JP2005270141A - Pyrotherapeutic instrument - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To appropriately determine a completion time of coagulation without directly grasping the coagulation state of an object tissue. <P>SOLUTION: This pyrotherapeutic instrument measures electric energy supplied from an output start to a set time T1 with the treatment object tissue clamped between the treatment parts 9 of coagulating/incising forceps 2, measures the dimension of the tissue to be coagulated from the electric energy, sets the electric energy necessary for the tissue coagulation based on the dimension of the tissue, supplies electric power corresponding to the electric energy to a heating element part 21 and coagulates and incises the biotissue. <P>COPYRIGHT: (C)2006,JPO&NCIPI

Description

  The present invention relates to a fever treatment device, and more particularly, to a fever treatment device that treats a diseased part by applying heat.

  Generally, this type of fever treatment device is used when performing treatment such as incision, coagulation, and hemostasis of an affected part in a surgical operation or an internal medicine operation. This fever treatment apparatus has a treatment part with a built-in heat generating means for heating the affected part, and heat generated by the heat generating means is given to the affected part through the treatment part, so that treatment such as incision, coagulation, and hemostasis is performed. I do.

As such a heat treatment apparatus, for example, Japanese Patent Publication No. 53-9031, as a heat generation means, has a plurality of divided heater segments and includes a treatment section that can heat each heater segment independently. Technology has been proposed. The treatment section disclosed in this publication performs treatment by applying heat generated in a plurality of heater segments set at the same temperature to the affected area.
Japanese Patent Publication No.53-9031

  However, the exothermic treatment device disclosed in the above-mentioned publication has a problem that the coagulation completion time cannot be accurately determined because the coagulation state of the tissue cannot be directly grasped during the coagulation treatment.

  In view of the above circumstances, the present invention provides an exothermic treatment apparatus that can accurately determine the completion time of coagulation without directly grasping the coagulation state of the tissue to be treated and can perform a coagulation incision in an optimal time. The purpose is to provide.

  In order to achieve the above object, a heat treatment apparatus according to the present invention comprises a temperature measuring means for measuring the temperature of a heat generating part provided in a treatment instrument, an applied power detecting means for measuring the power supplied to the heat generating part, and at least constant. Treatment tissue load amount detection means for detecting the size of the tissue to be treated based on the power supplied during the period, and coagulation for setting the amount of power necessary for tissue coagulation based on the detection result of the treatment tissue load amount detection means It is characterized by comprising required power setting means and output power control means for supplying the amount of power set by the coagulation required power setting means to the affected area.

  According to the present invention, since the amount of electric power necessary for tissue coagulation is set according to the size of the tissue, it is possible to accurately determine the completion time of coagulation without directly grasping the coagulation state of the tissue to be treated. Coagulation and incision can be performed at an optimal time.

  Hereinafter, an embodiment of the present invention will be described with reference to the drawings.

(First form)
1 to 13 relate to a first embodiment of the present invention, FIG. 1 is an overall configuration diagram of a heat treatment device, FIG. 2 is an external view of a device body provided in the heat treatment device, and FIG. 3 is provided in a heat treatment device. 4 is a side view of the coagulation / incision forceps, FIG. 5 is a schematic perspective view of the heat treatment section viewed from the side, and FIG. 6 is a schematic perspective view of the heat treatment section viewed from the top. Is a top sectional view of the heat treatment section, FIG. 8 is a side sectional view of the heat treatment section, FIG. 9 is a circuit block diagram of a control circuit provided in the heat treatment apparatus, and FIG. FIG. 11B is a waveform diagram showing a set temperature set in accordance with the state of FIG. 11A, and FIG. 11 is a graph showing calculated tissue load, treatment tissue size, and coagulation required power amount. FIG. 12 is a flowchart showing a power control routine.

  Reference numeral 1 in FIG. 1 denotes an exothermic treatment device. The coagulation / incision forceps 2 as a treatment tool and the coagulation / incision forceps 2 are detachably connected to each other, and power is output to the heating element portion 21 of the coagulation / incision forceps 2. And an apparatus main body 3 for driving control. Further, the coagulation / incision forceps 2 incorporates a heating element portion 21 (see FIG. 4) as a heating portion.

  As shown in FIGS. 1-3, the apparatus main body 3 has the front panel 3a and the back panel 3b. The front panel 3a includes a connector receiving portion 11, a power switch 12 for turning on / off the power, a temperature level UP switch 13a and a temperature level DOWN switch 13b, a temperature level display portion 15, an output display portion 16, a forceps abnormality display portion 17a, The power supply abnormality display part 17b, the warning means 17c, etc. are provided.

