JPH0241976B2 - - Google Patents

Description

[Detailed Description of the Invention] [Industrial Application Field] The present invention relates to a heating device for hyperthermia, and in particular, uses electromagnetic waves to locally heat cancer tissue in a living body, thereby heating the cancer tissue. This invention relates to a heating device for hyperthermia that stops the regeneration function of the body and causes death.

[Conventional technology]

In recent years, treatment methods using heating therapy (also known as "hyperthermia") have been in the spotlight, in particular in which malignant tumors are continuously heated to around 43°C for 1 to 2 hours, and this is repeated at regular intervals. A number of research reports have been published showing that this can inhibit the regenerative function of cancer cells and at the same time kill many of them (Measurement and Control).
Vol. 22, No. 10). This type of heating therapy is
There are general heating methods and local heating methods. Among these, methods using electromagnetic waves, methods using electromagnetic induction, methods using ultrasound, and the like have been proposed as local heating methods for selectively warming only the cancerous tissue and its surroundings.

On the other hand, as is already known among researchers in the art, the heating effect on cancer tissue is said to be around 43 [℃], and if it is lower than this, the effect will be diminished, and vice versa. If the concentration is too high, it may harm normal tissues and is not desirable. That is, in hyperthermia, the temperature of the body must be maintained within a narrow temperature range that causes lethal damage to cancerous tissues but does not cause much harm to normal tissues.

[Problem that the invention seeks to solve]

However, regarding deep heating within the body,
Due to the peculiarities of biological functions, such as the cooling effect of blood flow, it is not easy to maintain the target region at a temperature within a certain range of around 43° C. for one to two hours. In particular, heating therapy using electromagnetic waves tends to cause burns on the surface of a living body because the absorption rate of electromagnetic waves on the surface of a living body is extremely high.Therefore, conventional techniques were considered unsuitable for deep warming, and were neglected for a long time.

On the other hand, the inventors have previously developed a device that has a control function that can continuously and accurately heat a predetermined heating point within a living body to a predetermined temperature for a certain period of time using electromagnetic waves. We have proposed a heating device for hyperthermia (Japanese Patent Application No. 40793/1983).

The technology related to this proposal discloses various sufficiently effective attempts at heating therapy deep within the body, but on the other hand, it is not necessarily sufficient if it is based on the protection of normal tissue around the affected area in the body. Not yet.

[Purpose of the invention]

The present invention takes into account the above-mentioned prior art, etc., and aims to continuously heat a heating point at a predetermined depth within a living body to a predetermined temperature for a certain period of time. It is an object of the present invention to provide a hyperthermia heating device that has a control function that prevents abnormal heating of the tissue and protects the normal tissue.

[Means for solving problems]

Therefore, the present invention provides an electromagnetic wave generating means for outputting electromagnetic waves, an applicator for irradiating a living body with the electromagnetic waves output from the electromagnetic wave generating means, and a body surface cooling device installed on the electromagnetic wave irradiation opening side of the applicator. A hyperthermia heating device comprising: a first temperature measuring means for measuring the temperature of a heating treatment section in a living body in response to the output of the electromagnetic wave generating means; A second temperature measuring means for measuring the temperature on the surface of the living body and a third temperature measuring means for measuring the temperature at an intermediate portion located between the heating treatment section and the surface of the living body are provided. The main controller is equipped with a main controller that controls the output of the electromagnetic wave generating means to increase or decrease based on the temperature information from each of the first and second temperature measuring means and sets the temperature of the heating treatment section to an appropriate treatment temperature. There is. Further, when the third temperature measuring means detects a biological temperature higher than a preset temperature, an output interruption control means is provided in the main control unit to temporarily interrupt the output of the electromagnetic wave generating means until the biological temperature falls to a predetermined temperature. The structure is such that it is equipped with. This aims to achieve the above-mentioned purpose.

[Effect]

When the applicator is brought into contact with the surface side of the heating treatment part and the electromagnetic wave generation means outputs electromagnetic waves, the temperature of the living body surface at the contact surface, the intermediate part of the living body immediately below it, and the affected part of the living body which is the heating treatment part rises. On the other hand, the temperatures of the surface of the living body, the intermediate part of the living body, and the affected part of the living body are constantly measured at predetermined time intervals by first to third temperature measuring means provided at each part. Since all of this information is sent to the main control section, the output of the electromagnetic wave generating means is controlled to be lowered in response to an instruction from the main control section in case of excessive overheating of each part of the living body. Therefore, burns on the surface of the living body are effectively prevented, the temperature of the affected area in the living body is maintained approximately at the heating set temperature, and when the middle part of the living body is heated to a temperature higher than the set temperature, the aforementioned electromagnetic waves are immediately generated. Since the output of the means is controlled to be interrupted for a predetermined period of time by the output interruption control function of the main control unit, the heating therapy of the affected part of the body can be performed without causing pain to the patient while effectively protecting the normal tissue in the middle part of the body. It can be carried out efficiently and safely for a long time without any problems.

