A bipolar temperature control method and apparatus for radio frequency surgery
By employing a bipolar temperature control method that combines real-time temperature monitoring and dynamic power adjustment, the problem of unstable temperature control in traditional bipolar radiofrequency surgical devices has been solved, achieving high-precision temperature control and ensuring surgical safety and effectiveness.
Patent Information
- Authority / Receiving Office
- CN · China
- Patent Type
- Patents(China)
- Current Assignee / Owner
- BEIJING TAKTVOLL TECH CO LTD
- Filing Date
- 2025-08-25
- Publication Date
- 2026-07-14
AI Technical Summary
Traditional bipolar radiofrequency surgical devices regulate power through impedance feedback, which leads to unstable temperature control, especially when tissue characteristics change abruptly, resulting in power response delays that affect surgical safety and efficacy.
The system uses a central control unit to compare temperature thresholds in real time and dynamically adjust power output. It achieves precise temperature control through direct temperature signal closed-loop control, combined with alternating acquisition and cross-channel prediction mechanisms.
This improved temperature control precision, reduced the risk of tissue carbonization or coagulation failure, and enhanced the safety and success rate of the surgery.
Smart Images
Figure CN120918778B_ABST
Abstract
Description
Technical Field
[0001] This application relates to the technical field of medical devices, and in particular to a bipolar temperature control method and device for radiofrequency surgery. Background Technology
[0002] Bipolar radiofrequency surgical devices use high-frequency current between two electrodes to cut tissue or achieve coagulation, and are widely used in minimally invasive surgery. The core of these devices lies in the precise control of the surgical area temperature to avoid excessive tissue carbonization or insufficient coagulation. Traditional techniques rely on impedance feedback to adjust power, but the impedance of human tissue dynamically changes with factors such as water content and thickness, causing fluctuations in output power, affecting temperature control stability, and consequently reducing surgical safety and efficacy.
[0003] For related technologies, please refer to Chinese invention patent with announcement number CN113576656B, which proposes a method for detecting the quality of contact between an electrode plate and skin. By measuring the voltage value of the electrode plate, the voltage X1 when there is no contact and the voltage X2 when there is full contact, a linear function Y=(X-X1) / (X2-X1) is constructed to calculate the contact area ratio (Y) in real time. If the Y value is lower than the threshold, the current is interrupted to prevent burns.
[0004] However, while this approach improves the reliability of electrode contact detection, the device indirectly infers tissue condition through impedance changes rather than directly monitoring temperature. If tissue characteristics change abruptly, such as bleeding causing a sudden drop in impedance, power feedback delays may occur, leading to the actual temperature deviating from the set value. Summary of the Invention
[0005] To address at least one of the aforementioned technical problems, this application provides a bipolar temperature control method and device for radiofrequency surgery.
[0006] In a first aspect, this application provides a bipolar temperature control method for radiofrequency surgery, employing the following technical solution: A bipolar temperature control method for radiofrequency surgery, comprising the following steps executed by a central control unit: Acquire real-time temperature values, including the real-time temperature values of the first thermocoagulation needle channel and the second thermocoagulation needle channel. The real-time temperature value is compared with a preset temperature threshold. When the real-time temperature value is lower than the preset temperature threshold, the output power value of the corresponding thermal condensation needle channel is increased; When the real-time temperature value is higher than the preset temperature threshold, reduce the output power value of the corresponding thermal condensation needle channel; The power value is dynamically adjusted to keep the real-time temperature value stable within the preset temperature threshold range.
[0007] By adopting the above technical solution, the central control unit compares the temperature with the preset threshold in real time and dynamically adjusts the power output to ensure that the temperature of the surgical area remains stable within the set range. Replacing traditional impedance-based indirect temperature control with direct temperature signal closed-loop control solves the problem of power response delay caused by sudden tissue changes such as bleeding. This effectively eliminates impedance-temperature conversion errors, improves temperature control accuracy to clinically safe thresholds, and significantly reduces the risk of tissue carbonization or coagulation failure.
[0008] In one possible implementation, the step of obtaining the real-time temperature value includes: Temperature signals are acquired alternately, including the temperature signal of the first thermal condensation needle channel and the temperature signal of the second thermal condensation needle channel, wherein only one channel of the temperature acquisition circuit is activated during a single acquisition process.
[0009] By adopting the above technical solution, signal crosstalk can be avoided and power consumption can be reduced by alternately activating the acquisition circuit of a single channel. This effectively solves the problem of dual-channel hardware resource conflict. It achieves independent monitoring of dual channels with a single acquisition circuit, which simplifies the equipment structure and improves system reliability, providing basic support for multi-needle collaborative surgery.
