KR940000191B1 - Thermotherapy apparatus - Google Patents

Abstract

No content.

Description

Heat treatment device

Figure 1 is a block diagram illustrating the configuration of the heat treatment apparatus of the present invention.

2A, 2B, 2C, and 2D are flowcharts for explaining the operation of the heat treatment apparatus.

3, 4 and 5 show the configuration of a database set in a thermotherapy apparatus, respectively.

Fig. 6 is a diagram showing the relationship between tumor temperature and high frequency applied power in heat treatment.

7A, 7B and 7C show the relationship between the temperature range in vivo and tumors.

FIG. 8 shows an example of a CT image in which the contour of a tissue or organ and the location and size of a tumor are recorded.

9 is a diagram showing an example of a state in which a CT image is divided into minute regions.

FIG. 10 shows an example of a temperature distribution estimated by a heat treatment apparatus. FIG.

11 is a flowchart showing a modification for parameter correction.

12 is a graph showing temperature characteristics for explaining the principle of parameter correction.

FIG. 13 is a graph showing the relationship between the measured temperature and the estimated temperature with respect to the elapsed time in clinical practice.

14 is a block diagram showing the configuration of a heat treatment apparatus or a treatment plan support apparatus according to another embodiment.

FIG. 15 is a flowchart showing a part of the operation of the apparatus shown in FIG.

* Explanation of symbols for main parts of the drawings

2: control unit 3: image scanner

4: CT interface 6: control panel

7: mouse interface 9: cathode ray tube

10: printer 11: high frequency generator

12: constant temperature water circulation portion 13: thermometer side

13a: temperature sensor 14A, 14B: applicator

15A, 15B: Electrode 16A, 16B: Liquid Bag

The present invention relates to a heat treatment apparatus, and more particularly, to a heat treatment apparatus for estimating a temperature distribution in a living body and performing heating control based thereon. In addition, the present invention relates to a heat treatment apparatus having a treatment plan support function for easily establishing a treatment plan by estimating a temperature distribution in a living body during heat treatment. Moreover, the present invention relates to a treatment plan support apparatus used to make a heat treatment plan.

The thermotherapy device is composed of a pair of applicators, a high frequency generator, a constant temperature circulation unit and a thermometer side. The applicator includes an electrode and a liquid bag surrounding the electrode, and a high frequency voltage is applied to the electrode by the high frequency generator. On the other hand, the constant temperature solution is circulated by the constant temperature circulation unit in the liquid bag. The applicator supports and mounts the living body therebetween, and the living body is dielectrically warmed by applying a high frequency voltage to the electrode of the applicator. The liquid bag adheres to the body surface (or intestinal inner wall) to cool the body surface.

In the living body, a temperature sensor is inserted so that its tip is located in the tumor. The thermometer side measures the temperature of the tumor in accordance with the output signal of this temperature sensor. The high frequency applied power is controlled so that this measurement temperature becomes a predetermined value (for example, 42.5-43.0 degreeC). The tumor is allowed to warm to this temperature and maintained at that temperature for a period of time to remove the tumor.

In the conventional thermal therapy apparatus, high frequency applied power is controlled in accordance with the temperature of the "point" of the tip of the temperature sensor. Since the diameter of the electrode of the applicator uses a size of several centimeters to several tens of centimeters, and the high frequency power is scanned small in the "plane", it is necessary to measure the temperature distribution having a two-dimensional or three-dimensional area. Each patient's body type and fat thickness are different.

As a result, there have been a number of cases where a high-temperature area (hot spot) occurs or burns a patient where a conventional heat treatment apparatus does not even think about.

In addition, there is a fear that an infectious disease may occur from a site where the temperature sensor is inserted into the patient's body and the patient is in pain.

An object of the present invention is to provide a heat treatment apparatus for estimating a temperature distribution in a living body and controlling applied high frequency power according to the estimated temperature distribution.

It is another object of the present invention to provide a heat treatment apparatus or treatment plan support apparatus having a treatment plan support function for facilitating a careful treatment plan by estimating the temperature distribution in vivo and enabling safe and effective treatment. .

The thermal treatment apparatus according to the present invention includes an applicator having an electrode for applying high frequency power to a living body, a means for generating high frequency power applied to the electrode, a thermometer measuring means for measuring a temperature of a predetermined place of the living body, and a heating condition. And a warming condition setting means for setting the temperature, the CT image taking means for taking in the CT image of the living body, the biological parameter storing means for storing the tissue or the parameter of the living body, the taken CT image, and the stored The value of the biometric parameter such that the difference between the temperature of the predetermined location of the living body repeatedly measured by the temperature measuring means and the temperature of the predetermined location of the living body obtained from the estimated temperature distribution is reduced according to the biological parameter and the set heating condition The temperature distribution estimating means for estimating the temperature distribution on the CT image while repeatedly correcting It is characterized by the comparison.

