Adjustable laser treatment handpiece with negative pressure suction and method of treatment

Abstract

This application relates to the fields of medical devices and laser cosmetic technology, providing an adjustable laser treatment handpiece device with negative pressure adsorption and a treatment method. The method utilizes an adjustable laser treatment handpiece device with negative pressure adsorption, comprising a negative pressure adsorption module, an image acquisition module, a main control module, and a laser output module. The negative pressure adsorption module applies negative pressure to the skin at the treatment site, causing the skin to adhere and fix to the light-emitting end face of the handpiece. The image acquisition module acquires images of the skin at the treatment site under adsorption conditions, calculating the current skin curvature and actual focal length parameters. The actual focal length parameters are compared with preset target focal length parameters, and the actual focal length parameters are approximated to the target focal length parameters by adjusting the degree of skin protrusion. The laser output module controls the laser output to treat the treatment site, while the negative pressure adsorption module continuously removes smoke and dust generated by laser irradiation during the treatment process. This method can mitigate the drawbacks and the reduced efficacy and skin damage risk caused by repeated scanning.

Description

Technical Field

[0001] This application relates to the fields of medical devices and laser cosmetic technology, and in particular to an adjustable laser treatment handpiece device and treatment method with negative pressure adsorption. Background Technology

[0002] In the field of medical aesthetic laser treatment, the laser handpiece, as the connecting component between the end of the optical path and the patient's treatment site, directly determines the treatment effect through its fixation stability and focal length control precision.

[0003] Existing laser handpieces have several shortcomings, including: 1. Using direct contact to fix the treatment site makes it difficult to adhere stably to joints, curved skin, etc., and vibration is prone to occur during treatment, leading to defects in fractional scanning or repeated scanning. This can reduce the effectiveness of the treatment or even damage the dermis and cause pigmentation. 2. Focal length adjustment relies on changing to different length handpieces, manually adjusting the field lens, or using the built-in Z-axis module. The former two are cumbersome and have low precision, while the latter is technically difficult and costly, and cannot automatically compensate for focal length changes caused by differences in the curvature of skin in different parts of the body. 3. The smoke and dust generated when high-energy lasers irradiate the skin will instantly attenuate the laser energy reaching the skin surface, which will seriously affect the efficacy in delicate treatments that require constant light power; 4. The lack of real-time feedback and closed-loop control during the treatment process makes treatment parameters uncontrollable, and the final effect depends on the operator's experience.

[0004] Therefore, a method is urgently needed to solve at least one of the above problems. Summary of the Invention

[0005] This application provides an adjustable laser therapy handpiece device and treatment method with negative pressure adsorption, aiming to solve the various shortcomings of existing laser handpieces.

[0006] In a first aspect, embodiments of this application provide an adjustable laser therapy method with negative pressure adsorption, applied to an adjustable laser therapy handpiece device with negative pressure adsorption. The adjustable laser therapy handpiece device includes a negative pressure adsorption module, an image acquisition module, a main control module, and a laser output module, comprising: The negative pressure adsorption module applies negative pressure to the skin at the treatment site, causing the skin to adhere and fix to the light-emitting end face of the handpiece; the image acquisition module acquires images of the skin at the treatment site in the adsorption state, and calculates the current skin curvature and actual focal length parameters based on the skin images; The actual focal length parameter is compared with the preset target focal length parameter. The negative pressure of the negative pressure adsorption module is adjusted according to the comparison result. By changing the degree of skin protrusion, the actual focal length parameter is made closer to the target focal length parameter. When the actual focal length parameter reaches the allowable deviation range of the target focal length parameter, the laser output module is controlled to output laser to the treatment site for treatment. During the treatment process, the negative pressure adsorption module continuously removes the smoke and dust generated by the laser irradiation.

[0007] In some embodiments, applying negative pressure to the skin at the treatment site using the negative pressure adsorption module to adsorb and fix the skin at the treatment site to the light-emitting end face of the handpiece includes: attaching the light-emitting end face of the handpiece to the surface of the skin at the treatment site; activating the negative pressure adsorption module to extract air through the negative pressure holes arranged around the light-emitting end face to create a negative pressure environment inside the handpiece; and causing the skin at the treatment site to bulge towards the light-emitting end face and adhere tightly under the negative pressure, thus completing the adsorption and fixation of the treatment site.

[0008] In some embodiments, the step of acquiring skin images of the treatment site in the adsorption state through an image acquisition module and calculating the current skin curvature and actual focal length parameters based on the skin images includes: capturing skin images of the treatment site in the adsorption state through an image acquisition module hidden inside the handpiece; identifying structural markers in the skin images and calculating the curvature distribution of the skin surface based on the positional offset of the markers; and calculating the actual focal length parameters from the current laser focus to the skin surface based on the curvature distribution and preset parameters of the handpiece's optical path.

[0009] In some embodiments, comparing the actual focal length parameter with the preset target focal length parameter and adjusting the negative pressure of the negative pressure adsorption module according to the comparison result includes: reading the preset target focal length parameter and calculating the deviation value between the actual focal length parameter and the target focal length parameter; determining the negative pressure adjustment direction and adjustment range according to the sign and magnitude of the deviation value; and outputting a control signal to the negative pressure adsorption module according to the adjustment direction and adjustment range to increase or decrease the negative pressure value.

[0010] In some embodiments, the step of changing the degree of skin protrusion to make the actual focal length parameter approach the target focal length parameter includes: when the negative pressure value increases, the degree of protrusion of the skin at the treatment site towards the light-emitting end face increases, and the distance between the skin surface and the laser focus shortens; when the negative pressure value decreases, the degree of protrusion of the skin at the treatment site decreases, and the distance between the skin surface and the laser focus increases; by continuously adjusting the negative pressure value, the actual focal length parameter gradually approaches the target focal length parameter.

[0011] In some embodiments, controlling the laser output module to output laser to the treatment site for treatment when the actual focal length parameter reaches the allowable deviation range of the target focal length parameter includes: real-time monitoring of the deviation value between the actual focal length parameter and the target focal length parameter; generating a laser trigger permission signal when the deviation value falls within the preset allowable deviation range; and controlling the laser output module to output a laser beam to the treatment site for fractional scanning treatment according to the preset treatment energy parameters and scanning mode.

[0012] In some embodiments, the negative pressure adsorption module continuously removes the smoke and dust generated by laser irradiation during the treatment process, including: during laser treatment, the negative pressure adsorption module remains in operation; the smoke and dust generated by laser irradiation on the skin are removed from the light output area under the action of negative pressure airflow; the smoke and dust are discharged outside the handpiece through the negative pressure pipeline with the negative pressure airflow, maintaining the cleanliness of the light output path.

[0013] In some embodiments, the method further includes an adaptive target focal length generation step: before treatment, an initial skin image of the treatment site is acquired through an image acquisition module to identify the size and depth level of the lesion area; the corresponding treatment layer is matched according to the lesion depth level, and a target focal length parameter adapted to the current lesion is generated in combination with the handpiece optical path parameters; the generated target focal length parameter is used as the preset target focal length parameter for this treatment.

[0014] In some embodiments, the method further includes a treatment process abnormality protection step: during the treatment process, skin images are continuously acquired through the image acquisition module to monitor changes in skin color and displacement; when skin displacement exceeds a safety threshold or color abnormality is detected, the laser output is immediately paused and the negative pressure value is increased to allow the skin to re-adhere; after recalculating the actual focal length parameters and adjusting the negative pressure to the target range, the laser output treatment is resumed.

[0015] Secondly, this application provides an adjustable laser therapy handpiece device with negative pressure adsorption, including a negative pressure adsorption module, an image acquisition module, a main control module, and a laser output module.

[0016] The method provided in this application has the following beneficial effects: 1. Stable and reliable adsorption fixation. The negative pressure adsorption method tightly adheres the skin of the treatment area to the light-emitting end face, effectively overcoming the fixation difficulties of curved surfaces and joints. There is no shaking during treatment, the fractional scanning position is accurate, and the drawbacks and risks of decreased efficacy and skin damage caused by repeated scanning are avoided.

[0017] 2. Low-cost and high-precision focus adjustment. Focus adjustment is achieved by changing the degree of skin protrusion by adjusting the amount of negative pressure, eliminating the need for a built-in Z-axis field lens module and reducing hardware costs. Combined with real-time image acquisition feedback, it automatically adjusts the negative pressure to the target focus range, providing high adjustment precision and automatically compensating for differences in skin curvature in different areas.

[0018] 3. Precise and controllable closed-loop control. The image acquisition module acquires skin images in real time and calculates focal length parameters. The main control module dynamically adjusts the negative pressure according to the deviation, forming a complete closed-loop control link. The treatment parameters are controllable and directional, overcoming the shortcomings of traditional hand tools that rely on the operator's experience.

[0019] 4. Stable optical path quality. The negative pressure adsorption module operates continuously during treatment, simultaneously removing the smoke and dust generated by laser irradiation from the light area, maintaining constant laser energy, ensuring stable optical power during treatment, and good consistency in therapeutic effects.

[0020] 5. High treatment safety. The system monitors skin displacement and color changes in real time during treatment. If any abnormalities occur, the laser output is immediately paused and the focus is automatically refocused. Treatment resumes once the condition returns to normal, effectively protecting patient safety and reducing operational risks.

[0021] It should be understood that the above general description and the following detailed description are exemplary and explanatory only, and do not limit this application. Attached Figure Description

[0022] To more clearly illustrate the technical solutions of the embodiments of this application, the drawings used in the description of the embodiments will be briefly introduced below. Obviously, the drawings described below are some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0023] Figure 1 This is a schematic flowchart illustrating the steps of an adjustable laser therapy method with negative pressure adsorption provided in one embodiment of this application; Figure 2 This is a schematic diagram of the structure of an adjustable laser therapy handpiece device with negative pressure adsorption provided in an embodiment of this application; Figure 3 This is a schematic diagram illustrating the principle of an adjustable laser therapy method with negative pressure adsorption provided in one embodiment of this application; Figure 4 This is a schematic block diagram of an adjustable laser therapy system with negative pressure adsorption provided in one embodiment of this application; Figure 5 This is a schematic block diagram of the main control module provided in one embodiment of this application.

[0024] It should be understood that the above general description and the following detailed description are exemplary and explanatory only, and do not limit this application. Detailed Implementation

[0025] The technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some, not all, of the embodiments of this application. Based on the embodiments of this application, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of this application.

[0026] The flowchart shown in the attached diagram is for illustrative purposes only and does not necessarily include all content and operations / steps, nor does it necessarily have to be performed in the order described. For example, some operations / steps can be broken down, combined, or partially merged, so the actual execution order may change depending on the actual situation.