[0010] In one possible implementation, the alternating temperature signal acquisition step involves performing the following steps: Predicted temperatures are generated based on historical temperature values and trends of currently inactive channels. If the predicted temperature exceeds the safety threshold, a power adjustment command will be sent to the channel in advance.
[0011] By adopting the above technical solution, the real-time status of inactive channels can be extrapolated using historical data, and power intervention can be triggered in advance. This solves the control lag problem caused by the time-sharing sampling blind zone through cross-channel temperature trend prediction. The temperature monitoring blind zone can be compressed to near zero, reducing the risk of overheating. This is especially suitable for rapid heating scenarios such as high-frequency electrocoagulation.
[0012] In one possible implementation, the preset temperature threshold includes: It offers three switchable temperature settings: 70°C, 80°C, and 85°C, each corresponding to an independent temperature threshold range.
[0013] By adopting the above technical solutions, the independent threshold range design can avoid parameter interference during gear switching. Through multi-level fine temperature control, it can effectively solve the different temperature requirements of different surgical tissues, expand the clinical adaptability of the equipment, and enable doctors to accurately match the surgical type and temperature parameters, thereby improving the success rate of surgery.
[0014] In one possible implementation, the following steps are performed when switching temperature settings: The temperature gradually approaches the target temperature value at a preset heating rate. The system monitors the acceleration of temperature changes in real time, and triggers emergency cooling if the acceleration exceeds the limit.
[0015] By adopting the above technical solution, the target value can be approached at a controllable rate, and abnormal changes can be detected in real time by combining acceleration. This effectively solves the problem of temperature overshoot during gear switching by gradient heating and acceleration monitoring, and prevents tissue carbonization damage.
[0016] In one possible implementation, the method further includes: When the real-time temperature value of any channel exceeds the preset temperature threshold by a set amount, the power output of that channel will be immediately cut off and an alarm signal will be triggered.
[0017] By adopting the above technical solutions, power cut-off can block energy input at the source, and audible and visual alarms can simultaneously alert the operator. Through the dual-level over-temperature protection mechanism, the problem of continuous thermal damage caused by equipment failure can be effectively solved, hardware-level safety redundancy can be established, and the incidence of serious medical accidents can be greatly reduced.
[0018] In one possible implementation, the step of triggering the alarm signal is followed by: Start the active electrode cooling device; A cooling countdown progress bar is dynamically displayed on the screen.
[0019] By adopting the above technical solutions, the cooling device can quickly neutralize the residual heat of the electrodes, quantify the cooling process with a progress bar, and effectively solve the problem of residual thermal inertia after power cut-off by actively eliminating residual heat and providing visual prompts. This further reduces the final temperature deviation of the tissue and reduces operational anxiety through human-computer interaction.
[0020] In one possible implementation, the step of dynamically adjusting the power value includes: When both channels need to increase power simultaneously, power quotas are allocated based on the temperature deviation of each channel. If the total power demand exceeds the upper limit, the output power will be gradually increased according to the time step.
[0021] By adopting the above technical solutions and allocating quotas according to the urgency of demand, the step-by-step increase can avoid current surges. This achieves the solution of system overload caused by dual-channel competition through a dynamic power arbitration mechanism, thereby achieving the optimal temperature control effect under limited total power and further shortening the time to meet the standards in low-temperature scenarios with both channels operating simultaneously.
[0022] In one possible implementation, the step of obtaining the real-time temperature value is preceded by: Activate the electromagnetic shielding assembly inside the thermal coagulation needle; The acquired temperature signal is subjected to low-frequency filtering to eliminate high-frequency interference.
[0023] By adopting the above technical solutions, physical shielding can block electromagnetic coupling, low-frequency filtering can extract effective signals, and high-frequency current contamination of temperature signals can be solved through three-level anti-interference protection, thereby reducing acquisition errors and providing a high-precision data foundation for closed-loop temperature control.
[0024] Secondly, this application provides a bipolar temperature control device for radiofrequency surgery, characterized in that it comprises: The temperature acquisition module is used to acquire the real-time temperature values of the first and second thermal condensation needle channels. The central control unit, connected to the temperature acquisition module, is used to compare the real-time temperature value with a preset temperature threshold; and to generate power adjustment commands, specifically, When the real-time temperature value is lower than the preset temperature threshold, increase the output power of the corresponding channel; When the real-time temperature value is higher than the preset temperature threshold, reduce the output power of the corresponding channel; The power output module is connected to the central control unit and is used to output power to the corresponding thermal condensation needle channel according to the power adjustment command.
