Therapeutic apparatus and temperature control method thereof

Abstract

The application discloses a therapeutic instrument and a temperature control method thereof, and relates to the technical field of control. In the temperature control method of the therapeutic instrument, the operating parameters of the therapeutic instrument are acquired first, wherein the operating parameters include one or more of gears, working modes, and connected therapeutic head types; the temperature of the heating area is acquired, and the temperature change rate within a preset time length is calculated; then, the heat load demand value is determined based on the operating parameters and the temperature change rate; finally, the corresponding speed control instruction is output to the driving circuit according to the heat load demand value, so that the fan is driven to rotate at the speed matched with the speed control instruction. The application aims to improve the temperature overshoot problem caused by the heat conduction delay in the traditional temperature control mode, and improve the temperature control precision and user experience of the therapeutic instrument.

Description

Technical Field

[0001] This invention relates to the field of control technology, and in particular to a therapeutic device and its temperature control method. Background Technology

[0002] In the fields of medical aesthetics and home physiotherapy equipment, therapeutic devices are becoming increasingly powerful. Their core components (such as high-power LED (Light Emitting Diode) lamps, radio frequency generator modules, and semiconductor lasers) generate heat during operation. Currently, active air cooling is one of the commonly used heat dissipation methods, using fans to drive airflow and remove heat. However, traditional fan control strategies are usually based on real-time temperature feedback. The control device only starts the fan or increases its speed when the temperature reaches a preset temperature threshold. This passive response control method has a significant lag in dealing with rapidly changing dynamic heat loads. Heat can easily accumulate inside the therapeutic device, potentially triggering overheat protection mechanisms that cause the device to shut down, accelerating component aging, and even causing safety hazards such as burns. Summary of the Invention

[0003] The main objective of this invention is to provide a therapeutic device and its temperature control method, which improves the temperature overshoot problem caused by heat conduction delay in traditional temperature control methods, thereby enhancing the temperature control accuracy of the therapeutic device and the user experience.

[0004] To achieve the above objectives, the present invention proposes a therapeutic device and its temperature control method. The therapeutic device includes a temperature detection unit, a control device, a drive circuit, and a fan. The temperature detection unit is located in the heating area of ​​the therapeutic device and is used to detect the temperature of the heating area and output a temperature detection signal to the control device. The control device is used to output a speed control command to the drive circuit according to the temperature detection signal to drive the fan to operate. The temperature control method of the therapeutic device includes: Obtain the operating parameters of the therapeutic device, which include one or more of the following: power level, working mode, and type of connected treatment head; The temperature of the heating area is obtained, and the rate of temperature change within a preset time period is calculated; The heat load demand value is determined based on the operating parameters and the temperature change rate. The corresponding speed control command is output to the drive circuit according to the heat load demand value, so as to drive the fan to operate at a speed matched with the speed control command; The operating parameters include gear levels, and determining the heat load demand value based on the operating parameters and the temperature change rate includes: The reference power coefficient corresponding to the gear is determined according to the gear and the preset gear-reference power coefficient mapping table; The baseline power coefficient and the temperature change rate are weighted and calculated to obtain the basic heat load demand value, and the basic heat load demand value is determined as the heat load demand value. The light intensity or light frequency is arranged in ascending order as the first light intensity, the second light intensity, and the third light intensity. Under the same temperature change rate, the basic heat load demand value corresponding to the first light intensity is less than the basic heat load demand value corresponding to the second light intensity, and the basic heat load demand value corresponding to the second light intensity is less than the basic heat load demand value corresponding to the third light intensity.

[0005] In one embodiment, the reference power coefficient corresponding to the first gear is 0.3, the reference power coefficient corresponding to the second gear is 0.6, and the reference power coefficient corresponding to the third gear is 1.0.

[0006] In one embodiment, the step of weighting the reference power coefficient with the temperature change rate to obtain the basic heat load demand value includes: The basic heat load requirement value is determined based on the reference power coefficient corresponding to the gear, the preset thermal inertia weighting coefficient, the temperature change rate, and the preset heat load calculation formula. The formula for calculating the preset heat load is as follows: ; Based on the basic heat load demand value, This is the reference power coefficient corresponding to the gear position. This refers to the rated power of the therapeutic device at the specified setting. To preset the thermal inertia weighting coefficient, This represents the rate of temperature change.

[0007] This invention proposes a therapeutic device and its temperature control method. The therapeutic device includes a temperature detection unit, a control device, a drive circuit, and a fan. The temperature detection unit is located in the heating area of ​​the therapeutic device and is used to detect the temperature of the heating area and output a temperature detection signal to the control device. The control device is used to output a speed control command to the drive circuit according to the temperature detection signal to drive the fan to operate. The temperature control method of the therapeutic device includes: Obtain the operating parameters of the therapeutic device, which include one or more of the following: power level, working mode, and type of connected treatment head; The temperature of the heating area is obtained, and the rate of temperature change within a preset time period is calculated; The heat load demand value is determined based on the operating parameters and the temperature change rate. The corresponding speed control command is output to the drive circuit according to the heat load demand value, so as to drive the fan to operate at a speed matched with the speed control command; The operating parameters include operating modes, which include continuous light emission mode and pulsed light emission mode. The pulsed light emission mode has a corresponding pulse frequency. Determining the heat load demand value based on the operating parameters and the temperature change rate includes: When the working mode is continuous light output mode, the product of the temperature change rate and the preset first compensation coefficient is calculated to obtain the first heat load value, and the first heat load value is determined as the heat load demand value. When the working mode is pulse light output mode, the pulse frequency is obtained, and the second compensation coefficient is determined based on the pulse frequency; Calculate the product of the temperature change rate and the second compensation coefficient to obtain the second heat load value, and determine the second heat load value as the heat load demand value; Wherein, under the same temperature change rate, the preset first compensation coefficient is greater than the second compensation coefficient, so that the fan speed corresponding to the continuous light emission mode is greater than the fan speed corresponding to the pulse light emission mode.

[0008] In one embodiment, the pulsed light emission mode has a corresponding light emission duty cycle, and determining the second compensation coefficient based on the pulse frequency includes: Obtain the duration of a single light emission under the pulse emission mode; The emission duty cycle is calculated based on the pulse frequency and the single emission duration. The product of the preset first compensation coefficient and the light output duty cycle is determined as the second compensation coefficient; The preset first compensation coefficient is 1, and when the working mode is continuous light output mode, the light output duty cycle is 100%.

[0009] This invention proposes a therapeutic device and its temperature control method. The therapeutic device includes a temperature detection unit, a control device, a drive circuit, and a fan. The temperature detection unit is located in the heating area of ​​the therapeutic device and is used to detect the temperature of the heating area and output a temperature detection signal to the control device. The control device is used to output a speed control command to the drive circuit according to the temperature detection signal to drive the fan to operate. The temperature control method of the therapeutic device includes: Obtain the operating parameters of the therapeutic device, which include one or more of the following: power level, working mode, and type of connected treatment head; The temperature of the heating area is obtained, and the rate of temperature change within a preset time period is calculated; The heat load demand value is determined based on the operating parameters and the temperature change rate. The corresponding speed control command is output to the drive circuit according to the heat load demand value, so as to drive the fan to operate at a speed matched with the speed control command; The treatment head of the therapeutic device has an identification mark, which includes thermal resistance characteristics. The operating parameters include the type and power level of the connected treatment head. Determining the heat load requirement based on the operating parameters and the temperature change rate includes: The heat load demand value is determined based on the gear level and the temperature change rate. Obtain the identity identifier of the accessed treatment head type to obtain thermal resistance characteristic parameters, which characterize the resistance when heat is conducted from the internal components of the treatment head to the outside of the treatment head; The heat dissipation efficiency level is determined based on the aforementioned thermal resistance characteristic parameters; When the heat dissipation efficiency level is greater than or equal to a preset level threshold, the heat load demand value is kept constant. If the heat dissipation efficiency level is less than a preset level threshold, a heat dissipation compensation value is determined based on the temperature change rate, and the sum of the heat dissipation compensation value and the heat load demand value is used as the new heat load demand value, and the heat load demand value is updated.