  The connector receiving portion 11 allows the main body connector 5 provided on the coagulation / incision forceps 2 to be detachably connected. The temperature level UP switch 13a and the temperature level DOWN switch 13b are provided on the coagulation / incision forceps 2. The exothermic temperature level for the exothermic treatment section 7 is set to, for example, 1 to 5 levels. The heat generation temperature level is an initial setting temperature that is set when a set temperature level output switch 6b provided in the foot switch 6 described later is turned on.

  The temperature level display unit 15 displays the temperature level set by the temperature level UP switch 13a and the temperature level DOWN switch 13b by the number of lighting of a plurality of LEDs arranged. The output display unit 16 informs that the heating element unit 21 (see FIG. 4) provided in the coagulation / incision forceps 2 is energized by turning on an LED or the like. The forceps abnormality display unit 17a is for informing the LED when the coagulation / incision forceps 2 is abnormal. The power supply abnormality display unit 17b is for notifying by turning on an LED or the like when there is an abnormality in the internal circuit. The warning unit 17c is driven when an abnormality is detected to notify the operator of the abnormality, and is configured by a buzzer, a speaker, and the like.

  As shown in FIG. 3, a foot switch connector receiving portion 18, a power inlet 19 and the like are disposed on the back panel 3b.

  On the other hand, as shown in FIG. 4, the coagulation / incision forceps 2 is provided with a treatment portion 9 at the distal end portion and a handle portion 20 at the proximal end side. The treatment section 9 has a heat treatment section 7 and an elastic receiving section 8 that faces the heat treatment section 7. Further, the heat generating treatment section 7 has a heat generating element section 21 built therein. The connection cable 4 is connected to the heating element portion 21. The connection cable 4 extends rearward from the rear end of the handle portion 20, and a main body connection connector 5 is provided at the rear end. The main body connection connector 5 is connected to a connector receiving portion 11 provided on the front panel 3 a of the apparatus main body 3.

  The main body connection connector 5 of the coagulation / incision forceps 2 is connected to the connector receiving portion 11, the handle portion 20 is operated, the living tissue is grasped between the heat treatment portion 7 and the elastic receiving portion 8, and the device main body 3 By causing the heat treatment section 7 to generate heat by energization from the body, the grasped living tissue is coagulated and incised.

  The number of heat generating element portions 21 varies depending on the type of forceps set for each treatment purpose. Since the number of the heating element portions 21 cannot be easily recognized from the outside, in this embodiment, as shown in FIG. 9, the identifier 10 is built in the main body connection connector 5, and the main body connection connector 5 is connected to the connector receiving portion 11. The number of the heating element portions 21 is identified by the apparatus main body 3 when connected to.

  The identifier 10 is composed of a forceps identifier 10a representing the type of forceps and a heating element identifier 10b representing information on each heating element. Various identifiers such as an electric resistance element and a nonvolatile memory in which identification information is stored in advance can be considered as the identifier 10. The apparatus main body 3 according to the present embodiment can be connected to the coagulation / incision forceps 2 having a maximum of four heating element portions 21 built therein.

  The foot switch 6 is connected to the foot switch connector receiving portion 18 provided on the back surface of the apparatus body 3. The foot switch 6 operates the heat generation of the heat generating element portion 21 and includes a maximum temperature level output switch 6a and a set temperature level output switch 6b. By depressing the maximum temperature level output switch 6a, the temperature of the heating element portion 21 is raised to the maximum level. On the other hand, when the set temperature level output switch 6b is depressed, the heater element 21 is initially set to a temperature (initial set temperature) set by operating the temperature level UP switch 13a or the temperature level DOWN switch 13b.

  As shown in FIGS. 5 and 6, the heat generating element portion 21 includes, for example, three heat generating elements 21 a, 21 b, and 21 c made of the same member, which are thermally coupled to each other and the heat transfer plate 22. It is arranged.

  As shown in FIGS. 7 and 8, the heat treatment section 7 constituting the treatment section 9 has a heat treatment section body 7a, and the heat treatment section body 7a includes a plurality of heat generation elements constituting the heat generating element section 21. Elements 21a to 21c are incorporated. Each of the heating elements 21a to 21c is a thin plate resistor formed on, for example, a ceramic plate, and lead wires 23a to 23c extending from the heating elements 21a to 21c are conductively arranged in the connection cable 4 to be connected to the main body connection connector. 5 is connected to a connector terminal (not shown).

