JP3476871B2 - Fault surface temperature distribution display method and apparatus - Google Patents

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a method and apparatus for displaying a temperature distribution on a tomographic plane of a heated object such as a human body in high frequency heating treatment.

[0002]

2. Description of the Related Art Conventionally, there is known a high-frequency heating treatment apparatus for radiating and supplying high-frequency energy from a pair of electrodes sandwiching a living body to heat-treat an affected part of the living body (Japanese Patent Laid-Open No. 55-55). -130675, JP-A-56-80265). This high-frequency hyperthermia treatment apparatus heats both the abnormal cell tissue that constitutes cancer and other tumors and the surrounding normal cell tissue within a temperature range of 40 ° C. or higher to normalize the former abnormal cell tissue. Focusing on the fact that the temperature is higher by 2 to 2.5 ° C. than that of cellular tissue, while maintaining normal cellular tissue at 43 ° C. or below that does not necrosis,
The temperature was raised up to around 5 ° C to prevent necrosis and collapse.

Therefore, in such a device, it is extremely important to monitor the temperature in the living body. Therefore, during the heating treatment, a required number of needle-shaped needles are radiated into the body to radiate high frequency energy in order to monitor the temperature in the living body. The temperature was measured by inserting a thermometer.

[0004]

However, since the high-frequency energy radiated from the electrodes of the heating treatment apparatus is not uniform depending on the location and depends on the electrode structure and the position of the affected part of the living body, it is necessary to measure the body temperature. If the number of thermometers is small, there is a possibility that temperature measurement may not be performed appropriately, while if a large number of thermometers are used, temperature monitoring may be performed favorably, but the pain of the patient will increase. In addition, actually, it is unrealistic to puncture the needle at several points or more, and therefore there is a certain accuracy limit in measuring the body temperature.

The present invention has been made in view of the above,
For example, the in-vivo temperature distribution is obtained using the high-frequency energy distribution between electrodes, the characteristics of the living body, etc., and this can be displayed so that it can be used as important information for temperature monitoring during heating treatment. The present invention provides a method and apparatus for displaying a temperature distribution on a fault plane.

[0006]

According to the present invention, the temperature T (x, y) i + 1 at each part of the tomographic plane is calculated based on the previous calculated value T (x, y) i when a contrast agent is not used. The temperature rise rate D0 (x, y) due to the density, the temperature rise rate β · e (x, y) due to the high frequency energy, and the cooling efficiency U (x, y) due to the temperature rise were calculated and calculated. The temperature T (x, y) i + 1 of each part is displayed (claim 1 ).

The cooling efficiency U (x, y) is the temperature increase contribution rate D0 (x, y) due to the density when the contrast agent is not used and the temperature increase contribution rate D1 (x, y due to the density when the contrast agent is used. y) and the correction coefficient K (x, y) (= [D0
(x, y) −D1 (x, y)] · U (T) / n), and the correction coefficient K
Multiplying by (x, y), more practical cooling efficiency U (x, y) ′ = K
It may be corrected to (x, y) · U (x, y) (Claim 2 ).

The high-frequency energy amount detecting means is supplied to the object to be heated from the electromagnetic field detecting means for detecting the strength of the electromagnetic field in the vicinity of the object to be heated and the detected electromagnetic field strength. It may be composed of an arithmetic means for calculating the amount of high frequency energy (claim 3 ).

Further, the display may be performed by a color signal (claim 4 ) or by a density signal (claim 5 ). Furthermore, we installed a thermometer in the proper place on the fault plane,
It is preferable to correct the calculated temperature with the actual temperature from this thermometer (claim 6 ).

[0010]

According to the present invention, the temperature T (x, y) i + 1 at each part of the fault plane is
Is based on the previous calculated value T (x, y) i, the temperature rise contribution rate D0 (x, y) due to the density when the contrast agent is not used, the temperature rise rate β based on the high frequency energy amount, and the temperature according to the high frequency energy distribution. Increase contribution rate e (x, y) and cooling efficiency U (x, y) accompanying temperature rise
It is repeatedly calculated by a predetermined arithmetic expression in consideration of the above.
Then, the calculated temperature T (x, y) i + 1 of each part is superimposed on the tomographic plane and sequentially displayed on the display means (claim 1 ).

