WO2019233453A1 - 一种热电阻式发热器 - Google Patents

一种热电阻式发热器 Download PDF

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Publication number
WO2019233453A1
WO2019233453A1 PCT/CN2019/090204 CN2019090204W WO2019233453A1 WO 2019233453 A1 WO2019233453 A1 WO 2019233453A1 CN 2019090204 W CN2019090204 W CN 2019090204W WO 2019233453 A1 WO2019233453 A1 WO 2019233453A1
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Prior art keywords
temperature
heat
thermal resistance
thermally conductive
temperature sensor
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PCT/CN2019/090204
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English (en)
French (fr)
Inventor
俞雪利
Original Assignee
Yu Xueli
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Priority to US16/640,698 priority Critical patent/US20200352621A1/en
Priority to JP2020558676A priority patent/JP2021511167A/ja
Priority to CN201980036685.6A priority patent/CN112739279A/zh
Publication of WO2019233453A1 publication Critical patent/WO2019233453A1/zh

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/08—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by means of electrically-heated probes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/14—Probes or electrodes therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F7/00—Heating or cooling appliances for medical or therapeutic treatment of the human body
    • A61F7/007—Heating or cooling appliances for medical or therapeutic treatment of the human body characterised by electric heating
    • H—ELECTRICITY
    • H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
    • H05B—ELECTRIC HEATING; ELECTRIC LIGHT SOURCES NOT OTHERWISE PROVIDED FOR; CIRCUIT ARRANGEMENTS FOR ELECTRIC LIGHT SOURCES, IN GENERAL
    • H05B1/00—Details of electric heating devices
    • H05B1/02—Automatic switching arrangements specially adapted to apparatus ; Control of heating devices
    • H05B1/0227—Applications
    • H05B1/023—Industrial applications
    • H05B1/025—For medical applications
    • H—ELECTRICITY
    • H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
    • H05B—ELECTRIC HEATING; ELECTRIC LIGHT SOURCES NOT OTHERWISE PROVIDED FOR; CIRCUIT ARRANGEMENTS FOR ELECTRIC LIGHT SOURCES, IN GENERAL
    • H05B3/00—Ohmic-resistance heating
    • H05B3/10—Heating elements characterised by the composition or nature of the materials or by the arrangement of the conductor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00571—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body for achieving a particular surgical effect
    • A61B2018/00577—Ablation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00636—Sensing and controlling the application of energy
    • A61B2018/00696—Controlled or regulated parameters
    • A61B2018/00714—Temperature
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00636—Sensing and controlling the application of energy
    • A61B2018/00773—Sensed parameters
    • A61B2018/00791—Temperature
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F7/00—Heating or cooling appliances for medical or therapeutic treatment of the human body
    • A61F7/007—Heating or cooling appliances for medical or therapeutic treatment of the human body characterised by electric heating
    • A61F2007/0071—Heating or cooling appliances for medical or therapeutic treatment of the human body characterised by electric heating using a resistor, e.g. near the spot to be heated
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F7/00—Heating or cooling appliances for medical or therapeutic treatment of the human body
    • A61F2007/0088—Radiating heat
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F7/00—Heating or cooling appliances for medical or therapeutic treatment of the human body
    • A61F2007/0095—Heating or cooling appliances for medical or therapeutic treatment of the human body with a temperature indicator
    • A61F2007/0096—Heating or cooling appliances for medical or therapeutic treatment of the human body with a temperature indicator with a thermometer

Definitions

  • the invention relates to a thermal resistance type heater, in particular to a thermal resistance type heater for tumor treatment.
  • the tumor hyperthermia equipment currently used in clinical practice are radio frequency tumor hyperthermia equipment and microwave tumor hyperthermia equipment, which both use electromagnetic waves to heat tumor tissues.
  • the basic principle is that human tissues absorb electromagnetic waves and heat up.
  • the transformation of electromagnetic waves into heat by human tissues is not only related to the electromagnetic strength, but also has a lot to do with the structure and dielectric constant of the human tissues. Due to the coexistence of multiple tumor tissue structures, the use of radio frequency or microwave to treat tumors will result in uneven temperature of the entire tumor tissue, and the temperature inside the tumor will vary widely.
  • Some tumor tissues have been carbonized, and some tumor tissues are still The inactivation temperature is not reached, and tumor inactivation is incomplete.
  • a thermal resistance heater (hereinafter referred to as a heater) that causes the tumor tissue to heat up. Otherwise, it will not be able to completely inactivate the tumor, control the apoptotic process of the tumor, or cause damage to the normal tissues and organs of the patient. Therefore, the heater has two important properties in tumor hyperthermia. One is to generate thermal energy (no electromagnetic radiation), and the other is to control the surface temperature of the heater. For this reason, it is necessary to install a temperature sensor on the heater. However, the location of the temperature sensor will affect the accuracy of the temperature measurement.