  Since each of the heating elements 21 a to 21 c is thermally coupled to the heat transfer plate 22, the heat generated by these is transmitted to the heat transfer plate 22. In the present embodiment, the heat generating element portion 21 and the heat transfer plate 22 for performing treatment are separate, but they may be integrally formed to form a heat generating treatment portion. Further, the integrally formed heat treatment portion may be formed of a heat resistant metal body (for example, nichrome wire).

  Further, a temperature sensor 41 (see FIG. 9) is installed in the vicinity of the heating element portion 21 in the heating treatment section 7, and temperature information in the vicinity of the heating element portion 21 detected by the temperature sensor 41 is transmitted to the apparatus main body 3. To be processed.

  On the other hand, the elastic receiving portion 8 has an elastic receiving portion main body 8a, and a saw blade portion 24a is disposed on the elastic receiving portion main body 8a via an elastic member 24. The saw blade part 24 a is provided on the heat transfer plate 22 provided in the heat treatment part 7, and the living tissue is gripped between the saw blade part 24 a and the heat transfer plate 22. When the space between the elastic receiving portion 8 and the heat generating treatment portion 7 is closed by closing the handle portion 20, the living tissue is placed between the heat transfer plate 22 of the heat generating treatment portion 7 and the saw blade portion 24 a of the elastic receiving portion 8. It is gripped elastically. In this state, coagulation and incision can be performed by transferring heat from the heat transfer plate 22 to the living tissue.

  As shown in FIG. 9, the apparatus main body 3 includes a heat generation setting unit 31, a memory 32, a CPU 33, an applied power detection unit 34, a temperature measurement unit 35, and output power as means for performing heat generation processing on the heat generating element unit 21. The control means 36, the operation part 37, the foot switch input part 38, the display part 39, the identification means 40, the temperature sensor 41, etc. are provided. Further, the CPU 33 is provided with a treatment tissue load amount calculation means 42 and a coagulation required power amount determination means 43 as treatment tissue load amount detection means, and the memory 32 is connected to the CPU 33.

  The output power control unit 36 controls the output of drive power for generating heat from the heat generating element unit 21. The applied power detection unit 34 calculates the power applied to the heating element unit 21 based on the voltage value and the current value applied to the heating element unit 21.

  The temperature measuring means 35 reads temperature information from the temperature sensor 41 provided in the heat treatment section 7 of the coagulation / incision forceps 2 and measures the temperature in the vicinity of the heat generating element section 21. The identification means 40 reads the information of the identifier 10 provided on the main body connector 5 of the coagulation / incision forceps 2.

  The treatment tissue load amount calculating means 42 provided in the CPU 33 includes the temperature in the vicinity of the heating element portion 21 measured by the temperature measuring means 35, the power detected by the applied power detecting means 34, and the identification information read by the identifying means 40. Based on the above, the load amount of the organization is calculated. The coagulation required power amount determining means 43 provided in the CPU 33 calculates the power necessary for coagulating the tissue based on the load amount calculated by the treatment tissue load amount calculating means 42 and the information stored in the memory 32. decide. The information stored in the memory 32 includes, for example, a tissue load amount Pt [W · t] as shown in FIG. 11, a level indicating the size of the tissue, and a coagulation required power amount [W · t]. There is fixed data such as a table indicating the relationship.

  The apparatus body 3 can be connected to, for example, a coagulation / incision forceps having a heating element portion 21 composed of a maximum of four heating elements, and the apparatus body 3 has a coagulation / incision forceps having a heating element section 21 composed of four heating elements. Are connected, the applied power detection means 34 and the output power control means 36 respectively calculate the load amount and power for four channels corresponding to each heating element.

  The operation unit 37 is a general term for various switches such as the temperature level UP switch 13a and the temperature level DOWN switch 13b provided on the front panel 3a, and the display unit 39 is a display for various displays provided on the front panel 3a. This is the general term for the department.

  The foot switch input unit 38 outputs a signal from the maximum temperature level output switch 6 a provided on the foot switch 6 or the set temperature level output switch 6 b to both the CPU 33 and the heat generation setting means 31.

