CN118225769A

CN118225769A - Optical system of dry biochemical analyzer

Info

Publication number: CN118225769A
Application number: CN202410613067.6A
Authority: CN
Inventors: 孙尧; 王巧; 黄挺; 张晓婷
Original assignee: Xi'an Biolab Biotechnology Co ltd
Current assignee: Xi'an Biolab Biotechnology Co ltd
Priority date: 2024-05-17
Filing date: 2024-05-17
Publication date: 2024-06-21
Anticipated expiration: 2044-05-17
Also published as: CN118225769B

Abstract

The application provides an optical system of a dry biochemical analyzer, and relates to the technical field of biochemical detection. The system consists of a light source feedback unit, a uniform illumination light path and a collection light path, and the current of the light source can be adjusted through the light source feedback unit, 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 multi-channel light source current driver arranged in the light source feedback unit can realize the rapid switching control of the monochromatic light sources with different wavelengths. The incident light is subjected to uniform light treatment through the uniform light illumination light path, uniform illumination can be obtained on the dry reagent sheet to be measured, the light path is concise, and a plurality of monochromatic light sources with different wavelengths arranged off-axis can be overlapped and focused at the same position. By setting the collecting light path as a telecentric light path and setting a field diaphragm, the light rays of the whole illuminated surface can be uniformly collected. By adopting the system, the accuracy of the collected reaction light corresponding to the object to be detected can be improved, so that the accuracy of the subsequent analysis result of the object to be detected is improved.

Description

Optical system of dry biochemical analyzer

Technical Field

The application relates to the technical field of biochemical detection, in particular to an optical system of a dry biochemical analyzer.

Background

The principle of the dry biochemical analyzer is that a body fluid sample is added on a dry reagent sheet, and a measured object in the sample and a reagent sheet component react biochemically to cause the color of the reagent sheet, namely the reflection optical density to change. And (3) periodically measuring the reflection optical density of the reagent sheet to a specific wavelength in a fixed reaction time after sample addition, and finally drawing a reaction curve of the sample in the whole reaction time. And calculating a reaction curve to obtain a change value or a change rate of the reflected optical density, and then obtaining the concentration or the biological activity of the object to be detected in the sample according to the calibration curve.

Currently, the conventional dry biochemical analyzer optical system is as follows: the single-color LED (LIGHT EMITTING Diode) is used as a light source, a plurality of wavelength single-color LED light sources are concentrically arranged, the light source emits light beams, the light beams irradiate on the surface of the dry reagent sheet, a part of the light beams are absorbed, a part of the light beams are diffusely reflected, the diffusely reflected light is received by a photoelectric detector, the temperature of the light sources is controlled by a temperature control device and a temperature sensor, and the temperature drift of the single-color LED light sources is reduced, so that the luminous efficiency of the single-color LED light sources is stable.

But guarantee light source stability with temperature regulating device and temperature sensor, its effect is relatively poor, can't realize stable illumination intensity.

Disclosure of Invention

The application aims to overcome the defects in the prior art and provide an optical system of a dry biochemical analyzer so as to improve the accuracy of a sample concentration test result in a biochemical detection project.

In order to achieve the above purpose, the technical scheme adopted by the embodiment of the application is as follows:

The embodiment of the application provides an optical system of a dry biochemical analyzer, which comprises: the light source feedback unit, the uniform illumination light path and the collection light path; the optical system takes the central normal line of the measured dry reagent sheet as an axis, and the light source feedback unit is vertically arranged relative to the axis of the optical system; the optical axis of the uniform illumination light path coincides with the axis of the optical system; the optical axis of the collecting light path and the axis of the optical system form a first preset angle;

The light source feedback unit is used for controlling a light source with a specified wavelength to emit light beams corresponding to an object to be detected according to the type of the object to be detected; and collecting a feedback beam reflected or refracted by the beam emitted by the light source with the specified wavelength; performing feedback adjustment according to the feedback optical signal value acquired by the feedback light beam and a preset target optical signal value corresponding to the light source with the specified wavelength, so as to adjust the output optical signal value of the light source with the specified wavelength;

The uniform illumination light path is used for dividing and focusing the incident light beam after reflection or refraction of the light beam emitted by the light source with the specified wavelength and converging the incident light beam on the dry reagent sheet to be measured;

The collecting light path is used for collecting light rays reflected by the measured dry reagent sheet and having an included angle with the optical axis of the collecting light path meeting a second preset angle, and obtaining light signals.

Optionally, the light source feedback unit includes: the device 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 sequentially connected;

The data acquisition and conversion module is used for acquiring the feedback optical signal value and converting the feedback optical 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 with the specified wavelength according to the digital signal.

Optionally, the data acquisition and conversion module includes: the system comprises a first light source detector, a stream voltage converter, a gain amplifier and an analog-to-digital converter;

the first light source detector is used for collecting 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 carrying out 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 to indicate the current feedback optical signal value of the light source with the specified wavelength.

Optionally, the control module includes: a controller; the driving module includes: a multi-channel light source current driver;

the controller is used for controlling the multichannel light source current driver to adjust the output light signal value of the light source with the specified wavelength according to the digital signal.

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

Generating a current adjustment instruction of the current value of the light source according to the difference value;

And controlling the multichannel light source current driver to adjust the current value of the light source with the specified wavelength according to the current adjustment instruction so as to enable the output light signal value of the light source with the specified wavelength to reach the preset target light signal value.

Optionally, the data acquisition and conversion module further includes: a low pass filter; one end of the low-pass filter is connected with the stream-voltage converter, and the other end of the low-pass filter is connected with the gain amplifier;

The low-pass filter is used for filtering the voltage signal obtained by the conversion of the current-voltage converter to obtain a filtered voltage signal.

Optionally, the dodging illumination light path includes: fly-eye lens and integral lens; the fly-eye lens comprises a first surface lens and a second surface lens, wherein the first surface lens is a surface far away from the integral lens, and the second surface lens is a surface close to the integral lens;

The first face lens is used for dividing the incident light beam into sub-light beams and focusing the sub-light beams on the second face lens;

The second sub-lens and the integral lens jointly coincide the corresponding sub-beams to the focal plane of the integral lens; the dry reagent sheet to be measured is placed on the focal plane of the integrating lens.

Optionally, the integrating lens is a double-cemented lens, comprising a positive lens and a negative lens, wherein the positive lens is low-dispersion glass; the negative lens is high-dispersion glass.

Optionally, the collecting light path includes: a first lens, an aperture stop, a field stop, a second lens, and a second photodetector; the first lens, the aperture diaphragm, the field diaphragm, the second lens and the second photoelectric detector are sequentially arranged away from the dry reagent sheet to be tested along the optical axis of the collecting light path; the aperture diaphragm is arranged on the image space focal plane of the first lens and is arranged in parallel with the first lens; the field diaphragm is arranged at the image plane of the first lens;

Light rays reflected from the measured dry reagent sheet and having an included angle with the optical axis of the collecting light path meeting a preset angle are focused by the first lens, the focused light beams pass through the aperture diaphragm to reach an image plane, and enter the second lens through the field diaphragm, and are focused on the second photoelectric detector by the second lens.

Optionally, the size of the field diaphragm is determined according to the size of the area to be measured on the dry reagent sheet to be measured and the first preset angle formed by the optical axis of the collecting light path and the axis of the optical system.

Optionally, the optical system further comprises: a transmission device; at least one dry reagent sheet to be tested is arranged on the transmission device; each dry reagent piece to be tested corresponds to each photometric hole one by one;

The transmission device is driven by the motor to transmit so as to be used for switching the current dry reagent sheet to be tested;

The transmission device is used for periodic and cyclic transmission under the control of time sequence so as to finish the switching of each dry measuring reagent sheet in each period.

Optionally, the optical system further comprises: the light source module comprises a monochromatic light source with at least one wavelength; the light source with the specified wavelength is a light source in the light source module.

Optionally, the light source module includes 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 system;

The first light source module comprises a monochromatic light source with at least one wavelength;

The second light source module comprises a monochromatic light source with 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 those of the monochromatic light sources in the second light source module.

Optionally, the optical system further comprises: a spectroscope and a focusing lens; the spectroscope is placed at a third preset angle with the axis of the optical system;

the light beam emitted by the light source with the specified wavelength irradiates on the focusing lens after being refracted or reflected by the spectroscope, and irradiates on the first light source detector after being focused by the focusing lens.

Optionally, the controller is specifically configured to determine, according to the type of the object to be detected, a light source with a specified wavelength corresponding to the object to be detected; and sending 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 with the specified wavelength.

Optionally, the fly-eye lens comprises a first single-sided fly-eye lens and a second single-sided fly-eye lens; the first single-sided fly-eye lens and the second single-sided fly-eye lens are arranged in parallel, and the arrangement interval is the focal length of the sub-lens; the sub-lenses are lens units in the first single-sided fly-eye lens or the second single-sided fly-eye lens.

Optionally, the dodging illumination light path further includes: a glass lens; the glass lens is arranged between the fly-eye lens and the integrating lens, and the glass lens and the axis of the optical system form a fourth preset angle;

The light beam emitted by the light source with the specified wavelength irradiates the fly-eye lens after being refracted or reflected by the spectroscope, and is incident to the glass lens through the fly-eye lens;

the incident light is reflected or refracted through the glass lens, enters the focusing lens, is focused through the focusing lens, and irradiates on the first light source detector.