The thermotherapy apparatus of the present invention estimates the temperature distribution on the CT image according to a given CT image, biometric parameters and heating conditions. Since the first estimated temperature distribution is not different from the actual temperature distribution, it is corrected to be closer to the actual temperature distribution by using the temperature at one point or several points actually measured.

Since the temperature measured is used to correct the estimated temperature distribution, it does not necessarily need to be in vivo temperature, and the need to insert a temperature sensor into the patient's body is reduced. As a result, the patient does not suffer, and infection can be prevented.

In addition, since such a two-dimensional or three-dimensional temperature distribution can be obtained, it is possible to control the high frequency power output, the temperature of the constant temperature liquid in the liquid bag, the amount of circulating liquid, and the like accordingly. This improves the reliability of the treatment, prevents unexpected high temperature ranges and burns of the patient, and reduces the effects of individual differences such as body shape and fat thickness since the patient's CT burn is used. have.

The thermotherapy apparatus according to the present invention comprises an applicator having an electrode for applying a high frequency voltage to a living body, and a high frequency power generating means for generating a high frequency power applied to the electrode. CT image taking means for taking in, biological parameter storing means for storing parameters of tissue or organ of living body, and at least one of electrode size, position, high frequency power, and application time which are optimal for treatment in accordance with the taken CT image Treatment condition notification means for determining and informing a condition of a condition, temperature distribution estimation means for estimating a temperature distribution occurring on a CT image of a living body using biometric parameters stored in the treatment condition, and the estimated temperature distribution Characterized in that it comprises an output means for displaying or recording the.

According to the heat treatment apparatus of the present invention, it is possible to predict a temperature distribution on a CT image under a set heating condition. Therefore, it is possible to set various treatment conditions before the actual treatment and to develop a treatment plan to obtain the most desirable temperature distribution. And according to this treatment plan, a safe and effective treatment can be performed and an operator does not need a high level of skill. That is, even if you are not highly skilled, there is an advantage that can set appropriate heating conditions. It can also be used as a substitute for experiment by using it as a model planning apparatus.

Hereinafter, the present invention will be described in detail with reference to the accompanying drawings.

1 is a block diagram showing the configuration of a heat treatment apparatus according to an embodiment of the present invention.

The thermotherapy apparatus is provided with the control part 2 comprised from a microcomputer etc. The control unit 2 estimates the temperature distribution on the CT image, a function of taking an X-ray tomography (computerized tomography or tomogram) (hereinafter abbreviated as CT) image, a function of automatically selecting heating conditions, and a CT image. It has a function of correcting, controlling a high frequency generator and a constant temperature water circulation.

CT images can be created not only by X-ray tomography but also by nuclear magnetic resonance (NMR = Nuclear Magnetic Resonance). As long as the cross section of the living body A can be accurately depicted, a human may describe this CT image. The applicators 14A and 14B to be described later are generally circular in plan view. CT of the cross section (this cross section becomes the highest temperature) passing through the center of the applicator 14A, 14B among the cross-sectional views of the living body portion sandwiched (sandwiched between) by the pair of applicators 14A, 14B. It is best to make an image.

The CT image is given to the control unit 2 by the image scanner 3, the CT interface 4, or the floppy disk driver 5. Image. The scanner 3 reads by scanning a CT image displayed on a film, and the read image is given to the control unit 2. Image. Instead of the scanner 3, a configuration may be adopted in which a CT image is taken in by a video camera. Either way, these methods are effective when the CT image remains only on the film.

The CT interface 4 is used when data representing a CT image is directly transmitted online. The transmitted CT image data is taken into the control unit 2 via the CT interface 4.

The floppy disk drive (hereinafter abbreviated as FDD) 5 reads a data base stored in the floppy disk or stores data indicating the estimated temperature distribution on the floppy disk. When the CT image data is stored in the floppy disk, this CT image data is taken into the control unit 2 by the FDD 5. Other storage media such as hard disks and optical disks can also be used to store the database.

The operation unit 6 includes a keyboard and the like for inputting various commands and data to the control unit 2. The mouse 8 is also connected to the control unit 2 via a mouse interface 7. The mouse 8 is used to write the outline of a tissue or organ, the shape of an applicator, or the like. You can also use a tablet instead of the mouse.

A cathode ray tube display device (CRT = Cathode Ray Tabe, hereinafter abbreviated as CRT) 9 displays a captured CT image, estimated temperature distribution, heating condition, device state, and the like. The printer 10 prints out temperature distribution, heating conditions, and the like. Instead of the CRT, a liquid crystal display can be applied.

The high frequency generator 11 applies a high frequency voltage to the electrodes 15A, 15B of the applicators 14A, 14B, and the magnitude and on / off of the applied power are controlled by the controller 12.

The constant temperature water circulation unit 12 circulates the constant temperature water separately in the liquid walls 16A and 16B of the applicators 14A and 14B, respectively, and the temperature, the circulation flow rate, and the on / off of the circulation are also supplied to the control unit 2. Controlled by the

The thermometer side part 13 is equipped with the temperature sensor 13a, and measures the temperature T _M of the living body A. This measured temperature T _M is used in the correction process of the temperature distribution which is blown into the control part 2 and later. Since the measured temperature T _M is for correcting the temperature distribution, it may not necessarily be the temperature in the living body, or the temperature of the constant temperature in the body surface or the liquid bags 16A and 16B may be used. Therefore, it is not necessary to insert the temperature sensor into the living body (A).