Further, according to the present invention, the temperature increase contribution rate D0 (x, y) due to the density when the contrast agent is not used and the temperature increase contribution rate D1 (x, y) due to the density when the contrast agent is used are actually used. A correction coefficient K (x, y) based on the blood flow of is calculated, and the cooling efficiency U (x, y) is multiplied by the correction coefficient K (x, y) to obtain the cooling efficiency U (x corresponding to the actual blood flow. , y) ′ is calculated. And the temperature T of each part of the fault plane
(x, y) i + 1 is repeatedly calculated based on the previously calculated value T (x, y) i by a predetermined calculation formula that takes into consideration the cooling efficiency U (x, y) ′ according to the actual blood flow. (Claim 2 ).

Further, according to the present invention, the electromagnetic field intensity in the vicinity of the object to be heated is detected, the high frequency energy amount is calculated based on the detection result, and the temperature increase coefficient β is calculated according to the calculation result. Is calculated (claim 3 ).

Further, according to the present invention, the temperature display on the display means is performed for each color (claim 4 ). Further, the temperature display on the display means is performed for each concentration (claim 5 ). Further, the actual temperature from a thermometer installed at a proper position on the fault plane can be used to correct the calculated temperature by the calculating means (claim 3
6 ).

[0014]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS FIG. 1 shows a block diagram of a high-frequency heating treatment apparatus to which a tomographic plane temperature distribution display apparatus according to the present invention is applied.

The high-frequency heating treatment apparatus is a computer 1 for calculating the temperature inside the body, a camera 5 and an amplifier 6 for taking in the density distribution information of the tomographic plane, a heating section 7 for irradiating the affected area with high-frequency energy, and the obtained body temperature. Display section 8
And the operation units 9 and 91.

The computer 1 centrally controls the whole of the high-frequency heating treatment apparatus. In addition to the control program,
A ROM 2 in which arithmetic expressions to be described later, various kinds of information regarding a living body, distribution information of high-frequency energy, and the like are stored, and a RAM 3 for temporarily storing processing contents are connected.

Reference numeral 4 is a tomographic photograph having density (density) distribution information of the tomographic plane. This tomographic photograph 4 is a CT (Computer).
Tomography) X-ray photograph and MRI (Mag
It is a distribution photograph of tissue by netic Resonance Imaging. The density information may be not only the weight density but also the hydrogen density.

The camera 5 has a large number of CCDs (Ch
It has an arge-Coupled Device (solid-state imaging device) and reads the tomographic photograph 4 as density distribution information. The read information is converted into an electric signal and input to the amplifier 6 as a time series signal. The density distribution of the tomographic photograph 4 is obtained by the camera 5.
For example, it is read in 256 gradations, guided to the computer 1 via the amplifier 6, converted into a required number of levels, for example, 16 levels so as to be normalized so as not to be influenced by the photographic density, and stored in the RAM 3.

The 16-level signal is assigned an attribute like D1 to D16 so that the process of changing the coefficient can be easily performed. The computer 1 temporarily stores the captured image pickup signal in the RAM 3 or another display memory, and then displays it on the display unit 8 as a still image. Also this 1
The 6-level image pickup signal is stored in an external memory (not shown) for convenience of later use.

When the density distribution information of the tomographic image is transmitted through, for example, communication means or is fetched from an external memory, the interface may be used instead of the camera 5 to receive the data.

The operation unit 9 is a keyboard operation unit having a ten-key pad and keys for operating instructions.
The image is corrected to an appropriate shading state as necessary to correspond to the biological characteristics described later. In this grayscale correction, for example, the highest density portion of the tomographic photograph 4 is regarded as a bone, and the density of this bone is used as a reference to sequentially correct the density below that. Further, the keyboard operation section 9 is used to select various information as will be described later, for example, to select and instruct the electrode type to match the type of electrode actually used.

