A method and apparatus for measuring optical biohazards

Abstract

The application provides a photobiological hazard measurement method, aiming at solving the problems of complicated switching, easy omission of hazard peak value and large measurement error of the existing measurement technology, adopting a two-dimensional array detector matched with a correction filter, and matching a target photobiological hazard weighting function; the maximum hazard area of a measured light-emitting surface is located through pixel merging measurement under the matching standard geometric condition, and a measurement value is obtained; a correction coefficient is calculated by combining a measured light radiation relative spectral power distribution to complete measurement value correction. A matching device realizes fast switching of multiple hazard measurements through a color wheel, and realizes efficient cooperation of area array and spectral measurement through a switching mechanism. The application can be adapted to irradiance and radiance hazard measurement, effectively improves measurement efficiency, precision and comprehensiveness, and is suitable for photobiological safety detection of various light-emitting products.

Description

Technical Field

[0001] This invention relates to the field of photobiological hazard measurement, and specifically to a photobiological hazard measurement method and device. Background Technology

[0002] Photobiological hazard assessment refers to the evaluation of potential hazards that light sources or lighting products may pose to human health, primarily involving the biological effects of light radiation on the eyes and skin. With the rapid development of technologies such as LED lighting, display devices, and medical light sources, the application scenarios of artificial light sources are becoming increasingly widespread. However, improper exposure to light radiation may cause various health risks, including retinal damage, blue light hazard, ultraviolet damage, and thermal damage. Organizations such as the International Electrotechnical Commission (IEC) and the European Union have established relevant standards requiring photobiological hazard assessments of light sources and luminaires to ensure that products meet safety requirements.

[0003] Photobiological hazard measurement involves various photobiological hazard assessment parameters, including photochemical ultraviolet hazard, corneal infrared radiation hazard, retinal blue light hazard, and retinal thermal hazard. Each hazard has a different spectral weighting function, and the corresponding measurement geometry varies significantly depending on the hazard type and severity. These measurement geometry conditions include imaging and non-imaging reception (corresponding to radiance and irradiance parameters, respectively), measurement aperture, measurement field of view, and measurement distance. Furthermore, finding the maximum corresponding evaluation parameter is often required in photobiological radiation safety measurements, further increasing the measurement difficulty.

[0004] The common method in existing technologies is to use a spectroradiometer and corresponding sampling device to set up the measurement geometry to measure spectral irradiance or spectral radiance, and then perform weighted integration with a spectral weighting function to obtain hazard assessment parameters. However, only one measurement geometry can be achieved in a single measurement, and switching between measurement geometry conditions can only be achieved by switching sampling devices. Moreover, it is necessary to repeatedly adjust the positional relationship between the measuring instrument and the object being measured to find the maximum value of the evaluation parameters. This process is often time-consuming and prone to oversights, resulting in significant measurement errors. Summary of the Invention

[0005] To address the shortcomings of existing technologies, this invention provides a photobiological hazard measurement method and device, which can quickly, efficiently, and accurately measure the maximum values ​​of various photobiological hazard evaluation parameters of the tested object, thereby accurately and objectively assessing the photobiological hazard level of the tested object.

[0006] To solve the above-mentioned technical problems, the technical solution adopted by the present invention is as follows:

[0007] This invention provides a method for measuring photobiological hazards. The measuring device includes a two-dimensional array detector and a correction filter. The correction filter matches the spectral responsivity of the sensing pixels in the two-dimensional array detector to a specified photobiological hazard weighting function. The process of measuring photobiological hazard evaluation parameters includes:

[0008] S1: At a specified distance, the measured light radiation passes through the correction filter and reaches the two-dimensional array detector, and the response of each sensing unit in the two-dimensional array detector to the measured light radiation is obtained.

[0009] S2: Based on the geometric requirements of the photobiological hazard assessment parameters and the sensor unit size of the two-dimensional array detector, determine the pixel merging range corresponding to the photobiological hazard assessment parameters; using the pixel merging range as the measurement area, calculate the average value of the light radiation response of each measurement area in the two-dimensional array detector, and select the maximum average value as the measured value G.

[0010] S3: Calculate the correction coefficient K based on the relative spectral power distribution of the measured light radiation and the photobiohazard weighting function, and use the correction coefficient K to correct the measured value G in step S2 to obtain the corrected photobiohazard evaluation parameters.

[0011] In the above technical solution, the two-dimensional array detector consists of a large number of arrayed pixels, possessing key characteristics such as known spectral responsivity and insensitivity to polarized light. It can simultaneously capture the spatial distribution and intensity information of light radiation. By using a color filter correction, the spectral responsivity of the sensing pixels of the two-dimensional array detector can be matched to a specified photobiological hazard weighting function. The geometric conditions of the photobiological hazard assessment parameters include imaging or non-imaging reception conditions, measurement distance, and reception area. waitIn this context, imaging reception conditions correspond to radiance measurement scenarios, while non-imaging reception conditions correspond to irradiance measurement scenarios. In photobiological hazards, radiance-based evaluation parameters are generally used for hazards related to the retina, while irradiance-based evaluation parameters are used for hazards related to the skin and eye surfaces. In actual measurements, when the radiance field of view is small, it can be achieved through irradiance geometry. For example, retinal thermal hazards are evaluated using thermal hazard-weighted radiance. Imaging measurement conditions are used, referencing the actual application of the measured object. The measurement distance is 200 mm, 1 m, or other distances, and the aperture at the imaging lens is 7 mm. Depending on the hazard level, the measurement field of view includes 0.011 rad and 0.1 rad. According to this measurement geometry requirement, an imaging lens and aperture stop are set in front of a two-dimensional array detector, and the entrance pupil is positioned at a specified distance from the measured object to achieve light radiation image measurement. The pixel areas corresponding to the 0.011 rad and 0.1 rad field of view are used as the measurement areas, and the average maximum response value of each measurement area is calculated to obtain the hazard-weighted radiance value. By selecting the maximum output value from the light radiation image, the most severe hazard conditions can be accurately captured, avoiding misjudgments of safety risks due to the omission of local peaks, and ensuring that the measurement results reflect the characteristics of the most dangerous radiation area of ​​the light source. Addressing the issue that correction filters may not perfectly match the spectral responsivity of the sensing pixels with the photobiological hazard weighting function, resulting in spectral mismatch, step S3 further uses a correction coefficient K for compensation. The correction value is calculated by combining the relative spectral power distribution of the measured light radiation with the target weighting function, significantly reducing or eliminating this spectral mismatch error, thereby achieving higher measurement accuracy. This technical solution is highly versatile, covering a wide range of objects including various lamps and lamp systems, products for intentional and unintentional viewing, ophthalmic measuring instruments, LED light-emitting devices, etc. Simultaneously, the objects under test may also be products with similar functions to traditional light sources but excited by lasers, such as laser projectors, automotive laser lights, and other laser-excited broadband light sources.