Next, the operation of the heat treatment apparatus will be described with reference to FIGS. 2A to 2D.

First, a CT image is taken in to the control part 2 with reference to FIG. 2A (step 1). The CT image is input from the image scanner 3 as above, or input online or from a floppy disk. The CT image input to the control unit 2 is displayed on the CRT 9.

Next, the operator writes the outline of each tissue and organ on the image displayed on the CRT 9 using the mouse 8 (ST2). The extraction of the contours of tissues and organs can be automatically performed to some extent by computer processing depending on the difference in the density of CT images or the difference in CT values (for example, X-ray CT's transmission coefficient). However, there are some cases where tissues and organs are not clearly distinguishable. Therefore, it is recommended that the operator correct the automatically extracted contour using the mouse 8. Either way, it is up to the operator to decide whether to execute the automatic contour extraction, to modify it, or to contour it himself.

Subsequently, the operator further writes tumor T on the CT image on the CRT screen using the mouse 8 (ST3). This is because tumors are generally difficult to extract due to differences in CT images, CT values, and the like.

FIG. 8 shows an example of extracting outlines of tissues and organs on a CT image and additionally filling in the tumor tumor T. FIG. Where M is muscle, F is fat, B is bone, and m is bone marrow.

The operator again sets the room temperature and the initial temperature of the human body by using the operation unit 6 or the mouse 8 (ST4). These values are often within a predetermined range, so you can use the default values set in the device.

The operator again inputs the temperature increase rate set value (ΔTs) and the tumor target target temperature (T _ST ) (ST5).

The optimal heating condition is automatically selected (ST6). Examples of this heating condition include the following five types, which are presented on these CRT screens.

Iii) Applicator size and location

Ii) cooling water temperature

Iii) applied power

가 warming time

예비) pre-cooling time

The heating conditions presented are automatically selected as follows. Data stored in floppy, disk, etc. The database includes data of the central position and size of tumor T, as shown in FIG. 4, and the data matched to or closest to the position and size of tumor inputted in ST3. Is selected from the base. As shown in Fig. 5, data on these tumors is related to data of the applicator position, the size of the applicator, the cooling water temperature, and the like. These data are based on the data obtained by the temperature distribution calculation performed in advance.

The operator draws the applicator using the mouse 8 on the CT image displayed on the CRT 9. This is because the data of the CT image taken in by the image scanner 3 is generally different from the data stored in the data base shown in FIG. The image is then divided into spherical (or triangular) microregions so that the shapes of organs, tumors and applicators are approximated in units of microregions. 9 shows an image finally obtained. Where e represents an electrode and w represents boras (liquid bag or constant temperature water), respectively.

Once the initial warming condition is determined, the operator connects the designated applicator to the thermotherapy device and mounts the applicator to the patient. If the applicator can be automatically mounted, the applicator is mounted on the patient by continuously moving each part of the applicator's support mechanism, etc. so that the applicator is mounted on the device and then the applicator position is displayed in the initial heating condition.

When the applicator is mounted, the set temperature of the constant temperature water circulation unit 12 is switched to the value selected in ST6 according to the instruction from the control unit 2, and the water temperature is controlled. When the actual water temperature reaches this set temperature, the counting of the selected precooling time is started. When this precooling time has elapsed, the effect is alerted or displayed on CRT9. At the same time, a high frequency voltage is applied to the electrodes 15A and 15B of the applicators 14A and 14B by the high frequency generator 11 to the applied power selected in ST6 (ST7).

When the heating is started, the control unit 2 takes in the measured temperature T _M from the thermometer side unit 13 every predetermined time (for example, 30 seconds) (ST8).

The control unit 2 performs electric field analysis (ST9). This electric field analysis is performed by analyzing the following Laplace equation (1) regarding the potential ψ by obtaining the potential ψ for each microregion.

Here, the dielectric constant ε (F / m) is obtained from the relative dielectric constant ε _r of the tissue or organ and the dielectric constant ε _o of the vacuum. This relative dielectric constant? _R is set in advance for each tissue and organ in the database as shown in FIG.

Subsequently, energy analysis, that is, thermal energy Wh generated in each micro area is calculated (ST10). The electric field strength E is obtained by differentiating the electric potential?, And the thermal energy Wh is calculated by applying the electric field strength E to the formula (2).

In this formula (2), sigma (υ / m) is the electrical conductivity (conductivity), which is also stored in the data base for each tissue and organ (see FIG. 3).

The temperature distribution analysis, that is, the calculation of the temperature T _i of each micro area is executed (ST11). The biothermal heat transfer equation of formula (3) is solved.