[0010] In one embodiment, determining the heat load demand value based on the gear level and the temperature change rate includes: The reference power coefficient corresponding to the gear is determined according to the gear and the preset gear-reference power coefficient mapping table; The baseline power coefficient and the temperature change rate are weighted and calculated to obtain the basic heat load demand value, and the basic heat load demand value is determined as the heat load demand value. The light intensity or light frequency is arranged in ascending order as the first light intensity, the second light intensity, and the third light intensity. Under the same temperature change rate, the basic heat load demand value corresponding to the first light intensity is less than the basic heat load demand value corresponding to the second light intensity, and the basic heat load demand value corresponding to the second light intensity is less than the basic heat load demand value corresponding to the third light intensity.

[0011] This invention proposes a therapeutic device and its temperature control method. The therapeutic device includes a temperature detection unit, a control device, a drive circuit, and a fan. The temperature detection unit is located in the heating area of ​​the therapeutic device and is used to detect the temperature of the heating area and output a temperature detection signal to the control device. The control device is used to output a speed control command to the drive circuit according to the temperature detection signal to drive the fan to operate. The temperature control method of the therapeutic device includes: Obtain the operating parameters of the therapeutic device, which include one or more of the following: power level, working mode, and type of connected treatment head; The temperature of the heating area is obtained, and the rate of temperature change within a preset time period is calculated; The heat load demand value is determined based on the operating parameters and the temperature change rate. The corresponding speed control command is output to the drive circuit according to the heat load demand value, so as to drive the fan to operate at a speed matched with the speed control command; The operating parameters include the treatment head type and intensity level, whereby the treatment head type is determined by the wavelength of light transmission; determining the heat load requirement based on the operating parameters and the temperature change rate includes: The transmitted wavelength is determined based on the type of treatment head, and the target wavelength range to which the transmitted wavelength belongs is determined. The heat load demand value is determined based on the target band range and the gear level. The speed control command is a pulse width modulation signal, and the heat load demand value is the duty cycle of the pulse width modulation signal.

[0012] The present invention also proposes a therapeutic device, the therapeutic device comprising: A temperature detection unit is located in the heating area of ​​the therapeutic instrument. The temperature detection unit is used to detect the temperature of the heating area and output a corresponding temperature detection signal. fan; A drive circuit, electrically connected to the fan, is used to output a drive signal to drive the fan to operate; The control device is electrically connected to the temperature detection unit and the drive circuit, respectively, and the control device is used to execute the temperature control method of the therapeutic instrument described above.

[0013] In practical applications, this solution no longer relies solely on the current absolute temperature value for feedback control, but instead introduces operating parameters as feedforward signals. At the initial stage of starting the therapeutic device or switching gears / modes, the upcoming heat load can be predicted in advance based on the current operating parameters, and a speed control command can be output. This feedforward mechanism improves the response delay problem of traditional temperature control methods, which require waiting for the temperature to rise before initiating heat dissipation, thus suppressing excessive heat accumulation at the source. Furthermore, this application, combined with the rate of temperature change, can increase the fan speed to suppress the rate of temperature rise when a rapid upward trend in temperature is detected; conversely, it can appropriately reduce the speed when the temperature tends to stabilize or decrease. This feedback adjustment based on the rate of change allows the therapeutic device's heat dissipation system to sensitively respond to uncertainties such as changes in ambient temperature, airflow obstruction, or component aging, further improving temperature control effectiveness and heat dissipation performance. This enhances the user experience and ensures equipment safety. Attached Figure Description

[0014] The accompanying drawings, which are incorporated in and form part of this specification, illustrate embodiments consistent with the invention and, together with the description, serve to explain the principles of the invention.

[0015] To more clearly illustrate the technical solutions in the embodiments of the present invention or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, for those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0016] Figure 1 A flowchart illustrating an embodiment of the temperature control method for the therapeutic instrument of the present invention; Figure 2 A flowchart illustrating yet another embodiment of the temperature control method for the therapeutic instrument of the present invention; Figure 3 A flowchart illustrating another embodiment of the temperature control method for the therapeutic instrument of the present invention; Figure 4 A flowchart illustrating another embodiment of the temperature control method for the therapeutic instrument of the present invention; Figure 5 A flowchart illustrating yet another embodiment of the temperature control method for the therapeutic instrument of the present invention; Figure 6 This is a schematic flowchart illustrating another embodiment of the temperature control method for the therapeutic instrument of the present invention.

[0017] The objectives, features, and advantages of this invention will be further explained in conjunction with the embodiments and with reference to the accompanying drawings. Detailed Implementation

[0018] It should be understood that the specific embodiments described herein are merely illustrative of the technical solutions of the present invention and are not intended to limit the present invention.

[0019] To better understand the technical solution of the present invention, a detailed description will be provided below in conjunction with the accompanying drawings and specific embodiments.

[0020] In the fields of medical aesthetics and home physiotherapy equipment, therapeutic devices are becoming increasingly powerful. Their core components (such as high-power LED (Light Emitting Diode) lamps, radio frequency generator modules, and semiconductor lasers) generate heat during operation. Currently, active air cooling is one of the commonly used heat dissipation methods, using fans to drive airflow and remove heat. However, traditional fan control strategies are usually based on real-time temperature feedback. The control device only starts the fan or increases its speed when the temperature reaches a preset temperature threshold. This passive response control method has a significant lag in dealing with rapidly changing dynamic heat loads. Heat can easily accumulate inside the therapeutic device, potentially triggering overheat protection mechanisms that cause the device to shut down, accelerating component aging, and even causing safety hazards such as burns.

[0021] Therefore, refer to Figure 1 This invention proposes a temperature control method for a therapeutic device. The therapeutic device includes a temperature detection unit, a control device, a drive circuit, and a fan. The temperature detection unit is located in the heating area of ​​the therapeutic device. The temperature detection unit is used to detect the temperature of the heating area and output a temperature detection signal to the control device. The control device is used to output a speed control command to the drive circuit according to the temperature detection signal to drive the fan to operate. The temperature control method of the therapeutic device includes: Step S100: Obtain the operating parameters of the therapeutic device, including one or more of the following: gear level, working mode, and type of connected treatment head.

[0022] In this embodiment, the temperature control method of the therapeutic device of the present invention can be applied to the control device of the therapeutic device. The control device can be implemented using a main controller, such as an MCU (Microcontroller Unit), DSP (Digital Signal Processor), FPGA (Field Programmable Gate Array), PLC (Programmable Logic Controller), or SOC (System-on-Chip). The therapeutic device includes, but is not limited to, hair removal devices and skin rejuvenation devices.

[0023] Optionally, the temperature detection unit can be implemented using a temperature sensor, such as an NTC thermistor or a digital temperature sensor (e.g., DS18B20), with a temperature measurement accuracy of ±0.5°C. The fan can be a DC brushless fan, with a rated voltage matching the power supply voltage of the therapeutic device, such as 12V or 5V, and a speed range of 800 RPM to 3000 RPM. The control device can be a microcontroller unit (MCU), such as an STM32 series or ARM Cortex-M0 core chip, equipped with an analog-to-digital conversion interface to receive analog signals collected by the temperature detection unit, and to output PWM (Pulse Width Modulation) signals to the drive circuit through a PWM output interface to drive the fan.

[0024] In this embodiment, the heat-generating area includes the xenon lamp holder and the power module heat sink. The control device can read the voltage or resistance value of the temperature sensor (such as an NTC thermistor) located near the heat-generating area through the analog-to-digital conversion interface and convert it into the current actual temperature value T.

[0025] In this embodiment, optionally, acquiring the operating parameters of the therapeutic device includes acquiring the operating parameters based on user input information. For example, when a user triggers an operation signal to switch gears or change treatment heads, the updated operating parameters are acquired in real time. Optionally, acquiring the operating parameters of the therapeutic device includes acquiring the operating parameters in response to a power-on signal. For example, when the therapeutic device is powered on and performs an initialization action, the control device reads the preset initial operating parameters in the control device's memory, including the working mode and / or gear, and can also detect the type of treatment head connected. It is understood that the control device can acquire the operating parameters of the therapeutic device according to a preset period to achieve full-process temperature detection and speed adjustment during the operation of the therapeutic device. The preset period can be set by the developers and stored in advance in the internal or external memory of the control device, for example, the preset period is 50ms, 100ms, 200ms, 500ms, or 1s, etc. In this way, through a real-time or triggered parameter acquisition mechanism, it is ensured that the control device can sense changes in the heat generated by the therapeutic device in the first instance.

[0026] Step S200: Obtain the temperature of the heating area and calculate the temperature change rate within a preset time period.

[0027] In this embodiment, the control device can use an internal timer to read the temperature detection unit's value once every sampling period (e.g., every 50ms or 100ms) and calculate the temperature change rate within a preset time period. The preset time period can be set by the developers and stored in the control device's memory.

