Laser device for acne treatment based on lipid and moisture detection and method for determining parameters

Abstract

This invention discloses an acne laser treatment device and parameter determination method based on lipid and moisture detection, belonging to the field of adjunctive therapy technology. The device includes a laser module, a light receiving module, a signal processing module, and a control system. The laser module emits therapeutic and indicator light towards the target skin area. The light receiving module collects the light signals of the therapeutic and indicator light reflected from the target skin area. The signal processing module calculates the lipid and water volume fractions of the target skin area based on the incident and reflected light intensities. The control system inputs the lipid and water volume fractions into a pre-established neural network model to obtain a combination of laser treatment parameters. This device helps improve treatment accuracy and provides patients with personalized and precise treatment plans.

Description

Technical Field

[0001] This application relates to the field of adjunctive therapy technology, and in particular to an acne laser treatment device and parameter determination method based on lipid and moisture detection. Background Technology

[0002] Laser therapy has become an important treatment for acne. Its mechanism of action involves the photothermal effect generated in tissues under laser irradiation, which then acts on the sebaceous glands to inhibit sebum secretion. While commonly used equipment wavelengths (such as 1064nm or 1450nm) have some absorption for lipids, their primary target chromophore is water in the skin, which can easily lead to insufficient treatment precision and the risk of thermal damage. The volume fractions of lipids and water are closely related to the physiological activity of sebaceous glands and the overall skin condition, serving as key indicators for assessing acne severity and objectively determining parameters for laser treatment. Accurately and conveniently obtaining this volume fraction information, which characterizes skin condition, is crucial for personalized adjustment of laser parameters and optimization of treatment dosage and safety.

[0003] However, existing treatment devices generally lack the ability to detect lipids and water in real time. Treatment parameters often rely on operator experience or fixed protocols, making dynamic adjustments based on individual skin conditions impossible, thus limiting personalized and optimized treatment. Before clinical treatment, the Sebumeter sebum analyzer is often used, measuring lipid content based on photometry after applying matte adhesive tape. However, this is only used for disease diagnosis and does not guide parameter selection during laser treatment. Water content is measured using capacitance and conductivity methods, which require skin contact and are affected by contact area, applied pressure, and measurement time. Although some research and patented solutions have attempted to introduce technologies such as multispectral imaging to assess skin composition, aiming to obtain absolute information on the content of lipids and water through non-contact methods, this method involves complex measurement and calculation processes. Content calculations often require the introduction of predicted volume parameters, introducing estimation errors. Summary of the Invention

[0004] Therefore, it is necessary to provide an acne laser treatment device and parameter determination method based on lipid and moisture detection to address the above-mentioned technical problems.

[0005] The following technical solution is adopted in this specification: This specification provides an acne laser treatment device based on lipid and moisture detection. The device includes: a laser module, a light receiving module, a signal processing module, and a control system. The laser module is used to emit therapeutic and indicator light to the target skin area; the wavelength of the therapeutic light corresponds to the absorption peak of lipids, and the wavelength of the indicator light belongs to the visible light band. The light receiving module is used to collect the light signals of the therapeutic light and the indicator light reflected by the target skin area and transmit them to the signal processing module; The signal processing module is used to determine the incident and reflected light intensities of the treatment light and indicator light based on the light signals emitted and reflected by the treatment light and indicator light, and to calculate the volume fractions of lipids and water in the target skin area. The formula for calculating the volume fractions of lipids and water is based on the relationship between light energy and target chromophores in the skin, as well as the fact that the absorption rate of melanin is multiple of the absorption rate of lipids, and the absorption rate of hemoglobin is multiple of the absorption rate of water. Target chromophores include water, lipids, hemoglobin, and melanin. The control system is used to input the volume fractions of lipids and water into a pre-established neural network model to obtain a combination of laser treatment parameters; the laser module generates a treatment beam according to the combination of laser treatment parameters.