  When the ON signal from the set temperature level output switch 6b is input via the foot switch input unit 38, the heat generation setting means 31 operates by operating the temperature level UP switch 13a or the temperature level DOWN switch 13b constituting the operation unit 37. The set heat generation temperature (initial setting temperature) information is output to the CPU 33.

  When an abnormality occurs in the coagulation / incision forceps 2, the forceps abnormality display portion 17a is turned on and the warning means 17c is driven to notify the operator of the abnormality.

  FIG. 10 shows the relationship between the amount of electric power applied when performing the coagulation and incision using the coagulation and incision forceps 2 and the set temperature at that time. As shown in the figure, the energization time of the power [W] energized to the heating element portion 21 of the coagulation / incision forceps 2 includes an initial setting time T1 for detecting the coagulation power necessary for coagulating the tissue to be treated, and the treatment. There are three stages: a coagulation required time T2 required for actually coagulating the target tissue, and a necessary time (incision stage time) T3 in the incision stage.

  P1 in the waveform during the initial setting time T1 is the initial power consumption for detecting the necessary coagulation power. In addition, (P1 + P2) in the waveform is the necessary coagulation electric energy required for coagulating the target tissue.

  FIG. 11 shows the relationship between the calculated tissue load amount Pt [W · t] stored in the memory 32, the level indicating the size of the tissue, and the coagulation required power amount (P1 + P2) [W · t]. Indicates the contents of the table shown.

  The relationship between the calculated tissue load amount Pt and the coagulation required power amount (P1 + P2), which is the amount of power necessary for coagulating the target tissue of that magnitude, is determined and set in advance through experiments and the like. Furthermore, based on the calculated tissue load Pt, the size of the target tissue is divided into 1 to 5 levels from the smallest to the largest.

The calculated tissue load Pt is obtained by correcting the initial power consumption P1 with the force capacity of the forceps (heat amount escaping to the forceps) Pk as the power correction value for each treatment tool and the forceps heat capacity difference Po as the initial temperature power correction value. To calculate. That is,
Pt = P1- (Pk-Po) (1)
It becomes. In this case, the calculated tissue load amount Pt may be obtained simply by the following equation.

Pt = P1-Pk (1 ′)
Pt = P1 + Po (1 ″)
The heat capacity Pk of the forceps is a power loss accompanying the heat capacity of the forceps solid, and is a fixed value set in advance for each coagulation / incision forceps 2 to be used. The forceps heat capacity difference Po is a power difference depending on the element temperature (element initial temperature) immediately before the start of output.

  This calculated tissue load amount Pt is calculated by the treatment tissue load amount calculating means 42 provided in the CPU 33.

  Next, the control performed by the treatment tissue load amount calculating means 42 and the coagulation required power amount determining means 43 provided in the CPU 33 will be described according to the power control routine shown in FIG.

  When the power switch 12 of the apparatus main body 3 is turned on, the system is activated. First, the temperature measuring means 35 is based on the output signal from the temperature sensor 41 provided in the heat treatment section 7 of the coagulation incision forceps 2, and the heating element section 21. Monitoring of the temperature in the vicinity (hereinafter referred to as “element temperature”) is started, and the measured element temperature is output to the treatment tissue load calculation means 42.

  In the treatment tissue load amount calculation means 42, first, in step S100, the element vicinity temperature measured by the temperature measurement means 35 is read and set as the element initial temperature.

  Next, in step S101, it is checked whether or not an ON signal is output from the set temperature level output switch 6b provided in the foot switch 6. If an OFF signal is output, an ON signal is output from the set temperature level output switch 6b. Wait until is output.

  When the surgeon grasps the coagulation / incision forceps 2 and turns on the set temperature level output switch 6b, the procedure proceeds to step S102 to calculate the forceps heat capacity difference Po based on the element initial temperature set in step S100. The process proceeds to step S103.

  In step S103, the initial set temperature output from the heat generation setting means 31 is read, and the corresponding electric power is output to the heat generating element unit 21 (t0 in FIG. 10). At the same time, measurement of the power applied to the heating element unit 21 in the applied power detection means 34 is started, and the measured applied power is read.

