Optical system for dry biochemical analyzer

Abstract

An optical system for a dry biochemical analyzer. The system consists of a light-source feedback unit, a light-homogenizing illumination light path and a collection light path. The electric current of a light source can be adjusted by means of the light-source feedback unit, such that the intensity of light output by the light source is stable. The system has a simple structure, high adjustment precision and high stability. By means of a multi-channel light-source current driver provided in the light-source feedback unit, rapid switching control over monochromatic light sources with different wavelengths can be realized. By means of the light-homogenizing illumination light path, light-homogenizing processing is performed on incident light beams, such that uniform illumination can be obtained on a dry reagent strip under test, the light path is concise, and a plurality of monochromatic light sources with different wavelengths that are provided off-axis can be overlapped and focused at the same position. The collection light path is configured as a telecentric light path, and a field diaphragm is provided, such that light beams on an entire illuminated surface can be uniformly collected. By using the system, the accuracy of collected reaction light beams corresponding to an object to be tested can be improved, thereby improving the accuracy of a subsequent analysis result of said object.

Description

Optical system of dry biochemical analyzer

[0001] Cross-reference to Related Applications

[0002] The present disclosure claims priority to the Chinese patent application No. 2024106130676, filed on May 17, 2024, entitled “Optical system of dry biochemical analyzer”, the entire content of which is incorporated herein by reference. TECHNICAL FIELD

[0003] The present disclosure relates to the technical field of biochemical detection, in particular, to an optical system of a dry biochemical analyzer. BACKGROUND

[0004] The principle of a dry biochemical analyzer is to add a body fluid sample on a dry reagent sheet, the measured substance in the sample reacts with the components of the reagent sheet to cause a change in the color of the reagent sheet, i.e., the reflectance density. By periodically measuring the reflectance density of the reagent sheet at a specific wavelength after adding the sample within a fixed reaction time, a reaction curve of the sample within the entire reaction time is finally drawn. The change value or rate of the reflectance density is calculated from the reaction curve, and then the concentration or biological activity of the measured substance in the sample is obtained by corresponding to the calibration curve.

[0005] At present, the optical system of a traditional dry biochemical analyzer is as follows: a single-color LED (Light Emitting Diode) is used as a light source, multiple single-color LED light sources of different wavelengths are concentrically arranged, the light source emits a light beam, which is irradiated on the surface of the dry reagent sheet, a part of which is absorbed and a part of which is diffusely reflected, the diffusely reflected light is received by a photodetector, a temperature control device and a temperature sensor are used to control the temperature of the light source to reduce the temperature drift of the single-color LED light source, so as to stabilize the light emitting efficiency of the single-color LED light source.

[0006] However, the effect of using a temperature control device and a temperature sensor to ensure the stability of the light source is poor, and stable light intensity cannot be achieved.

[0007] SUMMARY

[0008] The present disclosure aims to provide an optical system of a dry biochemical analyzer to improve the accuracy of sample concentration test results in biochemical detection projects, in view of the deficiencies in the prior art.

[0009] To achieve the above-mentioned purpose, the technical solutions adopted by the embodiments of the present disclosure are as follows:

[0010] The optical system of the dry biochemical analyzer provided by the embodiments of the present disclosure comprises: a light source feedback unit, a uniform light illumination light path, and a collection light path; the optical system takes the central normal line of a dry reagent sheet to be measured as an axis, the light source feedback unit is arranged perpendicularly relative to the axis of the optical system; the optical axis of the uniform light illumination light path coincides with the axis of the optical system; and the optical axis of the collection light path forms a first preset angle with the axis of the optical system.

[0011] The light source feedback unit is configured to control the light beam of a specified wavelength corresponding to a to-be-measured object to be emitted by a light source according to the type of the to-be-measured object, collect a feedback light beam after the light beam emitted by the light source of the specified wavelength is reflected or refracted, and perform feedback adjustment on a feedback light signal value collected by the feedback light beam and a preset target light signal value corresponding to the light source of the specified wavelength, so as to adjust the output light signal value of the light source of the specified wavelength.

[0012] The uniform light illumination light path is configured to split, focus, and converge the incident light beam after the light beam emitted by the light source of the specified wavelength is reflected or refracted on the dry reagent sheet to be measured.

[0013] The collection light path is configured to collect the light rays reflected on the dry reagent sheet to be measured and satisfying a second preset angle with the optical axis of the collection light path, and obtain a light signal.

[0014] Optionally, the light source feedback unit comprises a data acquisition and conversion module, a control module, and a driving module; the data acquisition and conversion module, the control module, and the driving module are connected in sequence.

[0015] The data acquisition and conversion module is configured to collect the feedback light signal value and perform conversion processing on the feedback light signal value to obtain a digital signal.

[0016] The control module is configured to control the driving module to adjust the output light signal value of the light source of the specified wavelength according to the digital signal.

[0017] Optionally, the data acquisition and conversion module comprises a first light source detector, a current-to-voltage converter, a gain amplifier, and an analog-to-digital converter.

[0018] The first light source detector is configured to collect the feedback light beam, obtain a feedback light signal value of the feedback light beam according to the feedback light beam, and convert the feedback light signal value into a current signal.

[0019] The current-to-voltage converter is configured to convert the current signal into a voltage signal.

[0020] The gain amplifier is configured to perform signal amplification processing on the voltage signal to obtain a processed voltage signal.

[0021] The analog-to-digital converter is configured to perform analog-to-digital conversion on the processed voltage signal to obtain a digital signal; the digital signal is configured to indicate a current feedback optical signal value of the light source of the specified wavelength.

[0022] Optionally, the control module comprises a controller; and the driving module comprises a multi-channel light source current driver.

[0023] The controller is configured to control the multi-channel light source current driver to adjust an output optical signal value of the light source of the specified wavelength according to the digital signal.

[0024] Optionally, the controller is specifically configured to determine a difference between the current feedback optical signal value and a preset target optical signal value corresponding to the light source of the specified wavelength according to the current feedback optical signal value of the light source of the specified wavelength and the preset target optical signal value.

[0025] According to the difference, a current adjustment instruction of a light source current value is generated.

[0026] According to the current adjustment instruction, the current value of the light source of the specified wavelength is adjusted by the multi-channel light source current driver, so that the output optical signal value of the light source of the specified wavelength reaches the preset target optical signal value.

[0027] Optionally, the data acquisition and conversion module further comprises a low-pass filter; one end of the low-pass filter is connected with the flow-to-voltage converter, and the other end of the low-pass filter is connected with the gain amplifier.

[0028] The low-pass filter is configured to filter the voltage signal converted by the flow-to-voltage converter to obtain a filtered voltage signal.

[0029] Optionally, the uniform light illumination light path comprises an ommatidium lens and an integrating lens; the ommatidium lens comprises a first face sub-lens and a second face sub-lens, the first face sub-lens is a face away from the integrating lens, and the second face sub-lens is a face close to the integrating lens.

[0030] The first face sub-lens is configured to divide the incident light beam into sub-beams and focus the sub-beams on the second face sub-lens.

[0031] The second face sub-lens and the integrating lens are configured to coincide corresponding sub-beams on the focal plane of the integrating lens; and the dry reagent sheet to be measured is placed on the focal plane of the integrating lens.

[0032] Optionally, the integrating lens is a double-cemented lens comprising a positive lens and a negative lens; the positive lens is made of low-dispersion glass; and the negative lens is made of high-dispersion glass.

[0033] Optionally, the collection light path comprises: a first lens, an aperture stop, a field stop, a second lens, and a second photodetector; the first lens, the aperture stop, the field stop, the second lens, and the second photodetector are sequentially arranged away from the dry reagent sheet to be measured along an optical axis of the collection light path; the aperture stop is arranged on an image plane of the first lens and is placed parallel to the first lens; the field stop is arranged on an image plane of the first lens;

[0034] The light reflected from the dry reagent sheet to be measured and having an angle with the optical axis of the collection light path satisfying a preset angle is focused by the first lens, the focused light beam passes through the aperture stop to reach the image plane, and then passes through the field stop to be incident on the second lens, and is focused on the second photodetector by the second lens.

[0035] Optionally, the size of the field stop is determined according to the size of the region to be measured on the dry reagent sheet to be measured and the first preset angle between the optical axis of the collection light path and the axis of the optical system.

[0036] Optionally, the optical system further comprises: a transmission device; at least one dry reagent sheet to be measured is arranged on the transmission device; each dry reagent sheet to be measured corresponds to a light measurement hole.

[0037] The transmission device is driven by a motor to switch the dry reagent sheet to be measured.

[0038] The transmission device is periodically driven under time sequence control to switch the dry reagent sheet to be measured in each period.

[0039] Optionally, the optical system further comprises: a light source module, the light source module comprising at least one monochromatic light source of a specified wavelength; the light source of the specified wavelength is a light source in the light source module.

[0040] Optionally, the light source module comprises a first light source module and a second light source module.

[0041] The first light source module is arranged along the axis of the optical system, and the second light source module is arranged perpendicular to the axis of the optical system.

[0042] The first light source module comprises at least one monochromatic light source of a specified wavelength.

[0043] The second light source module comprises at least one monochromatic light source of a specified wavelength.

[0044] The wavelengths of the monochromatic light sources in the first light source module are different, the wavelengths of the monochromatic light sources in the second light source module are different, and the wavelengths of the monochromatic light sources in the first light source module are different from the wavelengths of the monochromatic light sources in the second light source module.

[0045] Optionally, the optical system further comprises a beam splitter and a focusing lens; the beam splitter is placed at a third preset angle with respect to the axis of the optical system.

[0046] The light beams emitted by the light sources of the specified wavelengths are refracted or reflected by the beam splitter and then irradiate on the focusing lens, and are focused by the focusing lens and then irradiate on the first light source detector.

[0047] Optionally, the controller is specifically configured to determine the light sources of the specified wavelengths corresponding to the to-be-detected object according to the type of the to-be-detected object, and send a control instruction to the multi-channel light source current driver to control the multi-channel light source current driver to turn on the light sources of the specified wavelengths.

[0048] Optionally, the compound eye lens comprises a first single-sided compound eye lens and a second single-sided compound eye lens; the first single-sided compound eye lens and the second single-sided compound eye lens are placed in parallel and the distance between them is the focal length of a sub-lens; wherein the sub-lens is a lens unit in the first single-sided compound eye lens or the second single-sided compound eye lens.

[0049] Optionally, the uniform light illumination light path further comprises a glass lens; the glass lens is placed between the compound eye lens and the integrating lens, and the glass lens is placed at a fourth preset angle with respect to the axis of the optical system.

[0050] The light beams emitted by the light sources of the specified wavelengths are refracted or reflected by the beam splitter and then irradiate on the compound eye lens, and are incident on the glass lens through the compound eye lens.

[0051] The incident light rays are reflected or refracted by the glass lens and then enter the focusing lens, and are focused by the focusing lens and then irradiate on the first light source detector.

[0052] Optionally, the light source module comprises a third light source module; the third light source module is arranged along an axis perpendicular to the optical system.

[0053] The third light source module comprises monochromatic light sources of at least one wavelength.