[0028] Considering that the core components of the therapeutic device (such as LED beads) may experience a rapid temperature surge within a very short time upon activation, a preset duration of too long (e.g., 10 seconds) would fail to accurately capture the instantaneous thermal shock, thus negating the purpose of advance prediction and resulting in a delayed response. Conversely, the temperature sensor may experience minute electrical signal fluctuations during data acquisition. If the preset duration is set too short (e.g., 0.01 seconds), the temperature difference between the two sampling points will be minimal, easily leading to the calculation of erroneous and drastic temperature jumps, causing frequent fluctuations in fan speed (suddenly fast and slow). Therefore, in this embodiment, the preset duration can range from 0.5 seconds to 5 seconds.

[0029] Step S300: Determine the heat load demand value based on the operating parameters and the temperature change rate.

[0030] In this embodiment, researchers can conduct numerous thermal experiments (e.g., testing the required fan speed to maintain the temperature within a safe range at different speeds and rates of temperature change under specific ambient temperatures) to summarize data patterns and establish a multidimensional mapping table, which can then be stored in the control device's memory in advance. Optionally, the index of the multidimensional mapping table is the operating parameters (such as speed I / II / III, operating mode) and the temperature change rate range, while the output value of the table is the corresponding heat load requirement value.

[0031] In this embodiment, the speed control command can be a PWM signal, and the heat load demand value can be configured as the duty cycle of the PWM signal. For example, under the condition of operating at the third gear (III) and a temperature change rate greater than 0.5℃ / s, the corresponding target duty cycle is set to 90%. This means that the control device will output a PWM signal with a 90% duty cycle to provide sufficient heat dissipation power to suppress the current temperature rise trend. Thus, the control device uses the real-time acquired operating parameters and the calculated temperature change rate as indexes to perform a lookup in a multi-dimensional mapping table, directly obtaining the corresponding target duty cycle. Through this lookup method, the control device can output the speed control command with a lower computational delay, further improving the response speed of the therapeutic device.

[0032] At the moment the therapeutic device is first turned on or the user switches modes, the temperature may not have had time to rise. By analyzing operating parameters, the control device can anticipate whether the temperature in the heating area will rise, and thus issue a speed control command in advance, intervening in heat dissipation before the temperature spikes. Compared to traditional methods, less heat accumulates and the temperature peak is lower within the same timeframe. If the actual heat dissipation environment of the therapeutic device deteriorates (e.g., the air inlet is blocked), or the actual heat generation is high, the temperature will rise rapidly. Therefore, by using the temperature change rate, the control device can sense this abnormal temperature rise trend and, before the temperature exceeds the preset temperature threshold set by traditional methods, increase the fan speed to suppress the temperature rise and reduce heat dissipation.

[0033] Step S400: Output the corresponding speed control command to the drive circuit according to the heat load demand value, so as to drive the fan to operate at a speed matching the speed control command.

[0034] In this embodiment, the control device can convert a determined heat load demand value (usually a value between 0 and 100 or the duty cycle of a PWM signal) into a drive signal with sufficient driving capability to control the drive circuit. For example, a PWM signal is a square wave signal with a fixed period but a variable high-level duration. For example, if the heat load demand value is 90%, the control device will output a square wave signal (i.e., a PWM signal) with a high level percentage of 90% and a low level percentage of 10%. In this embodiment, the drive circuit can be implemented using MOSFETs (Metal-Oxide-Semiconductor Field-Effect Transistors), H-bridge driver chips, dedicated fan driver chips, etc. The control device outputs the PWM signal to the control terminal of the drive circuit. The drive circuit chops and modulates the power supply provided to the fan according to the on / off frequency and duty cycle of the PWM signal. The fan receives the drive current modulated by the drive circuit and operates at a speed corresponding to the heat load demand value. For example, when the duty cycle corresponding to the heat load demand value increases, the average operating voltage of the fan increases, and the speed increases accordingly, thereby outputting a larger air volume to remove heat from the heat-generating area; conversely, when the duty cycle decreases, the fan speed decreases to reduce equipment operating noise and energy consumption.

[0035] refer to Figure 2 The operating parameters include gear settings, and determining the heat load demand value based on the operating parameters and the temperature change rate includes: Step S310: Determine the reference power coefficient corresponding to the gear position according to the gear position and the preset gear position-reference power coefficient mapping table; Step S320: The reference power coefficient and the temperature change rate are weighted and calculated to obtain the basic heat load demand value, and the basic heat load demand value is determined as the heat load demand value; The light intensity or light frequency is arranged in ascending order as the first light intensity, the second light intensity, and the third light intensity. Under the same temperature change rate, the basic heat load demand value corresponding to the first light intensity is less than the basic heat load demand value corresponding to the second light intensity, and the basic heat load demand value corresponding to the second light intensity is less than the basic heat load demand value corresponding to the third light intensity.

[0036] In this embodiment, for treatment devices such as hair removal devices or phototherapy devices, the power levels typically correspond to light intensity (energy density J / cm²) or light emission frequency (repeated bursts per second). Since the heating power of different power levels is known (measured during the research and development phase), when a user selects a power level, the control device does not need to wait for the temperature to rise to know "the minimum heat dissipation capacity required to maintain normal operation at this power level." This "minimum required heat dissipation capacity" is the baseline power coefficient. This ensures that a base rotation speed matching the heat output of the specified power level is obtained immediately upon device startup, reducing the risk of heat accumulation in the initial stage.

[0037] Optionally, the developers can store a gear-reference power coefficient mapping table in the memory of the control device in advance. For example, the reference power coefficient corresponding to the first gear is 0.3, the reference power coefficient corresponding to the second gear is 0.6, and the reference power coefficient corresponding to the third gear is 1.0. When the current gear is detected to be the third gear, the control device looks up the table to determine that the reference power coefficient is 1.0.

[0038] It should be noted that ambient temperature and heat dissipation conditions may vary. Therefore, this application combines the "static speed limit coefficient" with the "dynamic temperature change rate" (i.e., weighted calculation). If the temperature change rate is large (temperature spikes), the weighted calculation will further increase the final heat load demand value based on the basic heat load demand value, causing the fan to spin faster. Conversely, if the temperature change rate is negative (temperature drops), the weighted calculation will further reduce the final heat load demand value based on the basic heat load demand value, thereby reducing fan noise and achieving noise reduction.

[0039] Under the same rate of temperature change (i.e., the same environmental disturbance or temperature rise trend), the first setting has weak light intensity (low energy) or slow light frequency (slow flashing). In the process of the light-emitting component converting electrical energy into light energy per unit time, the waste heat (Joule heat) generated is relatively small. At this time, the heat accumulation rate inside the therapeutic device is very slow. Because of the low heat generation, only a small amount of airflow from the fan at a low speed (i.e., a smaller basic heat load requirement) is needed to remove the generated heat and ensure that the temperature does not exceed the standard. Conversely, the third setting has strong light intensity (high energy) or fast light frequency (continuous firing). The current is extremely high per unit time, the light-emitting component works intensely, and a large amount of waste heat is generated. At this time, the internal heat accumulation rate is extremely fast, and the temperature will rise rapidly. Because of the huge heat generation, if the fan maintains a low speed, the heat cannot be removed in time, and the temperature will instantly exceed the safety threshold, causing the device to shut down. Therefore, the fan must operate at a higher speed (i.e., a larger basic heat load requirement) to provide greater airflow and air pressure to achieve thermal balance. In this way, not only is heat dissipation safety guaranteed at high power levels, but noise reduction experience is also taken into account at low power levels.

[0040] In practical applications, this solution no longer relies solely on the current absolute temperature value for feedback control, but instead introduces operating parameters as feedforward signals. At the initial stage of starting the therapeutic device or switching gears / modes, the upcoming heat load can be predicted in advance based on the current operating parameters, and a speed control command can be output. This feedforward mechanism improves the response delay problem of traditional temperature control methods, which require waiting for the temperature to rise before initiating heat dissipation, thus suppressing excessive heat accumulation at the source. Furthermore, this application, combined with the rate of temperature change, can increase the fan speed to suppress the rate of temperature rise when a rapid upward trend in temperature is detected; conversely, it can appropriately reduce the speed when the temperature tends to stabilize or decrease. This feedback adjustment based on the rate of change allows the therapeutic device's heat dissipation system to sensitively respond to uncertainties such as changes in ambient temperature, airflow obstruction, or component aging, further improving temperature control effectiveness and heat dissipation performance. This enhances the user experience and ensures equipment safety.