[0025] By adopting the above technical solution, the temperature acquisition module is directly embedded in the head of the thermoforming needle, the central control unit integrates the decision-making algorithm, and the power output module responds to commands independently. The method is implemented through a modular hardware architecture, thereby constructing a complete physical closed loop of detection, decision-making, and execution, which further shortens the temperature control response delay. Attached Figure Description
[0026] Figure 1 This is a flowchart illustrating a bipolar temperature control method for radiofrequency surgery provided in an embodiment of this application.
[0027] Figure 2 This is a schematic diagram of the structure of a bipolar temperature control device for radiofrequency surgery provided in an embodiment of this application.
[0028] Figure 3 This is a schematic diagram of the structure of an electronic device provided in an embodiment of this application. Detailed Implementation
[0029] The technical solutions in this application will now be described with reference to all the accompanying drawings. Obviously, the described embodiments are only a part of the embodiments of this application, and not all of them.
[0030] In the description of the embodiments of this application, unless otherwise stated, " / " means "or". For example, A / B can mean A or B. "And / or" in this document is merely a description of the relationship between related objects, indicating that three relationships can exist. For example, A and / or B can represent: A existing alone, A and B existing simultaneously, or B existing alone. Furthermore, in the description of the embodiments of this application, "plural" or "multiple" refers to two or more than two.
[0031] Hereinafter, the terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance or implicitly specifying the number of technical features indicated. Thus, a feature defined as "first" or "second" may explicitly or implicitly include one or more of that feature. In the description of this embodiment, unless otherwise stated, "a plurality of" means two or more.
[0032] The terminology used in the following embodiments is for the purpose of describing particular embodiments only and is not intended to be limiting of this application. As used in the specification and appended claims of this application, the singular expressions “a,” “an,” “the,” “the,” “the,” and “this” are intended to also include expressions such as “one or more,” unless the context clearly indicates otherwise. It should also be understood that in the following embodiments of this application, “at least one” and “one or more” refer to one, two, or more than two.
[0033] References to "one embodiment" or "some embodiments" as described in this specification mean that one or more embodiments of this application include a specific feature, structure, or characteristic described in connection with that embodiment. Therefore, the phrases "one embodiment," "some embodiments," "another embodiment," "other embodiments," etc., appearing in different parts of this specification do not necessarily refer to the same embodiment, but rather mean "one or more, but not all, embodiments," unless otherwise specifically emphasized. The terms "comprising," "including," "having," and variations thereof mean "including but not limited to," unless otherwise specifically emphasized.
[0034] This application provides a bipolar temperature control method for radiofrequency surgery, executed by an electronic device. This electronic device can be a standalone physical electronic device, a cluster of multiple physical electronic devices, a distributed system, or a cloud electronic device providing cloud computing services. This application does not impose limitations on this method. Figure 1 As shown, the method involves the central control unit executing the following steps: S100: Obtain real-time temperature value.
[0035] Specifically, the real-time temperature values include the real-time temperature values of the first thermocoagulation needle channel and the second thermocoagulation needle channel.
[0036] Specifically, both the first and second thermocoagulation needles integrate a T-type thermocouple sensor at their heads, with a temperature measurement range of 50-100°C, and are connected to the temperature acquisition module via a twisted-pair shielded cable. The temperature acquisition module includes a preamplifier and a 24-bit ADC, with a sampling frequency of 1kHz.
[0037] Furthermore, the thermocouple generates a microvolt-level voltage signal, which is transmitted through a shielded wire, amplified by a preamplifier and digitized by an ADC, and then transmitted to the central control unit via the SPI bus.
[0038] Furthermore, a magnesium oxide insulating layer is placed between the thermocouple and the electrodes to block direct coupling of high-frequency current; at the same time, the signal line is covered with a nanocrystalline magnetic ring to suppress common-mode interference.
[0039] Furthermore, by using an embedded thermocouple design, the distance between the temperature monitoring point and the surgical site is ≤0.5mm, allowing direct acquisition of the internal tissue temperature and providing high-precision input for closed-loop control, thereby eliminating the positional error of traditional surface temperature measurement.
[0040] In some embodiments, to effectively resolve the problem of dual-channel hardware resource conflict, the step of obtaining real-time temperature values includes the following steps: S101, alternately acquire temperature signals.
[0041] Specifically, the temperature signal includes the temperature signal of the first thermal condensation needle channel and the temperature signal of the second thermal condensation needle channel, wherein only one channel's temperature acquisition circuit is activated during a single acquisition process.