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;

The third light source module comprises a monochromatic light source with at least one wavelength.

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;

the fourth light source module comprises a monochromatic light source with at least one wavelength.

Optionally, a first part of monochromatic light sources in the light source module are arranged along the axis of the optical system; the second part of monochromatic light sources in the light source module are arranged perpendicular to the axis of the optical system;

the spectroscope is a dichroic mirror, and the number of the dichroic mirrors corresponds to the number of the first part of monochromatic light sources;

each first partial monochromatic light source is aligned in the vertical direction with a corresponding dichroic mirror.

Optionally, the placement position of each monochromatic light source is determined according to the type of the dichroic mirror selected and the wavelength of each monochromatic light source;

the placement position of each dichroic mirror is determined according to the type of the dichroic mirror selected and the cut-off wavelength of each dichroic mirror.

The beneficial effects of the application are as follows:

The application provides an optical system of a dry biochemical analyzer, which can be composed of a light source feedback unit, a uniform illumination light path and a collection light path, and the current of a light source can be fed back and regulated through the light source feedback unit, so that the light intensity output by the light source is stable, the structure is simple, the regulation precision is high, and the stability is high. The multi-channel light source current driver arranged in the light source feedback unit can realize the fast switching control of the monochromatic light sources with different wavelengths. The incident light is subjected to uniform light treatment through the uniform light illumination light path, uniform illumination can be obtained on the dry reagent sheet to be measured, the light path is concise, and a plurality of monochromatic light sources with different wavelengths arranged off-axis can be overlapped and focused at the same position. By setting the collecting light path as a telecentric light path and setting a field diaphragm, the light rays of the whole illuminated surface can be uniformly collected. By adopting the system, the accuracy of the collected reaction light corresponding to the object to be detected can be improved, so that the accuracy of the subsequent analysis result of the object to be detected is improved.

Drawings

In order to more clearly illustrate the technical solutions of the embodiments of the present application, the drawings that are needed in the embodiments will be briefly described below, it being understood that the following drawings only illustrate some embodiments of the present application and therefore should not be considered as limiting the scope, and other related drawings may be obtained according to these drawings without inventive effort for a person skilled in the art.

FIG. 1 is a schematic diagram of a dry reagent tablet according to an embodiment of the present application;

FIG. 2 is a schematic diagram showing light distribution after illumination of a dry reagent sheet according to an embodiment of the present application;

FIG. 3 is a schematic diagram of an optical system of a conventional dry optical analyzer according to an embodiment of the present application;

FIG. 4 is a schematic diagram of an optical system of another conventional dry-type optical analyzer according to an embodiment of the present application;

FIG. 5 is a schematic diagram of an optical system of a dry biochemical analyzer according to an embodiment of the present application;

FIG. 6 is a schematic diagram of an optical system of another dry biochemical analyzer according to an embodiment of the present application;

FIG. 7 is a schematic diagram of an optical system of a dry biochemical analyzer according to an embodiment of the present application;

fig. 8 is a schematic layout diagram of a first light source module according to an embodiment of the present application;

Fig. 9 is a schematic layout diagram of a second light source module according to an embodiment of the present application;

FIG. 10 is a schematic view of an optical path according to an embodiment of the present application;

FIG. 11 is a schematic diagram of a light source switching optical signal according to an embodiment of the present application;

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

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

fig. 14 is a schematic hardware structure diagram of a light source feedback unit according to an embodiment of the present application;

FIG. 15 is a graph showing the comparison of the output optical signal values between PID feedback and non-PID feedback adjustment according to an embodiment of the present application;

FIG. 16 is a graph of the reflection optical density of p-nitrophenol provided by the embodiment of the application;

FIG. 17 is a schematic diagram of an alkaline phosphatase reagent strip according to an embodiment of the present application;

FIG. 18 is a schematic diagram showing a calibration curve corresponding to alkaline phosphatase according to an embodiment of the present application;

FIG. 19 is a schematic diagram of a uniform illumination light path according to an embodiment of the present application;

FIG. 20 is a schematic diagram of a dodging system according to an embodiment of the present application;

FIG. 21 is a schematic diagram of another dodging system provided by an embodiment of the present application;

FIG. 22 is a schematic view of a collecting light path according to an embodiment of the present application;

Fig. 23 is a schematic diagram of a telecentric light path principle according to an embodiment of the present application;

FIG. 24 is a schematic view of a field stop design light path provided by an embodiment of the present application;

FIG. 25 is a schematic view of another embodiment of a light path for uniform illumination;

FIG. 26 is a schematic diagram of another embodiment of a light path for uniform illumination;

fig. 27 is a schematic layout diagram of a light source module according to an embodiment of the application;

FIG. 28 is a schematic layout diagram of another light source module according to an embodiment of the present application;

fig. 29 is a schematic layout diagram of another light source module according to an embodiment of the application.

Detailed Description

For the purpose of making the objects, technical solutions and advantages of the embodiments of the present application more apparent, the technical solutions of the embodiments of the present application will be clearly and completely described with reference to the accompanying drawings in the embodiments of the present application, and it should be understood that the drawings in the present application are for the purpose of illustration and description only and are not intended to limit the scope of the present application. In addition, it should be understood that the schematic drawings are not drawn to scale. A flowchart, as used in this disclosure, illustrates operations implemented according to some embodiments of the present application. It should be understood that the operations of the flow diagrams may be implemented out of order and that steps without logical context may be performed in reverse order or concurrently. Moreover, one or more other operations may be added to or removed from the flow diagrams by those skilled in the art under the direction of the present disclosure.

In addition, the described embodiments are only some, but not all, embodiments of the application. The components of the embodiments of the present application generally described and illustrated in the figures herein may be arranged and designed in a wide variety of different configurations. Thus, the following detailed description of the embodiments of the application, as presented in the figures, is not intended to limit the scope of the application, as claimed, but is merely representative of selected embodiments of the application. All other embodiments, which can be made by a person skilled in the art without making any inventive effort, are intended to be within the scope of the present application.

It should be noted that the term "comprising" will be used in embodiments of the application to indicate the presence of the features stated hereafter, but not to exclude the addition of other features.

First, the relevant background knowledge related to the present application will be briefly described:

A dry biochemical analyzer is an analyzer for clinical chemical examination using a solid-phase carrier reagent, which quantitatively measures the concentration of a specific component in a sample by a reflection optical density method.

The principle of the dry biochemical analyzer is that a body fluid sample (serum, urine, etc.) is added on a dry reagent sheet, and the measured object in the sample and the components of the reagent sheet undergo biochemical reaction, so that the color of the reagent sheet, namely the reflection optical density, is changed. And (3) periodically measuring the reflection optical density of the reagent sheet to a specific wavelength in a fixed reaction time after sample addition, and finally drawing a reaction curve of the sample in the whole reaction time. And calculating a reaction curve to obtain a change value or a change rate of the reflected optical density, and then obtaining the concentration or the biological activity of the object to be detected in the sample according to the calibration curve.

Fig. 1 is a schematic structural diagram of a dry reagent tablet according to an embodiment of the present application. The dry reagent sheet is a multi-layer dry reagent thin layer fabricated on a transparent support substrate as shown in fig. 1. The typical reagent thin layer is a diffusion layer, a filter layer, a reagent layer and a color developing layer in sequence from top to bottom. In detecting a body fluid sample, the temperature of the dry reagent sheet should be always heated and stabilized around 37 ℃ which is the optimal reaction temperature. A certain amount of body fluid sample is dripped on the diffusion layer on the surface of the reagent sheet, the body fluid sample horizontally diffuses into a circular area on the diffusion layer, the contact area of the subsequent body fluid sample and the reagent for biochemical reaction can be increased, and the reaction speed is improved. At the same time, the body fluid sample also permeates down to the filter layer. The body fluid sample is filtered by the filter layer to remove the interfering substances and then permeates downwards to the reagent layer to carry out biochemical reaction with the dry reagent component solidified in the reagent layer. The reaction product absorbs light in a specific spectral range. The reaction product continues to penetrate down to the color-developing layer and becomes immobilized. Finally, a color change of the reagent thin layer can be observed from the transparent support substrate. The extent or rate of color change may reflect the concentration of the test substance. The concentration or biological activity of the analyte in the sample can be determined by measuring the change in color of the dry reagent strip. The subjective visual perception of the color change of the dry reagent sheet can be objectively and quantitatively detected by a method for measuring the reflected optical density of the dry reagent sheet.

Fig. 2 is a schematic diagram of light distribution after illumination of a dry reagent tablet according to an embodiment of the present application. As shown in fig. 2, when light of a certain wavelength is irradiated onto the dry reagent sheet from the bottom up, a part of the light is specularly reflected at the surface of the transparent support substrate, and the part does not reflect the color change of the reagent sheet. The rest of the light enters the color-developing layer through the transparent supporting substrate. Where the light interacts with the microscopic structure and molecules of the color-developing layer and returns to the surface after multiple reflections, refractions, and absorptions. The intensity of the reagent sheet is changed obviously, namely the color change of the reagent sheet is reflected. The direction of the reflected light does not follow the specular direction, but becomes diffuse, and the diffuse direction and intensity follow Lambert (lambertian) radiator law.