  Next, the process proceeds to step S104, where the elapsed time after the start of power supply is measured to check whether or not the initial set time T1 has elapsed. If not, the process branches to step S105. In step S105, it is checked whether or not an OFF signal is output from the set temperature level output switch 6b. If the ON signal is continuously output, the process returns to step S104 and the elapsed time is measured. On the other hand, when the OFF signal is output from the set temperature level output switch 6b, the process proceeds to step S106, the supply of power to the heating element unit 21 is stopped, the process returns to step S101, and the set temperature level output switch 6b is turned ON again. Wait until

  On the other hand, if it is determined in step S104 that the elapsed time has reached the initial set time T1 (t1 in FIG. 10), the process proceeds to step S107, and the total amount of electric power applied to the heating element unit 21 during the initial set time T1 (initial (Power consumption) P1 (see FIG. 10A) is calculated based on the applied power detected by the applied power detection means 34 and the initial set time T1 (f (P1) = (applied power, initial set time)) .

  Next, the process proceeds to step S108, and the calculation representing the capacity (size) of the treatment living tissue based on the total power amount (initial power consumption) P1, the forceps heat capacity difference Po, and the heat capacity of the forceps solid (heat amount escaping to the forceps) Pk. The tissue load amount Pt is calculated from the above-described equation (1). The calculated tissue load amount Pt is transmitted to the coagulation required power amount determining means 43.

  In step S109, the coagulation required power amount determining unit 43 refers to a table (see FIG. 11) stored in the memory 32 based on the calculated tissue load amount Pt, and a level indicating the size of the target tissue. And the electric power required for coagulation (P1 + P2) necessary for coagulating the tissue currently being treated is set. For example, when the calculated tissue load Pt is 25 [W · t], the level indicating the size of the target tissue is set to “2” and the coagulation required power amount (P1 + P2) is set to 80 [W · t] by referring to the table. Is done.

  In this case, as shown at t1 to t2 in FIG. 10B, the set temperature may be automatically lowered to the temperature at which the coagulation treatment is performed.

  Next, the process proceeds to step S110, in which it is determined whether or not the total power (total applied power) from the output start detected by the applied power detection unit 34 has reached the coagulation required power amount (P1 + P2) set in step S109. If not, the process branches to step S111. In step S111, it is checked whether or not an OFF signal is output from the set temperature level output switch 6b. If the ON signal is continuously output, the process returns to step S110. On the other hand, when the OFF signal is output from the set temperature level output switch 6b, the process proceeds to step S112, the supply of power to the heating element unit 21 is stopped, the process returns to step S101, and the set temperature level output switch 6b is turned ON again. Wait until

  Further, when the total applied power has reached the coagulation required power amount (P1 + P2), that is, it has been determined that the elapsed time since the start of power supply has reached the coagulation required time T2 shown in FIG. At this time, the process proceeds from step S110 to step S113 in order to shift to the incision stage.

  In step S113, the set temperature for the heating element unit 21 is increased. When a signal indicating the increased set temperature is output from the coagulation required power amount determining unit 43 to the output power control unit 36, the output power control unit 36 outputs the driving power corresponding to the input signal to the heating element unit. 21 to increase the temperature of the heating element section 21. As a result, the output control by the output power control means 36 is a cutting-dominant control in which the applied power is increased.

  For example, when the coagulation required electric energy (P1 + P2) is set to 80 [W · t], the tissue coagulated at 80 [W · t] is separated at this incision stage, and the coagulation incision is completed.

  Next, the process proceeds to step S114 to check whether or not an OFF signal is output from the set temperature level output switch 6b. When the ON signal is continuously output, the incision stage is continued and the OFF signal is When it is output, the process proceeds to step S115, the supply of power to the heating element unit 21 is stopped, and the process returns to step S101. In the incision stage, when an OFF signal is output from the set temperature level output switch 6b, it is determined that the coagulation incision is completed.

  As described above, according to the present embodiment, since the necessary power amount for coagulation is set according to the size of the target tissue, the coagulation completion time can be set without directly grasping the coagulation state of the target tissue. It is possible to make an accurate determination, and a coagulation incision can be performed at an optimal time.

(Second form)
FIG. 13 shows a second embodiment of the present invention. Note that the same components as those in the first embodiment are denoted by the same reference numerals and description thereof is omitted.

  In the first embodiment described above, the coagulation required power amount (P1 + P2) is set by referring to the table based on the calculated tissue load amount Pt. However, in this embodiment, the relationship between the coagulation required power amount (P1 + P2) and the calculated tissue load amount Pt. Is expressed as a first-order approximation.

  It can be seen that the calculated tissue load amount Pt and the coagulation required power amount (P1 + P2) are in a positive proportional relationship. The linear expression data ((P1 + P2) = α · Pt + β), the inclination data (α), and the intercept data (β) shown in the figure are stored in the memory 32 and read out by the CPU 33.