[0027] It should be understood that, in order to clearly describe the technical solutions of the embodiments of the present invention, the terms "first" and "second" are used in the embodiments of the present invention to distinguish identical or similar items with essentially the same function and effect. Those skilled in the art will understand that the terms "first" and "second" do not limit the quantity or execution order, and the terms "first" and "second" are not necessarily different.

[0028] It should be understood that the terminology used in this specification is for the purpose of describing particular embodiments only and is not intended to limit the scope of the application. As used in this specification and the appended claims, the singular forms “a,” “an,” and “the” are intended to include the plural forms unless the context clearly indicates otherwise.

[0029] It should also be understood that the term “and / or” as used in this application specification and the appended claims means any combination of one or more of the associated listed items and all possible combinations, and includes such combinations.

[0030] In the field of medical aesthetic laser treatment, the laser handpiece, as the connecting component between the end of the optical path and the patient's treatment site, directly determines the treatment effect through its fixation stability and focal length control precision.

[0031] Existing laser handpieces have several shortcomings, including: 1. Using direct contact to fix the treatment site makes it difficult to adhere stably to joints, curved skin, etc., and vibration is prone to occur during treatment, leading to defects in fractional scanning or repeated scanning. This can reduce the effectiveness of the treatment or even damage the dermis and cause pigmentation. 2. Focal length adjustment relies on changing to different length handpieces, manually adjusting the field lens, or using the built-in Z-axis module. The former two are cumbersome and have low precision, while the latter is technically difficult and costly, and cannot automatically compensate for focal length changes caused by differences in the curvature of skin in different parts of the body. 3. The smoke and dust generated when high-energy lasers irradiate the skin will instantly attenuate the laser energy reaching the skin surface, which will seriously affect the efficacy in delicate treatments that require constant light power; 4. The lack of real-time feedback and closed-loop control during the treatment process makes treatment parameters uncontrollable, and the final effect depends on the operator's experience.

[0032] Therefore, a method is urgently needed to solve at least one of the above problems.

[0033] To address at least one of the aforementioned technical problems, this application provides an adjustable laser treatment method with negative pressure adsorption. This method uses a negative pressure adsorption module to stably adsorb and fix the skin at the treatment site to the light-emitting end face of the handpiece, solving the problem of unstable fit at curved surfaces and joints. An image acquisition module acquires skin images in real time, calculating the skin curvature and actual focal length. By adjusting the negative pressure, the degree of skin protrusion is changed, causing the actual focal length to automatically approach the target focal length, achieving precise focal length adjustment without mechanical moving parts. During treatment, the negative pressure continuously removes smoke and dust generated by laser irradiation, ensuring a clean light path and constant energy. This method integrates adsorption fixation, automatic focal length adjustment, smoke and dust removal, and closed-loop control, significantly improving the stability, accuracy, and efficacy of laser treatment, while maintaining a simple structure and controllable cost.

[0034] Please refer to Figure 1 The adjustable laser therapy method with negative pressure adsorption provided in this application embodiment is applied to... Figure 2 , Figure 3 The adjustable laser therapy handpiece device with negative pressure adsorption is shown. The adjustable laser therapy handpiece device includes a negative pressure adsorption module, an image acquisition module, a main control module, and a laser output module.

[0035] Please refer to Figure 2 The handheld device is a gun-type or barrel-type handheld structure, including a main body 1 of the handpiece shell, inside which the laser optical path and various functional modules are integrated; a negative pressure adjustment interface 2 is set on the upper part of the shell for connecting to an external negative pressure source and adjusting the negative pressure; an image acquisition module 3 is set in the middle section of the shell, which adopts a hidden endoscope structure for acquiring skin images of the treatment area; a laser output module 4 is set below the image acquisition module, including a field lens and a scanning galvanometer for outputting a laser beam; a funnel-shaped light-emitting end face 5 is set at the front end of the handpiece, which is the end component that contacts the skin when the laser is emitted; a replaceable end contact head 6 is set on the outer side of the light-emitting end face, which can be replaced with different diameters according to the size of the lesion; an annular negative pressure holes 7 are arranged around the light-emitting end face for drawing air to form a negative pressure environment; a connection interface 8 is set at the rear end of the handpiece for connecting the laser host and the negative pressure pipeline.

[0036] Please refer to Figure 3 The main control module contains four functional units: a negative pressure adsorption and skin fixation unit, a skin image acquisition and curvature / focal length calculation unit, a negative pressure adjustment and focal length approximation unit, and a laser output treatment and continuous smoke extraction unit. The negative pressure adsorption module and the main control module form a feedback loop, adjusting the negative pressure based on image acquisition results. The smoke extraction and focusing unit adjusts the negative pressure suction force based on the smoke concentration in the optical path, ensuring a clean optical path. All units work collaboratively to achieve closed-loop control of the entire process, from adsorption and fixation, focal length calculation, negative pressure focusing, to laser treatment and smoke extraction.

[0037] It should also be noted that all skin image data, treatment parameter data, negative pressure adjustment data, and other information involved in the method provided in this application are collected and used with the authorization of the relevant users and in accordance with the regulations on medical data security and privacy protection, and will not infringe on user privacy or medical safety.

[0038] The provided adjustable laser therapy method with negative pressure adsorption includes steps S101 to S103. Details are as follows: Step S101. Apply negative pressure to the skin at the treatment site using the negative pressure adsorption module to adsorb and fix the skin at the treatment site to the light-emitting end face of the handpiece; acquire images of the skin at the treatment site under adsorption state using the image acquisition module, and calculate the current skin curvature and actual focal length parameters based on the skin images.

[0039] Specifically, the core objective of this step is to securely fix the skin at the treatment site to the light-emitting end face of the handpiece using negative pressure adsorption before treatment begins, eliminating problems such as unstable adhesion and treatment tremors on curved surfaces. At the same time, a hidden image acquisition module acquires skin images, and the current skin curvature and actual laser focal length are calculated based on image analysis, providing a quantitative basis for subsequent focal length adjustment.

[0040] During the negative pressure adsorption and fixation stage, the operator places the light-emitting end face of the handpiece against the skin surface of the treatment area, ensuring a sealed contact between the annular negative pressure holes around the light-emitting end face and the skin surface. The negative pressure adsorption module is activated; an external negative pressure source is connected to the negative pressure channel inside the handpiece via a negative pressure pipeline. The annular negative pressure holes around the light-emitting end face continuously draw in air, creating a negative pressure environment in the enclosed space between the light-emitting end face and the skin. Under the influence of the internal and external pressure difference, the skin at the treatment area bulges towards the light-emitting end face and adheres tightly to it, completing the adsorption and fixation of the treatment area. The negative pressure value is initially set to -20 kPa to -60 kPa based on the skin thickness and curvature characteristics of the treatment area, ensuring stable adsorption without detachment while avoiding excessive negative pressure that could cause skin discomfort or damage. After adsorption and fixation, there is no relative displacement between the treatment area and the handpiece, maintaining stability even in difficult-to-fix areas such as joints and curved skin, fundamentally eliminating the problem of shaking during treatment.

[0041] During the skin image acquisition stage, the image acquisition module employs a concealed endoscope structure, installed beside the optical path inside the handpiece, with the lens facing the light-emitting end face, without obstructing the main laser optical path. The endoscope acquires skin images of the treatment area in the adsorption state through a semi-transparent, semi-reflective mirror or the side optical path. The image resolution is no less than 640×480 pixels, and the frame rate is no less than 30 frames per second, ensuring image clarity and real-time performance. The acquired skin images are transmitted to the image processing unit of the main control module via internal data lines. The images include skin surface texture, pores, pigmented lesions, and pre-set structural markers.

[0042] In the skin curvature and actual focal length calculation stage, the main control module processes the acquired skin images. First, it identifies pre-set structural markers on the inner side of the light-emitting end face. These markers are tiny optical markers arranged at equal intervals, forming a regular dot matrix in the image. Based on the positional offset and deformation degree of the markers in the image, the curvature distribution of the skin surface is calculated: areas with increased marker spacing correspond to greater skin protrusion, while areas with decreased marker spacing correspond to skin depression or insufficient adhesion. Through multi-point fitting, the three-dimensional curvature distribution of the skin surface in the treatment area is obtained, quantitatively characterizing the protrusion morphology of the skin under negative pressure adsorption.

[0043] Based on the curvature distribution and preset parameters of the handpiece optical path (including field lens focal length, working distance, and scanning galvanometer parameters), the actual focal length parameter from the current laser focus to the skin surface is calculated. Specifically, the calculation method is as follows: based on the height of the skin surface center point's protrusion and the nominal working distance of the field lens, the distance deviation between the actual focus and the skin surface is calculated to obtain the actual focal length parameter. A positive actual focal length parameter indicates that the focus is above the skin surface (underfocus), a negative value indicates that the focus is deep within the skin (overfocus), and zero indicates that the focus falls exactly on the skin surface (positive focus). The calculation accuracy of the actual focal length parameter can reach 0.01 mm, meeting the focal length control requirements for precise treatment.

[0044] Step S102. Compare the actual focal length parameter with the preset target focal length parameter, and adjust the negative pressure of the negative pressure adsorption module according to the comparison result. By changing the degree of skin protrusion, the actual focal length parameter is made closer to the target focal length parameter.

[0045] Specifically, the core objective of this step is to adjust the degree of skin protrusion by adjusting the negative pressure in a closed loop based on the deviation between the actual focal length and the target focal length, thereby changing the distance between the skin surface and the laser focus, so that the actual focal length automatically approaches the target focal length, achieving precise focal length adjustment without the need for mechanical moving parts.

[0046] In the focal length deviation calculation stage, the main control module reads the preset target focal length parameters. The target focal length is set according to the treatment needs: for epidermal treatments (such as freckle removal and skin rejuvenation), the target focal length is set to 0 or a slightly positive value, so that the focus falls on the epidermis; for dermal treatments (such as deep freckles and scars), the target focal length is set to a negative value, so that the focus penetrates to a specific depth in the dermis. The deviation between the actual focal length parameter and the target focal length parameter is calculated. The deviation is equal to the actual focal length minus the target focal length. A positive deviation indicates that the current focus is too high, and the negative pressure needs to be increased to make the skin protrude further to shorten the focal length; a negative deviation indicates that the current focus is too deep, and the negative pressure needs to be decreased to make the skin fall back to increase the focal length.