[0054] Optionally, the light source module comprises a fourth light source module; the fourth light source module is arranged along the axis of the optical system.

[0055] The fourth light source module comprises monochromatic light sources of at least one wavelength.

[0056] Optionally, the first part of the monochromatic light sources in the light source module are arranged along the axis of the optical system; and the second part of the monochromatic light sources in the light source module are arranged perpendicular to the axis of the optical system.

[0057] The beam splitter is a dichroic mirror, and the number of the dichroic mirrors corresponds to the number of the first part of the monochromatic light sources.

[0058] Each first part of the monochromatic light sources is aligned with the corresponding dichroic mirror in the vertical direction.

[0059] Optionally, the arrangement position of each monochromatic light source is determined according to the type of the selected dichroic mirror and the wavelength of each monochromatic light source.

[0060] The arrangement position of each dichroic mirror is determined according to the type of the selected dichroic mirror and the cut-off wavelength of each dichroic mirror.

[0061] The beneficial effects of the present disclosure are:

[0062] The present disclosure provides an optical system of a dry biochemical analyzer, which can be composed of a light source feedback unit, a uniform light illumination light path and a collection light path. The light source feedback unit can feedback and adjust the current of the light source, so that the light intensity output by the light source is stable, and the structure is simple, the adjustment precision is high, and the stability is high. The multi-channel light source current driver arranged in the light source feedback unit can realize rapid switching control of monochromatic light sources of different wavelengths. The incident light is uniformly processed by the uniform light illumination light path, so that uniform illumination can be obtained on the measured dry reagent sheet, the light path is simple, and a plurality of monochromatic light sources of different wavelengths arranged off-axis can be focused at the same position. By setting the collection light path as a telecentric light path and setting a field stop, the light rays of the entire illuminated surface can be uniformly collected. The use of the system can improve the accuracy of the collected reaction light rays corresponding to the measured object, thereby improving the accuracy of the subsequent analysis results of the measured object. BRIEF DESCRIPTION OF DRAWINGS

[0063] In order to more clearly illustrate the technical solutions of the embodiments of the present disclosure, the following will briefly introduce the drawings needed to be used in the embodiments. It should be understood that the following drawings only show some embodiments of the present disclosure, and therefore should not be regarded as a limitation on the scope. For those skilled in the art, other related drawings can also be obtained without creative labor on the basis of these drawings.

[0064] FIG. 1 is a structural schematic diagram of a dry reagent sheet according to an embodiment of the present disclosure;

[0065] FIG. 2 is a schematic diagram of light distribution after light irradiation of a dry reagent sheet according to an embodiment of the present disclosure;

[0066] FIG. 3 is a structural schematic diagram of an optical system of a conventional dry optical analyzer according to an embodiment of the present disclosure;

[0067] FIG. 4 is a structural schematic diagram of another optical system of a conventional dry optical analyzer according to an embodiment of the present disclosure;

[0068] FIG. 5 is a structural schematic diagram of an optical system of a dry biochemical analyzer according to an embodiment of the present disclosure;

[0069] FIG. 6 is a structural schematic diagram of another optical system of a dry biochemical analyzer according to an embodiment of the present disclosure;

[0070] FIG. 7 is a structural schematic diagram of another optical system of a dry biochemical analyzer according to an embodiment of the present disclosure;

[0071] FIG. 8 is a layout schematic diagram of a first light source module according to an embodiment of the present disclosure;

[0072] FIG. 9 is a layout schematic diagram of a second light source module according to an embodiment of the present disclosure;

[0073] FIG. 10 is a light path schematic diagram according to an embodiment of the present disclosure;

[0074] FIG. 11 is a light source switching light signal schematic diagram according to an embodiment of the present disclosure;

[0075] FIG. 12 is a schematic diagram of a first light source module after being split by a beam splitter according to an embodiment of the present disclosure;

[0076] FIG. 13 is a schematic diagram of a second light source module after being split by a beam splitter according to an embodiment of the present disclosure;

[0077] FIG. 14 is a hardware structure schematic diagram of a light source feedback unit according to an embodiment of the present disclosure;

[0078] FIG. 15 is a comparison diagram of output light signal values when PID feedback is performed and when PID feedback is not performed according to an embodiment of the present disclosure;

[0079] FIG. 16 is a reflectance density spectrum diagram of p-nitrophenol according to an embodiment of the present disclosure;

[0080] FIG. 17 is a reaction curve schematic diagram of an alkaline phosphatase reagent sheet according to an embodiment of the present disclosure;

[0081] FIG. 18 is a schematic diagram of a calibration curve corresponding to alkaline phosphatase according to an embodiment of the present disclosure;

[0082] FIG. 19 is a schematic diagram of a light uniformity illumination light path according to an embodiment of the present disclosure;

[0083] FIG. 20 is a light uniformity system principle diagram according to an embodiment of the present disclosure;

[0084] FIG. 21 is a schematic diagram of another homogenization system according to an embodiment of the present disclosure;

[0085] FIG. 22 is a schematic diagram of a light collection path according to an embodiment of the present disclosure;

[0086] FIG. 23 is a schematic diagram of a telecentric light path according to an embodiment of the present disclosure;

[0087] FIG. 24 is a schematic diagram of a field stop design light path according to an embodiment of the present disclosure;

[0088] FIG. 25 is a schematic diagram of another homogenization illumination light path according to an embodiment of the present disclosure;

[0089] FIG. 26 is a schematic diagram of another homogenization illumination light path according to an embodiment of the present disclosure;

[0090] FIG. 27 is a schematic diagram of a light source module according to an embodiment of the present disclosure;

[0091] FIG. 28 is a schematic diagram of another light source module according to an embodiment of the present disclosure;

[0092] FIG. 29 is a schematic diagram of another light source module according to an embodiment of the present disclosure. DETAILED DESCRIPTION

[0093] In order to make the purpose, technical scheme and advantages of the embodiments of the present disclosure clearer, the technical scheme of the embodiments of the present disclosure will be described clearly and completely below in conjunction with the drawings in the embodiments of the present disclosure. It should be understood that the drawings in the present disclosure only serve the purpose of description and illustration, and are not used to limit the protection scope of the present disclosure. In addition, it should be understood that the schematic drawings are not drawn according to the actual proportions. The flowcharts in the present disclosure show the operations implemented according to some embodiments of the present disclosure. It should be understood that the operations of the flowcharts can not be implemented in sequence, and the steps without logical context relationship can be reversed in sequence or implemented simultaneously. In addition, one or more other operations can be added to the flowcharts or removed from the flowcharts under the guidance of the present disclosure by those skilled in the art.

[0094] In addition, the described embodiments are only some of the embodiments of the present disclosure, not all the embodiments. The components of the embodiments of the present disclosure described and shown in the drawings herein can be arranged and designed in various different configurations. Therefore, the following detailed description of the embodiments of the present disclosure provided in the drawings is not intended to limit the scope of the claimed present disclosure, but only represents selected embodiments of the present disclosure. Based on the embodiments of the present disclosure, all other embodiments obtained by those skilled in the art without creative labor are within the scope of protection of the present disclosure.

[0095] It should be noted that the term "comprising" will be used in the embodiments of the present disclosure to indicate the presence of the features that follow, but not to exclude the presence of other features.

[0096] First, the related background knowledge involved in the present disclosure is simply explained:

[0097] The dry biochemical analyzer is an analyzer for clinical chemical test using solid carrier reagent. It quantitatively measures the concentration of specific components in the sample by reflectance densitometry.

[0098] The principle of the dry biochemical analyzer is to add a body fluid sample (serum, urine, etc.) on the dry reagent sheet. The measured substance in the sample reacts with the reagent sheet components to cause the color change of the reagent sheet, i.e., the change of reflectance density. By periodically measuring the reflectance density of the reagent sheet at a specific wavelength after adding the sample within a fixed reaction time, the reaction curve of the sample within the entire reaction time is finally drawn. The change value or rate of the reflectance density is calculated from the reaction curve, and then the concentration or biological activity of the measured substance in the sample is obtained by corresponding to the calibration curve.

[0099] FIG. 1 is a structural schematic diagram of a dry reagent sheet provided by an embodiment of the present disclosure. As shown in FIG. 1, the dry reagent sheet is a multi-layer dry reagent sheet made on a transparent support substrate. The typical reagent sheet is sequentially composed of a diffusion layer, a filter layer, a reagent layer, and a color development layer from top to bottom. When detecting a body fluid sample, the temperature of the dry reagent sheet should be heated and stabilized at the optimum reaction temperature of about 37℃. A certain amount of body fluid sample is added to the diffusion layer on the surface of the reagent sheet, and the body fluid sample diffuses horizontally in the layer to form a circular area, which can increase the contact area between the subsequent body fluid sample and the reagent and improve the reaction speed. At the same time, the body fluid sample also penetrates downward to the filter layer. After the body fluid sample passes through the filter layer to filter out interfering substances, it penetrates downward to the reagent layer and reacts with the dry reagent components solidified therein to produce a reaction product. The reaction product will produce absorption to light in a specific spectral range. The reaction product continues to penetrate downward to the color development layer and is fixed. Finally, the color change of the reagent sheet can be observed from the transparent support substrate. The degree or rate of color change can reflect the concentration of the measured substance. By measuring the color change of the dry reagent sheet, the concentration or biological activity of the measured substance in the sample can be determined. The visual subjective feeling of the color change of the dry reagent sheet can be objectively and quantitatively detected by measuring the reflectance density thereof.

[0100] Figure 2 is a schematic diagram of light distribution after the light irradiation of the dry reagent sheet according to an embodiment of the present disclosure. As shown in Figure 2, when the light of a certain wavelength is irradiated from bottom to top on the dry reagent sheet, a part of the light is specularly reflected on the surface of the transparent support substrate, which does not reflect the color change of the reagent sheet. The remaining part of the light penetrates the transparent support substrate into the color developing layer. The light interacts with the microstructure and molecules of the color developing layer, and returns to the surface after multiple reflections, refractions and absorptions. The intensity of the light is significantly changed, i.e., reflects the color change of the reagent sheet. The direction of the reflected light also does not follow the direction of specular reflection, but becomes diffuse reflection. The direction of the diffuse reflected light and the light intensity follow the Lambertian radiation law.

[0101] Therefore, the change of the reflected light density of the diffuse reflected light at the bottom of the dry reagent sheet can be used to objectively and quantitatively detect the color change of the dry reagent sheet.

[0102] There are three major types of analysis methods commonly used in dry biochemical analyzers, endpoint method, fixed time method (two-point method) and continuous monitoring method (rate method).

[0103] The endpoint method refers to that after a period of incubation, the entire reaction reaches equilibrium, the concentration of the reactants no longer increases, and the increase or decrease degree of the reflected light density is proportional to the concentration of the measured substance.

[0104] The fixed time method refers to that within a certain reaction time, the reaction rate is proportional to the concentration of the reactants, the reactants are consumed continuously, the reaction speed decreases continuously, the speed of the increase or decrease of the light density slows down, and a long time is required for the reaction to reach equilibrium. Therefore, it is necessary to monitor within a specific time period.

