JP3154716B2 - Hyperthermia device - Google Patents

Description

Description: BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a hyperthermia device that radiates electromagnetic waves to a lesion to perform thermal treatment.

2. Description of the Related Art Conventionally, as a hyperthermia device for heating a lesion using electromagnetic waves, Japanese Patent Application Laid-Open No.
Japanese Patent Application Laid-Open No. -16150 and the like are known.

The main configuration of the conventional hyperthermia device is as shown in FIG. That is, the hyperthermia device
100 includes an apparatus main body 101 and an applicator 102. The apparatus main body 101 has an oscillator 103 for oscillating electromagnetic waves, and
Power meter 1 for measuring the power of electromagnetic waves output from 3
04 and a matching circuit 105 for adjusting the matching state with the applicator 102. The applicator 102 is connected to the apparatus main body 101 by a transmission cable 106.

Then, the electromagnetic wave output from the oscillator 103 is transmitted to the applicator 102 via the power meter 104, the matching circuit 105, and the transmission cable 106, and the electromagnetic wave radiating portion (not shown) provided in the applicator 102 is applied to the lesion. By the radiation, the hyperthermia treatment is performed.

[Problems to be Solved by the Invention] By the way, a conventional hyperthermia device is a device main body.
Only the power of the electromagnetic wave output from the oscillator 103 provided in the 101 can be known by the power meter 104, and there is no means for knowing whether or not the electromagnetic wave is reliably radiated from the electromagnetic wave radiating portion of the applicator 102.

Therefore, when thermal treatment is performed using a conventional hyperthermia device, for example, if the connection of the applicator 102 is defective or the applicator 102 itself has a defect, sufficient electromagnetic waves are emitted from the electromagnetic wave radiating portion of the applicator 102. Power meter 10 despite no radiation
In Fig. 4, since the electromagnetic wave output from the oscillator was measured, the operator assumed that a normalization plan would have been made, and provided treatment as it was. Therefore, the electromagnetic wave is not sufficiently radiated from the electromagnetic wave radiating portion of the applicator 102, so that not only the treatment of the affected part is not sufficiently performed, but also excessive reflection of the electromagnetic wave occurs, and the oscillator 103 and the like are excited. I was

The present invention has been made by focusing on the above circumstances, and the purpose thereof is to confirm that electromagnetic waves are radiated from the electromagnetic wave radiating portion, and to perform the heating treatment of the affected part by the electromagnetic waves without fail. A hyperthermia device is provided.

[Means for Solving the Problems] In order to solve the above problems, a hyperthermia device of the present invention includes an oscillator that generates an electromagnetic wave, a radiating unit that radiates an electromagnetic wave output from the oscillator to an affected part, and the radiating unit. At a predetermined relative position with respect to a receiving antenna for receiving the electromagnetic wave radiated from the radiating section, a detecting means for detecting the electromagnetic wave received from the receiving antenna, and the oscillator based on a detection result of the detecting means. And a control unit for controlling the output of.

[Operation] According to the above configuration, the electromagnetic wave generated from the oscillator and radiated from the radiating section is received by the receiving antenna, and the received electromagnetic wave is detected by the detecting means.
The output of the oscillator is controlled based on the detection result.

FIG. 1 shows a hyperthermia device 1 to which the present invention can be applied.
Is shown.

The hyperthermia device 1 includes a device main body 18 and a probe 2 for emitting 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 the connector 19.

The device main body 18 includes an oscillator 13 for generating a microwave (hereinafter, referred to as MW), a matching circuit 12 for adjusting a matching state with the probe 2, a control unit 15 and an input unit 16. 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
Similarly, the MW controlled by the control unit 15 and output from the oscillator 13 can be supplied to the probe 2 via the matching circuit 12. In addition, the apparatus main body 18 also includes a temperature display unit 17 and a cooling element drive circuit 14 described later.