[0012] Irradiance measurement is a measurement method under non-imaging receiving conditions. Its core is the light radiation flux within a specified receiving surface. In this type of measurement, the pixel merging region directly corresponds to the area covered by its physical size. The number of merged pixels is calculated based on the size of a single sensing unit in the two-dimensional array detector. For example, if the required measurement diameter for hazard-weighted irradiance is 1 mm, and the size of a single sensing unit in the two-dimensional array detector (considering the spacing between sensing units) is 2 μm, then the pixel merging region is a circular area with a diameter of 500 sensing units on the photosensitive surface of the two-dimensional array detector. Using the pixel merging range determined above as a single measurement area, the entire effective area of ​​the photosensitive surface of the two-dimensional array detector is traversed, and the average value of the light radiation response of all sensing units within each measurement area is calculated. The maximum value among all average values ​​is selected as the measurement value corresponding to the irradiance evaluation parameter, and the measurement proceeds to the correction step in step S3.

[0013] Radiance measurement is a measurement method under imaging reception conditions. Its core is to image the object being measured and measure the light radiant flux within a specified field of view. This type of measurement requires an imaging lens and an aperture stop in front of a two-dimensional array detector, and the measurement is completed through a conjugate imaging optical path. The determination of the pixel merging region is based on the standard required field of view, combined with the field of view calibration values ​​of the two-dimensional array detector's sensing units. First, the object-side field of view of a single sensing unit of the two-dimensional array detector is calibrated: a scale is placed at a specified measurement distance, and the length of the scale that the two-dimensional array detector can detect in one direction is read. The field of view corresponding to a single sensing unit can be calculated as: scale length / measurement distance / number of sensing units in that direction. The measurement generally also requires an aperture stop simulating the human eye's pupil to control the amount of light entering; its size is typically 7 mm. Subsequently, based on the standard field-of-view angle requirement corresponding to the radiance measurement, such as 0.011 rad or 0.1 rad, the ratio is calculated with the calibrated object-side field-of-view angle of a single sensing unit to obtain the number of sensing units to be merged. Finally, using the pixel merging range determined above as a single measurement area, the entire effective imaging area of ​​the photosensitive surface of the two-dimensional array detector is traversed, and the average value of the light radiation response of all sensing units in each measurement area is calculated. The maximum value is selected from all average values ​​as the measurement value corresponding to the radiance evaluation parameter, and then proceeds to the correction step S3.

[0014] As a technical solution, the photobiological hazard weighting function includes, but is not limited to, a photochemical ultraviolet hazard spectral weighting function, a corneal infrared radiation hazard spectral weighting function, a retinal blue light hazard spectral weighting function, a retinal thermal hazard spectral weighting function, an iris radiation hazard weighting function, an aphakic photochemical hazard weighting function, or a rectangular window function within a specified wavelength range used for custom band assessment. The aforementioned photobiological hazard weighting functions and measurement geometry can be obtained according to standards GB / T 20145, ISO 15004-2, and GB / T 30117.1, and the corresponding spectral response curves and calculation methods can also be determined through relevant standards. Among them, the targets of photochemical ultraviolet hazard and corneal infrared radiation hazard are human skin and anterior eye tissues. The imaging effect of the human eye's refractive system does not need to be considered. The corresponding risk assessment is completed using irradiance-based photobiological hazard assessment parameters. The targets of retinal blue light hazard and retinal thermal hazard are the fundus retinal tissue after imaging by refractive media such as the human eye's lens. The imaging geometry of the human eye needs to be matched. The corresponding measurement and risk assessment are completed using radiance-based photobiological hazard assessment parameters.

[0015] As a technical solution, the method for calculating the correction coefficient K in step S3 is as follows:

[0016]

[0017] in, The relative spectral power distribution of a standard light source used for calibrating and tracing two-dimensional array detectors. The relative spectral power distribution of the object under test can be obtained through actual measurement using a spectral measurement module. The relative spectral sensitivity of the sensing element of a two-dimensional array detector with known corrected color filters can be obtained through calibration. The weighting function for the aforementioned photobiological hazards can be determined through relevant standards. and They are respectively The minimum and maximum values ​​of the function's wavelength range.

[0018] The above technical solution compensates for residual spectral mismatch errors between the combined spectral response of the two-dimensional array detector and the standard weighting function under a standard light source, and between the actual response of the two-dimensional array detector and the weighting function under the measured object. This eliminates system measurement errors introduced by the difference in spectral distribution between the measured object and the calibration standard light source. The calibration of the two-dimensional array detector strictly matches the geometric conditions of the corresponding measurement mode, and is divided into calibration under non-imaging geometric conditions and calibration under imaging geometric conditions. Calibration under non-imaging geometric conditions, matching irradiance-based photobiohazard assessment parameters to non-imaging receiving measurement modes, can be implemented using metrologically traceable irradiance standard lamps or light intensity standard lamps with distributed color temperature. During calibration, an irradiance standard lamp is placed at the calibration distance. The light radiation emitted by the irradiance standard lamp passes through a field-of-view aperture and a correction filter before being incident on the photosensitive surface of the two-dimensional array detector. The responses of each sensing unit of the two-dimensional array detector are collected. The hazard-weighted irradiance of the irradiance standard lamp is obtained by combining its standard irradiance value and relative spectral power distribution, thus completing the irradiance response calibration of each sensing unit in the two-dimensional array detector. For calibration under imaging geometry conditions, an imaging receiving measurement mode matching the photobiohazard assessment parameters of radiance is used. A metrologically traceable standard radiance light source is employed. During calibration, the standard radiance light source is placed in the object plane of the imaging optical path, ensuring that the emitting surface of the standard radiance light source is completely imaged within the effective area of ​​the photosensitive surface of the two-dimensional array detector by the imaging lens. The response outputs of each sensing unit of the two-dimensional array detector are collected. The hazard-weighted radiance parameters of the standard radiance light source are obtained by combining its standard radiance value and relative spectral power distribution, thus completing the object-side field-of-view calibration of each sensing unit.

[0019] As a technical solution, in step S3, the spectral power distribution of the light radiation corresponds to the light radiation received by the region with the maximum average value in step S2. It should be noted that in practical applications, the object under test may exhibit spectral inhomogeneity, meaning that the light radiation emitted from different luminous regions of the object may have different spectral compositions. For example, some laser-excited broadband light sources, multi-chip integrated LED devices, and multi-color splicing display panels may have significantly different spectral power distributions in different regions of their luminous surfaces. If the average spectral power distribution of the entire object under test is used to calculate the correction coefficient K, it will fail to match the actual spectral characteristics of the high-hazard region (i.e., the measurement region corresponding to the maximum average value in step S2), leading to spectral mismatch correction deviation, affecting measurement accuracy, and even distorting the hazard level determination result. This technical solution specifically selects the light radiation received by the region corresponding to the maximum average value in step S2 to obtain its relative spectral power distribution, so that the calculated correction coefficient K can accurately match the actual spectral characteristics of the region with the highest photobiological hazard level, avoiding the correction error introduced by the spectral spatial inhomogeneity of the light source under test.

