TWI644589B - Heating system - Google Patents
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Abstract
本案提供一種加熱系統，其包含：一電源供應模組；一調控模組，電連結於該電源供應模組，調控該電源供應模組之作用；以及一加熱模組，包含一定位元件以及一導電元件；其中該加熱模組電連結於該電源供應模組與該調控模組，且該導電元件纏繞該定位元件。The present invention provides a heating system comprising: a power supply module; a control module electrically coupled to the power supply module to regulate the function of the power supply module; and a heating module including a positioning component and a The conductive component is electrically connected to the power supply module and the control module, and the conductive component is wound around the positioning component.
Description
本案涉及一種加熱系統，尤其是涉及一種運用內感應以及電阻加熱原理的加熱系統。The present invention relates to a heating system, and more particularly to a heating system that utilizes the principles of internal induction and resistance heating.
“熱”對於生物體而言，是很重要的免疫反應啟動因子。由於生物組織與細胞本身具不耐熱的特性，熱治療已被用於去除有害組織與細胞。"Heat" is an important immune response promoter for organisms. Because of the heat-labile nature of biological tissues and cells, heat treatment has been used to remove harmful tissues and cells.
熱治療主要是利用熱來燒灼組織與細胞，當組織與細胞受到高溫時會變質而遭受破壞，以便達到利於去除的目的。射頻燒灼治療技術 (Radio Frequency Ablation，RFA) 和微波熱療技術 (Microwave Ablation，MWA)是目前最廣泛使用的熱治療技術；但此兩種療程的花費甚高，常造成患者使用上的負擔。有鑑於此，應用各種加熱原理的熱療儀器開始推陳出新，例如：利用外感應加熱的熱療便是目前常見的熱療儀器，外感應熱療是使用大能量的外感應加熱器在體外產生交變磁場，誘發放入生物體內的感磁性材料或經皮穿刺到組織的感磁針來生熱，進而達到治療目的。但外感應技術會衍生諸多問題，例如：磁力未能深入人體深處、針具製作與材料選用困難，以及臨床操作會因高強度磁場而有安全疑慮等問題。除了外感應加熱之外，過去亦有應用電阻加熱的原理來設計熱療儀器，傳統的電阻熱療是嵌入電阻導熱基材於燒灼針內，根據電生熱特性使針尖生熱而達到治療效果，但常因為導熱基材的尺寸要求，衍生出燒灼針直徑過大的問題。Thermal therapy mainly uses heat to ablate tissues and cells. When tissues and cells are subjected to high temperatures, they will deteriorate and be destroyed in order to facilitate the removal. Radio Frequency Ablation (RFA) and Microwave Ablation (MWA) are currently the most widely used thermal therapy technologies; however, the cost of these two courses is very high, often causing a burden on patients. In view of this, thermotherapy instruments using various heating principles have begun to innovate. For example, hyperthermia using external induction heating is a common thermotherapy instrument, and external induction hyperthermia is the use of a large-energy external induction heater to generate in vitro The magnetic field is induced to induce a magnetic sensitive material placed in the living body or a magnetic sensitive needle percutaneously punctured into the tissue to generate heat, thereby achieving therapeutic purposes. However, external sensing technology will cause many problems, such as: the magnetic force fails to penetrate deep into the human body, the needle making and material selection are difficult, and the clinical operation will have safety concerns due to the high-intensity magnetic field. In addition to external induction heating, in the past, the principle of resistance heating was used to design a thermotherapy instrument. The traditional resistance thermal therapy is embedded in a heat-resistant substrate in a burning needle, and the needle tip generates heat according to the electrothermal property to achieve therapeutic effect. However, due to the size requirements of the thermally conductive substrate, the problem of excessive diameter of the burning needle is derived.
鑒於習用的熱療系統仍存有許多需要改善之處；本案申請人係經細心研究後，發展出本案，期使熱治療的運用可更為普及，且更易於操作並達降低醫療成本的效果。In view of the fact that there are still many areas for improvement in the conventional hyperthermia system; the applicants of this case developed the case after careful study, which made the use of heat treatment more popular and easier to operate and reduced the cost of medical care. .
就一方而言，本案提出了一種加熱系統，包含：一電源供應模組；一調控模組，電連結於該電源供應模組，調控該電源供應模組之作用；以及一加熱模組，包含一定位元件以及一導電元件；其中該加熱模組電連結於該電源供應模組與該調控模組，且該導電元件纏繞該定位元件；在該加熱系統作用時，該導電元件因電阻加熱效應而增溫。In one aspect, the present invention provides a heating system comprising: a power supply module; a control module electrically coupled to the power supply module to regulate the function of the power supply module; and a heating module, including a positioning component and a conductive component; wherein the heating module is electrically connected to the power supply module and the regulating module, and the conductive component is wound around the positioning component; when the heating system acts, the conductive component has a resistance heating effect And increase the temperature.
在一實施例中，該加熱模組更包含一作用元件，設置於該導電元件附近，且該作用元件在該加熱系統作用時受該導電元件之電磁感應作用而增溫。In one embodiment, the heating module further includes an active component disposed adjacent the conductive component, and the active component is heated by the electromagnetic induction of the conductive component when the heating system acts.
在一實施例中，該作用元件環繞該導電元件。In an embodiment, the active element surrounds the conductive element.
在一實施例中，該定位元件為一熱電偶元件，該導電元件為一漆包線，該作用元件為一磁感應元件，該漆包線與該磁感應元件間有一導熱膏。In one embodiment, the positioning component is a thermocouple component, the conductive component is an enameled wire, the active component is a magnetic sensing component, and a thermal paste is disposed between the enameled wire and the magnetic sensing component.
在一實施例中，該漆包線為直徑 0.08 – 2.00 mm 的 UEW+NY (尼龍外被聚胺酯)漆包線，該磁感應元件為SUS 304 不鏽鋼 或 SUS 316 不鏽鋼，該電源供應模組之使用電流為0.1 – 5 A，電壓介於 1.5 - 40 V。In one embodiment, the enameled wire is a UEW+NY (nylon urethane) enameled wire having a diameter of 0.08 - 2.00 mm, and the magnetic sensing element is SUS 304 stainless steel or SUS 316 stainless steel, and the power supply module uses a current of 0.1 - 5 A, the voltage is between 1.5 - 40 V.