[0047] In the stage of determining the direction and amplitude of negative pressure adjustment, the direction and amplitude of adjustment are determined based on the sign and magnitude of the deviation. Adjustment direction: increase the negative pressure value when the deviation is positive, and decrease the negative pressure value when the deviation is negative. The adjustment amplitude adopts a proportional adjustment method; the amount of negative pressure adjustment is directly proportional to the magnitude of the deviation. The proportional coefficient is determined based on a pre-calibrated relationship between negative pressure and skin protrusion, typically corresponding to a negative pressure adjustment of 2 kPa to 5 kPa for every 0.1 mm focal length deviation. Simultaneously, an upper limit for single adjustment amplitude is set, ensuring that each negative pressure adjustment does not exceed 20% of the current value to avoid skin discomfort or image jitter caused by sudden changes in negative pressure.

[0048] During the negative pressure adjustment phase, the main control module outputs control signals to the negative pressure adsorption module according to the determined adjustment direction and amplitude. This increases or decreases the negative pressure value by adjusting the opening of the proportional valve in the negative pressure pipeline. The negative pressure value is fed back to the main control module in real time, forming a closed-loop control system to ensure that the actual negative pressure value matches the target value. When the negative pressure value increases, the degree of skin protrusion towards the light-emitting end face at the treatment site increases, shortening the distance between the skin surface and the laser focal point, thus reducing the actual focal length. Conversely, when the negative pressure value decreases, the degree of skin protrusion at the treatment site decreases, and the skin surface recedes under elasticity, increasing the distance between the skin surface and the laser focal point, thus increasing the actual focal length.

[0049] During the focal length approach iteration phase, after negative pressure adjustment, the image acquisition module re-acquires skin images and recalculates the actual focal length parameters, comparing them with the target focal length. If the deviation still exceeds the allowable range, negative pressure adjustment continues, iterating repeatedly until the actual focal length parameters fall within the allowable deviation range of the target focal length. The allowable deviation range is set according to the treatment accuracy requirements, typically ±0.05 mm to ±0.1 mm. The entire adjustment process is completed within 1 to 3 seconds, offering fast adjustment speed and high precision. Furthermore, it requires no mechanical moving parts; precise focal length adjustment is achieved solely by changing the negative pressure. The structure is simple, low-cost, and highly reliable.

[0050] Step S103. When the actual focal length parameter reaches the allowable deviation range of the target focal length parameter, control the laser output module to output laser to the treatment site for treatment. During the treatment process, the negative pressure adsorption module continuously removes the smoke and dust generated by the laser irradiation.

[0051] Specifically, the core objective of this step is to trigger laser output for treatment after the focal length reaches the target range. At the same time, a negative pressure adsorption state is maintained throughout the treatment process to continuously remove the smoke and dust generated by the laser irradiation on the skin, ensuring the cleanliness of the light path and the constant laser energy reaching the skin. Simultaneously, the focal length stability is continuously monitored and dynamically adjusted as necessary.

[0052] During the laser trigger authorization and output phase, the main control module monitors the deviation between the actual focal length parameter and the target focal length parameter in real time. When the deviation value falls within the preset allowable deviation range for multiple consecutive sampling cycles (usually 3 to 5 cycles), it is determined that the focal length has stably reached the target, and a laser trigger authorization signal is generated. After the operator presses the treatment trigger switch, the main control module controls the laser output module to output a laser beam to the treatment site according to the preset treatment energy parameters (single pulse energy, pulse frequency, pulse width) and scanning mode (fractional scanning mode, scanning pattern, scanning density). After being focused by the field lens, the laser beam precisely acts on the skin layer corresponding to the target focal length for fractional scanning treatment. During the scanning process, the galvanometer scans point by point according to the preset pattern, and the dwell time and energy of each scanning point are consistent to ensure treatment uniformity.

[0053] During the continuous smoke removal phase, the negative pressure adsorption module remains operational throughout the laser treatment process. The annular negative pressure holes around the light-emitting end face continuously draw in air, creating a stable negative pressure airflow. When the laser irradiates the skin surface, especially when it reaches aged keratinocytes, hair, or pigmented tissue, tiny smoke particles are generated. These particles are immediately drawn away from the light-emitting area by the negative pressure airflow and discharged outside the handpiece through the negative pressure tubing. The negative pressure suction force is dynamically adjusted according to the amount of smoke generated: the negative pressure is appropriately increased during high-energy, high-density scans to enhance the removal effect; the negative pressure is appropriately decreased during low-energy, low-density scans to improve comfort. By continuously removing smoke, the cleanliness of the light-emitting path is maintained, preventing scattering and absorption of the laser by smoke, ensuring a constant laser energy reaching the skin surface, and eliminating energy attenuation and uneven treatment caused by smoke.

[0054] During the treatment process monitoring and dynamic maintenance phase, the image acquisition module continuously acquires skin images, monitoring real-time displacement changes and focal length stability on the skin surface. If the focal length deviates from the target range due to operator hand movements or changes in skin elasticity, the main control module automatically fine-tunes the negative pressure value to bring the focal length back to the target range, achieving closed-loop focal length maintenance throughout the treatment. Simultaneously, it monitors color changes and abnormal reactions on the skin surface; if any abnormality occurs, laser output is paused. After treatment, the laser output is turned off, negative pressure is maintained for a few seconds to remove residual smoke, then the negative pressure is released, the handpiece is removed, and the treatment is complete.

[0055] In some embodiments, applying negative pressure to the skin at the treatment site using the negative pressure adsorption module to adsorb and fix the skin at the treatment site to the light-emitting end face of the handpiece includes: attaching the light-emitting end face of the handpiece to the surface of the skin at the treatment site; activating the negative pressure adsorption module to extract air through the negative pressure holes arranged around the light-emitting end face to create a negative pressure environment inside the handpiece; and causing the skin at the treatment site to bulge towards the light-emitting end face and adhere tightly under the negative pressure, thus completing the adsorption and fixation of the treatment site.

[0056] The operator places the light-emitting end of the handpiece against the skin surface of the treatment area. Holding the handpiece, the operator gently presses the funnel-shaped light-emitting end onto the area to be treated, ensuring that the flexible sealing ring around the light-emitting end makes full contact with the skin surface, forming an initial seal. The light-emitting end adopts a funnel-shaped structure, with the front opening area larger than the laser scanning area, ensuring that the scanning range completely covers the treatment area. At the same time, the sidewalls of the funnel guide the even distribution of negative pressure airflow. A medical-grade flexible silicone sealing ring is set at the contact edge of the light-emitting end. The sealing ring has a lip-shaped cross-section, which not only ensures a sealing effect on skin surfaces with different curvatures but also improves contact comfort and avoids hard edge indentations.

[0057] The negative pressure adsorption module is activated. An external negative pressure source is connected to the negative pressure pipeline through the connection interface at the rear of the handpiece. A proportional regulating valve and a pressure sensor are installed within the pipeline. The main control module outputs a control signal to adjust the opening of the proportional valve. Air is then drawn in through the annular negative pressure holes arranged around the circumference of the light-emitting end face. These holes are evenly distributed around the circumference of the light-emitting end face, with 8 to 16 holes of 0.5 to 1.5 mm in diameter, ensuring uniform air extraction and a symmetrical negative pressure field. The extracted air is collected through the negative pressure channel inside the handpiece and discharged from the rear interface, creating a negative pressure environment in the enclosed space between the light-emitting end face of the handpiece and the skin. The pressure sensor monitors the pressure value within the negative pressure chamber in real time and feeds it back to the main control module to form a closed-loop control, ensuring the negative pressure value remains stable at the set value.

[0058] Under negative pressure, the skin at the treatment site bulges and adheres tightly to the light-emitting end face. Driven by the internal and external pressure difference, the skin surface rises towards the negative pressure cavity (i.e., the light-emitting end face). The height of the bulge is related to the negative pressure value, skin thickness, and elasticity. After the skin bulges, there is no gap between the treatment area and the light-emitting end face, resulting in a tight fit. Even in areas where traditional handpieces are difficult to fix, such as joints and curved skin, stable fixation can be achieved through negative pressure adsorption. The negative pressure value is set from -20 kPa to -60 kPa according to the characteristics of the treatment area. Lower negative pressure is used for thin skin areas (such as around the eyes), and higher negative pressure is used for thick skin areas (such as the jaw and back of the hand). After adsorption and fixation are completed, a rigid connection is formed between the treatment area and the handpiece, with a relative displacement of less than 0.02 mm, fundamentally eliminating the problem of shaking during the treatment process and ensuring the accuracy of fractional scanning.

[0059] In some embodiments, the step of acquiring skin images of the treatment site in the adsorption state through an image acquisition module and calculating the current skin curvature and actual focal length parameters based on the skin images includes: capturing skin images of the treatment site in the adsorption state through an image acquisition module hidden inside the handpiece; identifying structural markers in the skin images and calculating the curvature distribution of the skin surface based on the positional offset of the markers; and calculating the actual focal length parameters from the current laser focus to the skin surface based on the curvature distribution and preset parameters of the handpiece's optical path.

[0060] Images of the skin at the treatment site are captured in its adsorption state using an image acquisition module hidden inside the handpiece. This module employs a miniature endoscopic camera, concealed within the handpiece beside the laser beam path. The lens axis forms a small angle with the main laser beam path. A 45-degree tilted semi-transparent, semi-reflective mirror directs reflected light from the skin surface into the camera, ensuring clear image capture of the treatment area without obstructing the main laser beam path. The camera uses a near-infrared enhanced CMOS sensor with a resolution of at least 640×480 pixels and a frame rate of at least 30 frames per second. Combined with a near-infrared auxiliary illumination source within the handpiece, clear skin images can be acquired even in the intense light environment of laser treatment, preventing overexposure of the laser spot and image loss. The acquired image data is transmitted to the image processing unit of the main control module via an internal flexible cable.

[0061] The system identifies structural markers in skin images and calculates the curvature distribution of the skin surface based on the positional offset of these markers. Microstructural markers, arranged at equal intervals, are pre-fabricated on a transparent window inside the light-emitting end face. These markers are circular or cross-shaped optical marks, clearly imaged under near-infrared illumination. The marker array covers the entire treatment area, with a spacing of 1 to 2 millimeters. The image processing unit uses a feature point detection algorithm to identify the sub-pixel coordinates of all markers in the image and compares them with the standard coordinates (coordinates when the plane is undeformed) to calculate the positional offset and deformation of each marker. Areas where the spacing between markers increases in the image correspond to skin bulging towards the light-emitting end face (the larger the bulge, the larger the spacing between markers in the image projection); areas where the spacing decreases or the markers are deformed correspond to skin depression or insufficient adhesion. By performing surface fitting on the offsets of all markers, a three-dimensional curvature distribution and bulge height distribution map of the skin surface in the treatment area are obtained, quantitatively characterizing the three-dimensional morphology of the skin under negative pressure adsorption.