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 radiation section 4 is provided at the end of the coaxial cable 3, and MW from the oscillator 13 provided in the apparatus main body 18 can be radiated from the radiation section 4 via the coaxial cable 3. . Further, a coil-shaped receiving antenna 5 is provided substantially coaxially with the radiating portion on a portion inside the probe 2 where MW from the radiating portion 4 can be received, for example, on the outer periphery of the radiating portion 4. In this case, the MW radiated from the radiating section 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 a rectifier circuit 11 provided at the base end of the probe 3 by a cable (not shown). The output of the rectifier circuit 11 is
For example, the light emitting element 10 is connected to the light emitting element 10 such as an LED.
Can be confirmed through a notification window 9 provided at the base end of the probe 2.

A concave portion 8 is formed on the outer peripheral surface of the probe 2 along the circumferential direction at positions before and after the radiation portion 4, and a ring-shaped cooling element having a cooling function such as a Peltier element is formed in the concave portion 8. 6 is fitted and mounted. The outer diameter of the cooling element 6 is substantially the same as the outer diameter of the probe 2, and the outer peripheral surface of the cooling element 6 and the outer peripheral surface of the probe 2 are substantially It is becoming one. The cooling element 6 is connected to a cooling element drive circuit 14 provided in the apparatus main body by a lead wire (not shown), and is controlled by the control unit 15 so that the vicinity of the radiation unit 4 can be cooled.

Furthermore, the radiation part 4 and the cooling element 6 on the surface of the probe 2
Is provided with a temperature sensor (not shown).
The temperature measured by the temperature sensor is
The temperature is displayed on a temperature display section 17 provided in 18. Further, the signal of the measured temperature is input to the control unit 15, which controls the driving of the oscillator 13 and the cooling element drive circuit 14. For example, the oscillator 13 is turned off when the temperature of the outer periphery of the radiating section 4 is too high, and when the surface of the cooling element 6 is not cooled, the cooling capacity of the cooling element drive circuit 14 is increased.

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

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

First, after connecting the device main body 18 and the probe 2 with the connector 19, the connection failure of the probe 2 and the probe 2
To check your own faults, use a specific output (for example, 10
In W), a defect check for oscillating the oscillator 13 is performed.

At the time of this defect check, the MW oscillated from the oscillator 13 of the apparatus body 18 is transmitted to the radiating section 4 of the probe 2 by the coaxial cable 3 and is radiated from the radiating section 4.
A part of the MW is received by the receiving antenna 5. Therefore, when the MW is radiated from the radiating section 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, when the failure of the probe 2 or the connection failure occurs,
Since the MW is not radiated from the radiating section 4, the receiving antenna 5
When the MW is not received, or the MW is not so received, and the MW is received only slightly, the light-emitting element 10 does not emit light or emits only a small amount of light when the receiving antenna 5 receives only a small amount of MW. Becomes

That is, by checking the light emitting state of the light emitting element 10, a defect or the like of the probe 2 can be confirmed, whereby it can be determined whether the probe 2 can be normally used for the heating treatment. Things.

In the above defect check, the MW from the oscillator 13
Is not particularly limited. However, considering the case where the probe 2 has a defect and MW reflection occurs, it is desirable to perform the output at a low output. Also, a specific output (automatic control is required so that a specific MW output is always obtained.)
By performing a defect check every time, and comparing with the previous light emission amount, the defect state of the probe 2 can be confirmed by the light emission amount of the light emitting element 10.

Next, when the notification window 9 confirms that the probe 2 is normal, the oscillator 13 is stopped, the probe 2 is inserted into a luminal organ (for example, a bile duct) of the patient, and the radiating unit 4 is positioned at the lesion. . When the probe 2 is inserted into a luminal organ, the diameter of the probe 2 is such that the outer periphery of the probe 2 and the wall of the luminal organ are in close contact with each other. And the radiating section 4 of the probe 2
After confirming with X-rays and the like that the
The drive of the cooling element 6 is input from the input unit 16. Cooling element 6
Drives to cool the vicinity of the lesion. As a result, blood vessels around the lesion are contracted, causing blood flow to flow, and blood vessels near the lesion are contracted, thereby reducing blood flow through the lesion and cooling by blood flow when the lesion is heated. ,
The effect of heating the affected part by the electromagnetic wave can be improved.

