JPH04150872A - Hiper thermia apparatus - Google Patents

Abstract

PURPOSE:To make it possible to confirm radiation of electromagnetic wave and to perform surely heat therapy of a diseased part by providing a receiving antenna and an information device which is actuated by means of the electromagnetic wave received on the receiving antenna and informs receiving the electromagnetic wave. CONSTITUTION:When it is confirmed by means of an information window that a probe 2 is normal, an oscillator 13 is stopped and the probe 2 is inserted into a hollow organ of a patient and a radiating part 4 is positioned at a diseased part. As a diameter of the probe 2, such a diameter that the outer periphery of the probe 2 is tightly adhered with the wall of the hollow organ is selected. After it is confirmed by means of X-rays etc., that the radiating part 4 is fixed at the diseased part, driving of a cooling element 6 is input from an input part 16. The neighborhood of the diseased part is cooled by driving the cooling element 6. Blood vessels in the neighborhood of the diseased part are shrunk thereby to make bloodstream weak and the amt. of the bloodstream flowing at the diseased part is decreased by shrinking the blood vessel to suppress cooling caused by the bloodstream when the diseased part is heated and to attempt to improve heating effect of the diseased part by means of the electromagnetic wave.

Description

DETAILED DESCRIPTION OF THE INVENTION [Field of Industrial Application] The present invention relates to a hyperthermia device that performs thermotherapy by emitting electromagnetic waves to a lesion.

[Prior Art] Conventionally, as a hyperthermia device that heats a lesion using electromagnetic waves, those shown in Japanese Patent Laid-Open No. 61-50568, Japanese Patent Publication No. 2-16150, and the like are known.

The main structure of the conventional hyperthermia device is as shown in Fig. m12. That is, the iperthermia device 100 consists of a device main body 101 and an applicator 102, and the device main body 101 includes an oscillator 103 that oscillates electromagnetic waves.
, a power meter 104 that measures the power of the electromagnetic waves output from the oscillator 103, and a matching circuit 105 that adjusts the matching state with the applicator 102. Further, the applicator 102 is connected to the device main body 101 by a transmission cable 106.

Then, the electromagnetic waves output from the oscillator 103 are transmitted to the power meter 104, the matching circuit 105, and the transmission cable 10.
6 to the applicator 102, and is radiated to the lesioned area from an electromagnetic wave emitting section (not shown) provided in the applicator 102, thereby performing thermal treatment.

[Problem to be solved by the invention] By the way, the conventional hyperthermia device has a main body 1
The electromagnetic wave output from the oscillator 103 provided in the applicator 101 can only be known by the power meter 104, and there is no means for knowing whether the electromagnetic wave is reliably radiated from the electromagnetic wave emitting part of the applicator 102.

Therefore, when thermal treatment is performed using a conventional hyperthermia device, for example, if there is a poor connection of the applicator 102 or a defect in the applicator 102 itself, sufficient electromagnetic waves will be emitted from the electromagnetic wave emitting part of the applicator 102. Since the power meter 104 measures the electromagnetic waves output from the oscillator even though no radiation is emitted, the operator may assume that normal heating is being performed and proceed with the treatment. . Therefore, electromagnetic waves are not sufficiently radiated from the electromagnetic wave emitting part of the applicator 102, and not only is the lesion area not sufficiently treated, but also excessive reflection of electromagnetic waves occurs, making it necessary to use the oscillator 103, etc. It had become.

The present invention has been made in view of the above-mentioned circumstances, and its purpose is to be able to confirm that electromagnetic waves are being emitted from the electromagnetic wave emitting part, and to reliably perform heating treatment on the affected area using electromagnetic waves. The purpose of the present invention is to provide a hyperthermia device.

C Means for Solving Problems] In order to solve the above problems, the present invention provides a hyperthermia device that performs thermotherapy by heating a lesioned area with electromagnetic waves emitted from an electromagnetic wave emitting part. The apparatus is provided with a receiving antenna that receives electromagnetic waves received by the receiving antenna, and a notification means that is operated by the electromagnetic waves received by the receiving antenna to notify that the electromagnetic waves have been received by the receiving antenna.

[Operation] A part of the electromagnetic waves radiated from the electromagnetic wave radiating section is received by the receiving antenna, and the information is notified to the operator by the notification means.

[Example] FIG. 1 shows a first embodiment of the invention.