  Therefore, the power control routine of the present embodiment is the same as the power control routine shown in FIG. 12, but only the process of calculating the coagulation required power amount (P1 + P2) shown in step S109 is different.

  That is, in this embodiment, in step S109, it is necessary to coagulate the tissue currently being treated from the primary approximate expression (see FIG. 13) stored in the memory 32, based on the calculated tissue load Pt calculated in step S108. The electric power required for coagulation (P1 + P2) is set.

For example, when the calculated tissue load amount Pt calculated by the treatment tissue load amount calculation means 42 is 25 [W · t] and the slope α = 3 and the intercept β = 5, the coagulation required electric energy (P1 + P2) is ,
(P1 + P2) = 3 · 25 + 5 = 80 [W · t]
It becomes.

  As described above, according to the present embodiment, instead of allocating one coagulation incision necessary electric power for a certain group of calculated tissue load Pt, a coagulation necessary electric energy (P1 + P2) is obtained from a linear expression. As a result, the memory 32 can be reduced in capacity. Further, the coagulation necessary power amount (P1 + P2) corresponding to the calculated tissue load amount Pt is calculated and the optimum power necessary for the coagulation incision is supplied to the heating element portion 21, so that the coagulation completion timing is accurately determined. Judgment can be made.

Overall configuration diagram of a heat treatment apparatus according to the first embodiment Same as above, external view of the main body of the heat treatment device Same as above, rear view of the main body of the heat treatment device Side view of coagulation and incision forceps The schematic perspective view of the heat treatment section as seen from the side Schematic perspective view of the heat treatment section viewed from above Same as above, top sectional view of the heat treatment section Side sectional view of the heat treatment section A circuit block diagram of a control circuit provided in the heat treatment device (A) is a waveform diagram showing the amount of electric power applied when performing a coagulation incision, (b) is a waveform diagram showing a set temperature set according to the state of (a) Same as above, chart showing the relationship between the calculated tissue load, the size of the treated tissue, and the coagulation required electric energy Same as above, flowchart showing power control routine Chart showing the relationship between calculated tissue load and coagulation required power according to the second embodiment

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 ... Fever treatment apparatus, 2 ... Coagulation incision forceps, 3 ... Apparatus main body, 6b ... Setting temperature level output switch, 7 ... Heat generation treatment part, 7a ... Heat generation treatment part main body, 9 ... Treatment part, 21 ... Heating element part, 21a 21c ... heating element, 31 ... heat generation setting means, 33 ... CPU, 34 ... applied power detection means, 35 ... temperature measurement means, 36 ... output power control means, 42 ... treatment tissue load amount calculation means, 43 ... coagulation required power Quantity determining means, P1 ... initial power consumption, Po ... forceps heat capacity difference, Pt ... calculated tissue load, T1 ... initial setting time, T2 ... coagulation required time, T3 ... incision stage time

Agent Patent Attorney Susumu Ito

Claims (4)

Temperature measuring means for measuring the temperature of the heat generating part provided in the treatment tool;
Applied power detection means for measuring the power supplied to the heating unit;
Treatment tissue load detection means for detecting the size of the tissue to be treated based on the power supplied at least for a certain period;
Coagulation required power setting means for setting the amount of power required for tissue coagulation based on the detection result of the treatment tissue load amount detection means;
An exothermic treatment device comprising: output power control means for supplying the amount of power set by the coagulation required power setting means to the affected area. In the treatment tissue load amount detection means, initial power consumption is set based on the power supplied for a predetermined period, and the initial power consumption is corrected with an initial temperature power correction value that corrects a power difference due to an initial temperature of the heat generating unit. The heat treatment apparatus according to claim 1, wherein the size of the tissue to be treated is set. In the treatment tissue load amount detection means, initial power consumption is set based on the power supplied for a certain period, and the initial power consumption is a power correction value for each treatment tool that corrects power loss due to the heat capacity of the treatment tool. The heat treatment apparatus according to claim 1, wherein the size of the tissue to be treated is set by correction. In the treatment tissue load amount detection means, an initial power consumption is set based on the power supplied for a certain period, and the initial power consumption correction value for correcting the power difference due to the initial temperature of the heat generating unit and the initial power consumption correction value. The heat treatment apparatus according to claim 1, wherein the size of the tissue to be treated is set by correcting with a power correction value for each treatment tool that corrects power loss associated with the heat capacity of the treatment tool.

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