After confirming the driving of the cooling element 6 by the temperature of the temperature display section 17 and the like, the oscillator 13 is again oscillated by the therapeutic output in order to heat the lesion. At this time, a part of the MW is received by the receiving antenna 5 and the light emitting element 10 emits light.
When the MW is not radiated from the radiating section 4 for some reason during the insertion of the probe 2 or during the treatment, the light emitting element 10 stops emitting light and notifies that a defect has occurred.

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 the light emission, it is possible to confirm a state in which the treatment is completed and the MW radiation from the probe 2 is stopped.

As described above, according to the hyperthermia device 1 having the above-described configuration, a part of the MW radiated from the radiating unit 4 is received by the receiving antenna 5 and the power is applied to the light emitting element.
Since the light emitting device 10 emits light, it is possible to confirm that the light emitting element 10 emits light, thereby confirming that MW is being emitted from the radiating unit 4, and to perform a reliable thermal treatment. Therefore, although MW is not radiated from the radiating section 4 due to a connection failure or a defect of the probe 2 itself,
By mistakenly recognizing that MW is being radiated, it is possible to avoid an erroneous operation of performing treatment as it is. If the light emitting element 10 does not emit light sufficiently, the treatment may be performed after confirming the connection state or exchanging the probe 2 and confirming the state of sufficient heating.

FIG. 2 shows a modification of the notification system using the light emitting element 10 of FIG. The notification circuit 22 includes a reception antenna 23 for receiving MW and a reception antenna
The rectifier circuit 25 includes a rectifier circuit 25 for rectifying the received MW power and a notification unit 24 connected to the rectifier circuit 25 and having a plurality of light emitting elements 29, 30, 31.

The notification unit 24 is configured by connecting circuits having different emission voltages in parallel, and the resistors 32, 33, 34 and the light-emitting elements 29, 30,
31 and voltage generators 26, 27, 28 are connected in series.
The voltage sources 26, 27, and 28 are power sources that generate voltages in the opposite direction to the voltage generated by the rectifier circuit 25, and the magnitude relationship is such that the voltage sources 26 <27 <28. by the way,
In order for the light emitting elements 29, 30, 31 to emit light, the output voltage from the rectifier circuit 25 must be higher than the voltages of the voltage sources 26, 27, 28 that generate the reverse voltage. Therefore, when the output voltage from the rectifier circuit 25 gradually increases, the light emitting element is activated by the voltage relationship of the voltage generation source (voltage generation source 26 <27 <28).
Light is emitted in the order of 29, 30, and 31.

Utilizing this, for example, a 10 W MW
3, the voltage obtained by the rectifier circuit 25 when receiving and the voltage of the voltage source 26 are made the same. Similarly, the output voltage from the rectifier circuit 25 and the voltage of the voltage source 27 and the voltage of 30 W when receiving MW of 20 W are received.
Output voltage from the rectifier circuit 25 and the voltage source 28 when receiving MW
And the same voltage, the intensity of the MW received by the receiving antenna 23, in other words, radiated from the radiating unit 4
The number of light emission of the light emitting element differs depending on the intensity of MW, and the approximate number of MW radiation can be known from the number of light emission. That is, if only the light emitting element 29 emits light, MW of 10 W or more and 20 W or less is emitted from the radiating section 4, and if the light emitting element 30 emits light, 20 MW or more 3
This means that less than 0 MW is being emitted.

Looking at the MW radiation distribution, if the MW output is small, only the vicinity of the probe is heated, and as the MW output increases, the heating distribution in the deeper direction tends to gradually spread. The heating distribution in the depth direction can be estimated approximately according to the light emitting condition of the light emitting elements 29, 30, 31. For example, if the light emitting element 31 emits light, it is heated to about 2 cm in the depth direction. Further, if only the light emitting element 29 emits light, it can be inferred that up to about 0.5 cm in the depth direction will be the heating range.