The hyperthermia device 1 consists of a device main body 18 and a probe 2 for radiating electromagnetic waves to a lesion. A connector 19 is provided at the rear end of the probe 2, and the probe 2 is detachably connected to the apparatus main body 18 via this connector 19.

The device body 18 includes an oscillator 13 that generates microwaves (hereinafter referred to as MW), a matching circuit 12 that adjusts the matching state with the probe 2, a control section 15, and an input section 16, and the MW of the oscillator 13. The output is controlled by the control unit 15 to the output input at the input unit 16, and the matching state of the matching circuit 12 is also controlled by the control unit 15, and the MW output from the oscillator 13 is controlled by the matching circuit 12. It can be supplied to the probe 2.

Note that the device main body 18 also includes a temperature display section 17, which will be described later.
and a cooling element drive circuit 14.

On the other hand, the main body of the probe 2 is formed of an insulating member, and a coaxial cable 3 is provided inside the probe 2 substantially coaxially with the probe 2. A radiating section 4 is provided at the tip of this coaxial cable 3, so that the MW from the oscillator 13 provided in the device main body 18 can be radiated from the radiating section 4 via the coaxial cable 3. . Also,
A coil-shaped receiving antenna 5 is provided at a portion inside the probe 2 that can receive the MW from the radiating section 4, for example, on the outer periphery of the radiating section 4, so as to be substantially coaxial with the radiating section. In this case, the MW radiated from the radiator 4 passes through the insulating member of the probe 2 and is received by the receiving antenna 5.

Further, in order to notify that the receiving antenna 5 has received the MW, the MW received by the receiving antenna 5 is transmitted to the rectifier circuit 11 provided at the base end of the probe 2 via a cable (not shown). The output of the rectifier circuit 11 is connected to a light emitting element 10 such as an LED, and the light emitted from the light emitting element 10 can be confirmed through a notification window 9 provided at the base end of the probe 2.

Further, a recess 8 is formed along the circumferential direction on the outer peripheral surface of the probe 2 at the front and rear parts of the radiation section 4.
A ring-shaped cooling element 6 having a cooling function, such as a Peltier element, is fitted onto the ring. This cooling element 6 has an outer diameter between the outer diameter of the probe 2 and the path,
By being fitted into the recess 8 and mounted, the outer circumferential surface of the cooling element 6 and the outer circumferential surface of the probe 2 are brought into contact with the road surface. The cooling element 6 is connected to a cooling element drive circuit 14 provided in the main body of the apparatus by a lead wire (not shown), and is controlled by a control section 15 so that the vicinity of the radiation section 4 can be cooled.

Further, a temperature sensor (not shown) is provided outside the radiation section 4 and the cooling element 6 on the surface of the probe 2. The temperature measured by the temperature sensor is then
The temperature is displayed on a temperature display section 17 provided at 8. Further, this measured temperature signal is input to the control section 15, and thereby the driving of the oscillator 13 and the cooling element driving circuit 14 is controlled. For example, if the temperature around the radiator 4 rises too much, the oscillator 13 is turned off, and if the surface of the cooling element 6 is not cooled, the cooling capacity of the cooling element drive circuit 14 is increased.

Note that the receiving antenna 5 is not limited to a coil shape, and may have an appropriate shape depending on the situation.

Next, the operation of the hyperthermia device 1 will be explained.

First, after connecting the device main body 18 and the probe 2 using the connector 19, a defect check is performed in which the oscillator 13 is oscillated with a certain output (for example, 10 W) in order to confirm the connection failure of the probe 2 and the failure of the probe 2 itself. Let's do it.

During this defect check, the MW oscillated from the oscillator 13 of the device main body 18 is transmitted to the radiating section 4 of the probe 2 via the coaxial cable 3 and radiated from the radiating section 4, but a part of this MW is transmitted to the receiving antenna. It will be received by 5. Therefore, when the MW is radiated from the radiator 4 and the receiving antenna 5 receives a part of the MW, the light emitting element 10 emits light, and this light emission is confirmed by the notification window 9. In addition, if a defective probe 2 or a poor connection occurs, the receiving antenna 5 may not receive the MW because the MW is not radiated from the radiating section 4, or the receiving antenna 5 may not receive the MW even if it is radiated. When only a small amount of MW is received, the light emitting element 10 does not emit light,
Or even if it does emit light, it will only emit a small amount of light.

