shape of the larger diameter thereof. Consequently, the operation is simplified and the electrical danger is eliminated. The safe means is thus obtd.

Description

[Detailed Description of the Invention] [Field of Industrial Application] The present invention relates to a biological duct dilator for dilating a constricted part of a biological duct such as a narrowed blood vessel, esophagus, bile duct, urethra, or ureter. , medical capsules for administering drugs in body cavities such as the gastrointestinal tract of living organisms, absorbing and collecting body fluids, and indwelling devices such as vascular embolization devices that occlude venous skin during bypass surgery for femoral artery embolization; Regarding medical devices such as endoscopes.

[Prior Art] Japanese Unexamined Patent Publication No. 1-178252 discloses a dilator for dilating a stenosis occurring in a biological duct. This expansion device has a heater made of nichrome wire as a means for heating the expansion device main body.

As another example of a treatment instrument that is inserted and left in a living body, a medical capsule known from Japanese Patent Application Laid-Open No. 163309/1987 has a coil spring made of a shape memory alloy in the capsule body. When the capsule reaches the target site in the body, ultrasonic waves are transmitted from outside the body, and the ultrasonic waves heat a coil spring made of shape memory alloy, releasing the drug from the mouth of the capsule body and collecting body fluids. It is.

[Problems to be Solved by the Invention] However, in the method disclosed in the above-mentioned Japanese Unexamined Patent Application Publication No. 1-178252, the method uses a heater made of nichrome wire to heat the biological conduit dilator. ,
Electrical members such as lead wires must be inserted into the living body. Therefore, there was a problem in terms of electrical safety.

On the other hand, in the medical capsule known from Japanese Patent Application Laid-Open No. 57-163309, the heat generated by ultrasonic vibration is applied to a coil spring made of a shape memory alloy, so the heat generation efficiency is quite low. The coil springs tended to not heat up quickly and sufficiently to ensure drug release and body fluid collection.

In addition, as an indwelling treatment device inserted into a living body, a body duct dilator main body made of shape memory resin is placed on a balloon dilator, like the biological duct dilator shown in an unpublished application (Japanese Patent Application No. 1-157149). An indwelling procedure in which the balloon of the balloon dilator is fitted, warm water is perfused into the balloon of the balloon dilator, the dilator body is softened and expanded to dilate the stenotic region, and then cold water is perfused to maintain the dilator body in an expanded state. Some tools have been suggested.

However, with this biological duct dilator, in order to perfuse hot and cold water inside the balloon, the No. 1 rune dilator must be a multi-lumen type balloon dilator that has a water injection pipe and a drainage pipe. Instead, the outer diameter of the balloon dilator becomes thicker. Furthermore, since a large-scale perfusion device and hot water production device must be prepared outside the body, the preparation and operation thereof are complicated.

The present invention has been made with attention to the above-mentioned problems, and has a simple configuration and is capable of reliably heating a target area with a simple heating operation to perform a reliable operation in vivo. The purpose is to provide medical equipment for treatment.

[Means and Functions for Solving the Problems] In order to solve the above problems, the present invention provides a medical device which is inserted into a living body to perform a medical treatment and which performs a desired action through a heating operation. A heat storage material is provided which stores latent heat in a supercooled state and releases latent heat during a phase transition from a liquid phase to a solid phase due to an external stimulus to generate heat for the heating operation. A stimulus providing means is provided for initiating an exothermic action that causes a phase transition from a solid phase to a solid phase.

In the medical device having the configuration as described in 2, heat generation of the heating heat storage material of the medical device inserted into the living body can be started by the stimulus providing means. Therefore, it is possible to simplify the configuration, improve the ease of operation, improve safety, and further improve the reliability of operation.

[Example] A first example will be described with reference to FIGS. 1 to 6. This embodiment relates to a biological duct dilator, and FIG. 1 shows the entire biological duct dilator.

This biological channel dilator consists of a balloon dilator 1 and a stent 4. The balloon dilator 1 includes a balloon 2 made of an elastic material and a catheter 3 for supplying fluid. A stent 4 as shown in FIG. 2 is fitted onto the outer periphery of the balloon 2.

The material of the stent 4 is in the form of a sheet, which is wound into a cylindrical shape. Also,
The stent 4 has a two-layer structure including an outer layer 5 and an inner layer 6, and the outer layer 5 is made of shape memory resin. The memorized shape of the outer layer portion 5 made of the shape memory resin is set so that it recovers to a large diameter shape as shown in FIG. 5 at a predetermined temperature or higher. Examples of the shape memory resin material include polynorbornene, trans-1,4-polyisobrene, styrene-butadiene copolymer, and polyurethane. Above a predetermined shape recovery temperature, the material is in a so-called rubber state and recovers its shape while softening, and below the shape recovery temperature it is in a plastic state and hardens. Note that the temperature for the shape recovery is set between 40 and 60°C.

On the other hand, the inner layer 6 is fixed to the inner surface of the outer layer 5 by adhesive or the like, as shown in FIG. 3, in order to heat the cylindrical body made of the shape memory resin above a predetermined temperature. The inner layer portion 6 is composed of a bag-like member 7 made of an elastic film such as silicone or urethane, and a heat storage material 8 filled inside the bag-like member 7. As the heat storage material 8, for example, sodium acetate 3, which is an inorganic hydrated salt, is provided by NOK Corporation.
A latent heat storage material such as a hydrate is used. This heat storage material 8 is in a liquid state (supercooled state) even at temperatures below the freezing point.
However, if the supercooled state is broken by applying a stimulus such as a sudden pressure change, high voltage application, or ultrasonic vibration, the phase changes from a liquid to a solid phase, and latent heat is released during the phase change ( fever)
do.

Next, the operation when using this biological channel dilator will be explained.

First, as a preparation, the balloon 2 is deflated as shown in FIG. Place in the wind and soften by heating. This soft stent 4 is wrapped around the outer peripheral surface of the deflated balloon 2. When heating is stopped in this state and the material is cooled to below the shape recovery temperature, it becomes a relatively hard plastic having the shape shown in FIG. 3 and is fixed to the outer periphery of the balloon 2.

When this preparation is completed, the biological duct dilator is introduced into the biological duct 9 such as the blood vessel, esophagus, bile duct, pancreatic duct, urethra, ureter, etc. shown in FIG. 4 through a channel of an endoscope (not shown). do. Then, as shown in Fig. 4, a stent 4 is attached to the outer periphery.
The part of the balloon 2 equipped with the
position within.