Therefore, by giving a series of relations between the voltage obtained by the rectifier circuit 25 by the received MW and the voltages of the voltage sources 26, 27, and 28, the notification circuit 22 of the present modification simply transmits the MW from the radiating unit 4 to the MW. It is possible to not only check whether or not the radiation is radiated, but also to estimate the degree of the intensity of the output of the MW radiated from the radiation section 4 and the approximate distribution in the depth direction heated by the MW. And, in some cases, light emitting devices
It is also possible to control the output of the MW so as to perform appropriate heating for the treatment while checking the light emission state of 29, 30, 31.

FIG. 3 and FIG. 4 show a first embodiment of the present invention. In the drawings of the embodiments, the same reference numerals are given to the same parts as those in FIG. 1, and the description thereof will be omitted.

The hyperthermia device 37 shown in FIG. 3 includes a device main body 38 for generating and controlling MW and a probe 39 inserted into a luminal organ and radiating MW, as in FIG.

The oscillator 13 provided in the device main body 38 is connected to the probe 39 via the directional coupler 51. The directional coupler 51 is connected to an attenuator 50 for attenuating MW. The directionality of the MW transmission of the directional coupler 51 is such that the MW passes from the oscillator 13 side to the probe 39 side, but does not pass from the probe 39 side to the oscillator 13 side, and all the MW from the probe 39 side is attenuator.
Passed to the 50 side. Also, there is no MW transmission from the oscillator 13 side to the attenuator 50 side or from the attenuator 50 side to the oscillator 13 side. That is, 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 in the probe 39 is transmitted to the attenuator 50 by the directional coupler 51 and is consumed in the attenuator 50. Therefore, it is possible to avoid a situation in which the matching between the attenuator 50 and the probe 39 is not established, so that the reflected wave from the probe 39 flows toward the oscillator 13 and heats and excites the oscillator 13.

The coil-shaped receiving antenna 5 provided at the tip of the probe 39 is provided with a detection circuit provided in the device main body 38.
49 is connected 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 amplification circuit 47. The signal amplified by the amplifier 47 is output to the power meter 48 and the comparator 46. In the power meter 48, the power is displayed in watts to confirm how much MW is output from the radiation section 4. The comparison circuit 46 compares the MW output set value input from the input unit 16 with the MW output value of the radiation unit 4 output from the amplification circuit 47, and outputs a comparison result signal to the control unit 15. The control unit 15 controls the oscillation state of the oscillator 13 based on the comparison result signal so that the MW output value from the radiation unit 4 matches the MW set value input from the input unit 16.

On the other hand, balloons 40, 40 are provided on the outer periphery of the probe 39 and at positions before and after the radiation section 4. Further, a balloon expansion conduit 41 for expanding the balloons 40, 40 is provided in the probe 39. This balloon expansion conduit 41
Is an expansion pump whose base end is provided in the device body 38.
45, and the distal end side branches to each balloon 40,40. The balloons 40, 40 are expanded by a liquid such as a physiological saline solution sent from an expansion pump 45 so as to expand with a large radial force.

Further, a suction pipe 42 is provided in the probe 39. The suction pipe 42 has a proximal end connected to a suction pump 44 provided in the apparatus main body 38, a distal end branched and extending toward the outer periphery of the probe 39, and an extended distal end connected to a balloon. An opening is formed on the outer peripheral surface of the probe 39 between the 40 and 40 so that the inner wall or the like of the duct in the body cavity into which the probe 39 is inserted can be sucked to the outer peripheral surface of the probe 39 between the balloons 40 and 40. In other words, the inner wall or the like of the intraluminal conduit can be sucked into the portion of the outer peripheral surface of the probe 39 where the radiation section 4 is located.

The drive of each of the expansion pump 45 and the suction pump 44 is controlled by the control unit 15. In addition, a temperature sensor 43 such as a thermocouple is provided on the outer peripheral surface of the probe 39 which is considered to be heated most by the MW radiated from the radiating portion 4 and at a central portion of the radiating portion 4, and the temperature is displayed as a temperature It can be displayed by the unit 17.