In other words, by checking the light emitting state of the light emitting element 10, it is possible to confirm whether the probe 2 is defective or not, and thereby it can be determined whether the probe 2 can be used normally for heating treatment. It is something.

In addition, in the above defect check, M from the oscillator 13
The output of W is not particularly limited, but the output of probe 2
Considering the case where MW reflection occurs due to a defect, it is desirable to perform the operation at low output. In addition, if a defect check is performed each time at a certain output (automatically controlled so that the MW output is always a specific one) and compared with the previous light emission amount, it is possible to determine whether the probe 2 is defective depending on the light emission amount of the light emitting element 10. You can also check.

Next, when it is confirmed through the notification window 9 that the probe 2 is normal, the oscillator 13 is stopped, the probe 2 is inserted into the patient's luminal organ (for example, bile duct), and the radiation section 4 is positioned at the lesioned area. . The diameter of the probe 2 is selected so that the outer periphery of the probe 2 and the wall of the hollow organ come into close contact when it is inserted into the hollow organ. Then, the radiation part 4 of the probe 2
After confirming that the is fixed to the lesion using X-rays, etc.,
Drive of the cooling element 6 is inputted from the input section 16 . The vicinity of the lesion is cooled by driving the cooling element 6.

This causes the blood vessels around the lesion to constrict, slowing the blood flow, and by constricting the blood vessels near the lesion, the amount of blood flowing through the lesion decreases, and the blood flow cools the lesion when it is heated. It is possible to improve the heating effect of the affected area by electromagnetic waves.

After confirming the operation of the cooling element 6 by checking the temperature on the temperature display section 17, etc., the oscillator 13 is again caused to oscillate with the therapeutic output in order to warm the lesioned area. At this time as well, receiving antenna 5
A part of the MW is received by the light emitting element 10 and the light emitting element 10 emits light. However, if the MW is no longer emitted from the emitting part 4 for some reason during insertion of the probe 2 or during treatment, the light emitting element 10 stops emitting light. , to notify that a defect has occurred.

Further, when the probe 2 is normal, the light emitting element 10 continues to emit light from the start to the end of the treatment, and stops emitting light when the treatment time ends. Therefore, by stopping this light emission, it can be confirmed that the treatment has ended and the MW emission from the probe 2 has disappeared.

As explained above, according to the hyperthermia device 1 having the above configuration, a part of the MW radiated from the radiating section 4 is received by the receiving antenna 5, and the light emitting element 10 is caused to emit light by the electric power. By checking the presence or absence of light emission from the element 10, it can be confirmed that MW is being emitted from the radiation section 4, and reliable thermal treatment can be performed.

Therefore, it is possible to avoid an erroneous operation in which it is mistakenly recognized that MW is being emitted even though MW is not being emitted from the radiator 4 due to a poor connection or a defect in the probe 2 itself, and the treatment is performed as is. . In the unlikely event that the light emitting element 10 does not emit enough light, the connection state may be checked or the probe 2 replaced, and treatment may be performed after confirming that sufficient heating is achieved.

FIG. 2 shows a modification of the notification method using the light emitting device 10 of the first embodiment. The notification circuit 22 is a first
Similar to the figure, it has a receiving antenna 23 that receives MW, a rectifier circuit 25 that rectifies the power of the MW received by this receiving antenna 23, and a plurality of light emitting elements 29, 30° 31 connected to this rectifying circuit 25. It consists of a notification section 24.

The notification unit 24 is constructed by connecting circuits with different light emission voltages in parallel, each including a resistor 32.33° 34, light emitting elements 29, 30.31, and voltage generation sources 26, 27.28.
are connected in series. Voltage source 26.27.28
is a power source that generates a voltage in the opposite direction to the voltage generated by the rectifier circuit 25, and the relationship in magnitude is voltage source 26<27<28. By the way, light emitting element 2
9. In order to emit light from 30.31, the rectifier circuit 25
A voltage source 26.2 whose output voltage generates a reverse voltage
The voltage must be greater than 7.28. Therefore, when the output voltage from the rectifier circuit 25 gradually increases,
Voltage relationship of voltage source (voltage source 26<27<28)
Therefore, the light emitting elements emit light in the order of 29.30.31.

