JP2003010207A - Thermotherapy instrument - Google Patents

Abstract

PROBLEM TO BE SOLVED: To protect a patient against a feeling of incongruity and discomfort due to excessive cooling and allow effective thermotherapy. SOLUTION: The flow rate of cooling water when laser irradiation is not being conducted is made lower than when laser irradiation is being conducted. Conversely speaking, the flow rate of cooling water when laser irradiation is being done is made higher than when laser irradiation is not being done.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention is directed to inserting an insertion portion into a living body lumen such as a blood vessel, digestive tract, urethra, abdominal cavity, or chest cavity, or a lumen, or surgically pressing a portion pressed against living tissue. Touch or press the pressed part against the body surface, and then irradiate the biological tissue with energy such as laser light, microwaves, radio waves, or ultrasonic waves from the emission part installed in the insertion part or the pressed part. The present invention relates to a heat treatment device for performing heat treatment.

[0002]

2. Description of the Related Art A long insertion portion is inserted into a living body by utilizing a body cavity of the living body or by making a small incision in the living body, and laser light, microwaves, radio waves are applied to a lesion site of the living tissue. , Irradiating energy such as ultrasonic waves,
BACKGROUND ART A heat treatment apparatus is known that heat-treats a lesion site by heating, denaturing, necrosing, coagulating, cauterizing, or vaporizing the tissue at the lesion site to eliminate the tissue.

In general, this heat treatment apparatus directly irradiates energy to a lesion site located on or near the surface layer of a living tissue from one location or a plurality of locations to heat-treat the lesion site. Taking the case of treating the prostate, which is the treatment of the deep part of the living tissue, as an example, the treatment is performed as follows.

First, the operator inserts the insertion portion into the urethra by his / her own operation, and while observing the inside of the urethra with an endoscope, causes the emission portion to reach the prostatic urethra (the urethra surrounded by the prostate). . Then, the position of the emitting portion is aligned with the lesion site in the urethra, and energy is applied to the lesion site.

Since the emitting portion irradiates energy in a very narrow and sealed space, the heat treatment apparatus protects the emitting portion or the living tissue adjacent to the emitting portion from thermal injury, so that the emitting portion or the emitting portion is protected. A cooling device is provided for cooling the surface layer of the biological tissue that contacts the part and its vicinity.

[0006]

However, in the conventional heat treatment apparatus, the insertion portion is always cooled by the cooling device. Therefore, if it takes a long time to irradiate the energy, the treatment object is treated. The living tissue and its vicinity are cooled more than necessary.

[0007] For example, when treating the prostate, the operator moves the insertion part forward and backward while observing the inside of the urethra with an endoscope.
The emitting part is positioned at the lesion site. Since this positioning operation requires skill, there are individual differences in the time required for positioning. If this positioning takes a long time,
The living tissue adjacent to the emitting portion and its vicinity are cooled more than necessary. Therefore, depending on the temperature of the cooling liquid, symptoms such as frostbite may occur, and even if energy is emitted from the emitting part, the lesion site may not be sufficiently heated and a sufficient therapeutic effect may not be obtained. .

[0008] When inserting the insertion portion into the body lumen or lumen, a slight anesthesia is applied. Even so, if the living tissue and its vicinity are cooled more than necessary, the patient may feel discomfort or discomfort, and the patient may not be able to easily position the emitting portion at the lesion site as the patient moves.
When such a situation occurs, the burden on the patient becomes larger and the therapeutic effect of heating becomes smaller.

Generally, the cooling device circulates the cooling liquid by a pump. However, when the cooling liquid is constantly circulated at a large flow rate, the number of rotations of the pump increases and the pressure in the flow passage increases. Get higher In the case of a heat treatment device that is extremely required to be miniaturized, the rotation speed of the pump increases and
The increase in the pressure in the flow path leads to a failure of the pump and an increase in the load on the elements that constitute the cooling device, resulting in a shortened life.

Particularly, when the cooling liquid is circulated at a large flow rate, the pressure in the cooling liquid flow path of the insertion portion or the tube connecting the pump and the insertion portion becomes high, and the insertion portion or the tube is easily damaged.

Contrary to the above case, it is conceivable that the temperature of the living tissue adjacent to the emitting portion and the vicinity thereof may become higher than the specified value during the heat treatment. In such a case, the irradiation of the energy from the emitting portion is forcibly stopped, but the temperature is not easily lowered by merely stopping the irradiation, and the treatment of the lesion site is adversely affected.

The present invention has been made in order to reduce the occurrence of various problems as described above, and an object thereof is to provide a heat treatment apparatus which achieves the following objects.

1. By increasing the flow rate of the cooling liquid while irradiating energy and decreasing the flow rate of the cooling liquid when not irradiating energy, it is possible to prevent the patient from feeling uncomfortable or uncomfortable due to overcooling, and to provide effective heat treatment. Be able to do it. Furthermore, the life of the elements that make up the pump and the cooling device is improved.

2. When the temperature of the living tissue adjacent to the emitting part and the temperature in the vicinity of the part become higher than the specified value, the irradiation of energy is forcibly stopped without decreasing the flow rate of the cooling liquid, which adversely affects the treatment of the lesion site. So that it does not exceed

3. When the temperature of the living tissue adjacent to the emitting part and the vicinity thereof become higher than the specified value, the irradiation of energy is forcibly stopped and the flow rate of the cooling liquid is increased so that the temperature is quickly lowered. , Ensure that the treatment of the lesion site is not adversely affected.

4. When the temperature of the living tissue adjacent to the emitting part and its vicinity become higher than the specified value, the irradiation of energy is forcibly stopped and a low temperature cooling liquid is supplied at a high flow rate to Should be reduced more quickly so that treatment of the lesion site is not adversely affected.

[0017]

[Means for Solving the Problems] In order to solve the above problems,
In order to achieve the object, the heat treatment apparatus according to the invention as set forth in claim 1 includes an energy generating means for generating energy for irradiating a living tissue, an instructing means for instructing generation of the energy, and the energy. An energy irradiation unit that guides the energy from the energy generation unit to irradiate the living tissue, a cooling liquid supply unit that supplies a cooling liquid to a cooling liquid channel provided in the energy irradiation unit, and generation of the energy is instructed. When not present, a control unit that controls the cooling liquid supply unit so that the flow amount of the cooling liquid becomes smaller than the flow amount of the cooling liquid when the generation of the energy is instructed. .

A heat treatment apparatus according to a second aspect of the present invention is the heat treatment apparatus according to the first aspect, wherein the control means, when the generation of energy is instructed by the instructing means, after a predetermined time elapses. It further has a function of controlling the energy generating means so that the biological tissue is irradiated with energy.

A heat treatment apparatus according to a third aspect of the present invention is an energy generating means for generating energy for irradiating a living tissue, and an energy for guiding the energy from the energy generating means and irradiating the living tissue. Irradiation means, cooling liquid supply means for supplying a cooling liquid to a cooling liquid flow path provided in the energy irradiation means, and temperature detection means for detecting the temperature of living tissue adjacent to the energy irradiation means or the vicinity thereof, When the temperature of the living tissue adjacent to the energy irradiating means or the temperature in the vicinity thereof exceeds a preset temperature, a control means for forcibly stopping the generation of the energy without changing the flow rate of the cooling liquid, It is characterized by having.