[0105] The continuous monitoring method refers to that during the entire incubation process, the concentration of a certain reaction product of the measured substance is continuously monitored at equal intervals of time, and the reaction speed of the measured substance is calculated. That is, the light signal value is collected at equal intervals of time after the reagent sheet is added, and the concentration of the measured substance is calculated.

[0106] It is worth noting that when the dry biochemical analyzer is used to test different items (for different measured substances, such as albumin, alkaline phosphatase, cholesterol, etc.), the sample addition amount and test time corresponding to different items are different. The process of collecting the light signal by using the optical system provided in the present solution is the same. Therefore, in order to simultaneously detect multiple different items, the optical system of the dry biochemical analyzer should be able to detect the reflected light density of multiple wavelengths, and quickly switch the wavelengths to meet the purpose of simultaneously detecting the reaction curves of multiple reagent sheets.

[0107] Biochemical detection is periodically collected light signal value to calculate the concentration of the measured object, when the light irradiation on the dry reagent sheet at different time is inconsistent, the collected light signal value has error, leading to abnormal reaction curve, thereby affecting the accuracy of the experimental results. The dry biochemical reagent sheet is a multi-layer film structure, and the sample to be measured will appear uneven diffusion distribution when diffusing in the reagent sheet, and when the light irradiated on the sample surface is uneven, it will affect the stability of the measurement. The dry biochemical analyzer tests the diffuse reflection light at a fixed angle, so the collection light path can uniformly collect the light of the entire illuminated surface.

[0108] In summary, based on the principle of dry biochemical analyzer, the dry biochemical instrument should meet the following indicators:

[0109] 1. According to different detection items, different wavelength narrow-band light sources should be set;

[0110] 2. According to different detection items, the wavelength can be switched;

[0111] 3. Different wavelength light sources should be irradiated on the same dry reagent sheet position;

[0112] 4. The light irradiation on the dry reagent sheet needs to be stable;

[0113] 5. The light irradiation on the surface of the dry reagent sheet needs to be uniformly distributed;

[0114] 6. Detect the diffuse reflection light along the fixed angle of the dry reagent sheet surface, and the collection light path can uniformly collect the light of the entire illuminated surface.

[0115] FIG. 3 is a structural schematic diagram of a conventional dry optical analyzer optical system provided by an embodiment of the present disclosure. FIG. 4 is a structural schematic diagram of another conventional dry optical analyzer optical system provided by an embodiment of the present disclosure. There are two kinds of conventional dry optical analyzer optical system structures.

[0116] The first kind is shown in FIG. 3, using a single-color LED (Light Emitting Diode, i.e. light emitting diode) as a light source, a plurality of wavelength single-color LED light sources are concentrically arranged, the first light source 202, the second light source 203, the third light source 204, the fourth light source 205, the fifth light source 206 and the sixth light source 207 are single-color LEDs of different wavelengths, the light source emits a light beam, which irradiates on the surface of the measured dry reagent sheet 106, part of which is absorbed and part of which is diffusely reflected, and the diffusely reflected light is received by the photodetector 208; the temperature of the light source is controlled by the temperature control device and the temperature sensor, and the temperature drift of the single-color LED light source is reduced, so that the light emitting efficiency of the single-color LED light source is stable.

[0117] However, the first kind of conventional dry optical analyzer optical system has the following shortcomings:

[0118] 1. The temperature control device and temperature sensor are used to ensure the stability of the light source, and the light signal value has poor stability and poor precision;

[0119] 2. The light intensity on the surface of the dry reagent sheet is not uniform;

[0120] 3. The collection light path cannot uniformly collect the light of the entire illuminated surface.

[0121] The second structure is shown in FIG. 4. The illumination light path uses complex light as the light source. The seventh light source 301 emits a light beam. The filter wheel 302 is driven by a motor to rotate. After filtering through the filter wheel 302, the light is irradiated on the dry reagent sheet 106 to be measured. Part of the light is absorbed, and part of the light is diffusely reflected. The diffusely reflected light is focused by the lens 304 and received by the photodetector 208.

[0122] However, the second traditional dry optical analyzer optical system has the following disadvantages:

[0123] 1. Halogen tungsten lamp and xenon lamp are used as complex light sources. The light source generates a large amount of heat, has a short service life, and has high maintenance costs;

[0124] 2. The light source is preheated to ensure the stability of the output light intensity. The light intensity has poor stability and poor precision;

[0125] 3. The complex light source needs to be set with a filter wheel for light splitting. The filter wheel is switched by a motor. The mechanical structure is complex, and the spectrum cannot be quickly switched;

[0126] 4. The light intensity on the surface of the dry reagent sheet is not uniform;

[0127] 5. The collection light path cannot uniformly collect the light of the entire illuminated surface.

[0128] Based on the above-mentioned disadvantages of the traditional dry optical analyzer optical system, the present disclosure provides a dry biochemical analyzer optical system. The system is composed of a light source feedback unit, a uniform light illumination light path, and a collection light path. The light source feedback unit can feedback and adjust the current of the monochromatic LED light source, so that the light intensity output by the monochromatic LED is stable. The structure is simple, the adjustment precision is high, and the stability is high. The circuit switch is used to switch different wavelengths of monochromatic LED. There is no moving part for switching different wavelengths of light source. The switching speed is fast and stable. The uniform light illumination light path composed of a compound eye lens and an integrating lens processes the incident light. Uniform illumination can be obtained on the dry reagent sheet. The light spots of different wavelengths of monochromatic LED are coincided on the surface of the dry reagent sheet. The light path is simple. The collection light path is designed as a telecentric light path, which can uniformly collect the light of the entire illuminated surface. The use of the system can improve the accuracy of the collected reaction light corresponding to the measured object, thereby improving the accuracy of the subsequent analysis results of the measured object.

[0129] Next, the structure of the optical system of the dry biochemical analyzer provided by the present disclosure and the corresponding system use method are described through multiple embodiments.

[0130] FIG. 5 is a frame diagram of an optical system of a dry biochemical analyzer provided by an embodiment of the present disclosure. As shown in FIG. 5, the optical system of the dry biochemical analyzer can include a light source feedback unit, a uniform light illumination light path, and a collection light path.

[0131] The light source feedback unit is configured to control the light beam emitted by the light source of the specified wavelength corresponding to the to-be-measured substance according to the type of the to-be-measured substance, collect the feedback light beam after the light beam emitted by the light source of the specified wavelength is reflected or refracted, and perform feedback adjustment on the feedback light signal value collected by the feedback light beam and the preset target light signal value corresponding to the light source of the specified wavelength, so as to adjust the output light signal value of the light source of the specified wavelength.

[0132] Generally, in order to make the linear range of the finally generated reaction curve corresponding to the to-be-measured substance larger, the wavelength of the selected light source should be close to the reflection density peak. Therefore, different wavelengths of light sources need to be selected for illumination according to the type of the to-be-measured substance. Alternatively, the wavelengths of the light sources corresponding to different to-be-measured substances can be determined in advance according to experiments, so that the light source feedback unit can control the light beam emitted by the light source of the specified wavelength corresponding to the to-be-measured substance to the measured dry reagent sheet 106 according to the type of the current to-be-measured substance.

[0133] Table 1 below exemplarily shows the wavelengths of the detection light sources corresponding to different to-be-measured substances when different analysis methods are used for concentration analysis.

[0134] Table 1

[0135] The uniform light illumination light path is configured to split and focus the incident light beam after the light beam emitted by the light source of the specified wavelength is reflected or refracted, and converge the light beam on the measured dry reagent sheet 106.

[0136] Part of the light beam emitted by the light source of the specified wavelength after being reflected or refracted is incident to the uniform light illumination light path. The uniform light illumination light path can perform uniform light processing on the incident light rays, so that the light spot finally irradiated on the dry reagent sheet is uniform, and multiple monochromatic LED light sources of different wavelengths arranged off-axis are focused at the same position.

[0137] The collection light path is configured to collect the light rays reflected on the measured dry reagent sheet 106 and satisfying a second preset angle with the optical axis of the collection light path, and obtain a light signal.

[0138] When the light beam emitted by the light source of a specified wavelength is subjected to uniform light treatment by the uniform light illumination light path, the light beam can irradiate the dry reagent sheet 106 under test, and after being reflected by the dry reagent sheet 106 under test, the light is collected by the collection light path. The collection light path can collect the light reflected by the dry reagent sheet 106 under test at a specified angle with the optical axis of the collection light path, and obtain an optical signal value according to the collected light. The collection light path in the embodiment can be configured to uniformly collect the light of the entire illuminated surface.

[0139] In some embodiments, the optical signal value collected by the collection light path can be sent to an external processing device, for example, a processor, a server, or a host computer independent of the optical system. Thus, the external device can calculate the reflectance density according to the collected optical signal value, draw a reaction curve, and then obtain the change value or rate of the reflectance density according to the reaction curve, and then obtain the concentration of the test substance according to the calibration curve of the test substance. The calibration curve of the test substance can be generated by experiment in advance.

[0140] Of course, the concentration of the test substance obtained based on the reaction curve is only one application of the reaction curve. In actual use, the obtained reaction curve is not limited to analyzing the concentration of the test substance, but can also be used to analyze the temperature, pH (Pondus Hydrogenii, pH value), purity, etc. of the test substance.

[0141] In summary, the optical system of the dry biochemical analyzer provided in the embodiment can be composed of a light source feedback unit, a uniform light illumination light path, and a collection light path. The light source feedback unit can feedback and adjust the current of the light source, so that the light intensity output by the light source is stable, the structure is simple, the adjustment precision is high, and the stability is high. The uniform light illumination light path can uniformly process the incident light, so that uniform illumination can be obtained on the dry reagent sheet under test, and the light path is simple. The collection light path can uniformly collect the light of the entire illuminated surface. The use of the system can improve the accuracy of the collected reaction light corresponding to the test substance, thereby improving the accuracy of the subsequent analysis results of the test substance.

[0142] FIG. 6 is a structural schematic diagram of another optical system of a dry biochemical analyzer provided in the embodiment of the disclosure. As shown in FIG. 6, the optical system takes the central normal line of the dry reagent sheet 106 under test as the axis, and the light source feedback unit is vertically arranged relative to the axis of the optical system. The optical axis of the uniform light illumination light path coincides with the axis of the optical system. The optical axis of the collection light path is at a first preset angle with the axis of the system.

[0143] Optionally, the light source feedback unit comprises a data acquisition and conversion module 144, a control module 145 and a driving module 146, which are connected in sequence. The data acquisition and conversion module 144 is configured to acquire the feedback light signal value and perform conversion processing on the feedback light signal value to obtain a digital signal. The control module 145 is configured to control the driving module 146 to adjust the output light signal value of the light source of the specified wavelength according to the digital signal.

[0144] The data acquisition and conversion module 144 can receive the feedback light beam obtained by reflecting or refracting the light beam emitted by the light source, acquire the feedback light signal value according to the feedback light beam, and perform a series of conversion processing on the feedback light signal value to obtain a digital signal.

[0145] The control module 145 controls the driving module 146 to adjust the output light signal value of the light source of the specified wavelength according to the digital signal by using a feedback adjustment algorithm.