Next, the catheter 3 is inserted from outside the body using a syringe (not shown)
A fluid such as water or air is injected into the inside of the balloon 2 through the balloon 2. By injecting the fluid in this way, the balloon 2 is expanded as shown in FIG. 5, and pressure is applied to the inner layer 6 of the stent 4. This pressure is transmitted via the bag-like member 7 to the heat storage material 8 provided therein. The heat storage material 8 undergoes a phase change from a liquid phase to a solid phase due to this pressure change, and during the phase change, latent heat is released and heat is generated. This causes the temperature of the outer layer 5 made of shape memory resin to rise, and the outer layer 5 to soften. At the same time, due to the inflation pressure of the balloon 2, it begins to recover to its memorized shape with a large diameter, as shown in FIG.

Then, due to the expansion action of the balloon 2 and the action of the inner layer 5 of the stent 4 made of shape memory resin to restore the expanded shape, the stenotic part 10 is compressed in the expanding direction and is sufficiently expanded. Thus, the balloon 2 serves not only as a means for expanding the stent 4, but also as a means for stimulating the heat storage material 8 of the stent 4 to initiate a heat generating action that causes the phase transition from a liquid phase to a solid phase.

Moreover, when all the heat storage materials 8 have completed phase transition from liquid phase to solid phase,
The inner layer 6 stops generating heat, and the stent 4 becomes at the same temperature as the body temperature. As a result, the outer layer portion 5 made of shape memory resin is cooled and hardened to maintain this large diameter shape.

After this, the balloon 2 is deflated as shown in FIG.

However, the outer layer 5 and inner layer 6 of the stent 4 remain in their expanded state and are therefore placed in the stenosis 10. In this way, only balloon 2 is deflated.

Then, the catheter 3 is removed together with the balloon 2. Thereby, only the stent 4 in the expanded state can be placed in the stenotic part 10 of the biological duct 9, and the stenotic part 10 can be maintained in the expanded state.

The biological conduit dilator constructed in this way has a bag-like member 7 filled with a heat storage material 8 inside the outer layer 5 made of shape memory resin of the stent 4 and is mounted on the balloon 2. By simply applying pressure to the heat storage material 8 in the bag-like member 7 by injecting fluid into the balloon 2 and inflating the balloon 2, it becomes possible to heat the outer layer 5 made of shape memory resin. There is no need to use a large diameter balloon dilator for hot water perfusion.

In addition, there is no need to provide a large-scale perfusion device or hot water production device outside the body, which simplifies the operation.

Furthermore, since there is no need to heat the stent with a nichrome wire as in the past, electrical hazards are eliminated and the stent is safe.

A second embodiment of the present invention, which also relates to a biological channel dilator, will be described with reference to FIGS. 7 to 10.

FIG. 7 shows the balloon dilator 1 in this second embodiment. This balloon dilator 1 has a plurality of rigid projections 3 for applying pressure to the heat storage material 8 of the stent 4 on the outer peripheral surface of a balloon 2 made of an elastic material, similar to that shown in the first embodiment. It is.

As shown in FIG. 8, the stent 4 is formed into a substantially cylindrical shape from shape memory resin as in the first embodiment, and has upper, lower, left, and right inner circumferential surfaces that are located above the outer circumference of the nobulator 2. Four parts 14 are provided to correspond to the rigid protrusions 13. Each of the recesses 14 is provided with a bag-like member 7 filled with a heat storage material 8 similar to that of the first embodiment, and is fixed to the inner surface of the recess 14 by adhesive or the like.

The stent 4 is then fitted onto the balloon dilator 1 as shown in FIG. 8.

The biological conduit dilator configured in this manner is introduced into the constricted portion 10 of the biological conduit 9 through the channel of the endoscope, etc. in the same manner as in the first embodiment, and the balloon 2 portion is It is located in the narrowed part 10.

Next, when fluid is injected into the nolator 2 from outside the living body using a syringe or the like (not shown), the balloon 2
expands, and the rigid protrusion 13 on its outer periphery presses the heat storage material 8 provided inside through the bag-like member 7.

The heat storage material 8 stimulated by this pressure change undergoes a phase change from a liquid phase to a solid phase, and during this phase change, radiates latent heat and generates heat. As a result, the temperature of the stent 4 made of shape memory resin increases, softens it, and begins to recover its memorized shape with a large diameter as shown in FIG. Then, the stenotic region 10 is compressed and sufficiently expanded by the expansion action of the balloon 2 and the action of the stent 4 to restore the expanded shape. Then, as in the first embodiment described above, when the phase transition of the heat storage material 8 is completed, the heat generation stops and the stent 4 is cooled by body temperature and held in the expanded shape.

Then, when the balloon 2 is deflated and removed, only the stent 4 and the stenotic part 10 are left in the state shown in FIG.
It will be placed in place while maintaining its expanded shape.

As in the case of the first embodiment, the second embodiment also provides improved operability and electrical safety compared to the conventional type. Furthermore, in this second embodiment,
Since the rigid protrusions 13 are provided compared to those of the first embodiment, it is easier to apply pressure to the heat storage material 8, and it is possible to reliably stimulate it and generate heat.

What is shown in FIGS. 11 and 12 is a third embodiment of the present invention, and it is related to a biological channel dilator as in the case of the above-mentioned embodiments. That is, as in the first embodiment, a cylindrical stent 4 is fitted onto the outer periphery of the balloon 2 of this balloon dilator 1. As in the first embodiment, the stent 4 is composed of an outer layer 5 made of shape memory resin and an inner layer 6 made of a bag-like member 7 containing a heat storage material 8 therein.

In addition, in vitro, ultrasonic waves are used as a stimulus providing means for changing the phase of the heat storage material 8 filled in the bag-like member 7 of the inner layer 6 and generating heat to warm the outer layer 5 made of the shape memory resin. A generator 16 is provided. This ultrasonic generator 16 includes a transmission signal generator 17, an amplifier 18, an ultrasonic signal generator 19, and a pouch 20 for contacting the living body skin tissue 15.

In the biological conduit dilator constructed in this manner, the balloon 2 is introduced into the constricted portion 10 of the biological conduit 9 through the channel of the endoscope, etc., as in the first embodiment.

Next, a fluid such as air or water is injected into the balloon 2 using a syringe or the like (not shown).