The operation unit 91 is a trackball (or mouse) operable on the image displayed on the display unit 8.
Then, for the tomographic photograph 4 displayed as a still image on the display unit 8,
The area is used to specify a temperature calculation to be described later. It should be noted that the extraction of the living body contour for designating the calculation area may be performed by the computer 1 using an image processing technique.

The heating unit 7 has a known high-frequency energy generating structure, and is provided with a pair of electrodes 71, 72, a high-frequency generating unit 73 of several MHz, an impedance matching unit 74, and a high-frequency power meter 75. Yes (see FIG. 2).
The pair of electrodes 71, 72 are closely arranged so as to sandwich the affected part 121 on the cross section of the living body corresponding to the tomographic photograph 4, and in this state, high frequency energy such as high frequency electric field or magnetic field from the high frequency generating part is applied. The irradiation is performed mainly on the affected area 121.

The distribution state (high-frequency electric field distribution) of the high-frequency energy emitted from the pair of electrodes 71, 72 between the electrodes is stored in the ROM 2 in advance. Here, the preliminary measurement of the distribution state of the high frequency energy will be described.

As the dummy, for example, agar, which has a uniform density and approximates the human body density, is used.
In the state where the two are closely arranged, high frequency energy of rated power is radiated for a certain period of time. After radiating for a certain period of time, the irradiation cross section of the high frequency energy is cut, and the temperature distribution is measured on this cross section using a remote temperature measuring device such as thermography. Since the rising temperature of the object to be heated is uniquely determined according to the strength of the supplied high-frequency energy, the cross-sectional temperature distribution corresponds to the strength distribution of the high-frequency energy under the condition of uniform density. Therefore, this temperature distribution is replaced with the high frequency energy distribution and stored in the ROM 2.

When electrodes 71, 72 having different sizes, shapes, etc. are used depending on the position of the affected part 121, etc., and the dimension between electrodes is different, the distribution is the same for each type of electrode and dimension between electrodes. Information is measured and stored in the ROM 2 in correspondence with the type of electrode.

Next, various characteristics of the living body which are loaded into the ROM 2 in advance will be described. Various characteristic values shown in Table 1 below are previously stored in the ROM 2.

[0028]

[Table 1]

It should be noted that (x, y) indicates the position of each part of the tomographic plane, and corresponds to the address of the RAM 3, for example.

In Table 1, the temperature rise contribution rate e (x, y) is a value uniquely determined from the high frequency energy distribution information. The value e (x, y) may be a value obtained by normalizing the measurement temperature of the thermography described above. The temperature rise contribution rate D0 (x, y) is a value determined according to the density, and the density information (for example, ρ (x, y)) when the contrast agent is not used, which is captured from the camera 5, is Conversion is set in the calculation described later.

The cooling efficiency U (T) is a value related to the temperature of the living body, and is set by paying attention to the fact that the more the living body is heated, the larger the heat dissipation becomes. The cooling efficiency U (T) is empirically determined for each organ, and this general value can be used. However, since the heat radiation is mainly performed by the blood flow, and the actual blood flow state is different for each organ, it is desirable to use a more practical cooling efficiency U (T) ′ in consideration of the heat radiation effect by the blood flow. Better. The cooling efficiency U (T) 'will be described later.

Further, β0 represents a temperature increase coefficient of the high frequency energy with respect to the rated power P0, and is calculated by the following expression 3.

[0033]

[Equation 3]

Incidentally, this temperature rise coefficient β0 is e (x, y) =
It becomes 1 when D0 (x, y) = 1.

If the output of the high frequency generator 73 of the heating unit 7 always outputs the rated power P0, the temperature rise coefficient β0 is calculated in advance according to the volume V of the heating unit of the object to be heated. The calculation result may be stored in the ROM 2, but if the output can be arbitrarily changed, it is necessary to convert the temperature rise coefficient β to the actually output power P. In this case, the output power P is used in place of the rated power P0, and the ratio R (= P / P0) of the actual output power P to the rated power P0 is calculated by the above Equation 3 or the temperature rise coefficient β0 calculated in advance. The temperature rise coefficient β
(= R · β0) can be calculated.