According to a fourth aspect of the present invention, there is provided a heat treatment apparatus, wherein energy generating means for generating energy for irradiating a living tissue and energy for guiding the energy from the energy generating means and irradiating the living tissue. Irradiation means, cooling liquid supply means for supplying a cooling liquid to a cooling liquid flow path provided in the energy irradiation means, and temperature detection means for detecting the temperature of living tissue adjacent to the energy irradiation means or the vicinity thereof, When the temperature of the living tissue adjacent to the energy irradiating means or the vicinity thereof exceeds a preset temperature, the flow rate of the cooling liquid is higher than the flow rate of the cooling liquid when the temperature does not exceed the preset temperature. The cooling liquid supply means is controlled so as to increase, and the generation of the energy is forcibly stopped. And having a control means.

In the heat treatment apparatus according to the invention as defined in claim 5, the energy generating means for generating energy for irradiating the living tissue, and the energy for guiding the energy from the energy generating means and irradiating the living tissue. Irradiation means, cooling liquid supply means for selectively supplying cooling liquids of different temperatures to the cooling liquid passage provided in the energy irradiation means, and temperature of living tissue adjacent to the energy irradiation means or the temperature in the vicinity thereof is detected. Temperature detecting means for
When the temperature of the living tissue adjacent to the energy irradiating means or the vicinity thereof exceeds a preset temperature, a cooling liquid having a temperature lower than the temperature of the cooling liquid when the temperature does not exceed the preset temperature is set. A control means for controlling the cooling liquid supply means so as to supply the cooling liquid at a flow rate higher than that when the temperature does not exceed a preset temperature, and forcibly stopping the generation of the energy, It is characterized by having.

A heat treatment apparatus according to a sixth aspect of the present invention is the heat treatment apparatus according to any one of the first to fifth aspects, wherein the energy irradiating means is a long shape insertable into a living body. It is an insertion part of.

A heat treatment apparatus according to a seventh aspect of the present invention is the heat treatment apparatus according to the sixth aspect, wherein the insertion section emits the energy and the emission section is connected to the insertion section. It is characterized in that it has a moving means for moving back and forth in the longitudinal direction, and an interlocking means for changing the emission angle of the energy in accordance with the movement of the emission part.

The heat treatment apparatus according to an eighth aspect of the present invention is the heat treatment apparatus according to any one of the first to fifth aspects, wherein the cooling liquid supply means includes a cooling liquid in the cooling liquid flow path. It is characterized by circulating.

A heat treatment apparatus according to a ninth aspect of the present invention is the heat treatment apparatus according to any one of the first to eighth aspects, wherein the energy is laser light.

[0026]

BEST MODE FOR CARRYING OUT THE INVENTION Preferred embodiments of the heat treatment apparatus according to the present invention will be described in detail below with reference to the accompanying drawings. It should be noted that the present embodiment will be described by being divided into four modes, that is, the first to fourth embodiments, according to the control mode of the cooling flow rate.

First, the structure of the heat treatment apparatus common to all the embodiments will be described. FIG. 1 is a side view of a laser irradiation apparatus applied to the heat treatment apparatus according to the present invention, and FIG.
[Fig. 3] is a cross-sectional view for explaining an example of use of a laser irradiation device.

The heat treatment apparatus has a side irradiation type laser irradiation apparatus 1 for irradiating a living tissue with laser light. This heat treatment apparatus inserts the elongated insertion portion 121 of the laser irradiation device 1 into a living body, and emits laser light from a laser emission portion 122 installed in the insertion portion 121 to a living tissue 1001.
(Refer to FIG. 2) to perform heat treatment by irradiation. For example, it is used for treatment of benign prostatic hyperplasia and tumors such as various cancers.

As shown in FIGS. 1 and 2, the laser irradiation apparatus 1 includes a long insertion part 121, a laser emission part 122 for irradiating a laser beam, and a laser emission part 122 which is included and inserted. The housing 124 is connected to the tip of the portion 121.

The laser emitting portion 122 is constructed so as to be able to move back and forth in the axial direction, and a smooth laser reflecting surface 123 (mirror) for reflecting laser light is formed on one surface thereof. The reflection angle of the laser reflecting surface 123 changes as the laser emitting portion 122 moves back and forth. The laser emitting portion 122 is made of, for example, resin, glass, metal, or a composite material thereof. Further, the laser emitting section 122 is the laser emitting section 122.
A mirror temperature sensor 111 is provided to detect the temperature of the. Examples of the mirror temperature sensor 111 include a thermistor, a thermocouple, and a platinum resistance temperature detector.
It is not limited to these.

The mirror temperature sensor 111 is preferably installed on the back surface of the laser reflection surface 123. As a result, the mirror temperature sensor 111 is prevented from directly receiving the laser beam, so that the temperature detection accuracy is kept good and the mirror temperature sensor 111 is protected from damage. The installation position of the mirror temperature sensor 111 is not limited to the back surface of the laser reflection surface 123, and it can be installed in any area of the laser emission part 122 except the laser reflection surface 123.

The housing 124 is made of a hard tubular body such as stainless steel having a window 127 for laser light irradiation, and is covered with a laser light transmissive cover member. Inside the housing 124, temperature sensors 113a and 113b that detect the temperature of the living tissue adjacent to the laser emitting portion 122 and the vicinity thereof are arranged. The tip of the housing 124 is sealed by a cap 126.

In order to guide the laser light, the optical fiber 101
Are arranged inside the insertion portion 121. A lens may be provided at the tip of the optical fiber 101. This lens is an optical element for reducing the beam divergence angle of laser light. The optical fiber 101 transmits the laser light generated by the laser light source device 3 (see FIG. 4).
The shock absorber 132 accommodates the optical fiber forming the loop and absorbs the movement of the optical fiber.

The insertion portion 121 is provided with a cooling liquid flow path for cooling living tissue adjacent to or near the laser emitting portion 122. The coolant flow path is the insertion part 1
It is a closed flow path that extends from the root portion 125 of the reference numeral 21 toward the housing 124 and is folded back at the tip of the insertion portion 121.
Both ends of this cooling liquid flow path are connected to a cooling water inlet connector 103 and a cooling water outlet connector 104 (see FIG. 1) of the laser irradiation apparatus 1. To the cooling water inlet connector 103 and the cooling water outlet connector 104, a water supply tube 272 and a drainage tube 273 reaching the cooling unit are connected. Therefore, the cooling water supplied from the cooling unit circulates between the cooling liquid flow path in the insertion portion 121 and the insertion portion 12
1, in particular, the window 127 is cooled and the laser emitting unit 1
Living tissue adjacent to or near 22 is cooled.