Then, as described in the first embodiment, pressure is applied to the heat storage material 8 of the inner layer 6 of the stent 4. - On the other hand, at the same time as the fluid is injected into the balloon 2, the ultrasonic generator 16 provided outside the body is driven. That is, the transmission signal generator 1
The transmitted signal is amplified by an amplifier 18 and reaches an ultrasonic signal generator 19. Ultrasonic vibrations are generated from the ultrasonic signal generator 19, and the ultrasonic vibrations reach the stent 4 inserted into the stenosis 10 in the living body via the pouch 20 that is brought into close contact with the skin tissue 15 of the living body.

Due to the pressure change due to the expansion of the balloon 2 and the ultrasonic vibration, the heat storage material 8 in the bag-like member 7 in the inner layer 6 of the stent 4 is stimulated and undergoes a phase change from a liquid phase to a solid phase. Sometimes I get a fever. This heat causes the first and second
As in the case of the embodiment, the outer layer portion 5 made of shape memory resin
As the temperature rises, the material softens and begins to recover its memorized shape with a large diameter, as shown in FIG. And the narrowing part 10
is compressed and sufficiently expanded by the expansion action of the balloon 2 and the action of the stent 4 to restore its expanded shape.

Then, when the phase transition of the heat storage material 8 is completed, the heat generation stops.
Body temperature cools the stent 4 and holds it in the expanded configuration. Then, when balloon 2 is deflated and removed, the 12th
As shown in the figure, only the stent 4 is placed in the stenotic region 10 while maintaining its expanded shape.

Therefore, as in the first embodiment, it is possible to achieve improved operability and improved electrical safety compared to the conventional type. Furthermore, compared to the first and second embodiments, both the pressure change due to the expansion of the balloon 2 and the stimulation effect of ultrasonic vibration are applied to the heat storage material 8, so that heat can be generated more reliably.

What is shown in FIGS. 13 and 14 is a biological duct dilator showing a fourth embodiment of the present invention.

As shown in FIG. 13, the material of the stent 4 of this fourth embodiment includes an outer layer 5 made of a shape memory alloy such as a Ni-Ti alloy, Cu-Zn-A, or a Q alloy; and an inner layer section 6 for heating the alloy.

The stent 4 is then formed by winding the material into a flex shape as shown in FIG. In addition, the stent 4 having the outer layer portion 5 made of shape memory alloy has a small diameter in a low temperature state as shown in FIGS. 15 and 16, or has a small diameter in a high temperature state.
That is, it is set to expand to a thicker diameter as shown in FIG. 17 above the transformation temperature. Its transformation temperature is 40 to 60°C. Further, the inner layer part 6 of the stent 4 is provided with stimulation providing means made of a bag-like member 7 having a heat storage material 8 therein, in order to heat the outer layer part 5 made of a shape memory alloy and restore the shape to a larger diameter shape. It consists of The bag-like member 7 is fixed to the inner surface of the outer layer portion 5 by adhesive or the like.

When using the stent 4 configured in this way, the first
As shown in FIG. 5, the stent 4 is contracted to a small diameter and attached to the lumen at the distal end of the overtube 1.

Further, a bushing tube 12 is inserted into the rear side of the stent 4.

In this state, it is inserted into the biological conduit 9 so that the distal end becomes the narrowed part 10.
When reaching this point, the pusher tube 12 pushes the rear end of the stent 4 and pushes the stent 4 out from the tip of the overtube 11. Through this operation, the stent 4 is inserted into the stenotic region 10 and placed therein as shown in FIG. 16.

Thereafter, the pusher tube 12 is removed from the overtube 11, and the gripping forceps a are inserted into the inner cavity of the overtube 11 instead. Then, as shown in FIG.
It is grasped with grasping forceps a as a stimulation means. Stimulated by this gripping pressure, the heat storage material 8 within the bag-like member 7 undergoes a phase transition from a liquid phase to a solid phase, and during this phase transition, latent heat is radiated to generate heat.

The heat generated in this way is transmitted to the outer layer 5 made of the flexible shape memory alloy, causing the stent 4 to recover its shape to a larger diameter as shown in FIG. Expand.

When all the phase transitions are completed, the heat generation stops, the stent 4 is cooled by the ambient temperature, and is fixed in the large diameter shape as shown in FIG. 17.

Thereafter, when the overtube 11 and the grasping forceps a are removed, the stent 4 is left in the stenotic region 10 in an expanded state as shown in FIG. 17.

According to the configuration of this embodiment, the first to third
As in the embodiment described above, there is no need to provide a hot water rinsing device for heating, an electric heater, etc., and the structure can be simplified, operability improved, and electrical safety improved.

18 to 19 show a fifth embodiment in which the present invention is applied to a medical capsule.

The capsule body 21 of this medical capsule is made of a cylindrical member with a hemispherical bottom at one end.
A lid 22 is screwed onto the frontage end of 1. Inside the capsule body 21, there is a storage chamber 23 for accommodating the drug.
is formed, and a communication path 24 is provided in the hemispherical bottom portion 21a, through which the storage chamber 23 and the outside are communicated. The communication path 24 has a size such that, for example, a drug such as a drug solution stored in the storage chamber 23 does not easily leak. In addition, the lid body 22
A circular convex portion 22a is protruded from the inner tip of the holder.

On the other hand, there is a movable member 2 in the accommodation chamber 23 of the capsule body 21.
5 is slidably provided.

This movable member 25 is connected to the bottom portion 21 of the capsule body 21.
It is made of a bottomed cylindrical body having a hemispherical bottom portion 25a having approximately the same shape as the inner wall surface, and is located within the storage chamber 23 from the storage position where the volume inside the storage chamber 23 is increased, as shown in FIG.
As shown in FIG. 9, it functions as a piston that changes the volume of the storage chamber 23 by moving to an extrusion position where the volume inside the storage chamber 23 is reduced.

A coil-shaped operating member 26 is housed inside the cylindrical body of the movable member 25. One end of the operating member 26 is fixed to the bottom 25a inside the movable member 25, and the other end is a circular convex portion of the lid 22. It is fixedly attached to the portion 22a. The operating member 26 is made of a shape memory alloy such as a Ni-Ti alloy or a Cu-Zn-Al alloy. The operating member 26 is memorized in the shape of a stretched coil as shown in FIG. 19 in the high temperature phase, i.e., in a state higher than the transformation temperature, and is plastically deformed in the low temperature state.
As shown in the figure, the coil is formed into a contracted shape. The transformation temperature is set at 40 to 60°C.