Next, the calculation of the cross section surface temperature will be described. The temperature T (x, y) i + 1 of each part is calculated in advance by repeatedly calculating the following Expression 4.

[0037]

[Equation 4]

The initial temperature T0 can be measured using a normal thermometer or the like. Further, the temperature rise coefficient β is calculated by correcting the temperature rise coefficient β0 with respect to the equation 3 to the rated power P0 based on the output power P of the high frequency generator 73 of the heating element 7 as described above. The output of the high frequency generator 73 of the heating element 7 is the rated par P0.
In this case, the temperature increase coefficient β0 for the rated power P0 may be used as the temperature increase coefficient β. In particular, e (x, y)
= D0 (x, y) = 1, the temperature rise coefficient β0 = 1, so β0 · e (x, y) · D0 (x, y) = 1, and the second term of the above equation 4 The temperature T (x, y) i + 1 can be calculated without consideration.

By the way, the heating section 7 is provided with the impedance matching section 74, but the electrodes 71 and 72 are pressed against the living body (the body to be heated) and the matching state changes due to the movement of the living body. It is difficult to perfectly match the electrodes 71, 72 and the living body. Therefore, the high-frequency power supplied from the high-frequency generator 73 of the heating unit 7 to the living body via the electrodes 71 and 72 is likely to cause a transmission loss. On the other hand, the temperature rise due to the dielectric heating of the living body is caused by the heat generation due to the dielectric loss of the high frequency electric field, and is directly related to the high frequency energy distribution between the electrodes 71 and 72, that is, the amount of the high frequency energy actually supplied to the living body. It is related.

Therefore, it is preferable to calculate the temperature rise coefficient β based on the high frequency actually supplied to the living body. That is, it is preferable to apply the temperature rise coefficient β ′ calculated by using the equation 3 by the high frequency power P ′ actually supplied to the living body to the equation 4.

A part of the high frequency power actually supplied to the electrodes 71 and 72 causes a radiation loss (a loss due to radiation from the electrodes 71 and 72 as electromagnetic waves in space). High frequency power P'actually supplied to the living body, that is, high frequency power P'that contributes to dielectric heating.
It is generally difficult to measure directly. But,
According to the applicant, the strength of the electromagnetic field in the vicinity of the living body has a good correlation with the high frequency power P ′, and the temperature T using the temperature rise coefficient β ′ calculated from the strength of the electromagnetic field.
It was confirmed that when (x, y) i + 1 is calculated, the error between the calculation result and the actual temperature becomes smaller.

Therefore, the intensity W of the electromagnetic field in the vicinity of the living body can be equivalently treated as the high frequency power P ', and the correlation function F (= F (=) of the electromagnetic field intensity W and the temperature rise coefficient β'. If k · W, k; a proportional coefficient) is calculated in advance by experiments or the like, the correlation function F can be replaced with the above-mentioned equation 3.
The temperature rise coefficient β ′ can be calculated from the electromagnetic field strength W by using

FIG. 2 is a schematic diagram showing a method for measuring the electromagnetic field strength. In the figure, the electromagnetic field intensity meter 13 is composed of a sensor unit 131 composed of a minute coil and a receiver 132 that receives an electromagnetic field. The sensor unit 131 has a high-frequency magnetic field H on the coil surface in the vicinity of the living body 14. They are arranged so that they intersect at right angles.

From the high frequency generator 73 of the heating unit 7 through the impedance matching unit 74 and the high frequency power meter 75, the living body 1
When high frequency power is supplied to the electrodes 71, 72 attached with the electrode 4 interposed therebetween, a high frequency electric field E is generated between the electrodes 71, 72.
(The same figure, solid line arrow) occurs, the high frequency electric field E
A high-frequency magnetic field H (indicated by a dotted arrow in the figure) is generated around. The sensor unit 131 of the electromagnetic field intensity meter 13 picks up the magnetic field component of the electromagnetic field, and the receiver 132 detects the intensity W of the high frequency magnetic field H. The receiver 132 converts the electromagnetic field strength W into an energy amount (W / m ² ), an electric field strength (V / m) or a magnetic field strength (A / m), and is capable of outputting the detected strength W of the high frequency magnetic field H. Output in the set unit. The intensity W of the electromagnetic field may be calculated by detecting the electric field component of the electromagnetic field.