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

First, with the balloons 40, 40 contracted, the probe 39
Is inserted into the luminal organ, and the radiation part 4 is positioned at the lesion part 52. Then, the expansion pump 45 is driven to drive the balloons 40, 40.
A physiological saline solution is fed into the inside through the balloon dilatation conduit 41 to expand the balloons 40,40. After the probe 39 is fixed by the expansion of the balloons 40, 40, the suction pump 44
Is operated, suction is performed by the suction conduit 42, and as shown in FIG. 4, the tissue of the lesion 52 is brought into close contact with the portion of the outer peripheral surface of the probe 39 where the radiating portion 4 is located. Then, in this state, the oscillator 13 is operated by operating the input unit 16 to start the heating treatment of the lesion 52.

By the way, the expansion of the balloons 40,
The purpose is not only to fix to the lesion 52, but by expanding the balloons 40, 40,
This is to compress the tissue in the vicinity of the lesioned part 52, reduce the amount of blood flowing through the lesion, and reduce the cooling effect of the blood flow. In addition, the suction conduit 42 sucks the tissue in the vicinity of the diseased part 52 so that the balloons 40 and 40 are further inserted into the tissue, thereby reducing the flow of blood flow.
It has a function of bringing the tissue of the lesioned part 52 into close contact with the probe surface so that the 52 is reliably heated.

When the oscillator 13 is operated during the heating treatment, MW is radiated from the radiating unit 4 as in FIG.
Is received by the receiving antenna 5 and its intensity is displayed by the power meter 48. The output value displayed on the power meter 48 may cause a failure of the probe 39 itself or a poor connection. If not, the output setting value of the MW input from the input unit 16 is substantially the same. Therefore, in this case, the operator can confirm that the MW is correctly radiated from the radiating section 4 and that the heating treatment is sufficiently performed.

Also, if a defect occurs in the probe 39 or the like,
Despite the operation of the oscillator 13, the MW is not radiated from the radiating section 4, so that the power meter 48 does not operate. Therefore, in this case, the operator confirms the failure of the probe 39, interrupts the treatment, and replaces the probe 39.

The reason why the MW is not correctly radiated from the radiating unit 4, that is, the reason that the output set value of the MW input from the input unit 16 does not match the output value displayed on the power meter 48 is due to a cause other than the failure of the probe 39 and the like. is there. For example, this is the case when the probe 39 has a poor matching state with respect to the oscillator 13 or when the attenuation in the coaxial cable 3 is large. In these cases,
MW is radiated from the radiating section 4, but the intensity of the radiated MW is
Since the output value is smaller than the set output value of MW, the MW output value is also displayed on the power meter 48 with a value smaller than the set value, and the operator has not obtained the output value of MW required for treatment. And try to take appropriate measures. That is, the MW radiated from the radiating section 4 has a slightly different heating range and heating effect depending on the output value, and as an operator, the set output is radiated from the radiating section 4 and the MW is changed by the output. Because it is desirable that the part is heated, check the power meter 48 and manually increase the output of the oscillator 13,
An attempt is made to make the output from the radiator 4 equal to the set value.

However, in the present embodiment, the measured value and the set value are compared by the comparison circuit 46, and automatic control is performed so that the measured value matches the set value. Therefore, it is necessary to manually increase the output of the oscillator 13. There is no. Of course, it is also possible to carry out manually.

At this time, it is considered that the output of the oscillator 13 unilaterally increases due to the automatic control.Also, when the probe 39 is mismatched, the MW may be excessively reflected.
Reflected wave is attenuated by the attenuator 50, so that the oscillator
I don't encourage 13. Therefore, even if the output from the radiating unit 4 is controlled to be the same as the set value by the automatic control, the oscillator is not excited and no trouble occurs.