Further, 27 is an O-ring fitted onto the outer peripheral surface of the movable member 25.

Further, a recess 25b is provided on the inner surface of the cylindrical body of the movable member 25, and the operating member 26 is provided in the recess 25b.
A heat storage material 8 for heating and restoring the coil to its stretched shape, and a bag-shaped member 7 for accommodating the heat storage material 8 are fixed by adhesive or the like. Further, an ultrasonic signal generating device 16 as a stimulation means is provided outside the living body to start heat generation of the heat storage material 8. The ultrasonic signal generator 16 includes a transmission signal generator 17, an amplifier 18, an ultrasonic signal generator 19, a pouch 20, and the like.

When the medical capsule configured as described above is used for dispensing a medicine, the storage chamber 23 is filled with the medicine while the movable member 25 is held in the storage position shown in FIG. Then, the patient is made to swallow the capsule body 21 in this state.

When the capsule main body 21 reaches a predetermined position in the body cavity, the ultrasonic generator 16 is activated and ultrasonic vibrations are transmitted toward the capsule, and the ultrasonic vibrations are transmitted to the bag-like member 7 provided on the inner surface of the movable member 25. It reaches the heat storage material 8 inside.

The heat storage material 8 stimulated by this ultrasonic vibration undergoes a phase transition from a liquid phase to a solid phase, and during the phase transition, releases latent heat and generates heat. By this heat, the shape memory alloy forming the operating member 26 changes from the contracted shape of the coil shown in FIG.
It transforms into the stretched shape shown in the figure.

This deformation of the operating member 26 causes the movable member 25 to move to the first position.
It can be moved from the storage position shown in FIG. 8 to the extrusion position shown in FIG. 19. As the movable member 25 moves, the medicine filled in the storage chamber 23 is dispersed into the body cavity through the communication path 24.

The medical capsule configured in this manner is equipped with a heat storage material 8 that undergoes a phase transition due to ultrasonic vibration and generates heat during the phase transition in order to heat the operating member 26 made of a shape memory alloy, and is different from conventional medical capsules. As compared to the method of directly heating the shape memory alloy with the heat of ultrasonic vibration, the heat generation efficiency is improved and operation is reliable.

20 to 21 show a medical capsule representing a sixth embodiment of the present invention.

While the medical capsule of the fifth embodiment was used for dispersing medicine, the medical capsule of this embodiment is used for collecting body fluids. Hemispherical bottom portion 21 as in the fifth embodiment
The capsule body 21 has a cylindrical capsule body 21 having a diameter of 1.a, and a lid body 22 having a circular convex portion 22a is screwed onto the open end of the capsule body 21.

A storage chamber 23 for storing the collected body fluid C is formed inside the capsule body 21, and a communication path 24 is provided in the hemispherical bottom 21a.

In addition, a movable member 2 is provided in the storage chamber 23 of the capsule body 21.
8 is provided. This movable member 28 is made of a bottomed cylindrical body having a flat plate portion 28a at the bottom thereof, and
3, the volume of the storage chamber 23 is changed by moving from a position where the volume of the storage chamber 23 is reduced as shown in FIG. 20 to a storage position where the volume of the storage chamber 23 is increased as shown in FIG. It has the function of a piston. Further, a coil-shaped operating member 29 made of a shape memory alloy is housed inside the cylindrical interior of the movable member 28, and one end of this operating member 29 is fixed to the bottom of the movable member 28. The other end is fixed to the circular convex portion 22a of the lid 22. The shape of this coiled operating member 29 is memorized so that it becomes a contracted shape as shown in FIG. 21 in a high temperature phase, that is, a state above the transformation temperature, and is plastically deformed in a low temperature state. It is formed into an elongated shape as shown in Figure 20. In addition, the said transformation temperature is set to 40-60 degreeC. Further, 27 is an O-ring fitted onto the outer peripheral surface of the movable member 28. When the movable member 28 is located at the position shown in FIG. 20, no body fluid enters the communication passage 24, and when the movable member 28 is moved to the position shown in FIG. A check valve 30 is provided which acts to allow C to enter the storage chamber 23.

Further, as in the fourth embodiment, a recess 31 is provided in the cylindrical inner surface of the movable member 28, and a heat storage material 8 is provided for heating the operating member 29 and restoring the coil to its contracted shape. and a bag-like member 7 that accommodates it are fixed by adhesive or the like.

In addition, in vitro, there is an ultrasonic signal generator 1 for starting heat generation of the heat storage material 8, which has the same configuration as the fourth embodiment described above.
6 is provided.

When the medical capsule constructed in this manner is used for body fluid collection, the movable member 28 is held at the storage position shown in FIG. 20. In this state, the patient swallows the capsule body 21. Then, when the capsule main body 21 inserted into the body cavity reaches a predetermined position, the ultrasonic generator 16 is activated outside the body to transmit ultrasonic vibrations toward the medical capsule.

The ultrasonic vibration is caused by the bag-shaped member 7 provided on the inner surface of the movable member 28.
It reaches the heat storage material 8 inside.

Due to this ultrasonic vibration, the heat storage material 8 undergoes a phase transition from a liquid phase to a solid phase, and at the time of the phase transition, latent heat is released and heat is generated. The heat generated in this manner deforms the operating member 29 from the expanded shape shown in FIG. 20 to the contracted shape shown in FIG. 21.

This deformation of the operating member 29 causes the movable member 28 to move to the 20th position.
The body fluid 32 can be moved from the position shown in the figure to the storage position shown in FIG. .

According to the configuration of this embodiment, as in the fourth embodiment, the heat generation efficiency is improved over the conventional type, so that the collection operation of the medical capsule is reliable.

22 and 23 show a medical capsule representing a seventh embodiment of the present invention. The capsule body 33 is composed of a capsule container 34 made of a stretchable elastic material and a lid part 35.

The capsule container 34 and the lid 35 have a communication passage 36a.
, 36b are formed, respectively, thereby communicating the inside and outside of the capsule body 33.

Moreover, the volume of the inside of the capsule body 33 is reduced by heating, and the liquid impregnated inside is released.

A heat-sensitive mechanochemical gel 37 is housed therein.

As the heat-sensitive mechanochemical gel 37, for example, a gel crosslinked by irradiating an aqueous solution of polyvinyl methyl ether with gamma rays is used.