The laser irradiation device 1 is additionally provided with an observation device 8 for observing the surface layer of living tissue. This observation device 8
Is an endoscope 801 that is detachable from the laser irradiation device 1.
have. The endoscope 801 is inserted from the base end portion of the laser irradiation device 1 toward the tip end portion. Endoscope 80
A camera head 803 is attached to the base end side of 1, and an image can be sent through the camera signal lead 804. Note that it is also possible to directly view through the eyepiece lens attached to the endoscope 801 without attaching the camera head 803. The optical fiber of the endoscope 801 that illuminates the illumination light also has a function of illuminating the guide light sent through the light guide 802. Therefore, it is possible to perform the observation of the surface layer irradiated with the laser light, the positioning of the housing 124 based on the endoscopic observation, and the visual confirmation of the irradiation position of the laser light.

The distal end portion of the insertion portion 121 is inserted into the body cavity 1002, and the housing 124 containing the laser emitting portion 122 is placed on the surface layer near the lesion site, that is, the target site 1101 which is the target heating site. Make them adhere closely. At this time, the housing 801 is moved by the endoscope 801.
It is desirable to confirm the position of directly. The target point 110 in the longitudinal direction of the insertion portion 121
The position of 2 is adjusted by moving the entire laser irradiation apparatus 1 in the longitudinal direction of the insertion portion 121. Also,
Target point 1 in the circumferential direction of the insertion part 121
The position of 102 is adjusted by rotating the entire laser irradiation apparatus 1.

When irradiating the laser beam, the laser emitting portion 122 is reciprocated in the axial direction while changing the irradiation angle at a cycle of 0.1 to 10 Hz, preferably 1 to 6 Hz. Thus, the optical path of the laser light is continuously changed, but all intersect at the target point 1102.

As a result, the target point 1102 inside the living tissue 1001 and its vicinity are heated by the radiated laser light to reach the desired temperature. Also,
Since the insertion portion 121 is cooled to a desired temperature by the cooling water circulating through the cooling liquid flow path, it is possible to raise only the temperature inside the desired target portion 1101 while suppressing the temperature rise in the surface layer portion.

The laser light with which the living tissue 1001 is irradiated can be divergent light, parallel light, or convergent light. In order to make the laser light convergent light, an optical system for making the laser light convergent light is provided in the optical path of the laser light. Further, the laser light used is not particularly limited as long as it has a biological penetration property. However, the wavelength of laser light is 750 to 1300 nm or 1600 to 180.
About 0 nm is preferable because it has a particularly excellent biological penetration property. Examples of the laser light source device for generating laser light in the above wavelength range include gas lasers such as He-Ne lasers, solid-state lasers such as Nd-YAG lasers, and G.
A semiconductor laser such as an aAlAs laser may be used.

Further, the diameter of the insertion portion of the laser irradiation device 1,
That is, the outer diameter of the insertion portion 121 is not particularly limited as long as it can be inserted into the body cavity 1002. However, the insertion part 12
The outer diameter of 1 is preferably about 2 to 20 mm and 3 to 8 mm
The degree is more preferable.

FIG. 3 is a sectional view showing an example in which the heat treatment apparatus is used for treating the prostate. The insertion part 121 of the laser irradiation device 1 is inserted into the urethra 1003, and the vicinity of the tip of the insertion part 121 where the laser emission part is installed is the prostate 10.
It is brought into close contact with the surface layer near 04. Reference numeral 1005 in the figure indicates a bladder. The temperature sensors 113a and 113b are
It is arranged inside the tip of the insertion portion 121 and detects the temperature of the urethral wall.

Further, the heat treatment apparatus has a rectal probe 5. The rectal probe 5 includes an insertion portion 501 that is inserted from the anus 1007 into the rectum 1006, and a grip 502 that is grasped by an operator. The insertion section 501 of the rectal probe 5 is provided with a plurality of temperature sensors 503a to 503e for detecting the temperature of the rectal wall, and the detected values are transmitted through the sensor signal lead 504. . Thus, the temperature sensors 503a-50
3e is the urethra 1003 without being inserted into living tissue.
Seen from above, it is arranged deeper than the prostate 1004.

Therefore, the heat treatment apparatus can perform heat treatment using the detection results of the temperature of the urethral wall and the temperature of the rectal wall. This makes it possible to prevent the normal tissue of the urethra or the rectum existing near the prostate from being heated more than necessary. Here, the temperature sensor 11
Examples of 3a and 113b include a thermistor, a thermocouple, a platinum resistance thermometer, and the like. A thermocouple or an inexpensive thermistor having a small element and having a small influence on laser irradiation is preferable. In addition, the temperature sensors 503a to 503
Similarly, examples of e include a thermistor, a thermocouple, a platinum resistance thermometer, and the like, but an inexpensive thermistor is preferable.

FIG. 4 is a diagram showing the overall configuration of the heat treatment apparatus, FIG. 5 is a diagram showing the control body and the laser light source device, (A) is a front view, (B) is a side view, and (C). ) Is a rear view, and FIG. 6 is a view showing a cooling unit built in the control body.

As shown in FIG. 4, the heat treatment apparatus according to the present invention includes a laser irradiation device 1, a control body 2, a laser light source device 3, a drive unit 4, a rectal probe 5, a foot switch 6, and an observation device 8. Have The laser irradiation device 1, the laser light source device 3, the drive unit 4, the rectal probe 5, and the foot switch 6 are each connected to the control body 2. The foot switch 6 outputs a signal that prompts the control body 2 to emit laser light (instructs generation of energy) when stepped on by the operator.

The observation device 8 includes a light source device 805 for supplying illumination light for endoscopic observation, a television camera device 806 for taking in an image observed by the endoscope,
The television camera device 806 includes an image receiver 807 for displaying an image captured therein, and a cart 808 in which these are collectively installed and movable. Light source device 805
Are connected to the light guide 802. The television camera device 806 is also connected to the camera head 803 via the camera signal lead 804. As a result, the endoscope 8
01 makes it possible to perform heat treatment while observing.

The control body 2 controls the operation of the entire heat treatment apparatus by using the detection signals from various sensors and microswitches installed in the laser irradiation device 1, the drive unit 4, and the rectal probe 5.

As shown in FIG. 5, on the front surface of the control main body 2, a main switch 201 for turning on the power, an abnormality notification indicator light 202 for lighting and notifying when a predetermined abnormality occurs,
Abnormality notification buzzer 20 to notify by sound when a predetermined abnormality occurs
3. A media interface 204 for inputting information of the external storage medium is provided. The media interface 204 is a floppy (registered trademark) in which image information obtained by diagnosing a patient is stored.
It is a drive unit such as a disk (FD) or a magneto-optical disk (MO). In addition, on the upper part of the control body 2, a user interface 20 that displays predetermined information to the user and receives predetermined settings and operations.
5 are provided. The user interface 205 is
It is a touch-type operation panel including a display screen.

On the side surface of the control body 2, a drive unit connector 211 for connecting a signal lead wire extending from the drive unit 4, a sensor signal lead wire 102 extending from each sensor installed in the laser irradiation device 1, 11
A urethral sensor connector 212 for connecting 2 and a rectal sensor connector 213 for connecting a sensor signal lead wire 504 extending from each sensor installed in the rectal probe 5 are provided.