If the correlation function F calculated in advance by experiments or the like is stored in the ROM 2 and the detection result W of the receiver 132 is fed back to the computer 1, the detection is performed from the correlation function F. The temperature rise coefficient β ′ is calculated using the result W, and
Thus, the temperature T (x, y) i + 1 of each part is automatically calculated.

A conversion table for the electromagnetic field strength W and the temperature rise coefficient β'is stored in the ROM 2 instead of the correlation function F, and the temperature rise coefficient is directly calculated from the electromagnetic field strength W by the conversion table. β ′ may be obtained.

Next, a method of calculating the cooling efficiency U (T) 'will be described. For the cooling efficiency U (T) ′, for example, the actual blood flow state of each part is examined, and the correction coefficient K (x, y) in consideration of the heat radiation effect based on the actual blood flow is calculated, and the correction coefficient K (x , y) can be calculated by multiplying the cooling efficiency U (T). The correction coefficient K (x, y) is calculated by, for example, the tomographic photograph 4 taken without injecting the contrast agent and the tomographic photograph 4 in which the blood flow state is further revealed by injecting the contrast agent by the camera 5. It can be calculated by reading and comparing the read images and examining the actual blood flow state of the organ near the affected area. That is, assuming that the temperature rise rate due to the density obtained from the tomographic photograph 4 taken using the contrast agent is D1 (x, y) and the resolution of the density is n, the correction coefficient K (x, y) is given by It is represented by.

[0048]

[Equation 5]

Therefore, by calculating the temperature T (x, y) i + 1 of each part by the following expression 6 instead of the above expression 4, a more realistic temperature distribution can be calculated.

[0050]

[Equation 6]

As described above, the computer 1 supplies the imported density distribution information, that is, D0 (x, y) and the prestored high frequency energy distribution, that is, e (x, y) from the heating unit 7. Based on the temperature T (x, y) i + 1 of each part of the fault plane based on the value corresponding to the amount of high frequency energy, that is, the temperature rise coefficient β or β ', etc. calculate.

The calculated temperature T (x, y) i + 1 is displayed at the corresponding position (x, y) on the display unit 8. This display may be, for example, gradation display in black and white tones corresponding to temperature, or in accordance with temperature, white, red, pink, yellow, green, blue You may make it display by color so that it may become light blue. Further, the specific position, or the designated position around the affected area and its periphery may be displayed as it is in numerical data, for example, in a tabular form.

FIG. 3 is a diagram showing a display state of the display section 8. In the figure, 71 and 72 are electrodes, and 10 is a biological tomographic plane. In the living body tomographic plane 10, there are a spinal cord 11, respective organs 12, 12, ... It should be noted that although the display by tone or color is omitted in the drawing, the display of the tomographic plane may be performed not only by the contour display described above but also by the contour display for a boundary having a certain density difference. As a result, it is possible to clearly display the difference in density between the organs, the organs and the affected part in the organs by the contour lines, and the graspability of the position, shape, etc. of the organs is improved.

FIG. 4 is a flow chart for explaining the operation of displaying the temperature distribution by the high frequency heating treatment apparatus.

First, the power source is turned on (S1),
In this state, for example, a CT film, which is a tomographic photograph 4, is set at an appropriate position on the front surface of the camera 5 (S3). Then, the camera 5 has a built-in photometric unit and an automatic focus adjusting unit.
The focus, zoom and aperture are automatically adjusted (S5). This operation may be manually set by the operator. Then, by the operation from the keyboard operation unit 9,
The tomographic photograph 4 of the CT film is taken in as image data (S7), and is subjected to shading correction if necessary,
The computer 1 converts 256 gradations into 16 gradations (S9).