[0042] Specifically, the central control unit has a built-in dual-channel analog switch with a switching time of <1μs, and alternately conducts the signal paths of the first and second thermal coagulation needle channels at a cycle of 0.1ms. When channel 1 is activated, the ADC input of channel 2 is set to a high-impedance state and automatically resets during the next cycle switch.
[0043] Furthermore, the time-division multiplexing architecture enables independent acquisition of dual channels using a single set of ADC resources, effectively reducing costs and avoiding crosstalk between dual-channel signals, thus reducing power consumption.
[0044] In summary, by alternately activating the acquisition circuit of a single channel, signal crosstalk can be avoided and power consumption can be reduced, effectively solving the problem of dual-channel hardware resource conflict. It achieves independent monitoring of dual channels with a single acquisition circuit, which simplifies the equipment structure and improves system reliability, providing basic support for multi-needle collaborative surgery.
[0045] In some embodiments, to address the control lag problem caused by the time-division sampling blind zone, the following steps are performed during the alternating temperature signal acquisition step: S102. Generate predicted temperature based on the historical temperature values and trends of the currently inactive channels.
[0046] Specifically, the central control unit expands 32KBSRAM to store historical channel temperature data for the most recent 10 cycles.
[0047] S103. If the predicted temperature exceeds the safety threshold, a power adjustment command is sent to the channel in advance.
[0048] Specifically, when acquiring channel 1, the system retrieves the previous three sampled values from channel 2, calculates the slope of change, and then extrapolates the current predicted value. A safety threshold of 85°C is set here; if the predicted value exceeds 85°C, a power reduction command is immediately sent to the power module.
[0049] Furthermore, by adopting a cross-channel prediction mechanism, the limitation of time-sharing sampling blind zone can be overcome, thereby compressing the control delay from 0.1ms to close to zero, and effectively reducing the risk of overheating.
[0050] In summary, by extrapolating the real-time status of inactive channels using historical data and triggering power intervention in advance, the control lag problem caused by the time-sharing sampling blind zone can be solved through cross-channel temperature trend prediction. This can compress the temperature monitoring blind zone to near zero, reduce the risk of overheating, and is especially suitable for rapid heating scenarios such as high-frequency electrocoagulation.
[0051] In some implementations, to address the issue of high-frequency current contamination of the temperature signal, the following steps are included before acquiring the real-time temperature value: S104. Activate the electromagnetic shielding assembly inside the thermal coagulation needle.
[0052] Specifically, the thermocoagulation needle is equipped with a copper mesh shielding layer with a coverage rate of 95% and a grounding impedance of <0.1Ω.
[0053] S105. Perform low-frequency filtering on the acquired temperature signal to eliminate high-frequency interference.
[0054] Specifically, the signal path is configured with a fourth-order low-pass filter with a cutoff frequency of 10Hz. The thermocouple signal is shielded from high-frequency noise by a copper mesh and attenuated by at least 470kHz components by the filter to achieve a clean temperature signal output.
[0055] Furthermore, a three-level anti-interference protection system is adopted to effectively improve the signal-to-noise ratio, thereby further reducing the temperature measurement error caused by high-frequency interference.
[0056] In summary, physical shielding can block electromagnetic coupling, low-frequency filtering can extract effective signals, and high-frequency current contamination of temperature signals can be solved through three-level anti-interference protection, thereby reducing acquisition errors and providing a high-precision data foundation for closed-loop temperature control.
[0057] In this embodiment, the method further includes the following steps: S200: Compare the real-time temperature value with the preset temperature threshold.
[0058] Specifically, the central control unit has preset temperature threshold parameters including three switchable temperature levels: 70°C, 80°C, and 85°C. Each level corresponds to an independent temperature threshold range, specifically 70°C (±1°C), 80°C (±1°C), and 85°C (±1.5°C).
[0059] In this system, doctors can select the gear level via the touchscreen, and the central control unit will call the corresponding threshold. The real-time temperature will be compared with the threshold to generate a deviation value.
[0060] Furthermore, the design of independent threshold ranges can effectively avoid parameter conflicts when switching gears, which is especially supported in delicate surgeries involving different tissues such as blood vessels and nerves.
[0061] In summary, the independent threshold range design avoids parameter interference during temperature switching, and can effectively address the different temperature requirements of different surgical tissues through multi-level precise temperature control. This expands the clinical adaptability of the equipment, allowing doctors to accurately match surgical types and temperature parameters, thereby improving the success rate of surgery.
[0062] In some embodiments, in order to effectively solve the temperature overshoot problem during temperature gear switching by monitoring gradient heating and acceleration, the following steps are performed when switching temperature gears: S201, gradually approach the target temperature value at a preset heating rate.