[0006] Optionally, the formula for calculating the volume fractions of lipids and water is as follows: in, This represents the volume fraction of lipids. This represents the volume fraction of water. , These are the absorption coefficients of lipids and water at the therapeutic light wavelength, respectively. , These are the absorption coefficients of lipids and water at the indicated light wavelengths, respectively. , These are the reduced scattering coefficients under the treatment wavelength and the indicator wavelength laser, respectively. ∈[0.1, 15](cm) -1 ), ∈[1, 150](cm) -1 ), ∈[3×10 -3 ,0.1](cm -1 ), ∈[3×10 -5 ,0.1](cm -1 ), ∈[1, 10](cm) -1 ), ∈[15, 50](cm) -1 ); , These represent the incident light intensity at the therapeutic light wavelength and the indicator light wavelength, respectively. , These represent the reflected light intensity at the treatment wavelength and the indicator wavelength, respectively; the absorption rate of melanin at the treatment wavelength is that of lipids. a1 times, a 1∈(0,1]; the absorption rate of hemoglobin at the therapeutic wavelength is that of water. b 1 times, b 1∈(0,1]; the absorption rate of melanin at the indicated light wavelength is that of lipids. a 2 times, a 2∈[10 4 10 5 The absorbance of hemoglobin at the indicator wavelength is that of water. b 2 times, b 2∈[1, 10] 5 ].

[0007] Optionally, the laser module includes a laser, a laser driver, and a beam shaping mirror assembly; the laser driver is electrically connected to the control system; a beam splitter is provided at the rear end of the beam shaping mirror assembly; The laser driver is used to receive and execute start / stop commands and parameter adjustment commands from the control system, and to control the laser to emit coaxial therapeutic and indicator beams. The beam shaping lens assembly is used for collimation, focusing, and spot homogenization, and allows the treatment beam and indicator beam to be directly projected onto the skin via a beam splitter for positioning and treatment.

[0008] Optionally, the optical receiving module includes a photodetector and is equipped with a filter; The photodetector is used to collect reflected light signals from the therapeutic light and the indicator light, convert them into electrical signals and send them to the signal processing module, and to collect incident light directly incident through the beam splitter to obtain the incident light intensity. The signal processing module is used to filter and denoise the raw electrical signal, determine the intensity of reflected light, and calculate the volume fraction of lipids and water in the target skin area based on the incident light intensity and the intensity of reflected light.

[0009] Optionally, the neural network model includes support vector machine regression algorithm and Naive Bayes classification algorithm; The control system is also used to input the volume fractions of lipids and water and the optical properties of the skin into the support vector machine regression algorithm to obtain the combination of laser treatment parameters, and to input the volume fractions of lipids and water, the optical properties of the skin and the combination of laser treatment parameters into the Naive Bayes classification algorithm to obtain the predicted thermal damage risk level; the optical properties of the skin include the absorption coefficient and the reduced scattering coefficient.

[0010] Optionally, the device also includes a cooling module, which includes a TEC cooling chip, a contact cooling component, and a sapphire window. The TEC cooling chip is electrically connected to the control system. The contact cooling component is made of metal with a hollowed-out center at the front end, into which a sapphire window is embedded. TEC cooling elements are used to receive cooling parameter adjustment commands sent by the control system; The contact cooling component is a rotatable structure. When measuring the volume fraction of lipids and water, the contact cooling component is rotated to a position that does not affect the illumination and reception of light signals, and the front end of the handpiece is placed against the skin surface. The measurement distance is consistent with the distance from the sapphire window to the light outlet.

[0011] Optionally, the device includes a human-machine interaction module, which includes a touch screen, operation buttons, and is electrically connected to the control system. The touch screen is used to select the detection mode or treatment mode, as well as to adjust and input the laser parameters and cooling parameters. The control system then transmits the adjustment commands to the laser module or cooling module. The operation buttons are used for light emission control, and the measurement program is started via the touch screen when measuring the volume fraction of lipids and water.

[0012] Optionally, the therapeutic light wavelength ranges from 1.2 to 2 μm, and the indicator light wavelength ranges from 380 to 780 nm.

[0013] This specification provides a method for determining parameters of acne laser treatment based on lipid and moisture detection. This method is applied to the aforementioned device and includes: It emits therapeutic light and indicator light towards the target skin area; the wavelength of the therapeutic light corresponds to the absorption peak of lipids, and the wavelength of the indicator light belongs to the visible light band; Acquire the light signals of the therapeutic light and the indicator light reflected from the target skin area; The incident light intensity and reflected light intensity of the therapeutic light and indicator light are determined based on the light signals emitted and reflected by the therapeutic light and indicator light. The volume fractions of lipids and water in the target skin region are calculated based on the incident and reflected light intensities of the therapeutic and indicator light. The formulas for calculating the volume fractions of lipids and water are based on the relationship between light energy and target chromophores in the skin, as well as the fact that the absorption rates of melanin and lipids are multiples of each other, and the absorption rates of hemoglobin and water are multiples of each other. Target chromophores include water, lipids, hemoglobin, and melanin. The volume fractions of lipids and water are input into a pre-established neural network model to obtain a combination of laser treatment parameters; this combination of laser treatment parameters is used to generate a treatment beam for the target skin area.