Therefore, the color change of the dry reagent sheet can be objectively and quantitatively detected by measuring the change of the reflection optical density of the diffuse reflection light at the bottom of the dry reagent sheet.

The analysis methods commonly used for dry biochemical analyzers are three main types, namely an endpoint method, a fixed time method (two-point method) and a continuous monitoring method (rate method).

Endpoint refers to incubation over a period of time, the entire reaction reaches equilibrium, the concentration of the reactant no longer increases, and the increase or decrease in reflected optical density is directly proportional to the concentration of the analyte.

The fixed time method means that the reaction rate is proportional to the concentration of the reactant in a certain reaction time, the reactant is continuously consumed, the reaction rate is continuously reduced, the optical density is increased or the optical density is reduced slowly, and the reaction needs a longer time to reach the equilibrium, so that the reaction needs to be monitored in a specific time period.

The continuous monitoring method is a method for continuously monitoring the change of the concentration of a certain reaction product along with time in the reaction process of a detected object at equal intervals in the whole incubation process, and solving the reaction speed of the detected object. The optical signal values are collected at equal intervals after the reagent sheet is loaded for testing, and the concentration of the measured object is calculated.

It should be noted that when different items (for example, albumin, alkaline phosphatase, cholesterol, etc.) are tested by using the dry biochemical analyzer, the sample loading amounts and test times corresponding to the different items are different, and the flow of collecting the optical signals by using the optical system provided by the scheme is the same, so that in order to detect a plurality of different items at the same time, the optical system of the dry biochemical analyzer should be capable of detecting the reflection optical densities of a plurality of wavelengths, and the purpose of simultaneously detecting a plurality of reagent sheet reaction curves is satisfied by rapidly switching the wavelengths.

The biochemical detection is to periodically collect optical signal values to calculate the concentration of the measured object, and when the illuminance of the light irradiated on the dry reagent sheet at different moments is inconsistent, the collected optical signal values have errors, so that a reaction curve is abnormal, and the accuracy of an experimental result is affected. The dry biochemical reagent sheet is of a multi-layer film structure, when the sample to be measured is diffused, the diffusion distribution of the sample to be measured is uneven, and when the light irradiated on the surface of the sample is uneven, the measurement stability is affected. The dry biochemical analyzer is used for measuring diffuse reflection light with a fixed angle, so that the light of the whole illuminated surface can be uniformly collected by the collecting light path.

In summary, based on the principle of the dry biochemical analyzer, the dry biochemical analyzer needs to meet the following indexes:

1. According to different detection projects, narrow bandwidth light sources with different wavelengths are arranged;

2. The wavelength can be switched according to different detection items;

3. light sources with different wavelengths are irradiated on the same dry reagent sheet position;

4. the illuminance on the dry reagent sheet needs to be stable;

5. the illuminance irradiated on the surface of the dry reagent sheet needs to be uniformly distributed;

6. the diffuse reflection light of the surface of the dry reagent sheet along a fixed angle is detected, and the light of the whole illuminated surface can be uniformly collected by the collecting light path.

Fig. 3 is a schematic structural diagram of an optical system of a conventional dry optical analyzer according to an embodiment of the present application. Fig. 4 is a schematic structural diagram of another optical system of a conventional dry optical analyzer according to an embodiment of the present application. There are two types of conventional dry optical analyzer optical system configurations.

First, as shown in fig. 3, a single-color LED (LIGHT EMITTING Diode) is used as a light source, multiple 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 with different wavelengths, the light sources emit light beams, the light beams irradiate on the surface of the dry reagent sheet 106 to be tested, a part of the light beams are absorbed, a part of the light beams are 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, so that the temperature drift of the monochromatic LED light source is reduced, and the luminous efficiency of the monochromatic LED light source is stable.

The first conventional dry optical analyzer optical system has the following disadvantages:

1. The temperature control device and the temperature sensor are used for ensuring the stability of the light source, and the stability and the precision of the optical signal value are poor;

2. The illuminance of the light irradiated on the surface of the dry reagent sheet is uneven;

3. the collecting light path cannot uniformly collect the light of the whole illuminated surface.

The second structure is shown in fig. 4, in which the illumination light path uses light with multiple colors as a light source, the seventh light source 301 emits a light beam, the motor drives the filter wheel 302 to rotate, the light is filtered by the filter wheel 302 and then irradiates the dry reagent sheet 106 to be measured, a part of the light is absorbed, a part of the light is diffusely reflected, and the diffusely reflected light is received by the photodetector 208 after being focused by the lens 304.

The second conventional dry optical analyzer optical system has the following disadvantages:

1. halogen tungsten lamp and xenon lamp are used as multiple color light source, the light source has large heat generation, short service life and high maintenance cost;

2. the light source ensures stable output light intensity in a mode of preheating when being started in advance, and has poor light intensity stability and poor precision;

3. The light source with multiple colors is required to be provided with a light filter wheel for light splitting, the light filter wheel is driven by a motor for switching, the mechanical structure is complex, and the spectrum can not be switched rapidly;

4. The illuminance of the light irradiated on the surface of the dry reagent sheet is uneven;

5. the collecting light path cannot uniformly collect the light of the whole illuminated surface.

Based on the defects of the traditional optical system of the dry optical analyzer, the application provides the optical system of the dry biochemical analyzer, the system consists of a light source feedback unit, a uniform illumination light path and a collecting light path, and the light source current of the monochromatic LED can be fed back and regulated through the light source feedback unit, so that the light intensity output by the monochromatic LED is stable, the structure is simple, the regulation precision is high, and the stability is high; and the circuit switch can be used for switching monochromatic LEDs with different wavelengths, and the light sources with different wavelengths are switched without moving parts, so that the switching speed is high and stable. The even illumination light path formed by the fly eye lens and the integral lens is used for processing the incident light, so that even illumination can be obtained on the dry reagent sheet, and the single-color LED illumination light spots with different wavelengths are superposed on the surface of the dry reagent sheet, so that the light path is concise. By designing the collection light path as a telecentric light path, light rays of the entire illuminated surface can be collected uniformly. By adopting the system, the accuracy of the collected reaction light corresponding to the object to be detected can be improved, so that the accuracy of the subsequent analysis result of the object to be detected is improved.

Next, the structure of the optical system of the dry biochemical analyzer and the corresponding method of using the system according to the present application will be described in various embodiments.

FIG. 5 is a schematic diagram of an optical system of a dry biochemical analyzer according to an embodiment of the present application; as shown in fig. 5, the optical system of the dry biochemical analyzer may include: the device comprises a light source feedback unit, a uniform illumination light path and a collection light path.

The light source feedback unit is used for controlling a light source with a specified wavelength corresponding to the object to be detected to emit light beams according to the type of the object to be detected; and collecting a feedback beam reflected or refracted by the beam emitted by the light source with the specified wavelength; and carrying out feedback adjustment according to the feedback optical signal value acquired by the feedback light beam and a preset target optical signal value corresponding to the light source with the specified wavelength so as to adjust the output optical signal value of the light source with the specified wavelength.

In general, the wavelength of the light source is selected to be close to the reflection optical density peak in order to make the linear range of the reaction curve corresponding to the finally produced analyte larger. Therefore, according to the type of the object to be measured, light sources with different wavelengths need to be selected for illumination. Alternatively, the light sources with wavelengths corresponding to different objects to be tested may be determined in advance according to experiments, so that the light source feedback unit may control the light source with a specified wavelength corresponding to the object to be tested to emit a light beam to the dry reagent sheet 106 to be tested according to the type of the current object to be tested.

Table 1 below exemplarily shows wavelengths of detection light sources corresponding to different analytes when concentration analysis is performed by different analysis methods.

TABLE 1

The uniform illumination light path is used for dividing and focusing the incident light beam after reflection or refraction of the light beam emitted by the light source with the specified wavelength and converging the incident light beam on the dry reagent sheet 106 to be measured.

Some of the light beams emitted by the light source with the specified wavelength are reflected or refracted and then are incident into a uniform illumination light path, and the uniform illumination light path can perform uniform illumination treatment on the incident light so as to lead the light spots finally irradiated on the dry reagent sheet to be uniform; and a plurality of monochromatic LED light sources with different wavelengths which are arranged off-axis are overlapped and focused at the same position.

The collecting light path is used for collecting light rays reflected on the measured dry reagent sheet 106, and the included angle between the light rays and the optical axis of the collecting light path meets a second preset angle, and an optical signal is obtained.

When the light beam emitted by the light source with the specified wavelength is subjected to light homogenizing treatment by the light homogenizing illumination light path, the light beam can be irradiated onto the dry reagent sheet 106 to be detected, and is reflected by the dry reagent sheet 106 to be detected, and then the light beam is collected by the collecting light path. The collecting light path can collect the light reflected by the tested dry reagent sheet 106 and forms a designated angle with the optical axis of the collecting light path, and the light signal value is obtained according to the collected light. The collecting optical path in this embodiment may be configured to uniformly collect light of the entire illuminated surface.