Then, unnecessary image data is deleted from the captured image according to an instruction from the trackball 91, and the contour of the living body for designating the calculation region of the equation 4 is extracted (S11). This image contour extraction processing may be automatically performed using an image processing technique.

Next, the electrodes 71, 72 actually used
The type of is selected and set by the keyboard operating unit 9, and the electrode position and inclination are further instructed (S15). The electrode position is the dimension between the electrodes, and the inclination is for giving the high-frequency energy distribution stored in the ROM 2 rotation suitable for the electrode inclination.

Thereafter, the calculation for calculating the temperature is started based on the equation 4 (S17). That is, first, after the heating unit 7 is driven and power adjustment is performed, the high-frequency energy P, that is, the input power P data is received, and is input based on the received data, such as the electric field distribution and the biological body. Using the density distribution, the temperature is calculated for each pixel in the area specified in S11 (S19). In the case of a device in which high-frequency energy is constantly output at a rated value, the coefficient β may be set to a constant value, for example, “1”, that is, may be calculated without consideration.

Next, the temperature distribution obtained by the above equation 4 is converted into corresponding color signals and displayed on the display unit 8 which is a monitor (S21). At this time, if the positional relationship between the image contour and the temperature distribution is made to correspond to each other, the superimposed display can be performed. And when the temperature calculation is completed for the specified range,
The calculation is repeated by returning to the first pixel position (S2).
3). By repeating the calculation in this way, it is possible to continuously calculate the current temperature based on the previous temperature.

When calculating the temperature of each part based on the above equation 6, in steps S3 to S9, the image data of the CT film which does not use the contrast agent is taken in, and between steps S9 and S11. While capturing the image data of the CT film that uses the contrast agent in
The correction coefficient K (x, y) may be calculated from both image data, and the calculation for temperature calculation may be performed based on the equation 6 instead of the equation 4 in steps S17 and S19.

Further, if the processes of steps S19 to S23 are performed every predetermined time, for example, every one minute, it becomes easy to quantitatively grasp the temperature rise change. Alternatively,
Immediately after the end of step S23, the temperature calculation may be started by returning to the first pixel, or the required calculation cycle may be manually set. Further, the calculation cycle may be appropriately changed according to the rising gradient of the temperature so that the change in the temperature can be effectively tracked. By doing so, it is possible to display the temperature in more real time. In this case, β, β ', e (x, y), D (x, y), D0
For each value of (x, y), D1 (x, y), and U (T), it is necessary to store a plurality of numerical tables corresponding to the calculation cycle.

In the present embodiment, the current temperature is calculated based on the previous temperature, but the present invention is not limited to this calculation method, and the current temperature is calculated based on the initial temperature each time. The method of doing may be adopted.

In addition, one or a small number, for example, a needle thermometer, is inserted at an appropriate position (x, y) in the fault plane,
By comparing the deviation between the actual temperature from this thermometer and the temperature obtained by calculation, and if there is a deviation, it is possible to correct the deviation so that a more accurate temperature display is possible.

[0064]

As described above, according to the present invention,
A tomographic plane temperature distribution display device for superimposing and displaying a temperature distribution of a heated body, which is dielectrically heated by a high frequency, on a tomographic plane of the heated body. Since the temperature increase coefficient β and the cooling efficiency U (T) are taken into consideration, the current temperature T (x, y) i + 1 is repeatedly obtained based on the previous temperature T (x, y) i. , Can be closer to the actual temperature.

Further, the cooling efficiency U (T) is calculated by using the density increase contribution ratio D0 (x, y) due to the density when the contrast agent is not used and the temperature increase contribution ratio D1 (x, y) due to the density when the contrast agent is used. Since the correction coefficient K (x, y) obtained from is multiplied to correct the cooling efficiency U (T) 'in consideration of the heat radiation effect of the actual blood flow, each part of the heating element is corrected. The calculation accuracy of the temperature is further improved.