[Embodiments of the invention]

An embodiment of the present invention will be described below with reference to FIGS. 1 to 7.

FIG. 1 is an overall system diagram showing one embodiment of the present invention. In FIG. 1, the hyperthermia heating device includes an electromagnetic wave generation section 2, a control section 4 including first to sixth control functions, and a microwave irradiation section 6 as main parts.

The electromagnetic wave generating section 2 includes a magnetron 8 as an electromagnetic wave generating means, a directional coupler 10 installed on the output side of the magnetron 8, and a sensor that detects the output level of the magnetron 8 via the directional coupler 10. The power control unit 14 adjusts the output of the magnetron 8.

Among these, the power control unit 14 is
This is a control circuit that adjusts the output of the magnetron 8 by changing the anode voltage of the magnetron 8 under control using a thyristor. Further, the directional coupler 10 is a device that separately separates and takes out incident waves and reflected waves, and the electromagnetic waves taken out here are detected by a diode 12, converted into voltage, and then converted to an analog-to-digital converter (hereinafter referred to as , simply referred to as an "A/D converter") 16 to the main control section 18 in the control section 4.

This main control unit 18 calculates the difference between the power level value of the extracted incident wave and the power level value of the reflected wave, calculates the power of the microwave that is effectively supplied to the applicator 20, which will be described later, and It has a function of increasing or decreasing the output of the magnetron 8 based on the output of the magnetron 8.

On the other hand, in this embodiment, the microwave irradiation unit 6
It is composed of an applicator 20 that focuses microwaves and propagates them into the living body 32, and a cooling mechanism 34 that is installed on the opening side of the applicator 20 and has a function of cooling the surface of the living body 32, Further, there is a temperature sensor 30 as a first temperature measuring means that detects the temperature of the heating treatment section, and a third temperature sensor 30 that detects the temperature at an approximately intermediate portion between the surface of the living body and this heating treatment section, that is, the temperature of the intermediate portion within the living body. The structure is equipped with a temperature sensor 31 as a temperature measuring means.

The cooling mechanism 34 includes the cooling mechanism 34
A cooling device 21 that adjusts the temperature of the coolant flowing through the
, a pump 22 that circulates coolant between the cooling device 21 and the cooling mechanism 34, and the pump 2.
2, a flow sensor 26 for detecting the flow rate of the cooling liquid, and a pump control unit 24 as a pump drive control means for driving and controlling the cooling mechanism 3.
A temperature sensor 28 serves as a second temperature measuring means for indirectly specifying the temperature of the surface of the living body by detecting the temperature of the coolant flowing out from the cooling liquid, and controls the cooling device 21 to adjust the cooling of the coolant. Cooling control circuit 2
3 are connected and equipped as shown in FIG.

To explain this in more detail, first, applicator 2
0 is an antenna that is in close contact with a living body 32 and irradiates electromagnetic waves into the living body 32 to perform heating treatment on a target cancer tissue. For this reason, this applicator 20 is provided with the cooling mechanism 34 described above in order to prevent skin burns from overheating due to dielectric loss in the skin portion.

This cooling mechanism 34 is equipped with a pipe 36 for passing the water used as a cooling liquid in this embodiment, and the water cooled by the cooling device 21 (hereinafter referred to as cooling water) is forced by a pump 22. It is circulated. The rotation speed of this pump 22 is controlled to a constant flow rate by a pump control unit 24, and the flow rate of the cooling water is changed according to this rotation speed as necessary, and the temperature of this cooling water is controlled by the cooling device 21. However, the surface temperature of the living body 32 is adjusted by adjusting the temperature of the cooling water by changing the flow rate and temperature of the cooling water.