  • the temperature sensor is directly placed on the surface of the heater and in direct contact with the tumor tissue, there will be the following problems: 1. There is a point contact between the temperature sensor and the surface of the heater, and the measured value of the temperature sensor is only the temperature value of a certain point of the heater and not The average temperature value of the entire heater; 2. When the temperature measurement point of the temperature sensor is located in a poor heat dissipation area, the heat at that location cannot be transferred quickly, causing the temperature at that location to be higher than other areas with good heat dissipation, making the heater overall (average) The temperature is lower than the required treatment temperature value, which affects the treatment effect.
  • the invention designs a thermal resistance type heater.
  • the technical problem it solves is how to precisely control the surface temperature of the heater to make the tumor thermal therapy safe and effective.
  • the present invention adopts the following scheme:
  • a thermal resistance type heater is used for heating tumor tissue to inactivate and ablate tumor tissue, and is characterized in that it includes a guide
  • a thermal resistor which is located in the thermally conductive housing and causes itself to generate heat by current
  • a heat sink which is also located in the thermally conductive shell and dissipates and generates heat evenly from the thermal resistance to the thermally conductive shell;
  • a thermally conductive compensation arm which is connected to the heat sink and has a temperature at a specific position that is the same as the temperature on the thermally conductive shell or an error within a required range;
  • the temperature sensor reflects the average heating temperature value of the thermally conductive shell by collecting the temperature value of the specific position of the thermally conductive compensation arm.
  • it further comprises a controller, which adjusts the current through the thermal resistor according to the temperature signal collected by the temperature sensor, so that the temperature signal of the temperature sensor is stabilized at a set value, so as to accurately control the surface of the heat-conducting casing.
  • a controller which adjusts the current through the thermal resistor according to the temperature signal collected by the temperature sensor, so that the temperature signal of the temperature sensor is stabilized at a set value, so as to accurately control the surface of the heat-conducting casing. The purpose of temperature.
  • the temperature signal of the temperature sensor is transmitted to the controller through a temperature sensor wire (5), and the current output by the controller is sent to the thermal resistor through a thermal resistance wire.
  • the temperature at the end of the thermally conductive compensation arm connected to the heat sink is high, and the temperature of the end of the thermally conductive compensation arm far from the heat sink is low.
  • the heat conduction distance is adjusted to reach The purpose of temperature compensation and finally determine the specific location where the temperature sensor is installed.
  • the temperature sensor and the thermal resistor form an integrated structure through a heat sink and a thermally conductive compensation arm.
  • the heat conducting shell is a stainless steel shell, and / or the heat sink is a heat sinking copper core (2).
  • the outer wall of the heat sink is in contact with the inner wall of the thermally conductive shell without gaps, and the inner wall of the heat sink is in thermal contact with the thermal resistor.
  • the present invention adjusts the installation and fixed position of the temperature sensor on the thermal compensation arm so that the temperature sensed by the temperature sensor is the same as the surface temperature of the heater or the error is within the required range, so as to achieve accurate control of the heater by the controller Purpose of surface temperature.
  • the present invention inactivates and ablates tumor tissue by means of thermal resistance heating, and precisely controls the heating temperature of the heater through the temperature sensor on the thermally conductive compensation arm, so as to control the inactivation and apoptosis processes of the tumor, and It can prevent damage to the normal tissues and organs of patients.
  • the present invention uses thermal resistance heating to heat the tumor tissue in a thermally conductive manner, the internal temperature of the tumor tissue has a gradient distribution, that is, the temperature of the tissue near the temperature-controlled thermal resistance heater is high and the tissue is far from the temperature-controlled thermal resistance heater.
  • the temperature is low regardless of the structure of any tumor tissue.
  • the temperature value of the thermometer placed at the junction of tumor tissue and normal tissue indicates that the temperature of the entire tumor tissue is not lower than this temperature value. Therefore, when the temperature of the thermometer 2 placed at the junction of tumor tissue and normal tissue is stabilized between 43 ° C and 45 ° C and maintained for a period of time, it can achieve complete inactivation of tumor tissue without harming normal human tissue. Ideal tumor hyperthermia.
  • the present invention uses a thermal resistor to generate heat, it does not generate electromagnetic radiation and does not cause any interference to the temperature sensor.
  • the temperature data of the temperature-controlling thermal resistance heater and the temperature detector are authentic, reliable, and continuous.
  • the present invention uses a PID temperature control circuit to stabilize the temperature of the temperature-controlled thermal resistance heater 1 with high accuracy, minimize overshoot during temperature regulation, accurate temperature control, and make the thermotherapy process safe and reliable.
  • FIG. 1 is a schematic structural sectional view of an axial direction of a thermal resistance heater according to the present invention
  • FIG. 2 is a schematic diagram of a temperature distribution of a thermally conductive compensation arm in the present invention
  • FIG. 3 is a schematic diagram of the components of the novel tumor hyperthermia equipment of the present invention.