[0020] As a technical solution, the object under test includes two or more light sources with different relative spectral powers. The spectral power distribution of the light radiation in step S3 is obtained using one of the following methods: using a limiting aperture to define the spectral measurement area as the region corresponding to the maximum average value in step S2, wherein the limiting aperture is an aperture stop or a field stop; or measuring the comprehensive relative spectral power distribution of the object under test and extracting the relative spectral power distribution of the region corresponding to the maximum average value based on the photobiological hazard weighting function. In multi-light source scenarios, the measurement of the spectral power distribution of light radiation in step S3 can be performed in two specific ways: one is to use a limiting aperture to physically define the spatial range of the spectral measurement. Its light transmission size and installation position can be adapted and adjusted according to the size and spatial position of the measurement area corresponding to the maximum average value determined in step S2, ensuring that the receiving field of view of the spectral measurement matches the spatial range of the maximum hazard area. In practice, by physically blocking the aperture, the light radiation interference from other light-emitting units in the tested object is effectively shielded, allowing only the light radiation from the region corresponding to the maximum average value to pass through the aperture for measurement. This allows for direct and accurate acquisition of the light radiation signal, obtaining the relative spectral power distribution of that region, minimizing spectral interference from other light-emitting units, and directly locking the true spectral characteristics of the most hazardous region. This provides reliable data support for the accurate calculation of the correction coefficient K, and is particularly suitable for scenarios where multiple light sources are relatively dispersed and the boundaries of the most hazardous region are clear. Alternatively, the comprehensive relative spectral power distribution of the tested object is measured first, i.e., the overall spectral information of all light sources superimposed on the entire tested object is collected to obtain the comprehensive radiation power data at each wavelength. Subsequently, based on the weight distribution characteristics of the photobiological hazard weighting function, the spectral component that plays a dominant role in the photobiological hazard of the target within the measurement region corresponding to the maximum average value in step S2 is extracted from the comprehensive relative spectral power distribution and used as the input parameter for calculating the correction coefficient. For example, when the object under test is a red-blue combined light source, and the target evaluation parameter is retinal blue light hazard, according to the characteristics of the retinal blue light hazard spectral weighting function specified in relevant standards, the blue light component (usually the 400 nm-500 nm band) plays a major role in contributing to retinal blue light hazard, while the contribution weight of the red light component outside this band is close to 0. In this case, the relative spectral power distribution of the blue light band can be extracted from the comprehensive relative spectral power distribution using the weight distribution of this photobiological hazard weighting function, eliminating the interference of the red light component's spectral components, and ensuring that the correction coefficient K can accurately match the spectral characteristics that dominate the target hazard. This method does not require spatial physical confinement of the measured light radiation and is suitable for measurement scenarios where the spectra of multiple emitting units are closely superimposed and cannot be accurately separated spatially using an aperture. Through targeted extraction of spectral components, correction errors caused by multi-spectral superposition and confusion can be effectively avoided, ensuring correction accuracy.

[0021] As a technical solution, under the condition of ensuring the geometric condition of photobiological hazard assessment, the relative pose relationship between the two-dimensional array detector and the object under test is changed. Steps S1 to S3 are repeated under each pose relationship to obtain the photobiological hazard assessment parameters for the corresponding pose, and the maximum value is compared and output. The relative pose relationship includes spatial rotation and planar translation. Spatial rotation can be performed around the emitting center of the object under test, the main optical axis of light radiation emission, or a preset reference axis, with multi-angle adjustments of horizontal azimuth and elevation angles. Planar translation can be performed along a plane perpendicular to the receiving optical axis of the two-dimensional array detector, with horizontal and vertical translation traversal. The step size and angle range of pose adjustment can be flexibly set according to the shape and size of the object under test, the distribution characteristics of the emitting surface, and the spatial radiation distribution characteristics, ensuring that there are no spatial measurement blind spots during the traversal process and that the entire effective radiation range of the object under test is fully covered. Throughout the entire relative pose adjustment and measurement process, the core measurement parameters remain constant, including but not limited to: the reference measurement distance between the two-dimensional array detector and the emitting surface of the object under test, and the optical system configuration (correction filters, imaging lenses, aperture specifications, and relative installation positions).

[0022] The above technical solution effectively solves the technical deficiency that single-pose measurement cannot cover the entire effective radiation area of ​​the tested object, and adapts to the actual engineering characteristics of the spatial anisotropy of the light radiation of the tested object. Even if the tested object has irregular shape, dispersed spatial distribution of emitting surface, and significant differences in radiation intensity and spectral characteristics in different orientations, it can accurately capture the highest photobiological hazard level in the entire radiation range of the tested object through full-space multi-pose traversal measurement, completely avoiding the underestimation of hazard level due to measurement space omissions, greatly improving the comprehensiveness, accuracy and reliability of photobiological hazard measurement, and fully meeting the photobiological safety compliance evaluation needs of various irregularly shaped, large-size, and spatially anisotropic emitting products.

[0023] As a technical solution, an imaging lens and an aperture stop are set in the optical path in front of the two-dimensional array detector. In step S2, the pixel merging range is determined according to the field of view range required for the photobiological hazard assessment parameters. For radiance-based photobiological hazard assessment parameters such as retinal blue light hazard and retinal thermal hazard, which require measurement using an imaging reception mode, an imaging lens, an aperture stop, and a correction filter are sequentially set in the incident optical path of the two-dimensional array detector to construct a conjugate imaging optical path. The conjugate imaging optical path is used to accurately image the emitting surface of the object under test onto the photosensitive surface of the two-dimensional array detector, realizing spatial resolution imaging of the emitting surface under test and matching the imaging reception measurement requirements of radiance-based photobiological hazard assessment parameters. In this technical solution, the field of view corresponding to the sensing unit size of the two-dimensional array detector has been calibrated through object-image relationship. Based on the standard requirements corresponding to the photobiological hazard assessment parameters of the target radiance, the target field of view required for measurement is determined; then, the ratio of the target field of view to the object-side field of view of a single sensor unit obtained from the above calibration is calculated to obtain the number of sensor units that need to be merged to meet the field of view requirements. The adjacent sensor unit array corresponding to this number is the pixel merging range of this measurement.