Further, the flow rate of the cooling water is detected by the flow rate sensor 26, and this detected information is sent to the A/D converter 3.
8 to the main control unit 8, and serves as one reference value for controlling the rotation speed of the pump 22. Further, a temperature sensor 28 for detecting the water temperature of the cooling mechanism 34 is provided on the water discharge side of the cooling mechanism 34, and is brought into contact with the applicator 20 based on the temperature information detected here. Living body 3
The structure is such that the surface temperature of No. 2 is determined. This surface temperature becomes the main information for adjusting the rotation speed of the pump 22 and the water temperature of the cooling device 21.

The temperature sensor 30 is a sensor for detecting the temperature of the cancer tissue which is the heating treatment part, while the temperature sensor 31 is a sensor for detecting the temperature of the intermediate part in the living body between the cancer tissue and the living body surface. Based on the information obtained from each of these sensors, the output of the magnetron 8 is adjusted by the main control section 18.

In this embodiment, the main control unit 18 has a first control function for controlling the output of the magnetron 8 to decrease, a second control function for controlling the output of the magnetron 8 to interrupt, and a second control function for controlling the output of the magnetron 8 to increase. The third control function is also magnetron 8.
A fourth control function sets the maximum output of the pump, a fifth control function controls the rotation speed of the pump 22 via the pump control unit 24, and a fifth control function controls the cooling device 21 via the cooling control circuit 23 to control the cooling mechanism. 3
4, and a sixth control function for controlling the temperature of the coolant flowing through the cooling liquid, and each of these control functions is adapted to operate in response to an input signal as described later.

That is, within the main control unit 18, information obtained by the sensors 12, 26, 28, 30, and 31 is inputted via the A/D converters 16, 38, 40, and 41, and this information and the operator's Based on the information from the input/output unit 44 that received the instruction, the temperature of the cancerous tissue,
First, the rotational speed of the pump 22 is controlled by the fifth control function via the D/A conversion circuit 48 so that the temperatures of the intermediate part of the living body and the surface of the living body are maintained at desired values. The fourth control function controls the output of the magnetron 8, and at the same time notifies the operator of the heating state.

Next, the overall operation of the above device will be explained based on FIG. Here, applicator 20
The temperature of the living body surface in contact with the body is 20 [°C], the temperature of the intermediate part of the living body located directly below it is 40 [°C], and the temperature of the cancer tissue, that is, the temperature of the affected part of the living body, is 43.5 [°C].
shall be.

First, the cooling device 21 and the pump 22 are operated (Fig. 3, 50), and after the water has been sufficiently cooled, the fifth control function is activated based on the information detected from the flow rate sensor 26, and the cooling water is The rotation speed of the pump 22 is controlled so that the circulation is minimized (51 and 52 in the same figure).
Thereafter, the value inputted by the operator according to the depth of the cancerous tissue is set as the maximum output of the magnetron 8 (FIG. 53).

Here, the reason why the maximum output of the magnetron 8 is set to match the deep part of the cancer tissue is that if the microwave output is large, the temperature peak during heating will be near the surface, but if the output is small, the temperature peak will be near the surface. This is due to the temperature peak moving deeper. Figure 4 shows the experimental results.

This figure 4 shows a phantom model that approximates a living body by applying microwaves at a predetermined level of 2450 [MHz], which is generally the highest frequency used in heating therapy, and therefore the heating range is relatively superficial. Shows the temperature distribution when irradiated on. Among them, A shows the temperature distribution obtained by irradiation based on a predetermined reference value, and B shows the case where the output is reduced by 3 [dB] with respect to the reference amount. Temperature distribution with 3 [dB] reduced output (B)
It can be seen that the temperature peak is reached approximately 0.25 cm deeper. However, when the power is reduced, it takes more time to raise the cancer tissue to the desired temperature. FIG. 5 shows an increase in temperature distribution at regular intervals, and the rate of increase decreases as time passes. This is because the surface of the living body is cooled, so as the internal temperature rises, heat is taken away to the outside, and it is affected by the cooling effect of the blood flow of the living body.

The maximum output setting of the magnetron 8 mentioned above is
This is performed by the main control section 18 based on information from the directional coupler 10. That is, from the difference in the power values of the incident wave and the reflected wave detected by the directional coupler 10, the output of the microwave that is effectively supplied to the applicator 20 is determined, and this output is input to the input/output section 44 by the operator. The maximum output of the magnetron 8 is set by matching the set value.