Utilizing this fact, for example, when the receiving antenna 23 receives 10 W MW, the voltage obtained by the rectifier circuit 25 and the voltage of the voltage generation source 26 are made the same, and similarly the 20 W MW
Output voltage from rectifier circuit 25 and voltage source 27 during reception
If the output voltage from the rectifier circuit 25 and the voltage of the voltage generation source 28 are set to be the same when receiving a voltage of The number of light emitted from the light emitting element varies depending on the intensity of the MW emitted, and the approximate amount of MW radiation can be determined from this number of light emissions. That is, the light emitting element 2
If only 9 is emitting light, 10 is emitted from the radiation part 4.
This means that MW of W or more and 20W or less is being emitted.
In addition, if the light emitting element 30 emits light, it is 20W or more.
This means that a MW of less than W is being emitted.

In addition, looking at the MW radiation distribution, when the MW output is small, only the vicinity of the probe is heated, and as the MW output is increased, the heating distribution tends to gradually expand toward the deeper part. , the heating distribution in the deep direction can be approximately predicted by the light emitting condition of the light emitting element 29°30.31.

For example, if the light emitting element 31 is emitting light, it has been heated to about 2 marks in the deep direction. Further, if the light is emitted only up to the light emitting element 29, it can be estimated that the heating range is approximately 0.5 cm in the depth direction.

Therefore, by creating a series of relationships between the voltage obtained by the rectifier circuit 25 based on the received MW and the voltages of the voltage generation sources 26, 27, 28, the notification circuit 2 of this modification example
2 is not only to check whether MW is being radiated from the radiating part 4, but also to check the degree of the output strength of the MW being radiated from the radiating part 4 and the approximate depth direction heated by the MW. In some cases, it is possible to control the MW output so that appropriate heating is performed for treatment while checking the light emission status of the light emitting elements 29, 30, 31. .

3 and 4 show a second embodiment of the invention. Note that in the drawings of each embodiment below, parts common to those in FIG.

The hyperthermia device 37 shown in FIG.
8, and a probe 39 that is inserted into a hollow organ and emits MW.

The oscillator 13 provided within the device main body 38 is connected to the probe 39 via a directional coupler 51. Further, the directional coupler 51 is connected to an attenuator 50 that attenuates the MW. The low MW transmission directionality of the directional coupler 51 allows MW to pass from the oscillator 13 side to the probe 39 side, but not from the probe 39 side to the oscillator 13 side, and all MW from the probe 39 side is passed through the attenuator 50. It is designed to be passed to the side. Further, there is no low MW transmission from the oscillator 13 side to the attenuator 50 side or from the attenuator 50 side to the oscillator 13 side. In other words, the MW output from the oscillator 13 is transmitted only to the probe 39 side by the directional coupler 51,
All of the MW reflected within the probe 39 is transferred to the directional coupler 5.
1 and is transmitted to the attenuator 50 side and consumed within the attenuator 50. Therefore, since the attenuator 50 and the probe 39 are not matched, the reflected wave from the probe 39 side flows to the oscillator 13 side, and the oscillator 1
It is possible to avoid the situation where 3 is heated and recommended.

Further, the coil-shaped receiving antenna 5 provided at the tip of the probe 39 is connected to a detection circuit 49 provided within the device main body 38 by a transmission cable (not shown). The detection circuit 49 detects the MW received by the reception antenna 5, and the signal is amplified by the amplifier circuit 47. The signal amplified by the amplifier circuit 47 is output to a power meter 48 and a comparison circuit 46. The power meter 48 is displayed in watts to confirm how much MW is being output from the radiation section 4. The comparison circuit 46 is connected to the input section 16
The MW output setting value inputted in is compared with the MW output value of the radiating section 4 outputted from the amplifier circuit 47,
A comparison result signal is output for 5. Based on this comparison result signal, the control section 15 controls the oscillation state of the oscillator 13 so that the MW output value from the radiating section 4 and the MW setting value inputted at the input section 16 match.

On the other hand, balloons 40 and 40 are provided on the outer periphery of the probe 39 at the front and rear of the radiation section 4. Furthermore, a balloon expansion conduit 41 for expanding the balloon 40° 40 is provided within the probe 39. This balloon expansion conduit 41 has its proximal end connected to an expansion pump 45 provided within the device main body 38, and its distal end branched into each balloon 40, 40. Balloon 40.40 is
It is expanded by a liquid such as physiological saline sent from the expansion pump 45 so as to expand with a strong force in the radial direction.