在一實施例中，該調控模組是一頻率調控模組及/或一溫度調控模組。In an embodiment, the control module is a frequency control module and/or a temperature control module.
在一實施例中，該調控模組是一比例-積分-微分控制器模組。In an embodiment, the control module is a proportional-integral-derivative controller module.
另一方面而言，本案提出一種加熱系統，包含：一電源供應模組；以及一加熱模組，包含一導電組件以及一磁感應元件；其中該導電組件電連結於該電源供應模組，且在該加熱系統作用時，該磁感應元件受該導電組件之電磁感應作用而增溫，該導電組件因電阻加熱效應而增溫In another aspect, the present invention provides a heating system including: a power supply module; and a heating module including a conductive component and a magnetic sensing component; wherein the conductive component is electrically coupled to the power supply module, and When the heating system acts, the magnetic induction element is heated by the electromagnetic induction of the conductive component, and the conductive component is warmed by the resistance heating effect
在一實施例中，該導電組件包含一導電線圈與一定位元件，該導電線圈緊密纏繞該定位元件。In one embodiment, the conductive component includes a conductive coil and a positioning component that is tightly wound around the positioning component.
在一實施例中，該磁感應元件環繞該導電線圈；且該導電線圈為直徑 0.08 – 2.00 mm 的 UEW+NY (尼龍外被聚胺酯)漆包線，該磁感應元件為SUS 304 不鏽鋼 或 SUS 316 不鏽鋼，該電源供應模組之使用電流為0.1 – 5 A，電壓介於 1.5 - 40 V。In one embodiment, the magnetic induction element surrounds the conductive coil; and the conductive coil is a UEW+NY (nylon urethane) enameled wire having a diameter of 0.08 - 2.00 mm, and the magnetic induction element is SUS 304 stainless steel or SUS 316 stainless steel. The supply module uses a current of 0.1 – 5 A and a voltage between 1.5 and 40 V.
大致而言，本案提出一種加熱系統，其包含加熱模組、電源供應系統以及監控系統等組件；其中，結合了內感應和電阻加熱兩種原理來設計加熱模組，將導電線圈緊密繞於一熱電偶上形成感應線圈，再層套上具微感磁性的穿刺針。在運用時，將通以高頻電流使導電線圈產生交變磁場，並誘發微磁感性穿刺針之內壁生熱，再加上感應線圈本身根據阻抗自成一電阻發熱元件，藉由兩種原理生產之熱能達到加熱目的。其中，更可包含透過調整電源供應系統所輸出之頻率使其接近及/或等於感應線圈的諧振頻率，確保擁有較佳的加熱速率。Broadly speaking, the present invention proposes a heating system comprising a heating module, a power supply system, and a monitoring system; wherein the heating module is designed by combining the two principles of internal induction and resistance heating, and the conductive coil is tightly wound around the one. An induction coil is formed on the thermocouple, and a micro-magnetic piercing needle is placed on the layer. In the application, the high-frequency current will cause the conductive coil to generate an alternating magnetic field, and induce the heat generation of the inner wall of the micro-magnetic inductive puncture needle, and the induction coil itself is self-contained as a resistance heating element according to the impedance, by two kinds. The principle produces thermal energy for heating purposes. Among them, it may further include adjusting the frequency of the power supply system to make it close to and/or equal to the resonant frequency of the induction coil, ensuring a better heating rate.
本案得藉由以下圖式與實施方式說明而更易於讓在此領域具通常知識者瞭解本案的精神。In the present case, it is easier to let the general knowledge in this field understand the spirit of the case by the following drawings and implementation descriptions.
本案將可透過以下的實施例說明而讓在此領域具通常知識者瞭解其創作精神，並可據以完成。然本案的實施並非可由下列實施例而限制其實施型態。The case will be explained by the following examples, so that those with ordinary knowledge in this field can understand the spirit of their creation and can complete it accordingly. However, the implementation of the present invention is not limited to the implementation of the following embodiments.
請參閱圖1，其為本案加熱系統的一實施例示意圖。如圖1所示，在本實施例中，加熱系統1包含電源供應模組11，溫度監控與頻率自調模組12，以及加熱模組13，其中電源供應模組11，溫度監控與頻率自調模組12，以及加熱模組13彼此電連結。在本實施例中，加熱模組13為一燒灼針模組；電源供應模組11則更包含 Oscillator 晶片111、TLP250光偶合器 112、IR 2111電路元件113、TC4421晶片114、TC 4421 晶片115、絕緣閘雙極電晶體（Insulated Gate Bipolar Transistor，IGBT）驅動開關 116、IGBT驅動開關 117、以及ACS712電流量測晶片 118，溫度監控與頻率自調模組12更包含微處理器(Arduino)(MCU)晶片開發板121、TA7257P馬達驅動晶片122、Max6675熱偶晶片123、以及K型熱電偶124。Please refer to FIG. 1 , which is a schematic diagram of an embodiment of the heating system of the present invention. As shown in FIG. 1 , in the embodiment, the heating system 1 includes a power supply module 11 , a temperature monitoring and frequency self-adjusting module 12 , and a heating module 13 , wherein the power supply module 11 , temperature monitoring and frequency are The tuning module 12 and the heating module 13 are electrically connected to each other. In this embodiment, the heating module 13 is a cauterization needle module; the power supply module 11 further includes an Oscillator wafer 111, a TLP250 optical coupler 112, an IR 2111 circuit component 113, a TC4421 wafer 114, and a TC 4421 wafer 115. Insulated Gate Bipolar Transistor (IGBT) drive switch 116, IGBT drive switch 117, and ACS712 current measurement chip 118, temperature monitoring and frequency self-tuning module 12 further includes a microprocessor (Arduino) (MCU) The wafer development board 121, the TA7257P motor drive wafer 122, the Max6675 thermocouple wafer 123, and the K-type thermocouple 124.