[0024] As a technical solution, the geometric condition is non-imaging reception, with a field stop set in the optical path in front of the two-dimensional array detector to limit the receiving angle. For irradiance-based photobiological hazard assessment parameters such as photochemical ultraviolet hazards and corneal infrared radiation hazards, which require measurement using a non-imaging reception mode, the evaluation targets are human skin and anterior eye tissues. The imaging effect of the human eye's refractive system does not need to be considered; only the integrated light radiant flux within the target receiving surface is measured. In this technical solution, a field stop is set in the incident optical path of the two-dimensional array detector to limit the measurement receiving angle. The receiving angle limits the direction of light rays incident on the receiving surface, typically 1.4 rad. The light radiation emitted from the object under test is incident on the field stop, passes through the correction filter, and finally reaches the photosensitive surface of the two-dimensional array detector. The inner wall of the aperture of the field stop is treated with an anti-reflection blackening process to further suppress stray light generated by aperture wall reflection, improving accuracy and stability in low-light measurement scenarios.

[0025] This invention also provides a measuring device for the aforementioned photobiological hazard measurement method, comprising a two-dimensional array detector, a color wheel, and a data control and analysis module. The color wheel is positioned in the measurement optical path before the two-dimensional array detector. Multiple apertures are provided on the color wheel, and two or more correction filters are respectively disposed in different apertures. The rotation of the color wheel drives the correction filter at any aperture to be switched into the measurement optical path, allowing light radiation from the object under test to be filtered by the correction filter before entering the two-dimensional array detector, thus achieving rapid switching measurement of different types of photobiological hazards. The two-dimensional array detector is communicatively connected to the data control and analysis module, enabling real-time transmission of the collected light radiation response data to the data control and analysis module for subsequent processing and calculation. This technical solution achieves time-division acquisition of multi-band light radiation through rapid switching of the color wheel, adapting to the integrated measurement requirements of different types of light sources and different types of photobiological hazards. It possesses advantages such as strong versatility, high measurement efficiency, stable accuracy, and convenient operation. For the relative spectral power distribution of the measured object, this device can adopt two adaptation methods: First, when the relative spectral power distribution of the measured object has been pre-calibrated and is a known parameter, the data can be directly input into the control and analysis module for the calculation of the correction coefficient, thus achieving rapid measurement; Second, a spectral measurement module can be integrated inside the measuring device, or a spectral measurement module can be connected through an external interface to perform parallel measurements of the relative spectral power distribution of the measured object, providing reliable support for the accurate calculation of the correction coefficient and further improving the measurement accuracy.

[0026] As a technical solution, the system also includes a spectral measurement module and a switching mechanism. The switching mechanism simultaneously or sequentially switches the light radiation from the object under test to the measurement optical path containing the two-dimensional array detector and the spectral measurement module for measurement. The spectral measurement module is communicatively connected to the data control and analysis module. The spectral measurement module can be a spectrometer, which collects and outputs the relative spectral power distribution of the measured light radiation, providing accurate spectral input data for calculating the correction coefficient and ensuring the accuracy and versatility of the measurement results.

[0027] As a technical solution, it also includes an imaging lens. The light emitted by the object under test is received and measured by a two-dimensional array detector through the imaging lens and the correction filter. By constructing a conjugate imaging optical path through the imaging lens, spatial resolution imaging of the emitting surface under test can be achieved, matching the imaging reception and measurement requirements of radiance-type photobiological hazard evaluation parameters such as retinal blue light hazard and retinal thermal hazard.

[0028] As one technical solution, the switching mechanism includes a linear guide rail or a rotating guide rail; a two-dimensional array detector and a spectral measurement module are arranged on the linear guide rail or the rotating guide rail, and the switching measurement of the detector is realized by the linear movement or rotation of the guide rail; or the switching mechanism is a reflector that can be cut into or out of the measurement optical path. When the reflector is cut into the optical path, the measured light radiation is deflected by the reflector and then incident on the spectral measurement module to realize the measurement of the spectral measurement module. When the reflector is cut out of the optical path, the measured light radiation is directly incident on the two-dimensional array detector to realize the measurement of the area array light radiation response.

[0029] As a technical solution, the switching mechanism is a beam splitter, which divides the light emitted by the object under test into two or more paths, one of which is incident on a two-dimensional array detector, and the other is incident on a spectral measurement module. The beam splitter is generally a semi-transparent, semi-reflective mirror.

[0030] Furthermore, the switching mechanism is integrated into an empty slot on the color wheel and can enter or exit the measurement optical path as the color wheel rotates. Only when the slot with the integrated switching mechanism rotates with the color wheel to the measurement optical path position and the switching mechanism is entered into the optical path, a spectral measurement optical path is formed from the object under test through the switching mechanism to the spectral measurement module, completing the measurement of spectral power distribution. When the color wheel drives the slot with the correction filter to rotate to the measurement optical path position, the switching mechanism rotates away from the optical path with the color wheel, performing area array measurement of the two-dimensional array detector. This configuration highly integrates the spectral measurement switching mechanism with the filter switching color wheel, eliminating the need for separate drive and switching mechanisms, significantly simplifying the overall structure of the device, improving the coaxiality and switching accuracy of the optical path, and reducing the hardware cost and size of the device. Optionally, one or more plane mirrors are also included to fold the optical path, further reducing the instrument size.

[0031] The beneficial effects of this invention are as follows: This invention discloses a method for measuring photobiological hazards. Through a core architecture of a two-dimensional array detector paired with a correction filter, it achieves precise matching between the detector's spectral response and the standard photobiological hazard weighting function. By employing a pixel-merging measurement method that matches standard geometric conditions, it can automatically traverse and locate the maximum hazard area of ​​the measured luminescent surface, meeting the core requirements of photobiological safety evaluation standards and avoiding the peak omission problem of single-point measurements. Combined with a spectral correction scheme that precisely matches the maximum hazard area, it can effectively compensate for residual errors due to spectral mismatch and solve the correction deviation problem caused by spectral inhomogeneity in multi-source scenarios. Through a multi-pose traversal measurement scheme, it can completely cover the entire effective radiation range of the measured object in space, avoiding underestimation of the hazard level of spatially anisotropic light sources. Meanwhile, the supporting measuring device enables rapid switching between multiple types of hazard measurements through a color wheel, and achieves efficient coordination between area array measurement and spectral measurement through multiple optical path switching mechanisms. The overall structure is compact, highly integrated, and highly versatile, and can simultaneously adapt to the measurement needs of both irradiance-type and radiance-type photobiological hazards. The measurement results are accurate and traceable, and it can be widely used in photobiological safety compliance testing scenarios for various luminescent products. It has the core advantages of high measurement efficiency, stable accuracy, strong versatility, and convenient operation. Attached Figure Description

[0032] Appendix Figure 1 This is a schematic diagram of a photobiological hazard measurement device provided in Embodiment 1 of the present invention;

[0033] Appendix Figure 2 This is a schematic diagram of a photobiological hazard measurement device provided in Embodiment 2 of the present invention;

[0034] Appendix Figure 3 This is a schematic diagram of a photobiological hazard measuring device provided in Embodiment 4 of the present invention;

[0035] Appendix Figure 4 This is a schematic diagram of another photobiological hazard measuring device provided in Embodiment 4 of the present invention;