Here, ρ, c, k, F are the bulk density (kg / m 3), specific heat (J / kg ° C.), thermal conductivity (W / m ° C.), blood flow rate m 3 /kg.s of each tissue and organ, The data shown in Fig. 3 are calculated from the database. The blood flow rate is the amount of blood flowing per unit time in a unit weight of tissue or organ, and is generally a small value in tumors. Ρ _b , C _b , and T _B are the volumetric density of blood, specific heat of blood, and temperature of blood, respectively. The left side term 1 of formula (3) denotes heat storage in vivo, the left side term 2 indicates heat conduction, and the right side term 2 indicates cooling by blood flow.

In the above processing of ST 9-11, the present embodiment analyzes by applying the finite element method. Of course, as the analysis method, in addition to the finite element method, the boundary element method (slightly less accurate than the finite element method), the difference method, and the like can be applied.

When the temperature T _i for each micro area is obtained in ST 11, a temperature distribution is created using these data, which is displayed on the CRT9 and printed out from the printer 10. The calculation of the temperature T _i does not have to be performed for all the micro areas, but only a representative point including the temperature measured point.

A determination is made as to whether or not the calculated temperature T _i (indicated by the temperature T _R ) of the small region corresponding to the temperature measured point coincides with the measured temperature T _M (ST12). This determination branches to ST 24 for YES and ST 13 for NO.

Referring to FIG. 2B, when the calculated temperature T _i and the measured temperature T _M do not coincide (NO in ST12), the difference ΔT _R = | T _R -T _M | In the direction approaching this zero, the blood flow volume F which is one of the above coefficients (parameters) is increased (changed) (ST13), and equation (3) is solved again (ST14).

In the formula (3), the right side claim 2 including the blood flow volume F indicates thermal diffusion in the body due to blood flow, and when the blood flow volume F increases, the generated heat diffuses more and acts in the direction of suppressing the increase in temperature T _R. do. On the contrary, when blood flow volume F becomes small, the effect | action which suppresses raise of temperature T _R will become small. The value of blood flow F is corrected according to the magnitude of the positive, negative and absolute values of the difference ΔT _R.

It is determined whether or not the temperature T _R calculated using the new blood flow value F corresponds to the measured temperature T _M , and branches to ST24 for YES and ST16 for NO (ST15). If the calculated temperature T _R and the measured temperature T _M do not coincide, the flow may return to ST13 again and change the blood flow volume F value again.

In any case, it is determined that only the change of the value of the blood flow volume F cannot estimate the temperature distribution at which the calculated temperature T _R equivalent to the measured temperature T _M can be estimated, and then the other parameters are corrected.

First, the electric conductivity σ in the formula (2) is increased or decreased (changed) in the direction in which the difference ΔT _R decreases (ST16). Even if the blood flow volume F is changed, in the case of T _R ≠ T _M (or ΔT _R is not constant), the temperature distribution remains in some form in the electrical conductivity σ, and it is considered that an error occurs in the amount of heat energy generated Wh. Because it becomes.

Using the electrical conductivity σ after this change, equation (2) is solved to obtain thermal energy Wh (ST17), and equation (3) is solved using this newly calculated heat energy Wh to determine the temperature T _i of each microregion. Become.

In this way, it is determined whether or not the temperature T _R calculated using the new electrical conductivity σ coincides with the measured temperature T _M (ST19), and branches to ST24 for YES and ST20 for NO, respectively.

If the electrical conductivity σ is changed and T _R ≠ T _M (or ΔT _R is not constant), another parameter, dielectric constant ε, is also considered to have an influence on any factor and cause an error in the potential ψ. . Therefore, the dielectric constant epsilon is changed (ST20), formulas (1), (2), and (3) are sequentially interpreted (ST21-ST23), and the temperature T _i of each minute region is obtained. After the processing of ST23, the process returns to ST12 again to determine whether T _R = T _M.

In this way, the processing of ST12-ST23 is repeated until T _R = T _M.

FIG. 10A shows an example of the temperature distribution obtained as described above. FIG. 10B shows a temperature range indicating the temperature shown in FIG. 10A. This temperature distribution is displayed on the CRT9 or printed out by the printer 10.

In ST24, the temperature distribution obtained by the temperature distribution analysis determines whether the temperature T _T of the hottest part in the tumor T has reached the target temperature T _ST set by the operator in advance. If this determination is YES, branches to ST29 and, if NO, to ST25.

FIG. 6 shows the time course of the applied power at the electrodes 15A, 15B of the applicators 14A, 14B and the temperature in the tumor T. FIG. The temperature of the tumor initially rises monotonously and is maintained at this temperature T _ST when the target temperature T _ST is reached.

The process shown in FIG. 2C starting from ST25 relates to the control of the transient state until the tumor temperature reaches the target temperature T _ST . The process shown in Figure 2d starting from ST29, to a control in the normal state to maintain the tumor temperature to a target temperature T _ST After the temperature of the tumor reaches the target temperature T _ST.

Also in FIG. 2C, it is controlled so that the temperature increase rate (DELTA) T _T of a tumor may become equivalent to the temperature rise rate set value (DELTA) T _{S previously} set.