Further, a suction conduit 42 is provided within the probe 39 . The suction pipe line 42 has its proximal end connected to a suction pump 44 provided in the device main body 38, and its distal end branched and extends toward the outer periphery of the probe 39, and each extended distal end is connected to a balloon. Probe 3 between 40.40
9 is opened at the outer peripheral surface of the probe 39 so that the inner wall of the intrabody cavity channel into which the probe 39 is inserted can be sucked against the outer surface of the probe 39 between the balloons 40 and 40. In other words, it is possible to aspirate the inner wall of the intrabody cavity conduit and the like at a portion of the outer peripheral surface of the probe 39 where the radiation section 4 is located.

The expansion pump 45 and the suction pump 44 are each controlled by the control unit 15.
Its drive is controlled by In addition, a temperature sensor 43 such as a thermocouple is provided at the center of the radiation part 4 on the outer peripheral surface of the probe 39, which is thought to be heated most by the MW radiated from the radiation part 4, and the temperature is displayed. It is possible to display the image using the section 17.

Next, the operation of the hyperthermia device 37 will be explained.

First, the probe 39 is inserted into the hollow organ with the balloon 40 , 40 deflated, and the radiation section 4 is positioned at the lesion 52 . Then, the expansion pump 45 is driven to feed physiological saline into the balloon 40.40 via the balloon expansion circuit 41, thereby expanding the balloon 40.40. Once the probe 39 is fixed by expanding the balloon 40° 40, the suction pump 44 is operated and the suction line 42
As shown in FIG.
The tissue is brought into close contact with the area on the outer peripheral surface of the probe 39 where the radiation section 4 is located. Then, in this state, the oscillator 13 is operated by operating the input unit 16, and heating treatment of the lesioned area 52 is started.

By the way, the purpose of expanding the balloons 40, 40 is not only to fix the probe 39 to the lesion 52, but also to expand the tissue near the lesion 52 by expanding the balloons 40, 40. The aim is to compress the lesion, reduce the amount of blood flowing to the lesion, and reduce the cooling effect of the blood flow. In addition, the suction pipe 42 is connected to the lesion 5
By suctioning tissue near balloon 40.
40 further into the tissue to reduce blood flow and ensure that the lesioned area 52 is warmed.
It has the function of bringing the tissue of the lesion 52 into close contact with the probe surface.

Further, when the oscillator 13 is operated during the heating treatment, MW is radiated from the radiator 4 as in the first embodiment, and part of the MW is received by the receiving antenna 5, and its intensity is measured by the power meter. 48, the output value displayed on the power meter 48 is based on the MW output setting input from the input section 16, if there is no defect in the probe 39 itself or a poor connection. The value is almost the same as the value. Therefore, in this case, the operator can confirm that the MW is correctly radiated from the radiation section 4 and that the warming treatment is being sufficiently performed.

In addition, if a defect occurs in the probe 39 etc.,
Even though the oscillator 13 is operating, the radiation section 4
Since no MW is emitted from the power meter 48, the power meter 48 does not operate. Therefore, in this case, the operator
After confirming that the probe 39 is defective, the treatment is interrupted and the probe 39 is replaced.

The reason why the MW is not correctly radiated from the radiation section 4, that is, the MW output setting value inputted from the input section 16 and the output value displayed on the power meter 48 do not match is as follows.
There are other problems besides the probe 39 being defective. For example, this may occur if the probe 39 is poorly matched to the oscillator 13 or if the attenuation in the coaxial cable 3 is large. In such a case, MW is radiated from the radiation section 4, but the intensity of the radiated MW is a value smaller than the set output value of MW, so the power meter 48 also shows a MW output value smaller than the set value. is displayed, and the operator can calculate the MW required for treatment.
It is necessary to recognize that the output value is not obtained and try to take appropriate measures. In other words, the heating range and heating effect of the MW emitted from the radiation section 4 differs depending on its output value.As an operator, the set output is radiated from the radiation section 4, and depending on the output, the lesion is Since it is desirable that the part be heated, the user checks the power meter 48 and manually increases the output of the oscillator 13 in an attempt to make the output from the radiating part 4 equal to the set value.

However, in this embodiment, since the comparison circuit 46 compares the measured value and the set value and performs automatic control so that the measured value matches the set value, the oscillator 13 is manually operated.
There is no need to increase the output.

Of course, this can also be done manually.