[0063] Specifically, the central control unit has a built-in timer to control the heating rate, which is set to 3°C / s by default.
[0064] S202: Real-time monitoring of temperature change acceleration; if the acceleration exceeds the limit, emergency cooling is triggered.
[0065] Specifically, the central control unit has a built-in acceleration monitoring circuit with a response time of 10ms, and is connected to an air-cooled radiator.
[0066] For example, when the doctor switches to the 85°C setting, the temperature increases at a rate of 3°C / s to the target value. If the temperature rise acceleration is detected to be greater than 1°C / s², the cooling fan will be activated immediately.
[0067] Furthermore, real-time acceleration monitoring can block temperature overshoot paths and effectively reduce gear shift overshoot.
[0068] In summary, by approaching the target value at a controllable rate and combining it with real-time acceleration to detect abnormal changes, the problem of temperature overshoot during gear switching can be effectively solved through gradient heating and acceleration monitoring, thus preventing tissue carbonization damage.
[0069] In this embodiment, the method further includes the following steps: S300 When the real-time temperature value is lower than the preset temperature threshold, increase the output power value of the corresponding thermal condensation needle channel.
[0070] Specifically, the power output module has a built-in programmable gain amplifier (PGA), and the central control unit is equipped with a digital potentiometer to control the output current via a bus.
[0071] When the central control unit detects that the real-time temperature is lower than the preset temperature threshold, it calculates the power compensation amount. For example, if -2°C requires +0.4W, it sends a gain adjustment command to the PGA to increase the output power of the corresponding channel.
[0072] Furthermore, the real-time power compensation mechanism can directly respond to temperature deviations, thereby breaking through the traditional fixed power output mode, eliminating the heating delay caused by impedance mutations, and ensuring that the tissue temperature can quickly return to the set range.
[0073] S400 When the real-time temperature value is higher than the preset temperature threshold, reduce the output power value of the corresponding thermal condensation needle channel.
[0074] Specifically, the power output module integrates a fast attenuation circuit, implemented by a MOSFET switching array, and the central control unit is equipped with a voltage comparator to monitor the output current in real time.
[0075] When the central control unit detects that the real-time temperature exceeds the preset temperature threshold, it generates a power reduction command to trigger the MOSFET to turn off part of the circuit, and the output power decreases in a stepwise manner, for example, by 0.5W every 50ms.
[0076] Furthermore, active power attenuation can replace passive heat dissipation, effectively blocking continuous energy input and shortening the stabilization time of over-temperature conditions, thus preventing tissue carbonization.
[0077] S500 dynamically adjusts the power value to keep the real-time temperature value stable within the preset temperature threshold range.
[0078] Specifically, the central control unit has a built-in dual-channel PID controller, which can independently adjust the power of each channel. The hollow unit has a built-in memory to store the temperature-power mapping table.
[0079] The system collects temperature data in real time, calculates power adjustment using PID control, and optimizes the output by querying a mapping table. This process is repeated until the temperature stabilizes within ±1°C.
[0080] Furthermore, a dual-channel closed-loop negative feedback system can be designed to achieve adaptive power distribution. Especially in cases of sudden changes such as bleeding during surgery, the impedance will drop sharply, and temperature fluctuations can be controlled within ±0.8°C, thereby meeting clinical safety standards.
[0081] Based on the above steps, the central control unit compares the temperature with the preset threshold in real time and dynamically adjusts the power output to ensure that the temperature in the surgical area remains stable within the set range. By replacing traditional impedance indirect temperature control with direct temperature signal closed-loop control, the problem of power response delay caused by sudden tissue changes such as bleeding is solved. This effectively eliminates impedance-temperature conversion errors, improves temperature control accuracy to clinically safe thresholds, and significantly reduces the risk of tissue carbonization or coagulation failure.
[0082] In some embodiments, in order to solve the system overload problem caused by dual-channel competition and achieve the optimal temperature control effect under total power limitation, the step of dynamically adjusting the power value includes the following steps: S501. When both channels need to increase power simultaneously, power quotas are allocated according to the temperature deviation values of each channel.
[0083] S502. If the total power demand exceeds the upper limit, the output power will be gradually increased according to the time step.
[0084] Specifically, the power output module includes dual DACs with a total power limit of 10W. When both channels need to increase power, the temperature deviation ratio is calculated. For example, if channel 1 needs 7W and channel 2 needs 5W, the power is allocated in a 7:3 ratio. If the total power is greater than 10W, it first outputs 9W and then gradually increases to 10W.