[0014] This specification provides a computer-readable storage medium storing a computer program that, when executed by a processor, implements the above-described method for determining acne laser treatment parameters based on lipid and moisture detection.

[0015] This specification provides a computer device, including a memory, a processor, and a computer program stored in the memory and executable on the processor, wherein the processor executes the program to implement the above-described method for determining acne laser treatment parameters based on lipid and moisture detection.

[0016] The above-mentioned technical solutions adopted in this specification can achieve the following beneficial effects: This device first uses the therapeutic light and indicator light for acne treatment as detection light for lipids and water. Based on the incident and reflected light intensities, it obtains the volume fraction of lipids and water in the target skin area. When calculating the volume fraction of lipids and water, it considers not only target chromophores in facial skin (water and lipids) but also hemoglobin and melanin. Thus, by constructing formulas for calculating the volume fraction of lipids and water based on the relationship between light energy and target chromophores in the skin, and the proportional relationship between the absorption rates of melanin and lipids, and hemoglobin and water, the volume fraction of lipids and water is calculated. Then, the optimal combination of laser treatment parameters is selected based on the volume fraction values. This device can determine the combination of laser treatment parameters by calculating the volume fraction of lipids and water in the target skin area, achieving adaptive adjustment of laser treatment parameters. This device helps improve treatment accuracy and provides patients with personalized and precise treatment plans.

[0017] The innovations of this invention are as follows: ① Existing methods typically require irradiating the skin with 4-6 different wavelengths of light, and then obtaining lipid content by analyzing the reflected light signals. In this invention, the therapeutic light and indicator light are simultaneously the detection light for lipids and water, eliminating the need for additional light sources. ② This invention obtains the volume fractions of lipids and water through optical methods, which is simpler and more convenient to calculate than numerical content and requires no imaging structure. ③ This device can screen for optimal therapeutic light parameters based on the volume fractions of lipids and water and achieve adaptive adjustment of the light parameters. This device will help improve treatment accuracy and effectiveness, providing patients with personalized and precise treatment plans. Attached Figure Description

[0018] The accompanying drawings, which are included to provide a further understanding of this application and form part of this application, illustrate exemplary embodiments and are used to explain this application, but do not constitute an undue limitation of this application. In the drawings:

[0019] Figure 1 This is a schematic diagram of the structure of an acne laser treatment device based on lipid and moisture detection, as provided in this specification. Figure 2 This is a schematic diagram of a method for determining parameters for acne laser treatment based on lipid and moisture detection, as provided in this specification. Figure 3This is a schematic diagram of a computer device for implementing a method for determining parameters of acne laser treatment based on lipid and moisture detection, as provided in this specification. Detailed Implementation

[0020] To make the objectives, technical solutions, and advantages of this specification clearer, the technical solutions of this application will be clearly and completely described below in conjunction with specific embodiments and corresponding drawings. Obviously, the described embodiments are only a part of the embodiments of this application, and not all of them. All other embodiments obtained by those skilled in the art based on the embodiments in this specification without creative effort are within the scope of protection of this application.

[0021] Based on this, the present invention provides an acne laser treatment device and parameter determination method based on lipid and moisture detection. The device uses a laser with a lipid absorption peak wavelength of 1.2-2 μm as the treatment light, such as 1726 nm, which is the absorption peak of lipids and 1.8 times that of water, allowing for targeted action on sebum. Simultaneously, coaxial visible light of 380-780 nm is used as an indicator light, such as 650 nm, where sebum absorption is low. Before treatment, lipid and moisture levels are detected. Small amounts of treatment light and indicator light are emitted simultaneously or sequentially. The intensity of the light signal reflected by the skin in the detection area is obtained through signal acquisition and comparative analysis. Based on the difference in absorption and scattering of these two wavelengths by the skin, the volume fraction of lipids and water in that area is calculated. Then, a suitable treatment light parameter is selected through a deep learning-based "volume fraction-light parameter-thermal damage" relationship, and the laser parameters are adjusted in real time. During treatment, the indicator light remains constantly lit to locate and aim at the treatment area, while the treatment light operates according to the set light parameters. These laser parameters include, but are not limited to, laser power, pulse width, repetition rate, and treatment time.

[0022] The technical solutions provided by the various embodiments of this application are described in detail below with reference to the accompanying drawings.