The last, for example, the temperature and the temperature difference △ T _T of the tumor misleading calculation time of the tumor calculated at 30 seconds before is obtained, the temperature difference △ T _T is larger than the temperature increase rate set value _{△ T S (△ T T>} △ T _It is determined whether or not _S ) (ST25). In the case of YES, the safe power to the electrodes 15A, 15B by the high frequency generator 11 is reduced in accordance with the instruction of the control unit 2.

In the determination of ST25, in the case of NO, it is determined whether or not the temperature difference DELTA T _T is smaller than the set value DELTA T _S (ΔT T < DELTA T _S ) (ST27). If it is determined as such, the power applied to the electrodes 15A and 15B by the high frequency generator 11 is increased by the command of the controller 2.

During the processing of ST26 or ST28, or when DELTA T _T = DELTA T _S , the process returns to ST8 to estimate the temperature distribution again.

In FIG. 2d, control is maintained to maintain T _T = T _ST after the tumor temperature T _T reaches the target temperature T _ST once.

In ST24, when the tumor temperature T _T reaches the target temperature T _ST , the counting of the warming time is started.

It is determined whether the tumor temperature T _T is higher than the target temperature T _ST (T _T > T _ST ) (ST29), and in the case of YES in this determination, the high frequency generator 11 is commanded by the command of the control unit 2; The output of the high frequency power is stopped (ST30). Then move on to ST33.

Tumor temperature T _T is lower than target temperature T _ST (T _T T _ST ) is determined (ST31), and in the case of YES in this determination, the high frequency power output by the high frequency generator 11 is resumed by the command of the control unit 2 (ST32). Then move on to ST33.

In the case of T _T = T _ST , the phenomenon is maintained with respect to high frequency application without any processing.

As shown in FIG. 6, the present embodiment has a configuration in which the high temperature power is interrupted and the temperature is maintained with the applied power when the tumor temperature T _T reaches the set target temperature T _ST , but is limited thereto. Of course, a design change can be performed suitably.

The treatment of ST33 to ST37 is to match the high temperature zone to tumor inversion, and this treatment will be described with reference to FIGS. 7A to 7C.

According to the calculated temperature distribution, the size of the region (hereinafter referred to as high temperature region) reaching the target temperature T _ST is calculated by the control unit 2 (ST33). Subsequently, it is determined whether or not it is larger than the middle weight T of the high temperature region (ST34). This determination branches to ST35 in the case of YES and ST36 in the case of NO.

In ST35, the constant temperature water circulation part 12 reduces the temperature of the constant temperature water or increases the circulation flow rate in response to the command from the control unit 2. After the processing of ST35, the process advances to ST38.

7A and 7C are both cases where the high temperature region H is larger than the tumor T, and the determination of ST34 is YES. In the case of FIG. 7A, the water temperature of both the applicators 14A and 14B is lowered or the circulation flow rate is increased. On the other hand, in the case of FIG. 7C, not only the hot zone H is larger than the tumor but also the hot zone H is biased toward the applicator 14B, so that the water temperature of the applicator 14B is lowered and the circulation flow rate is increased.

In ST36, it is determined whether the hot zone is smaller than the tumor, and branches to ST37 in the case of YES and ST38 in the case of NO. In ST37, the constant temperature water circulation unit 12 increases the water temperature or decreases the circulation flow rate in response to the command from the control unit 2. After the processing of ST37, the process advances to ST38.

Figure 7b shows the case where the hot zone H is smaller than the tumor T. This is the case when the judgment of ST36 is YES. In addition, since the high temperature zone H is biased toward the applicator 14B, the water temperature of the applicator 14A is increased or the circulation flow rate is reduced.

If the regions of hot zone H and tumor T coincide, no treatment is performed.

After the above processing, it is determined whether or not the heating time set in ST6 has elapsed (ST38). If the warming time has not yet elapsed, return to ST8. When the warming time has elapsed, the heat treatment ends.

In the above embodiment, the blood flow volume F is corrected in the direction in which ΔT _R = | T _R -T _M | approaches zero in ST13. And if T _R = T _M , it is necessary to repeat this correction process.

In the modification described below, the optimum blood flow volume F is back estimated.

FIG. 11 shows the reverse estimation process of blood flow, and is replaced by the processing of ST7 to ST16 in FIGS. 2A and 2B. The other processing shown in FIG. 2A-FIG. 2B can be applied as it is.

In the thermotherapy apparatus shown in FIG. 1, the estimated temperature T _C (any micro area such as the calculated temperature T _i or T _R may be sufficient) and the measured temperature T _M , as shown in FIG. Change accordingly. The inventors have the following relationship between the estimated temperature T _C and the measured temperature T _M at two relatively close time points T _i and t 2 (for example, 5 seconds intervals) under the condition that the applied power is kept constant. Found to hold.

Here, F _C is the blood flow amount used to calculate the estimated temperature T _C , and F _M is the blood flow amount estimated back, and when measured, the blood flow amount will be this value.