On the rear surface of the control body 2, a foot switch signal input connector 214 for connecting a signal lead wire extending from the foot switch 6 and a foot switch signal output connector 215 for connecting a foot switch signal cable 291 are provided. And are provided. The foot switch signal cable 291 is for transmitting the foot switch signal from the foot switch 6 via the control body 2. Further, on the back surface of the control body 2, an interlock switch signal input connector 217 for connecting a signal lead wire extending from the interlock switch,
Interlock switch signal output connector 216 for connecting interlock switch signal cable 292
And are provided. The interlock switch signal cable 292 is for transmitting an interlock switch signal from the interlock switch via the control body 2. Note that reference numeral 218 in the drawing indicates an inlet to which a power supply cable (not shown) is connected.

On the front surface of the laser light source device 3, a main switch 301 for turning on power and setting dials 302a to 302 for the operator to set the output conditions of the laser light.
c, and an emergency stop switch 303 for stopping the output of the laser light in an emergency. With the setting dials 302a to 302c, output conditions such as laser output value, laser pulse time, laser pulse interval, and laser output time can be set. And the control body 2
The recommended value of the output condition of the laser light planned by is displayed on the user interface 205. The operator can arbitrarily set the output condition of the laser light with reference to the recommended value.

A laser output connector 304 for connecting the base end side of the optical fiber 101 is provided on the side surface of the laser light source device 3. Further, on the rear surface of the laser light source device 3, the foot switch signal cable 2 described above is provided.
91 and interlock switch signal cable 292
A foot switch signal input connector 305 and an interlock switch signal input connector 306 are provided for connecting to each other. Incidentally, reference numeral 30 in the drawing
Reference numeral 7 denotes an inlet to which a power supply cable (not shown) is connected.

As shown in FIG. 5, the laser light source device 3 is
The control main body 2 is provided separately from the control main body 2, and each has a casing forming a different outer frame. The laser light source device 3 combined with the control main body 2 is not limited to a dedicated one, and if the specifications of the foot switch signal and the interlock switch signal are within the same range, a different laser light source device is appropriately combined with the control main body 2. Can be used. For example, it is possible to prepare a plurality of laser light source devices having different rated output values of laser light and use them while appropriately exchanging them. As a result, the system property of the heat treatment apparatus as a whole is improved, and since the laser light source device can be easily removed, the maintainability is improved.

A cooling unit as shown in FIG. 6 is installed inside the control body 2, and a cooling unit door 206 is openably and closably attached to the front surface of the control body 2. The cooling unit is a bag 271 containing cooling water.
have. The bag 271 has a water supply tube 272.
And the drainage tube 273 are connected. The water supply tube 272 and the drainage tube 273 are connected to the cooling water inlet connector 103 and the cooling water outlet connector 104 (see FIG. 1) of the laser irradiation device 1 via the tube panel 207. The bag 271 has two side surfaces that are parallel to each other, and each side surface is constituted by a bag side wall 275. The bag 271 is formed of, for example, a silicon rubber plate or sheet, and the bag side wall 275 is formed of, for example, an aluminum plate or sheet having a good heat transfer coefficient.

In this cooling unit, the first cooling element 252a that contacts one side surface of the bag 271 through the bag side wall 275 and the cooling surface 253, and the bag side wall 275.
And a second cooling element 252b that is detachably provided on the other side surface of the bag 271 via the cooling surface 253. As the cooling elements 252a and 252b, for example, elements using Peltier elements can be used. The bag 271 is sandwiched and positioned by the first and second cooling elements themselves. A water temperature sensor 256 that detects the temperature of the cooling water and a water level sensor 257 that detects the water level of the cooling water are attached to the heat insulating door 278, and the detection results of these sensors can be transmitted. Sterile water or sterile physiological saline is used as the cooling water. The temperature is appropriately maintained in the range of 0 ° C to 30 ° C.

In the above example, the case where one cooling unit is provided in the control main body 2 has been illustrated, but there are cases where two cooling units having the same structure are provided. In this case, the temperature of the cooling water of each cooling unit is set to about normal temperature and the temperature of the other is lower than that. Which of the cooling units is to be used depends on the temperature sensors 113a and 113b or the temperature sensors 503a to 503.
It is selected according to the detected temperature of e.

FIG. 7 is a diagram for explaining the details of the control unit provided inside the control main body 2. Control body 2
Has a control unit 251a. Then, as shown in the figure, the control unit 251a includes a temperature measuring unit 233 and a light detecting unit 23.
4, mirror drive unit 235, connection detection unit 236, water temperature control unit 237, flow rate control unit 238, pressure detection unit 239, water level detection unit 240, laser light source device control unit 241, display / operation input unit 242, and data input / output. A peripheral control unit such as the unit 243, a CPU 231 that performs overall control of each of the peripheral control units, and a memory 232 that stores a predetermined program and data.

The temperature measuring unit 233 includes a urethral sensor connector 2
Mirror temperature sensor 111 and temperature sensor 1 via 12
The detection signals from 13a and 113b are also transmitted via the rectal sensor connector 213 to the temperature sensors 503a to 503.
The detection signal from e is input. The light detector 234 has
The detection signal from the optical sensor 114 is input via the urethral sensor connector 212. The optical sensor 114 is installed in the laser irradiation device 1 and optically detects that the insertion portion 121 of the laser irradiation device 1 is in contact with a laser light irradiation target. As a result, it is possible to prevent the situation where the insertion portion 121 is irradiated with the laser light, for example, in a state where the insertion portion 121 is not inserted into the living body.

The mirror drive section 235 is connected to the motor of the drive unit 4 via the drive unit connector 211, and exchanges signals. That is, the drive signal is output from the mirror drive unit to the motor. Further, the motor is provided with detection means (not shown) for detecting the rotation speed, the rotation angle position, and the rotation load, and signals from these detection means are fed back to the mirror drive section.

A detection signal from a micro switch for detecting that the drive unit 4 is connected to the laser irradiation device 1 is input to the connection detection unit 236 via the drive unit connector 211.

A detection signal from the water temperature sensor 256 is input to the water temperature control unit 237, and the water temperature control unit 237 supplies the cooling element 252 with electric power for cooling in response to the detection signal. Therefore, it becomes possible to control the temperature of the circulating cooling water within a range suitable for treatment. Further, the water temperature control unit 237 can stop the power supply to the cooling element when the thermostat detects an excessively high temperature state of the cooling element 252. Furthermore, when the temperature of the cooling water is not suitable for treatment, for example, when the temperature of the cooling water is out of the range of 0 ° C. to 30 ° C.,
Irradiation with laser may be prohibited.
A detection signal from the water level sensor 257 is input to the water level detection unit 240, and it is possible to determine whether or not the required amount of cooling water is secured.

The flow rate control unit 238 is connected to the pump 258 and exchanges signals. That is, a drive signal is output from the flow rate control unit 238 to the pump 258, and a detection signal regarding the flow rate is fed back from the pump 258 to the flow rate control unit 238. Thereby, the flow rate of the cooling water can be controlled. As the pump 258, for example, a roller pump, a diaphragm pump, a magnet pump or the like can be used. A detection signal from a pressure sensor 259 that detects the water pressure in the water supply tube 272 is input to the pressure detection unit 239. Pressure sensor 259
By monitoring the detection result of 1., it is possible to prevent the cooling water from having an excessively high pressure, for example.