[0041] Optionally, in one embodiment, the step of weighting the reference power coefficient with the temperature change rate to obtain the basic heat load demand value includes: The basic heat load requirement value is determined based on the reference power coefficient corresponding to the gear, the preset thermal inertia weighting coefficient, the temperature change rate, and the preset heat load calculation formula. The formula for calculating the preset heat load is as follows: ; Based on the basic heat load demand value, This is the reference power coefficient corresponding to the gear position. This refers to the rated power of the therapeutic device at the specified setting. To preset the thermal inertia weighting coefficient, This represents the rate of temperature change.

[0042] In this embodiment, This is a feedforward prediction term, representing the theoretical basic heat dissipation requirements. It determines the basic response speed when the device starts up. It determines the equipment's ability to suppress sudden temperature rises. The larger the value, the stronger the suppression of temperature spikes. Researchers can store the rated power corresponding to each power level in the control device's memory. Once the user selects a high power level (e.g., the third level), the control device can determine the rated power for that level. Even if the device has just been turned on and the temperature hasn't had time to rise (the rate of temperature change is close to 0), the control device can predict whether a large amount of heat will be generated based solely on the power level and its rated power, thus providing a basic fan speed in advance to prevent heat buildup. For example, when the device is in the first power level, the corresponding rated output power Pmax is 20W; when it's in the second power level, Pmax is 35W; and when it's in the third power level, Pmax is 50W (i.e., the maximum rated power of the entire device). As the power level increases, the value of Pmax increases accordingly, thus enabling the feedforward control term... The increased value ensures that the fan outputs a higher base speed in advance to match the high heat generation at higher settings. This breaks the lag of traditional temperature control schemes that only activate the fan after the temperature has risen. Regardless of the current absolute temperature, as soon as the higher setting is activated, a larger base fan speed is immediately provided, opening the heat dissipation channels in advance to prepare for the heat.

[0043] In this embodiment, This represents emergency compensation for sudden heat buildup. The rate of temperature change reflects the extent of the temperature spike. Considering unforeseen circumstances in real-world environments such as blocked air intakes or sudden increases in ambient temperature, if the temperature is rising rapidly (a large rate of temperature change), it indicates insufficient basic heat dissipation, and heat is accumulating internally. In this case, the differential term... It will immediately intervene, increasing the fan power to suppress temperature rise. The preset thermal inertia weighting coefficient is a coefficient that converts the rate of temperature change into the additional fan duty cycle, which can be set in advance by the R&D personnel and stored in the memory. In this embodiment, the preset thermal inertia weighting coefficient is 20 (unit: %·s / ℃, representing that for every 1℃ increase in temperature per second, the fan duty cycle increases by an additional 20%).

[0044] Based on the above embodiments, the user turns on the power of the therapeutic device and selects the third gear via the device panel or buttons. At this initial startup phase, the temperature change rate is close to 0. The control device, referring to a table, determines the base power coefficient to be 1.0 and the rated power to be 50W. Therefore, the basic heat load requirement value is... Although the temperature hasn't changed significantly yet, the control device can directly output a PWM signal with a 50% duty cycle to suppress heat in advance. This is because the heat may not dissipate after the treatment device has been running for a while, or the air inlet may be blocked by a towel. Assuming a preset duration of 3 seconds, the temperature detection unit detects a temperature change rate of 0.5℃ / s within those 3 seconds. Basic heat load requirement value. Due to the detection of heat accumulation ( (If the value is positive), the derivative term contributes an additional 10% duty cycle, increasing the basic heat load demand from 50% to 60%. The control device outputs a PWM signal with a 60% duty cycle to increase the fan speed.

[0045] By using the product of the reference power coefficient and the rated power as a feedforward control term, the control device can predict the theoretical heat generation power in advance based on the user-set power level. Even when the device is first started and the temperature has not yet risen, the cooling system can immediately provide basic heat dissipation capacity matching the current power, improving the temperature overshoot problem caused by heat conduction delay in traditional temperature control methods. In addition, by using the product of the preset thermal inertia weighting coefficient and the rate of temperature change as a dynamic feedback correction term, the rate of heat accumulation inside the therapeutic device can be captured in real time. When a sharp rise in temperature is detected (such as a deterioration in the heat dissipation environment), the heat load demand can be rapidly increased to provide emergency compensation to the cooling system. In this way, the thermal safety of the therapeutic device under high power output is ensured, while noise and energy waste under low load conditions are reduced, improving the temperature control accuracy of the therapeutic device and the user experience.

[0046] This application proposes a temperature control method for a therapeutic device. The therapeutic device includes a temperature detection unit, a control device, a drive circuit, and a fan. The temperature detection unit is located in the heating area of ​​the therapeutic device and is used to detect the temperature of the heating area and output a temperature detection signal to the control device. The control device is used to output a speed control command to the drive circuit according to the temperature detection signal to drive the fan to operate. The temperature control method of the therapeutic device includes: Step S100: Obtain the operating parameters of the therapeutic device, wherein the operating parameters include one or more of the following: gear level, working mode, and type of connected treatment head; Step S200: Obtain the temperature of the heating area and calculate the temperature change rate within a preset time period; Step S300: Determine the heat load demand value based on the operating parameters and the temperature change rate; Step S400: Output the corresponding speed control command to the drive circuit according to the heat load demand value, so as to drive the fan to operate at a speed matching the speed control command.

[0047] In this embodiment, the discussion of steps S100 to S400 is provided in the above embodiment and will not be repeated here.

[0048] refer to Figure 3The operating parameters include operating modes, which include continuous light emission mode and pulsed light emission mode. The pulsed light emission mode has a corresponding pulse frequency. Determining the heat load demand value based on the operating parameters and the temperature change rate includes: Step S330: When the working mode is continuous light output mode, calculate the product of the temperature change rate and the preset first compensation coefficient to obtain the first heat load value, and determine the first heat load value as the heat load demand value. Step S340: When the working mode is pulse light output mode, obtain the pulse frequency and determine the second compensation coefficient based on the pulse frequency; Step S350: Calculate the product of the temperature change rate and the second compensation coefficient to obtain the second heat load value, and determine the second heat load value as the heat load demand value; Wherein, under the same temperature change rate, the preset first compensation coefficient is greater than the second compensation coefficient, so that the fan speed corresponding to the continuous light emission mode is greater than the fan speed corresponding to the pulse light emission mode.

[0049] Understandably, in continuous light output mode, the therapeutic device outputs light energy stably and continuously. The heat source operates continuously, generating heat that easily accumulates inside the device, thus requiring high levels of continuity and stability in heat dissipation. In pulsed light output mode, the device releases high energy through an alternating "on-off-on" cycle with extremely short time intervals. Due to the intermittent off-off periods, the device has a certain natural cooling time, and under the same average power, the urgency of heat accumulation is generally lower in pulsed light output mode.

[0050] In this embodiment, the operating mode is typically selected manually by the user according to treatment needs. Common interaction methods include physical button switching and touchscreen / menu selection. For example, the treatment device panel may have a dedicated mode button. Each short press cycles between "continuous mode" and "pulse mode," with the current operating mode indicated by an indicator light (e.g., continuously lit / flashing) or on-screen text. Alternatively, on treatment devices with an LCD screen, the user can directly click the "continuous" or "pulse" icon on the UI interface. In this way, the control device can monitor the input signals from the buttons or touchscreen in real time to determine the operating mode of the treatment device.

[0051] Because the heat generated by continuous light emission is inexhaustible, once the temperature begins to rise (i.e., the rate of temperature change is greater than 0), it often means that heat is rapidly accumulating without any natural cooling intervals. Therefore, a large first compensation coefficient is needed to quickly bring the fan to a high speed, providing strong and continuous heat dissipation to prevent the device from overheating due to continuous heat accumulation. In this embodiment, when it is determined that the therapeutic device is currently in continuous light emission mode, a preset, large first compensation coefficient is directly invoked, multiplied by the real-time collected rate of temperature change, to obtain the first heat load value, which is then used as the heat load demand value. The preset first compensation coefficient can be pre-set by the researchers and stored in the memory of the control device.