Inside the heat-sensitive mechanochemical gel 37,
It is impregnated with drug a to be sprayed onto a target site within the body cavity.

Further, applying heat to the heat-sensitive mechanochemical gel 37,
A bag-like member 7 containing a heat storage material 8 therein is fixed to the inner peripheral surfaces of the capsule container 34 and the lid part 35 by adhesive or the like in order to spray the medicine to the target site. Furthermore, an ultrasonic signal generator 16 for generating heat in the heat storage material 8 is provided outside the living body, with the same configuration as that of the fifth embodiment described above.

When using a medical capsule configured in this way,
The patient swallows the capsule body 33.

Then, when the capsule body 33 reaches a predetermined position within the body cavity, the ultrasonic generator 16 is activated to transmit ultrasonic vibrations toward the capsule. The ultrasonic vibrations reach the heat storage material 8 in the bag-like member 7 provided on the inner peripheral surface of the capsule container 34 and the lid part 35.

Due to this ultrasonic vibration, the heat storage material 8 undergoes a phase transition from a liquid phase to a solid phase, and during this phase transition, latent heat is released and heat is generated. Due to the heat, the heat-sensitive mechanochemical gel 37 inside the capsule body 33 is dehydrated, contracts, and releases the drug a inside it to the outside. This drug a is passed through a communication path 36a as shown in FIG.

36b to the target site within the body cavity.

According to the configuration of this embodiment, the fifth and sixth
As in the case of the embodiment, the heat generation efficiency is higher than that of direct ultrasonic heating, and the operation is reliable.

The eighth to tenth embodiments shown below are examples of application to a blood vessel embolization device.

24 to 28 show an eighth embodiment of the present invention.

By the way, when the femoral artery is occluded, the upstream side of the occluded area,
Downstream, bypass surgery is performed, which connects the nearby femoral vein and directs blood flow through the femoral vein. In this case, it may be necessary to occlude the femoral vein so that arterial blood does not flow into the femoral vein. The vascular embolization device of this embodiment is used for occluding the femoral vein. The vascular embolization device main body 38 is composed of a container 39 and a lid 40, both of which are fixed by adhesive or the like. In addition, the container 39
The material of the lid portion 40 is made of shape memory resin, such as polynorbornene, trans-1,4-polyisoprene, styrene-butadiene copolymer, polyurethane, etc.

The container 39 and the lid 40 turn into a rubber state above the shape recovery temperature, and as shown in FIG. Below, it is in a plastic state and hardens. Note that the temperature for the shape recovery is 40 to 60°C.
Set between. On the other hand, the inside of the vascular embolizer main body 38 is filled with a heat storage material 8 for heating and softening the container 39 and the lid 40 made of the shape memory resin.

When using a vascular embolization device configured in this way,
As shown in FIG. 26, the endoscope 42 is inserted from the upstream side of the femoral vein 41, and while performing endoscopic observation, the introducer 43 is inserted from the downstream side of the femoral vein 41 up to the bifurcation 41a. do. The introducer 43 is
It consists of a hard sheath 44 and a curved distal end 45 provided on the distal end side thereof. Further, inside the introducer 43, a vascular embolization device body 38 deformed into a thin shape is provided, and a pusher tube 46 for pushing the vascular embolization device body 38 into the blood vessel is provided on the proximal side thereof. Once the introducer 43 has been inserted to the bifurcation 41a, the vascular embolizer main body 38 is pushed out from the inside of the introducer 43 into the femoral vein 41 using the pusher tube 46, as shown in FIG. After that, remove the introducer 43 and pusher tube 46,
As shown in FIG.
, an amplifier 18, an ultrasound signal generator 19, and a pouch 20. Example Sentence 4 of the femoral vein 41
Send ultrasonic vibrations towards 7. The ultrasonic vibrations reach the vascular embolization device main body 38 inserted into the example sentence 47. Due to this ultrasonic vibration, the heat storage material 8 provided in the vascular embolization device main body 38 undergoes a phase transition from a liquid phase to a solid phase, and during the phase transition, releases latent heat and generates heat. Then, due to the heat, the container 39 and lid part 40 of the vascular embolization device main body 38, which are made of shape memory resin, are softened and recovered to a shape with both ends enlarged as shown in FIG. It deforms into a shape that closely fits the blood vessel wall. When all of the heat storage material 8 completes the phase transition from the liquid phase to the solid phase, the heat generation stops, and the blood vessel embolizer body 38 is cooled by the surrounding blood, and the blood vessel of the blood vessel embolizer body 38 made of shape memory resin is It has a shape that fits closely to the wall, and it cools and hardens into a plastic-like shape, completely blocking blood flow in the side skin 47.

The vascular embolization device configured in this manner has a container 39 and a lid 40 made of shape memory resin, and a heat storage material 8 for heating inside thereof, so that it can be easily heated by applying ultrasonic vibration from outside the living body. It generates heat, and the shape of the vascular embolization device main body 38 can be made into a shape that closely contacts the blood vessel wall of the lateral skin of the femoral vein.

Therefore, it becomes possible to reliably block blood flow.

Furthermore, since it is in close contact with the blood vessel wall, there is no risk of it moving after placement.

29 to 32 show a vascular embolization device according to a ninth embodiment of the present invention. This vascular embolization device main body 48 has a container 49 made of shape memory resin as in the eighth embodiment described above.
and a lid portion 50 made of a thin metal plate, which are fixed by adhesive or the like. The container 49 made of the shape memory resin has a diameter of 40 to 60 mm as in the eighth embodiment.
The transformation temperature is set at 0° C., and the shape is memorized so that the tip expands as shown in FIG. 30 above the shape recovery temperature. Furthermore, a heat storage material 8 for heating and softening a container 49 made of shape memory resin is provided inside the vascular embolization device main body 48.

In order to use the vascular embolization device main body 48 constructed in this way, the femoral vein 4 should be used as shown in FIG.
The endoscope 42 is inserted from the upstream side of the femoral vein 41, and the introducer 43 is inserted from the downstream side of the femoral vein 41 to the branching part 41a with the lateral skin 47 under endoscopic observation.

Thereafter, the slender blood vessel embolization device main body 48 mounted within the introducer 43 is pushed out into the side skin 47 using a busher tube (not shown). In this case, the lid portion 50 is pushed out into the side skin 47 so as to face the introducer 43 side. Thereafter, the pusher tube is removed and a metal wire 51 is inserted into the introducer 43 instead.