Further, the intensity of the electromagnetic field in the vicinity of the object to be heated is detected, and the amount of high frequency energy supplied to the object to be heated is calculated based on the detection result. The temperature rise coefficient β becomes closer to the actual one, and the calculation accuracy of the temperature of each part to be heated is further improved.

Further, since the obtained temperature is displayed in stages by density and color, it is easy to grasp the temperature. Further, since it is possible to correct the actual temperature, more accurate temperature display can be performed.

[Brief description of drawings]

FIG. 1 is a block configuration diagram of a high-frequency heating treatment device to which a tomographic plane temperature distribution display device according to the present invention is applied.

FIG. 2 is a schematic diagram showing a method for measuring the strength of an electromagnetic field at a position near a living body.

FIG. 3 is a diagram showing a display state of a display unit.

FIG. 4 is a flowchart illustrating an operation of displaying a temperature distribution by the high-frequency heating treatment device to which the present invention is applied.

[Explanation of symbols]

1 computer 2 ROM 3 RAM 4 tomography 5 camera 6 amplifier 7 heating section 71,72 electrodes 73 High frequency generator 74 Impedance matching section 75 electricity meter 8 Display 9,91 Operation part 13 Electromagnetic field strength meter 131 Sensor part 132 Receiver section 14 living body

Continuation of front page (56) Reference JP-A-4-49977 (JP, A) JP-A-5-245217 (JP, A) JP-A-5-31080 (JP, A) JP-A-5-95909 (JP , A) JP-A-63-252172 (JP, A) Actual Kaihei 1-107307 (JP, U) (58) Fields investigated (Int.Cl. ⁷ , DB name) A61N 1/40 A61B 5/04

Claims (6)

(57) [Claims] 1. A heating target object that is dielectrically heated by high frequency
A fault whose temperature distribution is superimposed and displayed on the fault plane of the heated body
A surface temperature distribution display device, comprising:
Information capturing means for capturing density distribution information, and this information capturing
The density increase information captured by the means is used to calculate the temperature rise contribution ratio D0 (x,
The first storage means for converting to y) and storing the high frequency
Energy in high-frequency energy distribution between applied electrodes
-The temperature rise contribution rate e (x, y) due to the intensity is stored
2 storage means and high-frequency energy supplied to the heated body
The detection means for detecting the amount of energy and the detected high frequency energy
First calculation for calculating the temperature rise coefficient β according to the amount of rugies
Means and the temperature T (x, y) i + 1 of each part of the fault plane is calculated by the following equation 1.
Second calculation means for repeatedly executing the formula to calculate, and
And a display means for displaying the temperature T (x, y) i + 1 of each part
A fault surface temperature distribution display device. [Equation 1] 2. A fault surface temperature distribution display device according to claim 1.
At the time of using the contrast agent captured by the above information capture means,
The density distribution information of is converted into the temperature rise contribution rate D1 (x, y),
A second storage means for storing the third storage means;
Replaces the temperature T (x, y) i + 1 of each part of the fault plane with the above equation 1.
Japanese to repeatedly output calculated by executing the following Equation 2 arithmetic expression
Display device for temperature distribution of fault surface. [Equation 2] 3. A fault surface temperature distribution table according to claim 1 or 2.
In the apparatus shown, the high-frequency energy detecting means,
An electromagnetic wave that detects the strength of the electromagnetic field in the vicinity of the object to be heated.
From the magnetic field detection means and the detected electromagnetic field strength, the high frequency
It is characterized by comprising an arithmetic means for calculating the amount of energy
A device for displaying temperature distribution on a fault plane. 4. The calculation result is displayed on the display means.
4. The method according to claim 1, wherein the color signal is used.
The fault surface temperature distribution display device according to any one of 1. 5. The calculation result is displayed on the display means.
It is performed by using a density signal.
3. The fault surface temperature distribution display device according to any one of 3 above. 6. A tomographic plane according to claim 1.
In the temperature distribution display device, at the appropriate place (x, y) on the fault plane
Install one or more thermometers and use the measured temperature value
A feature characterized by adding a correction to the calculation result of the calculation means.
Layer surface temperature distribution display device.