[0052] In this embodiment, it is assumed that the preset first compensation coefficient is 30 (the unit can be %·s / ℃, that is, for every 1℃ / s change in temperature, the duty cycle increases by 30%). At a certain moment, the temperature change rate is 0.8℃ / s (this means that the internal temperature of the device is rising rapidly at a rate of 0.8 degrees Celsius per second). The control device multiplies the preset first compensation coefficient by the real-time collected temperature change rate, and calculates the heat load demand value as 24. This value can directly correspond to the fan speed control command. For example, if the heat load demand value is expressed as a percentage of the PWM signal's duty cycle, the control device will output a PWM signal with a duty cycle of 24% (or add it as an increment to the base speed). It should be noted that the larger the preset first compensation coefficient, the better the heat dissipation effect.

[0053] In this embodiment, the pulse frequency refers to the number of times the "light emission-extinguishing" cycle is completed per second in pulse mode, typically measured in Hertz (Hz). A higher frequency indicates more frequent light emission per unit time, and generally, greater heat generation. When the therapeutic device is determined to be in pulse light emission mode, the current pulse frequency (i.e., the number of light emission cycles per second) is further obtained. The control device can pre-store a "frequency-second compensation coefficient mapping table," allowing it to find and determine the corresponding second compensation coefficient based on the current pulse frequency. Thus, the heating characteristics of the pulse mode are strongly correlated with the frequency (higher frequency, shorter intervals, and heating closer to continuous mode). By obtaining the pulse frequency to determine the second compensation coefficient, the actual heat dissipation pressure under the current pulse state can be accurately assessed, preparing for precise temperature control in the next step.

[0054] Optionally, the pulse frequency range is [1Hz, 3Hz), which is a low-frequency pulse, and the second compensation coefficient is 10. The pulse frequency range is [3Hz, 6Hz), which is a medium-frequency pulse, and the second compensation coefficient is 18. The pulse frequency range is a high-frequency pulse range greater than or equal to 6Hz, and the second compensation coefficient is 25. The above values ​​are only examples. Researchers can adjust them according to the thermal inertia of the actual equipment, as long as they increase with frequency and are less than the first compensation coefficient.

[0055] In this embodiment, the control device can multiply the second compensation coefficient by the real-time temperature change rate to obtain the second heat load value.

[0056] Because the pulsed light emission mode inherently features intermittent cooling, its corresponding second compensation coefficient is set to be less than the first compensation coefficient of the continuous light emission mode. Under the same temperature rise trend, the fan speed in pulsed light emission mode will be lower. This utilizes the natural heat dissipation during the pulse intervals while avoiding fan overreaction (running wildly), thereby reducing equipment operating noise and improving the user experience while ensuring safety.

[0057] When the therapeutic device is in pulsed light emission mode with a pulse frequency of 2 Hz, the control device determines the current second compensation coefficient to be 10. If the temperature change rate is 0.8℃ / s, the heat load requirement is 8. It's understandable that in continuous light emission mode, the heat load requirement would be 24. Clearly, the fan speed requirement under low-frequency pulses is much lower than in continuous light emission mode, demonstrating quiet operation and energy saving. When the user increases the pulse frequency to 8 Hz, the risk of heat accumulation increases due to more frequent light emission. The control device, referring to a table, finds that this falls within the high-frequency pulse range, thus determining the current second compensation coefficient to be 25. Again, with a temperature change rate of 0.8℃ / s, the calculated second heat load value is 20. Therefore, as the frequency increases, the second compensation coefficient automatically increases from 10 to 25, the heat load requirement automatically increases from 8 to 20, and the fan speed automatically increases, thus meeting the heat dissipation requirements under high-frequency pulses.

[0058] To address the continuous heat buildup characteristic of continuous light emission mode, a larger first compensation coefficient is employed to further determine the heat load requirement. This allows the therapeutic device's cooling system to respond more sensitively to temperature rise trends, providing continuous and powerful heat dissipation capabilities. This effectively reduces the risk of overheating during prolonged continuous operation, ensuring thermal safety. For the intermittent cooling characteristic of pulsed light emission mode, a mechanism based on dynamically matching a second compensation coefficient to the pulse frequency is introduced. Because the second compensation coefficient is smaller than the first and adaptively adjusts with frequency changes, the control device can reduce fan speed while ensuring adequate heat dissipation. This not only reduces excessive heat dissipation and energy waste in pulsed mode but also lowers equipment operating noise, optimizing the user's treatment experience.

[0059] Alternatively, in one embodiment, reference is made to... Figure 4 The pulsed light emission mode has a corresponding light emission duty cycle, and determining the second compensation coefficient based on the pulse frequency includes: Step S341: Obtain the duration of a single light emission in the pulse light emission mode; Step S342: Calculate the emission duty cycle based on the pulse frequency and the single emission duration; Step S343: Determine the product of the preset first compensation coefficient and the output duty cycle as the second compensation coefficient; The preset first compensation coefficient is 1, and when the working mode is continuous light output mode, the light output duty cycle is 100%.

[0060] In this embodiment, the duration of a single light emission refers to the length of time the therapeutic device continuously emits light in pulsed light emission mode. For example, if the device flashes light once and lasts for 0.1 seconds, then the duration of a single light emission is 0.1 seconds. The light emission duty cycle refers to the proportion of a single light emission duration within a complete "on-off" cycle. It reflects the actual working time percentage per unit time. A higher duty cycle means a longer light emission time and a greater average heat generation.

[0061] In this embodiment, when generating a PWM signal, the control device can set a high-level duration (i.e., light emission time) through its internal timer module. The control device can then directly read this duration from a register (e.g., 200ms), or obtain the duration of a single light emission by recording the timestamp difference of the high-level I / O port. In this way, the control device knows the exact duration of each light emission, enabling it to assess the heat generated by a single light emission.

[0062] In this embodiment, the pulse frequency is f, and the pulse period is T. T equals 1 / f. Dividing the single emission duration (t) by the period (T) yields the emission duty cycle, i.e., emission duty cycle D = t / T = t × f. For example, with a frequency of 5Hz (period of 0.2 seconds) and a single emission duration of 0.1 seconds, the emission duty cycle is 0.5 (i.e., 50%). Thus, the emission duty cycle can be used to quantify the actual heat generation ratio.

[0063] In this embodiment, the first compensation coefficient in continuous light emission mode is used as a benchmark (i.e., the heat dissipation capacity at 100% duty cycle), and the heat dissipation coefficient in pulse mode is calculated proportionally by multiplying it by the light emission duty cycle. Assume the first compensation coefficient is preset to 1 (representing the full-speed heat dissipation benchmark at 100% duty cycle in continuous light emission). If the light emission duty cycle is 0.5, then the second compensation coefficient is 0.5. This means that, under the same temperature change rate, the fan compensation required in pulse light emission mode is only half that of continuous light emission mode. Based on the above embodiment, if the temperature change rate is 0.8℃ / s, the heat load requirement is 40% of the product of the temperature change rate and the second compensation coefficient. The control device outputs a PWM signal with a 40% duty cycle to the drive circuit to drive the fan.

[0064] The second compensation coefficient is determined by multiplying the preset first compensation coefficient by the real-time output duty cycle. This utilizes the physical characteristic that the duty cycle reflects average power, allowing the heat dissipation response in pulsed output mode to follow the actual heat generation ratio. This reduces excessive heat dissipation and noise under low-frequency pulses while ensuring heat dissipation safety under high-frequency pulses.

[0065] This application proposes a temperature control method for a therapeutic device. The therapeutic device includes a temperature detection unit, a control device, a drive circuit, and a fan. The temperature detection unit is located in the heating area of ​​the therapeutic device and is used to detect the temperature of the heating area and output a temperature detection signal to the control device. The control device is used to output a speed control command to the drive circuit according to the temperature detection signal to drive the fan to operate. The temperature control method of the therapeutic device includes: Step S100: Obtain the operating parameters of the therapeutic device, wherein the operating parameters include one or more of the following: gear level, working mode, and type of connected treatment head; Step S200: Obtain the temperature of the heating area and calculate the temperature change rate within a preset time period; Step S300: Determine the heat load demand value based on the operating parameters and the temperature change rate; Step S400: Output the corresponding speed control command to the drive circuit according to the heat load demand value, so as to drive the fan to operate at a speed matching the speed control command.

[0066] In this embodiment, the discussion of steps S100 to S400 is provided in the above embodiment and will not be repeated here.

[0067] refer to Figure 5 The treatment head of the therapeutic device has an identification mark, which includes thermal resistance characteristic parameters. The operating parameters include the type and power level of the connected treatment head. Determining the heat load requirement based on the operating parameters and the temperature change rate includes: Step S10: Determine the heat load demand value based on the gear level and the temperature change rate.