In some embodiments, the optical signal values collected by the collection optical path may be sent to an external processing device, for example, to a processor, server, or host computer, etc. that is independent of the present optical system. Thus, the external equipment can calculate the reflected optical density according to the collected optical signal value, so as to draw a reaction curve, obtain the change value or the change rate of the reflected optical density according to the reaction curve, and then correspond to the calibration curve of the object to be measured to obtain the concentration of the object to be measured. The calibration curve of the object to be tested can be generated in advance through experiments.

Of course, the concentration of the analyte based on the analysis of the reaction profile is only one application of the reaction profile. In practical use, the obtained reaction curve is not limited to the analysis of the concentration of the analyte, but can also be used for the analysis of the temperature, pH (Pondus Hydrogenii, pH value), purity and the like of the analyte.

In summary, the optical system of the dry biochemical analyzer provided in this embodiment may be composed of a light source feedback unit, a uniform illumination light path and a collection light path, and the current of the light source may be adjusted by the light source feedback unit, 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 incident light is subjected to uniform light treatment through the uniform light illumination light path, uniform illumination can be obtained on the dry reagent sheet to be measured, and the light path is concise. Through the collecting light path, the light of the whole illuminated surface can be uniformly collected. By adopting the system, the accuracy of the collected reaction light corresponding to the object to be detected can be improved, so that the accuracy of the subsequent analysis result of the object to be detected is improved.

FIG. 6 is a schematic diagram of an optical system of another dry biochemical analyzer according to an embodiment of the present application; as shown in fig. 6, the optical system takes the center normal line of the dry reagent sheet 106 to be measured as an axis, and the light source feedback unit is vertically arranged relative to the axis of the optical system; the optical axis of the uniform illumination light path coincides with the axis of the optical system; the optical axis of the collection light path forms a first preset angle with the axis of the system.

Optionally, the light source feedback unit includes: a data acquisition and conversion module 144, a control module 145, and a drive module 146; the data acquisition and conversion module 144, the control module 145 and the driving module 146 are sequentially connected. The data acquisition and conversion module 144 is configured to acquire a feedback optical signal value, and perform conversion processing on the feedback optical signal value to obtain a digital signal; the control module 145 is used for controlling the driving module 146 to adjust the value of the output light signal of the light source with the specified wavelength according to the digital signal.

The data acquisition and conversion module 144 may receive the feedback light beam reflected or refracted by the light beam emitted by the light source, acquire a feedback optical signal value according to the feedback light beam, and perform a series of conversion processes on the feedback optical signal value to obtain a digital signal.

The control module 145 employs a feedback adjustment algorithm based on the digital signal to control the drive module 146 to adjust the value of the output optical signal of the light source at the specified wavelength.

FIG. 7 is a schematic diagram of an optical system of a dry biochemical analyzer according to an embodiment of the present application; as will be appreciated in conjunction with fig. 6 and 7, the data acquisition and conversion module 144 includes: a first light source detector 108, a stream-to-voltage converter 114, a gain amplifier 116, an analog-to-digital converter 117. The control module 145 includes: a controller 118; the driving module 146 includes: a multi-channel light source current driver 119.

The first light source detector 108 is configured to collect a 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; the current-to-voltage converter 114 is used for converting the current signal into a voltage signal; the gain amplifier 116 is configured to perform signal amplification processing on the voltage signal, so as 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 (AD value, i.e., a value obtained by converting an analog quantity into a digital quantity); the digital signal is used to indicate the current feedback optical signal value for the light source at the specified wavelength.

The controller 118 is configured to control the multichannel light source current driver 119 to adjust the value of the output light signal of the light source at the specified wavelength based on the digital signal.

In some embodiments, the gain amplifier 116 may be an adjustable gain amplifier, the controller 118 may be an MCU (Microcontroller Unit, micro control unit), and the device may be flexibly selected in practical applications, so as to achieve a desired function.

As shown in fig. 7, a part of the feedback light beam emitted by the light source with the specified wavelength enters the light source feedback unit after refraction or reflection, the feedback light signal value is acquired by the first light source detector 108, the feedback light signal is converted into a current signal according to the feedback light beam, the current signal is converted into a voltage signal by the current-voltage converter 114, the voltage signal is amplified by the gain amplifier 116, the analog signal is converted into a digital signal by the analog-to-digital converter 117 and transmitted to the controller 118, and the multichannel light source current driver 119 is controlled by the controller 118 to adjust the current value of the light source with the specified wavelength so as to adjust the intensity of the light signal output by the light source with the specified wavelength, so that the light intensity stability output by the light source with the specified wavelength is higher.

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

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 includes a monochromatic light source of at least one wavelength; the second light source module 102 includes a monochromatic light source with at least one 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.

Fig. 8 is a layout diagram of a first light source module according to an embodiment of the application. Fig. 9 is a layout diagram of a second light source module according to an embodiment of the application. In this scheme, the light source of each wavelength can adopt monochromatic LED light source. As shown in fig. 8, the first light source module 101 may be provided with 4 single-color LEDs, and the 4 single-color LEDs are symmetrically distributed along the central axis. As shown in fig. 9, the second light source module 102 is provided with 3 single-color LEDs, and the 3 single-color LEDs have two distribution forms. As shown in fig. 9 (a), 3 single-color LEDs are symmetrically distributed. As shown in fig. 9 (b), the distribution form of each single-color LED light source in the second light source module 102 is identical to that of each single-color LED light source in the first light source module 101, and 1 LED placement bit is left, and the placement of the left LED placement bit can be any one of 4 LED placement bits.

The first light source module 101 and the second light source module 102 are provided with seven monochromatic LED light sources with different wavelengths, and the controller 118 in the light source feedback unit can control the multichannel light source current driver 119 to realize the switching of the monochromatic LEDs with different wavelengths.

In some embodiments, the first light source module 101 and the second light source module 102 may be used interchangeably, and the number of monochromatic light sources in the first light source module 101 is not limited to 3, and the number of monochromatic light sources in the second light source module 102 is not limited to 4. The light source module is not limited to the first light source module 101 and the second light source module 102, but may include only one module.

Optionally, referring to fig. 7, the optical system of the dry biochemical analyzer may further include: a beam splitter 103 and a focusing lens 107; the spectroscope 103 is placed at a third preset angle with the axis of the optical system of the dry biochemical analyzer; the third preset angle here may be 45 °. The light beam emitted from the light source of the specified wavelength is refracted or reflected by the beam splitter 103 and then irradiated onto the focusing lens 107, and is focused by the focusing lens 107 and then irradiated onto the first light source detector 108.

Fig. 10 is a schematic diagram of an optical path provided by an embodiment of the present application, as shown in fig. 10, a light beam emitted by a first light source module 101 irradiates onto a beam splitter 103, irradiates onto a focusing lens 107 after being reflected by the beam splitter 103, irradiates onto a first photodetector 108 after being focused by the focusing lens 107.

The light beam emitted by the second light source module 102 irradiates on the spectroscope 103, irradiates on the focusing lens 107 after being refracted by the spectroscope 103, irradiates on the first photoelectric detector 108 after being focused by the focusing lens 107.

In some embodiments, the optical system of the dry biochemical analyzer uses a single-color LED as a light source, the spectrum range of the single-color LED is narrow, no optical filter is required to be arranged for light splitting, the single-color LED with different wavelengths is selected to illuminate the dry reagent sheet 106 according to the characteristics of the object to be tested and the detection method used, in the implementation method, a plurality of objects to be tested such as albumin, alkaline phosphatase and the like can be tested, 7 test wavelengths are set to be 365nm, 400nm, 460nm, 540nm, 600nm, 630nm and 680nm respectively, and the wavelength of the current single-color LED is not limited to this and the number is not limited to 7.

The single-color LED is used as a light source, a single driving chip is used in combination with a single-color LED driving circuit design, a plurality of single-color LED light sources are controlled to be rapidly switched through a multi-path analog switch, and the current and the gain of each wavelength single-color LED can be independently controlled. The monochromatic LED light source only emits light when the light-measuring surface reaches the illumination position, so that the service life of the monochromatic LED is prolonged.

The controller 118 can determine the monochromatic LED light source with the specified wavelength corresponding to the object to be tested according to the type of the current object to be tested, so as to control the multi-channel light source current driver 119 to switch on the monochromatic LED light source with the specified wavelength, so as to control the monochromatic LED light source with the specified wavelength to illuminate the dry reagent sheet 106 to be tested, thereby realizing concentration test analysis of the object to be tested.

Fig. 11 is a schematic diagram of a light source switching optical signal according to an embodiment of the present application. As shown in fig. 11, the light signal diagram of 7 single-color LEDs switched on and off sequentially, wherein the rising edge is the LED-on process, the falling edge is the LED-off process, the time for turning on and off the LEDs is in the order of ms, and the LEDs can be quickly stabilized within 3ms after being turned on.

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

Fig. 12 is a schematic diagram of a first light source module according to an embodiment of the application after being split by a beam splitter. As shown in fig. 12, the first light source module 101 irradiates on the focusing lens 107 after being reflected by the beam splitter 103, irradiates on the first photodetector 108 after being focused by the focusing lens 107. The first light source module 101 is refracted by the spectroscope 103 and enters a uniform illumination light path.