In this case, the maximum output may be set in advance using a phantom model. After the maximum output of the magnetron 8 is set, microwave irradiation is started (FIG. 3, 54), and the temperature of each part of the living body is measured (FIG. 3, 55). In this case, temperature measurement begins after a predetermined time input by the operator has elapsed. This is because, during microwave irradiation, each part of the living body is not heated to near the set value until a certain amount of time has elapsed. However, the intermediate temperature measurement is always in operation, and if it becomes higher than the set value,
In order to protect the normal tissue in the intermediate region, the output of the magnetron 8 is preferentially interrupted to stop heating.

This temperature measurement is performed using a temperature sensor 28 for measuring the surface temperature of the living body 32, a temperature sensor 30 for measuring the temperature of the cancer tissue, and a temperature sensor 28 for measuring the temperature of the surface of the living body 32, a temperature sensor 30 for measuring the temperature of the cancer tissue, and a temperature sensor 28 for measuring the temperature of the surface of the living body 32 and a temperature sensor 30 for measuring the temperature of the cancer tissue. This is done by a temperature sensor 31 for measuring temperature. In this case, the microwave continues to be irradiated even during temperature measurement.

After the temperature is measured, it is first determined whether the temperature of the intermediate portion within the living body 32 is higher than a set value (40° C.) input in advance by the operator (56 in the same figure). If this temperature is higher than the set value, the second control function in the main control section 18 immediately sends a signal to the power control unit 14 to interrupt the output of the magnetron 8 (FIG. 80). After that, the temperature of the intermediate part is measured by the temperature sensor 31.
The temperature measurement loop is repeated until the temperature falls to the low level set value inputted in advance by the operator (81 and 82 in the same figure). In this case, if the output of the magnetron 8 is interrupted, the temperature of the intermediate portion will drop within a relatively short time because the cooling mechanism 34 is functioning as described above.

Then, when this temperature drops to the low level set value, the first control function in the main control section 18
A signal is applied to the power control unit 14 to lower the output level setting value of the magnetron 8 by one step (83 in the same figure). Next, the second control function in the main control section 18 gives a reset signal to the power control unit 14, cancels the output interruption of the magnetron 8 (84 in the same figure), and returns to 55 in the same figure again.
2. Measure the temperature of each part.

On the other hand, if the intermediate part temperature is lower than the intermediate part temperature set value (40°C) inputted by the operator, then the surface temperature of the living body 32 is lowered to the set value of the surface temperature inputted in advance by the operator. It is determined whether the temperature is higher than (20°C) (Fig. 3, 57). When the surface temperature is higher than the set value, the fifth control function in the main control unit 18 functions and gives an instruction to the pump control unit 24 to increase the rotation speed of the pump 22, and the sixth control function in the main control unit 18 functions. The control function instructs the cooling control circuit 23 to lower the temperature of the cooling water, and controls the rotation speed of the pump 22 and the cooling device 2 until the surface temperature of the living body 32 falls below the set value.
1's output (cooling effect) is increased step by step (73 in the same figure). By lowering the water temperature, the surface of the living body 32 is quickly cooled.

After the surface temperature has fallen below the set value, the rotation speed of the pump 22 is lowered by one step (however, the water flow does not go below the minimum circulation) to prevent the surface of the living body 32 from being cooled too much. The output (cooling effect) of the cooling device 21 is lowered by one step (FIG. 58), and then the temperature of the heating treatment section is adjusted (FIG. 59). In this case, since water is being circulated by the pump 22, no burns will occur on the surface layer of the living body 32, so the output of the cooling device 21 may be turned off.

Here, when the temperature of the heating treatment section is lower than the affected area temperature set value (43.5°C) input by the operator, the third control function in the main control section 18 instructs the power control unit 14. The output setting value of the magnetron 8 is increased by giving In this case, the initially set maximum output power will not be exceeded (60 in the same figure). Then, the microwave irradiation level is immediately adjusted based on this output setting value. That is, the magnetron 8 is heated until the cancer tissue in the heating treatment area reaches a temperature higher than the set temperature.
Microwave irradiation is performed by increasing the output setting value step by step. As a result, it is determined whether the temperature has increased for the first time (70 in the same figure), and if it has become high, measurement of the heating time is started (71 in the same figure).
Proceed to step 2. That is, when the temperature of the cancer tissue becomes higher than the set temperature of the affected area, the first control function in the main control section 18 instructs the power control unit 14 to lower the output set value of the magnetron 8 by one step (the same 72), then the fifth and sixth control functions in the main control section 18 give instructions to the pump control unit 24 and the cooling control circuit 23, and control the rotational speed of the pump 22 and the output of the cooling device 21 for each step. (to increase the cooling effect).
This is to compensate for lowering the rotational speed of the pump 22 and the output of the cooling device 21 by one step at 58 in FIG. That is, when the temperature of the cancerous tissue becomes higher than the set value, it is necessary to cool the surface temperature of the living body 32 so that the temperature of the cancerous tissue approaches the set value as quickly as possible.