[0068] Optionally, step S10 includes: Step S310: Determine the reference power coefficient corresponding to the gear position according to the gear position and the preset gear position-reference power coefficient mapping table; Step S330: The reference power coefficient and the temperature change rate are weighted and calculated to obtain the basic heat load demand value, and the basic heat load demand value is determined as the heat load demand value; The light intensity or light frequency is arranged in ascending order as the first light intensity, the second light intensity, and the third light intensity. Under the same temperature change rate, the basic heat load demand value corresponding to the first light intensity is less than the basic heat load demand value corresponding to the second light intensity, and the basic heat load demand value corresponding to the second light intensity is less than the basic heat load demand value corresponding to the third light intensity.

[0069] Based on the above embodiments, the control device can determine the reference power coefficient by consulting a preset gear-reference power coefficient mapping table. For example, the information in the preset gear-reference power coefficient mapping table includes, but is not limited to, a reference power coefficient of 0.3 for the first gear, 0.6 for the second gear, and 1.0 for the third gear. Simultaneously, the heat load demand value can be determined according to a preset heat load calculation formula.

[0070] Step S20: Obtain the identity identifier of the accessed treatment head type to obtain thermal resistance characteristic parameters, which characterize the resistance when heat is conducted from the internal components of the treatment head to the outside of the treatment head.

[0071] In this embodiment, the identification tag is an electronic ID card for the treatment head. Researchers can implant a storage chip, RFID tag, or specific resistor-encoded circuit inside the treatment head handle. When the treatment head is inserted into the main unit of the treatment device, the main unit's control device automatically reads the identification tag. The thermal resistance characteristic parameter is core data stored in the electronic ID card, characterizing the resistance to heat conduction from the internal heat source (such as a laser diode) to the external surface of the treatment head. High thermal resistance indicates that the internal thermally conductive material of the treatment head is generally poor (or the structure is thermally insulated), and heat easily accumulates inside, making it difficult to transfer to the outer shell. Low thermal resistance indicates that the internal thermally conductive material of the treatment head is of good quality (such as high thermal conductivity ceramics or a copper substrate), allowing heat to be quickly conducted away from the inside.

[0072] Optionally, thermal resistance characteristics include thermal resistance, which is a physical quantity used to measure an object's ability to impede heat conduction, measured in Kelvin per watt (K / W).

[0073] In this embodiment, when the treatment head is inserted into the host interface, the control device can read the data stored in the chip inside the treatment head through the communication interface (such as I2C, single bus, etc.) and parse the pre-stored thermal resistance characteristic parameters from the data (the thermal resistance characteristic parameter may be a specific value, such as 5.0 K / W, or a code representing the thermal conductivity level).

[0074] Step S30: Determine the heat dissipation efficiency level based on the thermal resistance characteristic parameters.

[0075] In this embodiment, the control device's memory can pre-store a thermal resistance-heat dissipation efficiency level mapping table. For example: thermal resistance < 5.0 K / W is classified as Level 3 (high-efficiency heat dissipation treatment head); 5.0 K / W ≤ thermal resistance ≤ 10.0 K / W is classified as Level 2 (ordinary heat dissipation treatment head); thermal resistance > 10.0 K / W is classified as Level 1 (inefficient heat dissipation treatment head). The higher the thermal resistance, the more difficult it is to dissipate heat, and the lower the heat dissipation efficiency level. The control device can classify the current treatment head into the corresponding heat dissipation efficiency level based on the value of the thermal resistance characteristic parameter.

[0076] Step S40: If the heat dissipation efficiency level is greater than or equal to the preset level threshold, control the heat load demand value to remain unchanged; Step S50: If the heat dissipation efficiency level is less than the preset level threshold, determine the heat dissipation compensation value based on the temperature change rate, and use the sum of the heat dissipation compensation value and the heat load demand value as the new heat load demand value, and update the heat load demand value.

[0077] In this embodiment, if the heat dissipation efficiency level of the treatment head is very high (greater than or equal to a preset threshold), it indicates that the treatment head itself has strong thermal conductivity, and the heat can be smoothly conducted out and blown away by the fan. For example, if the preset threshold is 2, assuming the control device obtains a thermal resistance of 6 K / W based on the identification, and by consulting the thermal resistance-heat dissipation efficiency level mapping table, the level is 2, which is equal to the preset threshold, then the basic heat load requirement value calculated in step S10 is directly output. At this time, the fan runs at the original speed, which is both safe and does not generate excessive noise.

[0078] Considering that if the heat dissipation efficiency level of the treatment head is low (less than the preset threshold, such as level 1), it means that heat is easily trapped inside the treatment head and cannot be conducted out. In this case, if only the basic heat load requirement value is relied upon, the internal core temperature may exceed the standard. Therefore, it is necessary to increase the heat dissipation capacity. In this embodiment, an additional compensation amount (heat dissipation compensation value) is calculated based on the current temperature change rate. For example, a compensation coefficient K_comp is set for inefficient heat dissipation treatment heads, and the heat dissipation compensation value is equal to the product of K_comp and the temperature change rate. Then, the heat dissipation compensation value is superimposed on the basic heat load requirement value calculated in step S10 to obtain a new heat load requirement value. The control device can output a corresponding PWM signal to the drive circuit according to the new heat load requirement value to force the fan to increase its speed to compensate for the insufficient heat conduction capacity of the treatment head itself.

[0079] Understandably, the compensation coefficient reflects how much additional fan speed (heat dissipation) is needed to offset the temperature rise rate of 1℃ / s when the treatment head's own thermal conductivity is insufficient (high thermal resistance). The compensation coefficient can be pre-set by researchers and stored in the control device's memory. Researchers can build a realistic test environment in the laboratory, for example, preparing a "standard high-efficiency treatment head" (low thermal resistance) and a "low-efficiency treatment head under test" (high thermal resistance, i.e., the object requiring compensation). Under the same ambient temperature and the same speed setting, both treatment heads are run simultaneously, and an identical temperature rise rate is artificially created (e.g., controlling the temperature rise at a rate of 0.5℃ / s). For the high-efficiency treatment head, it is assumed that a fan speed of 30% (basic heat load) is sufficient to stabilize the temperature. For the low-efficiency treatment head, since heat cannot be conducted out, 30% speed is certainly insufficient. Researchers will gradually increase the fan speed until they find that when the speed reaches 40%, the internal core temperature of the low-efficiency treatment head can be suppressed and no longer rise. At this point, the additional heat dissipation requirement (heat dissipation compensation value) is 10%. Based on the current temperature change rate of 0.5℃ / s, the heat dissipation compensation value is determined to be 20.

[0080] Assuming a user connects a treatment head with good thermal conductivity, the control device reads its identifier and obtains a thermal resistance of 6 K / W. Looking up the mapping table, 6 K / W falls within the range of 5.0 K / W ≤ thermal resistance ≤ 10.0 K / W. Therefore, its heat dissipation efficiency level is determined to be 2, which equals the preset threshold of 2 (meeting the condition of "greater than or equal to the preset threshold"). The treatment head is considered to have adequate thermal conductivity and requires no further intervention. The basic heat load requirement (e.g., 30) becomes the final heat load requirement. Assuming a user connects an old or poor-quality treatment head, the control device reads its identifier and obtains a thermal resistance of 12 K / W. Looking up the mapping table, 12 K / W falls within the range of thermal resistance > 10.0 K / W. Therefore, its heat dissipation efficiency level is determined to be 1, which is less than the preset threshold of 2 (meeting the condition of "less than the preset threshold"). Therefore, it is identified that this treatment head is prone to heat accumulation and requires forced enhanced heat dissipation. If the temperature change rate is 0.6℃ / s, the calculated heat dissipation compensation value is 12, and the final heat load requirement is 42. Thus, the control unit increases the duty cycle of the PWM signal from the base of 30% to 42%. The fan speed is forcibly increased to compensate for the poor thermal conductivity (high thermal resistance) of the treatment head itself and to prevent the internal core from overheating.

[0081] This application can identify the heat dissipation performance of the treatment head and dynamically add heat dissipation compensation values ​​based on the real-time temperature change rate. This effectively compensates for the inherent thermal conductivity limitations of the hardware, prevents heat accumulation in the internal core, and improves the operational safety of the treatment device when compatible with treatment heads of different specifications. Furthermore, for high-efficiency heat dissipation treatment heads with low thermal resistance and excellent thermal conductivity, it maintains the basic heat load requirements and avoids excessive heat dissipation. In this way, it not only fully utilizes the physical thermal conductivity of the hardware but also significantly reduces fan noise and overall power consumption, optimizing the user experience.