Fig. 13 is a schematic diagram of a second light source module according to an embodiment of the application after being split by a beam splitter. As shown in fig. 13, the light source emitted from the first light source module 101 is refracted by the beam splitter 103, irradiates on the focusing lens 107, 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 spectroscope 103 and enters the uniform illumination light path.

The light beam combining of different wavelengths and the light beam splitting function of a single wavelength can be realized by using one mirror. The light source is not limited to be placed on two sides of the beam splitter 103 in the present application, and the light source may be placed on one side of the beam splitter 103. The beam splitter 103 may be a prism, a dichroic mirror, a common plate glass, or the like, but is not limited thereto.

Optionally, with continued reference to fig. 7, the data acquisition and conversion module 144 may further include: a low pass filter 115; one end of the low-pass filter 115 is connected to the current-voltage converter 114, and the other end of the low-pass filter 115 is connected to the gain amplifier 116; the low-pass filter 115 is used for filtering the voltage signal converted by the dc-to-ac converter 114 to obtain a filtered voltage signal.

Optionally, the controller 118 is specifically configured to determine a difference between the current feedback optical signal value and the target optical signal value according to the current feedback optical signal value of the light source with the specified wavelength and the target optical signal value corresponding to the light source with the specified wavelength; generating a current adjustment instruction of the current value of the light source according to the difference value; according to the current adjustment instruction, the multichannel light source current driver 119 is controlled to adjust the current value of the light source of the specified wavelength so that the output light signal value of the light source of the specified wavelength reaches the target light signal value.

In some embodiments, the light source feedback unit may use a PID (Proportional-Integral-Derivative) adjustment algorithm to feedback and adjust the current of the monochromatic LED light source, and at any moment, keep the stable output of the light intensity of the monochromatic LED, and have a simple structure, high adjustment accuracy and high stability.

Fig. 14 is a schematic hardware structure diagram of a light source feedback unit according to an embodiment of the present application. The monochromatic LED light source emits a light beam, which irradiates the beam splitter 103, the beam splitter 103 splits the irradiation light into two beams, one beam irradiates the dodging light path as an output light beam, and the other beam irradiates the light source feedback unit as a feedback light beam. The feedback light beam irradiates on the first photoelectric detector 108 after being focused by the focusing lens 107, the first photoelectric detector 108 collects a feedback light signal value, the light signal is converted into a current signal, the current signal is converted into a voltage signal by the current-voltage converter 114, the voltage signal is filtered by the low-pass filter 115, the signal is amplified by the gain amplifier 116, the analog signal is converted into a digital signal by the analog-digital converter 117 and is transmitted to the controller 118, the multichannel power supply current driver 119 is controlled by the controller 118, and the feedback is independently controlled to regulate the seven-wavelength monochromatic LED current.

Wherein the low pass filter 115 may be an active low pass filter. The first photodetector 108 may be a photodiode, photomultiplier tube, avalanche photodiode, silicon photomultiplier tube, or the like.

Alternatively, the PID feedback process is generally as follows: the controller 118 selects a single-color LED wavelength according to the type of the object to be detected, sets an initial current value of the wavelength, sets a gain value of the wavelength, sets a target light 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 light signal value as a feedback light signal value and sends the feedback light signal value to the controller 118, the controller 118 compares the feedback light signal value with a preset target light signal value, and utilizes a PID control algorithm to adjust and control the multi-channel light source current driver 119 so as to modify the current value required by controlling the single-color LED, thereby controlling the intensity of the output light signal value of the single-color LED. The PID control algorithm adjusts the current value through proportional, integral and differential control, respectively, according to the deviation, accumulated deviation and rate of change of the optical signal value. By closed-loop control of the monochromatic LED current, the optical signal value is enabled to be converged to the target value stably, and accurate control of the optical signal value is achieved.

FIG. 15 is a graph showing the comparison of the output optical signal values between PID feedback and non-PID feedback adjustment according to an embodiment of the present application. As shown in fig. 15, the abscissa is time, the ordinate is the collected optical signal value, PID feedback adjustment is performed, and the optical signal value has reached stability within 3 ms; and PID feedback is not performed, and as the lamp is turned on, the light signal value of the monochromatic LED is in a descending trend due to self-heating.

It is worth noting that feedback adjustment based on PID feedback may be continuously performed to continuously converge the optical signal value of the single color LED output to the target optical signal value.

Optionally, the optical system of the dry biochemical analyzer may further include: a transmission (not shown); at least one dry reagent sheet to be tested is arranged on a transmission device; each dry reagent piece to be tested corresponds to each photometric hole one by one; the transmission device is driven by the motor to transmit so as to be used for switching the current dry reagent sheet to be tested; the transmission device is used for periodic and cyclic transmission under the control of time sequence so as to finish the switching of each dry measuring reagent sheet in each period.

In one implementation manner, the optical system of the dry biochemical analyzer provided by the scheme can be used for detecting the concentration of a plurality of different objects to be detected. Reagent pieces corresponding to different objects to be tested are placed on a mechanical transmission device, the reagent pieces are in one-to-one correspondence with the light measuring holes, the mechanical transmission device is positioned above an optical system of the dry biochemical analyzer, the mechanical transmission device is driven by a motor to transmit, and a plurality of reagent pieces can realize periodic test of light signals in fixed reaction time. In the light measurement process, the mechanical transmission device transmits at a constant speed, a driving chip is used, a plurality of monochromatic LED light sources are controlled to be switched rapidly through a multipath analog switch, monochromatic LEDs with corresponding wavelengths of the hole site reagent pieces are only turned on when a light measurement hole is about to reach an illumination area, the hole site reagent pieces are turned off when the light measurement hole leaves the illumination area, and the mechanical transmission device transmits a period to complete the test of light signals of all the reagent pieces in one light measurement period. Through time sequence control, the test of optical signals of different objects to be tested in the whole reaction period can be completed by circulating for a plurality of times. And calculating the reflection optical density according to the optical signal value, so as to draw response curves corresponding to different objects to be detected, obtaining the change value or the change rate of the reflection optical density through the response curves, and finally obtaining the concentration of the objects to be detected according to calibration curves corresponding to different objects to be detected.

Taking an object to be measured as an alkaline phosphatase as an example, a test of the concentration of the object to be measured is described.

The alkaline phosphatase reagent tablet is mainly used for quantitative analysis of alkaline phosphatase activity in human serum or blood plasma. The sample is added on the reagent sheet, passes through the diffusion layer and the filter layer, then enters the reagent layer, the reagent layer contains p-nitrophenyl phosphate substrate and other components required by the reaction, alkaline phosphatase in the sample catalyzes the hydrolysis of p-nitrophenyl phosphate into p-nitrophenol and phosphoric acid under alkaline condition (pH value is 10.5), and the p-nitrophenol diffuses to the color development layer, and is monitored by a reflectometry method.

FIG. 16 is a graph of the reflection optical density of p-nitrophenol according to an embodiment of the present application. As shown in FIG. 16, the reflection optical density spectrum of p-nitrophenol is shown in FIG. 16, the reflection optical density of p-nitrophenol is highest at 400nm, and the reflection optical density is almost zero at 480-700 nm.

FIG. 17 is a schematic diagram showing the reaction of an alkaline phosphatase reagent tablet according to an embodiment of the present application. As shown in fig. 17, after the alkaline phosphatase reagent sheet is applied, the reaction curve of the reaction optical density is periodically tested in a fixed reaction time by using a single-color LED light source with a center wavelength of 400nm, wherein the abscissa is the reaction time, and the ordinate is the reflection optical density, the reflection optical density of p-nitrophenol after the application of the sample for a period of time is linearly changed with time, and the analysis is performed by using a continuous monitoring method, and the optical density intensity of the p-nitrophenol is directly proportional to the alkaline phosphatase activity, and the activity of the alkaline phosphatase in the sample is calculated by continuously monitoring the change rate of the optical density of the p-nitrophenol.

It should be noted that the reflected optical density in fig. 16 and 17 is a logarithmic value of reflectance.

FIG. 18 is a schematic diagram showing a calibration curve corresponding to alkaline phosphatase according to an embodiment of the present application. And adding alkaline phosphatase sample with known concentration on the dry reagent sheet, obtaining the change rate of the reflected optical density according to the reaction curve, and obtaining the calibration curve of the alkaline phosphatase by taking the change rate of the reflected optical density as an ordinate and the sample concentration as an abscissa.

In the sample concentration test analysis, the change rate of the reflected optical density of the alkaline phosphatase can be obtained based on the plotted response curve corresponding to the alkaline phosphatase. Thus, the concentration corresponding to the change rate of the reflected optical density of alkaline phosphatase can be determined as the concentration of alkaline phosphatase to be measured by comparing the calibration curve of alkaline phosphatase.

Fig. 19 is a schematic diagram of a uniform illumination light path according to an embodiment of the present application. Alternatively, as shown in fig. 19, the dodging illumination light path may include:

Fly-eye lens 104 and integrator lens 105; the fly-eye lens 104 includes a first sub-lens which is a surface away from the integrator lens 105, and a second sub-lens which is a surface close to the integrator lens 105.

The first sub-lens is used for dividing an incident light beam into sub-beams and focusing the sub-beams on the second sub-lens.