Further, when the treatment is completed, the display of the power meter 48 is also displayed as 0 W, so that the operator can confirm that the output from the radiation unit 4 has stopped and the heating by the MW has surely ended.

As described 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. The output of the MW radiated from the radiating section 4 can be confirmed. Therefore,
The intensity of the MW output from the radiating unit 4 can be controlled to an output required for treatment. In this embodiment, the traveling wave (oscillator 13 → probe 39) and the reflected wave (probe 39 → oscillator 13) are separated by the directional coupler 51, and the reflected wave is attenuated.
Attenuated by 50. Therefore, even if the output of the oscillator 13 is increased and the output from the radiating section 4 is automatically controlled to be a specific output, the oscillator 13 is not excited and the thermal treatment by the automatic control can be performed safely. it can.

FIG. 5 to FIG. 7 show a second embodiment of the present invention.

As shown in FIG. 5, the hyperthermia device 53 is
As in the third embodiment, the apparatus comprises a main body 54 and a probe 56.

The probe 56 has therein a space 60 having a ring-shaped longitudinal section and formed coaxially with the probe 56 along the axial direction of the probe 56. The receiving antenna 5 is accommodated in the space 60 coaxially with the probe 56, so that the receiving antenna 5 can move in the axial direction. Note that the space 69 is filled with, for example, a physiological saline solution or the like in order to easily transmit the MW.

An operation wire 58 is connected to the receiving antenna 5. The operation wire 58 is operated by operating an operation knob 57 of an operation unit provided on the base end side of the probe 56,
The probe 56 can move in the axial direction.

Further, a compression ring 59 is provided on the outer periphery of the probe 56 at a position before and after the radiating portion 4 so as to be fitted.
The compression ring 59 is formed of a shape memory alloy or the like, and has a characteristic that can be expanded by heating, for example.

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 a conducting section 55 of the apparatus main body 54 by a lead wire (not shown). The energizing section 55 is controlled by the control section 15, but when the energizing section 55 is energized, the heating element 61 generates heat. This heat causes the diameter of the compression ring 59 to expand, and the compression ring 59 becomes a probe.
It is going away from 56.

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

First, before inserting the probe 56 into the treatment site, the receiving antenna 5 is adjusted to the outer peripheral position of the radiating section 4 by operating the operation knob 57 in order to confirm a defect or the like of the probe 56. Then, the oscillator 13 is oscillated, the state of MW radiation from the radiation section 4 is confirmed, and the state of the probe 56 is confirmed.

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

After the probe 56 is fixed, the power supply to the heating element 61 is started by operating the input unit 16. Due to this energization, the diameter of the compression ring 59 expands as shown in FIG.
Enters the tissue near the lesion 52. As with the balloon 40 of the first embodiment, this is to reduce the amount of blood flow flowing through the lesion 52 to improve the heating effect by the MW. After the compression ring 59 is expanded and separated from the outer periphery of the probe 56 and fixed in the tissue, the oscillator 13 is driven to start treatment. At the start of the treatment, as in the first embodiment, the MW radiated from the radiating section 4 is received by the receiving antenna 5, and the value is displayed by the power meter 48, and the measured output and the set value are displayed. In this embodiment, when the MW output from the radiating section 4 becomes equal to the set value, the operation of the operation knob 57 causes the receiving antenna 5 to be controlled. The outer peripheral position of the radiating portion 4 is shifted from the outer peripheral position of the radiating portion 4 by pulling in the base end direction. This is because the receiving antenna 5
If such a member is located, the radiation distribution of MW will be disturbed to some extent, and it will be different from the temperature distribution of the probe without the conventional receiving antenna,
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 a conventional probe.

Perform treatment as described above.
As shown in FIG. 7, only the probe 56 is removed from the treatment site. When the probe 56 is withdrawn, a compression ring 59 is placed in the vicinity of the lesion 52, but this always restricts the blood flow flowing into the lesion 52, and also suppresses the growth of the diseased tissue. Usually, the thermal treatment is repeated many times thereafter, but the placed compression ring 59 also serves as a positioning means when inserting the probe 56 in the thermal treatment to be performed again. That is, the insertion of the probe 56 is performed, for example, while looking at an X-ray image. At this time, since the compression ring 59 is monitored so as to indicate the range of the lesion 52, the positioning of the probe 56 with respect to the lesion 52 is performed. It will be easier.