[0082] This application proposes a temperature control method for a therapeutic device. The therapeutic device includes a temperature detection unit, a control device, a drive circuit, and a fan. The temperature detection unit is located in the heating area of ​​the therapeutic device and is used to detect the temperature of the heating area and output a temperature detection signal to the control device. The control device is used to output a speed control command to the drive circuit according to the temperature detection signal to drive the fan to operate. The temperature control method of the therapeutic device includes: Step S100: Obtain the operating parameters of the therapeutic device, wherein the operating parameters include one or more of the following: gear level, working mode, and type of connected treatment head; Step S200: Obtain the temperature of the heating area and calculate the temperature change rate within a preset time period; Step S300: Determine the heat load demand value based on the operating parameters and the temperature change rate; Step S400: Output the corresponding speed control command to the drive circuit according to the heat load demand value, so as to drive the fan to operate at a speed matching the speed control command.

[0083] In this embodiment, the discussion of steps S100 to S400 is provided in the above embodiment and will not be repeated here.

[0084] refer to Figure 6 The operating parameters include the treatment head type and intensity level, wherein the treatment head type is determined by the wavelength of light transmission; determining the heat load requirement based on the operating parameters and the temperature change rate includes: Step S60: Determine the light transmission wavelength based on the treatment head type, and determine the target wavelength range to which the light transmission wavelength belongs; Step S70: Determine the heat load demand value based on the target band range and the gear level; The speed control command is a pulse width modulation signal, and the heat load demand value is the duty cycle of the pulse width modulation signal.

[0085] In this embodiment, the transmitted wavelength is a physical property determined by the type of light source of the therapeutic device. Different therapeutic devices (such as red light, infrared light, and blue light) emit different wavelengths of light. For example, the transmitted wavelength range of a red light therapeutic device is typically 600nm-700nm, while that of an infrared light therapeutic device is 800nm-1000nm. The target wavelength range is a wavelength classification label that is preset and stored in the control device by the researchers. Continuous wavelength values ​​are divided into several large ranges (e.g., visible light band, near-infrared band, mid-infrared band, etc.).

[0086] Optionally, the treatment device also includes a treatment head type detection unit for detecting the treatment head type and outputting a corresponding type detection signal to the control device. The treatment head type detection unit can be implemented by using a Hall sensor in conjunction with a magnet on the treatment head, or by using a resistance recognition circuit and a camera unit.

[0087] In this embodiment, the control device can read the chip inside the treatment head when the treatment head is inserted into the host to obtain the treatment head type (e.g., type A is for skincare, type B is for hair removal). Researchers can use a preset "type-wavelength mapping table," for example: type A: 580nm±5nm; type B: 850nm±20nm. The control device compares the read transmitted wavelength value with preset wavelength ranges. For example, the wavelength range corresponding to green light is [500nm, 565nm], yellow light is [565nm, 590nm], orange light is [590nm, 600nm], red light is [600nm, 780nm], and infrared light is [780nm, 1200nm]. Yellow light primarily acts on the superficial dermis, helping to lighten pigmentation, improve redness, and brighten skin tone. Green light primarily acts on the epidermis, helping to balance oil production and soothe inflammation. Red light has extremely strong penetrating power, reaching directly to the hair follicle root and acting as the core light wave for destroying hair follicles. Orange light has slightly less penetrating power than red light but can also effectively reach deep into the hair follicle. Infrared light (the broadband light of home hair removal devices typically covers this range) is invisible to the naked eye but penetrates the deepest, working in conjunction with red light to more thoroughly heat the hair follicle. Assuming the treatment head type is B and the wavelength is 850nm±20nm, it is determined to fall within the corresponding infrared light wavelength range.

[0088] In this embodiment, the control device memory can store a band-gear-heat load mapping table developed by researchers based on a large amount of experimental data. The band-gear-heat load mapping table is shown in Table 1. Table 1

[0089] The data in the table represents the heat load demand value, which is the duty cycle of the PWM signal.

[0090] As shown in Table 1, at the same speed setting, shorter wavelengths result in a stronger thermal effect, while longer wavelengths result in a weaker thermal effect. This means that short-wavelength light (such as yellow / green light) is mainly absorbed by the surface tissue of the skin, has high photothermal conversion efficiency, and easily generates localized high heat, thus requiring greater heat dissipation (matching a high duty cycle). Long-wavelength light (such as infrared light), on the other hand, has strong penetrating power, low absorption rate by skin tissue, and generates less waste heat, thus requiring lower heat dissipation (lower duty cycle). Furthermore, the basic heat load requirement for the first speed setting is less than that for the second speed setting, and the basic heat load requirement for the second speed setting is less than that for the third speed setting. In other words, a higher speed setting represents a greater output light power from the light source, naturally generating more heat, thus requiring a higher fan speed (higher duty cycle) to dissipate the heat. Therefore, at the same wavelength (i.e., using the same type of treatment head), the duty cycle of the PWM signal increases with the increase of the speed setting.

[0091] In this embodiment, assuming the control device recognizes that the treatment head type is B and the user selects the second gear II, then by querying the band-gear-heat load mapping table, it can be found that the heat load requirement is 50%. Therefore, a PWM signal with a duty cycle of 50% is output to the drive circuit to control the drive circuit to drive the fan to run.

[0092] By acquiring the treatment head type and matching the corresponding wavelength range, the main unit achieves adaptive control for different types of treatment heads. Users do not need to manually set the cooling mode; the device automatically applies a cooling strategy based on the physical properties (wavelength) of the inserted treatment head and the set working intensity (level), improving the ease of use and safety of the device and ensuring stable thermal management in different treatment scenarios. Simultaneously, dynamic adjustment based on the rate of temperature change and heat load demand effectively suppresses the temperature rise rate of the treatment head and key electronic components inside the main unit, preventing the device from triggering forced shutdown protection due to overheating. This ensures the continuity of the treatment process and effectively extends the lifespan of electronic components.

[0093] The present invention also proposes a therapeutic device, the therapeutic device comprising: A temperature detection unit is located in the heating area of ​​the therapeutic instrument. The temperature detection unit is used to detect the temperature of the heating area and output a corresponding temperature detection signal. fan; A drive circuit, electrically connected to the fan, is used to output a drive signal to drive the fan to operate; The control device is electrically connected to the temperature detection unit and the drive circuit, respectively, and the control device is used to execute the temperature control method of the therapeutic instrument described above.

[0094] In this embodiment, the temperature detection unit can be implemented using a temperature sensor, such as an NTC thermistor or a digital temperature sensor (e.g., DS18B20), with a temperature measurement range covering 0-150℃. The control device can be a microcontroller unit (MCU), such as an STM32 series or ARM Cortex-M0 core chip, equipped with an analog-to-digital conversion interface to receive the analog signal collected by the temperature detection unit and to output a PWM (Pulse Width Modulation) signal to the drive circuit via a PWM output interface to drive the fan. The drive circuit can be a drive circuit composed of transistor switching circuits or an integrated drive chip.

[0095] Optionally, the treatment device includes, but is not limited to, hair removal devices, phototherapy devices, and phototherapy masks.

[0096] The control device for the therapeutic instrument provided by this invention is based on the temperature control method for the therapeutic instrument described above. Compared with the prior art, the beneficial effects of the therapeutic instrument provided by this invention are the same as those of the temperature control method for the therapeutic instrument provided in the above embodiments, and other technical features of the therapeutic instrument are the same as those disclosed in the methods of the above embodiments, and will not be repeated here.

[0097] The above description is only a part of the embodiments of the present invention and does not limit the patent scope of the present invention. All equivalent structural transformations made under the technical concept of the present invention using the contents of the present invention specification and drawings, or direct / indirect applications in other related technical fields, are included within the patent protection scope of the present invention.