The second sub-lens and the integral lens 105 together coincide the corresponding sub-beams onto the focal plane of the integral lens 105; the dry reagent sheet 106 to be measured is placed on the focal plane of the integrator lens 105.

Referring to fig. 19, the light emitted from the first light source module 101 is refracted by the beam splitter 103 and then irradiated onto the fly eye lens 104 of the uniform illumination light path. The light emitted by the second light source module 102 is reflected by the beam splitter 103 and then irradiates on the fly eye lens 104.

The surface of the fly-eye lens 104 close to the beam splitter 103 is called a first sub-lens, the surface of the fly-eye lens 104 close to the integrating lens 105 is called a second sub-lens, the first sub-lens of the fly-eye lens 104 divides an incident light beam into sub-light beams and focuses the sub-light beams on a second sub-lens array, the second sub-lens and the integrating lens 105 jointly overlap the corresponding sub-light beams on the focal plane of the integrating lens 105, and the measured dry reagent sheet 106 is placed on the focal plane of the integrating lens 105.

Fig. 20 is a schematic diagram of a dodging system according to an embodiment of the present application. As shown in fig. 20, the first sub-lens of the first row splits the incident beam into sub-beams and focuses the sub-beams onto the second sub-lens array of the second row, which together with the integrator lens 105 coincide the corresponding sub-beams on the focal plane of the integrator 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 beam of the light source into a plurality of beamlets, the non-uniformity across each beamlet will be smoothed during the coincidence process to obtain uniform illumination.

Alternatively, the integrating lens 105 is preferably a double cemented lens including a positive lens and a negative lens, the positive lens being a low-dispersion glass; the negative lens is a high-dispersion glass. Of course, it may be a plano-convex lens, a biconvex lens, an aspherical lens, or the like.

In the present embodiment, the integrator lens 105 is a double-cemented lens, which uses low-dispersion glass and high-dispersion glass, and adopts a positive-negative structure, and the positive lens is low-dispersion glass with a small refractive index; the negative lens is high-dispersion glass, the refractive index is larger, and the two lenses are glued, and the refractive characteristics are utilized to compensate each other, so that astigmatism and coma are eliminated. The off-axis light beam passing through the fly-eye lens 104 is converged on the back focal plane of the integrating lens 105, and a light spot with sharp edge and uniform brightness is formed.

The shape of the light spot may 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, rectangular, circular, hexagonal, etc.

Fig. 21 is a schematic diagram of another dodging system according to an embodiment of the present application. As can be seen from fig. 21, the multiple light sources are designed off-axis, and the combined mode of the fly-eye lens 104 and the integrator lens 105 is used, so that the projections can be focused on the same position in a superposition way no matter whether the center of the light source is on the central optical axis of the uniform illumination light path.

With reference to fig. 20 and 21, the geometric relationship of light propagation within fly-eye lens 104 can be obtained:

The maximum exit aperture angle of the fly-eye sub-lens (here, the sub-lens means one sub-lens unit of the first sub-lens or the second sub-lens, each of which is composed of a plurality of sub-lenses) is determined by the target illumination surface size and the focal length of the integrator lens 105, and it is possible to obtain:

The light beam split by fly eye lens 104 is a beamlets, and thus can be approximated as:

According to the refractive index formula: The method can obtain: /(I) 。

So that the focal length of fly-eye lens 104 can be calculated。

Based on the radius of curvature of the sub-lens and the focal length of the fly-eye lens 104Functional relationship between: /(I)

The radius of curvature of the available sub-lenses is:

Wherein:

The fly-eye lens 104 has a neutron lens length of ；

The illuminated area is of length；

The focal length of the sub-lens is；

The focal length of the integrator lens 105 is；

The fly-eye lens 104 has a refractive index n;

The back surface incidence angle of fly-eye lens 104 is ω;

The refractive angle of the back surface of fly-eye lens 104 is ω';

the calculation of the optical system parameters may be performed according to the above formula.

In the present embodiment, the spot irradiated on the dry reagent sheet 106 to be measured is designed to be 8.4X8.4 mm, the integrator lens 105 is selected to have a focal length of 40mm, and the fly-eye sub-lens is set to have a size of 6mm according to the area diameter of the light source irradiated on the fly-eye lens 104Mm, fly-eye lens 104 has a refractive index of 1.5, according to formula/>Availability/>The focal length of the sub-lens of the fly-eye lens 104 is obtained as/>According to the calculation formula/>, based on the curvature radius of the plano-convex lensWherein/>R ₁ is the radius of curvature of the sub-lens, which is the focal length of the sub-lens.

I.e.The radius of curvature of the sub-lenses was found to be 2.96mm.

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

Fig. 22 is a schematic diagram of a collecting light path according to an embodiment of the present application. As shown in fig. 22, the collection optical path may be disposed at an angle θ to the axis of the optical system of the dry biochemical analyzer.

The light beam after the light homogenizing treatment through the light homogenizing illumination light path irradiates on the surface of the dry reagent sheet 106 to be measured, a part of the light beam is absorbed by the dry reagent sheet 106 to be measured, a part of the light beam is subjected to diffuse reflection, the diffuse reflection light direction is random, the collecting light path is arranged in the direction of an included angle theta with the irradiation light path, the diffuse reflection light enters the collecting light path, the light beam is focused through the first lens 109, the focused light beam passes through the aperture diaphragm 110, the aperture diaphragm 110 is arranged on the image space focal plane of the first lens 109, the aperture diaphragm 110 is placed in parallel with the first lens 109, the light beam passing through the aperture diaphragm 110 reaches the image surface, a view field diaphragm 111 is arranged at the image surface, the view field diaphragm 111 is used for limiting the detection range on the surface of the dry reagent sheet 106 to be measured, and the light beam passing through the view field diaphragm 111 is incident on the second lens 112 and is focused on the second photodetector 113 through the second lens 112.

In this embodiment, the collection optical path forms an angle θ with the axis of the optical system of the dry biochemical analyzer, and the angle θ may be 45 °, but is not limited thereto.

Fig. 23 is a schematic diagram of a telecentric light path principle according to an embodiment of the present application. As shown in fig. 23, the aperture stop 110 is disposed on the focal plane of the image side of the first lens 109 to form an object-side telecentric optical path, and the aperture stop 110 can select a detection beam, and only a very thin beam of light, in which the principal ray emitted from the dry reagent sheet 106 is parallel to the optical axis, can enter the collecting optical path, so that the collecting optical path can uniformly collect the light of the entire illuminated surface of the dry reagent sheet 106. When the position of the measured dry reagent sheet 106 is deviated, the principal rays still coincide, and the projection center points of the principal rays are the same, so that the test error caused by the position deviation of the surface to be measured is reduced.

Fig. 24 is a schematic view of a field stop design light path according to an embodiment of the present application. The optical axis of the collecting optical path and the normal line of the center of the measured dry reagent sheet 106 are arranged at an angle theta, so that the included angle theta between the principal ray of the measured dry reagent sheet 106 and the direction orthogonal to the optical axis of the collecting optical path is the angle theta. Since the light collected by the collecting light path is diffuse reflection light, the angle θ is preferably 30 ° to 60 °, but is not limited thereto.

It should be noted that, the aperture stop 110 is disposed on the focal plane of the first lens 109 in the image side, and is used to control an aperture angle u (an angle shown in fig. 23, where the aperture angle u refers to the second preset angle described above) for receiving the diffuse reflected light of the dry reagent sheet 106. The diameter of the aperture stop 110 isWhere f ₃ is the focal length of the first lens 109.

In the present embodiment, the focal length of the first lens 109 is 15mm, the aperture angle u is 5 °, and the diameter of the aperture stop 110 ismm。

Optionally, the size of the field stop 111 is determined according to the size of the area to be measured on the dry reagent sheet 106 and a first preset angle formed between the optical axis of the collecting light path and the axis of the optical system.

Referring to FIG. 24, in some embodiments, a field stop 111 is disposed on the image plane of the first lens 109 for limiting the detection range on the surface of the dry reagent sheet 106 to be detected, the field stop 111 forming an angle with the direction orthogonal to the optical axis of the collecting light pathAnd (5) setting.

When the dry reagent sheet 106 is tilted with respect to the optical axis of the collecting optical path, the image of the dry reagent sheet 106 formed by the first lens 109 is also tilted with respect to the optical axis of the collecting optical path, and the process of calculating the image plane tilt angle is as follows:

Vertical axis magnification

Axial magnification

Then:

Wherein, the included angle between the measured dry reagent sheet 106 and the orthogonal direction of the optical axis of the collecting light path is ；

The included angle between the field diaphragm 111 and the orthogonal direction of the optical axis of the collecting light path is；/>

The half height of the measured dry reagent sheet 106 perpendicular to the optical axis of the collecting light path is；

The half height of the measured dry reagent sheet 106 parallel to the optical axis of the collecting light path is；

The half height of the imaging perpendicular to the optical axis of the collecting light path is；

The half height of the imaging parallel to the optical axis of the collecting light path is。

The circular inclined dry reagent sheet 106 is imaged by the first lens 109, and the image is elliptical, and the vertical axis magnification of the major axis of the ellipse isThe vertical axis magnification of the short axis is/>。

In the present embodiment of the present invention,The radius of the detection area of the dry reagent sheet 106 to be detected is 3mm, and the vertical axis magnification/>, after the dry reagent sheet 106 to be detected is imaged by the first lens 109, is designedIs-0.5 times, can be obtained:

elliptical image has a major axis ratio and a minor axis ratio of about I.e. the major axis of the ellipse is 3mm and the minor axis is 2.37mm.