  • FIG. 4 is a schematic diagram of the first setting of a thermal resistance heater and a temperature detector in the present invention
  • FIG. 5 is a schematic diagram of the second setting of the temperature measuring resistance heater and the temperature measuring device in the present invention.
  • FIG. 6 is a schematic diagram of the third setting of the temperature-measuring resistance heater and the temperature detector in the present invention.
  • FIG. 7 is a schematic diagram of a temperature control process function in the present invention.
  • FIG. 8 is a schematic structural diagram of a temperature detector in the present invention.
  • 11 thermo resistance type heater
  • 12 thermometer
  • 121 sensor housing
  • 122 temperature sensor
  • 23 temperature sensor lead
  • 13 tumor tissue
  • 14 normal tissue.
  • FIGS. 1 to 8 The present invention is further described below with reference to FIGS. 1 to 8:
  • the invention uses thermal resistance heating to heat the tumor tissue in a thermally conductive manner, so the internal temperature of the tumor tissue has a gradient distribution law, that is, the temperature of the tissue near the thermal resistance heater is high, and the temperature of the tissue far from the thermal resistance heater is low, regardless of any Tumor tissue structure is no exception.
  • the tumor tissue is heated by a thermal resistance heater. When the edge temperature of the tumor tissue reaches the inactivation temperature, the temperature of the entire tumor tissue must be above the inactivation temperature, so that the entire tumor tissue is completely inactivated.
  • the present invention uses a thermal resistor to generate heat, it does not generate electromagnetic radiation and does not cause any interference to nearby electronic equipment and electronic devices.
  • a thermal resistance wire 4 is connected to the controller, and a temperature sensor wire 5 is connected to the controller.
  • the heating current output by the controller is sent to the thermal resistor 3 through the wire 4.
  • the thermal resistor 3 generates heat under the action of a current.
  • the heat raises the heat-dissipating copper core 2 through heat conduction, and the temperature rise of the heat-dissipating copper core 2 raises the thin-walled stainless steel casing 1 through heat conduction.
  • the temperature of the heat-dissipating copper core 2 is transmitted to the temperature sensor 6 through the heat conduction compensation arm 7.
  • the temperature signal of the temperature sensor 6 is transmitted to the controller through the temperature sensor wire 5.
  • the controller adjusts the heating current according to the signal of the temperature sensor 6, so that the temperature signal of the temperature sensor 6 is stabilized at a set value, so as to achieve the purpose of accurately controlling the surface temperature of the hot knife.
  • the temperature of the surface of the stainless steel casing 1 is much lower than that of the heat-dissipating copper core 2 during heating. If the temperature sensor 6 is simply mounted on the heat-dissipating copper core 2, the temperature display of the temperature sensor 6 is much different from the actual temperature on the surface of the stainless steel casing 1. If the temperature sensor 6 is set on the stainless steel casing 1, it may contact the poor heat dissipation area and cause the temperature value collected by the temperature sensor 6 to be distorted.
  • the temperature sensor 6 In order to make the temperature sensor 6 installed on the heat-dissipating copper core accurately reflect the average temperature of the surface of the stainless steel casing 1, the temperature sensor 6 is installed on the thermal compensation arm 7 and adjusted by adjusting the position of the temperature sensor 6 on the thermal compensation arm.
  • the heat conduction distance achieves the purpose of temperature compensation, so that the temperature sensed by the temperature sensor 6 is the same as the surface temperature of the stainless steel casing 1 or the error is within the allowable range.
  • the present invention adjusts the installation and fixed position of the temperature sensor on the heat-conducting compensation arm so that the temperature sensed by the temperature sensor is the same as the temperature of the surface of the heat knife or the error is within the required range, thereby achieving accurate control of the surface temperature of the heat knife by the controller. purpose.
  • the temperature at the connection end of the right side of the thermally conductive compensation arm 7 and the heat sink copper core 2 is higher than the average true temperature T of the surface of the stainless steel casing 1, which is far from
  • the temperature of the heat-conducting compensation arm 7 at the connection end gradually decreases.
  • there are six temperature measurement points on the thermally conductive compensation arm 7, and the temperatures measured from left to right are: T-2, T-1, T, T + 1, T + 2, and T + 3.
  • the temperature sensor 6 should be installed at a temperature measuring point whose temperature is displayed as T, so that it can truly reflect or infinitely approach the average temperature of the surface of the stainless steel casing 1.
  • a new type of tumor thermal therapy device includes a thermal resistance type heater 11 which is placed in the center of the tumor and heats the tumor by means of thermal resistance heating, which simultaneously accurately controls the self-heating temperature;
  • the thermostat 12 is placed at the boundary between the tumor tissue and the normal tissue to measure the temperature; the controller is connected to the thermal resistance heater 11 to display and control the heating temperature; it is also connected to the thermostat 12 to display the measured temperature.
  • the thermal resistance type heater 11 is used for heating tumor tissue to inactivate and ablate the tumor tissue, and includes a thermally conductive shell for contacting the tumor tissue and conducting heat to the tumor tissue; a thermal resistor located in the thermally conductive shell Self-heating is caused by the current; the heat sink is also located in the thermally conductive shell to dissipate the heat generated by the thermal resistance and uniformly conduct it to the thermally conductive shell; the thermally conductive compensation arm is connected to the heat sink and the temperature at its specific position is on the thermally conductive shell The temperature is the same or the error is within the required range; the temperature sensor reflects the average heating temperature value of the thermally conductive shell by collecting the specific position temperature value of the thermally conductive compensation arm.
  • It also includes a controller, which adjusts the current through the thermal resistor according to the temperature signal collected by the temperature sensor, so that the temperature signal of the temperature sensor is stabilized at a set value, so as to achieve the purpose of accurately controlling the surface temperature of the heat-conducting casing.
  • the temperature signal of the temperature sensor is transmitted to the controller through the temperature sensor wire 5, and the current output by the controller is sent to the RTD through the RTD wire.
  • the temperature at the end of the thermally conductive compensation arm connected to the heat sink is high, and the temperature of the end of the thermally conductive compensation arm away from the heat sink is low.
  • the temperature sensor and the thermal resistor form an integrated structure through a heat sink and a thermally conductive compensation arm.
  • the thermally conductive shell is a stainless steel shell, and / or the heat sink is a heat sink copper core 2.
  • the outer wall of the heat sink is in contact with the inner wall of the heat-conducting shell without gaps, and the inner wall of the heat sink is in thermal contact with the thermal resistor.
  • the controller includes a display adjustment circuit, an A / D conversion circuit, and a PID control circuit.
  • the display adjustment circuit is used to display the heating temperature of the thermal resistance heater 11 and the measurement temperature of the thermometer 2 to adjust the thermal resistance heating.
  • the PID temperature control circuit is used to control the heating temperature of the RTD heater 11 accurately and stably. PID temperature control is to use proportional, integral, differential and other algorithms to adjust and control the heating temperature.
  • the new tumor hyperthermia device works as follows:
  • Step 1 The thermal resistance heater 11 is placed at the center of the tumor tissue 13 and the thermometer 12 is placed at the area where the tumor tissue 13 and the normal tissue 14 border;
  • Step 2 After the new tumor hyperthermia equipment enters the heating state, the thermal resistance heater 11 continuously heats the tumor tissue 3 according to the set temperature value, and the temperature analog signal of the thermometer 12 is converted into a digital signal through the A / D conversion circuit and sent to The display adjustment circuit displays the temperature of the temperature measuring device 12, and the temperature analog signal of the thermal resistance heater 11 is converted into a digital signal by the A / D conversion circuit and sent to the display adjustment circuit to display the heating temperature of the thermal resistance heater 11.
  • the PID control circuit automatically controls the heating current according to the difference between the real-time temperature value of the thermal resistance heater 11 and the set temperature value, so that the heating temperature of the thermal resistance heater 11 is accurately stabilized at the set value.
  • Step 3 According to the difference between the real-time temperature value measured by the thermometer 12 and the required value, adjust the stable operating temperature (set value) of the thermal resistance heater 11 to stabilize the measured temperature of the thermometer 12 at the required value. And keep it for a period of time needed to inactivate and ablate tumor tissue.
  • the temperature-controlled thermal resistance heater 11 is placed at the center of the tumor tissue 13, and the thermometer 12 is placed at the boundary between the tumor tissue 13 and the normal tissue 14.
  • the thermometer 12 is only normal.
  • Organization 14 contacts.
  • the temperature-controlled thermal resistance heater 11 is placed at the center of the tumor tissue 13, and the temperature detector 12 is placed at the boundary between the tumor tissue 13 and the normal tissue 14. For example, the temperature detector 12 is only connected with the tumor. Organization 3 contacts.
  • thermometer 2 is placed at the area where the tumor tissue 13 and the normal tissue 14 border, such as: the thermometer 12 is simultaneously with the tumor The tissue 13 is in contact with the normal tissue 14.
  • the temperature of the thermal resistance heater 11 is stabilized and highly accurate due to the PID temperature control circuit.
  • the overshoot is small, the temperature control is accurate, and the thermal treatment process is safe and reliable.
  • the thermometer 12 includes a housing 121, a temperature sensor 122, and a temperature sensor lead wire 123.
  • the temperature sensor 122 is connected to the inner wall of the lower end of the sensor housing 121 and is connected to the controller through a temperature sensor wire 123.
  • the temperature sensor 22 in the thermometer 12 is a platinum resistor, or a thermocouple, or a thermistor.
  • the new tumor hyperthermia equipment has the following beneficial effects:
  • the present invention uses thermal resistance heating to heat the tumor tissue in a thermally conductive manner, the internal temperature of the tumor tissue has a gradient distribution law, that is, the temperature of the tissue near the temperature-controlled thermal resistance heater 11 is high, and it is far from the temperature-controlled thermal resistance heater Tissue temperature is low regardless of the structure of any tumor tissue.
  • the temperature value of the thermometer 2 placed at the boundary between the tumor tissue and the normal tissue indicates that the temperature of the entire tumor tissue is not lower than the temperature value. Therefore, when the temperature of the thermometer 2 placed at the junction of tumor tissue and normal tissue is stabilized between 43 ° C and 45 ° C and maintained for a period of time, it can achieve complete inactivation of tumor tissue without harming normal human tissue. Ideal tumor hyperthermia.
  • the present invention uses a thermal resistor to generate heat, it does not generate electromagnetic radiation and does not cause any interference to the temperature sensor.
  • the temperature data of the temperature-controlling thermal resistance heater and the temperature detector are authentic, reliable, and continuous.
  • the present invention uses a PID temperature control circuit to stabilize the temperature of the temperature-controlled thermal resistance heater 1 with high accuracy, minimize overshoot during temperature regulation, control temperature accurately, and make the thermal therapy process safe and reliable.

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Abstract

一种热电阻式发热器，包括：导热外壳（1），其用于与肿瘤组织接触并将热量传导至肿瘤组织；热电阻（3），其位于导热外壳（1）内部通过电流使得自身发热；散热体（2），其位于导热外壳（1）内部并将热电阻（3）产生的热量分散并均匀传导至导热外壳（1）；导热补偿臂（7），其与散热体（2）连接，在其特定位置上的温度与导热外壳（1）上的温度相同或误差在要求的范围之内；温度传感器（6），其安装在导热补偿臂的上述特定位置上，通过采集该特定位置温度值反映出导热外壳（1）的表面平均温度值。该发热器通过调节温度传感器在导热补偿臂上的安装固定位置，使温度传感器感应到的温度与外壳发热区表面温度相同或误差在要求的范围之内，从而达到通过控制器精确控制发热器表面温度的目的。

Description

一种热电阻式发热器 技术领域
本发明涉及一种热电阻式发热器，尤其是涉及一种用于肿瘤治疗的热电阻式发热器。
背景技术
现在临床使用的肿瘤热疗设备均是射频类肿瘤热疗设备和微波类肿瘤热疗设备，都是使用电磁波对肿瘤组织加热，其基本原理是人体组织吸收电磁波而升温。人体组织将电磁波转变为热不仅与电磁强度有关，还与人体组织本身的结构、介电常数等有很大关系。由于肿瘤组织是多种结构共存的，因此在使用射频或微波对肿瘤热疗时会产生整个肿瘤组织温度不均匀，肿瘤内部温度差异大，会出现有的肿瘤组织已经炭化、有的肿瘤组织还没达到灭活温度的现象，肿瘤灭活不完全。
在肿瘤热疗过程中，精确控制使肿瘤组织升温的热电阻式发热器(以下简称发热器)表面温度是十分重要的。否则，就不能彻底灭活肿瘤、控制肿瘤凋亡过程，或者会对患者的正常组织、器官造成损害。所以肿瘤热疗中发热器有两个重要性能一是产生热能(没有电磁辐射)，二是发热器表面温度可控。为此，在发热器上设置温度传感器是必须的选择。但是，温度传感器设置部位却会影响到测温的准确性。如果将温度传感器直接设置在发热器表面与肿瘤组织直接接触，会存在以下问题：1、温度传感器与发热器表面之间为点接触，温度传感器测量值只是发热器某个点的温度值而不是整个发热器的平均温度值；2、当温度传感器的测温点恰好位于不良散热区时，该处的热量不能快速转移造成该处温度高于其他散热良好的区域，使发热器总体(平均)温 度低于需要的治疗温度值，影响治疗效果。
发明内容
本发明设计了一种热电阻式发热器，其解决的技术问题是如何精准控制发热器表面温度，使肿瘤热疗安全有效。
为了达到上述目的，本发明采用了以下方案：
一种热电阻式发热器，所述热电阻式发热器用于给肿瘤组织加热使肿瘤组织灭活、消融，其特征在于：包括导
热外壳，其用于与所述肿瘤组织接触并将热量传导至所述肿瘤组织中；
热电阻，其位于所述导热外壳中通过电流使得自身发热；
散热体，其也位于所述导热外壳中将热电阻产生的热量分散并均匀传导至所述导热外壳；
导热补偿臂，其与所述散热体连接，在其特定位置上的温度与所述导热外壳上的温度相同或误差在要求的范围之内；
温度传感器，其通过采集导热补偿臂的所述特定位置温度值反映出所述导热外壳的平均加热温度值。
进一步，还包括控制器，所述控制器根据所述温度传感器采集的温度信号调节通过热电阻的电流大小，使温度传感器的温度信号稳定在设定的数值上，达到精确控制所述导热外壳表面温度的目的。
进一步，所述温度传感器的温度信号通过温度传感器导线(5)传送至所述控制器，所述控制器输出的电流经热电阻导线送至所述热电阻。
进一步，所述导热补偿臂与所述散热体连接的一端温度高，所述导热补偿臂远离所述散热体的一端温度低，通过调整温度传感器在导热补偿臂上的位置，调节导热距离，达到温度补偿的目的并最终确定安装所述温度传感器的所述特定位置。
进一步，所述温度传感器与热电阻通过散热体、导热补偿臂形成一体结构。
进一步，所述导热外壳为不锈钢外壳，和/或所述散热体为散热铜芯(2)。
进一步，所述散热体的外壁与所述导热外壳内壁无间隙接触，所述散热体的内壁与所述热电阻导热接触。
该热电阻式发热器具有以下有益效果：
(1)本发明通过调节温度传感器在导热补偿臂上的安装固定位置，使温度传感器感应到的温度与发热器表面温度相同或误差在要求的范围之内，从而达到通过控制器精确控制发热器表面温度的目的。
(2)本发明通过热电阻发热的方式对肿瘤组织进行灭活、消融，并且通过导热补偿臂上的温度传感器对发热器的加热温度精准控制，从而控制肿瘤的灭活、凋亡过程，而且可以避免对患者的正常组织、器官造成损害。
(3)本发明由于采用热电阻加热以热传导方式对肿瘤组织加热，因此肿瘤组织内部温度呈梯度分布规律，即靠近控温热电阻加热器的组织温度高，远离控温热电阻加热器的组织温度低，无论任何肿瘤组织结构没有例外。置于肿瘤组织与正常组织交界区域测温器的温度值就表明整个肿瘤组织的温度都不低于该温度值。所以，当置于肿瘤组织与正常组织交界区域测温器2的温度稳定在43℃-45℃之间并保持一段时间后，就能实现既对肿瘤组织完全灭活又不伤害正常人体组织的理想肿瘤热疗方法。
(4)本发明由于使用热电阻发热，其不会产生电磁辐射，不会对温度传感器产生任何干扰，控温热电阻加热器和测温器的温度数据真实、可靠、连续。
(5)本发明由于采用PID温控电路，使控温热电阻加热器1的温度稳定，精确度高，在调控温度过程中过冲很小、温度控制精确，热疗过程安全、可靠。
附图说明
图1是本发明热电阻式发热器轴向剖面结构示意图；
图2是本发明中导热补偿臂的温度分布示意图；
图3是本发明新型肿瘤热疗设备部件构成示意图；
图4是本发明中热电阻式发热器和测温器第一种置位示意图；
图5是本发明中测温电阻加热器和测温器第二种置位示意图；
图6是本发明中测温电阻加热器和测温器第三种置位示意图；
图7是本发明中控温过程函数示意图；
图8是本发明中测温器的结构示意图。
附图标记说明：
1—不锈钢外壳；2—散热铜芯；3—热电阻；4—热电阻导线；5—温度传感器导线；6—温度传感器；7—导热补偿臂；
11—热电阻式发热器；12—测温器；121—传感器壳体；122—温度传感器；23—温度传感器导线；13—肿瘤组织；14—正常组织。
具体实施方式
下面结合图1至图8，对本发明做进一步说明：
本发明是采用热电阻发热以热传导方式对肿瘤组织加热，因此肿瘤组织内部温度呈梯度分布规律，即靠近热电阻式发热器的组织温度高，远离热电阻式发热器的组织温度低，无论任何肿瘤组织结构没有例外。通过热电阻式发热器给肿瘤组织加热，当肿瘤组织边缘温度达到灭活温度时，整个肿瘤组织的温度一定在灭活温度以上，使整个肿瘤组织完全灭活。
本发明由于使用热电阻发热，其不会产生电磁辐射，不会对邻近的电子设备和电子器件产生任何干扰。
如图1所示，热电阻导线4与控制器连接，温度传感器导线5与控制器连接。控制器输出的加热电流经导线4送至热电阻3。热电阻3在电流作用下产生热量。热量通过热传导使散热铜芯2升温，散热铜芯2的升温通过热传导使薄壁不锈钢外壳1升温，同时散热铜芯2的温度经过导热补偿臂7传至温度传感器6。温度传感器6的温度信号通过温度传感器导线5传送至控制器。控制器根据温度传感器6的信号 调节加热电流大小，使温度传感器6的温度信号稳定在设定的数值上，达到精确控制热刀表面温度的目的。
由于不锈钢的热导率低，所以加热时不锈钢外壳1表面温度低于散热铜芯2温度很多。如果简单地将温度传感器6安装在散热铜芯2上，温度传感器6的温度显示与不锈钢外壳1表面的实际温度相差很多。如果将温度传感器6设置在不锈钢外壳1上，可能接触到散热不良区域而造成温度传感器6采集温度值失真。
为了使安装在散热铜芯体上的温度传感器6能精确反应不锈钢外壳1表面的平均温度，将温度传感器6安装在导热补偿臂7上，通过调整温度传感器6在导热补偿臂上的位置，调节导热距离，达到温度补偿的目的，使温度传感器6感应到的温度与不锈钢外壳1表面温度一样或误差在允许范围之内。
本发明通过调节温度传感器在导热补偿臂上的安装固定位置，使温度传感器感应到的温度与热刀表面温度相同或误差在要求的范围之内，从而达到通过控制器精确控制热刀表面温度的目的。
如图2所示，假设不锈钢外壳1表面的平均温度真实值为T度，导热补偿臂7右侧与散热铜芯2连接端的温度要高于不锈钢外壳1表面的平均温度真实值T，远离于连接端的导热补偿臂7温度逐渐衰减。例如，在导热补偿臂7上有六个测温点，从左到右测得的温度依次为：T-2、T-1、T、T+1、T+2和T+3。温度传感器6应当安装在温度显示为T的测温点上，这样就可以真实反映或无限接近不锈钢外壳1表面的平均温度。
如图3所示，一种新型肿瘤热疗设备，包括热电阻式发热器11，其被置于肿瘤内部中心位置并通过热电阻发热的方式给肿瘤加热，其同时精确控制自身发热温度；测温器12，其放置在肿瘤组织与正常组织交界区域测量温度；控制器，其与热电阻式发热器11连接，显示并控制加热温度；其还与测温器12连接，显示测量温度。
该热电阻式发热器11，用于给肿瘤组织加热使肿瘤组织灭活、消 融，包括导热外壳，其用于与肿瘤组织接触并将热量传导至肿瘤组织中；热电阻，其位于导热外壳中通过电流使得自身发热；散热体，其也位于导热外壳中将热电阻产生的热量分散并均匀传导至导热外壳；导热补偿臂，其与散热体连接，在其特定位置上的温度与导热外壳上的温度相同或误差在要求的范围之内；温度传感器，其通过采集导热补偿臂的特定位置温度值反映出导热外壳的平均加热温度值。
还包括控制器，控制器根据温度传感器采集的温度信号调节通过热电阻的电流大小，使温度传感器的温度信号稳定在设定的数值上，达到精确控制导热外壳表面温度的目的。温度传感器的温度信号通过温度传感器导线5传送至控制器，控制器输出的电流经热电阻导线送至热电阻。
导热补偿臂与散热体连接的一端温度高，导热补偿臂远离散热体的一端温度低，通过调整温度传感器在导热补偿臂上的位置，调节导热距离，达到温度补偿的目的并最终确定安装温度传感器的特定位置。
温度传感器与热电阻通过散热体、导热补偿臂形成一体结构。导热外壳为不锈钢外壳，和/或散热体为散热铜芯2。散热体的外壁与导热外壳内壁无间隙接触，散热体的内壁与热电阻导热接触。
控制器包括显示调节电路、A/D转换电路和PID控制电路；其中，显示调节电路，其用于显示热电阻式发热器11的加热温度以及测温器2的测量温度，调节热电阻式发热器11的加热温度；A/D转换电路，其用于将热电阻式发热器11温度模拟信号和测温器温度模拟信号转换成数字信号。PID温度控制电路，其用于控制热电阻式发热器11加热温度精确稳定。PID温控就是采用比例、积分、微分等算法调节控制加热温度。
该新型肿瘤热疗设备的工作原理如下：
步骤1：将热电阻式发热器11置于肿瘤组织13中心位置，测温器12置于肿瘤组织13与正常组织14交界的区域；