Claims

1. A temperature control method for a therapeutic instrument, characterized in that, The therapeutic device includes a temperature detection unit, a control device, a drive circuit, and a fan. The temperature detection unit is located in the heating area of ​​the therapeutic device and is used to detect the temperature of the heating area and output a temperature detection signal to the control device. The control device is used to output a speed control command to the drive circuit according to the temperature detection signal to drive the fan to operate. The temperature control method of the therapeutic device includes: Obtain the operating parameters of the therapeutic device, which include one or more of the following: power level, working mode, and type of connected treatment head; The temperature of the heating area is obtained, and the rate of temperature change within a preset time period is calculated; The heat load demand value is determined based on the operating parameters and the temperature change rate. The corresponding speed control command is output to the drive circuit according to the heat load demand value, so as to drive the fan to operate at a speed matched with the speed control command; The operating parameters include gear levels, and determining the heat load demand value based on the operating parameters and the temperature change rate includes: The reference power coefficient corresponding to the gear is determined according to the gear and the preset gear-reference power coefficient mapping table; The baseline power coefficient and the temperature change rate are weighted and calculated to obtain the basic heat load demand value, and the basic heat load demand value is determined as the heat load demand value. The light intensity or light frequency is arranged in ascending order as the first light intensity, the second light intensity, and the third light intensity. Under the same temperature change rate, the basic heat load demand value corresponding to the first light intensity is less than the basic heat load demand value corresponding to the second light intensity, and the basic heat load demand value corresponding to the second light intensity is less than the basic heat load demand value corresponding to the third light intensity.

2. The temperature control method for the therapeutic instrument as described in claim 1, characterized in that, The reference power coefficient corresponding to the first gear is 0.3, the reference power coefficient corresponding to the second gear is 0.6, and the reference power coefficient corresponding to the third gear is 1.

0.

3. The temperature control method for the therapeutic instrument as described in claim 1, characterized in that, The step of weighting the reference power coefficient with the temperature change rate to obtain the basic heat load demand value includes: The basic heat load requirement value is determined based on the reference power coefficient corresponding to the gear, the preset thermal inertia weighting coefficient, the temperature change rate, and the preset heat load calculation formula. The formula for calculating the preset heat load is as follows: ； Based on the basic heat load demand value, This is the reference power coefficient corresponding to the gear position. This refers to the rated power of the therapeutic device at the specified setting. To preset the thermal inertia weighting coefficient, This represents the rate of temperature change.

4. A temperature control method for a therapeutic instrument, characterized in that, The therapeutic device includes a temperature detection unit, a control device, a drive circuit, and a fan. The temperature detection unit is located in the heating area of ​​the therapeutic device and is used to detect the temperature of the heating area and output a temperature detection signal to the control device. The control device is used to output a speed control command to the drive circuit according to the temperature detection signal to drive the fan to operate. The temperature control method of the therapeutic device includes: Obtain the operating parameters of the therapeutic device, which include one or more of the following: power level, working mode, and type of connected treatment head; The temperature of the heating area is obtained, and the rate of temperature change within a preset time period is calculated; The heat load demand value is determined based on the operating parameters and the temperature change rate. The corresponding speed control command is output to the drive circuit according to the heat load demand value, so as to drive the fan to operate at a speed matched with the speed control command; The operating parameters include operating modes, which include continuous light emission mode and pulsed light emission mode. The pulsed light emission mode has a corresponding pulse frequency. Determining the heat load demand value based on the operating parameters and the temperature change rate includes: When the working mode is continuous light output mode, the product of the temperature change rate and the preset first compensation coefficient is calculated to obtain the first heat load value, and the first heat load value is determined as the heat load demand value. When the working mode is pulse light output mode, the pulse frequency is obtained, and the second compensation coefficient is determined based on the pulse frequency; Calculate the product of the temperature change rate and the second compensation coefficient to obtain the second heat load value, and determine the second heat load value as the heat load demand value; Wherein, under the same temperature change rate, the preset first compensation coefficient is greater than the second compensation coefficient, so that the fan speed corresponding to the continuous light emission mode is greater than the fan speed corresponding to the pulse light emission mode.

5. The temperature control method for the therapeutic instrument as described in claim 4, characterized in that, The pulsed light emission mode has a corresponding light emission duty cycle, and determining the second compensation coefficient based on the pulse frequency includes: Obtain the duration of a single light emission under the pulse emission mode; The emission duty cycle is calculated based on the pulse frequency and the single emission duration. The product of the preset first compensation coefficient and the light output duty cycle is determined as the second compensation coefficient; The preset first compensation coefficient is 1, and when the working mode is continuous light output mode, the light output duty cycle is 100%.

6. A temperature control method for a therapeutic instrument, characterized in that, The therapeutic device includes a temperature detection unit, a control device, a drive circuit, and a fan. The temperature detection unit is located in the heating area of ​​the therapeutic device and is used to detect the temperature of the heating area and output a temperature detection signal to the control device. The control device is used to output a speed control command to the drive circuit according to the temperature detection signal to drive the fan to operate. The temperature control method of the therapeutic device includes: Obtain the operating parameters of the therapeutic device, which include one or more of the following: power level, working mode, and type of connected treatment head; The temperature of the heating area is obtained, and the rate of temperature change within a preset time period is calculated; The heat load demand value is determined based on the operating parameters and the temperature change rate. The corresponding speed control command is output to the drive circuit according to the heat load demand value, so as to drive the fan to operate at a speed matched with the speed control command; The treatment head of the therapeutic device has an identification mark, which includes thermal resistance characteristics. The operating parameters include the type and power level of the connected treatment head. Determining the heat load requirement based on the operating parameters and the temperature change rate includes: The heat load demand value is determined based on the gear level and the temperature change rate. Obtain the identity identifier of the accessed treatment head type to obtain thermal resistance characteristic parameters, which characterize the resistance when heat is conducted from the internal components of the treatment head to the outside of the treatment head; The heat dissipation efficiency level is determined based on the aforementioned thermal resistance characteristic parameters; When the heat dissipation efficiency level is greater than or equal to a preset level threshold, the heat load demand value is kept constant. If the heat dissipation efficiency level is less than a preset level threshold, a heat dissipation compensation value is determined based on the temperature change rate, and the sum of the heat dissipation compensation value and the heat load demand value is used as the new heat load demand value, and the heat load demand value is updated.

7. The temperature control method for the therapeutic instrument as described in claim 6, characterized in that, The determination of the heat load demand value based on the gear level and the temperature change rate includes: The reference power coefficient corresponding to the gear is determined according to the gear and the preset gear-reference power coefficient mapping table; The baseline power coefficient and the temperature change rate are weighted and calculated to obtain the basic heat load demand value, and the basic heat load demand value is determined as the heat load demand value. The light intensity or light frequency is arranged in ascending order as the first light intensity, the second light intensity, and the third light intensity. Under the same temperature change rate, the basic heat load demand value corresponding to the first light intensity is less than the basic heat load demand value corresponding to the second light intensity, and the basic heat load demand value corresponding to the second light intensity is less than the basic heat load demand value corresponding to the third light intensity.

8. A temperature control method for a therapeutic instrument, characterized in that, The therapeutic device includes a temperature detection unit, a control device, a drive circuit, and a fan. The temperature detection unit is located in the heating area of ​​the therapeutic device and is used to detect the temperature of the heating area and output a temperature detection signal to the control device. The control device is used to output a speed control command to the drive circuit according to the temperature detection signal to drive the fan to operate. The temperature control method of the therapeutic device includes: Obtain the operating parameters of the therapeutic device, which include one or more of the following: power level, working mode, and type of connected treatment head; The temperature of the heating area is obtained, and the rate of temperature change within a preset time period is calculated; The heat load demand value is determined based on the operating parameters and the temperature change rate. The corresponding speed control command is output to the drive circuit according to the heat load demand value, so as to drive the fan to operate at a speed matched with the speed control command; The operating parameters include the treatment head type and intensity level, whereby the treatment head type is determined by the wavelength of light transmission; determining the heat load requirement based on the operating parameters and the temperature change rate includes: The transmitted wavelength is determined based on the type of treatment head, and the target wavelength range to which the transmitted wavelength belongs is determined. The heat load demand value is determined based on the target band range and the gear level. The speed control command is a pulse width modulation signal, and the heat load demand value is the duty cycle of the pulse width modulation signal.

9. A therapeutic device, characterized in that, The therapeutic device includes: A temperature detection unit is located in the heating area of ​​the therapeutic instrument. The temperature detection unit is used to detect the temperature of the heating area and output a corresponding temperature detection signal. fan; A drive circuit, electrically connected to the fan, is used to output a drive signal to drive the fan to operate; A control device is electrically connected to the temperature detection unit and the drive circuit, respectively. The control device is used to execute the temperature control method of the therapeutic instrument as described in any one of claims 1 to 3, or the temperature control method of the therapeutic instrument as described in any one of claims 4 to 5, or the temperature control method of the therapeutic instrument as described in any one of claims 6 to 7, or the temperature control method of the therapeutic instrument as described in claim 8.

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