The ellipse of the field stop 111 with an inclination angle of 26.56 °, a major axis of 3mm and a minor axis of 2.37mm can be determined.

Through the above calculation process, the size of the detection area of the dry reagent sheet 106 can be calculated according to the known size of the field stop 111; the size of the field stop 111 to be set can also be calculated according to the size of the detection area of the known dry reagent sheet 106 to be detected.

Optionally, the controller 118 is specifically configured to determine, according to the type of the object to be detected, a light source with a specified wavelength corresponding to the object to be detected; and sends control instructions 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.

As can be seen from table 1, the detection wavelengths corresponding to different analytes under different analysis methods are different, and the light source with the specified wavelength corresponding to the analyte can be determined according to the type of the analyte and the analysis method adopted.

For example, when the concentration of the object to be detected is analyzed by the continuous monitoring method, the light source with the specified wavelength corresponding to the object to be detected is determined to be 400nm, and then the controller 118 may send a control instruction to the multi-channel light source current driver 119 according to the determined light source with the specified wavelength, so as to control the multi-channel light source current driver 119 to switch the light source, so that the monochromatic light source with the wavelength of 400nm is turned on currently.

Optionally, the detection of a plurality of different biochemical items can be achieved based on the optical system of the dry biochemical analyzer provided in the above embodiments. Reagent sheets of different biochemical items are placed on a mechanical transmission device, the reagent sheets are in one-to-one correspondence with the photometric holes, the mechanical transmission device is positioned above an optical system of the dry biochemical analyzer, the mechanical transmission device is driven by a motor to transmit, and a plurality of reagent sheets can realize periodic test of optical signals in fixed reaction time. In the light measurement process, the mechanical transmission device transmits at a constant speed, a driving chip is used, a plurality of monochromatic LED light sources are controlled to be switched rapidly through a multipath analog switch, monochromatic LEDs with corresponding wavelengths of the hole site reagent pieces are only turned on when a light measurement hole is about to reach an illumination area, the hole site reagent pieces are turned off when the light measurement hole leaves the illumination area, and the mechanical transmission device transmits a period to complete the test of light signals of all the reagent pieces in one light measurement period. Through time sequence control, the optical signals of different biochemical detection items can be tested in the whole reaction period by circulating for a plurality of times. Calculating the reflection optical density of different biochemical detection items according to the optical signal values of the different biochemical detection items in the whole reaction period, drawing reaction curves of the different biochemical detection items, obtaining the change value or the change rate of the reflection optical density of the different biochemical detection items through the reaction curves of the different biochemical detection items, and finally obtaining the concentration of the to-be-detected object in the samples of the different biochemical detection items according to the calibration curves corresponding to the different biochemical detection items.

Some alternatives to the present solution are described below:

fig. 25 is a schematic diagram of another uniform illumination light path according to an embodiment of the present application. Alternatively, in the present embodiment, the fly-eye lens 104 includes a first single-sided fly-eye lens 104-1 and a second single-sided fly-eye lens 104-2; the first single-sided fly-eye lens 104-1 and the second single-sided fly-eye lens 104-2 are placed in parallel with a placement interval being the focal length of the sub-lens; wherein the sub-lenses are lens units in the first single-sided fly-eye lens 104-1 or the second single-sided fly-eye lens 104-2.

As shown in fig. 25, the light beam emitted from the first light source module 101 irradiates the beam splitter 103, irradiates the focusing lens 107 after being reflected by the beam splitter 103, irradiates the first photodetector 108 after being focused by the focusing lens 107. The light beam emitted by the second light source module 102 irradiates on the spectroscope 103, irradiates on the focusing lens 107 after being refracted by the spectroscope 103, irradiates on the first photoelectric detector 108 after being focused by the focusing lens 107.

The light emitted from the first light source module 101 is refracted by the beam splitter 103 and then irradiated onto the first single-sided fly-eye lens 104-1. The light emitted from the second light source module 102 is reflected by the beam splitter 103 and then irradiates the first single-sided fly-eye lens 104-1. The sub-lenses of the first single-sided fly-eye lens 104-1 divide the incident beam into sub-beams and focus the sub-beams on the second single-sided fly-eye lens 104-2 array, the first single-sided fly-eye lens 104-1 and the second single-sided fly-eye lens 104-2 are symmetrically arranged in parallel, the sub-lenses in the second single-sided fly-eye lens 104-2 and the integral lens 105 together overlap the corresponding sub-beams on the focal plane of the integral lens 105, and the dry reagent sheet 106 to be measured is placed on the focal plane of the integral lens 105. The multiple light sources are off-axis, and the projection of the multiple light sources is overlapped and focused on the same position by using a combined mode of the fly-eye lens 104 and the integrating lens 105.

Fig. 26 is a schematic diagram of another uniform illumination light path according to an embodiment of the present application.

Optionally, the dodging illumination light path may further include: a glass lens 135; the glass lens 135 is arranged between the fly-eye lens 104 and the integrating lens 105, and the glass lens 135 forms a fourth preset angle with the axis of the optical system; the light beam emitted from the light source of the specified wavelength is refracted or reflected by the spectroscope 103, irradiated in the fly eye lens 104, and is incident to the glass lens 135 via the fly eye lens 104; incident light is reflected or refracted by the glass lens 135, enters the focusing lens 107, is focused by the focusing lens 107, and is irradiated on the first light source detector 108.

In this embodiment, beam splitter 103 may be replaced with a dichroic mirror, with the addition of glass lens 135. As shown in fig. 26, the first light source module 101 emits a light beam to irradiate onto the beam splitter 103, the light beam is refracted by the beam splitter 103 and then is incident on the fly eye lens 104, the second light source module 102 emits a light beam to irradiate onto the beam splitter 103, the light beam is reflected by the beam splitter 103 and then is incident on the fly eye lens 104, the first lens of the fly eye lens 104 divides the incident light beam into sub-light beams and focuses the sub-light beams on the second lens array, the light beam passing through the second lens irradiates on the glass lens 135, a part of the light beam is reflected by the glass lens 135 and enters the light source feedback unit, and the light beam is focused by the focusing lens 107 and then irradiates on the first photodetector 108. A part of light rays enter the integrating lens 105 after being refracted by the glass lens 135, are focused by the integrating lens 105 and then irradiate on the dry reagent sheet 106 to be measured, and the dry reagent sheet 106 to be measured is placed on the focal plane of the integrating lens 105.

The multiple light sources are off-axis, and the projection of the multiple light sources is overlapped and focused on the same position by using a combined mode of the fly-eye lens 104 and the integrating lens 105.

Fig. 27 is a schematic layout diagram of a light source module according to an embodiment of the application. Optionally, in the present embodiment, the light source module includes a third light source module 120; the third light source module 120 is disposed along an axis perpendicular to the optical system; the third light source module 120 includes a monochromatic light source of at least one wavelength.

In this embodiment, the third light source module 120 is used to replace the previous first light source module 101 and second light source module 102. As shown in fig. 27, the third light source module 120 is disposed along the optical axis of the light source feedback unit. The third light source module 120 is composed of seven wavelength monochromatic LED light sources. The light beam emitted by the third light source module 120 irradiates on the spectroscope 103, irradiates on the focusing lens 107 after being refracted by the spectroscope 103, irradiates on the first photodetector 108 after being focused by the focusing lens 107.

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

Fig. 28 is a schematic layout diagram of another light source module according to an embodiment of the application. Optionally, in this embodiment, the light source module includes a fourth light source module 140; the fourth light source module 140 is disposed along the axis of the optical system; the fourth light source module 140 includes a monochromatic light source of at least one wavelength.

In this embodiment, the fourth light source module 140 is used to replace the previous first light source module 101 and second light source module 102, which is different from the arrangement of fig. 27, and in fig. 28, the fourth light source module 140 is arranged along the optical axis of the uniform illumination light path.

The fourth light source module 140 is composed of seven wavelength monochromatic LED light sources. The light beam emitted by the fourth light source module 140 irradiates on the beam splitter 103, irradiates on the focusing lens 107 after being reflected by the beam splitter 103, irradiates on the first photodetector 108 after being focused by the focusing lens 107.

The light emitted by the fourth light source module 140 is refracted by the spectroscope 103 and then irradiates on the fly eye lens 104 of the uniform light illumination light path. The first sub-lens of the fly-eye lens 104 divides the incident beam into sub-beams and focuses the sub-beams on the second sub-lens array, the sub-lenses in the second sub-lens and the integrator lens 105 together overlap the corresponding sub-beams on the focal plane of the integrator lens 105, and the dry reagent sheet 106 to be measured is placed on the focal plane of the integrator lens 105.