[0146] FIG. 7 is a structural schematic diagram of an optical system of another dry biochemical analyzer provided by the embodiment of the present disclosure; in combination with FIGS. 6 and 7, the data acquisition and conversion module 144 comprises a first light source detector 108, a flow pressure converter 114, a gain amplifier 116 and an analog-to-digital converter 117. The control module 145 comprises a controller 118. The driving module 146 comprises a multi-channel light source current driver 119.

[0147] The first light source detector 108 is configured to acquire the feedback light beam, obtain the feedback light signal value of the feedback light beam according to the feedback light beam, and convert the feedback light signal value into a current signal. The flow pressure converter 114 is configured to convert the current signal into a voltage signal. The gain amplifier 116 is configured to perform signal amplification processing on the voltage signal to obtain a processed voltage signal. The analog-to-digital converter 117 is configured to perform analog-to-digital conversion on the processed voltage signal to obtain a digital signal (an AD value, i.e., a value after converting an analog quantity into a digital quantity). The digital signal is used to indicate the current feedback light signal value of the light source of the specified wavelength.

[0148] The controller 118 is configured to control the multi-channel light source current driver 119 to adjust the output light signal value of the light source of the specified wavelength according to the digital signal.

[0149] In some embodiments, the gain amplifier 116 can be an adjustable gain amplifier, and the controller 118 can be an MCU (Microcontroller Unit). In actual applications, the devices can be flexibly selected as long as the required functions can be achieved.

[0150] As shown in FIG. 7, the light emitted by the light source of a specified wavelength enters the light source feedback unit via refraction or reflection, a part of the feedback light beam enters the first light source detector 108, and the feedback light signal value is obtained according to the feedback light beam. The feedback light signal is converted into a current signal, the current signal is converted into a voltage signal through the current-voltage converter 114, the signal is amplified through the gain amplifier 116, the analog signal is converted into a digital signal through the analog-digital converter 117 and transmitted to the controller 118, and the controller 118 controls the multi-channel light source current driver 119 to adjust the current value of the light source of the specified wavelength, so as to adjust the intensity of the light signal output by the light source of the specified wavelength, so that the light source of the specified wavelength can output higher light intensity stability.

[0151] Optionally, referring to FIG. 7, the optical system of the dry biochemical analyzer further comprises: a light source module, the light source module comprising a first light source module 101 and a second light source module 102.

[0152] The first light source module 101 is arranged along the axis of the optical system of the dry biochemical analyzer, and the second light source module 102 is arranged perpendicular to the axis of the optical system of the dry biochemical analyzer; the first light source module 101 comprises at least one monochromatic light source of a wavelength; the second light source module 102 comprises at least one monochromatic light source of a wavelength; the wavelengths of the monochromatic light sources in the first light source module 101 are different, the wavelengths of the monochromatic light sources in the second light source module 102 are different, and the wavelengths of the monochromatic light sources in the first light source module 101 are different from the wavelengths of the monochromatic light sources in the second light source module 102.

[0153] FIG. 8 is a layout schematic diagram of a first light source module provided by an embodiment of the present disclosure. FIG. 9 is a layout schematic diagram of a second light source module provided by an embodiment of the present disclosure. In the present scheme, the light source of each wavelength can adopt a monochromatic LED light source. As shown in FIG. 8, the first light source module 101 can be provided with four monochromatic LEDs, and the four monochromatic LEDs are symmetrically distributed along the central axis. As shown in FIG. 9, the second light source module 102 is provided with three monochromatic LEDs, and the three monochromatic LEDs have two distribution forms. As shown in FIG. 9(a), the three monochromatic LEDs are symmetrically distributed. As shown in FIG. 9(b), the distribution form of each monochromatic LED light source in the second light source module 102 is consistent with that of each monochromatic LED light source in the first light source module 101, and one LED placement position is left empty. The empty placement can be any one of the four LED placement positions.

[0154] Seven monochromatic LED light sources of different wavelengths are arranged in the first light source module 101 and the second light source module 102, and the switching of the monochromatic LEDs of each wavelength can be realized through the controller 118 of the light source feedback unit and the multi-channel light source current driver 119.

[0155] In some embodiments, the first light source module 101 and the second light source module 102 can be used alternately, and the number of monochromatic light sources in the first light source module 101 is not limited to three, and the number of monochromatic light sources in the second light source module 102 is not limited to four. The light source module is not limited to containing the first light source module 101 and the second light source module 102, and can contain only one module.

[0156] Optionally, referring to FIG. 7, the optical system of the dry biochemical analyzer can further include a beam splitter 103 and a focusing lens 107; the beam splitter 103 is placed at a third preset angle with the axis of the optical system of the dry biochemical analyzer; the third preset angle can be 45°. The light beam emitted by the light source of a specified wavelength is refracted or reflected by the beam splitter 103, and then irradiates on the focusing lens 107, and is focused by the focusing lens 107, and then irradiates on the first light detector 108.

[0157] FIG. 10 is a schematic diagram of an optical path provided by an embodiment of the present disclosure. As shown in FIG. 10, the first light source module 101 emits a light beam to irradiate on the beam splitter 103, is reflected by the beam splitter 103, and then irradiates on the focusing lens 107, is focused by the focusing lens 107, and then irradiates on the first light detector 108.

[0158] The second light source module 102 emits a light beam to irradiate on the beam splitter 103, is refracted by the beam splitter 103, and then irradiates on the focusing lens 107, is focused by the focusing lens 107, and then irradiates on the first light detector 108.

[0159] In some embodiments, the optical system of the dry biochemical analyzer uses a monochromatic LED as a light source. The spectral range of the monochromatic LED is narrow, and there is no need to set a filter for light splitting. Different wavelengths of monochromatic LEDs are selected according to the characteristics of the to-be-tested substances and the detection method used to irradiate the dry reagent sheet 106. In the present embodiment, multiple to-be-tested substances such as albumin and alkaline phosphatase can be tested. Seven test wavelengths are set as 365 nm, 400 nm, 460 nm, 540 nm, 600 nm, 630 nm, and 680 nm. The wavelength of the current monochromatic LED is not limited to this, and the number of monochromatic LEDs is not limited to seven.

[0160] Using a monochromatic LED as a light source, combined with a monochromatic LED driving circuit design, using a driving chip, through a multi-channel analog switch, the current and gain of each wavelength of monochromatic LED can be controlled. The monochromatic LED light source only emits light when the light irradiation position reaches the light irradiation position, which improves the service life of the monochromatic LED.

[0161] The controller 118 can determine a specified wavelength of the monochromatic LED light source corresponding to the current to-be-tested substance according to the type of the current to-be-tested substance, so as to control the multi-channel light source current driver 119 to switch to turn on the specified wavelength of the monochromatic LED light source, so as to control the current to-be-tested substance to be irradiated by the specified wavelength of the monochromatic LED light source, so as to realize the concentration test analysis of the to-be-tested substance.

[0162] FIG. 11 is a schematic diagram of a light source switching light signal provided by an embodiment of the present disclosure. As shown in FIG. 11, the light signal diagram of sequentially switching on and off of 7 monochromatic LEDs, wherein the rising edge is the process of turning on the LED, the falling edge is the process of turning off the LED, the time of turning on and turning off the LED is ms level, and the LED can be quickly stabilized within 3 ms after being turned on.

[0163] The beam splitter 103 can split a beam of light into two beams according to certain reflection and transmission ratios, and can also combine light incident from different directions into one beam. The first light source module 101 and the second light source module 102 incident to the beam splitter 103 from different directions are refracted and reflected on the surface of the beam splitter 103.

[0164] FIG. 12 is a schematic diagram of the first light source module after being split by the beam splitter provided by an embodiment of the present disclosure. As shown in FIG. 12, the first light source module 101 is reflected by the beam splitter 103 and irradiates on the focusing lens 107, and then is focused by the focusing lens 107 and irradiates on the first photodetector 108. The first light source module 101 is refracted by the beam splitter 103 and enters the uniform light illumination light path.

[0165] FIG. 13 is a schematic diagram of the second light source module after being split by the beam splitter provided by an embodiment of the present disclosure. As shown in FIG. 13, the light source emitted by the first light source module 101 is refracted by the beam splitter 103 and irradiates on the focusing lens 107, and then is focused by the focusing lens 107 and irradiates on the first photodetector 108. The light source emitted by the second light source module 102 is reflected by the beam splitter 103 and enters the uniform light illumination light path.

[0166] A mirror can be used to realize the functions of combining light beams of different wavelengths and splitting light beams of a single wavelength. In the present disclosure, the light sources are not limited to be placed on both sides of the beam splitter 103, but can also be placed on one side of the beam splitter 103. The beam splitter 103 can also be a prism, a dichroic mirror, a common flat glass, etc., and is not limited thereto.

[0167] Optionally, still referring to FIG. 7, the data acquisition and conversion module 144 can further include a low-pass filter 115, one end of the low-pass filter 115 is connected with the flow pressure converter 114, and the other end of the low-pass filter 115 is connected with the gain amplifier 116; the low-pass filter 115 is used to filter the voltage signal converted by the flow pressure converter 114 to obtain a filtered voltage signal.

[0168] Optionally, the controller 118 is specifically configured to determine a difference between the current feedback optical signal value and the target optical signal value of the light source of the specified wavelength according to the current feedback optical signal value of the light source of the specified wavelength and the target optical signal value corresponding to the light source of the specified wavelength, generate a current adjustment instruction of the light source current value according to the difference, and control the multi-channel light source current driver 119 to adjust the current value of the light source of the specified wavelength according to the current adjustment instruction, so that the output optical signal value of the light source of the specified wavelength reaches the target optical signal value.

[0169] In some embodiments, the light source feedback unit can use a PID (Proportional-Integral-Derivative) adjustment algorithm to adjust the current of the monochromatic LED light source, and keep the monochromatic LED light intensity stable at any moment, which has a simple structure, high adjustment precision and high stability.

[0170] FIG. 14 is a schematic diagram of a hardware structure of a light source feedback unit according to an embodiment of the present disclosure. The monochromatic LED light source emits a light beam, which is irradiated on a beam splitter 103. The beam splitter 103 divides the irradiated light into two beams, one of which is irradiated on the uniform light illumination light path as an output light beam, and the other of which is irradiated on the light source feedback unit as a feedback light beam. The feedback light beam is focused on the first photodetector 108 after being focused by the focusing lens 107. The first photodetector 108 collects the feedback optical signal value, converts the optical signal into a current signal, converts the current signal into a voltage signal through the current-voltage converter 114, filters the voltage signal through the low-pass filter 115, amplifies the signal through the gain amplifier 116, converts the analog signal into a digital signal through the analog-to-digital converter 117, and transmits the digital signal to the controller 118. The controller 118 controls the multi-channel power current driver 119 to independently control the feedback adjustment of the current of the seven-wavelength monochromatic LED.

[0171] The low-pass filter 115 can be an active low-pass filter. The first photodetector 108 can be a photodiode, a photomultiplier tube, an avalanche photodiode, a silicon photomultiplier, or the like.