[0036] Appendix Figure 5 This is a schematic diagram of the comprehensive spectral power distribution provided in Embodiment 4 of the present invention;

[0037] Appendix Figure 6 This is a schematic diagram of the blue light spectral power distribution provided in Embodiment 4 of the present invention;

[0038] Appendix Figure 7 This is a schematic diagram of a photobiological hazard measurement device provided in Embodiment 5 of the present invention;

[0039] In the figure, 1 is the field stop, 2 is the two-dimensional array detector, 3 is the aperture stop, 4 is the object under test, 5 is the color wheel, 6 is the data control and analysis module, 7 is the spectral measurement module, 8 is the switching mechanism, 9 is the imaging lens, 10 is the correction filter, 11 is the drive motor, 12 is the entrance slit, 13 is the dispersive element, and 14 is the second array detector. Detailed Implementation

[0040] The technical solution of the present invention will be further clearly and completely described below with reference to specific embodiments. The embodiments described below are only preferred embodiments of the present invention, used to help understand the core concept of the present invention, and should not be regarded as limiting the scope of protection of the present invention. All other embodiments obtained by those skilled in the art based on the core concept of the present invention without creative effort are within the scope of protection of the present invention. The experimental methods in this embodiment that do not specify specific conditions are all implemented in accordance with conventional optical radiation metrology standards and optical measurement specifications in the art. All optical components are coaxially arranged along the main optical axis of measurement to ensure the stability of optical path transmission and the accuracy of measurement results.

[0041] Example 1

[0042] This embodiment provides a photobiological hazard measurement device and method in a non-imaging receiving mode, applicable to the measurement of photobiological hazards such as photochemical ultraviolet hazard and corneal infrared radiation hazard based on irradiance parameters. Figure 1As shown, this embodiment provides a photobiohazard measurement device, including a switching mechanism 8, a field stop 1, a color wheel 5, a two-dimensional array detector 2, a spectral measurement module 7, and a data control and analysis module 6. The switching mechanism 8 is a plane mirror that can be cut in and out of the measurement optical path. The field stop 1 is used to limit the measurement area to achieve measurement of the measured light radiation within a specified receiving angle. In this embodiment, the field stop 1, the color wheel 5, and the two-dimensional array detector 2 are arranged sequentially along the optical path. When the plane mirror cuts out of the measurement optical path, the light radiation emitted from the object under test 4 passes sequentially through the field stop 1 and the corresponding correction filters 10 on the color wheel 5 before reaching the photosensitive surface of the two-dimensional array detector 2. When the plane mirror enters the measurement optical path, the light radiation emitted from the object under test 4 is deflected by the plane mirror before reaching the spectral measurement module 7, thus achieving spectral measurement. The inner wall of the aperture of the field stop 1 is treated with a matte black finish to limit the receiving angle of the two-dimensional array detector 2 to 1.4 rad, matching the measurement geometry requirements of photochemical ultraviolet hazard (the aperture can also be replaced with a corresponding aperture to achieve flexible adjustment of the receiving angle and measurement area according to different measurement needs). A color wheel 5 is positioned in the optical path between the field stop 1 and the two-dimensional array detector 2. A drive motor 11, a stepper motor, is connected to the center of the color wheel 5 via a rotating shaft. This drive motor 11 communicates with the data control and analysis module 6 and can receive commands from the module to achieve precise rotation control. Five holes are evenly distributed circumferentially on the end face of the color wheel 5. Different correction filters 10 are fixedly installed in each of these holes. The spectral transmittance characteristics of each correction filter 10 are matched to the standard weighting functions of different types of photobiological hazards, such as photochemical ultraviolet hazard, near-ultraviolet hazard, corneal infrared radiation hazard, and iris radiation hazard. These filters are used to correct the pixel spectral responsivity of the two-dimensional array detector 2 sensing unit to the target weighting function corresponding to the hazard. The two-dimensional array detector 2 is a CMOS area array detector, internally composed of arrayed sensing units, each with a physical size of 3μm × 3μm (including inter-unit spacing). The two-dimensional array detector 2 is communicatively connected to the data control and analysis module 6, enabling real-time transmission of the acquired optical radiation response data. The spectral measurement module 7 is a high-resolution fast spectrometer, including an entrance slit 12, a dispersive element 13, and a second array detector 14. It can accurately acquire the relative spectral power distribution of the measured optical radiation. The spectral measurement module 7 is also communicatively connected to the data control and analysis module 6, enabling real-time transmission of the acquired spectral data. The data control and analysis module 6 is a computer with a built-in standardized photobiological hazard measurement program. It can perform drive control of all hardware components, signal acquisition, data processing, calibration calculation, and automatic hazard level determination. It also pre-stores standard light source parameters and system calibration parameters with metrological traceability, providing data support for measurement calculations.

[0043] The photobiological hazard irradiance measurement method based on the above-mentioned device in this embodiment is as follows:

[0044] A1: System Calibration. An irradiance standard lamp traceable by a national metrology institution is used as the calibration benchmark. The distance from the irradiance standard lamp to the array detector is set as the calibration distance of the standard lamp. The light radiation emitted by the irradiance standard lamp passes through a field stop and a correction filter before being incident on the photosensitive surface of the two-dimensional array detector. The responses of each sensing unit of the two-dimensional array detector under each correction filter are collected. Combining the standard spectral irradiance value of the irradiance standard lamp with the photobiological hazard weighting function corresponding to each correction filter, the hazard-weighted irradiance standard value generated by the irradiance standard lamp at the two-dimensional array detector is obtained. This standard value is used to complete the irradiance response calibration of each sensing unit in the two-dimensional array detector under each correction filter. All calibration parameters are pre-stored in the data control and analysis module.

[0045] A2: Acquisition of Optical Radiation Response Data. The object under test is fixed on the optical adjustment frame. The relative position of the object under test and the measuring device is adjusted so that the emitting surface of the lamp is parallel to the photosensitive surface of the two-dimensional array detector, with a measurement distance of 200 mm between them. The data control and analysis module sends commands to drive the color wheel to rotate, switching each correction filter into the measurement optical path. Simultaneously, the switching mechanism (i.e., the plane mirror) is controlled to cut out the measurement optical path, ensuring that the measured light radiation is incident on the two-dimensional array detector. The two-dimensional array detector is activated to complete the acquisition of the optical radiation signal, and the raw response data is transmitted to the data control and analysis module in real time.