Then, the lid portion 50 made of a thin metal plate of the vascular embolization device main body 48 is activated by the metal wire 51 as a stimulation means.
is pressed as shown in FIG. Due to such stimulation, the heat storage material 8 provided inside the vascular embolization device main body 48 undergoes a phase transition from a liquid phase to a solid phase, and releases latent heat to generate heat. Due to this generated heat, the shaped resin container 49 of the vascular embolization device main body 48 is moved into the femoral vein 4 as shown in FIG.
The shape of the side skin 47 of No. 1 is restored to a large diameter shape that comes into close contact with the blood vessel wall.

When all of the heat storage material 8 completes the phase transition from the liquid phase to the same phase, the heat generation stops, the vascular embolization device main body 48 is cooled by the surrounding blood flow, and the four containers made of shape memory resin are attached to the blood vessel wall of the side skin 47. The close-fitting shape provides a plastic-like cooling effect and blocks blood flow in the side skin 47.

Therefore, as in the eighth embodiment described above, blood flow can be reliably blocked, and movement of the vascular embolus device main body 48 after placement is eliminated.

Furthermore, compared to the seventh embodiment, since there is no need to apply ultrasonic vibrations from outside the body, preparation time and effort are reduced and operability is improved.

33 to 35 show a tenth embodiment of the present invention. The vascular embolization device main body 52 of this embodiment is the eighth
Like the embodiment described above, it is composed of a lid part 53 made of shape memory resin and a container 55 having a locking part 54, and the lid part 53 and container 55 are fixed by adhesive or the like. A heat storage material 8 is provided inside the vascular embolization device body 52 to heat and soften the vascular embolization device body 52 made of shape memory resin.

Furthermore, when the locking portion 54 of the container 55 made of the shape memory resin is heated above the set transformation temperature of 40 to 60° C., it changes from the folded shape shown in FIG. 33 to the expanded shape shown in FIG. 34. It is stored in shape memory to take the same shape.

When using the vascular embolization device main body 52 configured in this way, the endoscope 42 is inserted from the upstream side of the lower limb femoral vein 41, and the introducer 43 is inserted under the observation. It is inserted up to the branching part 41a of the lower limb femoral vein 41 with the side skin 47.

Further, as in the eighth embodiment, the introducer 43
A slender blood vessel embolization device main body 52 is attached therein, and a pusher tube (not shown) is provided on the proximal side of the introducer 43. Then, the vascular embolization device main body 52 is pushed out into the example sentence 47 using the pusher tube.

Thereafter, as shown in FIG. 35, the introducer 43
A grasping forceps 51a serving as a stimulation means is inserted into the inner cavity of the vessel, and the rear end of the vascular obturator main body 52 is grasped.

Due to the gripping pressure, the heat storage material within the vascular obturator main body 52 undergoes a phase transition from a liquid phase to a solid phase, and begins to generate heat during the phase transition. Due to the generated heat, the locking portion 54 of the container 55 made of shape memory resin of the vascular embolizer main body 52 expands as shown in FIG. 34 and comes into close contact with the blood vessel wall of the side skin 47. Then, when all of the heat storage material 8 changes from a liquid phase to a solid phase and heat generation stops, the vascular embolization device main body 52 is cooled by the surrounding blood, and the locking portion 54 of the container 55 made of shape memory resin is connected to the side skin 47.
It hardens into a plastic-like state in close contact with the blood vessel wall of the lateral skin 47, and blocks blood flow in the side skin 47.

Therefore, this embodiment also provides the same effects as those of the eighth embodiment described above.

As shown in FIG. 36, a heat storage material 8 is provided inside the vascular embolizer main body 52 consisting of a container 56 made of silicone or the like, which is biocompatible, and a lid 57. Even if the blood vessel adhesion part 59 made of shape memory resin and having the locking part 54 is fixed by adhesive or the like, the same effect as that of this embodiment can be obtained.

In addition, in the eighth to tenth embodiments, an example was shown in which it is used for occluding the venous skin during femoral artery bypass surgery, but the invention is not limited to this, and for example, it can be used for bypass surgery on various blood vessels in a living body. It can also be used as an embolization device for embolization therapy for liver diseases, or for vascular embolization for the treatment of arteriovenous sinuses and vascular malformations.

The eleventh embodiment and the twelfth embodiment described below apply the present invention to a rigid endoscope.

FIG. 37 shows a rigid endoscope 60 showing an eleventh embodiment of the present invention. The main body of the rigid endoscope 60 of this embodiment is composed of an eyepiece 61 and a rigid sheath 62. The eyepiece 61 has an eyepiece 63a, and the rigid sheath 6
An objective lens 63b is provided at the tip of the lens 2, and a plurality of relay lenses 63c are provided within the rigid sheath 62. Also,
The inside of the rigid sheath 62 is filled with a heat storage material 8 for heating the rigid mirror 60 and preventing the lenses 63a, 63b, and 63c from fogging up during use. Further, a trigger section 64 is provided at the rear end of the rigid sheath 62 as a stimulation means for starting heat generation in the heat storage material 8 .

A trigger button 66 having a compression needle 65 is provided on the trigger portion 64 so as to be movable forward and backward via a waterproof ring 68 while being biased by a coil spring 67 .

When using the rigid endoscope 60 configured in this way,
First, the rigid scope 60 is sterilized under high temperature and pressure in an autoclave. By heating to the high temperature, the heat storage material 8 within the hard sheath 62 becomes a supercooled liquid.

When the trigger button 66 is pressed immediately before inserting the rigid scope 60 into the patient's body, the compression needle 65 collides with the opposing rigid sheath 62, causing a pressure change at the collision site. Due to this pressure change, the liquid heat storage material 8 undergoes a phase transition to a solid state,
During phase transition, latent heat is released and heat is generated. The heat generated at this time heats the lenses 63a, 63b, and 63c to the same temperature as body temperature. The device is then inserted into the patient's body and observed.

Therefore, due to heat generation from the heat storage material 8, the lenses 63a,
63b and 63c are heated to about the same temperature as the body temperature, so there is no risk of clouding the observation field of view during observation, and observation performance is improved.

Furthermore, fogging can be prevented with a simple operation without the need for a dedicated heater for heating the rigid scope, unlike in the past.

Furthermore, by autoclave sterilization, the heat storage material 8
Since the heat storage material 8 returns to a supercooled state, sterilization work and regeneration work of the heat storage material 8 can be performed simultaneously.