[0172] Optionally, the PID feedback process is roughly as follows: the controller 118 selects a single-color LED wavelength according to the type of the measured object, sets an initial current value of the wavelength, sets a gain value of the wavelength, sets a target optical signal value of the wavelength, controls the single-color LED light source to be turned on through the multi-channel light source current driver 119, the first photodetector 108 collects the optical signal value as a feedback optical signal value and sends it to the controller 118, the controller 118 compares the feedback optical signal value with the preset target optical signal value, and adjusts the control of the multi-channel light source current driver 119 by using the PID control algorithm to modify the current value required to control the single-color LED, so as to control the intensity of the single-color LED output optical signal value. The PID control algorithm adjusts the current value through proportional, integral and derivative control according to the deviation, cumulative deviation and rate of change of the optical signal value. Through closed-loop control of the single-color LED current, the optical signal value stably converges to the target value, and precise control of the optical signal value is achieved.

[0173] FIG. 15 is a comparison chart of the output optical signal value when PID feedback and non-PID feedback adjustment are performed according to an embodiment of the present disclosure. As shown in FIG. 15, the horizontal axis is time, and the vertical axis is the collected optical signal value. When PID feedback adjustment is performed, the optical signal value reaches stability within 3 ms; when non-PID feedback is performed, the optical signal value shows a downward trend due to self-heating of the single-color LED as the light-on time increases.

[0174] It is worth noting that the feedback adjustment based on PID feedback can be continuously performed to continuously converge the optical signal value output by the single-color LED to the target optical signal value.

[0175] Optionally, the optical system of the dry biochemical analyzer further comprises: a transmission device (not shown in the figure); at least one measured dry reagent sheet is placed on the transmission device; each measured dry reagent sheet corresponds to a light measurement hole; the transmission device is driven by the motor to perform transmission, so as to switch the current measured dry reagent sheet; the transmission device is controlled by the timing to perform periodic transmission, so as to complete the switching of each measured dry reagent sheet in each cycle.

[0176] In an implementable manner, the optical system of the dry biochemical analyzer provided in the present solution can be used to implement detection of the concentrations of multiple different to-be-measured substances. The reagent sheets corresponding to the different to-be-measured substances are placed on a mechanical transmission device, the reagent sheets correspond to the light measurement holes one by one, the mechanical transmission device is located above the optical system of the dry biochemical analyzer, the mechanical transmission device is driven by a motor, and multiple reagent sheets can be periodically tested for light signals within a fixed reaction time. During the light measurement process, the mechanical transmission device is uniformly driven, a driving chip is used, a plurality of single-color LED light sources are quickly switched through a multi-channel analog switch, and only when the light measurement hole is about to reach the light irradiation area, the single-color LED of the wavelength corresponding to the reagent sheet of the hole is turned on, and when the light measurement hole leaves the light irradiation area, the single-color LED is turned off. The mechanical transmission device drives a cycle to complete the light signal test of all reagent sheets in one light measurement cycle. Through timing control, the light signal test of different to-be-measured substances in the entire reaction cycle can be completed by repeating multiple times. According to the light signal value, the reflectance density is calculated, and the reaction curve corresponding to different to-be-measured substances is drawn. The change value or change rate of the reflectance density is obtained through the reaction curve, and finally the concentration of the to-be-measured substance is obtained according to the calibration curve corresponding to the different to-be-measured substances.

[0177] Taking alkaline phosphatase as an example, the concentration of the to-be-measured substance is tested.

[0178] The alkaline phosphatase reagent sheet is mainly used for quantitative analysis of alkaline phosphatase activity in human serum or plasma. The sample is added to the reagent sheet, passes through the diffusion layer and the filter layer, and enters the reagent layer. The reagent layer contains a nitrophenyl phosphate substrate and other components required for the reaction. The alkaline phosphatase in the sample catalyzes the hydrolysis of the nitrophenyl phosphate to nitrophenol and phosphoric acid under alkaline conditions (pH 10.5). The nitrophenol diffuses to the color development layer, and is monitored by reflectance photometry.

[0179] FIG. 16 is a reflectance density spectrum of nitrophenol provided by an embodiment of the present disclosure. As shown in FIG. 16, the reflectance density spectrum of nitrophenol is shown in FIG. 16. The reflectance density of nitrophenol is the highest at 400 nm, and the reflectance density is almost zero at 480-700 nm.

[0180] FIG. 17 is a schematic diagram of a reaction curve of an alkaline phosphatase reagent sheet according to an embodiment of the present disclosure. As shown in FIG. 17, the reaction curve is obtained by periodically testing the reaction light density of the alkaline phosphatase reagent sheet using a monochromatic LED light source with a central wavelength of 400 nm within a fixed reaction time after sample loading, where the abscissa represents the reaction time and the ordinate represents the reflected light density. The reflected light density of p-nitrophenol changes linearly with time after a certain period of sample loading, and the analysis is performed using a continuous monitoring method. The light density of p-nitrophenol is proportional to the activity of alkaline phosphatase, and the activity of alkaline phosphatase in the sample is calculated by continuously monitoring the change rate of the light density of p-nitrophenol.

[0181] It is worth noting that the reflected light density in FIG. 16 and FIG. 17 is the logarithmic value of reflectivity.

[0182] FIG. 18 is a schematic diagram of a calibration curve of alkaline phosphatase according to an embodiment of the present disclosure. The known concentration of alkaline phosphatase sample is added to the dry reagent sheet, and the change rate of the reflected light density is obtained according to the reaction curve. The change rate of the reflected light density is taken as the ordinate, and the sample concentration is taken as the abscissa, and then the calibration curve of alkaline phosphatase is obtained.

[0183] In the sample concentration test analysis, the change rate of the reflected light density of alkaline phosphatase can be obtained based on the reaction curve of alkaline phosphatase. By comparing the calibration curve of alkaline phosphatase, the concentration corresponding to the change rate of the reflected light density of alkaline phosphatase can be determined as the concentration of the alkaline phosphatase to be tested.

[0184] FIG. 19 is a schematic diagram of a uniform light illumination light path according to an embodiment of the present disclosure. Optionally, as shown in FIG. 19, the uniform light illumination light path can include:

[0185] The compound eye lens 104 and the integrating lens 105; the compound eye lens 104 includes a first face sub-lens and a second face sub-lens, the first face sub-lens is away from the integrating lens 105, and the second face sub-lens is close to the integrating lens 105.

[0186] The first face sub-lens is used to divide the incident light beam into sub-beams and focus them on the second face sub-lens.

[0187] The second face sub-lens and the integrating lens 105 together superimpose the corresponding sub-beams on the focal plane of the integrating lens 105; the dry reagent sheet 106 to be tested is placed on the focal plane of the integrating lens 105.

[0188] Referring to FIG. 19, the light emitted by the first light source module 101 is refracted by the beam splitter 103 and then irradiates the compound eye lens 104 of the uniform light illumination light path. The light emitted by the second light source module 102 is reflected by the beam splitter 103 and then irradiates the compound eye lens 104.

[0189] The side of the fly-eye lens 104 close to the beam splitter 103 is called the first side sub-lens, and the side of the fly-eye lens 104 close to the integrating lens 105 is called the second side sub-lens. The first side sub-lens of the fly-eye lens 104 divides the incident light beam into sub-beams and focuses the sub-beams on the second side sub-lens array. The second side sub-lens and the integrating lens 105 together superimpose the corresponding sub-beams on the focal plane of the integrating lens 105. The dry reagent sheet 106 to be measured is placed on the focal plane of the integrating lens 105.

[0190] FIG. 20 is a schematic diagram of a light homogenization system according to an embodiment of the present disclosure. As shown in FIG. 20, the first sub-lens of the first row divides the incident light beam into sub-beams and focuses the sub-beams on the second sub-lens array of the second row. The second sub-lens and the integrating lens 105 together superimpose the corresponding sub-beams on the focal plane of the integrating lens 105. The thickness of the fly-eye lens 104 is the focal length of the sub-lens. Since the first sub-lens divides the entire wide light beam of the light source into multiple fine light beams, the non-uniformity in each fine light beam range will be smoothed in the superimposition process to obtain uniform illumination.

[0191] Optionally, the integrating lens 105 is preferably a double-cemented lens, which includes a positive lens and a negative lens. The positive lens is made of low-dispersion glass, and the negative lens is made of high-dispersion glass. Of course, the integrating lens 105 can also be a plano-convex lens, a biconvex lens, an aspheric lens, etc.

[0192] In this embodiment, the integrating lens 105 is a double-cemented lens, which uses low-dispersion glass and high-dispersion glass, adopts a positive-negative structure, the positive lens is made of low-dispersion glass and has a small refractive index, and the negative lens is made of high-dispersion glass and has a large refractive index. The two lenses are cemented together to compensate for each other by using the refractive characteristics, thereby eliminating astigmatism and coma. The off-axis light beam passing through the fly-eye lens 104 converges on the back focal plane of the integrating lens 105, forming a light spot with sharp edges and uniform brightness.

[0193] The shape of the light spot can be determined according to the shape of the fly-eye lens 104 selected, and the shape of the light spot includes but is not limited to a rectangle, a circle, a hexagon, etc.

[0194] FIG. 21 is a schematic diagram of another light homogenization system according to an embodiment of the present disclosure. As shown in FIG. 21, multiple light sources are designed to be off-axis, and the combination of the fly-eye lens 104 and the integrating lens 105 is used. Regardless of whether the center of the light source is on the central optical axis of the light homogenization illumination light path, the projection of the light source can be superimposed and focused on the same position.

[0195] Combining FIGS. 20 and 21, according to the geometric relationship of the light propagation in the fly-eye lens 104, it can be obtained that:

[0196] The maximum exit aperture angle of the compound eye sub-lens (herein the sub-lens refers to one sub-lens unit in the first surface sub-lens or the second surface sub-lens, both the first surface sub-lens and the second surface sub-lens are composed of multiple sub-lenses) is determined by the size of the target irradiation surface and the focal length of the integrating lens 105, and can be obtained as follows:

[0197] The light beam split by the compound eye lens 104 is a fine light beam, and thus can be approximated as:

[0198] According to the refractive index formula: n sin ω ≈ sin ω', the following can be obtained:

[0199] Thus, the focal length f1 of the compound eye lens 104 can be calculated.

[0200] According to the functional relationship between the radius of curvature of the sub-lens and the focal length f1 of the compound eye lens 104:

[0201] The radius of curvature of the sub-lens can be obtained as:

[0202] Wherein:

[0203] The length of the sub-lens in the compound eye lens 104 is a1;

[0204] The length of the illuminated area is a2;

[0205] The focal length of the sub-lens is f1;

[0206] The focal length of the integrating lens 105 is f2;

[0207] The refractive index of the compound eye lens 104 is n;

[0208] The incident angle of the rear surface of the compound eye lens 104 is ω;

[0209] The refractive angle of the rear surface of the compound eye lens 104 is ω';

[0210] The optical system parameters can be calculated according to the above formulas.