在本案的一實施例中，電源供應模組11是遵循感應加熱原理開發而成，能調整供應電壓3~40 V 以及頻率 20~100 kHz 之能量輸出，而使用的轉換器（未圖示）是將直流電源切換成高頻之交流電源並供應至負載，以便作為加熱能量來源。In an embodiment of the present invention, the power supply module 11 is developed according to the principle of induction heating, and can adjust the energy output of the supply voltage of 3 to 40 V and the frequency of 20 to 100 kHz, and the converter (not shown) is used. The DC power is switched to a high frequency AC power source and supplied to the load as a source of heating energy.
在一實施例中，使用半橋式串聯諧振轉換器（如圖2所示）來製作所需之電源供應模組。在圖2的實施例中，半橋式串聯諧振轉換器2在切換頻率大於諧振頻率時，功率開關具有零電壓切換之條件；當切換頻率小於諧振頻率，則功率具有零電流切換之條件；當電路操作在輕載時，諧振槽之電流相對較小，開關之切換損失較小，因此可改善輕載之效率。在此實施例中，半橋式串聯諧振轉換器2包含： -電源AC：家用單相交流電壓 110 V； - 整流23與濾波24：提供整流與濾波功能，並且產生一穩定直流電壓 VDC，使用市售的電源供應器 S-40-12 Mean Well，其規格為輸出電壓 12 V，輸出電流 3.5 A； -半橋式諧振轉換器 25：在此實施例中，選用 IGBT 型號 GT60M303 為其驅動開關，開關責任週期(Duty Cycle)各為 50 %，此設計擁有高效率及切換速度快的優點，適用於高頻率操作； -振盪器 IC 21：產生頻率訊號單元，在本實施例中，利用一振盪器搭配微處理器(Arduino) 提供一範圍的頻率以利頻率改變；利用 MC74HC74AN、 AD654JN、2904D 以及 IRF 7805 等等電路元件組成一振盪器； -開關驅動 IC 22：驅動開關之單元；利用 TLP250 光偶合器建立隔離電路，以利傳遞不同電壓準位之驅動控制訊號。使用電路元件 IR2111 接收 Oscillator 單元所傳送之頻率訊號，並將訊號放大傳送至 TC4421 放大電壓以供兩顆 IGBT 開關驅動所用，進而產生高頻交流電到負載作動； - 等效電感Lr；以及 - 電容Cr。In one embodiment, a half bridge series resonant converter (shown in Figure 2) is used to fabricate the required power supply module. In the embodiment of FIG. 2, the half bridge series resonant converter 2 has a zero voltage switching condition when the switching frequency is greater than the resonant frequency; and the power has a zero current switching condition when the switching frequency is less than the resonant frequency; When the circuit is operated at light load, the current of the resonant tank is relatively small, and the switching loss of the switch is small, so the efficiency of the light load can be improved. In this embodiment, the half-bridge series resonant converter 2 comprises: - a power supply AC: a household single-phase AC voltage of 110 V; - a rectification 23 and a filter 24: providing a rectification and filtering function, and generating a stable DC voltage VDC, using Commercially available power supply S-40-12 Mean Well, its specifications are output voltage 12 V, output current 3.5 A; - Half-bridge resonant converter 25: In this embodiment, IGBT model GT60M303 is selected as its drive switch The duty cycle of the switch is 50% each. This design has the advantages of high efficiency and fast switching speed, and is suitable for high frequency operation. - Oscillator IC 21: generates a frequency signal unit. In this embodiment, a The oscillator is equipped with a microprocessor (Arduino) to provide a range of frequencies for frequency changes; an oscillator is formed by circuit components such as MC74HC74AN, AD654JN, 2904D, and IRF 7805; - Switching driver IC 22: unit for driving the switch; using TLP250 The optical coupler establishes an isolation circuit to facilitate driving control signals of different voltage levels. The circuit component IR2111 receives the frequency signal transmitted by the Oscillator unit, and amplifies the signal to the TC4421 amplification voltage for driving the two IGBT switches, thereby generating high frequency alternating current to the load; - equivalent inductance Lr; and - capacitance Cr .
圖3為本案一溫度監控模組實施例之作動原理示意圖，如圖3所示，在本實施例之溫度控制模組中，使用K型熱電偶33以及加熱模組13作搭配，並使用微處理器(Arduino) 31，型號為 Mega 2560 單晶片開發板設計比例-積分-微分控制器（PID控制器）進行溫度控制，搭配採用 Visual Studio 軟體撰寫使用者人機介面，能輸入所需最大之溫度以及即時監控溫度上升情形。在溫度監控方面之週邊電路採用 MAX6675 熱偶晶片32和 TA7257P 馬達驅動晶片34。MAX6675 熱偶晶片32的主要功能有二：將類比的溫度訊號轉為數位訊號以供微處理器(Arduino) 單晶片讀取；以及具有增益作用來放大訊號讓讀進的微小電壓直(mV)可經由晶片增益值來讀取並轉換連算。使用 TA7257P馬達驅動晶片34，藉由微處理器(Arduino) 31的 PWM 腳位(輸出電壓 0~5 V)，透過比例-積分-微分控制器（PID控制器）理論調整輸出電壓來達到溫度監控，藉此方式進行溫度回饋控制。FIG. 3 is a schematic diagram of an operation principle of an embodiment of a temperature monitoring module of the present invention. As shown in FIG. 3, in the temperature control module of the embodiment, a K-type thermocouple 33 and a heating module 13 are used for matching, and micro-use is used. Processor (Arduino) 31, model Mega 2560 single-chip development board design proportional-integral-derivative controller (PID controller) for temperature control, with Visual Studio software to write user man-machine interface, can input the maximum required Temperature and real-time monitoring of temperature rise. The peripheral circuit for temperature monitoring uses the MAX6675 thermocouple die 32 and the TA7257P motor to drive the die 34. The main function of the MAX6675 thermocouple chip 32 is two: to convert the analog temperature signal into a digital signal for the microprocessor (Arduino) single-chip read; and to have a gain to amplify the signal to read the tiny voltage straight (mV) The continuous calculation can be read and converted via the wafer gain value. The wafer 34 is driven by the TA7257P motor. The temperature is monitored by the PWM pin of the microprocessor (Arduino) 31 (output voltage 0~5 V), and the output voltage is theoretically adjusted by a proportional-integral-derivative controller (PID controller). In this way, temperature feedback control is performed.
比例-積分-微分控制器（PID控制器）由於可靠度與穩定性高，已廣泛地用於各式各樣的控制系統上，是一個在工業控制應用中常見的反饋迴路部件。本實施例根據 Ziegler–Nichols method 進行比例-積分-微分控制器（PID控制器）調整，利用適當的調整比例-積分-微分控制器（PID控制器）參數來使得其溫度曲線能以較快速率，並使溫度上升曲線符合要求，最後達到指定溫度且能隨時間穩定推演。實施例中的比例-積分-微分控制器（PID控制器）溫度控制的設定是藉由實際溫度與設定溫度兩者的誤差值。在操作時已先根據多次離體豬肝實驗，先訂出線圈長度與電壓的參考配合數值，如下表1所示，其中，在一實施例中，加熱線圈選用直徑 0.08 mm 的 UEW+NY (尼龍外被聚胺酯)漆包線，實際使用時則仍需依照情況來加以調整，如運用在活體實驗則需增加比離體豬肝實驗來得大的電壓以達到所需溫度，或者離體豬肝溫度不同也皆有影響。
在感應加熱設計中，工作頻率是很重要的考量因素，攸關著感應加熱系統的好壞。感應線圈中流過的電流越大，其產生的磁通量也就越大，因此提高感應線圈中的電流，可以使工件中產生的渦電流加大，從而增加發熱效果，使工件升溫更快。另外，渦電流的大小也與金屬的截面大小、截面形狀、導電率以及透入深度有關。當輸出頻率在匹配的狀態下，渦電流大部份會密集集中在靠近感應線圈處，遠離感應線圈處較不會生熱，但仍有主要是從被加熱處經由熱傳導輸送過來之些微能量，但不至於溫度過高。由於感應線圈內電流對加熱效果有關鍵性的影響力，而當輸出頻率靠近及/或等於諧振頻率時，電路可等效視為一個純電阻性電路，此時電源所提供的絕大部份能量都會傳送到電阻上，電路中的電流因而達到最大值，故調整的感應線圈頻率需越靠近諧振頻率。In the induction heating design, the operating frequency is an important consideration, and the quality of the induction heating system is good or bad. The larger the current flowing in the induction coil, the larger the magnetic flux generated. Therefore, increasing the current in the induction coil can increase the eddy current generated in the workpiece, thereby increasing the heating effect and making the workpiece warm up faster. In addition, the magnitude of the eddy current is also related to the cross-sectional size, cross-sectional shape, electrical conductivity, and penetration depth of the metal. When the output frequency is in the matched state, most of the eddy current will be concentrated close to the induction coil, and there will be no heat generation away from the induction coil, but there are still some micro-energy that is mainly transmitted from the heated place via heat conduction. But not too high temperature. Since the current in the induction coil has a critical influence on the heating effect, when the output frequency is close to and/or equal to the resonance frequency, the circuit can be regarded as a purely resistive circuit, and most of the power supply is provided. The energy is transferred to the resistor, and the current in the circuit is thus maximized, so the adjusted induction coil frequency needs to be closer to the resonant frequency.
圖4為本案的一實施例之頻率自調的運作原理示意圖。如圖4所示，在實施例中，利用微處理器(Arduino) 41 傳送 PWM 訊號 (0~5 V)至振盪器IC 42，並利用兩個可調電阻分別將 0.1 V 設定為掃描頻率區間最低值，而 5 V 設定為頻率最高值。之後振盪器IC 42會依據接收電壓值依比例調整頻率訊號，並傳送至驅動開關 IC43，接著驅動 IGBT 輸出高頻交流電至負載，此時藉由 ACS 712 電流量測 IC 44量測輸入至負載的電流值，傳回微處理器(Arduino) 41後紀錄當時輸出此 PWM 電壓值(對應一個頻率值)收到的電流值，完成一個循環。之後藉由變動不同的 PWM 訊號值來調整輸出頻率，量測電流後並紀錄，依此循環完成掃描20~100 kHz 區間之頻率，接著撰寫程式比較這些紀錄的電流值大小，比較過後擇出一具有最大電流時候的頻率輸入到負載，完成頻率自調動作，使感應加熱效率接近或達到最佳化。FIG. 4 is a schematic diagram of the operation principle of frequency self-tuning according to an embodiment of the present invention. As shown in FIG. 4, in the embodiment, a microprocessor (Arduino) 41 is used to transmit a PWM signal (0~5 V) to the oscillator IC 42, and two adjustable resistors are used to set 0.1 V as a scanning frequency interval. The lowest value, and 5 V is set to the highest frequency. After that, the oscillator IC 42 adjusts the frequency signal according to the received voltage value and transmits it to the driving switch IC43, and then drives the IGBT to output the high-frequency alternating current to the load. At this time, the ACS 712 current measuring IC 44 measures the input to the load. The current value is returned to the microprocessor (Arduino) 41 and the current value received by the PWM voltage value (corresponding to a frequency value) is recorded to complete a cycle. After that, the output frequency is adjusted by changing the value of the different PWM signals. After measuring the current and recording, the frequency of scanning the interval of 20~100 kHz is completed according to the cycle, and then the program compares the current values of the records, and compares and selects one. The frequency with the maximum current is input to the load, and the frequency self-adjusting action is completed, so that the induction heating efficiency is close to or optimized.
而由感應加熱理論得知，當電流在感應線圈內達到最大值時，此時輸入頻率靠近及/或等於諧振頻率。此外，感應線圈會因線圈匝數、長度以及疏密等等不同造成電感值的變化，將影響所量測的電流值大小的特性，因此，在本實施例中，藉由掃描電流在頻率區間內的變動來找尋具最大電流的頻率。According to the induction heating theory, when the current reaches a maximum value in the induction coil, the input frequency is close to and/or equal to the resonance frequency. In addition, the inductance coil may change the inductance value due to the difference in the number of turns, the length, the density, and the like, which will affect the characteristics of the measured current value. Therefore, in the present embodiment, the scanning current is in the frequency interval. The change inside finds the frequency with the largest current.
請參閱圖5，其為本案一實施例之加熱模組示意圖。如圖5所示，在本實施例中，加熱模組13為一燒灼針模組，包含：熱電偶133、外針132、以及加熱線圈131。其中，利用繞線機以單芯繞線法來將加熱線圈131繞於熱電偶133前端部分形成一密集加熱線圈段，之後再放入外針132之內完成一組燒灼針模組。在一實施例中，加熱線圈131為直徑0.08mm、耐熱溫度200°C的漆包線。在一實施例中，外針132選用醫學上內臟穿刺專用的 PTC 穿刺針。除此之外，PTC 穿刺針主要由不鏽鋼 SUS 304 或 SUS 316 材料製作，此兩種材料在經過一系列如加熱、穿孔以及抽製等等之加工工藝後，會變成具備微感磁性之材料，故符合本系統對外管針具的需求。在一實施例中，使用的 18-gauge PTC 穿刺針外徑與內徑分別為 1.24 mm 以及0.96 mm，長度 150 mm。需要注意的是，在用於燒灼時，必須封住PCT穿刺針的前端空心部分，以避免在操作上造成問題，如血液或組織跑進針具內部等。在一實施例中，熱電偶133是使用K-type 熱電偶測溫棒，其系使用不鏽鋼 SUS 314 或是 SUS 316 材料包覆內部金屬線的部份，具有一定剛度可供線圈緊密纏繞於上面，加熱線圈的規格為直徑 0.5 mm，長度 200 mm，耐熱溫 800 °C。在一實施例中，加熱線圈131選用直徑 0.08 mm 的 UEW+NY (尼龍外被聚胺酯)漆包線，這種漆包線在高速捲繞或自動繞線時具有極佳之繞線性、能提供生產密度高之線圈及繞組、在高頻下具有良好品質係數、良好之密著性及捲繞性，以及可避免繞線時之損傷等等之優點，而其可承受之溫度約200 °C。而當輸入電流不大時，漆包線電壓可以承受至30 - 40V，因此在此規格下，電源供應器的規格約 30 W，使用電流不超過 1.5A，電壓不超過 40 V。在其他實施例中，漆包線為直徑 0.08 – 2.00 mm 的 UEW+NY (尼龍外被聚胺酯)漆包線，該磁感應元件為SUS 304 不鏽鋼 或 SUS 316 不鏽鋼，該電源供應模組之使用電流為0.1 – 5 A，電壓介於 1.5 - 40 V。另外，若頻率匹配時，只有加熱線圈所在位置會被明顯加熱，遠離線圈處則只有因導線電阻生熱而稍微增溫。Please refer to FIG. 5 , which is a schematic diagram of a heating module according to an embodiment of the present invention. As shown in FIG. 5, in the embodiment, the heating module 13 is a cauterization needle module, and includes a thermocouple 133, an outer needle 132, and a heating coil 131. Wherein, the heating coil 131 is wound around the front end portion of the thermocouple 133 by a winding machine to form a dense heating coil segment, and then placed in the outer needle 132 to complete a set of cauterizing needle modules. In one embodiment, the heating coil 131 is an enameled wire having a diameter of 0.08 mm and a heat resistant temperature of 200 °C. In one embodiment, the outer needle 132 is a PTC needle for medical visceral puncture. In addition, PTC needles are mainly made of stainless steel SUS 304 or SUS 316 materials, which become micro-magnetic materials after a series of processes such as heating, perforating and pumping. Therefore, it meets the requirements of the external pipe needles of this system. In one embodiment, the 18-gauge PTC needle used has an outer diameter and an inner diameter of 1.24 mm and 0.96 mm, respectively, and a length of 150 mm. It should be noted that when used for cauterization, the hollow end of the PCT puncture needle must be sealed to avoid operational problems such as blood or tissue running into the interior of the needle. In one embodiment, the thermocouple 133 is a K-type thermocouple temperature measuring rod that is coated with stainless steel SUS 314 or SUS 316 material to cover the inner metal wire portion, and has a certain rigidity for the coil to be tightly wound thereon. The heating coil is 0.5 mm in diameter, 200 mm in length and 800 °C in heat resistance. In one embodiment, the heating coil 131 is a UEW+NY (nylon urethane) enameled wire having a diameter of 0.08 mm. The enameled wire has excellent linearity at high speed winding or automatic winding, and can provide high production density. Coils and windings, good quality coefficient at high frequencies, good adhesion and winding, and the ability to avoid damage during winding, etc., can withstand temperatures of about 200 °C. When the input current is not large, the enameled wire voltage can withstand 30 - 40V, so under this specification, the power supply has a specification of about 30 W, a current of no more than 1.5A, and a voltage of no more than 40V. In other embodiments, the enameled wire is a UEW+NY (nylon urethane) enameled wire having a diameter of 0.08 - 2.00 mm, and the magnetic sensing element is SUS 304 stainless steel or SUS 316 stainless steel, and the power supply module uses a current of 0.1 - 5 A. The voltage is between 1.5 - 40 V. In addition, if the frequency is matched, only the position of the heating coil will be obviously heated, and away from the coil, the temperature will be slightly increased only due to the heat generation of the wire.
圖6為本案一實施例之加熱模組示意圖。如圖6所示，加熱模組13包含熱電偶133、內套管134，加熱線圈131、外套管137以及針頭135；其中，熱電偶133位於內套管134之內，加熱線圈131緊密纏繞於內套管134之外，而外套管137則內包熱電偶133、內套管134，加熱線圈131。內套管134材質為SUS 304不銹鋼，外徑0.69 mm，內徑 0.55 mm。利用內套管134(長度210 mm)與熱電偶133(長度200 mm)的相對配置，致使測溫點會位於加熱線圈最大的中間區塊，以便量測到最精準的溫度。在一實施例中，熱電偶133位於內套管134之內，外套管137材質為SUS 304不銹鋼，結合針頭135，將針頭135部分設計成圓錐形以利加工與穿刺，針頭135中間有一類似卡榫136，主要是讓內套管134在置入時可以有一種位置引導的功用並且固定。外套管137與針頭135則利用雷射焊接來準確地結合，如圖7所示。在一實施例中，外套管137與內套管134之間可以使用導熱膏 138來提高熱傳導的效率。6 is a schematic view of a heating module according to an embodiment of the present invention. As shown in FIG. 6, the heating module 13 includes a thermocouple 133, an inner sleeve 134, a heating coil 131, an outer sleeve 137, and a needle 135. The thermocouple 133 is located inside the inner sleeve 134, and the heating coil 131 is tightly wound around The outer sleeve 137 is surrounded by a thermocouple 133, an inner sleeve 134, and a heating coil 131. The inner sleeve 134 is made of SUS 304 stainless steel with an outer diameter of 0.69 mm and an inner diameter of 0.55 mm. Using the relative arrangement of the inner sleeve 134 (length 210 mm) and the thermocouple 133 (length 200 mm), the temperature measurement point is located in the largest intermediate block of the heating coil to measure the most accurate temperature. In one embodiment, the thermocouple 133 is located inside the inner sleeve 134, and the outer sleeve 137 is made of SUS 304 stainless steel. The needle 135 is combined with the needle 135 to design a conical shape for processing and puncture. The needle 135 has a similar card in between. The 榫 136 is primarily such that the inner sleeve 134 can have a position-directed function and be fixed when placed. The outer sleeve 137 and the needle 135 are accurately joined by laser welding, as shown in FIG. In an embodiment, a thermally conductive paste 138 may be used between the outer sleeve 137 and the inner sleeve 134 to increase the efficiency of heat transfer.
在本案一實施例中，可由一電源供應系統 (含比例-積分-微分控制器（PID控制器）)搭配一組加熱模組，並藉由一微處理器(Arduino) 來控制多台電源供應系統。這樣的方式，得以避免一組電源供應系統供應多根針，可能由於電壓與電流分配問題，產生溫度差異過大的問題；並且方便往後若需要更多加熱模組時，只需增加電源供應系統，即可擴充至指定針數，避免電壓與電流分配以及產生其他問題。 活體動物實驗In an embodiment of the present invention, a power supply system (including a proportional-integral-derivative controller (PID controller)) can be combined with a set of heating modules, and a plurality of power supplies are controlled by a microprocessor (Arduino). system. In this way, it is necessary to avoid the supply of multiple pins in a group of power supply systems, which may cause excessive temperature differences due to voltage and current distribution problems; and it is convenient to increase the power supply system if more heating modules are needed later. , can be expanded to the specified number of pins to avoid voltage and current distribution and other problems. Live animal experiment
在一實施例中，使用的 18-gauge PTC 穿刺針外徑與內徑分別為 1.24 mm 以及0.96 mm，長度 150 mm；K-type 熱電偶測溫棒，其系使用不鏽鋼 SUS 314 或 SUS 316 材料包覆內部金屬線的部份，具有一定剛度可供線圈緊密纏繞於上面，熱電偶測溫棒的規格為直徑 0.5 mm，長度 200 mm，耐熱溫 800 °C。在一實施例中，加熱線圈133選用直徑 0.08 mm 的 UEW+NY (尼龍外被聚胺酯)漆包線。另外，若頻率匹配時，只有加熱線圈所在位置的PTC針前端會被加熱，而遠離加熱線圈的針後端則不太熱。In one embodiment, the 18-gauge PTC needle used has an outer diameter and an inner diameter of 1.24 mm and 0.96 mm, respectively, and a length of 150 mm; a K-type thermocouple temperature measuring rod using stainless steel SUS 314 or SUS 316 material. The part covering the inner metal wire has a certain rigidity for the coil to be tightly wound thereon, and the thermocouple temperature measuring rod has a diameter of 0.5 mm, a length of 200 mm, and a heat-resistant temperature of 800 °C. In one embodiment, the heating coil 133 is a UEW+NY (nylon urethane) enameled wire having a diameter of 0.08 mm. In addition, if the frequency is matched, only the front end of the PTC needle where the heating coil is located will be heated, and the rear end of the needle away from the heating coil will be less hot.
選用國立成功大學動物中心之新化畜產所生產之豬隻，搭配動物中心醫事人員進行手術操作。實驗主要利用兩種加熱線圈長度(1.5 和 3 cm)，分作兩種實驗，1.5 cm 針(兩支)配合超音波影像儀從豬隻體外***，3 cm 針則先開刀後再直接***豬肝，藉以觀察肝臟燒灼的體積及形狀。 經皮穿刺實驗條件： 設定溫度：120 或 110 °C 線圈長度：1.5 cm 加熱時間：5, 10 min 輸出電壓：18 V 頻率：34 kHz (匹配頻率) 先將豬隻肚子剖開再將針具直接***肝臟內，實驗條件如下： 設定溫度：120 °C 線圈長度：3 cm 加熱時間：10 min 輸出電壓：22 V 頻率：30 kHz (匹配頻率)The pigs produced by the new animal husbandry of the National Cheng Kung University Animal Center were selected for operation with the medical staff of the animal center. The experiment mainly uses two kinds of heating coil lengths (1.5 and 3 cm), which are divided into two experiments. The 1.5 cm needle (two) is inserted from the pig outside with the ultrasonic imager, and the 3 cm needle is inserted into the pig first. Liver, to observe the volume and shape of the liver burning. Percutaneous puncture experimental conditions: Set temperature: 120 or 110 °C Coil length: 1.5 cm Heating time: 5, 10 min Output voltage: 18 V Frequency: 34 kHz (matching frequency) First cut the pig's stomach and then the needle Insert directly into the liver, the experimental conditions are as follows: Set temperature: 120 °C Coil length: 3 cm Heating time: 10 min Output voltage: 22 V Frequency: 30 kHz (matching frequency)
圖8為1.5 cm 加熱線圈穿刺試驗結果圖；圖9為3 cm 加熱線圈穿刺試驗結果圖。由圖8與圖9實驗結果顯示，本案所發展出來的針具結構強度夠，可以經皮穿刺豬隻皮膚，且能在短時間內約 30 秒即提高到止血溫度。而在活體豬隻的肝臟內搭配適當輸出電壓，能有效地升溫至設定溫度，並且有明顯的燒灼範圍。Figure 8 is a graph showing the results of a puncture test of a 1.5 cm heating coil; Figure 9 is a graph showing the results of a puncture test of a 3 cm heating coil. The experimental results shown in Fig. 8 and Fig. 9 show that the needle developed in this case has sufficient structural strength, can percutaneously puncture the pig skin, and can be raised to a hemostatic temperature in about 30 seconds in a short time. In the liver of a living pig with an appropriate output voltage, it can effectively warm up to a set temperature and has a significant burning range.
在前述實施例中，本案提出了一種新的加熱系統，其整合發展出包含加熱模組、電源供應系統以及監控系統等組件，並以實作證明所提之設計可行性高。而在實施例中，乃透過結合內感應和電阻加熱兩種原理來設計加熱模組，將導線緊密繞於熱電偶上形成感應線圈，外層套上具微感磁性的穿刺針。並透過對感應線圈通以高頻電流產生交變磁場，誘發外層的磁感性穿刺針之內壁生熱，加上感應線圈段根據阻抗自成一電阻發熱元件，藉由兩種原理生產之熱能達到特定區域加熱之目的。另外，再搭配溫度與頻率控制，再輔以電腦人機介面來設定所需溫度以及監控溫度上升情形。在一實施例中，若一加熱模組的最適發熱之所需電源供應頻率為已知時，則可透過直接操作電源供應模組的作動而將溫度與頻率調控模組省去。而在另一實施例中，若加熱線圈與其所緊密纏繞的套管之發熱特性為已知時，則熱電偶可改為其他定位元件。再者，雖然本案實施例是以活體動物實驗作為驗證，但本案的運用範圍並不限醫療用途，凡同時利用電阻加熱與內感應加熱的各項運用不脫本案所欲保護之範圍。In the foregoing embodiment, the present invention proposes a new heating system, which integrates and develops components including a heating module, a power supply system, and a monitoring system, and demonstrates the high feasibility of the design. In the embodiment, the heating module is designed by combining the two principles of internal induction and resistance heating, and the wire is tightly wound around the thermocouple to form an induction coil, and the outer layer is covered with a micro-magnetic magnetic needle. And by generating an alternating magnetic field through the high-frequency current of the induction coil, the inner wall of the magnetic inductive puncture needle of the outer layer is induced to generate heat, and the induction coil segment is self-contained as a resistance heating element according to the impedance, and the heat energy produced by the two principles is generated. Achieve heating in a specific area. In addition, with temperature and frequency control, and then with the computer man-machine interface to set the required temperature and monitor the temperature rise. In an embodiment, if the power supply frequency required for optimal heating of a heating module is known, the temperature and frequency control module can be omitted by directly operating the power supply module. In yet another embodiment, if the heating characteristics of the heating coil and its tightly wound sleeve are known, the thermocouple can be changed to other positioning elements. Furthermore, although the embodiment of the present invention is verified by a live animal experiment, the scope of application of the present invention is not limited to medical use, and the use of both resistance heating and internal induction heating is not deviated from the scope of the case.
經由前述實施例的說明以及實驗結果，充分說明本案已成功地結合內感應與電阻加熱的方式來開創新的加熱系統，並且跟同領域單獨使用內感應或電阻之加熱系統顯著不同。搭配微處理器(Arduino)的程式撰寫來控制各項條件，能達到預期效果。大體而言，本案實施例已具有以下幾點的具體成果： 1. 成功開發並證明內感應結合電阻式加熱達成發熱效果。 2. 所開發出來的針具可以小於或等於 18-gauge。 3. 所發展的熱療針具可使用 SUS 304 或 SUS 316 不鏽鋼，與現今醫療系統所使用的材料相同。 4. 已證明所發展的系統可加熱活體組織。 5. 頻率自調技術為適應性控制的一環，可應用於大功率的感應加熱或儲能充電系統。 6. 成功開發出多針燒灼，加大燒灼斷面積。Through the description of the foregoing embodiments and the experimental results, it is fully demonstrated that the present invention has successfully combined the internal induction and resistance heating to open an innovative heating system, and is significantly different from the heating system in which the internal induction or resistance is used alone. With the programming of the microprocessor (Arduino) to control the conditions, the expected results can be achieved. In general, the examples in this case have the following specific results: 1. Successfully developed and proved that the internal induction combined with resistive heating achieves a heating effect. 2. The developed needle can be less than or equal to 18-gauge. 3. The developed thermotherapy needles can be made of SUS 304 or SUS 316 stainless steel, which is the same material used in today's medical systems. 4. The developed system has been shown to heat living tissue. 5. Frequency self-adjusting technology is a part of adaptive control and can be applied to high-power induction heating or energy storage charging systems. 6. Successfully developed multi-needle cauterization and increased the burning area.
以上所提僅是本案的較佳實施例樣態，並不是用於限定本案的實施範圍；任何在此領域具有通常知識者，在不脫離本案的精神與範圍下所作的諸般變化與修飾，都不脫如附申請專利範圍所欲保護者。The above is only the preferred embodiment of the present invention and is not intended to limit the scope of implementation of the present invention; any changes and modifications made by those who have ordinary knowledge in this field without departing from the spirit and scope of the case are Not to be protected as intended by the scope of the patent application.