As described above, the hyperthermia device 53 having the above configuration allows the receiving antenna 5 provided in the space 60 in the probe 56 to be radiated by the operating wire 58 only when it is desired to confirm the output of the MW radiated from the radiating portion 4. 4 Moved on the outer circumference so that MW output can be measured. Therefore, when it is not necessary to measure the output of the MW, the receiving antenna 5 is shifted from the radiating section 4 so that the same heating as that of the conventional probe having no receiving antenna can be performed. Therefore, the experience at the time of treatment using the conventional probe can be utilized as it is.

FIG. 8 and FIG. 9 show a third embodiment of the present invention.

The hyperthermia device 65 shown in FIG. 8 is of an RF type for performing thermal treatment by sandwiching an affected part or the like between two electrodes.

The hyperthermia device 65 includes an in-vivo applicator 70 inserted into a body cavity, and an extracorporeal applicator 71 fixed outside the body.
And an apparatus main body 66 for performing RF wave oscillation, control, and the like.

The apparatus main body 66 is provided with an oscillator 13 for generating an RF wave, and the RF wave generated by the oscillator 13 is supplied to the extracorporeal applicator 71 and the internal body applicator 70 via the matching circuit 12. In addition, the external applicator 71 and the internal applicator
A temperature sensor (not shown) is provided in 70, and each temperature sensor is provided with a temperature detector 68 provided in the apparatus main body 66.
It is connected to the. The control unit 15 controls the oscillation of the oscillator 13 in accordance with the output of the temperature detector 68.

The in-vivo applicator 70 is provided with an internal electrode 72, and a receiving antenna 73 for receiving an RF wave is provided on the outer periphery of the internal electrode 72. Also, this receiving antenna 73
A balloon 75 is provided on the outer periphery of the balloon 75, and the inside of the balloon 75 is filled with a physiological saline solution for cooling the surface of the heating section. This physiological saline is
It is circulated by an internal pump 67 provided therein. Further, the in-vivo applicator 70 is provided with a tissue compression roller 74 for compressing the tissue near the lesion. As shown in FIG. 9, the pressing roller 74 is divided into a plurality in the circumferential direction when viewed from the distal end side of the in-vivo applicator 70. The roller 74 presses the blood vessel near the lesion in order to increase the heating effect similarly to the first and second embodiments. This is to facilitate insertion of 70 into the organ. In addition, a physiological saline solution is circulated in the extracorporeal applicator 71 by the extracorporeal pump 69 in order to cool the surface of the heating unit.

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

First, the in-vivo applicator 70 is inserted into a treatment site to perform treatment. By operating the in-vivo applicator 70, the internal electrode 72 is fixed to the lesion. 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 the physiological saline in the respective applicators 70 and 71. In this state, the oscillator 13 is operated to start the heating treatment. At this time, the RF wave is received by the receiving antenna 73, and the output value is displayed on the parameter 48,
The comparison circuit 46 compares the set value. And
The output of the oscillator 13 is controlled so that the output of the measured value matches the output of the set value.

As described above, even in the case of the RF system as shown in the present embodiment, for example, the receiving antenna 73 is attached to the in-vivo applicator 70.
The strength of the RF wave output for heating can be confirmed by providing the heater, and the failure of the applicators 70 and 71 can also be confirmed. The receiving antenna 73 can be provided on the extracorporeal applicator 71 as shown in FIG. 10 to detect the output of the RF wave.

FIG. 11 shows a fourth embodiment of the present invention, in which a hyperthermia device 80 can check the output of an MW probe 85 having no receiving antenna, which has been conventionally used.

The hyperthermia device 80 is a conventional MW probe 85 having no device body 81 and no receiving antenna.
And an antenna unit 82 for detecting the output of the MW.