In addition, C _t is the specific heat of the tissue or organ whose temperature is measured.

The T _C1, T _C2, such as 12 degrees, shown is the estimated temperature at the time _{t i, t 2 T M1,} T M2 is the measured temperature at the time t _i, t _2.

The blood flow F _c is used to estimate the temperature T _c , and the new blood flow F _M is back estimated using equations (4) and (5). This back estimated blood flow volume F _M is used in the following temperature distribution analysis.

Also in FIG. 11, the initial value F _o is set as the surface ST7 where the temperature is started and the blood flow rate F _C (ST40). This initial value F _o is 5.0 × 10 ⁻⁷ in fat, 8.3 × 10 ⁻⁶ in muscle, 4.2 × 10 ⁻⁷ in bone and 5.0 × 10 ⁻⁷ in tumor.

After that, the electric field analysis ST41 and the energy analysis ST42 are executed. This is the same as ST9 and ST10 in FIG. 2A.

Next, the measured temperature T _M is taken in from the temperature sensor 13a (ST43). Counter C is set to 1 (ST44) and advances to temperature distribution analysis (ST45). The temperature distribution analysis corresponds to (ST11) in FIG. 2A, and analyzes (3) to obtain the estimated temperature _Ti (T _R ). As the blood flow F of formula (3), the value F _C set in ST40 is used.

After the estimated operation of the temperature and the actual measurement of the temperature are performed at least two points close to each other, a back estimation of the blood flow volume F _M is performed according to the formula (4) using the temperature data thus obtained (ST46).

Next, it is determined whether T _R = T _M , that is, whether | T _R -T _M | is within a predetermined value (ST47). If YES, branching is made to (ST24), if NO, branching is made to (ST48), and it is determined whether the contents of the counter C have reached a predetermined value C _MAX .

Initially therefore the NO in the (ST48) branches to ST49, and returns the counter C by one increment at the same time, the F _M obtained by inverse estimation calculation of ST46 to the new F _C (ST49), ST45 to.

Then, the temperature distribution analysis is performed again using the new blood flow F _C (ST45), and the blood flow F _M is again estimated using the new F _C , the estimated temperature, and the measured temperature according to equation (4) (ST46). .

The processing of ST45-ST49 is repeated until T _R = T _M is established (ST47) or the counter C becomes C _MAX (e.g., C _MAX = 4) (ST48). In this repetition, if the estimated temperature T _R coincides with the measured temperature T _M (ST47), the flow branches to ST24. If C = C _MAX is mismatched (ST48), counter C is reset (ST50) and then advances to ST16.

As described above, in the present embodiment, the measured results of these measured temperature data and the in vivo temperature distribution analysis routine using the time-series actual temperature data of the temperature at the point of interest obtained by clinical heating are displayed. The method of repeatedly estimating the parameter values of the biological tissue of interest and its temperature-dependent characteristics so as to be thermally well matched is taken. In other words, the measured temperature at an arbitrary point of interest is compared with the corresponding analysis result. If the two values coincide with each other within a certain error range, the value used for analysis as a parameter value of the biological tissue of interest is estimated correctly. It is assumed that the process has been performed, and the process is returned to the in vivo temperature distribution analysis routine again, and the process proceeds to the temperature distribution calculation after a certain time has elapsed. If there is a site where the estimated temperature and the measured temperature do not coincide in the site of interest, the parameters of their biological tissues, for example, the blood flow, are corrected by the above method, and then electric field calculation, thermal energy calculation and temperature distribution calculation are performed again. To return to the temperature distribution analysis routine.

If the temperature distribution estimation calculation is performed while performing the back estimation of blood flow as in the present embodiment, as shown in FIG. Measured temperature and The estimated temperatures shown in the table are approximately matched, and the accuracy of the estimated temperature is improved, making it possible to estimate the adaptive temperature distribution absorbing the solid differences. In addition, the inverse estimation method uses data of other biological parameters. There is also the possibility of judging the progress of the tumor and applying it to cancer diagnosis by the base construction and its utilization.

Figure 13 shows clinical data on muscles. The table shows the measured temperature, The table shows the estimated temperature at the temperature distribution estimated distance including the reverse estimation process of blood flow according to FIG. Δ represents the blood flow volume estimated at this temperature distribution estimated distance. ○ Table shows applied voltage.

The table is a temperature data for comparison, and shows the temperature estimated by the temperature distribution estimation process according to FIGS. 2A and 2B with the blood flow constant.

The present invention can be applied not only to the high frequency heat treatment device, but also to the ultrasonic heat treatment device.

14 and 15 illustrate an embodiment of a heat treatment apparatus or a treatment plan support apparatus having a treatment plan support function for heat treatment. Also in these drawings, the same blocks and the same processes as those shown in FIGS. 1 and 2A are denoted by the same reference numerals, and redundant description thereof is omitted. In addition, in FIG. 14, the high frequency generation part, the high temperature water circulation part, and the thermometer side part are omitted.