[0023] Figure 1 This is a schematic diagram of the structure of an acne laser treatment device based on lipid and moisture detection, as described in this specification. The device includes: a laser module, a light receiving module, a signal processing module, and a control system.

[0024] The laser module is used to emit therapeutic light and indicator light to the target skin area; the wavelength of the therapeutic light corresponds to the absorption peak of lipids, and the wavelength of the indicator light belongs to the visible light band; optionally, the wavelength range of the therapeutic light is 1.2-2μm, and the wavelength range of the indicator light is 380-780nm.

[0025] The laser module includes a laser, a laser driver, and a beam shaping mirror assembly; the laser driver is electrically connected to the control system; and a beam splitter is located at the rear end of the beam shaping mirror assembly.

[0026] The laser driver is used to receive and execute start / stop commands and parameter adjustment commands from the control system, and to control the laser to emit coaxial therapeutic and indicator beams.

[0027] The beam shaping lens assembly is used for collimation, focusing, and spot homogenization, allowing the treatment laser and indicator laser to be directly projected onto the skin via a beam splitter for positioning and treatment. The spot size is 1-10mm. A beam splitter is located at the rear end of the beam shaping lens assembly in the laser module. This beam splitter allows most of the treatment and indicator laser light to be directly projected onto the skin for positioning and treatment, while a small portion is incident on a photodetector, which then obtains the intensity information of the incident light.

[0028] Lasers can be of various types, such as semiconductor lasers, fiber lasers, and solid-state lasers, and are used to emit coaxial therapeutic and indicator light. The two wavelengths can be output individually or simultaneously.

[0029] The light receiving module is used to collect the light signals of the therapeutic light and the indicator light reflected by the target skin area and transmit them to the signal processing module.

[0030] The light receiving module includes a photodetector and a filter. The photodetector is used to collect reflected light signals from the therapeutic light and the indicator light, convert them into electrical signals and send them to the signal processing module, and to collect incident light directly incident through a beam splitter to obtain the incident light intensity. The signal processing module is used to filter and denoise the raw electrical signal, determine the reflected light intensity, and calculate the volume fraction of lipids and water in the target skin area based on the incident light intensity and the reflected light intensity.

[0031] Optionally, the light receiving module is equipped with a filter and acquires the reflected light signals of the therapeutic light and the indicator light respectively through a photodetector. This module is located at the laser output port.

[0032] The signal processing module is used to determine the incident light intensity and reflected light intensity of the treatment light and indicator light based on the light signals emitted and reflected by the treatment light and indicator light, and to calculate the volume fraction of lipids and water in the target skin area. The formula for calculating the volume fraction of lipids and water is constructed based on the relationship between light energy and target chromophores in the skin, as well as the fact that the absorption rate of melanin is multiple of the absorption rate of lipids, and the absorption rate of hemoglobin is multiple of the absorption rate of water. Target chromophores include water, lipids, hemoglobin, and melanin.

[0033] In addition to water and lipids, the target chromophores in facial skin also include hemoglobin and melanin. According to Lambert-Beer's law, the relationship between light energy and target chromophores is as follows:

[0034] in, , These are the reduced scattering coefficients under the treatment light wavelength and the indicator light wavelength laser, respectively; , , , These are the absorption coefficients of lipids, water, hemoglobin, and melanin at the therapeutic light wavelength, respectively. , , , These are the absorption coefficients of lipids, water, hemoglobin, and melanin at the indicated light wavelength, respectively. , , , These represent the volume fractions of lipids, water, hemoglobin, and melanin, respectively. , These refer to the penetration depth of the therapeutic light and the indicator light in the tissue, respectively. , These represent the incident light intensity at the therapeutic light wavelength and the indicator light wavelength, respectively. , These are the reflected light intensities at the therapeutic light wavelength and the indicator light wavelength, respectively.

[0035] Among them, the absorption rate of melanin at the therapeutic wavelength is that of lipids. a 1 times, a 1∈(0,1]; the absorption rate of hemoglobin is that of water. b 1 times, b 1∈(0,1). The absorbance of melanin at the indicated light wavelength is that of lipids. a 2 times, a 2∈[10 4 10 5 The absorption rate of hemoglobin is [missing information - likely a percentage] of water. b 2 times, b 2∈[1, 10] 5 ]. a 1、 a 2、 b 1、 b 2 is a constant, and the effect of hemoglobin and melanin absorption on light signals is quantified by the absorption ratio with lipids and water.

[0036] Preferably, in one embodiment, 1.7 μm is used as the treatment light and 690 nm is used as the indicator light. a 1≈8.9×10 -5 , b 1≈0.024, a 2≈6.7×10 4 ,b 2≈24.5, =6.23cm -1 , =0.0049cm -1 , =11.214cm -1 , =0.0033cm -1 , ≈5cm -1 , ≈20cm -1 .

[0037] Penetration depth of indicator light and therapeutic light in tissue , The calculation formula is: in, , These are the absorption coefficients of the skin tissue for the therapeutic wavelength and the indicator wavelength laser, respectively. Depending on the target chromophore, they can be written as: Substituting the above formula into the relationship between light energy and target chromophore, we can obtain the formulas for calculating the volume fraction of lipids and water: in, ∈[0.1, 15](cm) -1 ), ∈[1, 150](cm) -1 ), ∈[3×10 -3 ,0.1](cm -1 ), ∈[3×10 -5 ,0.1](cm -1 ), ∈[1, 10](cm) -1 ), ∈[15, 50](cm) -1 ).

[0038] In one embodiment, when measuring the volume fraction of lipids and water, multiple light signals can be acquired from a target skin area, and the resulting volume fraction is the average of the multiple measurements.

[0039] Optionally, the light receiving module collects the incident light signal of the treatment light and the indicator light and the reflected light signal after the light irradiates the skin and converts them into electrical signals and transmits them to the signal processing module. The information processing module first performs filtering and noise reduction processing on the original light signal, and then calculates the volume fraction of lipids and water in the target skin area based on the incident light intensity and the reflected light intensity.

[0040] The control system is used to input the volume fractions of lipids and water into a pre-established neural network model to obtain a combination of laser treatment parameters; the laser module generates a treatment beam according to the combination of laser treatment parameters.

[0041] Optionally, the neural network model includes a support vector machine regression algorithm and a Naive Bayes classification algorithm; the control system is also used to input the volume fractions of lipids and water and the optical properties of the skin into the support vector machine regression algorithm to obtain a combination of laser treatment parameters, and to input the volume fractions of lipids and water, the optical properties of the skin and the combination of laser treatment parameters into the Naive Bayes classification algorithm to obtain a predicted thermal damage risk level; the optical properties of the skin include the absorption coefficient and the reduced scattering coefficient.

[0042] The control system achieves overall control and drive of the device through a main controller. The main controller adopts an embedded design, integrating an algorithm chip and carrying an optical parameter selection module. This module constructs a neural network model of "volume fraction-optical parameters-thermal damage" through machine learning. After the signal processing module transmits the volume fraction data of lipids and water to the main controller, the optical parameter selection module can determine the optimal combination of laser treatment parameters (pulse width, power, repetition rate, energy density, etc.) and control the laser module to generate a personalized treatment beam. The process of constructing the neural network model of "volume fraction-optical parameters-thermal damage" is as follows:

[0043] Input data acquisition: Through clinical trials or simulation platforms, collect data on the volume fractions of lipids and water for different skin types, corresponding optical parameters (pulse width, power, repetition rate, energy density, etc.), and thermal damage assessment indicators (such as temperature distribution, tissue damage degree, etc.). Model input variables include the volume fractions of lipids and water and skin optical properties (such as absorption coefficient, scattering coefficient, etc.). Output variables include the combination of laser treatment parameters and the predicted thermal damage risk level.

[0044] Feature extraction and preprocessing: The collected lipid and water volume fraction data, optical parameters, and thermal damage data were normalized, denoised, and standardized to eliminate dimensional differences and outlier interference. Key features were extracted, such as the spatiotemporal characteristics of lipid and water distribution, the combined characteristics of optical parameters, and the thermal damage threshold.

[0045] Model Training and Optimization: Machine learning algorithms were used to establish a mapping relationship between volume fraction, optical parameters, and thermal damage. First, a lipid-optical parameter model was built using support vector regression. Second, a Naive Bayes classification algorithm was used to predict the thermal damage risk level based on the volume fraction-optical parameter relationship. Finally, cross-validation and hyperparameter tuning (such as grid search and Bayesian optimization) were employed to improve the model's generalization ability.

[0046] The support vector regression algorithm model searches for an optimal hyperplane by mapping low-dimensional data to a high-dimensional feature space, such that most data points lie within the ε-separation band of this hyperplane. Its mathematical model function is as follows: in, The weights are used to determine the aforementioned optimal regression hyperplane. For model bias, x This is sample data. Among them... For the first Each sample data point includes the spatiotemporal characteristics of lipid and water volume fraction distribution, combined characteristics of optical parameters, and thermal damage threshold, among other things. dimensional features, It is the first The weights of each sample data point For the first The combination of laser treatment parameters corresponding to each sample data determines the position of the optimal hyperplane in the feature space. The effective relationship between the volume fraction of lipids and water and the optical parameters can be established through the support vector regression algorithm.

[0047] By introducing kernel functions Mapping low-dimensional data to a high-dimensional feature space, the function can be rewritten as: The optimization objectives of the support vector regression algorithm include maximizing the margin and minimizing the loss. The optimization objectives are as follows: in This determines the complexity and generalization ability of the model. The smaller the value, the stronger the generalization ability. C is the regularization parameter, which controls the model's tolerance to errors.

[0048] Introducing slack variables The minimal soft margin representation is formalized as follows: in, For insensitive band width, For upper bound slack variables, As a lower bound slack variable, This represents the actual combination of laser treatment parameters corresponding to the i-th sample data.

[0049] The Naive Bayes classification algorithm classifies objects by finding the maximum posterior probability of the target, assuming no correlation between features. Given a training dataset, where each sample... All include dimensional features, i.e. The class tag set contains Types of thermal damage risk levels, namely .

[0050] According to Bayes' theorem, the samples can be obtained. belong Probability of category as follows: The category with the highest posterior probability is denoted as the predicted category. The final representation of the Naive Bayes classification model is as follows: in The total number of samples, For the sample Features This represents the predicted risk level of thermal damage.

[0051] Model Validation and Deployment: Model performance was evaluated on an independent test set, and mean squared error (MSE) was used for quantitative validation. Finally, the trained model was embedded into the optical parameter selection module of the main controller. By receiving lipid data transmitted from the signal processing module, the model was invoked to calculate the optimal optical parameters, and control commands were output to the laser module to dynamically adjust the treatment beam.

[0052] The device also includes a cooling module that provides contact cooling to the skin with an adjustable temperature range (0-15℃). The cooling module consists of a TEC cooling chip, a contact cooling component, and a sapphire window. The TEC cooling chip is electrically connected to the control system. The contact cooling component is made of metal with a hollowed-out center at the front end, into which a sapphire window is embedded, located 3-10cm from the light outlet.

[0053] TEC cooling elements are used to receive cooling parameter adjustment commands sent by the control system.

[0054] The contact cooling component is a rotatable structure. When measuring the volume fraction of lipids and water, the contact cooling component is rotated to a position that does not affect the illumination and reception of the light signal, and the front end of the handpiece is placed against the skin surface. The measurement distance is consistent with the distance from the sapphire window to the light outlet, which is 3-10cm. This can reduce the attenuation of the laser during transmission and avoid the signal-to-noise ratio being too low, which would affect the measurement accuracy.

[0055] In one embodiment, the device includes a human-machine interface module (HMI) comprising a touchscreen display, operation buttons, and is electrically connected to a control system. The touchscreen display is used to select lipid and water detection modes or treatment modes, and to adjust and input laser and cooling parameters. The control system transmits adjustment commands to the laser or cooling module. The operation buttons are used for light output control. When measuring the volume fraction of lipids and water, the measurement program is initiated via the touchscreen display. At this time, the laser module outputs continuous treatment and indicator light by default, with a fixed power value that meets the safety threshold range (≤0.1W / cm²). 2 Press the operation button, the device emits light, and the photodetector starts working.

[0056] The modules in the aforementioned acne laser treatment device based on lipid and moisture detection can be implemented entirely or partially through software, hardware, or a combination thereof. These modules can be embedded in or independent of the processor in a computer device, or stored in the computer device's memory as software, so that the processor can call and execute the corresponding operations of each module.

[0057] The above are one or more embodiments of the acne laser treatment device based on lipid and moisture detection provided in this specification. Based on the same idea, this specification also provides corresponding methods for determining acne laser treatment parameters based on lipid and moisture detection, such as... Figure 2 As shown, this embodiment includes the following steps: S201, the laser module emits therapeutic light and indicator light towards the target skin area; the wavelength of the therapeutic light corresponds to the absorption peak of lipids, and the wavelength of the indicator light belongs to the visible light band.

[0058] S202, the light receiving module collects the light signals of the therapeutic light and the indicator light reflected by the target skin area.

[0059] S203, the signal processing module determines the incident light intensity and reflected light intensity of the treatment light and indicator light based on the light signals emitted and reflected by the treatment light and indicator light; and calculates the volume fraction of lipids and water in the target skin area based on the incident light intensity and reflected light intensity of the treatment light and indicator light; the calculation formula for the volume fraction of lipids and water is constructed based on the relationship between light energy and target chromophores in the skin, and the fact that the absorption rate of melanin is multiple of the absorption rate of lipids, and the absorption rate of hemoglobin is multiple of the absorption rate of water. Target chromophores include water, lipids, hemoglobin and melanin.

[0060] S204, the control system inputs the volume fractions of lipids and water into a pre-established neural network model to obtain a combination of laser treatment parameters; the combination of laser treatment parameters is used to generate a treatment beam for the target skin area.

[0061] When applying the method for determining acne laser treatment parameters based on lipid and moisture detection provided in this manual, it is not necessary to follow the... Figure 2 The steps shown are executed in sequence. The specific execution order of each step can be determined as needed, and this manual does not impose any restrictions on it.

[0062] For specific limitations on the method for determining parameters of acne laser treatment based on lipid and moisture detection, please refer to the limitations on acne laser treatment devices based on lipid and moisture detection mentioned above, which will not be repeated here.

[0063] This specification also provides a computer-readable storage medium storing a computer program that can be used to execute the above-described... Figure 2 A method for determining parameters for acne laser treatment based on lipid and moisture detection is provided.

[0064] This instruction manual also provides Figure 3 The schematic diagram of the computer device shown is as follows: Figure 3 At the hardware level, the computer device includes a processor, internal bus, network interface, memory, and non-volatile memory, and may also include other hardware required for business operations. The processor reads the corresponding computer program from the non-volatile memory into memory and then runs it to achieve the above-mentioned functions. Figure 2 A method for determining parameters for acne laser treatment based on lipid and moisture detection is provided.

[0065] Those skilled in the art will understand that all or part of the processes in the methods of the above embodiments can be implemented by a computer program instructing related hardware. The computer program can be stored in a non-volatile computer-readable storage medium, and when executed, it can include the processes of the embodiments of the methods described above. Any references to memory, storage, databases, or other media used in the embodiments provided in this application can include at least one of non-volatile and volatile memory. Non-volatile memory can include read-only memory (ROM), magnetic tape, floppy disk, flash memory, or optical storage, etc. Volatile memory can include random access memory (RAM) or external cache memory. By way of illustration and not limitation, RAM can be in various forms, such as static random access memory (SRAM) or dynamic random access memory (DRAM), etc.

[0066] The technical features of the above embodiments can be combined in any way. For the sake of brevity, not all possible combinations of the technical features in the above embodiments are described. However, as long as there is no contradiction in the combination of these technical features, they should be considered to be within the scope of this specification.

Claims

1. An acne laser treatment device based on lipid and moisture detection, characterized in that, The device includes: a laser module, an optical receiving module, a signal processing module, and a control system; The laser module is used to emit therapeutic and indicator light to the target skin area; the wavelength of the therapeutic light corresponds to the absorption peak of lipids, and the wavelength of the indicator light belongs to the visible light band. The light receiving module is used to collect the light signals of the therapeutic light and the indicator light reflected by the target skin area and transmit them to the signal processing module; The signal processing module is used to determine the incident and reflected light intensities of the treatment light and indicator light based on the light signals emitted and reflected by the treatment light and indicator light, and to calculate the volume fractions of lipids and water in the target skin area. The formula for calculating the volume fractions of lipids and water is based on the relationship between light energy and target chromophores in the skin, as well as the fact that the absorption rate of melanin is multiple of the absorption rate of lipids, and the absorption rate of hemoglobin is multiple of the absorption rate of water. Target chromophores include water, lipids, hemoglobin, and melanin. The control system is used to input the volume fractions of lipids and water into a pre-established neural network model to obtain a combination of laser treatment parameters; the laser module generates a treatment beam according to the combination of laser treatment parameters.

2. The apparatus according to claim 1, characterized in that, The formulas for calculating the volume fractions of lipids and water are as follows: in, This represents the volume fraction of lipids. This represents the volume fraction of water. , These are the absorption coefficients of lipids and water at the therapeutic light wavelength, respectively. , These are the absorption coefficients of lipids and water at the indicated light wavelengths, respectively. , These are the reduced scattering coefficients under the treatment wavelength and the indicator wavelength lasers, respectively. , These represent the incident light intensity at the therapeutic light wavelength and the indicator light wavelength, respectively. , These represent the reflected light intensity at the treatment wavelength and the indicator wavelength, respectively; the absorption rate of melanin at the treatment wavelength is that of lipids. a 1 times, a 1∈(0,1]; the absorption rate of hemoglobin at the therapeutic wavelength is that of water. b 1 times, b 1∈(0,1]; the absorption rate of melanin at the indicated light wavelength is that of lipids. a 2 times, a 2∈[10 4 10 5 The absorbance of hemoglobin at the indicator wavelength is that of water. b 2 times, b 2∈[1, 10] 5 ].

3. The apparatus according to claim 1, characterized in that, The laser module includes a laser, a laser driver, and a beam shaping mirror assembly; the laser driver is electrically connected to the control system; a beam splitter is located at the rear end of the beam shaping mirror assembly; The laser driver is used to receive and execute start / stop commands and parameter adjustment commands from the control system, and to control the laser to emit coaxial therapeutic and indicator beams. The beam shaping lens assembly is used for collimation, focusing, and spot homogenization, and allows the treatment beam and indicator beam to be directly projected onto the skin via a beam splitter for positioning and treatment.

4. The apparatus according to claim 3, characterized in that, The optical receiving module includes a photodetector and is equipped with a filter; The photodetector is used to collect reflected light signals from the therapeutic light and the indicator light, convert them into electrical signals and send them to the signal processing module, and to collect incident light directly incident through the beam splitter to obtain the incident light intensity. The signal processing module is used to filter and denoise the raw electrical signal, determine the intensity of reflected light, and calculate the volume fraction of lipids and water in the target skin area based on the incident light intensity and the intensity of reflected light.

5. The apparatus according to claim 1, characterized in that, Neural network models include support vector machine regression algorithm and Naive Bayes classification algorithm; The control system is also used to input the volume fractions of lipids and water and the optical properties of the skin into the support vector machine regression algorithm to obtain the combination of laser treatment parameters, and to input the volume fractions of lipids and water, the optical properties of the skin and the combination of laser treatment parameters into the Naive Bayes classification algorithm to obtain the predicted thermal damage risk level. The optical properties of skin include the absorption coefficient and the reduced scattering coefficient.

6. The apparatus according to claim 1, characterized in that, The device also includes a cooling module, which includes a TEC cooling chip, a contact cooling component, and a sapphire window. The TEC cooling chip is electrically connected to the control system. The contact cooling component is made of metal with a hollowed-out center at the front end, into which a sapphire window is embedded. TEC cooling elements are used to receive cooling parameter adjustment commands sent by the control system; The contact cooling component is a rotatable structure. When measuring the volume fraction of lipids and water, the contact cooling component is rotated to a position that does not affect the illumination and reception of light signals, and the front end of the handpiece is placed against the skin surface. The measurement distance is consistent with the distance from the sapphire window to the light outlet.

7. The apparatus according to claim 6, characterized in that, The device includes a human-computer interaction module, which includes a touch screen and operation buttons, and is electrically connected to the control system. The touch screen is used to select the detection mode or treatment mode, as well as to adjust and input the laser parameters and cooling parameters. The control system then transmits the adjustment commands to the laser module or cooling module. The operation buttons are used for light emission control, and the measurement program is started via the touch screen when measuring the volume fraction of lipids and water.

8. The apparatus according to claim 1, characterized in that, The therapeutic light wavelength ranges from 1.2 to 2 μm, and the indicator light wavelength ranges from 380 to 780 nm.

9. A method for determining parameters for acne laser treatment based on lipid and moisture detection, characterized in that, The method is applied to the apparatus according to any one of claims 1-8, and the method includes: It emits therapeutic light and indicator light towards the target skin area; the wavelength of the therapeutic light corresponds to the absorption peak of lipids, and the wavelength of the indicator light belongs to the visible light band; Acquire the light signals of the therapeutic light and the indicator light reflected from the target skin area; The incident light intensity and reflected light intensity of the therapeutic light and indicator light are determined based on the light signals emitted and reflected by the therapeutic light and indicator light. The volume fractions of lipids and water in the target skin region are calculated based on the incident and reflected light intensities of the therapeutic and indicator light. The formulas for calculating the volume fractions of lipids and water are based on the relationship between light energy and target chromophores in the skin, as well as the fact that the absorption rates of melanin and lipids are multiples of each other, and the absorption rates of hemoglobin and water are multiples of each other. Target chromophores include water, lipids, hemoglobin, and melanin. The volume fractions of lipids and water are input into a pre-established neural network model to obtain a combination of laser treatment parameters; this combination of laser treatment parameters is used to generate a treatment beam for the target skin area.

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