[0046] A3: Pixel Merging Range Determination and Measurement Value Calculation. The data control and analysis module determines the pixel merging range for this measurement based on the geometric requirements of photobiological hazard measurement and the pre-stored physical size of a single sensing unit (3μm). Taking the measurement and evaluation of medical equipment as an example, the weighted ultraviolet hazard irradiance... The evaluation area is 3mm. Therefore, for the light radiation image under the photochemical ultraviolet hazard function correction filter, after geometric conversion, the pixel merging range is a circular area with a diameter of 1000 sensing units. Taking this pixel merging range as a single measurement area, the sliding window traversal method is used to cover the entire effective photosensitive area of ​​the two-dimensional array detector. The average value of the light radiation response of all sensing units in each measurement area is calculated. Finally, the maximum value is selected from all the average values ​​as the basic measurement value G for this measurement. At the same time, the measurement area corresponding to the maximum average value is locked as the maximum hazard area of ​​weighted ultraviolet radiation.

[0047] A4: Acquisition of spectral data for the area of ​​greatest hazard. A plane mirror is inserted into the measurement optical path, so that the light radiation from the area of ​​greatest hazard is deflected by the mirror and then incident on the spectral measurement module. The relative spectral power distribution is measured.

[0048] A5: Correction Coefficient Calculation. The data control and analysis module will combine the acquired relative spectral power distribution of the measured object with the pre-stored relative spectral power distribution of the irradiance standard lamp, the relative spectral sensitivity of the two-dimensional array detector sensing unit, and the photochemical ultraviolet hazard standard weighting function to calculate the correction coefficient K according to the following formula:

[0049]

[0050] in, The relative spectral power distribution of the irradiance standard lamp used to calibrate the two-dimensional array detector. The relative spectral power distribution of the area of ​​greatest hazard to the tested object. The relative spectral sensitivity of the sensing unit of the two-dimensional array detector after the color filter has been corrected. The photochemical ultraviolet hazard spectral weighting function is used. The wavelength of light radiation. and They are respectively The minimum and maximum values ​​of the function's wavelength range.

[0051] A6: Measurement Value Correction and Result Output. Using the calculated correction coefficient K, the basic measurement value G obtained in step A3 is corrected to obtain the calibrated photochemical ultraviolet hazard weighted irradiance parameter. The data control and analysis module compares this parameter with the pre-stored hazard level threshold, automatically completes the photobiological hazard level determination of the tested lamp, and outputs the final result.

[0052] Example 2

[0053] This embodiment provides a photobiological hazard measurement device in a non-imaging receiving mode, suitable for detecting photobiological hazards such as photochemical ultraviolet hazard, near-ultraviolet hazard, and corneal infrared radiation hazard based on irradiance parameters. It differs from Embodiment 1 in that... Figure 2 As shown, in this embodiment, the switching mechanism 8 is a plane mirror, which is set on the hole of the color wheel 5 and can enter or exit the measurement optical path as the color wheel 5 rotates; the measurement optical path from the object under test 4 through the switching mechanism 8 to the spectral measurement module 7 is formed only when the switching mechanism 8 is entered into the measurement optical path, thus completing the spectral acquisition; when the color wheel drives the hole with the correction filter 10 to rotate into the measurement optical path, the plane mirror rotates away from the optical path with the color wheel 5, and the measured light radiation is incident on the two-dimensional array detector 2 to complete the area array acquisition.

[0054] To address situations where the tested object has an irregular shape and significant differences in radiation intensity and spectral characteristics at different orientations, this embodiment mounts the tested object on a high-precision motorized turntable and the measuring device on a three-dimensional translation stage for multi-pose spatial traversal measurements. While maintaining constant core measurement conditions such as measurement distance and field-of-view aperture specifications, the relative pose of the measuring device and the tested object is adjusted using the high-precision motorized turntable and the three-dimensional translation stage: multi-angle traversal measurements are performed around the luminaire's light-emitting center and the principal optical axis of light radiation emission, with elevation angles from 0° to 90° and horizontal azimuth angles from 0° to 360°, fully covering the luminaire's entire effective spatial radiation range. Under each adjusted relative pose, the measurement process described in Embodiment 1 is completely repeated to obtain the photochemical ultraviolet hazard weighted irradiance parameters for the corresponding pose.

[0055] After all pose measurements are completed, the data control and analysis module compares the measurement results of all poses and outputs the maximum weighted irradiance value in the entire space range as the final measurement result. The final measurement result is compared with the preset photochemical ultraviolet hazard emission limit, and the photobiological hazard level of the tested object is automatically determined and a standardized measurement report is generated.

[0056] Example 3

[0057] This embodiment provides a photobiological hazard measurement device and method in imaging reception mode, applicable to the detection of photobiological hazards such as retinal blue light hazard and retinal thermal hazard based on radiance parameters. The measured object includes RGB three-color light sources, and the target of this measurement is retinal blue light hazard.

[0058] This embodiment provides a photobiohazard measurement device, including an imaging lens 9, an aperture stop 3, a color wheel 5, a switching mechanism 8, a two-dimensional array detector 2, a spectral measurement module 7, and a data control and analysis module 6. In this embodiment, the switching mechanism 8 is a linear moving guide rail, on which the two-dimensional array detector 2 and the spectral measurement module 7 are respectively mounted. Switching measurement is achieved through the linear movement of the guide rail. When measuring the response value of the measured light radiation, such as... Figure 3As shown, the aperture stop 3, imaging lens 9 (optical lens), color wheel 5, and two-dimensional array detector 2 are arranged sequentially along the optical path, forming a conjugate imaging optical path between the emitting surface of the object under test and the photosensitive surface of the two-dimensional array detector. The color wheel 5 is located on the optical path between the aperture stop 3 and the two-dimensional array detector 2. The center of the color wheel 5 is connected to a drive motor 11 via a rotating shaft. The drive motor 11 is communicatively connected to the data control and analysis module 6 and can receive instructions from the data control and analysis module 6 to complete precise rotation control. Five holes are evenly distributed circumferentially on the end face of the color wheel 5, and different correction filters 10 are fixedly installed on them. The spectral transmittance characteristics of each correction filter 10 are matched with the standard weighting functions of different types of photobiological hazards such as retinal blue light hazard, retinal thermal hazard, and aphakic photochemical hazard, which can correct the spectral responsivity of the two-dimensional array detector sensing unit to the target weighting function of the corresponding hazard. The two-dimensional array detector 2 is a CCD area array detector, which is communicatively connected to the data control and analysis module 6; the spectral measurement module 7 is a fiber optic spectrometer, which is also communicatively connected to the data control and analysis module 6 and can acquire the relative spectral power distribution of the measured light radiation. When measuring and acquiring the relative spectral power distribution of the measured light radiation, such as... Figure 4 As shown, the spectral measurement module 7 is inserted into the optical path via a linear moving guide rail. A field stop 1 is also provided on the optical path in front of the spectral measurement module 7. The field stop 1 is as close as possible to the object under test 4 to define the measurement area. The data control and analysis module 6 is a microprocessor or embedded industrial control host with a built-in standardized photobiological hazard measurement program. It can complete the drive control of all hardware components, signal acquisition, data processing, correction calculation, and automatic hazard level determination. At the same time, it pre-stores system calibration parameters, field angle calibration parameters, standard light source parameters, and standard hazard weighting function data.