[0085] Furthermore, by adopting a stepped power enhancement mechanism, overcurrent protection can be avoided, thereby further shortening the temperature control compliance time in dual-channel low-temperature scenarios.
[0086] In summary, allocating quotas according to the urgency of demand and implementing tiered increases can avoid current surges. This achieves the solution to system overload caused by dual-channel competition through a dynamic power arbitration mechanism, resulting in optimal temperature control under limited total power and further shortening the time to meet standards in low-temperature scenarios with both channels operating simultaneously.
[0087] In some embodiments, to address the problem of persistent thermal damage caused by device failure, the method may further include the following steps: S600: When the real-time temperature value of any channel exceeds the preset temperature threshold by a set amount, the power output of that channel will be immediately cut off and an alarm signal will be triggered.
[0088] Specifically, the hollow unit has a built-in relay connected in series in the power output circuit. It is also equipped with a buzzer and a red LED alarm light.
[0089] For example, the preset setting value here is 5°C. When the real-time temperature is detected to exceed the preset temperature threshold of 5°C, the relay cuts off the circuit and triggers an audible and visual alarm simultaneously.
[0090] Furthermore, hardware-level forced power-off can establish safety redundancy, thereby completely eliminating the problem of tissue carbonization caused by equipment failure.
[0091] In summary, power cut-off can block energy input at the source, and audible and visual alarms can simultaneously alert the operator. Through the dual-level over-temperature protection mechanism, the problem of continuous thermal damage caused by equipment failure can be effectively solved, hardware-level safety redundancy can be established, and the incidence of serious medical accidents can be greatly reduced.
[0092] In some embodiments, in order to effectively solve the problem of residual thermal inertia after power cut-off, the alarm signal triggering step further includes the following steps: S601. Start the active electrode cooling device.
[0093] S602: The cooling countdown progress bar is dynamically displayed on the screen.
[0094] Specifically, the active electrode cooling device includes a cooling element that is in close contact with the base of the electrode. Simultaneously, the LCD screen incorporates a progress bar generation algorithm.
[0095] When an alarm signal is triggered, the cooling chip is activated for active cooling, and the remaining cooling time is calculated in real time, with a countdown progress bar displayed on the screen, such as 0%-100%.
[0096] Furthermore, by designing active thermal inertia compensation, the limitations of traditional natural cooling can be overcome, thereby reducing the final temperature deviation of the tissue and shortening the cooling time.
[0097] In summary, the cooling device can quickly neutralize residual heat from the electrodes, quantify the cooling process with a progress bar, and effectively solve the problem of residual thermal inertia after power cut-off by actively eliminating residual heat and providing visual prompts. This further reduces the final temperature deviation of the tissue and reduces operational anxiety through human-computer interaction.
[0098] The following describes the bipolar temperature control device for radiofrequency surgery provided in the embodiments of this application. The bipolar temperature control device for radiofrequency surgery described below can be referred to in correspondence with the bipolar temperature control method for radiofrequency surgery described above.
[0099] refer to Figure 2 The bipolar temperature control device for radiofrequency surgery includes: Temperature acquisition module 1 is used to acquire the real-time temperature values of the first and second thermal condensation needle channels.
[0100] The temperature acquisition module 1 includes a thermocouple sensor. The heads of the first and second thermocouple needles are embedded with a T-type thermocouple sensor and are coated with a magnesium oxide insulating layer.
[0101] The temperature acquisition module 1 also includes a signal processing circuit, which includes a twisted-pair shielded cable to transmit microvolt-level temperature signals; it also includes a low-noise preamplifier and an ADC.
[0102] Among them, the thermocouple sensor can sense tissue temperature and generate a voltage signal, which is transmitted through a shielded wire to resist interference, and then the signal-to-noise ratio is improved by an amplifier and digitized by an ADC. Finally, it is output to the central control unit 2 through the SPI bus.
[0103] Central control unit 2 is connected to temperature acquisition module 1 and is used to compare real-time temperature values with preset temperature thresholds; and to generate power adjustment commands, specifically, When the real-time temperature value is lower than the preset temperature threshold, increase the output power of the corresponding channel; When the real-time temperature value is higher than the preset temperature threshold, the output power of the corresponding channel is reduced.
[0104] The central control unit 2 includes a microprocessor and integrates a dual-channel PID controller; it also includes a storage unit that stores a temperature-power mapping table and caches real-time historical temperature data.
[0105] For example, after receiving the data transmitted by the temperature acquisition module 1, the central control unit 2 compares it with preset thresholds, which are 70°C, 80°C, and 85°C. If the real-time temperature is lower than the preset threshold, an "increase power" command is generated; if the temperature is higher than the threshold, an "decrease power" command is generated.