At this time, it is possible that the output of the oscillator 13 increases unilaterally due to automatic control, and if the probe 39 is mismatched, the MW may be reflected excessively, but the reflected MW is attenuated by the attenuator 50, and therefore does not excite the oscillator 13. Therefore, even if the output from the radiating section 4 is controlled to be the same as the set value through automatic control, the oscillator will not be excited and any problems will not occur.

In addition, when the treatment is finished, the power meter 48 will also display OW.
is displayed, so the operator can confirm that the output from the radiation section 4 has stopped and that the heating by MW has definitely ended.

As explained above, according to the hyperthermia device 37 having the above configuration, the MW radiated from the radiating section 4 is displayed by the power meter 48, so that it is possible to not only check whether the probe 39 is defective, etc. The output of MW radiated from the radiation section 4 can be confirmed. Therefore, the intensity of the MW output from the radiation section 4 can be controlled to the output necessary for treatment. Further, in this embodiment, the directional coupler 51 separates the traveling wave (oscillator 13 - probe 39) from the reflected wave (probe 39 - oscillator 13), and the reflected wave is attenuated by the attenuator 5o. Therefore, even if the output of the oscillator 13 is increased and the output of the radiating section 4 is automatically controlled to a specific output, the oscillator 13 will not be used, and thermotherapy can be safely performed through automatic control. can.

5 to 7 show a third embodiment of the present invention.

As shown in FIG. 5, the hyperthermia device 53 consists of a device body 54 and a probe 56, as in each of the above embodiments.

The probe 56 has a space 60 therein, which has a ring-shaped longitudinal section and is formed coaxially with the probe 56 along the axial direction of the probe 56 .

In this space 60, the receiving antenna 5 is connected to the probe 5.
The receiving antenna 5 is housed coaxially with the receiving antenna 6, thereby allowing the receiving antenna 5 to move in the axial direction. Note that the space 60 is filled with, for example, physiological saline to prevent MW from passing through.

Further, an operating wire 58 is connected to the receiving antenna 5. The operating wire 58 can be moved in the axial direction of the probe 56 by operating an operating knob 57 of an operating section provided on the proximal end side of the probe 56.

Further, a compression ring 59 is fitted on the outer circumference of the probe 56 at the front and back of the radiation section 4 . The compression ring 59 is made of a shape memory alloy or the like, and has the property of being expandable by heating, for example.

Further, a heating element 61 is provided on the contact surface between the compression ring 59 and the probe 56. The heating element 61 is connected to the current-carrying portion 55 of the device main body 54 by a lead wire (not shown). The energizing section 55 is controlled by the control section 15, and when the energizing section 55 is energized, the heating element 61 generates heat, and this heat generation expands the diameter of the compression ring 59 so that the compression ring 59 separates from the probe 56. It has become.

Next, the operation of the hyperthermia device 53 will be explained.

First, before inserting the probe 56 into the treatment site, in order to check for defects in the probe 56, the receiving antenna 5 is adjusted to the outer peripheral position of the radiating section 4 by operating the operating knob 57. Then, the oscillator 13 is caused to oscillate, and the MW from the radiation section 4 is
The state of the probe 56 is checked.

Next, in order to perform the treatment, the probe 56 is inserted into the treatment site, the radiation section 4 is positioned at the lesion 52, and the probe 56 is fixed at the treatment site.

After fixing the probe 56, by operating the input section 16,
The heating element 61 starts to be energized. This energization causes the sixth
As shown in the figure, the diameter of the compression ring 59 expands, and the compression ring 59 embeds into the tissue near the lesion 52. Similar to the balloon 40 of the second embodiment 9, this is intended to reduce the amount of blood flow flowing through the lesion 52 and improve the warming effect by MW. After the compression ring 59 is expanded and moved away from the outer periphery of the probe 56, embedded in the tissue and fixed, the oscillator 13 is driven to start treatment. Note that at the start of this treatment, similarly to the second embodiment, the receiving antenna 5 receives the MW radiated from the radiating section 4, the power meter 48 displays the value, and the measured output and the set value are In this embodiment, when the MW ratio output set value from the radiating section 4 becomes the same as the MW ratio output setting value, the operation knob 57 is operated to control the MW output.
The receiving antenna 5 is pulled toward the base end from the outer circumferential position of the radiating part 4 and is shifted from the outer circumferential position of the radiating part 4 . This is because if a member such as the receiving antenna 5 is located outside the radiating section 4, it will disturb the MW radiation distribution to some extent, and the temperature distribution of a probe without a conventional receiving antenna. Therefore, after confirming that the required MW radiation amount has been obtained, an attempt is made to obtain a MW heating distribution similar to that of the conventional probe.