步骤2：新型肿瘤热疗设备进入加热状态后，热电阻式发热器11 依设定温度值给肿瘤组织3持续加热，测温器12的温度模拟信号通过A/D转换电路成为数字信号送至显示调节电路显示测温器12测量温度，热电阻式发热器11的温度模拟信号通过A/D转换电路成为数字信号送至显示调节电路显示热电阻式发热器11的加热温度。PID控制电路根据热电阻式发热器11的实时温度值和设定温度值的差异自动控制加热电流，使热电阻式发热器11的加热温度精准稳定在设定值上。
步骤3：根据测温器12测量的实时温度值与需要值的差异，调节热电阻式发热器11的稳定工作温度(设定值)，使测温器12的测量温度稳定在需要值上，并保持一段时间以供灭活、消融肿瘤组织所需。
如图4所示，控温的热电阻加热器11置于肿瘤组织13内中心位置，而测温器12置于肿瘤组织13与正常组织14交界的区域，如：测温器12仅与正常组织14接触。
如图5所示，控温的热电阻加热器11置于肿瘤组织13内中心位置，而测温器12置于肿瘤组织13与正常组织14交界的区域，如：测温器12仅与肿瘤组织3接触。
如图6所示，控温的热电阻加热器11置于肿瘤组织13内中心位置，而测温器2置于肿瘤组织13与正常组织14交界的区域，如：测温器12同时与肿瘤组织13与正常组织14接触。
如图7所示，由于采用PID温控电路，使热电阻式发热器11的温度稳定，精确度高，在调控温度过程中过冲很小、温度控制精确，热疗过程安全、可靠。
如图8所示，测温器12包括壳体121、温度传感器122和温度传感器导线123。温度传感器122连接在传感器壳体121最下端的内壁上，并通过温度传感器导线123与控制器连接。测温器12中的温度传感器22为铂电阻，或是热电偶，或是热敏电阻。
该新型肿瘤热疗设备与现有肿瘤热疗设备相比，具有以下有益效果：
(1)本发明由于采用热电阻加热以热传导方式对肿瘤组织加热， 因此肿瘤组织内部温度呈梯度分布规律，即靠近控温热电阻加热器11的组织温度高，远离控温热电阻加热器的组织温度低，无论任何肿瘤组织结构没有例外。置于肿瘤组织与正常组织交界区域测温器2的温度值就表明整个肿瘤组织的温度都不低于该温度值。所以，当置于肿瘤组织与正常组织交界区域测温器2的温度稳定在43℃-45℃之间并保持一段时间后，就能实现既对肿瘤组织完全灭活又不伤害正常人体组织的理想肿瘤热疗方法。
(2)本发明由于使用热电阻发热，其不会产生电磁辐射，不会对温度传感器产生任何干扰，控温热电阻加热器和测温器的温度数据真实、可靠、连续。
(3)本发明由于采用PID温控电路，使控温热电阻加热器1的温度稳定，精确度高，在调控温度过程中过冲很小、温度控制精确，热疗过程安全、可靠。
上面结合附图对本发明进行了示例性的描述，显然本发明的实现并不受上述方式的限制，只要采用了本发明的方法构思和技术方案进行的各种改进，或未经改进将本发明的构思和技术方案直接应用于其它场合的，均在本发明的保护范围内。

Claims (7)

  1. 一种热电阻式发热器，所述热电阻式发热器用于给肿瘤组织加热使肿瘤组织灭活、消融，其特征在于：包括
    导热外壳，其用于与所述肿瘤组织接触并将热量传导至所述肿瘤组织中；
    热电阻，其位于所述导热外壳中通过电流使得自身发热；
    散热体，其位于所述导热外壳中将热电阻产生的热量分散并均匀传导至所述导热外壳；
    导热补偿臂，其与所述散热体连接，在其特定位置上的温度与所述导热外壳上的温度相同或误差在要求的范围之内；
    温度传感器，其通过采集导热补偿臂的所述特定位置温度值反映出所述导热外壳的平均加热温度值。
  2. 根据权利要求1所述热电阻式发热器，其特征在于：还包括控制器，所述控制器根据所述温度传感器采集的温度信号调节热电阻通过的电流大小，使温度传感器的温度信号稳定在设定的数值上，达到精确控制所述导热外壳表面温度的目的。
  3. 根据权利要求2所述热电阻式发热器，其特征在于：所述温度传感器的温度信号通过温度传感器导线(5)传送至所述控制器，所述控制器输出的电流经热电阻导线送至所述热电阻。
  4. 根据权利要求1-3中任何一项所述热电阻式发热器，其特征在于：所述导热补偿臂与所述散热体连接的一端温度高，所述导热补偿臂远离所述散热体的一端温度低，通过调整温度传感器在导热补偿臂上的位置，调节导热距离，达到温度补偿的目的并最终确定安装所述 温度传感器的所述特定位置。
  5. 根据权利要求1-4中任何一项所述热电阻式发热器，其特征在于：所述温度传感器与热电阻通过散热体、导热补偿臂形成一体结构。
  6. 根据权利要求1-5中任何一项所述热电阻式发热器，其特征在于：所述导热外壳为不锈钢外壳(1)，和/或所述散热体为散热铜芯(2)。
  7. 根据权利要求1-6中任何一项所述热电阻式发热器，其特征在于：所述散热体的外表面与所述导热外壳内壁无间隙接触，所述散热体的内壁与所述热电阻导热接触。
PCT/CN2019/090204 2018-06-06 2019-06-05 一种热电阻式发热器 WO2019233453A1 (zh)

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