In exactly the same way as described above, after taking the CT image, extracting the contours of the tissues and organs, inputting the size and location of the tumor, and entering the room temperature or the initial temperature of the human body, the optimal heating conditions are automatically selected for the electric field. Analysis, energy analysis and temperature distribution analysis are performed (ST1 to ST6, ST9 to ST11).

The temperature distribution is created using the temperature T _i for each micro area thus obtained, which is graphically displayed on the CRT9 as shown in FIG. 10A and printed out by the printer 10 (ST51).

The operator looks at the display or print to determine whether the desired temperature distribution is being obtained (ST52). If this determination is YES, the processing is sorted. The warming condition at this time is the optimum condition and is used for the actual treatment.

On the other hand, if the judgment of ST52 is NO, it moves to ST53 and the operator corrects the heating condition. Then, the processes of ST9 to ST11 and ST51 are executed again, and the temperature distribution under the corrected heating condition is created and displayed or printed out. ST9 to ST11 and ST51 to ST53 are repeated until the desired temperature distribution is obtained.

The temperature distribution on the CT cross section under the heating conditions set as described above can be predicted. Therefore, it is possible to establish a treatment plan to obtain the best temperature distribution by setting various heating conditions before actually performing the treatment. According to this treatment plan, safe and effective treatment can be performed, and the operator does not need to be highly skilled.

Claims (27)