[0059] The photobiological hazard radiance measurement method based on the above-mentioned device in this embodiment is as follows:

[0060] B1: System Calibration. First, the object-side field of view (FSR) of a single sensing unit in the 2D array detector is calibrated: A ruler is placed at the measurement distance, and the focusing parameters of the imaging lens are adjusted so that the ruler is clearly imaged on the photosensitive surface of the 2D array detector. The length of the ruler that the 2D array detector can detect in that direction is read. The FSR of a single sensing unit is calculated using geometric relationships. The formula is: FSR of a single sensing unit = Ruler length / Measurement distance / Number of sensing units in that direction. In this embodiment, the ruler length is 40.96 mm, the measurement distance is 200 mm, the number of sensing units in that direction is 2048, and the FSR of a single sensing unit is 0.0001 rad. Radiation responsivity calibration is performed using a standard luminance source: the color wheel is driven to rotate, the corresponding correction filter is switched to the measurement optical path, the standard luminance source is placed in the object plane of the imaging optical path, and the response output of each sensing unit of the two-dimensional array detector is collected; the standard radiance value, relative spectral power distribution, and photobiohazard weighting function of the correction filter are combined with the standard radiance value of the standard luminance source, the relative spectral power distribution, and the photobiohazard weighting function of the correction filter are used to calculate the target hazard weighted radiance parameters of the standard luminance source, and the radiance responsivity calibration of each sensing unit in the two-dimensional array detector is completed. The calibration parameters are pre-stored in the data control and analysis module.

[0061] B2: Acquisition of Optical Radiation Response Data. The RGB three-color light source to be measured is fixed on the optical adjustment frame, ensuring the emitting surface of the panel is perpendicular to the main optical axis of the measuring device. The measurement distance is set to 200 mm according to the standard. The focusing parameters of the imaging lens are adjusted to ensure that the effective emitting surface of the panel is clearly imaged within the photosensitive surface of the two-dimensional array detector. The data control and analysis module sends a command to drive the color wheel to rotate, switching the correction filter matching the spectral weighting function for retinal blue light hazard to the measurement optical path. The two-dimensional array detector is then activated. The light radiation emitted from the object under test is spatially imaged by the imaging lens, and after spectral weighting matching by the correction filter, it is incident on the photosensitive surface of the two-dimensional array detector. The two-dimensional array detector acquires the response signals of all sensing units to the measured light radiation through a single exposure and transmits the raw response data to the data control and analysis module in real time. The control switching mechanism moves and switches, allowing the light radiation emitted from the object under test to be incident on the spectral measurement module, acquiring the comprehensive relative spectral power distribution of the entire emitting surface of the panel under test. For example... Figure 5 As shown, the comprehensive spectrum contains complete superimposed information of the blue light band of about 450 nm, the green light band of about 520 nm, and the red light band of about 620 nm, and transmits the spectral data to the data control and analysis module in real time.

[0062] B3: Pixel Merging Range Determination. The data control and analysis module determines the pixel merging range for this measurement based on the geometric requirements for measuring retinal blue light hazard radiance, combined with the pre-stored object-side field-of-view calibration value of 0.0001 rad for a single sensing unit. In this embodiment, for the retinal blue light hazard exemption group (RG0) evaluation requirements, the receiving angle is 0.1 rad. After geometric conversion, the pixel merging range is a circular area with a diameter of 1000 sensing units; sensing units that completely fall within this circular area and those with more than 50% of their effective photosensitive area falling within this area are all included in the pixel merging range of the single-group measurement area. For the retinal blue light hazard risk group (RG1 / RG2) evaluation requirements, the receiving angle is 0.011 rad, corresponding to a pixel merging range of a circular area with a diameter of 110 sensing units.

[0063] B4: Measurement Value Calculation and Spectral Data Optimization. Using the pixel merging range determined in step B3 as a single measurement area, a sliding window traversal method is employed to cover the entire effective imaging area of ​​the two-dimensional array detector's photosensitive surface. The average value of the light radiation response of all sensing units within each measurement area is calculated. Finally, the maximum value is selected from the average values ​​of all measurement areas as the base measurement value G for this retinal blue light hazard measurement. Simultaneously, the measurement area corresponding to this maximum average value is identified as the maximum hazard area for this measurement. For the tested RGB three-color light source, after location confirmation, the maximum hazard area corresponds to the core emitting area of ​​the blue LED chip in the display panel, matching the weight distribution characteristics of the retinal blue light hazard weighting function. Based on the weight distribution characteristics of the photobiological hazard weighting function, from the measured comprehensive relative spectral power distribution, the spectral component that plays a dominant contribution to the target photobiological hazard within the measurement area corresponding to the maximum average value (i.e., the spectral power distribution of the 400 nm-500 nm blue light dominant band) is extracted, while non-contributing spectral components in the green and red light bands are removed. Figure 6 As shown, these serve as input parameters for subsequent correction coefficient calculations.

[0064] B5: Correction Coefficient Calculation. The data control and analysis module will combine the relative spectral power distribution of the maximum hazard area obtained from the data collection with the pre-stored relative spectral power distribution of the standard radiance light source used for calibration, the relative spectral sensitivity of the two-dimensional array detector sensing unit, and the standard weighting function for retinal blue light hazard, and calculate the correction coefficient according to the following formula.

[0065]

[0066] in, The relative spectral power distribution of a standard radiance light source is used to calibrate the two-dimensional array detector. The relative spectral power distribution of the area of ​​greatest hazard to the tested object. The relative spectral sensitivity of the sensing unit of the two-dimensional array detector after the color filter has been corrected. The spectral weighting function for the blue light hazard to the retina. The wavelength of light radiation. and They are respectively The minimum and maximum values ​​of the function's wavelength range.

[0067] B6: Measurement value correction and result output: The basic measurement value G is corrected using the calculated correction coefficient K, and the corrected spatial average weighted radiance parameter of retinal blue light hazard is finally obtained as the photobiological hazard evaluation parameter under this measurement pose.

[0068] To address the challenges posed by the large luminous surface of the display panel under test and significant differences in radiant brightness at different angles, a full-space multi-pose traversal measurement can be performed while maintaining core measurement conditions such as the object-image relationship in the imaging optical path, field of view, and measurement distance constant. A high-precision motorized turntable is used to change the relative pose of the measuring device and the panel under test, performing multi-angle traversal adjustments around the panel's luminous center in terms of horizontal azimuth and pitch angles to ensure complete coverage of the panel's effective radiation range throughout space. Under each adjusted relative pose, the above measurement process is repeated to obtain the retinal blue light hazard weighted radiant parameters for that pose. After all preset pose measurements are completed, the data control and analysis module compares the measurement results for all poses, selects and outputs the maximum value as the final photobiological hazard measurement result within the full-space radiation range of the display panel under test, ensuring that the measurement results accurately reflect the panel's highest photobiological hazard level.