AC‧‧‧電源AC‧‧‧ power supply
Cr‧‧‧電容 Cr‧‧‧ capacitor
Lr‧‧‧等效電感 Lr‧‧‧ equivalent inductance
1‧‧‧加熱系統 1‧‧‧ heating system
11‧‧‧電源供應模組 11‧‧‧Power supply module
111‧‧‧Oscillator晶片 111‧‧‧Oscillator wafer
112‧‧‧TLP250光偶合器 112‧‧‧TLP250 optical coupler
113‧‧‧IR 113‧‧‧IR
2111‧‧‧電路元件 2111‧‧‧ circuit components
114‧‧‧TC4421晶片 114‧‧‧TC4421 chip
115‧‧‧TC 115‧‧‧TC
4421‧‧‧晶片 4421‧‧‧ wafer
116‧‧‧IGBT驅動開關 116‧‧‧IGBT drive switch
117‧‧‧IGBT驅動開關 117‧‧‧IGBT drive switch
118‧‧‧ACS712電流量測晶片 118‧‧‧ACS712 current measuring chip
12‧‧‧溫度監控與頻率自調模組 12‧‧‧ Temperature monitoring and frequency self-adjusting module
121‧‧‧微處理器(Arduino)(MCU)晶片開發板 121‧‧‧Microprocessor (Arduino) (MCU) chip development board
122‧‧‧TA7257P馬達驅動晶片 122‧‧‧TA7257P motor drive chip
123‧‧‧Max6675熱偶晶片 123‧‧‧Max6675 thermocouple wafer
124‧‧‧K型熱電偶 124‧‧‧K type thermocouple
13‧‧‧加熱模組 13‧‧‧heating module
131‧‧‧加熱線圈 131‧‧‧heating coil
132‧‧‧外針 132‧‧‧outer needle
133‧‧‧熱電偶 133‧‧‧ thermocouple
134‧‧‧內套管 134‧‧‧Inner casing
135‧‧‧針頭 135‧‧‧ needle
136‧‧‧卡榫 136‧‧‧Carmen
137‧‧‧外套管 137‧‧‧Outer casing
138‧‧‧導熱膏 138‧‧‧ Thermal paste
2‧‧‧半橋式串聯諧振轉換器 2‧‧‧Half-bridge series resonant converter
21‧‧‧振盪器IC 21‧‧‧Oscillator IC
22‧‧‧開關驅動IC 22‧‧‧Switch Driver IC
23‧‧‧整流 23‧‧‧Rectification
24‧‧‧濾波 24‧‧‧Filter
25‧‧‧半橋式諧振轉換器 25‧‧‧Half-bridge resonant converter
31‧‧‧微處理器(Arduino) 31‧‧‧Microprocessor (Arduino)
32‧‧‧MAX6675熱偶晶片 32‧‧‧MAX6675 thermocouple chip
33‧‧‧K型熱電偶 33‧‧‧K type thermocouple
34‧‧‧TA7257P馬達驅動晶片 34‧‧‧TA7257P motor drive chip
41‧‧‧微處理器(Arduino) 41‧‧‧Microprocessor (Arduino)
42‧‧‧振盪器IC 42‧‧‧Oscillator IC
43‧‧‧驅動開關IC 43‧‧‧Drive Switch IC
44‧‧‧ACS 44‧‧‧ACS
712‧‧‧電流量測IC 712‧‧‧ Current Measurement IC
圖1為本案加熱系統的一實施例示意圖。FIG. 1 is a schematic view of an embodiment of a heating system of the present invention.
圖2為由半橋式串聯諧振轉換器所製作之電源供應器實施例示意圖。2 is a schematic diagram of an embodiment of a power supply fabricated by a half bridge series resonant converter.
圖3為本案一溫度監控模組實施例之作動原理示意圖。FIG. 3 is a schematic diagram showing the operation principle of an embodiment of a temperature monitoring module of the present invention.
圖4為本案的一實施例之頻率自調的運作原理示意圖。FIG. 4 is a schematic diagram of the operation principle of frequency self-tuning according to an embodiment of the present invention.
圖5其為本案一實施例之加熱模組示意圖。FIG. 5 is a schematic diagram of a heating module according to an embodiment of the present invention.
圖6為本案一實施例之加熱模組示意圖。6 is a schematic view of a heating module according to an embodiment of the present invention.
圖7為本案一實施例之加熱模組截面示意圖。FIG. 7 is a schematic cross-sectional view of a heating module according to an embodiment of the present invention.
圖8為1.5 cm 加熱線圈穿刺試驗結果圖。Figure 8 is a graph showing the results of a 1.5 cm heating coil puncture test.
圖9為3 cm 加熱線圈穿刺試驗結果圖。Figure 9 is a graph showing the results of a puncture test of a 3 cm heating coil.
Claims (6)
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| TW103146667A TWI644589B (en) | 2014-12-31 | 2014-12-31 | Heating system |
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| PL3679765T3 (en) * | 2017-09-06 | 2022-01-10 | Jt International Sa | Induction heating assembly for a vapour generating device |
| JP2020187685A (en) * | 2019-05-17 | 2020-11-19 | アズビル株式会社 | Temperature controller and abnormality determination method |
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|---|---|---|---|---|
| US20040078038A1 (en) * | 2001-01-19 | 2004-04-22 | Kai Desinger | Device for the electrothermal treatment of the human or animal body |
| US6895282B2 (en) * | 2002-10-04 | 2005-05-17 | Boston Scientific Scimed, Inc. | Induction heating for the delivery of thermal therapy |
| WO2007014063A2 (en) * | 2005-07-21 | 2007-02-01 | Vnus Medical Technologies, Inc. | Systems and methods for treating a hollow anatomical structure |
| TW201008543A (en) * | 2008-08-21 | 2010-03-01 | Univ Nat Cheng Kung | Thermal therapy needle heated by induction of high frequency magnetic field |
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