38 to 39 show a rigid endoscope 60 showing a twelfth embodiment of the present invention. This rigid scope 60 has an eyepiece 61
and a hard sheath 62, the eyepiece 6
1 and the inside of the rigid sheath 62 are provided with an eyepiece lens 6381, an objective lens 63b1, and a relay lens 63C, as in the eleventh embodiment described above. Furthermore, as shown in FIG. 39, the inside of the rigid sheath 62 is provided independently from a first space 69 on the upper side and a second space 70 on the lower side. Further, as shown in FIG. 39, a light guide 71 is provided near the lens 63c.

In order to prevent the lenses 63a, 63b, and 63c from fogging up during use, the first space 69 and the second space 70 are each filled with heat storage material 8, as in the eleventh embodiment. Furthermore, a first trigger section 72 and a second trigger section 73 are provided for starting heat generation in each of the heat storage materials 8.

Each of the trigger parts 71 and 72 has a similar configuration, and is provided so that it can move forward and backward via a waterproof ring 68 in a state where a trigger button 75 having a compression needle 74 is biased by a coil spring 76. .

In order to use the rigid scope 60 configured as described above, first, the rigid scope 60 is sterilized under high temperature and pressure in an autoclave. In the above operation, the heat storage material 8 inside each of the first space 69 and the second space 70 in the hard sheath 62 becomes a supercooled liquid.

Immediately before inserting the rigid scope 60 into the patient's body, the trigger button 75 of the first trigger section 72 is pressed. Then, the compression needle 74 collides with the opposing rigid sheath 62,
A pressure change occurs at the collision site.

Stimulated by this pressure change, the liquid heat storage material 8 in the first space 69 undergoes a phase transition to a solid state, and generates heat during the phase transition. The heat generated in this way causes the lenses 63a and 63b to
, 63c are heated to the same temperature as body temperature.

When the heat storage material 8 stops generating heat and the lenses 63 a, 63 b, 63 c start to fog up again while the rigid endoscope 60 is in use, next press the trigger button 75 of the second trigger part 73 to release the compression needle 74. It collides with the opposing rigid sheath 62, and as before, this time the heat storage material 8 in the second space 70
This heat causes the lenses 63a, 63b, 63c to
is heated again to the same temperature as body temperature.

According to this twelfth embodiment, the rigid sheath 6
The heat storage material 8 is independently loaded into each of the spaces 69 and 70 on the upper end side and the lower end side of the interior of the
2.73 allows for selective heating, making it possible to extend the time during which fogging can be prevented.

Note that the structure may be such that the heat storage material 8 is provided only near the tip lens, or the heat storage material 8 may be caused to generate heat by applying a high voltage instead of the pressurizing means as a trigger for generating heat. good. 40 to 42 show a thirteenth embodiment of the present invention. This embodiment is applied to a grasping forceps 77 as a hard treatment instrument inserted into a living body.

The forceps body 78 of the grasping forceps 77 includes an outer sheath 79, a grasping portion 80 provided at the tip of the outer sheath 79, and the outer sheath 79.
It consists of an operating nozzle 81 provided at the rear end, and the grip part 80 and the operating nozzle 81 are connected to a bendable coil sheath 8.
2 are connected.

Furthermore, the outer sheath 79 is composed of a double cylindrical sheath member 83a that forms a space 83 into which the heat storage material 8 is placed;
A trigger portion 84 is connected to the rear end of this sheath member 83a. The sheath member 83a is made of a shape memory material such as shape memory resin or shape memory foam that can be deformed into any shape at temperatures above the deformation temperature and retains the deformed shape at temperatures below the deformation temperature. The heat storage material 8 is a supercooled liquid that releases latent heat and generates heat when changing phase from liquid to solid, such as sodium acetate trihydrate.

The trigger part 84 is connected to the waterproof ring 8 when a trigger button 86 having a compression needle 85 is biased by a coil spring 87.
8, so that it can move forward and backward freely.

The forceps body 78 is fixed to the outer sheath 79 by a fixing member 89 made of elastic rubber.

When the trigger button 86 of the trigger section 84 is pressed, the compression needle 85 collides with the opposing sheath member 83a, and a minute pressure change occurs at the collision site. This pressure change stimulates the heat storage material 8, which was a supercooled liquid, and changes its phase to a solid while releasing latent heat and generating heat. The heat generated at this time heats and softens the sheath member 83, allowing it to be deformed into any shape as shown in FIG. 41, for example. Since the phase change progresses rapidly and the heat generation ends when the phase change ends, if the sheath member 83a is left deformed,
It cools down and retains its deformed shape.

In addition, if the phase-changed heat storage material 8 is liquefied to a temperature higher than the freezing point and then allowed to cool naturally, it can be regenerated as a supercooled liquid again. In addition, regeneration work can be performed simultaneously with heat disinfection and sterilization processes using autoclaves, etc.

Next, the actual state of use will be explained with reference to FIG. In FIG. 42, 90 is the abdominal wall, 91 is a tissue site in the living body,
92 is a rigid endoscope, and 93 is a light guide cable attached to the rigid endoscope 92. The grasping forceps 77 are used after being changed into an arbitrary shape as described above so that the target region can be easily grasped under observation with the rigid endoscope 92. Therefore, according to this embodiment, the shape of the insertion portion of the treatment instrument can be easily changed.

Note that when using the rigid endoscope 92, if the main body is inserted into the body while it is cold, water vapor will adhere to and condense on the surfaces of the optical system members such as the lens portion, causing fogging. For this reason, it is usually inserted into the body after being heated to near body temperature.

In order to heat the rigid endoscope 92 for this purpose, a heating tool as shown in FIG. 43 is used here.

This heating tool has an insertion section cover 94 that covers the insertion section of the rigid endoscope 92. The insertion section cover 94 is made of a material such as metal that has good heat conductivity. Inside the wall of this insertion part cover 94, there is a space 9 in which the heat storage material 8 is enclosed.
4a is formed.

As shown in FIG. 43, one end of the insertion section cover 94 is provided with a trigger button 86 having a compression needle 85, similar to that of the trigger section 84 of the grasping forceps 77 described above. When the trigger button 86 is pressed, the heat storage material 8 generates heat in the same way as the gripping forceps 77, and the endoscope can be moistened.

44 and 45 show a fourteenth embodiment of the present invention. This embodiment relates to a laser probe.