A signal from the foot switch 6 is input to the laser light source device control section 241 via the foot switch signal input connector 214. The laser light source device control unit 241 outputs a signal for outputting laser light to the laser light source device 3 via the foot switch signal cable 291 as necessary. In addition, when a signal from the interlock switch 7 is input via the interlock switch signal input connector 217, the laser light source device control unit 241 causes the interlock switch signal cable 2
Via 92, a signal for stopping the output of the laser light is output to the laser light source device 3. Interlock switch 7
Outputs a signal for outputting a signal for stopping the operation of the laser light source device 3, for example, in conjunction with the door of the laser management area being opened.

The display / operation input section 242 turns on the abnormality notification indicating lamp 202 when a predetermined abnormal situation occurs,
A signal to operate the abnormality notification buzzer 203 is output. The display / operation input unit 242 is connected to the user interface 205, and exchanges signals. That is, the display / operation input unit 242 outputs predetermined information to the user interface 205, and the user interface 205 outputs, to the display / operation input unit 242, a signal corresponding to, for example, a predetermined setting or operation by the operator. .

The data input / output unit 243 is connected to the media interface 204 and can input / output various information such as patient diagnostic information and heat treatment history via an external storage medium. There is. Note that it is also possible to directly connect to an external storage device to input / output information without using a medium.

In the case of using the heat treatment apparatus configured as described above, first, the lesion site of the patient is diagnosed in advance. Diagnosis of a lesion site is performed by, for example, optical endoscopy, ultrasonic endoscopy, X-ray imaging, magnetic resonance imaging (MRI), computer-assisted tomography (C) using X-rays or magnetic resonance.
T; computed tomography), positron emission tomography (P
ET; positron emissiontomography), single photon emission computed tomography (SPECT)
n emission computed tomography).

Then, for example, the image information around the lesion site obtained by previously diagnosing the patient is FD
It is input from the media interface 204 via the above. The input image information around the lesion site is displayed on the user interface 205. The operator determines a target site 1101 which is a target heating site from the displayed lesion site, and the user interface 205
The information about the target part 1101 is input through.

The control body 2 plans the treatment condition based on the target site 1101 determined by the operator,
The recommended value of the treatment condition is displayed on the user interface 205. The surgeon refers to the recommended value and sets the output condition of the laser light as the treatment condition using the setting dials 302a to 302c of the laser light source device 3.

The output condition of the laser beam as the treatment condition is
For example, a laser output value, a laser output time, etc. As the other treatment conditions such as the temperature of the cooling water, the flow rate of the cooling water, and the moving speed of the laser emitting portion, general values in the heat treatment are adopted.

Further, the control unit 251a includes the drive unit 4
When it is determined from the rotation speed, the rotation angle position, the detection signal of the rotation load, etc. fed back from the motor of the motor that there is a stop of the motor or the deviation of the command value exceeds a predetermined allowable range, the laser light source device 3 Stop the operation. Further, the control unit 251a includes the drive unit 4
Even if it is determined from the detection signal of the micro switch that the drive unit 4 is not securely connected to the laser irradiation device 1, the operation of the laser light source device 3 is stopped. In this way, it is possible to irradiate the laser beam toward the lesion site while surely reciprocating the laser emitting section 122 at a predetermined frequency.

If an abnormal state occurs during heating treatment, for example, when the door of the laser control area is opened, the interlock switch operates and the control section 251a is activated.
Stops the operation of the laser light source device 3. Control unit 251
a is also another sensor in the heat treatment device,
The signals from the microswitch, the thermostat, etc., and the operating state of each part are monitored, and the operation of each part in the heat treatment apparatus such as the laser light source device 3 is controlled as necessary.

The general structure of the heat treatment apparatus according to the present invention is as described above. Next, an embodiment of the present invention will be described based on the flowcharts of FIG. 8 and subsequent figures. (Embodiment 1) FIG. 8 is a flowchart showing the processing of Embodiment 1 of the heat treatment apparatus according to the present invention. In this flowchart, the one shown on the left side shows the operating procedure of the operator, and the one shown on the right side shows the control procedure processed by the control unit 251a.

In this embodiment, before the laser irradiation is started (while the foot switch is OFF), the flow rate of the cooling water is set to 50 ml / min and the laser irradiation is started (the foot switch is turned on). (While is ON), the flow rate of cooling water is set to 250 ml / min. That is, when the laser irradiation is not performed, the flow rate of the cooling water is smaller than the flow rate of the cooling water when the laser irradiation is performed.

First, the operator inserts the insertion section 121 into, for example, the urethra, and sets the laser emission section 122 at the target site 1101 of the biological tissue (S1). Flow controller 258
Controls the flow rate of the cooling water to 50 ml / min (S
2). As described above, if the flow rate is reduced before the laser irradiation is started, the operator receives the target region 1101.
Even if it takes time to position the living body around the insertion part 121, the living tissue around the insertion part 121 can be protected from being supercooled.
The patient does not feel discomfort or discomfort due to supercooling. In particular, it is very effective when the temperature of the cooling water is low (0 ° C to 10 ° C).

When the positioning on the target site 1101 is completed, the operator turns on the foot switch 6 (S
3). When the foot switch 6 is turned on, an instruction to start laser irradiation is output. Upon receiving this instruction (S4), the CPU 231 turns on the idling timer (S5). The flow rate control unit 258 controls the flow rate of the cooling water to 50 m.
Increase from 1 / min to 250 ml / min (S
6). This idling timer is a timer formed as software by the CPU 231, and its set time is set between 1 second and 120 seconds, preferably between 1 second and 10 seconds.

When a predetermined time has passed since the idling timer was turned on (S7), the idling timer is turned off (S8), and the laser light source device controller 241 starts laser irradiation (S9). In addition, the foot switch 6 is O
The laser irradiation is started after a predetermined time has elapsed since the flow of N was changed when the flow rate of the cooling water is 50 to 250 ml.
This is because there is a time lag before the temperature rises to 0, and the laser irradiation is performed after the flow rate of the cooling water is completely stabilized at 250 ml / min.

As described above, if the flow rate of the cooling water is increased during the laser irradiation, the target portion 1101
In the surroundings, in other words, it is possible to effectively cool the portion other than the living tissue irradiated with the laser, and the target portion 11
01 treatment can be effectively performed.

When the laser irradiation to the target region 1101 is completed, the operator turns off the foot switch 6 (S10). When the foot switch 6 is turned off (S1
1), the laser light source device controller 241 ends the laser irradiation (S12).