When the treatment is completed in the manner described above, only the probe 56 is removed from the treatment site, as shown in FIG. When the probe 56 is removed, a compression ring 59 is placed in the vicinity of the lesion 52, which always restricts the blood flow into the lesion 52, thereby suppressing the growth of the lesion tissue. Further, although the heat treatment is usually repeated many times after that, the indwelled compression ring 59 is used as the probe 56 during the heat treatment performed again.
It also serves as a positioning means when inserting. That is, the insertion of the probe 56 is performed while looking at, for example, an X-ray image, and at that time, the compression ring 59 is monitored so as to represent the range of the lesion 52, so the positioning of the probe 56 with respect to the lesion 52 is easy. This makes it easier.

As explained above, in the hyperthermia device 53 having the above configuration, only when it is desired to check the output of MW radiated from the radiating section 4, the receiving antenna 5 provided in the space 60 inside the probe 56 is connected to the radiating section using the operating wire 58. 4 on the outer periphery so that MW specific output can be measured. Therefore, when it is not necessary to measure the MW output, the receiving antenna 5 can be shifted from the radiating section 4 to perform the same heating as a conventional probe that does not have a receiving antenna. Therefore, the experience gained from treatment using conventional probes can be utilized as is.

8 and 9 show a fourth embodiment of the present invention.

The hyperthermia device 65 shown in FIG. 8 is an RF type device that performs thermal treatment by sandwiching an affected area between two electrodes.

The hyperthermia device 65 includes an in-body applicator 70 inserted into a body cavity, an extra-corporeal applicator 71 fixed outside the body, and a device main body 66 that performs oscillation and control of RF waves, etc.
It consists of.

The device main body 66 is provided with an oscillator 13 that generates RF waves, and the RF waves generated by the oscillator 13 are passed through the matching circuit 12.
The liquid is supplied to the extracorporeal applicator 71 and the intracorporeal applicator 70 via. Further, the extracorporeal applicator 71 and the intracorporeal applicator 70 are provided with temperature sensors (not shown), and each temperature sensor is connected to a temperature detector 68 provided within the device main body 66. Then, in response to the output of this temperature detector 68, the control section 15 activates the oscillator 13.
oscillation control.

The intracorporeal applicator 70 is provided with an internal electrode 72, and a receiving antenna 73 for receiving RF waves is provided on the outer periphery of the internal electrode 72. Further, a balloon 75 is provided around the outer periphery of the receiving antenna 73, and the inside of the balloon 75 is filled with physiological saline for cooling the surface of the heating section. This physiological saline is supplied to an internal pump 67 provided within the device main body 66.
is circulated by In addition, the internal applicator 70
A tissue compression roller 74 is provided in order to compress tissue in the vicinity of the lesion. As shown in FIG. 9, this compression roller 74 is divided into a plurality of parts in the circumferential direction when viewed from the distal end side of the internal applicator 70. This roller 7
4 is intended to increase the warming effect by compressing the blood vessels near the lesion, as in the second and third embodiments. This is to facilitate insertion into an organ. Note that physiological saline is also circulated within the extracorporeal applicator 71 by the extracorporeal pump 69 in order to cool the surface of the heating section.

Next, the operation of the hyperthermia device 65 will be explained.

First, in order to perform treatment, the intracorporeal applicator 70 is inserted into the treatment site. The internal electrode 72 is fixed to the lesion by operating the intracorporeal applicator 70. Further, outside the body, the extracorporeal applicator 71 is fixed to a portion facing the internal electrode 72. Then, the internal pump 67 and the external pump 69 are driven to circulate physiological saline through the respective applicators 70 and 71. In this state, the oscillator 13 is operated to start the heating treatment. At this time, the receiving antenna 73
The RF wave is received by the power meter 48, and the output value thereof is displayed on the power meter 48, and the comparison circuit 46 compares it with a set value. Then, the output of the oscillator 13 is controlled so that the measured value and the output of the set value match.

In this way, even with the RF method as shown in this embodiment, it is possible to check the intensity of the RF waves output for heating by, for example, providing the receiving antenna 73 on the intracorporeal applicator 70. can be used, and applicator 70.7
You can also confirm the defect in item 1. In addition, the receiving antenna 7
3 can also be provided in an extracorporeal applicator 71 to detect the output of the RF waves, as shown in FIG.