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

The antenna unit 82 is connected to the apparatus main body 81, 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 described.

First, before starting the treatment, the MW probe 85 is inserted into the probe insertion portion 84 of the antenna unit 82. Then, the oscillator 13 of the apparatus main body 81 is operated, and the MW output from the radiating section of the probe 85 at that time is received by the antenna 83. The intensity of the received MW is displayed on the power meter 48, and is controlled so that the output of the MW becomes the same between the measured value and the set value, as in the first to third embodiments. .
When the MW output of the probe 85 becomes equal to the set value, the main body 81 stores the output of the oscillator 13 at that time, and
Stop output of At this point, the operator has
Is in a normal state and that the output of the MW radiated from the probe 85 has been correctly adjusted, and the probe 85 is inserted into the lesion to start treatment. If the MW output of the probe 85 does not match the set value, 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 lesion, and the oscillator 13 is oscillated with the output value stored at the time of the output adjustment to start the conventional treatment.

As described above, the hyperthermia device 80 having the above-described configuration can perform a defect check and the like even in the conventional probe 85, and after always confirming an accurate MW output value, starts treatment. A heating effect can always be obtained.

[Effects of the Invention] As described above, the hyperthermia device of the present invention includes the receiving antenna that receives the electromagnetic wave radiated from the radiating unit, and the detecting unit that detects the electromagnetic wave received from the receiving antenna. That is, the electromagnetic wave generated from the oscillator and radiated from the radiating section is received from the receiving antenna,
The received electromagnetic wave is detected by a detecting means to detect the intensity of the electromagnetic wave radiated from the radiation section. Therefore, it can be confirmed that the electromagnetic wave is radiated from the electromagnetic wave radiating portion. Further, the hyperthermia device of the present invention includes an output control unit that controls an output of the oscillator based on a detection result of the detection unit. That is, the output of the oscillator is controlled based on the intensity of the detected electromagnetic wave. Therefore, the output of the oscillator is automatically controlled, and the heating treatment of the lesion can be reliably performed by the electromagnetic wave. For example, according to the setting value input from the input unit,
The output of the intensity of the electromagnetic wave radiated from the electromagnetic wave radiating section can be automatically controlled.

[Brief description of the drawings]

FIG. 1 is a schematic configuration diagram of a hyperthermia device to which the present invention can be applied. FIG. 2 is a circuit diagram showing a modification of the notifying means of the hyperthermia device of FIG. 3 and 4 show a first embodiment of the present invention. FIG. 3 is a schematic configuration diagram of a hyperthermia device, and FIG. 4 shows a state where a probe of the hyperthermia device of FIG. 3 is inserted into a lesion. FIG. 5 to 7 show a second embodiment of the present invention. FIG. 5 is a schematic structural view of a hyperthermia device, and FIG. 6 shows a state where a probe of the hyperthermia device of FIG. 5 is inserted into a lesion. FIG. 7 is a schematic cross-sectional view showing a state where the compression ring is placed in the lesion and the probe is extracted. 8 and 9 show a third embodiment of the present invention. FIG. 8 is a schematic configuration diagram of an RF type hyperthermia device, and FIG. It is the front view seen from the direction. FIG. 10 is a sectional view of an extracorporeal applicator having a receiving antenna. FIG. 11 is a schematic configuration diagram of a hyperthermia device showing a fourth 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 ... radiator, 5,73,85 ... receiver antenna, 9 ... notification window, 10 ...
... light-emitting element, 48 ... power meter.

Claims (1)

(57) [Claims] An oscillator for generating an electromagnetic wave, a radiating unit for radiating an electromagnetic wave output from the oscillator to an affected part, and receiving an electromagnetic wave radiated from the radiating unit at a predetermined relative position with respect to the radiating unit. A hyperthermia device, comprising: a receiving antenna that detects the electromagnetic wave received from the receiving antenna; and a control unit that controls the output of the oscillator based on a detection result of the detecting unit. .