[0211] In this embodiment, the light spot irradiated on the dry reagent sheet 106 is designed as 8.4×8.4mm, the focal length of the integrating lens 105 is selected as 40mm, according to the area diameter 6mm of the light source irradiated on the compound eye lens 104, the size of the compound eye sub-lens is set as 1.25×1.25mm, the refractive index of the compound eye lens 104 is 1.5, and according to the formula The following can be obtained: The focal length f1 of the sub-lens of the compound eye lens 104 can be obtained, and according to the formula for calculating the radius of curvature of the plano-convex lens Wherein f1 is the focal length of the sub-lens, and R1 is the radius of curvature of the sub-lens.

[0212] That is The radius of curvature of the sub-lens is 2.96 mm.

[0213] Optionally, the collection light path can include: a first lens 109, an aperture stop 110, a field stop 111, a second lens 112, and a second photodetector 113; the first lens 109, the aperture stop 110, the field stop 111, the second lens 112, and the second photodetector 113 are sequentially arranged away from the measured dry reagent sheet 106 along the optical axis of the collection light path; the aperture stop 110 is arranged on the image-side focal plane of the first lens 109 and is placed parallel to the first lens 109; the field stop 111 is arranged at the image plane of the first lens 109; the light reflected from the measured dry reagent sheet 106 and having an angle with the optical axis of the collection light path satisfying a preset angle is focused by the first lens 109, the focused light beam passes through the aperture stop 110 to reach the image plane, and then passes through the field stop 111 to be incident on the second lens 112 and is focused on the second photodetector 113 by the second lens 112.

[0214] FIG. 22 is a schematic diagram of a collection light path according to an embodiment of the present disclosure. As shown in FIG. 22, the collection light path can be arranged at an angle θ with respect to the axis of the optical system of the dry biochemical analyzer.

[0215] The light beam after the uniform light treatment via the uniform light illumination light path is irradiated on the surface of the measured dry reagent sheet 106, a part of which is absorbed by the measured dry reagent sheet 106 and a part of which is diffusely reflected. The direction of the diffusely reflected light is random, the collection light path is arranged at an angle θ with respect to the irradiation light path, the diffusely reflected light enters the collection light path, is focused by the first lens 109, the focused light beam passes through the aperture stop 110, the aperture stop 110 is arranged on the image-side focal plane of the first lens 109, the aperture stop 110 is placed parallel to the first lens 109, the light passing through the aperture stop 110 reaches the image plane, the field stop 111 is arranged at the image plane, the field stop 111 is used to limit the detection range on the surface of the measured dry reagent sheet 106, the light passing through the field stop 111 is incident on the second lens 112, and is focused on the second photodetector 113 by the second lens 112.

[0216] In this embodiment, the collection light path is arranged at an angle θ with respect to the axis of the optical system of the dry biochemical analyzer, and the angle θ can be 45°, but is not limited thereto.

[0217] FIG. 23 is a schematic diagram of a telecentric optical path according to an embodiment of the present disclosure. As shown in FIG. 23, the aperture stop 110 is placed on the image-side focal plane of the first lens 109 to form a telecentric optical path on the object side. The aperture stop 110 can select a detection light beam, and only a very thin light beam emitted by the main light ray of the measured dry reagent sheet 106 parallel to the optical axis can enter the collection optical path. Therefore, the collection optical path can uniformly collect light rays of the entire illuminated surface of the measured dry reagent sheet 106. When the measured dry reagent sheet 106 is shifted, the main light ray still coincides, and the projection center point is the same. Therefore, the test error caused by the position deviation of the measured surface is reduced.

[0218] FIG. 24 is a schematic diagram of a field stop design optical path according to an embodiment of the present disclosure. The optical axis of the collection optical path is arranged at an angle θ with the central normal line of the measured dry reagent sheet 106. Therefore, the angle between the main light ray of the measured dry reagent sheet 106 and the optical axis of the collection optical path in the orthogonal direction is θ. Since the collection optical path collects diffuse reflection light, the angle θ is preferably 30°-60°, but is not limited thereto.

[0219] It should be noted that the aperture stop 110 is placed on the image-side focal plane of the first lens 109 to control the aperture angle u (the angle shown in FIG. 23) of the received diffuse reflection light of the measured dry reagent sheet 106. The diameter of the aperture stop 110 is 2f3tan u, where f3 is the focal length of the first lens 109.

[0220] In the present embodiment, the focal length of the first lens 109 is 15 mm, and the aperture angle u is 5°. Therefore, the diameter of the aperture stop 110 is 2x15xtan5°=2.6 mm.

[0221] Alternatively, the size of the field stop 111 is determined according to the size of the measured region on the measured dry reagent sheet 106 and the first preset angle between the optical axis of the collection optical path and the optical axis of the optical system.

[0222] Referring to FIG. 24, in some embodiments, the field stop 111 is placed on the image plane of the first lens 109 to limit the detection range on the surface of the measured dry reagent sheet 106. The field stop 111 is arranged at an angle θ' with the optical axis of the collection optical path in the orthogonal direction.

[0223] When the measured dry reagent sheet 106 is inclined relative to the optical axis of the collection optical path, the image of the measured dry reagent sheet 106 formed by the first lens 109 is also inclined relative to the optical axis of the collection optical path. The inclination angle of the image plane is calculated as follows:

[0224] Perpendicular magnification

[0225] Axial magnification α=β 2

[0226] Then:

[0227] Wherein, the angle between the measured dry reagent sheet 106 and the optical axis of the collection light path is θ;

[0228] The angle between the field stop 111 and the optical axis of the collection light path is θ';

[0229] The half-height of the measured dry reagent sheet 106 perpendicular to the optical axis of the collection light path is y;

[0230] The half-height of the measured dry reagent sheet 106 parallel to the optical axis of the collection light path is dl;

[0231] The half-height of the image perpendicular to the optical axis of the collection light path is y';

[0232] The half-height of the image parallel to the optical axis of the collection light path is dl'.

[0233] The circularly inclined measured dry reagent sheet 106 is imaged by the first lens 109, and the image is an ellipse, the vertical axis magnification of the major axis of the ellipse is β, and the vertical axis magnification of the minor axis is βcosθ'cosθ+αsinθ' sinθ.

[0234] In this embodiment, θ is 45°, the radius of the detection area of the measured dry reagent sheet 106 is 3mm, and the vertical axis magnification β of the measured dry reagent sheet 106 after imaging by the first lens 109 is-0.5 times, so that: θ'=26.56°

[0235] The ratio of the major axis to the minor axis of the elliptical image is about 1:0.79, that is, the major axis of the ellipse is 3mm, and the minor axis is 2.37mm.

[0236] That is, the field stop 111 can be determined as an ellipse with an inclination angle of 26.56°, a major axis of 3mm, and a minor axis of 2.37mm.

[0237] Through the above calculation process, the size of the detection area of the measured dry reagent sheet 106 can be calculated according to the known size of the field stop 111, and the size of the field stop 111 to be set can be calculated according to the known size of the detection area of the measured dry reagent sheet 106.

[0238] Optionally, the controller 118 is specifically configured to determine a light source of a specified wavelength corresponding to the to-be-measured object according to the type of the to-be-measured object, and send a control instruction to the multi-channel light source current driver 119 to control the multi-channel light source current driver 119 to turn on the light source of the specified wavelength.

[0239] It can be known from Table 1 that the detection wavelength corresponding to different analytes is different under different analysis methods. The light source of the specified wavelength corresponding to the analyte can be determined according to the type of the analyte and the analysis method used.

[0240] For example, the analyte is alkaline phosphatase. When the continuous monitoring method is used to analyze the concentration of the analyte, the light source of the specified wavelength corresponding to the analyte is determined to be 400 nm. Then, the controller 118 can send a control instruction to the multi-channel light source current driver 119 according to the determined light source of the specified wavelength, so as to control the multi-channel light source current driver 119 to switch the light source, and to turn on the monochromatic light source with a wavelength of 400 nm at present.

[0241] Alternatively, based on the optical system of the dry biochemical analyzer provided in the above embodiment, the detection of multiple different biochemical items can be realized. The reagent sheets of different biochemical items are placed on a mechanical transmission device, and the reagent sheets correspond to the light measurement holes one by one. The mechanical transmission device is located above the optical system of the dry biochemical analyzer. The mechanical transmission device is driven by a motor. Multiple reagent sheets can be periodically tested for light signals within a fixed reaction time. During the light measurement process, the mechanical transmission device is uniformly driven. A driving chip is used to control the rapid switching of multiple monochromatic LED light sources through a multi-channel analog switch. The monochromatic LED of the wavelength corresponding to the reagent sheet of the light measurement hole is turned on when the light measurement hole is about to reach the light irradiation area, and the monochromatic LED is turned off when the light measurement hole leaves the light irradiation area. The mechanical transmission device drives a cycle to complete the light signal test of all reagent sheets within one light measurement cycle. Through timing control, the light signal test of different biochemical detection items within the entire reaction cycle can be completed multiple times. The reflectance density of different biochemical detection items is calculated according to the light signal values of different biochemical detection items within the entire reaction cycle, so as to draw the reaction curves of different biochemical detection items. The change value or rate of the reflectance density of different biochemical detection items is obtained through the reaction curves of different biochemical detection items. Finally, the concentration of the analyte in the sample of different biochemical detection items is obtained according to the corresponding calibration curve of different biochemical detection items.

[0242] Next, some alternative schemes derived from the present scheme will be described:

[0243] FIG. 25 is a schematic diagram of another uniform illumination light path provided in an embodiment of the present disclosure. Alternatively, in the present embodiment, the compound eye lens 104 includes a first single-sided compound eye lens 104-1 and a second single-sided compound eye lens 104-2. The first single-sided compound eye lens 104-1 and the second single-sided compound eye lens 104-2 are placed in parallel and the distance between them is the focal length of the sub-lens. The sub-lens is a lens unit in the first single-sided compound eye lens 104-1 or the second single-sided compound eye lens 104-2.

[0244] As shown in FIG. 25, the first light source module 101 emits a light beam to the beam splitter 103, and the light beam is reflected by the beam splitter 103 to the focusing lens 107, and then is focused by the focusing lens 107 to the first photodetector 108. The second light source module 102 emits a light beam to the beam splitter 103, and the light beam is refracted by the beam splitter 103 to the focusing lens 107, and then is focused by the focusing lens 107 to the first photodetector 108.

[0245] The light emitted by the first light source module 101 is refracted by the beam splitter 103 and then is incident on the first single-sided fly's eye lens 104-1. The light emitted by the second light source module 102 is reflected by the beam splitter 103 and then is incident on the first single-sided fly's eye lens 104-1. The sub-lenses of the first single-sided fly's eye lens 104-1 split the incident light beam into sub-beams and focus the sub-beams on the array of the second single-sided fly's eye lens 104-2. The first single-sided fly's eye lens 104-1 and the second single-sided fly's eye lens 104-2 are symmetrically arranged in parallel. The sub-lenses in the second single-sided fly's eye lens 104-2 and the integrating lens 105 together superimpose the corresponding sub-beams on the focal plane of the integrating lens 105. The measured dry reagent sheet 106 is placed on the focal plane of the integrating lens 105. The multiple light sources are designed to be off-axis. The fly's eye lens 104 and the integrating lens 105 are combined to project and focus on the same position.