FIG. 11 shows a fifth embodiment of the present invention, in which a hyperthermia device 80 is capable of checking the output of a conventionally used MW probe 85 without a receiving antenna.

This hyperthermia device 80 consists of a device main body 81, a conventionally used MW probe 85 without a receiving antenna, and an antenna unit 82 for detecting the MW output.

The antenna unit 82 is provided with a probe insertion section 84 into which the MW probe 85 is inserted, and an antenna 83 which receives the MW output from the probe 85. Further, the antenna unit 82 itself is formed of an insulating part.

The antenna unit 82 is connected to the main body 81 of the apparatus, and the MW received by the antenna 83 is detected by the detection circuit 49.

Next, the operation of the hyperthermia device 80 having the above configuration will be explained.

First, before starting treatment, the MW probe 85 is inserted into the probe insertion portion 84 of the antenna unit 82. and,
The oscillator 13 of the device main body 81 is operated, and the MW small output antenna 83 receives the signal from the radiating section of the probe 85 at that time. The intensity of this received MW is determined by the power meter 4.
Similarly to the second to fourth embodiments, the MW output is controlled so that the measured value and the set value are the same. When the MW small output setting value of the probe 85 becomes the same, the device main body 81 stores the output of the oscillator 13 at that time and stops the output of the oscillator 13. At this point, the operator confirms that the probe 85 is in a normal state and that the output of the MW emitted from the probe 85 has been properly adjusted, and then moves the probe 85 to the lesion in order to start treatment. insert. If it does not match the small MW output setting value of the probe 85, that is, if it is confirmed that the probe 85 is defective, the probe is repaired or replaced.

Then, the probe 85 is fixed at the lesioned area, and the oscillator 13 is oscillated with the output value stored during the output adjustment to start the conventional treatment.

As explained above, the hyperthermia device 80 with the above configuration can check for defects even in the conventional probe 85, and starts treatment after always confirming the accurate MW output value, so it is the same as the conventional probe 85. A warming effect can always be obtained.

[Effects of the Invention] As explained above, according to the present invention, a part of the electromagnetic waves radiated from the electromagnetic wave radiating section is received by the receiving antenna, and the information is notified to the operator by the notification means. The operator can perform treatment after confirming that sufficient electromagnetic waves necessary for treatment are being emitted from the electromagnetic wave emitting section.

Therefore, the affected area will be reliably heated and treated by electromagnetic waves.

[Brief explanation of the drawing]

FIG. 1 is a schematic diagram of a hyperthermia device showing a first embodiment of the present invention. FIG. ti/42 is a circuit diagram showing a modification of the notification means of the hyperthermia device shown in FIG. Figures 3 and 384 show a second embodiment of the present invention, Figure 3 is a schematic configuration diagram of a hyperthermia device, and Figure 4 shows a state in which the probe of the hyperthermia device in Figure 3 is inserted into a lesion. It is a schematic sectional view. 5 to 7 show a third embodiment of the present invention;
The figure is a schematic diagram of the hyperthermia device, and Figure 6 is the 5th diagram.
FIG. 7 is a schematic cross-sectional view showing how the probe of the hyperthermia device is inserted into the lesion, and FIG. 7 is a schematic cross-sectional view showing how the compression ring is left in the lesion and the probe is removed. 8 and 9 show a fourth embodiment of the present invention, FIG. 8 is a schematic configuration diagram of an RF type hyperthermia device, and FIG. FIG. FIG. 10 is a cross-sectional view of an extracorporeal applicator with a receiving antenna. FIG. 11 is a schematic configuration diagram of a hyperthermia device showing a fifth embodiment of the present invention, and FIG. 12 is a schematic configuration diagram of a conventional hyperthermia device. 1.37.53, 65.80...Hyperthermia device, 4.72...Radiating part, 5,73.85...Receiving antenna, 9...Notification window, 10...Light emitting element, 48
...Power meter.

Claims (1)

[Claims] A hyperthermia device that performs thermotherapy by heating a lesioned area using electromagnetic waves emitted from an electromagnetic wave emitting part includes a receiving antenna that receives electromagnetic waves emitted from the emitting part, and an electromagnetic wave received by the receiving antenna. 1. A hyperthermia device comprising: a notification means that operates to notify that electromagnetic waves have been received by the receiving antenna.