Fig. 29 is a schematic layout diagram of another light source module according to an embodiment of the application. Alternatively, in this embodiment, the monochromatic light sources of the wavelengths in the light source module are disposed independently. Wherein, the first part of monochromatic light sources in the light source module are arranged along the axis of the optical system; the second part of monochromatic light sources in the light source module are arranged perpendicular to the axis of the optical system; the spectroscope is a dichroic mirror, and the number of the dichroic mirrors corresponds to the number of the first part of monochromatic light sources. Each first partial monochromatic light source is aligned in the vertical direction with a corresponding dichroic mirror.

The first partial monochromatic light sources here may include a first monochromatic light source 122, a second monochromatic light source 123, a third monochromatic light source 124, a fourth monochromatic light source 125, a fifth monochromatic light source 126, a sixth monochromatic light source 127 as illustrated in fig. 29. The second part of the monochromatic light source comprises: a seventh monochromatic light source 121. In the first part of monochromatic light sources, each light source is correspondingly provided with a dichroic mirror. Illustratively, first monochromatic light source 122 corresponds to first dichroic mirror 128, second monochromatic light source 123 corresponds to second dichroic mirror 129, third monochromatic light source 124 corresponds to third dichroic mirror 130, fourth monochromatic light source 125 corresponds to fourth dichroic mirror 131, fifth monochromatic light source 126 corresponds to fifth dichroic mirror 132, and sixth monochromatic light source 127 corresponds to sixth dichroic mirror 133.

The plurality of monochromatic light sources in this embodiment are combined beams by a plurality of dichroic mirror stages. The placement position of each monochromatic light source can be determined according to the type of dichroic mirror.

Optionally, the placement position of each monochromatic light source is determined according to the type of the dichroic mirror selected and the wavelength of each monochromatic light source; the placement position of each dichroic mirror is determined according to the type of the dichroic mirror selected and the cut-off wavelength of each dichroic mirror.

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

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

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 a plurality of dichroic mirrors and then irradiated on the sixth dichroic mirror 133, the combined light is reflected by the sixth dichroic mirror 133 and then enters a uniform illumination light path, and the combined light is refracted by the sixth dichroic mirror 133 and then enters a light source feedback unit. The seventh monochromatic light source 127 enters the uniform illumination light path after being refracted by the sixth dichroic mirror 133, the seventh monochromatic light source 127 enters the light source feedback unit after being reflected by the sixth dichroic mirror 133, and the light entering the light source feedback unit is focused by the focusing lens 107 and then irradiates on the first photodetector 108.

Light entering the dodging illumination light path is incident on fly eye lens 104. The fly-eye lens 104 divides an incident beam into sub-beams and focuses the sub-beams on the second sub-lens array, the sub-lenses in the second sub-lens and the integrating lens 105 together coincide 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.

Alternatively, the number of the monochromatic light sources is not limited to 7, the monochromatic light sources may be monochromatic LED light sources, and the number of the dichroic mirrors is not limited to 6.

In summary, the optical system of the dry biochemical analyzer provided in this embodiment may be composed of a light source feedback unit, a uniform illumination light path and a collection light path, and the current of the light source may be adjusted by the light source feedback unit, 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 multi-channel light source current driver arranged in the light source feedback unit can realize the fast switching control of the monochromatic light sources with different wavelengths. The incident light is subjected to uniform light treatment through the uniform light illumination light path, uniform illumination can be obtained on the dry reagent sheet to be measured, the light path is concise, and a plurality of monochromatic light sources with different wavelengths arranged off-axis can be overlapped and focused at the same position. By setting the collecting light path as a telecentric light path and setting a field diaphragm, the light rays of the whole illuminated surface can be uniformly collected. By adopting the system, the accuracy of the collected reaction light corresponding to the object to be detected can be improved, so that the accuracy of the subsequent analysis result of the object to be detected is improved.

In the several embodiments provided by the present application, it should be understood that the disclosed systems and methods may be implemented in other ways. For example, the embodiments of the system described above are merely illustrative, e.g., the division of the elements is merely a logical functional division, and there may be additional divisions when actually implemented, e.g., multiple elements or components may be combined or integrated into another system, or some features may be omitted, or not performed. Alternatively, the coupling or direct coupling or communication connection shown or discussed with each other may be an indirect coupling or communication connection via some interfaces, devices or units, which may be in electrical, mechanical or other form.

Claims

1. An optical system of a dry biochemical analyzer, comprising: the light source feedback unit, the uniform illumination light path and the collection light path; the optical system takes the central normal line of the measured dry reagent sheet as an axis, and the light source feedback unit is vertically arranged relative to the axis of the optical system; the optical axis of the uniform illumination light path coincides with the axis of the optical system; the optical axis of the collecting light path and the axis of the optical system form a first preset angle;

2. The optical system of a dry biochemical analyzer according to claim 1, wherein the light source feedback unit comprises: the device 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 sequentially connected;

3. The optical system of a dry biochemical analyzer according to claim 2, wherein,

The data acquisition and conversion module comprises: the system comprises a first light source detector, a stream voltage converter, a gain amplifier and an analog-to-digital converter;

4. The optical system of claim 3, wherein the optical system further comprises: a spectroscope and a focusing lens; the spectroscope is placed at a third preset angle with the axis of the optical system;

5. The optical system of claim 2, wherein the control module comprises: a controller; the driving module includes: a multi-channel light source current driver;

6. The optical system of a dry biochemical analyzer according to claim 5, wherein,

The controller is specifically configured to determine a difference value between the current feedback optical signal value and the preset target optical signal value according to the current feedback optical signal value of the light source with the specified wavelength and the preset target optical signal value corresponding to the light source with the specified wavelength;

7. The optical system of a dry biochemical analyzer according to claim 5, wherein,

The controller is specifically used for determining a light source with a specified wavelength corresponding to the object to be detected according to the type of the object to be detected; and sending 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 with the specified wavelength.

8. The optical system of claim 3, wherein the data acquisition and conversion module further comprises: a low pass filter; one end of the low-pass filter is connected with the stream-voltage converter, and the other end of the low-pass filter is connected with the gain amplifier;

9. The optical system of claim 4, wherein the dodging illumination light path comprises: fly-eye lens and integral lens; the fly-eye lens comprises a first surface lens and a second surface lens, wherein the first surface lens is a surface far away from the integral lens, and the second surface lens is a surface close to the integral lens;

The second sub-lens and the integral lens jointly coincide the corresponding sub-beams to the focal plane of the integral lens; the measured dry reagent sheet is arranged on the focal plane of the integrating lens.

10. The optical system of claim 9, wherein the integrating lens is a doublet lens comprising a positive lens and a negative lens, the positive lens being a low-dispersion glass; the negative lens is high-dispersion glass.

11. The optical system of a dry biochemical analyzer according to claim 9, wherein,

The fly-eye lens comprises a first single-sided fly-eye lens and a second single-sided fly-eye lens; the first single-sided fly-eye lens and the second single-sided fly-eye lens are arranged in parallel, and the arrangement interval is the focal length of the sub-lens; the sub-lenses are lens units in the first single-sided fly-eye lens or the second single-sided fly-eye lens.

12. The optical system of claim 9, wherein the dod illumination light path further comprises: a glass lens; the glass lens is arranged between the fly-eye lens and the integrating lens, and the glass lens and the axis of the optical system form a fourth preset angle;

13. The optical system of claim 1, wherein the collection optical path comprises: a first lens, an aperture stop, a field stop, a second lens, and a second photodetector; the first lens, the aperture diaphragm, the field diaphragm, the second lens and the second photoelectric detector are sequentially arranged away from the dry reagent sheet to be tested along the optical axis of the collecting light path; the aperture diaphragm is arranged on the image space focal plane of the first lens and is arranged in parallel with the first lens; the field diaphragm is arranged at the image plane of the first lens;

Light rays reflected from the measured dry reagent sheet and having an included angle with the optical axis of the collecting light path meeting the second preset angle are focused by the first lens, the focused light beams pass through the aperture diaphragm to reach an image plane, pass through the field diaphragm and are incident on the second lens, and are focused on the second photoelectric detector by the second lens.

14. The optical system of claim 13, wherein the size of the field stop is determined according to the size of the area to be measured on the dry reagent sheet to be measured and the first predetermined angle formed by the optical axis of the collecting optical path and the axis of the optical system.

15. The optical system of the dry biochemical analyzer according to claim 4, wherein the optical system further comprises: the light source module comprises a monochromatic light source with at least one wavelength;

The light source with the specified wavelength is a light source in the light source module.

16. The optical system of claim 15, wherein 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;

17. The optical system of claim 15, wherein 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;

18. The optical system of claim 15, wherein the light source module comprises a fourth light source module; the fourth light source module is arranged along the axis of the optical system;

19. The optical system of claim 15, wherein a first portion of the monochromatic light sources in the light source module are disposed along an axis of the optical system; the second part of monochromatic light sources in the light source module are arranged perpendicular to the axis of the optical system;

20. The optical system of claim 19, wherein the placement position of each monochromatic light source is determined according to the type of dichroic mirror selected and the wavelength of each monochromatic light source;

21. The optical system of a dry biochemical analyzer according to any one of claims 1-20, wherein said optical system further comprises: a transmission device; at least one dry reagent sheet to be tested is arranged on the transmission device; each measured dry reagent sheet corresponds to each measuring hole one by one;

The transmission device is used for periodic and cyclic transmission under the control of time sequence so as to complete the switching of each tested dry reagent sheet in each period.