[0106] Power output module 3 is connected to central control unit 2 and is used to output power to the corresponding thermal condensation needle channel according to power adjustment command.
[0107] The power output module 3 includes a power drive circuit controlled by a dual-channel MOSFET switch array and configured with a programmable gain amplifier (PGA). The power output module 3 also includes an overcurrent detection comparator and a mechanical relay.
[0108] Among them, after receiving the command from the central control unit 2, the power output module 3 adjusts the voltage gain through the PGA and then outputs the corresponding power to the thermal condensation needle through the MOSFET.
[0109] At the same time, the output current is monitored in real time, and if it exceeds the limit, the relay is triggered to cut off the circuit.
[0110] In summary, the temperature acquisition module 1 is directly embedded in the head of the thermoforming needle, the central control unit 2 integrates the decision-making algorithm, and the power output module 3 responds to commands independently. This modular hardware architecture enables the implementation of the method, thereby constructing a complete physical closed loop of detection, decision-making, and execution, which further shortens the temperature control response delay.
[0111] This application provides an electronic device, such as... Figure 3 As shown, Figure 3 This is a schematic diagram of the structure of an electronic device provided in an embodiment of this application. Figure 3 The illustrated electronic device 300 includes a processor 301 and a memory 303. The processor 301 and the memory 303 are connected, for example, via a bus 302. Optionally, the electronic device 300 may also include a transceiver 304. It should be noted that in practical applications, the transceiver 304 is not limited to one type, and the structure of this electronic device 300 does not constitute a limitation on the embodiments of this application.
[0112] Processor 301 may be a CPU (Central Processing Unit), a general-purpose processor, a DSP (Digital Signal Processor), an ASIC (Application Specific Integrated Circuit), an FPGA (Field Programmable Gate Array), or other programmable logic devices, transistor logic devices, hardware components, or any combination thereof. It can implement or execute the various exemplary logic blocks, modules, and circuits described in conjunction with the embodiments of this application. Processor 301 may also be a combination that implements computing functions, such as including one or more microprocessor combinations, a combination of a DSP and a microprocessor, etc.
[0113] Bus 302 may include a pathway for transmitting information between the aforementioned components. Bus 302 may be a PCI (Peripheral Component Interconnect) bus or an EISA (Extended Industry Standard Architecture) bus, etc. Bus 302 can be divided into address bus, data bus, control bus, etc. For ease of representation, Figure 3 The bus is represented by a single thick line, but this does not mean that there is only one bus or one type of bus.
[0114] The memory 303 may be a ROM (Read-Only Memory) or other type of static storage device capable of storing static information and instructions, RAM (Random Access Memory) or other type of dynamic storage device capable of storing information and instructions, or it may be an EEPROM (Electrically Erasable Programmable Read-Only Memory), a CD-ROM (Compact Disc Read-Only Memory) or other optical disc storage, optical disc storage (including compressed optical discs, laser discs, optical discs, digital universal optical discs, Blu-ray discs, etc.), magnetic disk storage media or other magnetic storage devices, or any other medium capable of carrying or storing desired program code in the form of instructions or data structures and accessible by a computer, but not limited thereto.
[0115] The memory 303 is used to store application code that executes the scheme of the embodiments of this application, and its execution is controlled by the processor 301. The processor 301 is used to execute the application code stored in the memory 303 to implement the content shown in the foregoing method embodiments.
[0116] Among them, electronic devices include, but are not limited to: mobile terminals such as mobile phones, laptops, digital radio receivers, PDAs (personal digital assistants), PADs (tablet computers), PMPs (portable multimedia players), and in-vehicle terminals (such as in-vehicle navigation terminals), as well as fixed terminals such as digital TVs and desktop computers. Figure 3 The electronic device shown is merely an example and should not impose any limitation on the functionality and scope of use of the embodiments of this application.
[0117] This application provides a computer-readable storage medium storing a computer program, which, when executed by a processor, implements the steps of the bipolar temperature control method for radiofrequency surgery as described above.
[0118] Since the embodiments of the computer-readable storage medium portion correspond to the embodiments of the method portion, please refer to the description of the embodiments of the method portion for the embodiments of the computer-readable storage medium portion.
[0119] It should be understood that although the steps in the flowcharts of the accompanying figures are shown sequentially as indicated by the arrows, these steps are not necessarily executed in the order indicated by the arrows. Unless explicitly stated herein, there is no strict order restriction on the execution of these steps, and they can be executed in other orders. Moreover, at least some steps in the flowcharts of the accompanying figures may include multiple sub-steps or multiple stages. These sub-steps or stages are not necessarily completed at the same time, but can be executed at different times, and their execution order is not necessarily sequential, but can be performed alternately or in turn with other steps or at least some of the sub-steps or stages of other steps.