When the scheduled laser irradiation of all irradiation points is completed (S13: YES), the control section 251a.
Ends the laser irradiation process. On the other hand, if irradiation at all planned irradiation points has not been completed (S1
3: NO), the flow rate control unit 258 sets the flow rate of the cooling water to 25
It is lowered from 0 ml / min to 50 ml / min and the foot switch 6 is turned on. When the laser irradiation of one target region 1101 is completed, the operator determines whether or not there is another region where laser irradiation must be performed (S14). If the part to be irradiated next is the same as the previous irradiation position (S15: YE
S), turn on the foot switch 6 without moving the insertion section 121.
N On the other hand, when the part to be irradiated next is different from the irradiation position of the previous time (S15: NO), the insertion part 121 is moved to set the laser emission part 122 to the next target part 1101 and the foot switch 6 is set. Turn on.

As described above, in the present embodiment, the flow rate of the cooling water is set to 250 ml / min only after the foot switch 6 is turned on until it is turned off, and otherwise the flow rate of the cooling water is set to 50 ml / min. It is set to min.

In the above flow chart, the flow of the cooling water is simply waited for from the time the idling timer is turned on to the time it is turned off, but the foot switch 6 is turned off during the waiting. Sometimes
The operation may be accepted as an interrupt and the laser irradiation process may be ended.

Further, in this embodiment, the case where the flow rate of the cooling water when the laser irradiation is not performed is set to 50 ml / min is exemplified, but this flow rate is 0 to 100 ml / m.
It can be appropriately selected within the range of in. Also, the flow rate of the cooling water during laser irradiation is 250 ml / m
Although the case where the flow rate is set to in is illustrated, this flow rate is 150 to 35
It can be appropriately selected within the range of 0 ml / min. (Embodiment 2) FIG. 9 is a flowchart showing the processing of Embodiment 2 of the heat treatment apparatus according to the present invention. Also in this flowchart, the one shown on the left side shows the operation procedure of the operator, and the one shown on the right side shows the control procedure processed by the control unit 251a.

In this embodiment, in addition to the operation of the first embodiment, the temperature sensor 113a, 113b or the temperature sensors 503a to 503e are used to make the target part 1
When it is detected that the temperature of 101 and its vicinity are higher than the predetermined temperature, the flow rate of the cooling water is 2
The laser irradiation is forcibly stopped while keeping the flow rate at 50 ml / min.

First, the operator inserts the insertion section 121 into, for example, the urethra, and sets the laser emission section 122 at the target site 1101 of the biological tissue (S1). Flow controller 258
Controls the flow rate of the cooling water to 50 ml / min (S
2). When the positioning to the target site 1101 is performed, the operator turns on the foot switch 6 (S3). C
When the foot switch 6 is turned on, the PU 231 operates (S
4) Turn on the idling timer (S5). The flow rate control unit 258 increases the flow rate of the cooling water from 50 ml / min to 250 ml / min (S6). When a predetermined time has passed since the idling timer was turned on (S
7), the idling timer is turned off (S8), and the laser light source device control unit 241 starts laser irradiation (S).
9).

When the laser irradiation is started, the temperature measuring unit 23
3 inputs detection signals from the temperature sensors 113a and 113b or the temperature sensors 503a to 503e (S).
10). When the temperature around the target portion 1101 detected by these temperature sensors exceeds the upper limit value of the preset temperature (S11: YES),
The laser light source device control unit 241 controls the target part 110.
In order to prevent overheating of No. 1, laser irradiation is forcibly stopped (S12). Then, the temperature sensor 11 continues.
3a, 113b, or temperature sensors 503a to 503.
The detection signal from e is input (S13), and while the detected temperature exceeds the upper limit value (S14: YES), 250
Wait for the temperature to drop while maintaining the flow rate of cooling water of ml / min. By this control, the target site 1
It is possible to minimize thermal damage to the living tissue 101 or the vicinity thereof. If the detected temperature becomes lower than the upper limit value (S14: NO), once set the flow rate to 50 ml.
/ Min, and waits for the foot switch 6 to be turned on.

When the laser irradiation to the target region 1101 is completed, the operator turns off the foot switch 6 (S15). When the foot switch 6 is turned off (S1
6), the laser light source device control unit 241 ends the laser irradiation (S17). When the laser irradiation of all the planned irradiation points is completed (S18: YES), the control unit 2
51a ends the laser irradiation process. On the other hand, if the scheduled irradiation of all irradiation points has not been completed (S18: NO), the flow rate control unit 258 reduces the flow rate of the cooling water from 250 ml / min to 50 ml / min, and the foot switch 6 operates. Wait for it to be turned on. When the laser irradiation of one target region 1101 is completed, the operator determines whether or not there is another region where the laser irradiation should be performed (S19). If the next irradiation site is the same as the previous irradiation position (S
20: YES), the foot switch 6 is turned on without moving the insertion portion 121. On the other hand, if the next irradiation site is different from the previous irradiation position (S20: N
O), the insertion part 121 is moved to set the laser emission part 122 to the next target part 1101.

As described above, in the present embodiment, the flow rate of the cooling water is set to 250 ml / min from when the foot switch 6 is turned on to when it is turned off, and even when the temperature detected by the temperature sensor becomes high. , The cooling water flow rate is 25
Laser irradiation is forcibly stopped while maintaining 0 ml / min.

In this embodiment, the case where the flow rate of the cooling water is 250 ml / min has been illustrated, but this flow rate can be appropriately selected within the range of 150 to 350 ml / min. (Embodiment 3) FIG. 10 is a flow chart showing the processing of Embodiment 3 of the heat treatment apparatus according to the present invention.
Also in this flowchart, the one shown on the left side shows the operation procedure of the operator, and the one shown on the right side shows the control procedure of the control unit 251a.

In this embodiment, in addition to the operation of the second embodiment, the temperature sensor 113a, 113b or the temperature sensors 503a to 503e are used to make the target part 1
When it is detected that the temperature of 101 and its vicinity are higher than the predetermined temperature, the laser irradiation is forcibly stopped and the flow rate of the cooling water is increased from 250 ml / min to 350 ml / min. .

First, the operator inserts the insertion section 121 into, for example, the urethra, and sets the laser emission section 122 at the target site 1101 of the biological tissue (S1). Flow controller 258
Controls the flow rate of the cooling water to 50 ml / min (S
2). When the positioning to the target site 1101 is performed, the operator turns on the foot switch 6 (S3). C
When the foot switch 6 is turned on, the PU 231 operates (S
4) Turn on the idling timer (S5). The flow rate control unit 258 increases the flow rate of the cooling water from 50 ml / min to 250 ml / min (S6). When a predetermined time has passed since the idling timer was turned on (S
7), the idling timer is turned off (S8), and the laser light source device control unit 241 starts laser irradiation (S).
9).

When the laser irradiation is started, the temperature measuring unit 233
Inputs detection signals from the temperature sensors 113a and 113b or the temperature sensors 503a to 503e (S1).
0). When the temperature around the target portion 1101 detected by these temperature sensors exceeds the upper limit value of the preset temperature (S11: YES), the laser light source device control unit 241 causes the target portion 1101 to operate.
In order to prevent overheating, the laser irradiation is forcibly stopped (S12). Then, the flow rate control unit 258 changes the flow rate of the cooling water from 250 ml / min to 350 ml / min.
(S13). As a result, the temperature of the target site 1101 and the living tissue in the vicinity thereof is rapidly lowered, and thermal damage can be minimized. Then, the detection signals from the temperature sensors 113a and 113b or the temperature sensors 503a to 503e are input (S1).
4) While the detected temperature exceeds the upper limit value (S1
5: YES), wait for the temperature to drop while maintaining the flow rate of the cooling water of 350 ml / min. When the detected temperature becomes lower than the upper limit value (S15: NO), the flow rate control unit 258 changes the flow rate of the cooling water from 350 ml / min to 50%.
The flow rate is decreased to ml / min (S2), and the foot switch 6 is turned on again.