By the way, the correlation between the heating time and the lethality of cancer tissue depends on the time it takes for the cancer tissue to reach a temperature around 43 [°C]. Therefore, in this example, the heating time is measured from the time when the cancer tissue exceeds the set value (71 in the same figure), and the heating is started when the heating time inputted by the operator in advance has arrived. The process ends (62 in the same figure).

FIG. 6 shows the temperature state of the cancer tissue and the output state of the magnetron 8 during each microwave irradiation and measurement. In this figure, intervals where the temperature distribution is rising are times when the microwave output is rising, and intervals where the temperature distribution is falling is when the microwave output is falling. Point A in the figure indicates the point at which measurement begins because the temperature of the affected area exceeds the set temperature for the first time as a result of microwave irradiation using the maximum output of magnetron 8, and the above-mentioned heating time starts from this point. be done. After this, the microwave output reduction control continues until the temperature of the affected area falls below 43.5°C (BC in the figure). Therefore, the slope between BC and AB is decreasing.

In addition, if the temperature does not reach 43.5 [℃] immediately because the output setting value of the magnetron 8 has been lowered too much (for example, CD in the figure), then As the microwave output is immediately increased, the slope rises again (for example, DE in the figure). By repeating such control, temperature control with almost no ripples can be obtained.

In addition, during the microwave irradiation time, the temperature was initially 43.5 [℃]
It is necessary to set the maximum output and irradiation time of the magnetron 8 so that the temperature does not rise more than 1.5 [°C] even if the temperature exceeds 43.5 [°C]. This is because if the temperature rises by more than 1.5 degrees Celsius, the temperature will exceed 45 degrees Celsius, which will have an adverse effect on normal tissue. As a method of determining this set value, for example, the temperature rise at the initial stage of microwave irradiation (OP in Figure 6) is
One possible setting method is to set the temperature below [°C].
This is based on the fact that, as shown in Figure 5, the temperature increase rate for each hour tends to increase in the early stages, and the rate of increase becomes about 1/2 at around 43.5 [℃]. .

Figure 7 shows the temperature state of the cancer tissue when the maximum output of the magnetron 8 is set lower than in Figure 6, and the start of heating is delayed compared to that in Figure 6. .

In addition, since it is sufficient to use a relatively low frequency to heat the affected area, an oscillator and a linear amplifier suitable for oscillating low-frequency microwaves are used instead of the magnetron 8 used in the above embodiment. It's okay. In this case, the power output is varied by changing the power of the oscillator or the plate voltage of the linear amplifier under control using a thyristor, similar to the case where the magnetron 8 is controlled. However, in this case, it is necessary to use an isolator to eliminate the influence of reflected waves.

Furthermore, in the above-mentioned embodiment, the temperature measurement on the surface of the living body was determined by detecting the water temperature of the cooling mechanism 34, but the present embodiment is not limited to this, and is configured to directly measure the surface of the living body with a temperature sensor. You may. Further, in order to adjust the cooling capacity, the rotation speed of the pump 22 and the output of the cooling device 21 are variably controlled, but either one may be controlled to adjust the cooling water temperature.

FIG. 8 shows the temperature state of the deep part of the living body when the intermediate part temperature is detected to be higher than the set value. In this figure, if the intermediate temperature at point A' exceeds the set value, if microwaves are continuously irradiated, the intermediate area of the body will reach a temperature that adversely affects normal tissues (in the figure), regardless of the strength of the microwave. In such a case, microwave irradiation must be immediately interrupted.

Here, FIG. 9 shows a flowchart (the dotted line portion of the flowchart in FIG. 3 has been changed) when microwave irradiation is interrupted when measuring the temperature of each part of the living body in the above embodiment. That is, after setting the maximum output of the magnetron 8, microwaves are irradiated to the living body for a certain period of time (see Fig. 9 and 10).
0), then turn off the output of the magnetron 8 (101 in the same figure), measure the temperature of the surface, middle part, and affected area of the living body (102 in the same figure), and if the temperature of the middle part of the living body is higher than the set value, The middle part temperature measurement loop is repeated until the temperature of the middle part of the living body falls to the low level set value (see Figures 104 and 105), and when the temperature of the middle part falls to the set value, the output of the magnetron 8 is increased by one step. Then, the microwave irradiation is performed again for a certain period of time (100 in the same figure).