[0062] Based on the curvature distribution and the preset parameters of the handpiece optical path, the actual focal length from the current laser focus to the skin surface is calculated. The preset parameters of the handpiece optical path include the nominal focal length of the field lens, the nominal working distance (distance from the field lens to the focus), the deflection angle of the scanning galvanometer, and the scanning range. The bulge height h of the center point of the skin surface (i.e., the laser scanning center) is calculated based on the curvature distribution; this is the height of the skin surface bulging towards the light-emitting end face relative to the reference plane (the skin position at zero negative pressure). The formula for calculating the actual focal length is: Actual Focal Length = Nominal Working Distance - Buzz Height h - Field Lens Mounting Reference Correction. The nominal working distance is the distance from the focus to the lower surface of the field lens at the factory, a known constant; the bulge height h is calculated from the curvature distribution; and the field lens mounting reference correction is a constant obtained from assembly calibration, used to compensate for assembly errors. A positive actual focal length indicates the focus is above the skin surface (underfocused), a negative value indicates the focus is deep within the skin (overfocused), and zero indicates the focus falls exactly on the skin surface (positive focus). The actual focal length calculation accuracy can reach 0.01 mm, which meets the focal length control requirements for fine treatment.

[0063] In some embodiments, comparing the actual focal length parameter with the preset target focal length parameter and adjusting the negative pressure of the negative pressure adsorption module according to the comparison result includes: reading the preset target focal length parameter and calculating the deviation value between the actual focal length parameter and the target focal length parameter; determining the negative pressure adjustment direction and adjustment range according to the sign and magnitude of the deviation value; and outputting a control signal to the negative pressure adsorption module according to the adjustment direction and adjustment range to increase or decrease the negative pressure value.

[0064] The system reads preset target focal length parameters, which are pre-set and stored in the main control module according to the treatment layer requirements. For epidermal treatments (such as superficial pigmentation, phototherapy, and enlarged pores), the target focal length is set to 0 mm or +0.05 mm to +0.1 mm, ensuring the laser focus falls precisely on or slightly above the epidermis, concentrating energy in the epidermis. For superficial dermal treatments (such as melasma and superficial scars), the target focal length is set to -0.1 mm to -0.3 mm, allowing the focus to penetrate deep into the superficial dermis. For deep dermal treatments (such as deep pigmentation, atrophic scars, and tattoo removal), the target focal length is set to -0.3 mm to -0.6 mm, allowing the focus to penetrate deep into the deep dermis. The target focal length can be automatically loaded after the operator selects the treatment mode through the host computer interface, or it can be manually fine-tuned in increments of 0.01 mm.

[0065] Calculate the deviation between the actual focal length and the target focal length: Deviation = Actual Focal Length - Target Focal Length. A positive deviation indicates that the current focal position is higher than the target position (excessive underfocus or insufficient overfocus), requiring the skin to protrude further to shorten the actual focal length. A negative deviation indicates that the current focal position is lower than the target position (excessive overfocus), requiring the skin to recede to increase the actual focal length. The absolute value of the deviation reflects the required adjustment range; a larger deviation requires a larger negative pressure adjustment. After calculating the deviation, check its trend. If the deviation is increasing rapidly, increase the adjustment range appropriately to accelerate convergence; if the deviation has stabilized, use a smaller adjustment range to avoid overshoot.

[0066] The direction and magnitude of negative pressure adjustment are determined based on the sign and magnitude of the deviation. Adjustment direction: when the deviation is positive, increase the negative pressure value (more negative); when the deviation is negative, decrease the negative pressure value (returning to zero). The adjustment magnitude uses a proportional-derivative control algorithm: negative pressure adjustment amount = Kp × deviation + Kd × deviation change rate, where Kp is the proportional coefficient and Kd is the derivative coefficient, determined by a pre-calibrated negative pressure-protrusion response curve. A typical calibration relationship is: for every 10 kPa increase in negative pressure, the skin protrusion height increases by approximately 0.05 mm to 0.15 mm (the specific value varies depending on skin thickness and elasticity), and the proportional coefficient is calculated accordingly. A single adjustment magnitude limit is also set, with each negative pressure adjustment not exceeding 20% ​​of the current absolute value and not exceeding 10 kPa, to avoid skin discomfort or severe image jitter caused by sudden negative pressure changes. For deviations less than 0.02 mm, no adjustment is performed to avoid frequent fine-tuning leading to negative pressure instability.

[0067] The main control module outputs control signals to the negative pressure adsorption module according to the adjustment direction and amplitude, increasing or decreasing the negative pressure value. The main control module converts the calculated negative pressure target value into a control voltage signal for the proportional valve, which is then output to the proportional regulating valve of the negative pressure adsorption module. The opening of the regulating valve changes the flow area of ​​the negative pressure pipeline, thereby increasing or decreasing the negative pressure value in the negative pressure chamber. The pressure sensor in the negative pressure chamber detects the actual negative pressure value in real time and feeds it back to the main control module. After comparing it with the target value, fine adjustments are made to form a negative pressure closed-loop control, ensuring that the actual negative pressure value reaches the target value quickly and accurately, with a response time of less than 200 milliseconds. After adjustment, the system waits for the skin morphology to stabilize (approximately 200 to 500 milliseconds), then re-acquires images to calculate the actual focal length, and begins the next iteration.

[0068] In some embodiments, the step of changing the degree of skin protrusion to make the actual focal length parameter approach the target focal length parameter includes: when the negative pressure value increases, the degree of protrusion of the skin at the treatment site towards the light-emitting end face increases, and the distance between the skin surface and the laser focus shortens; when the negative pressure value decreases, the degree of protrusion of the skin at the treatment site decreases, and the distance between the skin surface and the laser focus increases; by continuously adjusting the negative pressure value, the actual focal length parameter gradually approaches the target focal length parameter.

[0069] As the negative pressure increases, the degree of skin bulging towards the light-emitting end face at the treatment site increases, and the distance between the skin surface and the laser focal point shortens. When the absolute value of the negative pressure increases, the pressure difference between the inside and outside of the skin increases, driving the skin tissue to bulge further towards the negative pressure cavity (light-emitting end face), increasing the bulge height. Since the spatial position of the laser focal point is fixed (determined by the field lens position), the skin surface moves towards the focal point, reducing the distance between them, and the actual focal length parameter (distance from the focal point to the skin surface) decreases accordingly. The increase in bulge height has a non-linear relationship with the increase in negative pressure: in the low negative pressure range, skin elastic deformation is dominant, and the bulge increases rapidly with the increase in negative pressure; in the high negative pressure range, the skin tissue is stretched to near its limit, and the increase in bulge slows down. This non-linear relationship is pre-calibrated and stored in the main control module to improve the prediction accuracy of focal length adjustment.

[0070] When the negative pressure decreases, the bulge of the skin at the treatment site decreases, and the distance between the skin surface and the laser focal point increases. When the absolute value of the negative pressure decreases, the pressure difference between the inside and outside decreases, and the skin tissue, under its own elastic recoil force, falls back to its original position, reducing the bulge height. The skin surface moves away from the laser focal point, increasing the distance between them, and the actual focal length parameter increases accordingly. The skin's fall-back process has a certain viscoelastic hysteresis characteristic; that is, after the negative pressure decreases, the skin does not immediately and completely fall back, but rather there is a brief delay. Therefore, when the negative pressure decreases, the stabilization waiting time should be appropriately extended (approximately 300 to 500 milliseconds) until the skin morphology stabilizes before calculating the actual focal length to avoid overshoot due to the hysteresis effect.

[0071] By continuously adjusting the negative pressure value, the actual focal length parameter gradually approaches the target focal length parameter. The entire adjustment process adopts an iterative closed-loop approach: after each adjustment of the negative pressure, the skin morphology is allowed to stabilize, the image is re-acquired, the actual focal length is calculated, and compared with the target focal length. If the deviation still exceeds the allowable range, the adjustment continues until the deviation falls within the allowable range. The allowable deviation range is usually ±0.05 mm to ±0.1 mm, which can be adjusted according to the treatment precision requirements. During the iteration process, the main control module records the negative pressure value and the corresponding actual focal length for each iteration, and updates the negative pressure-focal length response curve of the treatment area in real time, making subsequent adjustments increasingly precise. Usually, 2 to 4 iterations are sufficient to reach the target, and the entire process is completed within 1 to 3 seconds. Through this purely pneumatic focal length adjustment method, no mechanical moving parts (such as Z-axis motors or adjustable field lenses) are required. The structure is simple, low-cost, has no mechanical wear, and is highly reliable. Moreover, the skin remains in a fixed state of adhesion throughout the adjustment process, which does not affect the stability of the treatment.

[0072] In some embodiments, controlling the laser output module to output laser to the treatment site for treatment when the actual focal length parameter reaches the allowable deviation range of the target focal length parameter includes: real-time monitoring of the deviation value between the actual focal length parameter and the target focal length parameter; generating a laser trigger permission signal when the deviation value falls within the preset allowable deviation range; and controlling the laser output module to output a laser beam to the treatment site for fractional scanning treatment according to the preset treatment energy parameters and scanning mode.

[0073] The system monitors the deviation between the actual focal length parameter and the target focal length parameter in real time. After the focal length adjustment is completed, the main control module enters the focal length stabilization monitoring state. The image acquisition module continuously acquires skin images at a fixed frame rate. The image processing unit calculates the current actual focal length parameter in real time and compares it with the target focal length parameter to obtain the real-time deviation value. During the monitoring process, the fluctuation range of the deviation is also calculated. If the deviation is within the allowable range but the fluctuation is large (such as frequent jumps near the boundary), it is determined that the focal length has not been fully stabilized, and the system continues to wait. If the deviation falls stably within the allowable deviation range for several consecutive sampling periods (usually 3 to 5 periods, corresponding to about 100 to 200 milliseconds), and the fluctuation range is less than half of the deviation range, it is determined that the focal length has stabilized and met the standard.

[0074] When the deviation value falls within the preset allowable deviation range, a laser trigger permission signal is generated. The allowable deviation range is set according to the treatment precision requirements: ±0.05 mm for fine treatment (such as periocular and superficial spots), ±0.1 mm for routine treatment, and ±0.2 mm for coarse adjustment treatment. Once the deviation consistently and stably falls within the allowable range, the main control module generates a laser trigger permission signal and sends it to the laser safety interlock circuit to unlock the laser output channel. Before the permission signal is generated, even if the operator presses the trigger switch, the laser will not output, ensuring from a hardware perspective that light is only emitted when the focal length is correct, avoiding treatment depth deviations caused by incorrect focal length. After the permission signal is generated, the main control module prompts the operator via a buzzer or indicator light that the focal length is ready and treatment can begin.

[0075] Based on preset treatment energy parameters and scanning modes, the laser output module is controlled to output laser beams to the treatment area for fractional scanning treatment. After the operator presses the treatment trigger switch, the main control module reads the preset treatment parameters: single pulse energy (set from 5 mJ to 200 mJ depending on the treatment type and skin type), pulse frequency (1 Hz to 20 Hz), pulse width (femtosecond or nanosecond level, determined according to the laser type), scanning density (10 to 200 points per square centimeter), and scanning pattern (rectangle, circle, or custom pattern). After receiving the control command, the laser output module controls the laser to output laser pulses with the specified parameters, and simultaneously controls the two-dimensional scanning galvanometer to deflect point by point according to the preset scanning pattern, projecting the laser pulses sequentially onto each scanning point in the treatment area to form a fractional scanning pattern. The laser energy and residence time of each scanning point are consistent to ensure treatment uniformity. During the scanning process, the negative pressure adsorption module maintains the adsorption state continuously, and the image acquisition module continuously monitors the focal length. If the focal length deviates, the negative pressure is automatically fine-tuned or the scanning is paused to ensure the accuracy of the entire treatment.

[0076] In some embodiments, the negative pressure adsorption module continuously removes the smoke and dust generated by laser irradiation during the treatment process, including: during laser treatment, the negative pressure adsorption module remains in operation; the smoke and dust generated by laser irradiation on the skin are removed from the light output area under the action of negative pressure airflow; the smoke and dust are discharged outside the handpiece through the negative pressure pipeline with the negative pressure airflow, maintaining the cleanliness of the light output path.

[0077] During laser treatment, the negative pressure adsorption module remains operational, maintaining the negative pressure value at the target value after focus adjustment. This ensures both secure skin adhesion and a continuous airflow. Pressure sensors within the negative pressure chamber monitor the negative pressure in real time. If the negative pressure drops due to dust blockage or tubing bends, the main control module automatically increases the proportional valve opening to compensate and maintain stable negative pressure. The negative pressure airflow enters evenly from the annular negative pressure holes around the laser emission face and converges into the negative pressure channel inside the handpiece, forming a radially converging airflow centered on the laser emission area. The airflow velocity is highest in the central area of ​​the emission face, effectively removing dust generated in that area.

[0078] The smoke and dust generated by laser irradiation on the skin are drawn out of the light-emitting area under the action of negative pressure airflow. When high-energy laser pulses irradiate the skin surface, especially when irradiating pigmented lesions, aged keratin, or hair, the tissue instantly vaporizes, generating tiny smoke and dust particles (typically 0.1 to 10 micrometers in diameter). If these particles are suspended in the optical path, they will scatter and absorb subsequent laser pulses, leading to energy attenuation reaching the skin. In severe cases, the energy of a single pulse can decrease by more than 20%. Because the negative pressure airflow forms a continuous radial converging flow in the light-emitting area, the smoke and dust particles are immediately entrained by the airflow after generation and drawn out of the light-emitting area within milliseconds, preventing them from accumulating in the optical path. The magnitude of the negative pressure suction force can be dynamically matched according to the treatment parameters: when scanning with high energy, high frequency, and high density, the amount of smoke and dust generated is large, so the negative pressure value should be appropriately increased (an absolute increase of 5 to 10 kPa) to enhance the extraction effect; when scanning with low energy and low density, there is less smoke and dust, so maintaining the basic negative pressure is sufficient to balance extraction effect and user comfort.

[0079] Smoke and dust are discharged from the handpiece via negative pressure airflow through negative pressure tubing, maintaining the cleanliness of the light output path. The airflow carrying smoke and dust enters the handpiece through the annular negative pressure port, where it is initially filtered by built-in filter cotton to remove large particles. It then converges at the negative pressure interface at the rear of the handpiece and is discharged through an external negative pressure tubing to an external smoke and dust filtration device (such as a HEPA filter and activated carbon adsorption device). After purification, it is discharged, preventing indoor air pollution. The internal light path and negative pressure channel of the handpiece are isolated from each other; the negative pressure airflow does not pass through optical components such as field lenses and galvanometers, preventing smoke and dust contamination of optical lenses. By continuously removing smoke and dust, the light output path remains clean, with laser energy fluctuations reaching the skin surface less than 5%. This ensures consistent treatment energy at each scanning point, eliminating energy attenuation, uneven treatment, and reduced efficacy caused by smoke and dust, making it particularly suitable for precision laser treatments requiring constant light power.

[0080] In some embodiments, the method further includes an adaptive target focal length generation step: before treatment, an initial skin image of the treatment site is acquired through an image acquisition module to identify the size and depth level of the lesion area; the corresponding treatment layer is matched according to the lesion depth level, and a target focal length parameter adapted to the current lesion is generated in combination with the handpiece optical path parameters; the generated target focal length parameter is used as the preset target focal length parameter for this treatment.

[0081] Before treatment, an initial skin image of the treatment area is acquired via an image acquisition module. Under conditions of no negative pressure or with only slight pre-negative pressure (-10 kPa to -20 kPa), the image acquisition module captures the initial skin image of the treatment area, containing information on the morphology, color, and texture of the lesions. The image processing unit of the main control module analyzes the image. First, through color space conversion and threshold segmentation, it identifies pigmented lesion areas (such as melasma, age spots, tattoos, etc.) and calculates the area, boundary, and pigment density of the lesions. Simultaneously, by comparing the color depth and texture features of the lesions with a preset depth grading model, the depth level of the lesions is assessed, categorized into three levels: superficial (epidermal layer), intermediate (superficial dermis), and deep (deep dermis). For non-pigmented lesions such as scars, they are identified and graded based on texture and convexity features.

[0082] The treatment layer is matched according to the lesion depth level, and the target focal length parameters adapted to the current lesion are generated by combining the handpiece optical path parameters. A preset layer-focal length mapping table is stored in the main control module: superficial lesions correspond to target focal lengths of 0 mm to +0.05 mm (focus on the epidermis), intermediate lesions correspond to -0.1 mm to -0.3 mm (focus on the superficial dermis), and deep lesions correspond to -0.3 mm to -0.6 mm (focus on the deep dermis). Simultaneously, the target focal length is fine-tuned according to the pigment density and area of ​​the lesion: for lesions with high pigment density and large area, the focal depth is appropriately increased (more negative focal length) to ensure sufficient energy is applied to the lesion; for lesions with light pigment and small area, the depth is appropriately decreased to avoid overtreatment. Combined with the handpiece optical path parameters (field lens working distance, scanning range corresponding to focal length drift correction), the final target focal length parameters are generated with an accuracy of 0.01 mm.

[0083] The generated target focal length parameter is used as the preset target focal length parameter for this treatment, replacing the default fixed target focal length. The generated target focal length is also displayed on the host computer interface for operator confirmation, and the operator can manually fine-tune it based on experience. After confirmation, this target focal length is used as the preset target focal length for this treatment, and subsequent negative pressure adjustments in step S102 are based on this target. Through adaptive target focal length generation, the optimal treatment focal length can be automatically matched according to the actual depth characteristics of each lesion, avoiding the depth inaccuracy problem caused by the operator manually setting the focal length based on experience, improving the accuracy and efficacy of treatment, and is especially suitable for complex treatment scenarios with large differences in lesion depth.

[0084] In some embodiments, the method further includes a treatment process abnormality protection step: during the treatment process, skin images are continuously acquired through the image acquisition module to monitor changes in skin color and displacement; when skin displacement exceeds a safety threshold or color abnormality is detected, the laser output is immediately paused and the negative pressure value is increased to allow the skin to re-adhere; after recalculating the actual focal length parameters and adjusting the negative pressure to the target range, the laser output treatment is resumed.

[0085] During treatment, the image acquisition module continuously acquires skin images, monitoring changes in skin color and displacement. During laser treatment, the image acquisition module continuously acquires skin images of the treatment area at a frame rate of no less than 30 frames per second. The main control module analyzes two indicators in real time: first, displacement change, which calculates the amount of displacement of the skin surface relative to the start of treatment by tracking the skin texture and the position of marker points in the image. Displacement includes horizontal displacement (skin sliding) and vertical displacement (focal length change caused by changes in protrusion height); second, color change, which monitors skin color changes in the treatment area by analyzing the RGB or HSV color space of the skin image, including signs of adverse reactions such as abnormal whitening (tissue coagulation caused by excessive energy), abnormal redness (congestion reaction), and purpura (subcutaneous hemorrhage).

[0086] When skin displacement exceeds the safety threshold or color abnormality is detected, the laser output is immediately paused and the negative pressure is increased to re-adhere the skin. The preset safety thresholds are: horizontal displacement exceeding 0.5 mm (which may cause scanning misalignment), focal length deviation corresponding to vertical displacement exceeding the allowable range, and color indicators exceeding the normal treatment response range. Once any abnormal condition is triggered, the main control module immediately sends a pause command to the laser output module to stop laser output, with a response time of less than 10 milliseconds, to avoid damage caused by continued light emission under abnormal conditions. At the same time, if the abnormality is caused by displacement or poor adhesion, the main control module automatically increases the negative pressure (the absolute value increases by 10 kPa to 20 kPa) to enhance the adhesion and make the skin re-adhere tightly to the light-emitting end face, eliminating displacement; if the abnormality is a color reaction, the negative pressure is maintained and the abnormality is recorded, awaiting operator confirmation.

[0087] After recalculating the actual focal length parameters and adjusting the negative pressure to the target range, laser output treatment is resumed. Following anomaly handling, the image acquisition module re-acquires skin images, calculates the current actual focal length parameters, and if the focal length deviates from the target range, the negative pressure adjustment process in step S102 is executed to readjust the focal length to the target range and stabilize it. Once the focal length is stable and the skin color returns to normal (or the operator confirms it can continue), the main control module regenerates the laser trigger permission signal and continues the remaining scanning treatment from the paused position, avoiding repeated scanning of already treated areas. The entire anomaly protection process is completed automatically without manual intervention from the operator. Simultaneously, the time, location, type, and processing result of the anomaly are recorded and stored in the treatment record for later reference. Through anomaly protection during treatment, displacement, poor adhesion, and abnormal skin reactions can be detected and addressed promptly, avoiding treatment errors or skin damage caused by continuous light output under abnormal conditions, significantly improving the safety and reliability of the treatment process.

[0088] In some embodiments, please refer to Figure 2 The adjustable laser therapy handpiece with negative pressure adsorption is a cylindrical handheld structure, including a main body 1 made of medical-grade polymer material with a non-slip surface. The main body integrates the laser optical path and various functional modules. A negative pressure adjustment interface 2 is located at the top of the outer shell for connecting to an external negative pressure source pipeline. The interface has a built-in proportional adjustment valve and pressure sensor, allowing the negative pressure to be electrically adjusted by the main control module. An image acquisition module 3 is located in the middle of the inner shell, employing a hidden miniature endoscope structure with the lens facing the light-emitting end face. It acquires skin images through a semi-transparent, semi-reflective mirror without obstructing the main laser optical path. Below the image acquisition module is a laser output module 4, including a field lens, a two-dimensional scanning galvanometer, and the optical path. The coupling interface is used to output and scan the laser beam; the front end of the handpiece is equipped with a funnel-shaped light-emitting end face 5, which is the end component that contacts the skin when the laser is emitted. The funnel structure ensures that the negative pressure airflow is evenly converged; a replaceable end contact head 6 is provided on the outer side of the light-emitting end face, which can be replaced with different diameters (such as 5 mm, 10 mm, 15 mm) according to the size of the lesion and the treatment site. The contact head is a disposable or sterilizable reusable part; the periphery of the light-emitting end face is arranged with annular negative pressure holes 7, with 8 to 16 holes evenly distributed, which are used to draw air to form a negative pressure environment and remove smoke and dust; the rear end of the handpiece is equipped with a connection interface 8, which integrates a laser fiber interface, a negative pressure pipeline interface and a data communication interface, for connecting the laser host and external equipment.

[0089] Please refer to Figure 3The main control module system architecture comprises the physical components of the handpiece on the left and the control logic on the right. The left side is the laser treatment handpiece housing, integrating image acquisition and laser output modules, with a light-emitting end face (annular negative pressure suction port) at the bottom for alignment with the skin at the treatment site. The right side is the main control module, containing four cascaded functional units: the first unit is for negative pressure adsorption and skin fixation, controlling the negative pressure module to generate negative pressure to adsorb the skin; the second unit is for skin image acquisition and curvature / focal length calculation, acquiring skin images through the image acquisition module and calculating curvature and actual focal length; the third unit is for adjusting the negative pressure and bringing the focal length close to the target value, adjusting the negative pressure module based on focal length deviation feedback to form a negative pressure-focal length closed loop; the fourth unit is for laser output treatment and continuous smoke extraction, outputting laser treatment once the focal length reaches the target value, while the negative pressure module continuously extracts smoke. Furthermore, the smoke adjustment and focusing unit adjusts the negative pressure suction force based on the smoke concentration in the optical path to ensure a clean optical path. The data flow of each unit is clear, forming a complete closed-loop control system from adsorption, detection, adjustment to treatment.

[0090] The complete treatment procedure is as follows: The first step involves the operator selecting and installing a replaceable end contact head of the corresponding diameter according to the size of the lesion, placing the light-emitting end face of the handpiece against the treatment area, activating the negative pressure adsorption module, drawing air from the annular negative pressure hole to create negative pressure, causing the skin to bulge and tightly adhere to the light-emitting end face, thus completing the adsorption and fixation.

[0091] The second step involves the hidden image acquisition module acquiring skin images, the main control module identifying structural markers, calculating the skin curvature distribution and protrusion height, and combining the optical path parameters to calculate the current actual focal length parameters.

[0092] The third step is to read the preset target focal length (or automatically generate it based on the lesion depth through the adaptive target focal length generation module), calculate the deviation between the actual focal length and the target focal length, adjust the negative pressure proportional valve according to the direction and magnitude of the deviation, change the degree of skin protrusion, and iteratively adjust until the actual focal length falls within the target allowable deviation range, and generate laser trigger permission.

[0093] The fourth step involves the operator triggering the laser output. The laser output module outputs the laser according to the preset energy parameters and scanning mode, and the galvanometer scans for fractional treatment. During the treatment, negative pressure continuously removes smoke and dust, and the image module continuously monitors the focal length and skin condition. If any abnormality occurs, the treatment will automatically pause and resume.

[0094] Fifth step: After the treatment is completed, turn off the laser, maintain negative pressure for a few seconds to remove residual smoke and dust, release the negative pressure, remove the handpiece, save the parameters and records of this treatment, and the treatment is complete.

[0095] In some embodiments, the method further includes: intelligent lesion identification and automatic recommendation of treatment parameters based on deep learning; collecting skin images before treatment; identifying the lesion type, depth and area through a deep learning model; automatically recommending matching treatment parameters such as laser energy, focal length, and scanning density; and executing the treatment after confirmation by the operator.

[0096] A lesion intelligent recognition model is constructed, employing a convolutional neural network architecture. Taking skin images as input, it outputs lesion type classification (melasma, age spots, freckles, tattoos, scars, telangiectasia, etc.), lesion region segmentation mask, depth level (superficial / intermediate / deep), and area and pigment density scores. The model is trained on a large amount of labeled clinical skin image data, combined with diagnostic annotations from dermatologists, to learn the correspondence between image features and depth for different lesions, achieving a recognition accuracy of no less than 90%. The model is deployed in the main control module or host computer, performing inference analysis on the acquired skin images before treatment.

[0097] Before treatment, the image acquisition module acquires initial skin images of the treatment area, inputs them into the intelligent lesion recognition model, and the model outputs analysis results such as lesion type, depth level, area, and pigment density. Based on the analysis results, the main control module automatically matches a recommended treatment plan from a preset treatment parameter library, including target focal length (based on depth level), single pulse energy (based on lesion type and pigment density), pulse frequency, scan density, scan pattern (automatically adapted to lesion shape), and number of treatment passes. The recommended plan is displayed on the host computer interface, along with the basis for the recommendation and precautions. The operator can directly confirm and adopt the plan, or manually fine-tune any parameters.

[0098] Once confirmed, the recommended target focal length is used as the preset target focal length for this treatment, and the energy and scanning parameters are used as laser output parameters, automatically loaded into the main control module. Through deep learning-based intelligent lesion recognition and automatic parameter recommendation, reliance on operator experience is reduced, improving the accuracy and consistency of treatment parameter settings. This is particularly suitable for inexperienced operators or scenarios with complex lesions, while also increasing pre-treatment preparation efficiency. After treatment, the images, parameters, and efficacy feedback are stored in the database for continuous model iteration and optimization, constantly improving recognition and recommendation accuracy.

[0099] In some embodiments, the method further includes: digital twin-based treatment process simulation and efficacy prediction, simulating the interaction between laser and skin tissue in a digital twin environment before treatment, predicting the thermal damage range and efficacy under different parameters, and optimizing treatment parameters before performing actual treatment.

[0100] A digital twin for laser skin treatment is constructed, comprising a multi-layered structural model of skin tissue (epidermis, papillary dermis, reticular dermis, and subcutaneous tissue), optical and thermal properties of each layer (absorption coefficient, scattering coefficient, thermal conductivity, specific heat capacity, and thermal damage threshold), a laser transmission and absorption model (Monte Carlo light transmission simulation), a heat conduction model (Pennes biothermal equation), and a thermal damage assessment model (Arrhenius integral). The digital twin can simulate the energy deposition distribution, spatiotemporal evolution of the temperature field, and the extent and degree of thermal damage in different skin layers under given laser parameters (wavelength, energy, pulse width, focal length, and scanning mode), predicting treatment efficacy and the risk of adverse reactions.

[0101] Before treatment, the lesion depth, area, and pigment density identified by the image acquisition module, along with the proposed treatment parameters (focal length, energy, scan density, etc.), are input into the digital twin. The entire treatment process is simulated in a virtual environment, outputting the predicted thermal damage depth, lateral damage range, lesion clearance rate, degree of normal tissue damage, and adverse reaction risk level (such as the probability of pigmentation, scarring, and blisters). The rationality of the parameter scheme is evaluated based on the simulation results: if the predicted damage depth is insufficient or the lesion clearance rate is low, it is recommended to increase the energy or deepen the focal length; if the predicted normal tissue damage is excessive or the risk of adverse reactions is high, it is recommended to decrease the energy or reduce the scan density. Through multiple simulation iterations, the optimal parameter combination balancing efficacy and safety is found.

[0102] After the optimized parameters are confirmed by the operator, they are used in actual treatment. During treatment, real-time collected skin temperature (estimated indirectly through infrared images or impedance) and focal length data are injected into the digital twin model to correct model parameters and dynamically update parameter predictions for subsequent treatment points, achieving real-time adaptive adjustment. Through digital twin simulation, the selection of treatment parameters can be upgraded from "experience-based trial and error" to "simulation verification," improving the predictability and controllability of treatment effects and reducing the risk of adverse reactions. This is especially suitable for high-risk treatment scenarios such as high-energy treatments and treatments for deep lesions.

[0103] In some embodiments, the method further includes: cross-institutional collaborative optimization of treatment parameters through federated learning, where the original skin data of each medical institution does not leave its local machine, but only the model gradient is uploaded, and after aggregation, the lesion identification and parameter recommendation model is globally optimized, thereby protecting patient privacy while improving treatment effectiveness.

[0104] A laser treatment parameter optimization model is constructed under a federated learning framework. Each treatment device or medical institution acts as a local node, storing local patient skin images, treatment parameters, and efficacy follow-up data. The original data remains on the local device, ensuring patient medical data privacy and security. A cloud-based federated coordination node is set up to be responsible for the aggregation, distribution, and iterative management of the global model. This node never accesses the original patient data, and all transmitted model gradients undergo differential privacy encryption to prevent gradients from being used to back-calculate the original data.

[0105] Each local node trains its local lesion identification model and treatment parameter recommendation model based on locally accumulated clinical data, learning the skin characteristics and optimal treatment parameter patterns of the local population. After training, only the model's parameter gradients are encrypted and uploaded to the coordinating node. The coordinating node performs weighted aggregation of the gradients uploaded by all nodes, with weights positively correlated with the data volume and model quality score of each node, generating an updated global baseline model, which is then encrypted and distributed to each local node. The aggregation process uses a secure aggregation protocol to ensure that the coordinating node cannot reverse-engineer the gradient information of any individual node.

[0106] After receiving the global model, each local node fine-tunes it based on the skin type, age distribution, and lesion characteristics of its local population, resulting in a locally optimized personalized model. This approach leverages the treatment experience from a multi-population global dataset while retaining the specificity of the local population. Through multiple rounds of federated iterations, the global model integrates extensive clinical experience from different regions, skin colors, age groups, and lesion types, exhibiting superior lesion recognition generalization ability and parameter recommendation accuracy. This allows for more reasonable initial treatment parameter recommendations for new equipment or less experienced institutions, shortening the learning curve. Simultaneously, all original patient data remains stored locally, complying with medical data privacy protection and compliance requirements, and avoiding the risk of leakage associated with centralized data storage.

[0107] Through federated learning and collaborative optimization, it is possible to aggregate clinical treatment experience from multiple institutions while protecting patient privacy, continuously improve the accuracy of lesion identification and parameter recommendation, and achieve a common improvement in the treatment level of the entire industry. It is especially suitable for scenarios such as chain medical aesthetic institutions and multi-center clinical collaboration.

[0108] In some embodiments, the method further includes: real-time monitoring and adaptive energy regulation of the treatment process through multimodal fusion, fusing multimodal data such as skin images, infrared temperature, impedance, and acoustic signals, monitoring the treatment response in real time, and dynamically adjusting the single-pulse energy according to the tissue response to achieve individualized and precise treatment.

[0109] A multimodal sensing unit is integrated into the handpiece. In addition to the image acquisition module, it includes a miniature infrared temperature sensor (monitoring changes in skin surface temperature), a bioimpedance detection electrode (detecting changes in skin impedance through contact with the light-emitting end face, reflecting tissue water content and the degree of thermal damage), and an acoustic sensor (monitoring the acoustic signal generated by the interaction between the laser and tissue, i.e., the photoacoustic effect, reflecting tissue vaporization and the degree of damage). The multimodal sensors and image acquisition are synchronized and time-stamped to form multimodal treatment monitoring data.

[0110] During treatment, multimodal data is fused and analyzed in real time: image data monitors skin color changes and displacement; infrared temperature data monitors the rate of skin surface temperature rise and peak temperature; impedance data monitors changes in tissue impedance (sudden impedance drops indicate a rapid change in tissue water content, potentially indicating excessive damage); and acoustic signals monitor the intensity and spectrum of the photoacoustic signal generated by each laser pulse (abnormal signal enhancement indicates excessive tissue vaporization or carbonization). A multimodal anomaly assessment model is established, integrating the characteristics of the four signals to assess the degree of tissue response at each scanning point in real time, classifying it into four levels: normal response, mild overreaction, moderate overreaction, and severe overreaction.

[0111] The laser energy at subsequent scanning points is adaptively adjusted based on the real-time tissue response level: For normal responses, the preset energy is maintained; for mild overreaction, the energy is appropriately reduced by 5% to 10%; for moderate overreaction, the energy is reduced by 10% to 20% and the pulse interval is extended; for severe overreaction, treatment of that area is immediately paused, skipping that point and continuing to subsequent areas, while recording any abnormalities. Energy adjustment is performed in real-time on a per-scan basis, with the energy at each point dynamically adjusted based on the tissue response at the preceding points. This achieves individualized, precise treatment based on "energy delivery according to tissue response," avoiding overtreatment or undertreatment of certain areas due to fixed energy levels.

[0112] Multimodal data and energy adjustment records are simultaneously stored in the treatment log, and a treatment response heatmap is generated after treatment for operator evaluation. Through real-time monitoring and adaptive energy regulation via multimodal fusion, the treatment energy can be dynamically adjusted according to the actual tissue response of each patient and each area, significantly improving the accuracy and safety of treatment, reducing adverse reactions, and making it particularly suitable for challenging treatment scenarios with complex skin types and heterogeneous lesions.

[0113] Please see Figure 4 As shown, Figure 4This is a schematic diagram of the structure of the adjustable laser therapy system 200 with negative pressure adsorption provided in this application embodiment. The adjustable laser therapy system 200 with negative pressure adsorption is used to perform the steps of the adjustable laser therapy methods with negative pressure adsorption shown in the above embodiments. The adjustable laser therapy system 200 with negative pressure adsorption can be a single server or a server cluster, or it can be a terminal, such as a handheld terminal, a laptop computer, a wearable device, or a robot.

[0114] like Figure 4 As shown, the adjustable laser therapy system 200 with negative pressure adsorption includes: The parameter calculation unit 201 is used to apply negative pressure to the skin of the treatment site through the negative pressure adsorption module, so that the skin of the treatment site is adsorbed and fixed to the light-emitting end face of the handpiece; the image acquisition module acquires the image of the skin of the treatment site in the adsorption state, and calculates the current skin curvature and actual focal length parameters based on the skin image. The parameter changing unit 202 is used to compare the actual focal length parameter with the preset target focal length parameter, and adjust the negative pressure of the negative pressure adsorption module according to the comparison result, so as to make the actual focal length parameter approach the target focal length parameter by changing the degree of skin protrusion. The smoke and dust extraction unit 203 is used to control the laser output module to output laser to the treatment site for treatment when the actual focal length parameter reaches the allowable deviation range of the target focal length parameter. During the treatment process, the negative pressure adsorption module continuously extracts the smoke and dust generated by the laser irradiation.

[0115] In some embodiments, applying negative pressure to the skin at the treatment site using the negative pressure adsorption module to adsorb and fix the skin at the treatment site to the light-emitting end face of the handpiece includes: attaching the light-emitting end face of the handpiece to the surface of the skin at the treatment site; activating the negative pressure adsorption module to extract air through the negative pressure holes arranged around the light-emitting end face to create a negative pressure environment inside the handpiece; and causing the skin at the treatment site to bulge towards the light-emitting end face and adhere tightly under the negative pressure, thus completing the adsorption and fixation of the treatment site.

[0116] In some embodiments, the step of acquiring skin images of the treatment site in the adsorption state through an image acquisition module and calculating the current skin curvature and actual focal length parameters based on the skin images includes: capturing skin images of the treatment site in the adsorption state through an image acquisition module hidden inside the handpiece; identifying structural markers in the skin images and calculating the curvature distribution of the skin surface based on the positional offset of the markers; and calculating the actual focal length parameters from the current laser focus to the skin surface based on the curvature distribution and preset parameters of the handpiece's optical path.

[0117] In some embodiments, comparing the actual focal length parameter with the preset target focal length parameter and adjusting the negative pressure of the negative pressure adsorption module according to the comparison result includes: reading the preset target focal length parameter and calculating the deviation value between the actual focal length parameter and the target focal length parameter; determining the negative pressure adjustment direction and adjustment range according to the sign and magnitude of the deviation value; and outputting a control signal to the negative pressure adsorption module according to the adjustment direction and adjustment range to increase or decrease the negative pressure value.

[0118] In some embodiments, the step of changing the degree of skin protrusion to make the actual focal length parameter approach the target focal length parameter includes: when the negative pressure value increases, the degree of protrusion of the skin at the treatment site towards the light-emitting end face increases, and the distance between the skin surface and the laser focus shortens; when the negative pressure value decreases, the degree of protrusion of the skin at the treatment site decreases, and the distance between the skin surface and the laser focus increases; by continuously adjusting the negative pressure value, the actual focal length parameter gradually approaches the target focal length parameter.

[0119] In some embodiments, controlling the laser output module to output laser to the treatment site for treatment when the actual focal length parameter reaches the allowable deviation range of the target focal length parameter includes: real-time monitoring of the deviation value between the actual focal length parameter and the target focal length parameter; generating a laser trigger permission signal when the deviation value falls within the preset allowable deviation range; and controlling the laser output module to output a laser beam to the treatment site for fractional scanning treatment according to the preset treatment energy parameters and scanning mode.

[0120] In some embodiments, the negative pressure adsorption module continuously removes the smoke and dust generated by laser irradiation during the treatment process, including: during laser treatment, the negative pressure adsorption module remains in operation; the smoke and dust generated by laser irradiation on the skin are removed from the light output area under the action of negative pressure airflow; the smoke and dust are discharged outside the handpiece through the negative pressure pipeline with the negative pressure airflow, maintaining the cleanliness of the light output path.

[0121] In some embodiments, the method further includes an adaptive target focal length generation step: before treatment, an initial skin image of the treatment site is acquired through an image acquisition module to identify the size and depth level of the lesion area; the corresponding treatment layer is matched according to the lesion depth level, and a target focal length parameter adapted to the current lesion is generated in combination with the handpiece optical path parameters; the generated target focal length parameter is used as the preset target focal length parameter for this treatment.

[0122] In some embodiments, the method further includes a treatment process abnormality protection step: during the treatment process, skin images are continuously acquired through the image acquisition module to monitor changes in skin color and displacement; when skin displacement exceeds a safety threshold or color abnormality is detected, the laser output is immediately paused and the negative pressure value is increased to allow the skin to re-adhere; after recalculating the actual focal length parameters and adjusting the negative pressure to the target range, the laser output treatment is resumed.

[0123] It should be noted that those skilled in the art will understand that, for the sake of convenience and brevity, the specific working process of the adjustable laser therapy system with negative pressure adsorption and each module described above can be referred to the corresponding content in the various embodiments of the adjustable laser therapy method with negative pressure adsorption described above, and will not be repeated here.

[0124] The aforementioned adjustable laser therapy method with negative pressure adsorption can be implemented as a computer program, which can, for example... Figure 4 It runs on the system shown.

[0125] Please see Figure 5 , Figure 5 This is a schematic block diagram of the main control module provided in an embodiment of this application. The main control module includes a processor, a memory, and a network interface connected via a device bus, wherein the memory may include a storage medium and internal memory.

[0126] The storage medium can store operating devices and computer programs. The computer program includes program instructions that, when executed, cause the processor to perform any adjustable laser therapy method with negative pressure adsorption.

[0127] The processor provides computing and control capabilities to support the operation of the entire main control module.

[0128] The internal memory provides an environment for the execution of computer programs in non-volatile storage media. When the computer program is executed by the processor, it enables the processor to perform any adjustable laser treatment method with negative pressure adsorption.

[0129] This network interface is used for network communication, such as sending assigned tasks. Those skilled in the art will understand that... Figure 5 The structure shown is merely a block diagram of a portion of the structure related to the solution of this application and does not constitute a limitation on the terminal to which the solution of this application is applied. The specific main control module may include more or fewer components than shown in the figure, or combine certain components, or have different component arrangements.

[0130] It should be understood that the processor can be a Central Processing Unit (CPU), but it can also be other general-purpose processors, digital signal processors (DSPs), application-specific integrated circuits (ASICs), field-programmable gate arrays (FPGAs), or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components, etc. Among these, a general-purpose processor can be a microprocessor or any conventional processor.

[0131] In one embodiment, the processor is configured to run a computer program stored in memory to perform the following steps: The negative pressure adsorption module applies negative pressure to the skin at the treatment site, causing the skin to adhere and fix to the light-emitting end face of the handpiece; the image acquisition module acquires images of the skin at the treatment site in the adsorption state, and calculates the current skin curvature and actual focal length parameters based on the skin images; The actual focal length parameter is compared with the preset target focal length parameter. The negative pressure of the negative pressure adsorption module is adjusted according to the comparison result. By changing the degree of skin protrusion, the actual focal length parameter is made closer to the target focal length parameter. When the actual focal length parameter reaches the allowable deviation range of the target focal length parameter, the laser output module is controlled to output laser to the treatment site for treatment. During the treatment process, the negative pressure adsorption module continuously removes the smoke and dust generated by the laser irradiation.

[0132] In some embodiments, applying negative pressure to the skin at the treatment site using the negative pressure adsorption module to adsorb and fix the skin at the treatment site to the light-emitting end face of the handpiece includes: attaching the light-emitting end face of the handpiece to the surface of the skin at the treatment site; activating the negative pressure adsorption module to extract air through the negative pressure holes arranged around the light-emitting end face to create a negative pressure environment inside the handpiece; and causing the skin at the treatment site to bulge towards the light-emitting end face and adhere tightly under the negative pressure, thus completing the adsorption and fixation of the treatment site.

[0133] In some embodiments, the step of acquiring skin images of the treatment site in the adsorption state through an image acquisition module and calculating the current skin curvature and actual focal length parameters based on the skin images includes: capturing skin images of the treatment site in the adsorption state through an image acquisition module hidden inside the handpiece; identifying structural markers in the skin images and calculating the curvature distribution of the skin surface based on the positional offset of the markers; and calculating the actual focal length parameters from the current laser focus to the skin surface based on the curvature distribution and preset parameters of the handpiece's optical path.

[0134] In some embodiments, comparing the actual focal length parameter with the preset target focal length parameter and adjusting the negative pressure of the negative pressure adsorption module according to the comparison result includes: reading the preset target focal length parameter and calculating the deviation value between the actual focal length parameter and the target focal length parameter; determining the negative pressure adjustment direction and adjustment range according to the sign and magnitude of the deviation value; and outputting a control signal to the negative pressure adsorption module according to the adjustment direction and adjustment range to increase or decrease the negative pressure value.

[0135] In some embodiments, the step of changing the degree of skin protrusion to make the actual focal length parameter approach the target focal length parameter includes: when the negative pressure value increases, the degree of protrusion of the skin at the treatment site towards the light-emitting end face increases, and the distance between the skin surface and the laser focus shortens; when the negative pressure value decreases, the degree of protrusion of the skin at the treatment site decreases, and the distance between the skin surface and the laser focus increases; by continuously adjusting the negative pressure value, the actual focal length parameter gradually approaches the target focal length parameter.

[0136] In some embodiments, controlling the laser output module to output laser to the treatment site for treatment when the actual focal length parameter reaches the allowable deviation range of the target focal length parameter includes: real-time monitoring of the deviation value between the actual focal length parameter and the target focal length parameter; generating a laser trigger permission signal when the deviation value falls within the preset allowable deviation range; and controlling the laser output module to output a laser beam to the treatment site for fractional scanning treatment according to the preset treatment energy parameters and scanning mode.

[0137] In some embodiments, the negative pressure adsorption module continuously removes the smoke and dust generated by laser irradiation during the treatment process, including: during laser treatment, the negative pressure adsorption module remains in operation; the smoke and dust generated by laser irradiation on the skin are removed from the light output area under the action of negative pressure airflow; the smoke and dust are discharged outside the handpiece through the negative pressure pipeline with the negative pressure airflow, maintaining the cleanliness of the light output path.

[0138] In some embodiments, the method further includes an adaptive target focal length generation step: before treatment, an initial skin image of the treatment site is acquired through an image acquisition module to identify the size and depth level of the lesion area; the corresponding treatment layer is matched according to the lesion depth level, and a target focal length parameter adapted to the current lesion is generated in combination with the handpiece optical path parameters; the generated target focal length parameter is used as the preset target focal length parameter for this treatment.

[0139] In some embodiments, the method further includes a treatment process abnormality protection step: during the treatment process, skin images are continuously acquired through the image acquisition module to monitor changes in skin color and displacement; when skin displacement exceeds a safety threshold or color abnormality is detected, the laser output is immediately paused and the negative pressure value is increased to allow the skin to re-adhere; after recalculating the actual focal length parameters and adjusting the negative pressure to the target range, the laser output treatment is resumed.

[0140] This application also provides a computer-readable storage medium storing a computer program that, when executed by a processor, causes the processor to perform the steps of the adjustable laser therapy method with negative pressure adsorption as provided in any embodiment of this application.

[0141] The computer-readable storage medium can be an internal storage unit of the main control module as described in the foregoing embodiments, such as the hard disk or memory of the main control module. Alternatively, the computer-readable storage medium can be an external storage device of the main control module, such as a plug-in hard disk, Smart Media Card (SMC), Secure Digital (SD) card, or Flash Card equipped on the main control module.

[0142] The above description is merely a specific embodiment of this application, but the scope of protection of this application is not limited thereto. Any person skilled in the art can easily conceive of various equivalent modifications or substitutions within the technical scope disclosed in this application, and these modifications or substitutions should all be covered within the scope of protection of this application. Therefore, the scope of protection of this application should be determined by the scope of the claims.

Claims

1. An adjustable laser therapy method with negative pressure adsorption, applied to an adjustable laser therapy handpiece device with negative pressure adsorption, wherein the adjustable laser therapy handpiece device comprises a negative pressure adsorption module, an image acquisition module, a main control module, and a laser output module, characterized in that, include: The negative pressure adsorption module applies negative pressure to the skin at the treatment site, causing the skin at the treatment site to be adsorbed and fixed to the light-emitting end face of the handpiece; The image acquisition module acquires skin images of the treatment area under adsorption conditions, and calculates the current skin curvature and actual focal length parameters based on the skin images. The actual focal length parameter is compared with the preset target focal length parameter. The negative pressure of the negative pressure adsorption module is adjusted according to the comparison result. By changing the degree of skin protrusion, the actual focal length parameter is made closer to the target focal length parameter. When the actual focal length parameter reaches the allowable deviation range of the target focal length parameter, the laser output module is controlled to output laser to the treatment site for treatment. During the treatment process, the negative pressure adsorption module continuously removes the smoke and dust generated by the laser irradiation.

2. The method according to claim 1, characterized in that, The process of applying negative pressure to the skin at the treatment site via a negative pressure adsorption module, causing the skin at the treatment site to adhere and fix to the light-emitting end face of the handpiece, includes: Place the light-emitting end of the handpiece against the skin surface of the treatment area; Activate the negative pressure adsorption module to draw air out through the negative pressure holes arranged around the light-emitting end face, creating a negative pressure environment inside the handpiece. Under negative pressure, the skin at the treatment site bulges towards the light-emitting end face and adheres tightly, thus completing the adsorption and fixation of the treatment site.

3. The method according to claim 1, characterized in that, The process involves acquiring skin images of the treatment area under adsorption conditions via an image acquisition module, and calculating the current skin curvature and actual focal length parameters based on the skin images, including: The image acquisition module, hidden inside the handpiece, captures images of the skin at the treatment site during the adsorption state. Identify structural markers in skin images and calculate the curvature distribution of the skin surface based on the positional offset of the markers; Based on the curvature distribution and the preset parameters of the handpiece optical path, the actual focal length parameters from the current laser focus to the skin surface are calculated.

4. The method according to claim 1, characterized in that, The step of comparing the actual focal length parameter with the preset target focal length parameter and adjusting the negative pressure of the negative pressure adsorption module according to the comparison result includes: Read the preset target focal length parameters and calculate the deviation between the actual focal length parameters and the target focal length parameters; The direction and magnitude of the negative pressure adjustment are determined based on the sign and magnitude of the deviation. The system outputs control signals to the negative pressure adsorption module according to the adjustment direction and amplitude, thereby increasing or decreasing the negative pressure value.

5. The method according to claim 4, characterized in that, The method of adjusting the skin's protrusion to make the actual focal length parameter approach the target focal length parameter includes: When the negative pressure value increases, the degree of skin protrusion towards the light-emitting end face at the treatment site increases, and the distance between the skin surface and the laser focus shortens; When the negative pressure value decreases, the degree of skin protrusion at the treatment site decreases, and the distance between the skin surface and the laser focus increases; By continuously adjusting the negative pressure value, the actual focal length parameter gradually approaches the target focal length parameter.

6. The method according to claim 1, characterized in that, When the actual focal length parameter reaches the allowable deviation range of the target focal length parameter, the laser output module is controlled to output laser to the treatment site for treatment, including: Real-time monitoring of the deviation between the actual focal length parameter and the target focal length parameter; When the deviation value falls within the preset allowable deviation range, a laser trigger permission signal is generated; Based on the preset treatment energy parameters and scanning mode, the laser output module is controlled to output a laser beam to the treatment area for fractional scanning treatment.

7. The method according to claim 6, characterized in that, During the treatment process, the negative pressure adsorption module continuously removes the smoke and dust generated by laser irradiation, including: During laser treatment, the negative pressure adsorption module remains operational; The smoke and dust generated by laser irradiation on the skin are drawn out of the light area under the action of negative pressure airflow; The smoke and dust are discharged from the outside of the handpiece through the negative pressure pipeline along with the negative pressure airflow, maintaining the cleanliness of the light output path.

8. The method according to claim 1, characterized in that, The method further includes an adaptive target focal length generation step: Before treatment, an initial skin image of the treatment area is acquired using an image acquisition module to identify the size and depth level of the lesion area; Based on the depth level of the lesion, the corresponding treatment layer is matched, and the target focal length parameters that are adapted to the current lesion are generated by combining the optical path parameters of the handpiece. The generated target focal length parameters will be used as the preset target focal length parameters for this treatment.

9. The method according to claim 1, characterized in that, The method also includes steps to protect against abnormalities during the treatment process: During the treatment, skin images are continuously acquired through the image acquisition module to monitor changes in skin color and displacement. If skin displacement exceeds the safety threshold or color abnormality is detected, immediately pause the laser output and increase the negative pressure to re-adhere the skin. After recalculating the actual focal length parameters and adjusting the negative pressure to the target range, laser output treatment is resumed.

10. An adjustable laser therapy handpiece device with negative pressure adsorption, used to implement the method as described in any one of claims 1-9, characterized in that, It includes a negative pressure adsorption module, an image acquisition module, a main control module, and a laser output module.

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