When the laser irradiation to the target region 1101 is completed, the operator turns off the foot switch 6 (S17). When the foot switch 6 is turned off (S1
8), the laser light source device controller 241 ends the laser irradiation (S19). When laser irradiation of all planned irradiation points is completed (S20: YES), the control unit 2
51a ends the laser irradiation process. On the other hand, if irradiation at all planned irradiation points has not been completed (S20: NO), the flow rate control unit 258 reduces the flow rate of the cooling water from 250 ml / min to 50 ml / min, and the foot switch 6 operates. Wait for it to be turned on. When the laser irradiation of one target site 1101 is completed, the operator determines whether or not there is another site where the laser irradiation should be performed (S21). If the next irradiation site is the same as the previous irradiation position (S
22: YES), the foot switch 6 is turned on without moving the insertion portion 121. On the other hand, if the part to be irradiated next is different from the irradiation position of the previous time (S22: N
O), the insertion part 121 is moved to set the laser emission part 122 to the next target part 1101.

As described above, in this embodiment, if the temperature detected by the temperature sensor is not high from the time the foot switch 6 is turned on to the time it is turned off, the flow rate of the cooling water is set to 250 ml / min, When the temperature detected by the sensor becomes high, the laser irradiation is forcibly stopped and the flow rate of the cooling water is increased to 350 ml / min.

In the present embodiment, the case where the flow rate of the cooling water is set to 350 ml / min is illustrated, but this flow rate can be appropriately selected within the range of 100 to 500 ml / min. (Embodiment 4) This embodiment is provided with two cooling units, a cooling unit that keeps cooling water at a temperature of about 20 ° C. and a cooling unit that keeps cooling water at a temperature of about 4 ° C. The assumption is that

In this embodiment, in addition to the operation of the third embodiment, the temperature sensor 113a, 113b or the temperature sensors 503a to 503e are used to make the target part 1
When it is detected that the temperature of 101 and its vicinity are higher than the predetermined temperature, the cooling water of 20 ° C. is switched to the cooling water of 4 ° C. to obtain a larger cooling effect.

FIG. 11 is a flowchart showing the processing according to the fourth embodiment of the heat treatment apparatus of the present invention. Also in this flowchart, the one shown on the left side shows the operation procedure of the operator. The one shown on the right side shows the control procedure of the control unit 251a.

First, the operator inserts the insertion part 121 into, for example, the urethra, and sets the laser emission part 122 to the target site 1101 of the biological tissue which is the irradiation position (S1). The flow rate control unit 258 is connected to a cooling unit that holds cooling water at 20 ° C., and the flow rate of the cooling water from there is 50 ml
/ Min (S2). Target part 1101
Is positioned, the surgeon operates the foot switch 6
Is turned on (S3). When the foot switch 6 is turned on (S4), the CPU 231 turns on the idling timer.
N (S5). The flow rate control unit 258 increases the flow rate of the cooling water from 50 ml / min to 250 ml / min (S6). When a predetermined time has passed since the idling timer was turned on (S7), the idling timer is turned off (S8), and the laser light source device controller 241 starts laser irradiation (S9).

When the laser irradiation is started, the temperature measuring unit 233
Inputs detection signals from the temperature sensors 113a and 113b or the temperature sensors 503a to 503e (S1).
0). When the temperature detected by these sensors exceeds the preset upper limit of the temperature (S
11: YES), the laser light source device control unit 241 forcibly stops laser irradiation in order to prevent overheating of the target portion 1101 (S12). Then, the flow rate control unit 258 switches the connection from the cooling unit holding the cooling water of 20 ° C. to the cooling unit holding the cooling water of 4 ° C. (S13). Furthermore, the flow rate control unit 258
Is a cooling water flow rate of 250 ml / min to 350 ml
/ Min (S14). As a result, the temperature of the target site 1101 and the living tissue in the vicinity thereof drops more rapidly than in the case of the third embodiment, and thermal damage can be minimized. Then, the temperature sensors 113a and 113b or the temperature sensor 503a.
The detection signal from ˜503e is input (S15), and while the detected temperature exceeds the upper limit value (S16: YE
S) Wait for the temperature to drop while keeping the flow rate of cooling water at 350 ml / min. When the detected temperature becomes lower than the upper limit value (S16: NO), the flow rate control unit 258.
This time, the connection is switched from the cooling unit holding the cooling water of 4 ° C. to the cooling unit holding the cooling water of 20 ° C. (S17). Then, the flow rate control unit 258
The cooling water flow rate from 350 ml / min to 50 ml / min.
It is lowered to min (S18), and the foot switch 6 is pressed again.
Wait for is turned on.

When the laser irradiation to the target region 1101 is completed, the operator turns off the foot switch 6 (S19). When the foot switch 6 is turned off (S2
0), the laser light source device controller 241 ends the laser irradiation (S21). When the laser irradiation at all irradiation points is completed (S22: YES), the control unit 251a ends the laser irradiation process. On the other hand, if the irradiation at all irradiation points has not been completed (S22: NO), the flow rate control unit 2
58 is a cooling water flow rate of 250 ml / min to 50 m
It is decreased to 1 / min, and the foot switch 6 is turned on. When the laser irradiation of one target region 1101 is completed, the operator determines whether or not there is another region where the laser irradiation should be performed (S23).
If the part to be irradiated next is the same as the previous irradiation position (S24: YES), the foot switch 6 is turned on without moving the insertion part 121. On the other hand, when the part to be irradiated next is different from the irradiation position of the previous time (S24: NO), the insertion part 121 is moved to set the laser emission part 122 to the next target part 1101.

As described above, in the present embodiment, if the temperature detected by the temperature sensor is not high from the time the foot switch 6 is turned on to the time it is turned off, cooling water at 20 ° C. is supplied at a flow rate of 250 ml / min. When the temperature is supplied and the temperature detected by the temperature sensor becomes high, the laser irradiation is forcibly stopped and the cooling water at 4 ° C. is supplied at a flow rate of 350 ml / min.

In this embodiment, the normal cooling is 2
Although cooling water of 0 ° C. was used, the temperature can be appropriately selected within the range of 7 ° C. to 30 ° C. Also, cooling water at 4 ° C was used for cooling at abnormal times, but the temperature was 0 ° C to 15 ° C.
Can be appropriately selected within the range.

In this embodiment, the case where two cooling units are provided to supply the cooling water having different temperatures has been described as an example, but the cooling water can be rapidly raised and lowered from one cooling unit. Cooling water having different temperatures may be supplied via the water temperature controller.