On the other hand, if the temperature in the middle part is lower than the set value,
The same process as shown in the flowchart shown in FIG.
(see Figure 9) enters a temperature measurement loop (see Figures 111, 112, 113, and 108) to lower the respective temperatures. The loop is repeated, and when these temperatures have fallen below the set values, the temperature returns to 100 in the figure according to the output level of the magnetron 8 adjusted during this time, and microwave irradiation is performed for a certain period of time. The other configurations are the same as in FIG. 3.

Even with this configuration, as shown in FIG. 10, the rise time for heating the cancer tissue is somewhat longer, but the effect is almost the same as that of the one in FIG. 3.
This is particularly advantageous for heating treatments that use high-frequency electromagnetic waves.

As described above, in this embodiment, the output of the magnetron 8 and the output of the cooling device 21 are controlled in the main control unit, so it is possible to cope with heating treatments with different depths of the heating area. By inputting each heating setting value into the main control unit 18, heating treatment can be performed easily, and the surface of the living body and the affected part of the living body are less likely to be overheated than necessary. Since the control is performed simultaneously, the cooling effect is large. Furthermore, since the temperature of the intermediate part of the living body is constantly measured, abnormal overheating of normal tissue within the living body can be prevented in advance, so that highly accurate heating treatment can be performed. Furthermore, since the output of the magnetron 8 is not interrupted or controlled during temperature measurement, energy loss due to on/off operations can be reduced and treatment can be speeded up.

〔Effect of the invention〕

Since the present invention is configured and operates as described above,
According to this, when the biological surface becomes overheated, the main control unit can immediately stop the irradiation of electromagnetic waves and thereby quickly cool the biological surface, without causing burns on the biological surface. Warming therapy can be performed continuously for a relatively long period of time, and in particular, the third temperature measurement means and the output interruption control function in the main control unit prevent unnecessary overheating of normal tissue around the affected area. Therefore, it is possible to provide a heating device for hyperthermia that is unprecedented and excellent in that it can protect this.

[Brief explanation of the drawing]

Fig. 1 is an overall system diagram showing one embodiment of the present invention, Fig. 2 is a perspective view showing how the applicator is used, Fig. 3 is a flowchart showing an example of the operation of Fig. 1, and Fig. 4 is a An explanatory diagram showing the change in the temperature peak in the living body when the maximum output of the magnetron is changed, Figure 5 is an explanatory diagram showing the temperature distribution increase in the living body during each heating time, and Figures 6 and 7 are each An explanatory diagram showing the temperature state of the cancer tissue and the output state of the magnetron during microwave irradiation, FIG. 8 is an explanatory diagram showing the abnormal heating state of the middle part of the body, and FIG. 9 is a flowchart showing other examples. FIG. 10 is an explanatory diagram showing the temperature state of cancer tissue and the output state of the magnetron during microwave irradiation and temperature measurement in another embodiment. 8...Magnetron as a means of generating electromagnetic waves,
10... Directional coupler, 18... Main control unit, 20
... Applicator, 28 ... Temperature sensor as second temperature measurement means, 30 ... Temperature sensor as first temperature measurement means, 31 ... Temperature sensor as third temperature measurement means, 32 ... Living body, 34...
...cooling mechanism.

Claims (1)

[Scope of Claims] 1. An electromagnetic wave generating means for outputting electromagnetic waves, an applicator for irradiating a living body with the electromagnetic waves output from the electromagnetic wave generating means, and a living body surface cooling device installed on the electromagnetic wave irradiation opening side of the applicator. A hyperthermia heating device comprising a cooling mechanism for heating, a first temperature measuring means for measuring the temperature of a heating treatment section in a living body in response to the output of the electromagnetic wave generating means; a second temperature measuring means for measuring the temperature on the living body surface side; and a third temperature measuring means for measuring the temperature at an intermediate portion located between the heating treatment section and the living body surface; A main control section is provided which controls the output of the electromagnetic wave generating means to increase or decrease based on the temperature information from each of the first and second temperature measuring means and sets the temperature of the heating treatment section to an appropriate treatment temperature; If the temperature measurement means of No. 3 detects a biological temperature higher than a preset temperature, output interruption control means for temporarily interrupting the output of the electromagnetic wave generation means until the biological temperature falls to a predetermined temperature is provided in the main control section. A hyperthermia heating device characterized by: