A design method of a deep tissue phototherapy device based on a custom spectral LED array

Abstract

The present application relates to a kind of based on the design method of deep tissue phototherapy device of custom spectrum LED array.The method includes obtaining reference spectrum data of halogen lamp or water filtration infrared A light and candidate LED chip parameters, the spectrum data of different sampling intervals is interpolated to uniform 1nm wavelength coordinate, the radiation power distribution proportion and the number of each peak wavelength LED chip are calculated according to the energy proportion of reference spectrum, and closed-loop calibration is carried out through multi-channel constant current drive, irradiance sensor and temperature sensor.The output spectrum of system is limited to 630nm to 1350nm, the effective band energy proportion is not less than 99%, and the effective radiation intensity at the distance target irradiation surface 14cm is 200mW / cm 2 To 500mW / cm 2 The similarity of LED fitting spectrum and halogen lamp effective spectrum can reach 99.05%, the risk of epidermal thermal burn can be reduced and water filtration structure can be simplified by reducing more than 1400nm of heat generating band from light source level.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, and in particular to a design method for a deep tissue phototherapy device based on a customized spectral LED array. Background Technology

[0002] Phototherapy utilizes the interaction of light energy in specific wavelengths with biological tissues to produce photochemical and photothermal effects, and is widely used in analgesia, anti-inflammation, and tissue repair promotion. Currently, the mainstream technology for treating deep tissues (such as muscles, joint capsules, and abdominal cavities 7-10 cm below the skin) is water-filtered infrared A-light therapy.

[0003] Existing technologies typically use halogen lamps as the light source. However, halogen lamps, as a source of thermal radiation, have an extremely wide original spectral coverage (200-3000nm). According to measured data, the OSRAM 500W halogen lamp, without filtering, produces a total irradiance of 1274.8 mW / cm². 2 The effective therapeutic wavelength (630nm~1350nm) has a radiation irradiance of only 734.5mW / cm². 2 This accounts for approximately 57.6%. This means that more than 42% of the energy is distributed in the infrared B region and far-infrared region with wavelengths greater than 1400nm.

[0004] However, existing technologies have the following drawbacks: High risk of thermal damage: Spectra with wavelengths greater than 1400nm are easily absorbed by water molecules on the skin surface and converted into heat. The penetration depth is very shallow, and the heat mainly accumulates in the epidermis and upper dermis, which is the main reason for excessive heat sensation or even burns during treatment.

[0005] The system is complex and bulky: To filter out the aforementioned harmful wavelengths, current technologies must rely on a composite system of water filtration and optical filters. While water filtration technology can mimic the absorption characteristics of atmospheric water to filter out long-wave infrared radiation, it results in bulky equipment, requires regular water quality maintenance, and carries the risk of leakage.

[0006] Low energy efficiency: After the light emitted by the halogen lamp passes through water filtration and a filter, the total irradiance drops sharply. Data shows that the total irradiance after filtration decreases from 1274.8 mW / cm². 2 Reduced to 339.0 mW / cm 2 Energy attenuation is as high as 73.4%, with a large amount of electrical energy being converted into heat energy and wasted. Summary of the Invention

[0007] Therefore, the technical problem to be solved by the present invention is to overcome the problems of high risk of thermal damage, large and complex system and low energy utilization of halogen lamps as thermal radiation light sources in the prior art.

[0008] To address the aforementioned technical problems, this invention provides a design method for a deep tissue phototherapy device based on a customized spectral LED array, comprising: The reference spectral data of the reference light source within a preset effective wavelength band are obtained, and the peak wavelength, package size, rated drive current, operating voltage and single-chip optical power parameters of multiple candidate LED chips are obtained. The preset effective wavelength band is 630nm to 1350nm, and the reference light source is a halogen lamp. The reference spectral data and the candidate spectral data of each candidate LED chip are mapped to a unified wavelength coordinate, and the mapped spectral data are normalized. Based on the spectral energy of each candidate LED chip at or in the neighborhood of the peak wavelength of the reference spectral data, the normalized power allocation ratio of each candidate LED chip is calculated, and the target allocation power of each candidate LED chip is calculated based on the total radiant power of the array. Based on the target power allocation of each candidate LED chip and the single optical power of the corresponding candidate LED chip, the number of LED chips configured for each peak wavelength is determined, and an LED light source array is formed according to the number of LED chips configured for each peak wavelength. The fitted spectrum of the LED light source array is generated based on the candidate spectral data and normalized power allocation ratio of each candidate LED chip, and the spectral similarity is calculated based on the fitted spectrum and the reference spectral data. When the spectral similarity does not reach the preset similarity threshold, the normalized power allocation ratio, the number of chips and / or the channel drive current of each candidate LED chip are adjusted. By using a multi-channel constant current driving circuit to drive LED chips with different peak wavelengths, the output wavelength range of the LED light source array is limited to 630nm-1350nm.

[0009] In one embodiment of the present invention, power allocation includes: Calculate the percentage of the peak wavelength data points of each candidate LED chip in the sampled energy of the reference spectral data; The normalized power allocation ratio of each sampled energy is obtained by normalizing the energy ratio of each candidate LED chip. Multiply the total radiated power of the array by the normalized power allocation ratio of each candidate LED chip to obtain the target allocated power of the corresponding candidate LED chip.

[0010] In one embodiment of the present invention, when the total radiated power of the array is 30W, the target allocated power corresponding to the LED chips with peak wavelengths of 630nm, 660nm, 810nm, 850nm, 940nm, 1050nm, 1140nm, 1240nm and 1350nm are 2748.21mW, 3246.05mW, 4644.44mW, 4897.35mW, 4483.69mW, 5139.55mW, 2495.60mW, 2034.53mW and 310.59mW respectively.

[0011] In one embodiment of the present invention, the candidate LED chip has a package size of 3535 and a rated drive current of 700mA; wherein the operating voltage of the LED chip with peak wavelengths of 630nm and 660nm is 2.1V to 2.5V, the operating voltage of the LED chip with peak wavelengths of 810nm and 850nm is 1.5V to 1.9V, the operating voltage of the LED chip with peak wavelengths of 940nm and 1050nm is 1.4V to 1.8V, the operating voltage of the LED chip with peak wavelength of 1140nm is 1.0V to 1.4V, and the operating voltage of the LED chip with peak wavelengths of 1240nm and 1350nm is 0.9V to 1.3V.

[0012] In one embodiment of the present invention, the peak wavelengths of the candidate LED chips include 630nm, 660nm, 810nm, 850nm, 940nm, 1050nm, 1140nm, 1240nm, and 1350nm; the number of LED chips corresponding to the peak wavelengths configured in the LED light source array are 3, 4, 12, 10, 11, 13, 25, 25, and 4, respectively.

[0013] In one embodiment of the present invention, in the spectral fitting verification, the spectral similarity is the normalized dot product similarity, and the preset similarity threshold is not less than 95%; the spectral similarity between the fitted spectrum of the LED light source array and the reference spectral data in the range of 630nm to 1350nm is 99.05%.

[0014] In one embodiment of the present invention, an optical homogenizing and focusing component forms a light spot with a diameter of 15 cm at a distance of 14 cm from the target irradiation surface, and the irradiance in the effective wavelength band of 630 nm to 1350 nm is controlled at 200 mW / cm². 2 Up to 500mW / cm 2 .

[0015] In one embodiment of the present invention, the effective wavelength energy ratio of the LED light source array output is not less than 99%, and the total irradiance measured at a distance of 14 cm from the target irradiation surface is 350 mW / cm². 2 Furthermore, the total irradiance is used as the effective band irradiance for photobiological regulation of deep tissues.

[0016] In one embodiment of the present invention, the reference spectral data includes multiple data points in the range of 630nm to 1350nm, and the wavelength interval between adjacent data points is 5nm; the candidate spectral data of the candidate LED chip includes multiple peak wavelength data points in the range of 630nm to 1350nm, and the wavelength interval between the multiple peak wavelength data points is not fixed.

[0017] The technical solution of the present invention has the following advantages compared with the prior art: This invention uses an LED light source that emits light through electronic band transitions and limits the output spectrum to 630nm to 1350nm through a customized spectral array. This minimizes (or eliminates) the proportion of radiation energy with wavelengths greater than 1400nm, thereby reducing the energy in the infrared B region and far-infrared region with wavelengths greater than 1400nm from the source. This reduces the risk of skin burns without the need for a large water filtration structure.

[0018] This invention calculates the power distribution ratio and number of LEDs using reference spectral data and candidate LED chip parameters, enabling the LED light source array to reproduce the spectral profile of the effective wavelength band of water-filtered infrared A light or halogen lamps. The similarity between the LED fitted spectrum and the effective spectrum of the halogen lamp reaches 99.05%, demonstrating high spectral consistency. Furthermore, after complex water filtration and filter processing, the halogen lamp achieves an energy share of 94.8% in the effective wavelength band (630nm~1350nm), with a radiant intensity of 321.5 mW / cm². 2 This invention utilizes a customized spectral LED, achieving an effective wavelength energy ratio of over 99%. Under the same electrical power input, the effective light energy output of this invention is higher than that of a halogen lamp solution, and it is easier to achieve 300mW / cm² at a distance of 14cm. 2 The above-mentioned high-irradiation treatment needs.

[0019] This invention integrates total radiation power, single LED light power, peak wavelength, driving current and spectral similarity into the design process, enabling parameter replacement and recalibration according to different LED batches or different treatment power requirements, avoiding spectral shift and insufficient energy caused by simply stacking LED chips based on experience.

[0020] This invention can generate an effective band radiation irradiance of 200 mW / cm² at a distance of 14 cm from the target irradiation surface. 2 Up to 500mW / cm 2The light spot, in the example, showed a total irradiance of 350 mW / cm². 2 Furthermore, the irradiance is basically within the effective wavelength range, thereby improving energy utilization and reducing the size of the device. Attached Figure Description

[0021] To make the content of this invention easier to understand, the invention will be further described in detail below with reference to specific embodiments and accompanying drawings.

[0022] Figure 1 This is a flowchart illustrating the design method of a deep tissue phototherapy device based on a customized spectral LED array, as described in this invention.

[0023] Figure 2 This is a schematic diagram comparing the LED spectrum with the effective spectrum of a halogen lamp in an embodiment of the present invention.

[0024] Figure 3 This is a schematic diagram of the structure of the LED light source, reflector, heat sink and fan in an embodiment of the present invention. Detailed Implementation

[0025] The present invention will be further described below with reference to the accompanying drawings and specific embodiments, so that those skilled in the art can better understand and implement the present invention. However, the embodiments described are not intended to limit the present invention.

[0026] In this invention, when directions (up, down, left, right, front, and back) are described, it is only for the convenience of describing the technical solution of this invention, and does not indicate or imply that the technical features referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, it should not be construed as a limitation of this invention.

[0027] In this invention, "several" means one or more, "multiple" means two or more, "greater than," "less than," "exceeding," etc., are understood to exclude the stated number; "above," "below," "within," etc., are understood to include the stated number. In the description of this invention, the terms "first" and "second" are used only to distinguish technical features and should not be construed as indicating or implying relative importance, or implicitly indicating the number of indicated technical features, or implicitly indicating the order of the indicated technical features.

[0028] In this invention, unless otherwise explicitly defined, the terms "setting," "installing," and "connecting" should be interpreted broadly. For example, they can refer to a direct connection or an indirect connection through an intermediate medium; a fixed connection, a detachable connection, or an integrally formed connection; a mechanical connection, an electrical connection, or a connection capable of mutual communication; or the internal connection of two components or the interaction between two components. Those skilled in the art can reasonably determine the specific meaning of the above terms in this invention based on the specific content of the technical solution.

[0029] Example 1 Reference Figure 1 As shown, this embodiment provides a design method for a deep tissue phototherapy device based on a customized spectral LED array, including: S1. Obtain reference spectral data of the reference light source within a preset effective wavelength band, and obtain the peak wavelength, package size, rated drive current, operating voltage and single-chip optical power parameters of multiple candidate LED chips. The preset effective wavelength band is 630nm to 1350nm, and the reference light source is a halogen lamp, which is processed by water filtration and a filter to obtain the reference spectral data.

[0030] The halogen lamp spectrum after water filtration and filter treatment can be used as a reference spectrum for traditional deep phototherapy, with 630nm to 1350nm being the main effective treatment band. At the same time, parameters such as peak wavelength, current, voltage, and single-chip optical power of candidate LED chips are collected to facilitate the determination of which LED chips can be combined to produce output light close to the reference spectrum.

[0031] S2. Map the reference spectral data and the candidate spectral data of each candidate LED chip to a unified wavelength coordinate, and normalize the mapped spectral data.

[0032] Since the reference spectrum and the spectral test data of different LED chips may use different wavelength intervals, they need to be interpolated to the same set of wavelength coordinates first. Normalization process transforms the spectra of different intensities to the same scale to avoid affecting the comparison of spectral shapes due to different test power.

[0033] S3. Based on the spectral energy of each candidate LED chip at or in the neighborhood of the peak wavelength of the reference spectral data, calculate the normalized power allocation ratio of each candidate LED chip, and calculate the target allocation power of each candidate LED chip based on the total radiant power of the array.

[0034] LED power is allocated according to the energy requirements of the target spectrum. If the reference spectrum has high energy near a certain LED peak wavelength, it indicates that this wavelength is more important in the target spectrum, and therefore, the LED at that wavelength should be allocated higher power. Conversely, if the reference spectrum has low energy near that wavelength, the corresponding LED should be allocated lower power. In this way, the energy distribution of the reference spectrum can be converted into the power ratio of LEDs at each wavelength.

[0035] S4. Based on the target power allocation of each candidate LED chip and the single optical power of the corresponding candidate LED chip, determine the number of LED chips configured for each peak wavelength, and form an LED light source array based on the number of LED chips configured for each peak wavelength.

[0036] Since the individual optical power of each LED chip is known, the required number of chips can be obtained by dividing the target power allocated to the LED of that wavelength by the individual optical power. The LEDs of different wavelengths are then combined according to the calculated number to form an LED light source array that approximates the target spectrum.

[0037] S5. Generate a fitted spectrum of the LED light source array based on the candidate spectral data and normalized power allocation ratio of each candidate LED chip, and calculate the spectral similarity between the fitted spectrum and the reference spectral data. If the spectral similarity does not reach the preset similarity threshold, adjust the normalized power allocation ratio, the number of configured LED chips, and / or the channel drive current of each candidate LED chip.

[0038] This step enables spectral fitting and feedback correction. By superimposing the spectra of each wavelength LED according to their power ratio, the simulated output spectrum of the LED array can be obtained. This fitted spectrum is then compared with a reference spectrum. If the similarity is insufficient, it indicates that the energy in certain bands is too high or too low. The power ratio, number of chips, or drive current of the corresponding LEDs need to be adjusted until the fitted spectrum meets the preset similarity requirements.

[0039] S6. LED chips with different peak wavelengths are driven separately using a multi-channel constant current driving circuit, limiting the output wavelength range of the LED light source array to 630nm-1350nm. Stable and controllable mixed light output is achieved through channel-specific driving. LED chips with different peak wavelengths are driven independently by different constant current channels, allowing for individual adjustment of the output intensity of each wavelength LED. This ensures the overall array spectrum stably falls within the 630nm~1350nm range and avoids outputting long-wave infrared heating bands greater than 1400nm.

[0040] Specifically, power allocation includes: Calculate the percentage of the peak wavelength data points of each candidate LED chip in the sampled energy of the reference spectral data; The normalized power allocation ratio of each sampled energy is obtained by normalizing the energy ratio of each candidate LED chip. Multiply the total radiated power of the array by the normalized power allocation ratio of each candidate LED chip to obtain the target allocated power of the corresponding candidate LED chip.

[0041] It's important to note that the power allocation principle is based on the energy levels of the reference spectrum at the peak wavelengths of each candidate LED, determining the appropriate power output for each wavelength. The energy values ​​corresponding to the peak wavelengths of each candidate LED chip are read from the reference spectrum data. For example, if the peak wavelengths of the candidate LED chips are 660nm, 810nm, and 850nm, the energy at these wavelengths is read respectively. A higher energy value indicates that the reference spectrum requires more light energy in that wavelength band. Then, the energy values ​​at each peak wavelength are normalized, which means calculating the proportion of each wavelength's energy in the total energy of all candidate wavelengths. This yields the power allocation ratio for each candidate LED chip, ensuring that the sum of the allocation ratios for all LED chips is 100%. Finally, the total radiated power of the LED array is multiplied by the power allocation ratio for each candidate LED chip to obtain the target allocated power for each type of LED chip.

[0042] In one embodiment, when the total radiated power of the array is 30W, the target allocated power for LED chips with peak wavelengths of 630nm, 660nm, 810nm, 850nm, 940nm, 1050nm, 1140nm, 1240nm, and 1350nm are 2748.21mW, 3246.05mW, 4644.44mW, 4897.35mW, 4483.69mW, 5139.55mW, 2495.60mW, 2034.53mW, and 310.59mW, respectively.

[0043] The candidate LED chips have a package size of 3535 and a rated drive current of 700mA. Specifically, the operating voltage of LED chips with peak wavelengths of 630nm and 660nm is 2.1V to 2.5V; the operating voltage of LED chips with peak wavelengths of 810nm and 850nm is 1.5V to 1.9V; the operating voltage of LED chips with peak wavelengths of 940nm and 1050nm is 1.4V to 1.8V; the operating voltage of LED chips with a peak wavelength of 1140nm is 1.0V to 1.4V; and the operating voltage of LED chips with peak wavelengths of 1240nm and 1350nm is 0.9V to 1.3V.

[0044] The peak wavelengths of the candidate LED chips include 630nm, 660nm, 810nm, 850nm, 940nm, 1050nm, 1140nm, 1240nm, and 1350nm; the number of LED chips in the LED light source array corresponding to the peak wavelengths are 3, 4, 12, 10, 11, 13, 25, 25, and 4, respectively.

[0045] In the spectral fitting verification, the spectral similarity is the normalized dot product similarity, and the preset similarity threshold is not less than 95%; the spectral similarity between the fitted spectrum of the LED light source array and the reference spectral data in the range of 630nm to 1350nm is 99.05%.

[0046] Specifically, an optical homogenizing and focusing component is used to form a 15cm diameter light spot at a distance of 14cm from the target illumination surface, and the irradiance in the effective wavelength range of 630nm to 1350nm is controlled at 200mW / cm². 2 Up to 500mW / cm 2 .

[0047] Specifically, the effective wavelength energy output by the LED light source array accounts for no less than 99%, and the total irradiance measured at a distance of 14 cm from the target irradiation surface is 350 mW / cm². 2 Furthermore, the total irradiance is used as the effective band irradiance for photobiological regulation of deep tissues.

[0048] Specifically, the reference spectral data includes multiple data points in the range of 630nm to 1350nm, with a wavelength interval of 5nm between adjacent data points; the candidate spectral data of the candidate LED chip includes multiple peak wavelength data points in the range of 630nm to 1350nm, and the wavelength interval between the multiple peak wavelength data points is not fixed.

[0049] Specifically, to enable similarity comparison and power allocation calculation of the two sets of data under the same coordinate system, an interpolation algorithm is used to map the first and second data tables to a unified 1nm wavelength interval horizontal coordinate, resulting in unified wavelength coordinates. The interpolation algorithm can be linear interpolation, cubic spline interpolation, or piecewise polynomial interpolation.

[0050] After interpolation, the two sets of spectral data are normalized, for example, by normalizing their maximum spectral energy to 1, or by normalizing their total energy within the effective wavelength band to 1. This eliminates differences in test power or overall brightness, focusing the comparison on the similarity of spectral shapes. Subsequently, the two sets of normalized spectral data are compared point-by-point under a unified wavelength coordinate system. Spectral similarity can be calculated using methods such as cosine similarity, correlation coefficient, or mean square error. For example, the closer the cosine similarity is to 1, the closer the shapes of the two spectral curves are; the smaller the mean square error, the smaller the differences between the two spectra at each wavelength.

[0051] In this way, the reference spectrum and the fitted spectrum of the LED array can be compared under the same wavelength coordinates and the same normalization scale, thereby determining whether the output spectrum of the LED light source array meets the preset similarity requirements.

[0052] Example 2

[0053] In this embodiment, the LED light source array uses 3535 packaged LED chips with peak wavelengths of 630nm, 660nm, 810nm, 850nm, 940nm, 1050nm, 1140nm, 1240nm, and 1350nm, with a rated drive current of 700mA for each. The parameters of the LED chips with different peak wavelengths are shown in Table 1 below.

[0054] Table 1: Parameters of LED chips with different peak wavelengths

[0055] The aforementioned 630nm chip is a visible-red light chip, which suppliers often indicate using luminous flux. In array design, it can be converted to equivalent radiant flux using a spectroradiometer, or the individual chip power used for chip count calculation can be obtained through calibration testing. For chips ranging from 660nm to 1350nm, the individual chip radiant power can be directly used as the chip count calculation parameter.

[0056] Calculation of the number of particles under a total radiant power of 30W.

[0057] In this embodiment, it is approximately assumed that the irradiance of the target illumination surface is proportional to the radiant power of the LED chip, and the calculation is performed with a total radiant power of 30W for the LED light source array. For the nine candidate peak wavelengths, the sampling energy percentage is first obtained based on the reference spectrum, and then the sampling energy percentage is normalized to the power distribution ratio under a total radiant power of 30W. The calculation results are shown in Table 2 below.

[0058] Table 2: Allocation Results Table

[0059] As shown in the table above, under the example of 30W total radiant power, the number of LED chips for 630nm, 660nm, 810nm, 850nm, 940nm, 1050nm, 1140nm, 1240nm, and 1350nm are 3, 4, 12, 10, 11, 13, 25, 25, and 4, respectively. The above configuration is not limited to a single configuration. When the light power of a single LED, the efficiency of the optical lens, or the heat dissipation conditions change, the number of chips can be recalculated using the above formula or the output of each wavelength band can be finely adjusted by adjusting the drive current.

[0060] When calculating similarity, the reference spectral data and the fitted spectrum are first normalized, and then the normalized dot product similarity is calculated. This calculation method is used to evaluate the overall shape consistency of the two spectral curves under the same wavelength coordinates. The closer the similarity is to 1, the closer the fitted spectrum is to the reference spectrum.

[0061] like Figure 3 As shown, the deep tissue phototherapy device of this embodiment includes a controller, a multi-channel constant current drive circuit, an LED light source array, an optical homogenizing and focusing component, a heat dissipation component, an irradiance sensor, a temperature sensor, and a human-machine interaction module. The heat dissipation component may include a heat sink and a fan to remove the heat generated by the LED light source array during operation; the optical homogenizing and focusing component may include a reflector, a lens, a homogenizing plate, or a diffuser plate to mix and focus light beams with different peak wavelengths.

[0062] In this embodiment, refer to Figure 2 As shown, the data processing is explained below: The first data table contains multiple data points with a wavelength interval of 5 nm, ranging from 630 nm to 1350 nm; the second data table contains 9 data points with a variable wavelength interval, ranging from 630 nm to 1350 nm. Smoothing was achieved by mapping both sets of data to a uniform 1 nm interval on the horizontal axis using an interpolation algorithm to ensure smooth curves and accurate trends. Based on the interpolated data, the similarity between the LED fitted spectrum and the effective spectrum of the halogen lamp is 99.05%.

[0063] In this embodiment, the output wavelength of the LED light source array is limited to 630nm to 1350nm, and the effective wavelength energy ratio is not less than 99%. The LED light source array can be supported by an aluminum substrate, a copper substrate, or a ceramic substrate. The LED chips with different peak wavelengths are arranged in a centrally symmetrical, ring-shaped, or matrix-shaped manner to ensure that the beams of different wavelengths are fully mixed at the optical homogenizing and focusing component.

[0064] The optical homogenizing and focusing assembly may include a reflector, a lens, a homogenizer, or a diffuser. To form a more uniform therapeutic light spot, in one embodiment, the distance between the light-emitting surface of the LED light source array and the target irradiation surface is set to 14 cm, and the optical homogenizing and focusing assembly forms a light spot with a diameter of approximately 15 cm on the target irradiation surface. The total irradiance at the target irradiation surface is measured to be 350 mW / cm² using an irradiance sensor. 2 Since the output spectrum of the LED light source array is almost entirely within the effective wavelength range of 630nm to 1350nm, the total irradiance can be regarded as the effective wavelength irradiance.

[0065] Compared to the effective wavelength irradiance of 321.5 mW / cm² after water filtration, halogen lamps... 2 The effective irradiance of this embodiment reaches 350 mW / cm². 2 Furthermore, no water filtration structure is required. In a traditional OSRAM 500W halogen lamp without filtration, approximately 42.4% of the energy is in the wavelength range greater than 1400nm. This embodiment, by employing an LED light source array, avoids the presence of energy in the 1400nm wavelength range, thereby reducing the risk of overheating of the skin.

[0066] In practical applications, the target irradiance can be set from 200mW / cm² to 500mW / cm² via the human-machine interface module, and the controller adjusts the multi-channel constant current drive circuit based on feedback from the irradiance sensor. If the temperature sensor detects that the temperature of the target irradiated surface, LED substrate, or heat sink has reached a preset temperature threshold, the controller reduces the current of the corresponding channel or shuts down the LED light source array.

[0067] This invention actively constructs a spectral profile within the effective wavelength range of 630nm to 1350nm by selecting LED chips with specific peak wavelengths, avoiding the passive filtering of harmful wavelengths from the original broadband light source. This technical approach not only avoids the thermally active wavelength range above 1400nm but also optimizes the energy distribution within the 630nm to 1350nm range based on a reference spectrum, ensuring that the output spectrum meets the biological tissue penetration requirements of both red and near-infrared wavelengths.

[0068] It should be noted that the parameters for spectral fitting and number calculation in this invention can be replaced according to different treatment scenarios, different total radiation power, and different batches of LED chips. For example, when the total radiation power is not 30W, the normalization ratio can be kept unchanged and the target power allocation can be recalculated; when the light power of a single LED chip at a certain peak wavelength changes, the number of chips can be re-determined, or the driving current of that band can be finely adjusted by a multi-channel constant current driving circuit when the number of chips is fixed.

[0069] In one optional embodiment, the LED light source array 8 includes at least two concentric regions. The LED chips near the central region can be preferentially set to near-infrared bands such as 850nm, 940nm, and 1050nm to improve the deep penetration energy of the central region; the LED chips near the outer peripheral region can be set to 630nm, 660nm, 1140nm, 1240nm, and 1350nm bands to compensate for spectral profile and improve the uniformity of the light spot edge.

[0070] In another alternative embodiment, the LED light source array adopts a grouped series-parallel structure, with LED chips of the same peak wavelength controlled by the same driving channel, and LED chips of different peak wavelengths controlled by different driving channels. The multi-channel constant current driving circuit can use pulse width modulation dimming, constant current analog dimming, or a combination of both to change the output intensity of different wavelength bands.

[0071] Finally, it should be noted that the above specific embodiments are only used to illustrate the technical solutions of the present invention and not to limit it. Although the present invention has been described in detail with reference to examples, those skilled in the art should understand that modifications or equivalent substitutions can be made to the technical solutions of the present invention without departing from the spirit and scope of the technical solutions of the present invention, and all such modifications or substitutions should be covered within the scope of the claims of the present invention.

Claims

1. A design method for a deep tissue phototherapy device based on a customized spectral LED array, characterized in that, include: The reference spectral data of the reference light source within a preset effective wavelength band are obtained, and the peak wavelength, package size, rated drive current, operating voltage and single-chip optical power parameters of multiple candidate LED chips are obtained. The preset effective wavelength band is 630nm to 1350nm, and the reference light source is a halogen lamp. The reference spectral data and the candidate spectral data of each candidate LED chip are mapped to a unified wavelength coordinate, and the mapped spectral data are normalized. Based on the spectral energy of each candidate LED chip at or in the neighborhood of the peak wavelength of the reference spectral data, the normalized power allocation ratio of each candidate LED chip is calculated, and the target allocation power of each candidate LED chip is calculated based on the total radiant power of the array. Based on the target power allocation of each candidate LED chip and the single optical power of the corresponding candidate LED chip, the number of LED chips configured for each peak wavelength is determined, and an LED light source array is formed according to the number of LED chips configured for each peak wavelength. The fitted spectrum of the LED light source array is generated based on the candidate spectral data and normalized power allocation ratio of each candidate LED chip, and the spectral similarity is calculated based on the fitted spectrum and the reference spectral data. When the spectral similarity does not reach the preset similarity threshold, the normalized power allocation ratio, the number of chips and / or the channel drive current of each candidate LED chip are adjusted. By using a multi-channel constant current driving circuit to drive LED chips with different peak wavelengths, the output wavelength range of the LED light source array is limited to 630nm-1350nm.

2. The design method of a deep tissue phototherapy device based on a customized spectral LED array according to claim 1, characterized in that, Power allocation includes: Calculate the percentage of the peak wavelength data points of each candidate LED chip in the sampled energy of the reference spectral data; The normalized power allocation ratio of each sampled energy is obtained by normalizing the energy ratio of each candidate LED chip. Multiply the total radiated power of the array by the normalized power allocation ratio of each candidate LED chip to obtain the target allocated power of the corresponding candidate LED chip.

3. The design method of a deep tissue phototherapy device based on a customized spectral LED array according to claim 1, characterized in that, When the total radiated power of the array is 30W, the target allocated power of the LED chips with peak wavelengths of 630nm, 660nm, 810nm, 850nm, 940nm, 1050nm, 1140nm, 1240nm and 1350nm are 2748.21mW, 3246.05mW, 4644.44mW, 4897.35mW, 4483.69mW, 5139.55mW, 2495.60mW, 2034.53mW and 310.59mW respectively.

4. The design method of a deep tissue phototherapy device based on a customized spectral LED array according to claim 1, characterized in that, The candidate LED chips have a package size of 3535 and a rated drive current of 700mA. Specifically, the operating voltage of LED chips with peak wavelengths of 630nm and 660nm is 2.1V to 2.5V; the operating voltage of LED chips with peak wavelengths of 810nm and 850nm is 1.5V to 1.9V; the operating voltage of LED chips with peak wavelengths of 940nm and 1050nm is 1.4V to 1.8V; the operating voltage of LED chips with a peak wavelength of 1140nm is 1.0V to 1.4V; and the operating voltage of LED chips with peak wavelengths of 1240nm and 1350nm is 0.9V to 1.3V.

5. The design method of a deep tissue phototherapy device based on a customized spectral LED array according to claim 1, characterized in that, The peak wavelengths of the candidate LED chips include 630nm, 660nm, 810nm, 850nm, 940nm, 1050nm, 1140nm, 1240nm, and 1350nm; the number of LED chips in the LED light source array corresponding to the peak wavelengths are 3, 4, 12, 10, 11, 13, 25, 25, and 4, respectively.

6. The design method of a deep tissue phototherapy device based on a customized spectral LED array according to claim 1, characterized in that, In the spectral fitting verification, the spectral similarity is the normalized dot product similarity, and the preset similarity threshold is not less than 95%; the spectral similarity between the fitted spectrum of the LED light source array and the reference spectral data in the range of 630nm to 1350nm is 99.05%.

7. The design method of a deep tissue phototherapy device based on a customized spectral LED array according to claim 1, characterized in that, An optical homogenizing and focusing component is used to form a 15cm diameter light spot at a distance of 14cm from the target surface, and the irradiance in the effective wavelength range of 630nm to 1350nm is controlled at 200mW / cm². 2 Up to 500mW / cm 2 .

8. The design method of a deep tissue phototherapy device based on a customized spectral LED array according to claim 1, characterized in that, The effective wavelength energy ratio of the LED light source array output is not less than 99%, and the total irradiance measured at a distance of 14cm from the target surface is 350mW / cm². 2 Furthermore, the total irradiance is used as the effective band irradiance for photobiological regulation of deep tissues.

9. The design method of a deep tissue phototherapy device based on a customized spectral LED array according to claim 1, characterized in that, The reference spectral data includes multiple data points in the range of 630nm to 1350nm, with a wavelength interval of 5nm between adjacent data points; the candidate spectral data of the candidate LED chip includes multiple peak wavelength data points in the range of 630nm to 1350nm, and the wavelength interval between the multiple peak wavelength data points is not fixed.

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