An applicator having an electrode for applying high frequency power to the living body, high frequency power generating means for generating high frequency power applied to the electrode, thermometer measuring means for measuring a temperature of a predetermined part of the living body, and setting a heating condition A thermal therapy apparatus comprising a warming condition setting means, comprising: a cross-sectional image taking means for taking in a cross-sectional image of a living body, a bio-parameter storage means for storing parameters of tissues or organs of a living body, a taken-up cross-sectional image, and stored The biometric parameter may have a small difference between the temperature of the predetermined location of the living body repeatedly measured by the thermometer measuring means and the temperature of the predetermined location of the living body obtained from the estimated temperature distribution according to the biological parameter and the set heating condition. Temperature component for estimating the temperature distribution on the cross-sectional image while repeatedly correcting the value Thermal treatment apparatus comprising a foraging means. The thermotherapy apparatus according to claim 1, further comprising output control means for controlling the output of said high frequency power generating means in accordance with an estimated temperature of a predetermined part in the living body estimated by said temperature distribution estimating means. 2. The thermotherapy apparatus according to claim 1, wherein the applicator comprises a liquid bag for cooling the body surface, and a constant temperature solution circulation means for circulating a constant temperature solution in the liquid bag. 4. The constant temperature liquid control according to claim 3, wherein at least one of the temperature and the circulation amount of the constant temperature liquid circulated by said constant temperature liquid circulation means is controlled in accordance with the estimated temperature distribution at a predetermined location in the living body estimated by said temperature distribution estimation means. Thermal treatment apparatus characterized in that it further comprises a means. 4. The control apparatus according to claim 3, wherein the means for setting a tumor region to be treated on the cross-sectional image, the means for obtaining a high temperature region exceeding a predetermined temperature from the estimated temperature distribution, and the maximum temperature of the tumor region are controlled. Output control means for applying a high frequency power output to the electrode when the temperature value is less than the temperature value, and controlling to reduce the high frequency power applied when the temperature value is higher than the control temperature value, and lowering the circulating fluid temperature when the high temperature area is larger than the tumor area. And thermostatic control means for controlling to increase the circulation amount and to increase the circulating fluid temperature when the hot region is smaller than the tumor area, or to reduce the circulation amount. Device. The storage means according to claim 1, wherein the means for setting a tumor area to be treated on the cross-sectional image, storage means for storing in advance a plurality of set warming conditions, and warming conditions suitable for the taken cross-sectional image and the set tumor area. And a means for selecting from among a plurality of heating conditions stored in the thermal treatment apparatus. An applicator having an electrode for applying high frequency power to the living body, high frequency power generating means for generating high frequency power applied to the electrode, thermometer measuring means for measuring a temperature of a predetermined part of the living body, and setting a heating condition A thermal therapy apparatus comprising a warming condition setting means, comprising: a cross-sectional image taking means for taking in a cross-sectional image of a living body, a bio-parameter storage means for storing parameters of tissues or organs of a living body, a taken-up cross-sectional image, and stored The difference of the temperature of the predetermined location of the living body obtained from the estimated temperature distribution from the temperature of the predetermined location of the living body repeatedly measured by the thermometer measuring means according to the living body parameter and the set heating condition is reduced. Estimating the temperature distribution on the cross-sectional image while repeatedly correcting the value A parameter distribution estimating means and a parameter inverse estimating means for inversely calculating the biometric parameters according to the estimated temperature and the estimated biometric temperature used for estimating the temperature distribution, wherein the biometric parameter value used in the temperature distribution estimating means is A thermotherapy apparatus characterized in that it is repeatedly modified by the back estimation by the parameter back estimation means. 8. The thermotherapy apparatus according to claim 7, further comprising output control means for controlling the output of the high frequency power generating means in accordance with an estimated temperature of a predetermined part in the living body estimated by the temperature distribution estimating means. 8. The thermotherapy apparatus according to claim 7, wherein the applicator comprises a body bag cooling liquid bag and a constant temperature liquid circulation means for circulating a constant temperature solution in the liquid bag. The constant temperature liquid control according to claim 9, wherein at least one of the temperature and the circulation amount of the constant temperature liquid circulated by said constant temperature liquid circulation means is controlled in accordance with the estimated temperature distribution of a predetermined part in the living body estimated by said temperature distribution estimating means. Thermal treatment apparatus characterized in that it further comprises a means. The method according to claim 9, wherein the means for setting a tumor region to be treated on the cross-sectional image, the means for obtaining a high temperature region exceeding a predetermined temperature from the estimated temperature distribution, and the maximum temperature of the tumor region is a predetermined control temperature value. Output control means for applying a high frequency power output to the electrode when less than the control temperature value, and for reducing the high frequency power to be applied when the control temperature value is lower than the control temperature value; And thermostatic control means for increasing the circulating fluid temperature or reducing the amount of circulation when the hot zone is smaller than the tumor zone. 8. The storage means according to claim 7, wherein the means for setting the tumor area to be treated on the cross-sectional image, the storage means for storing in advance a plurality of the set warming conditions, and the warming conditions suitable for the taken cross-sectional image and the set tumor area are stored in the storage means. And a means for selecting from among the plurality of warming conditions stored. A thermal therapy apparatus comprising an applicator having an electrode for applying a high frequency power to a living body, and a high frequency power generating means for generating a high frequency power applied to the electrode, comprising: a cross-sectional image taking means for taking a cross-sectional image of a living body; Notification of treatment conditions for determining and notifying at least one condition of the size and position of the electrode most suitable for the treatment, high frequency power, and application time according to the biological parameter storage means for storing the tissue or organ parameters of the living body and the taken cross-sectional image. Means for estimating the temperature distribution on the cross-sectional image of the living body using the living body parameters stored in the treatment condition, and an output means for displaying or recording the estimated temperature distribution. Thermotherapy device. 15. The thermotherapy apparatus according to claim 13, wherein the applicator includes a liquid bag for cooling the body surface, and further includes constant temperature liquid circulation means for circulating the constant temperature solution in the liquid bag. 15. The thermotherapy apparatus according to claim 13, wherein the treatment condition notification means informs at least one of the temperature and the precooling time of the liquid bag as an optimal treatment condition. Means for inputting a cross-sectional image into a living body, means for clarifying the boundaries of different biological tissues in the input cross-sectional image, storage means for previously storing biometric parameters for each of the plurality of biological tissues, and And a temperature estimating means for estimating the temperature distribution generated by the applied electric field corresponding to the input cross-sectional image using the intensity of the applied electric field and the biometric parameters stored in the storage means. Device. The treatment plan support apparatus according to claim 16, wherein the means for clarifying extracts the outline of the living tissue by image processing of the input cross-sectional image. 17. The treatment plan support apparatus according to claim 16, wherein the means for clarification is means for inputting data indicative of contours of living tissue. 17. The apparatus according to claim 16, further comprising: temperature measuring means for measuring a temperature of a predetermined part of the living body and means for correcting the biometric parameter according to a difference between a temperature measured by the measuring means and a temperature estimated by the estimating means. Treatment plan support device, characterized in that provided. The treatment plan support apparatus according to claim 19, wherein the correction means modifies the biometric parameter such that the difference between the measured temperature and the estimated temperature is small. 21. The treatment plan supporting apparatus according to claim 20, wherein the correcting means estimates a new biometric parameter using the biometric parameter used in the estimating means and the measured temperature and the estimated temperature at least at two points in time. The data representing the cross-sectional image of the living body is taken in to a computer, the boundary between different biological tissues in the cross-sectional image displayed by the data taken into the computer is clarified, and the intensity of the electric field and the individual parts of the biological tissue are cleared. And estimating a temperature distribution generated by an electric field applied to the living body on the cross-sectional image using a biometric parameter set in advance. The method according to claim 22, wherein the boundary is clarified by extracting the outline of the biological tissue by the computer image processing of the cross-sectional image. 23. The method of claim 22, wherein the boundary is clarified according to data representing the contour of the living tissue input to the computer. 23. The computer-implemented method according to claim 22, wherein the data indicative of the temperature measured for the location of the living body is taken into the computer, and the biological parameter is modified according to the difference between the measured temperature and the estimated temperature. Method of processing temperature distribution data. 27. The method of claim 25, wherein the biometric parameter is modified to reduce the difference between the measured temperature and the estimated temperature. 27. The estimated temperature distribution data of a living body by a computer according to claim 26, wherein a new biological parameter is estimated using the biological parameter used for the temperature distribution estimation and at least the measured temperature and the estimated temperature at that time. Treatment method.