[0103]

As described above, according to the present invention,
The flow rate of the cooling liquid is increased when the energy is being irradiated, and the flow amount of the cooling liquid is decreased when the energy is not being irradiated, so that the patient does not feel discomfort or discomfort due to overcooling, and effective heat treatment can be performed. become able to.

When the temperature of the living tissue adjacent to the emitting portion and the temperature in the vicinity thereof become higher than the specified value, the irradiation of energy is forcibly stopped without reducing the flow rate of the cooling liquid. The temperature in the vicinity can be rapidly lowered, and the treatment of the lesion site will not be adversely affected.

When the temperature of the living tissue adjacent to the emitting portion and the vicinity thereof become higher than the specified value, the irradiation of energy is forcibly stopped and the flow rate of the cooling liquid is increased. The temperature can be rapidly lowered, and the treatment of the lesion site is not adversely affected.

When the temperature of the living tissue adjacent to the emitting portion and the vicinity thereof become higher than the specified value, the irradiation of energy is forcibly stopped and the cooling liquid having a low temperature is supplied at a high flow rate. Therefore, the temperature of the living tissue and its vicinity can be rapidly lowered, and the treatment of the lesion site is not adversely affected.

[Brief description of drawings]

FIG. 1 is a side view of a laser irradiation apparatus applied to a heat treatment apparatus according to the present invention.

FIG. 2 is a cross-sectional view for explaining a usage example of a laser irradiation device.

FIG. 3 is a cross-sectional view showing an example in which the heat treatment apparatus is used for treating the prostate.

FIG. 4 is a diagram showing an overall configuration of a heat treatment apparatus.

5A and 5B are diagrams showing a control main body and a laser light source device, FIG. 5A being a front view, FIG. 5B being a side view, and FIG.

FIG. 6 is a view showing a cooling unit built in a control body.

FIG. 7 is a diagram illustrating details of a control unit provided inside the control body.

FIG. 8 is a flowchart showing a process of the first embodiment of the heat treatment apparatus according to the present invention.

FIG. 9 is a flowchart showing the processing of the second embodiment of the heat treatment apparatus according to the present invention.

FIG. 10 is a third embodiment of the heat treatment apparatus according to the present invention.
It is a flowchart which shows the process of.

FIG. 11 is a fourth embodiment of the heat treatment apparatus according to the present invention.
It is a flowchart which shows the process of.

[Explanation of symbols]

1 ... Laser irradiation device, 3 ... Laser light source device, 6 ... foot switch, 113a, 113b ... Temperature sensor, 121 ... insertion part, 122 ... laser emitting part, 238 ... Flow rate control unit, 241 ... Laser light source device control unit, 251a ... Control unit, 503a to 503e ... Temperature sensors.

Continued front page    (72) Inventor Wataru Kano             1500 Inoguchi, Nakai-cho, Ashigarakami-gun, Kanagawa Prefecture             Terumo Corporation (72) Inventor Satoshi Sakaguchi             1500 Inoguchi, Nakai-cho, Ashigarakami-gun, Kanagawa Prefecture             Terumo Corporation (72) Inventor Taisuke Sato             2-43 Hatagaya, Shibuya-ku, Tokyo Ori             Inside Npus Optical Industry Co., Ltd. (72) Inventor Norihiko Haruyama             2-43 Hatagaya, Shibuya-ku, Tokyo Ori             Inside Npus Optical Industry Co., Ltd. (72) Inventor Takefumi Uesugi             2-43 Hatagaya, Shibuya-ku, Tokyo Ori             Inside Npus Optical Industry Co., Ltd. F-term (reference) 4C026 AA01 AA04 BB04 BB07 BB08                       DD03 DD06 FF34 GG02 GG03                       GG07 HH02 HH07 HH13 HH15                       HH24                 4C060 EE21 MM24 MM26

Claims (9)

[Claims] 1. An energy generating means for generating energy for irradiating a living tissue, an instructing means for instructing generation of the energy, and an energy irradiation for guiding the energy from the energy generating means and irradiating the living tissue. Means, a cooling liquid supply means for supplying a cooling liquid to a cooling liquid passage provided in the energy irradiating means, and when the generation of the energy is not instructed, the flow rate of the cooling liquid is the generation of the energy. And a control means for controlling the cooling liquid supply means so as to be smaller than the flow rate of the cooling liquid when instructed. 2. The control means further has a function of controlling the energy generation means such that, when the energy generation is instructed by the instruction means, the biological tissue is irradiated with energy after a lapse of a certain time. The heat treatment apparatus according to claim 1, wherein the heat treatment apparatus is a heat treatment apparatus. 3. An energy generating means for generating energy for irradiating a living tissue, an energy irradiating means for guiding the energy from the energy generating means and irradiating the living tissue, and the energy irradiating means. Cooling liquid supply means for supplying a cooling liquid to a cooling liquid flow path, temperature detecting means for detecting a temperature of living tissue adjacent to the energy irradiating means or its vicinity, and living tissue adjacent to the energy irradiating means or its vicinity And a control means for forcibly stopping the generation of the energy without changing the flow rate of the cooling liquid when the temperature exceeds the preset temperature. 4. An energy generating means for generating energy for irradiating a living tissue, an energy irradiating means for guiding the energy from the energy generating means and irradiating the living tissue, and the energy irradiating means. Cooling liquid supply means for supplying a cooling liquid to a cooling liquid flow path, temperature detecting means for detecting a temperature of living tissue adjacent to the energy irradiating means or its vicinity, and living tissue adjacent to the energy irradiating means or its vicinity When the temperature exceeds the preset temperature, the cooling liquid supply means is controlled so that the flow rate of the cooling liquid becomes larger than the flow rate of the cooling liquid when the temperature does not exceed the preset temperature. And a control means for forcibly stopping the generation of the energy. Care unit. 5. An energy generating means for generating energy for irradiating the living tissue, an energy irradiating means for guiding the energy from the energy generating means to irradiate the living tissue, and the energy irradiating means. Cooling liquid supply means for selectively supplying cooling liquids of different temperatures to the cooling liquid flow path, temperature detecting means for detecting temperature of living tissue adjacent to the energy irradiating means or its vicinity, and adjacent to the energy irradiating means When the temperature of the living tissue or its vicinity exceeds a preset temperature, the cooling liquid having a temperature lower than the temperature of the cooling liquid when the temperature does not exceed the preset temperature is preset. The cooling liquid supply means is controlled so that the cooling liquid is supplied at a flow rate higher than that when the temperature is not exceeded. To together, thermal treatment apparatus, characterized in that and a control means for forcibly stopping the generation of said energy. 6. The heat treatment apparatus according to claim 1, wherein the energy irradiation means is a long insertion part that can be inserted into a living body. 7. The insertion unit emits the energy, a moving unit for moving the emission unit back and forth in the longitudinal direction of the insertion unit, and the energy emission along with the movement of the emission unit. The heat treatment apparatus according to claim 6, further comprising: interlocking means for changing an angle. 8. The heat treatment apparatus according to claim 1, wherein the cooling liquid supply unit circulates the cooling liquid in the cooling liquid flow path. 9. The heat treatment apparatus according to claim 1, wherein the energy is laser light.