[0069] Example 4

[0070] This embodiment provides a photobiological hazard measurement device, including an imaging lens 9, an aperture stop 3, a color wheel 5, a switching mechanism 8, a two-dimensional array detector 2, a spectral measurement module 7, and a data control and analysis module 6. Figure 7 As shown, in this embodiment, the switching mechanism 8 is a plane mirror that can be cut in and out. When the plane mirror is cut into the optical path, the measured light radiation is incident on the two-dimensional array detector; when the plane mirror is cut out of the optical path, the measured light radiation is incident on the spectral measurement module. The spectral measurement module 7 is a fast spectrometer. The two-dimensional array detector 2 is a CMOS area array detector.

[0071] The switching mechanism described above can also be a perforated mirror or a semi-transparent mirror, or a linear moving guide rail.

Claims

1. A method for measuring photobiological hazards, characterized in that, The system includes a two-dimensional array detector and a correction filter, wherein the correction filter matches the spectral responsivity of the sensing pixels in the two-dimensional array detector to a specified photobiological hazard weighting function; the process of measuring photobiological hazard assessment parameters includes: S1: At a specified distance, the measured light radiation passes through the correction filter and reaches the two-dimensional array detector, and the response of each sensing unit in the two-dimensional array detector to the measured light radiation is obtained. S2: Based on the geometric requirements of the photobiological hazard assessment parameters and the sensor unit size of the two-dimensional array detector, determine the pixel merging range corresponding to the photobiological hazard assessment parameters; using the pixel merging range as the measurement area, calculate the average value of the light radiation response of each measurement area in the two-dimensional array detector, and select the maximum average value as the measured value G. S3: Calculate the correction coefficient K based on the relative spectral power distribution of the measured light radiation and the photobiohazard weighting function, and use the correction coefficient K to correct the measured value G in step S2 to obtain the corrected photobiohazard evaluation parameters.

2. The method for measuring photobiological hazards according to claim 1, characterized in that, The photobiological hazard weighting function is a photochemical ultraviolet hazard spectral weighting function, a corneal infrared radiation hazard spectral weighting function, a retinal blue light hazard spectral weighting function, a retinal thermal hazard spectral weighting function, an iris radiation hazard weighting function, an aphakic photochemical hazard weighting function, or a rectangular window function within a specified wavelength range.

3. The method for measuring photobiological hazards according to claim 1, characterized in that, The method for calculating the correction coefficient K in step S3 is as follows: ,in The relative spectral power distribution of the standard light source used to calibrate the two-dimensional array detector. The relative spectral power distribution of the measured object. Given the relative spectral sensitivity of the sensing element of a two-dimensional array detector with known modified color filters, The weighting function for the aforementioned photobiological hazards. and They are respectively The minimum and maximum values ​​of the function's wavelength range.

4. A method for measuring photobiological hazards according to claim 1, 2, or 3, characterized in that, In step S3, the spectral power distribution of the light radiation corresponds to the light radiation received by the region with the maximum average value in step S2.

5. The method for measuring photobiological hazards according to claim 4, characterized in that, The object under test includes two or more light sources with different relative spectral powers. The spectral power distribution of the light radiation in step S3 is obtained using one of the following methods: the spectral measurement area is limited to the region corresponding to the maximum average value in step S2 using a limiting aperture, wherein the limiting aperture is an aperture stop or a field stop; or the comprehensive relative spectral power distribution of the object under test is measured, and the relative spectral power distribution of the region corresponding to the maximum average value is extracted based on the photobiological hazard weighting function.

6. A method for measuring photobiological hazards according to claim 1, 2, or 3, characterized in that, Under the geometric conditions required for photobiological hazard assessment parameters, the relative pose relationship between the two-dimensional array detector and the object under test is changed. Steps S1 to S3 are repeated under each pose relationship to obtain the photobiological hazard assessment parameters under the corresponding pose, and the maximum value is compared and output.

7. A method for measuring photobiological hazards according to any one of claims 1 to 3, characterized in that, An imaging lens and an aperture stop are set in the optical path in front of the two-dimensional array detector. In step S2, the pixel merging range is determined according to the field of view range required by the photobiohazard assessment parameters.

8. A method for measuring photobiological hazards according to claims 1 to 3, characterized in that, The geometric condition is non-imaging reception, with a field stop set in the optical path in front of the two-dimensional array detector to limit the reception angle.

9. A measuring device based on the photobiological hazard measurement method according to claim 1, characterized in that, It includes a two-dimensional array detector (2), a color wheel (5), and a data control and analysis module (6); the color wheel (5) is set in the measurement optical path before the two-dimensional array detector (2), and multiple holes are opened on the color wheel (5). Two or more correction filters (10) are respectively set in different holes. By rotating the color wheel (5), the correction filter (10) on any hole can be switched to the measurement optical path, so that the light radiation from the object under test (4) is filtered by the correction filter (10) and then incident on the two-dimensional array detector (2); the two-dimensional array detector (2) is communicatively connected to the data control and analysis module (6).

10. The measuring device according to claim 9, characterized in that, It also includes a spectral measurement module (7) and a switching mechanism (8). The switching mechanism (8) switches the light radiation from the object under test (4) to the measurement optical path where the two-dimensional array detector (2) and the spectral measurement module (7) are located simultaneously or sequentially to achieve measurement. The spectral measurement module (7) is communicatively connected to the data control and analysis module (6).

11. The measuring device according to claim 9, characterized in that, It also includes an imaging lens (9), through which the light emitted by the object under test (4) is received and measured by a two-dimensional array detector (2) via the imaging lens (9) and the correction filter (10).

12. The measuring device according to claim 10, characterized in that, The switching mechanism (8) includes a linear guide rail or a rotating guide rail; a two-dimensional array detector (2) and a spectral measurement module (7) are provided on the linear guide rail or the rotating guide rail, and the switching measurement is realized by the linear movement or rotation of the guide rail; or the switching mechanism (8) is a reflector that can be cut into or cut out from the measurement optical path. When the reflector cuts into the measurement optical path, the measurement of the spectral measurement module is realized, and when the reflector cuts out from the measurement optical path, the measurement of the two-dimensional array detector is realized.

13. The measuring device according to claim 10, characterized in that, The switching mechanism (8) is a beam splitting device. The beam splitting device splits the light emitted by the object under test (4) into two or more paths, one of which is incident on the two-dimensional array detector (2), and the other is incident on the spectral measurement module (7).

14. The measuring device according to claim 10, characterized in that, The switching mechanism (8) is located on the hole of the color wheel (5) and can enter or exit the measurement optical path as the color wheel (5) rotates; the measurement optical path from the object under test (4) through the switching mechanism (8) to the spectral measurement module (7) is formed only when the switching mechanism (8) is entered into the measurement optical path.

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