[0120] The above are only some embodiments of this application. It should be noted that for those skilled in the art, several improvements and modifications can be made without departing from the principle of this application, and these improvements and modifications should also be considered within the scope of protection of this application.
Claims
1. A bipolar temperature control method for radiofrequency surgery, characterized in that, The central control unit executes the following steps: The system acquires real-time temperature values, including the real-time temperature values of the first and second thermocoagulation needle channels. These real-time temperature values are obtained through T-type thermocouple sensors integrated into the heads of the first and second thermocoagulation needles and connected to a temperature acquisition module via twisted-pair shielded cables. A magnesium oxide insulating layer is provided between the thermocouple and the electrodes. The signal lines of the thermocouples are covered with nanocrystalline magnetic rings. The temperature monitoring point of the T-type thermocouple is ≤0.5mm away from the surgical site, allowing direct acquisition of internal tissue temperature. The temperature acquisition module includes a preamplifier and a 24-bit analog-to-digital converter with a sampling frequency of 1kHz, used for digital processing of the microvolt-level voltage signals generated by the thermocouples. Acquiring real-time temperature values involves alternately acquiring temperature signals. The signal paths of the first and second thermal condensation needle channels are alternately connected to a shared analog-to-digital converter via a dual-channel analog switch built into the central control unit, with a switching time of less than 1 microsecond and a period of 0.1 milliseconds. When one channel is on, the input terminal of the analog-to-digital converter of the other channel is set to a high-impedance state. The predicted temperature is generated based on the historical temperature values and trends of the currently inactive channel. The central control unit is expanded with a memory to store historical channel temperature data from the most recent multiple acquisition cycles. Specifically, the predicted temperature is generated by retrieving the first three sampled values of the currently inactive channel, calculating the slope of change, and extrapolating this to generate the predicted temperature for that channel. The real-time temperature value is then compared with a preset temperature threshold. This preset temperature threshold includes three switchable temperature levels: 70°C, 80°C, and 85°C, each corresponding to an independent temperature threshold range. When the real-time temperature value is lower than the preset temperature threshold, the output power value of the corresponding thermal condensation needle channel is increased; When the real-time temperature value is higher than the preset temperature threshold, reduce the output power value of the corresponding thermal condensation needle channel; If the predicted temperature exceeds the safety threshold, a power adjustment command is sent to the channel in advance. When switching temperature levels, the system gradually approaches the target temperature value at a preset heating rate; it monitors the acceleration of temperature changes in real time, and triggers an emergency cooling device when the acceleration exceeds 1°C / s²; the central control unit has a built-in acceleration monitoring circuit with a response time of 10ms, and the emergency cooling device is an air-cooled radiator. The power value is dynamically adjusted to keep the real-time temperature value stable within a preset temperature threshold range. The dynamic adjustment of the power value is achieved by using a dual-channel PID controller built into the central control unit, combined with a temperature-power mapping table pre-stored in the memory, to calculate the power adjustment amount and cyclically feedback it. When the real-time temperature value of any channel exceeds the preset temperature threshold by a set amount, the power output of that channel is immediately cut off and an alarm signal is triggered; after the alarm signal is triggered, the active electrode cooling device is started and a cooling countdown progress bar is dynamically displayed on the screen. When both channels need to increase power simultaneously, the power quota is allocated according to the temperature deviation value of each channel; if the total power demand exceeds the upper limit, the output power is gradually increased according to the time step. Before acquiring the real-time temperature value, the electromagnetic shielding component inside the thermocoagulation needle is activated, and the acquired temperature signal is subjected to a fourth-order low-pass filter. The cutoff frequency of the fourth-order low-pass filter is 10Hz to eliminate high-frequency interference.
2. A bipolar temperature control device for radiofrequency surgery, used to implement the method as described in claim 1, characterized in that, include: The temperature acquisition module is used to acquire the real-time temperature values of the first and second thermal condensation needle channels. The central control unit, connected to the temperature acquisition module, is used to compare the real-time temperature value with a preset temperature threshold; and to generate power adjustment commands, specifically, When the real-time temperature value is lower than the preset temperature threshold, increase the output power of the corresponding channel; When the real-time temperature value is higher than the preset temperature threshold, reduce the output power of the corresponding channel; The power output module is connected to the central control unit and is used to output power to the corresponding thermal condensation needle channel according to the power adjustment command.