The second laser probe is attached to a shape memory material sheath 9 having a rubber cap 96 at the rear end via a gasket holding member 95.
7, and within this sheath 97 is provided an optical fiber 99 having a coating material 98.

A heat generating section 100 having a heat storage material 8 inside is loaded on the outer periphery of the sheath 97 . This heat generating part 100 is provided with a trigger button 86 having a compression needle 85 as in the twelfth embodiment described above.

Then, as in the case of the twelfth embodiment, by pressing the trigger button 86, the phase change of the heat storage material 8 starts and heat is generated. The sheath 97 is heated by the heat generated and can be deformed into any shape as shown in FIG. 45. therefore,
The same effects as in the twelfth embodiment can be obtained.

[Effects of the Invention] As explained above, the present invention has a simpler structure and easier heating operations than conventional medical treatment instruments that require heating.

Furthermore, since heating is performed reliably, the operation of the medical device within the living body is reliably performed.

Furthermore, it is no longer necessary to use heating means such as a heater as in the past, and electrical safety is also improved.

[Brief explanation of the drawing]

1 to 6 show a first embodiment of the present invention, in which FIG. 1 is a side view of the biological duct dilator, FIG. 2 is a perspective view of the stent, and FIG. 3 is a biological duct dilator. 4 is a sectional view showing the state when inserting the biological duct dilator into the biological duct; FIG. 5 is a vertical sectional view of the expanded biological duct dilator;
FIG. 6 is a sectional view of a state in which the biological duct expander has been inserted into the biological duct. 7 to 10 show a second embodiment of the present invention,
Figure 7 is a side view of the balloon dilator of the biological duct dilator, Figure 8 is a longitudinal cross-sectional view of the biological duct dilator with a stent attached, and Figure 9 is the biological duct dilator in an expanded state. FIG. 10 is a longitudinal cross-sectional view of the expanded stent. 11 and 12 show a third embodiment of the present invention, in which FIG. 11 is a longitudinal cross-sectional view of a state in which a biological duct expander is inserted into a biological duct and expanded, and FIG. FIG. 3 is a cross-sectional view of a state in which the biological duct dilator has been completely inserted into the tract. 13 to 17 show a fourth embodiment of the present invention, in which FIG. 13 is a sectional view of the material of the biological duct dilator, FIG. 14 is a perspective view of the biological duct dilator, and FIG. The figure is a sectional view of the biological duct dilator inserted into the biological duct, FIG. 16 is a sectional view of the biological duct dilator about to begin expanding, and FIG. 17 is the biological duct dilator. FIG. 3 is a cross-sectional view of a state in which the biological duct dilator has been completely inserted into the tract. 18 to 19 show a fifth embodiment of the present invention, in which FIG. 18 is a cross-sectional view of the state in which the medical capsule is operated in vivo, and FIG. 19 is the operating state of the medical capsule when the operation is completed. FIG. FIGS. 20 and 21 show a sixth embodiment of the present invention, FIG. 20 is a sectional view of a state in which a medical capsule is operated in a living body, and FIG. 21 is an operating state of a medical capsule when the operation is completed. FIG. FIGS. 22 and 23 show a seventh embodiment of the present invention, FIG. 22 is a sectional view of the medical capsule in a state in which it is operated in a living body, and FIG. 23 is an operating state of the medical capsule when the operation is completed. FIG. 24 to 28 show an eighth embodiment of the present invention, in which FIG. 24 is a sectional view of the vascular embolization device, FIG. 25 is a sectional view of the vascular embolization device in a deformed state, and FIGS. 26 to 28 The figures are explanatory diagrams sequentially showing the procedure for inserting the blood vessel embolization device. 29 to 32 show a ninth embodiment of the present invention, in which FIG. 29 is a sectional view of the vascular embolization device, FIG. 30 is a sectional view of the vascular embolization device in a deformed state, and FIGS. 31 to 32 The figures are explanatory diagrams sequentially showing the procedure for inserting the blood vessel embolization device. 33 to 35 show a tenth embodiment of the present invention, FIG. 33 is a sectional view of a vascular embolization device, and FIGS. 34 to 35 are explanatory diagrams sequentially showing the procedure for inserting the vascular embolization device. It is. FIG. 36 is a sectional view of a vascular embolization device showing a modification of the tenth embodiment of the present invention. FIG. 37 is a sectional view of a rigid endoscope according to an eleventh embodiment of the present invention. 38 to 39 show a twelfth embodiment of the present invention, FIG. 38 is a sectional view of a rigid endoscope, and FIG. 39 is a sectional view of a rigid endoscope.
It is a sectional view taken along the line AA in the figure. 40 to 43 show a thirteenth embodiment of the present invention, FIG. 40 is a sectional view of the treatment instrument, FIG. 41 is a side view of the treatment instrument, and FIG. 42 is a sectional view of the treatment instrument in use. Yes, 43rd
The figure is a cross-sectional view of an endoscope heating tool used therein. 44 and 45 show a fourteenth embodiment of the present invention, in which FIG. 44 is a sectional view of a laser probe, and FIG. 45 is a side view of the laser probe. 1... Balloon dilator, 2... Balloon, 4... Stent, 8... Heat storage material, 9... Biological conduit, 16...
Ultrasonic generator, 21... Capsule body, 25...
Movable member, 26... operating member, 28... movable member,
29... Operating member, 33... Capsule body, 37.
...Mechanochemical gel, 42...Endoscope, 48...
- Vascular embolization device main body, 51... Wire, 52... Vascular embolization device main body, 55... Container, 60... Rigid scope, 62.
... Rigid sheath, 64 ... Trigger part, 65 ... Compression needle, 71.72 ... Trigger part, 77 - Grasping forceps, 84
...Trigger part, 85...Compression needle, 97...Sheath. Applicant Representative Patent Attorney Atsushi TsuboiFigure 5Figure 6Figure 18Figure 19Figure 20Figure 21Figure 13 Area 14 Area 17Figure 22Figure 23 Area 26 Area 27Figure 29 Figure 30 Figure 41 Figure 44 Figure 45

Claims (1)

[Claims] In a medical device that is inserted into a living body to perform medical treatment, a device is provided in the main body of the medical device to store latent heat in a supercooled state and release latent heat when the phase transition from a liquid phase to a solid phase occurs due to external stimulation. 1. A medical device comprising: a heat storage material to be operated; and stimulation providing means for starting a heat generating action that causes a phase transition of the heat storage material from a liquid phase to a solid phase.