[0246] FIG. 26 is a schematic diagram of another uniform light illumination light path provided by the embodiment of the present disclosure.

[0247] Optionally, the uniform light illumination light path can further include a glass lens 135. The glass lens 135 is placed between the fly's eye lens 104 and the integrating lens 105, and the glass lens 135 is at a fourth preset angle with respect to the optical axis of the optical system. The light beam emitted by the light source of the specified wavelength is refracted or reflected by the beam splitter 103, and then is incident on the fly's eye lens 104, and then is incident on the glass lens 135 through the fly's eye lens 104. The incident light is reflected or refracted by the glass lens 135, and then is incident on the focusing lens 107, and then is focused by the focusing lens 107 to the first photodetector 108.

[0248] In this embodiment, the beam splitter 103 can be replaced by a dichroic mirror, and a glass lens 135 is added. As shown in FIG. 26, the first light source module 101 emits a light beam to the beam splitter 103, which is refracted by the beam splitter 103 and then incident on the fly's eye lens 104. The second light source module 102 emits a light beam to the beam splitter 103, which is reflected by the beam splitter 103 and then incident on the fly's eye lens 104. The first surface sub-lens of the fly's eye lens 104 divides the incident light beam into sub-beams and focuses them on the second surface sub-lens array. The light beams passing through the second surface sub-lens are incident on the glass lens 135, of which a part of the light is reflected by the glass lens 135 and then enters the light source feedback unit, which is focused by the focusing lens 107 and then incident on the first photodetector 108. A part of the light is refracted by the glass lens 135 and then enters the integrating lens 105, which focuses the light and then the light is incident on the dry reagent sheet 106 to be measured, which is placed on the focal plane of the integrating lens 105.

[0249] The multiple light sources are designed off-axis, and the fly's eye lens 104 and the integrating lens 105 are combined, and the projection is focused on the same position.

[0250] FIG. 27 is a layout schematic diagram of a light source module provided by an embodiment of the present disclosure. Optionally, in this embodiment, the light source module includes a third light source module 120; the third light source module 120 is arranged along an axis perpendicular to the optical system; and the third light source module 120 includes at least one monochromatic light source of a wavelength.

[0251] In this embodiment, the third light source module 120 is used to replace the first light source module 101 and the second light source module 102. As shown in FIG. 27, the third light source module 120 is arranged along the optical axis of the light source feedback unit. The third light source module 120 is composed of seven monochromatic LED light sources of different wavelengths. The third light source module 120 emits a light beam to the beam splitter 103, which is refracted by the beam splitter 103 and then incident on the focusing lens 107, which focuses the light and then the light is incident on the first photodetector 108.

[0252] The light emitted by the third light source module 120 is reflected by the beam splitter 103 and then incident on the fly's eye lens 104 of the uniform light illumination light path. The first surface sub-lens of the fly's eye lens 104 divides the incident light beam into sub-beams and focuses them on the second surface sub-lens array. The sub-lenses in the second surface sub-lens and the integrating lens 105 together superimpose the corresponding sub-beams on the focal plane of the integrating lens 105, and the dry reagent sheet 106 to be measured is placed on the focal plane of the integrating lens 105.

[0253] The multiple light sources are designed off-axis, and the fly's eye lens 104 and the integrating lens 105 are combined, and the projection is focused on the same position.

[0254] Fig. 28 is a schematic diagram of another layout of a light source module according to an embodiment of the present disclosure. Optionally, in the present embodiment, the light source module comprises a fourth light source module 140; the fourth light source module 140 is arranged along the optical axis of the optical system; the fourth light source module 140 comprises monochromatic light sources of at least one wavelength.

[0255] In the present embodiment, the fourth light source module 140 is used instead of the first light source module 101 and the second light source module 102. Different from the arrangement in Fig. 27, in Fig. 28, the fourth light source module 140 is arranged along the optical axis of the homogenizing illumination light path.

[0256] The fourth light source module 140 comprises monochromatic LED light sources of seven wavelengths. The fourth light source module 140 emits a light beam to the beam splitter 103, which is reflected by the beam splitter 103 to the focusing lens 107, and is focused by the focusing lens 107 to the first photodetector 108.

[0257] The light emitted by the fourth light source module 140 is refracted by the beam splitter 103 to the fly's eye lens 104 of the homogenizing illumination light path. The first face sub-lens of the fly's eye lens 104 divides the incident light beam into sub-beams and focuses them to the second face sub-lens array, and the sub-lenses in the second face sub-lens array and the integrating lens 105 together superimpose the corresponding sub-beams on the focal plane of the integrating lens 105, on which the dry reagent sheet 106 is placed.

[0258] The multiple light sources are designed to be off-axis, and the fly's eye lens 104 and the integrating lens 105 are used in combination, and the projection is focused and superimposed on the same position.

[0259] Fig. 29 is a schematic diagram of another layout of a light source module according to an embodiment of the present disclosure. Optionally, in the present embodiment, the monochromatic light sources of different wavelengths in the light source module are independently arranged. Among them, a first part of the monochromatic light sources in the light source module is arranged along the optical axis of the optical system; a second part of the monochromatic light sources in the light source module is arranged perpendicular to the optical axis of the optical system; the beam splitter is a dichroic mirror, and the number of dichroic mirrors corresponds to the number of the first part of the monochromatic light sources. Each first part of the monochromatic light sources is aligned with the corresponding dichroic mirror in the vertical direction.

[0260] The first part of the monochromatic light sources here can include the first monochromatic light source 122, the second monochromatic light source 123, the third monochromatic light source 124, the fourth monochromatic light source 125, the fifth monochromatic light source 126, and the sixth monochromatic light source 127 as shown in FIG. 29. The second part of the monochromatic light sources includes the seventh monochromatic light source 121. Each of the light sources in the first part of the monochromatic light sources is provided with a corresponding dichroic mirror. For example, the first monochromatic light source 122 is provided with the first dichroic mirror 128, the second monochromatic light source 123 is provided with the second dichroic mirror 129, the third monochromatic light source 124 is provided with the third dichroic mirror 130, the fourth monochromatic light source 125 is provided with the fourth dichroic mirror 131, the fifth monochromatic light source 126 is provided with the fifth dichroic mirror 132, and the sixth monochromatic light source 127 is provided with the sixth dichroic mirror 133.

[0261] The plurality of monochromatic light sources in the embodiment are combined by the plurality of dichroic mirrors. The arrangement positions of the monochromatic light sources can be determined according to the types of the dichroic mirrors.

[0262] Alternatively, the arrangement positions of the monochromatic light sources are determined according to the types of the dichroic mirrors selected and the wavelengths of the monochromatic light sources, and the arrangement positions of the dichroic mirrors are determined according to the types of the dichroic mirrors selected and the cut-off wavelengths of the dichroic mirrors.

[0263] As shown in FIG. 29, if the dichroic mirror is a long-pass dichroic mirror, the wavelength of the seventh monochromatic light source 121 is greater than the wavelength of the first monochromatic light source 122, which is greater than the wavelength of the second monochromatic light source 123, which is greater than the wavelength of the third monochromatic light source 124, which is greater than the wavelength of the fourth monochromatic light source 125, which is greater than the wavelength of the fifth monochromatic light source 126, which is greater than the wavelength of the sixth monochromatic light source 127, and the cut-off wavelength of the first dichroic mirror 128 is greater than the cut-off wavelength of the second dichroic mirror 129, which is greater than the cut-off wavelength of the third dichroic mirror 130, which is greater than the cut-off wavelength of the fourth dichroic mirror 131, which is greater than the cut-off wavelength of the fifth dichroic mirror 132, which is greater than the cut-off wavelength of the sixth dichroic mirror 133.

[0264] If the dichroic mirror is a short-pass dichroic mirror, the wavelength of the seventh monochromatic light source 121 is less than the wavelength of the first monochromatic light source 122, which is less than the wavelength of the second monochromatic light source 123, which is less than the wavelength of the third monochromatic light source 124, which is less than the wavelength of the fourth monochromatic light source 125, which is less than the wavelength of the fifth monochromatic light source 126, which is less than the wavelength of the sixth monochromatic light source 127, and the cut-off wavelength of the first dichroic mirror 128 is less than the cut-off wavelength of the second dichroic mirror 129, which is less than the cut-off wavelength of the third dichroic mirror 130, which is less than the cut-off wavelength of the fourth dichroic mirror 131, which is less than the cut-off wavelength of the fifth dichroic mirror 132, which is less than the cut-off wavelength of the sixth dichroic mirror 133. Wherein, “>” means greater than; “<” means less than.

[0265] The seventh monochromatic light source 121, the first monochromatic light source 122, the second monochromatic light source 123, the third monochromatic light source 124, the fourth monochromatic light source 125, and the fifth monochromatic light source 126 are combined by the plurality of dichroic mirrors and irradiate the sixth dichroic mirror 133. The combined light is reflected by the sixth dichroic mirror 133 and enters the uniform light illumination light path. The combined light is refracted by the sixth dichroic mirror 133 and enters the light source feedback unit. The seventh monochromatic light source 127 is refracted by the sixth dichroic mirror 133 and enters the uniform light illumination light path. The seventh monochromatic light source 127 is reflected by the sixth dichroic mirror 133 and enters the light source feedback unit. The light entering the light source feedback unit is focused by the focusing lens 107 and irradiates the first photodetector 108.

[0266] The light entering the uniform light illumination light path is incident on the compound eye lens 104. The first face sub-lens of the compound eye lens 104 divides the incident light beam into sub-beams and focuses them on the second face sub-lens array. The sub-lenses in the second face sub-lens array and the integrating lens 105 together superimpose the corresponding sub-beams on the focal plane of the integrating lens 105. The measured dry reagent sheet 106 is placed on the focal plane of the integrating lens 105.

[0267] Optionally, the number of monochromatic light sources is not limited to seven. The monochromatic light sources can be monochromatic LED light sources. The number of dichroic mirrors is not limited to six.

[0268] In summary, the optical system of the dry biochemical analyzer provided in the embodiment can be composed of a light source feedback unit, a uniform light illumination light path, and a collection light path. The light source feedback unit can feedback and adjust the current of the light source, so that the light intensity output by the light source is stable. The structure is simple, and the adjustment precision and stability are high. The multi-channel light source current driver provided in the light source feedback unit can realize rapid switching control of different wavelengths of monochromatic light sources. The uniform light illumination light path performs uniform light processing on the incident light, so that uniform illumination is obtained on the measured dry reagent sheet. The light path is simple, and multiple monochromatic light sources of different wavelengths arranged off-axis can be superimposed and focused at the same position. The collection light path is set as a telecentric light path, and a field stop is provided, so that the light rays of the entire illuminated surface can be uniformly collected. The use of the system can improve the accuracy of the collected reaction light corresponding to the measured object, thereby improving the accuracy of the subsequent analysis results of the measured object.

[0269] In several embodiments provided in the present disclosure, it should be understood that the disclosed system and method can be implemented in other manners. For example, the embodiments of the system described above are merely illustrative. For example, the division of the units is only a logical function division. There can be another division manner for the actual implementation. For example, multiple units or components can be combined or integrated into another system, or some features can be ignored or not executed. In addition, the displayed or discussed mutual couplings or direct couplings or communication connections can be indirect couplings or communication connections through some interfaces, devices or units, and can be in electrical, mechanical or other forms. Industrial applicability

[0270] The present disclosure provides an optical system of a dry biochemical analyzer, which can be composed of a light source feedback unit, a uniform light illumination light path and a collection light path. The light source feedback unit can feed back and adjust the current of the light source, so that the light intensity output by the light source is stable. The structure is simple, and the adjustment precision and stability are high. The multi-channel light source current driver arranged in the light source feedback unit can realize rapid switching control of monochromatic light sources of different wavelengths. The incident light is uniformly processed by the uniform light illumination light path, so that uniform illumination can be obtained on the measured dry reagent sheet. The light path is simple, and multiple monochromatic light sources of different wavelengths arranged off-axis can be focused at the same position. The collection light path is set as a telecentric light path, and a field stop is arranged, so that the light of the entire illuminated surface can be uniformly collected. The system can improve the accuracy of the collected reaction light corresponding to the measured object, thereby improving the accuracy of the subsequent analysis result of the measured object.

[0271] In addition, it can be understood that the optical system of the dry biochemical analyzer provided by the embodiments of the present disclosure is reproducible and can be used in various industrial applications. For example, the optical system of the dry biochemical analyzer provided by the embodiments of the present disclosure can be used in the field of circuit control technology.

Claims

1. An optical system of a dry biochemical analyzer, characterized by, The optical system comprises a light source feedback unit, a uniform light illumination light path and a collection light path; the optical system has a central normal line of a dry reagent sheet to be measured as an axis, the light source feedback unit is arranged perpendicularly to the axis of the optical system; an optical axis of the uniform light illumination light path coincides with the axis of the optical system; an optical axis of the collection light path forms a first preset angle with the axis of the optical system; The light source feedback unit is used for controlling a light beam of a specified wavelength corresponding to a to-be-measured object according to a type of the to-be-measured object, collecting a feedback light beam after the light beam emitted by the light source of the specified wavelength is reflected or refracted, and performing feedback adjustment according to a feedback light signal value collected by the feedback light beam and a preset target light signal value corresponding to the light source of the specified wavelength, so as to adjust an output light signal value of the light source of the specified wavelength. The uniform light illumination light path is used for splitting, focusing and converging an incident light beam after the light beam emitted by the light source of the specified wavelength is reflected or refracted on the dry reagent sheet to be measured. The collection light path is used for collecting light rays reflected on the dry reagent sheet to be measured and satisfying a second preset angle with an optical axis of the collection light path, and obtaining a light signal. The light source feedback unit comprises a data acquisition and conversion module, a control module and a driving module; the data acquisition and conversion module, the control module and the driving module are connected in sequence.

2. The optical system of a dry biochemical analyzer according to claim 1, characterized in that, The data acquisition and conversion module is used for acquiring the feedback light signal value and performing conversion processing on the feedback light signal value to obtain a digital signal. The control module is used for controlling the driving module to adjust the output light signal value of the light source of the specified wavelength according to the digital signal.

3. The optical system of the dry biochemical analyzer according to claim 2, wherein The data acquisition and conversion module comprises a first light source detector, a current-to-voltage converter, a gain amplifier and an analog-to-digital converter. The first light source detector is used for acquiring the feedback light beam, obtaining a feedback light signal value of the feedback light beam according to the feedback light beam, and converting the feedback light signal value into a current signal. The current-to-voltage converter is used for converting the current signal into a voltage signal. The gain amplifier is used for performing signal amplification processing on the voltage signal to obtain a processed voltage signal. The analog-to-digital converter is used for performing analog-to-digital conversion on the processed voltage signal to obtain a digital signal; the digital signal is used for indicating a current feedback light signal value of the light source of the specified wavelength. The optical system further comprises a beam splitter and a focusing lens; the beam splitter is arranged at a third preset angle with the axis of the optical system.

4. The optical system of a dry biochemical analyzer according to claim 3, characterized in that, The light beam emitted by the light source of the specified wavelength is refracted or reflected by the beam splitter, irradiated on the focusing lens, and focused by the focusing lens and irradiated on the first light source detector. The control module comprises a controller; the driving module comprises a multi-channel light source current driver.

5. The optical system of a dry biochemical analyzer according to claim 2, wherein The controller is used for controlling the multi-channel light source current driver to adjust the output light signal value of the light source of the specified wavelength according to the digital signal. ​ 6. The optical system of the dry biochemical analyzer according to claim 5, wherein the controller is configured to determine a difference between the current feedback light signal value of the light source of the specified wavelength and a preset target light signal value corresponding to the light source of the specified wavelength according to the current feedback light signal value of the light source of the specified wavelength and the preset target light signal value corresponding to the light source of the specified wavelength; generate a current adjustment instruction of the light source current value according to the difference; and control the multi-channel light source current driver to adjust the current value of the light source of the specified wavelength according to the current adjustment instruction, so that the output light signal value of the light source of the specified wavelength reaches the preset target light signal value.

7. The optical system of the dry biochemical analyzer according to claim 5, wherein the controller is configured to determine the light source of the specified wavelength corresponding to the to-be-measured substance according to the type of the to-be-measured substance, and send a control instruction to the multi-channel light source current driver to control the multi-channel light source current driver to turn on the light source of the specified wavelength. The data acquisition and conversion module further comprises a low-pass filter, one end of the low-pass filter is connected with the flow pressure converter, and the other end of the low-pass filter is connected with the gain amplifier. The low-pass filter is configured to filter the voltage signal converted by the flow pressure converter to obtain a filtered voltage signal. The uniform light illumination light path comprises a compound eye lens and an integrating lens; the compound eye lens comprises a first face sub-lens and a second face sub-lens, the first face sub-lens is away from the integrating lens, and the second face sub-lens is close to the integrating lens; 8. The optical system of a dry biochemical analyzer according to claim 3, characterized in that, The first face sub-lens is configured to divide the incident light beam into sub-beams and focus the sub-beams on the second face sub-lens; The second face sub-lens and the integrating lens are configured to coincide corresponding sub-beams on the focal plane of the integrating lens; and the dry reagent sheet to be measured is placed on the focal plane of the integrating lens.

9. The optical system of a dry biochemical analyzer according to claim 4, wherein, The integrating lens is a double-cemented lens comprising a positive lens and a negative lens, the positive lens is made of low-dispersion glass, and the negative lens is made of high-dispersion glass.

11. The optical system of the dry biochemical analyzer according to claim 9, wherein the compound eye lens comprises a first single-face compound eye lens and a second single-face compound eye lens; the first single-face compound eye lens and the second single-face compound eye lens are placed in parallel with a spacing being the focal length of a sub-lens; and the sub-lens is a lens unit in the first single-face compound eye lens or the second single-face compound eye lens. The uniform light illumination light path further comprises a glass lens; the glass lens is placed between the compound eye lens and the integrating lens, and the glass lens is at a fourth preset angle with respect to the axis of the optical system; 10. The optical system of a dry biochemical analyzer according to claim 9, characterized in that, The light beam emitted by the light source of the specified wavelength is refracted or reflected by the beam splitter, then irradiates in the compound eye lens, and then enters the glass lens through the compound eye lens; The incident light is reflected or refracted by the glass lens, then enters the focusing lens, and then irradiates on the first light source detector after being focused by the focusing lens. ​ 12. The optical system of a dry biochemical analyzer according to claim 9, characterized in that, ​ ​ ​ 13. The optical system of a dry biochemical analyzer according to claim 1, characterized in that, The collection light path comprises a first lens, an aperture diaphragm, a field diaphragm, a second lens and a second photodetector; the first lens, the aperture diaphragm, the field diaphragm, the second lens and the second photodetector are sequentially arranged away from the dry reagent sheet to be measured along an optical axis of the collection light path; the aperture diaphragm is arranged on an image plane of the first lens and is placed in parallel with the first lens; the field diaphragm is arranged on an image plane of the first lens; The light reflected from the dry reagent sheet to be measured and having an included angle with the optical axis of the collection light path satisfying the second preset angle is focused by the first lens, the focused light beam passes through the aperture diaphragm to reach the image plane, and then passes through the field diaphragm to be incident on the second lens, and is focused on the second photodetector by the second lens.

14. The optical system of a dry biochemical analyzer according to claim 13, characterized in that, The size of the field diaphragm is determined according to the size of the region to be measured on the dry reagent sheet to be measured and the first preset angle between the optical axis of the collection light path and the axis of the optical system.

15. The optical system of a dry biochemical analyzer according to claim 4, characterized in that, The optical system further comprises a light source module, and the light source module comprises monochromatic light sources of at least one wavelength. The light source of the specified wavelength is a light source in the light source module.

16. The optical system of a dry biochemical analyzer according to claim 15, characterized in that, The light source module comprises a first light source module and a second light source module. The first light source module is arranged along the axis of the optical system, and the second light source module is arranged perpendicular to the axis of the optical system. The first light source module comprises monochromatic light sources of at least one wavelength. The second light source module comprises monochromatic light sources of at least one wavelength. The wavelengths of the monochromatic light sources in the first light source module are different, the wavelengths of the monochromatic light sources in the second light source module are different, and the wavelengths of the monochromatic light sources in the first light source module are different from the wavelengths of the monochromatic light sources in the second light source module.

17. The optical system of a dry biochemical analyzer according to claim 15, characterized in that, The light source module comprises a third light source module; the third light source module is arranged perpendicular to the axis of the optical system. The third light source module comprises monochromatic light sources of at least one wavelength.

18. The optical system of a dry biochemical analyzer according to claim 15, characterized in that, The light source module comprises a fourth light source module; the fourth light source module is arranged along the axis of the optical system. The fourth light source module comprises monochromatic light sources of at least one wavelength.

19. The optical system of a dry biochemical analyzer according to claim 15, wherein, A first part of the monochromatic light sources in the light source module is arranged along the axis of the optical system, and a second part of the monochromatic light sources in the light source module is arranged perpendicular to the axis of the optical system. The beam splitter is a dichroic mirror, and the number of the dichroic mirrors corresponds to the number of the first part of the monochromatic light sources. Each first part of the monochromatic light sources is aligned with the corresponding dichroic mirror in the vertical direction.

20. The optical system of a dry biochemical analyzer according to claim 19, characterized in that, The arrangement position of each monochromatic light source is determined according to the type of the selected dichroic mirror and the wavelength of each monochromatic light source. The arrangement position of each dichroic mirror is determined according to the type of the selected dichroic mirror and the cut-off wavelength of each dichroic mirror.

21. The optical system of a dry chemistry biochemical analyzer according to any one of claims 1-20, characterized in that, The optical system further comprises a transmission device; at least one dry reagent sheet to be measured is arranged on the transmission device; each dry reagent sheet to be measured corresponds to a light measurement hole position; The transmission device is driven by a motor to switch the current dry reagent sheet to be measured. The transmission device is used for periodic cycle transmission under time sequence control to complete switching of each dry reagent piece to be measured in each cycle.

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