Centrifugal microfluidic biochemical analyzer and concentration detection system

Abstract

A centrifugal microfluidic biochemical analyzer (10) and a concentration detection system, the analyzer (10) uses a shading disc and a microfluidic disc in conjunction with each other, and uses a first light beam emitted from a light hole in the shading disc to position a detection hole in the microfluidic disc, so that a positioning hole in the microfluidic disc can be omitted, and the detection efficiency can be improved. The micro-fluidic disc with the same volume can expand more detection holes, and each detection hole can be positioned by using the detection signal of the first light beam without positioning the detection hole by using a positioning hole, so that the influence of error tolerance of the positioning hole and the detection hole is avoided, and the accuracy of a detection result is improved.

Description

Centrifugal microfluidic biochemical analyzer, concentration detection system Technical Field

[0001] The present application relates to the field of biochemical analysis and detection technology, and more specifically, to a centrifugal microfluidic biochemical analyzer and a concentration detection system. Background Art

[0002] A centrifugal microfluidic biochemical analyzer, often referred to as a microfluidic biochemical analyzer, is a commonly used medical device in the field of in vitro diagnostics. It uses microfluidic technology to perform tests on samples such as blood, urine, and body fluids. Microfluidic technology is implemented on a microfluidic disk (or microfluidic chip). A centrifugal microfluidic biochemical analyzer applies centrifugal force to the microfluidic disk, causing the sample to form a tiny fluid within the disk and then fill each well with reagents. The analyzer's concentration detection system then measures the concentration of the sample within the well, and then generates test results based on the concentration of the sample.

[0003] Since there are multiple detection holes set on the microfluidic disk, different detection holes can be used for the detection of different biochemical items. Therefore, after the microfluidic biochemical analyzer obtains the detection results corresponding to each detection hole, it is necessary to determine the detection hole corresponding to each detection result, and then determine the detection item corresponding to the detection result.

[0004] Therefore, a technical point involved in microfluidic biochemical analyzers is how to locate different detection holes. Currently, the structure of the microfluidic disc is shown in Figure 1a, and the concentration detection system supporting the microfluidic biochemical analyzer is shown in Figure 1b. The microfluidic disc is provided with multiple colorimetric holes (a specific form of detection hole) along the circumference, and a positioning hole is opened between every two colorimetric holes through injection molding. The test sample is placed in each colorimetric hole. The microfluidic biochemical analyzer controls the microfluidic disc to rotate along the rotation axis at a preset speed. The detection beam (not shown) can sequentially measure the test results of the test sample in each colorimetric hole. The infrared beam emitted by the infrared LED will pass through each positioning hole in turn. The infrared beam reflected by the positioning hole is detected by the infrared detector. The position of each positioning hole in the microfluidic disc can be determined based on the time when the infrared detector detects the infrared beam and the rotation speed of the microfluidic disc. Since the positioning holes and the colorimetric holes are set according to a preset spacing, the position of the positioning hole and the preset spacing can be used to obtain the position of the adjacent colorimetric holes of the positioning hole.

[0005] However, in real-world applications, there is often a certain error between the actual spacing between the positioning holes and the colorimetric holes in the microfluidic disks manufactured, and the pre-designed spacing. Therefore, the positioning accuracy of the colorimetric holes will be affected by the distance tolerance between the colorimetric holes and the positioning holes.

[0006] Summary of the Invention

[0007] In view of this, the present application provides a centrifugal microfluidic biochemical analyzer and a concentration detection system for accurately determining the correspondence between the test results and the test wells (ie, test items), thereby accurately obtaining the test results of each test item.

[0008] In a first aspect, an embodiment of the present application provides a centrifugal microfluidic biochemical analyzer, comprising: a first light source assembly, a second light source assembly, a first color separation assembly, a rotation drive mechanism, a first detection module, a second detection module, and a control device;

[0009] The first light source assembly is used to emit a first light beam, and the second light source assembly is used to emit a second light beam, wherein a spectral range of the first light beam does not overlap with a preset spectral range of the second light beam used for detecting the sample to be tested;

[0010] The first color separation component is used to integrate the optical path of the first light beam and the optical path of the second light beam into the same optical path to obtain a combined incident light beam;

[0011] The rotary drive mechanism includes a rotating shaft, and the rotating shaft is used to mount the microfluidic disk and the optical shielding plate, wherein the microfluidic disk is provided with a plurality of detection holes along a circumferential direction, and the optical shielding plate is provided with a plurality of light-transmitting holes along a circumferential direction, and the size of a target light-transmitting hole among the plurality of light-transmitting holes is different from the sizes of the other light-transmitting holes other than the target light-transmitting hole, and when the microfluidic disk and the optical shielding plate are mounted on the rotating shaft, the positions of the detection holes and the light-transmitting holes correspond one-to-one;

[0012] The rotary drive mechanism is used to drive the rotary shaft to rotate so as to drive the microfluidic disk to rotate, so that the combined incident light beam passes through the corresponding groups of light-transmitting holes and the detection holes in sequence to obtain each combined output light beam;

[0013] The first detection module is configured to detect a pulse signal of the first light beam based on each of the combined outgoing light beams, and send the pulse signal of the first light beam to the control device;

[0014] The second detection module is used to detect the energy of the preset spectral band based on each of the combined output light beams, and send the energy of each of the preset spectral bands to the control device;

[0015] The control device is used to determine the detection item corresponding to each pulse waveform in the pulse signal of the first light beam, and determine the detection result of the sample to be tested under each detection item according to the detection item corresponding to each pulse waveform and the energy of each preset spectral segment.

[0016] In a second aspect, an embodiment of the present application provides a concentration detection system, comprising: a first light source assembly, a second light source assembly, a first color separation assembly, a rotation drive mechanism, a first detection module, a second detection module, and a control device;

[0017] The first light source assembly is used to emit a first light beam, and the second light source assembly is used to emit a second light beam, wherein a spectral range of the first light beam does not overlap with a preset spectral range of the second light beam used to detect the concentration of the sample to be tested;

[0018] The first color separation component is used to integrate the optical path of the first light beam and the optical path of the second light beam into the same optical path to obtain a combined incident light beam;

[0019] The rotary drive mechanism includes a rotating shaft, and the rotating shaft is used to mount the detection disk and the optical shielding plate, wherein the detection disk is provided with a plurality of detection holes along the circumferential direction, and the detection holes are used to accommodate samples to be tested, and the optical shielding plate is provided with a plurality of light-transmitting holes along the circumferential direction, and the size of a target light-transmitting hole among the plurality of light-transmitting holes is different from the sizes of the other light-transmitting holes other than the target light-transmitting hole, and when the detection disk and the optical shielding plate are mounted on the rotating shaft, the positions of the detection holes and the light-transmitting holes correspond one-to-one;

[0020] The rotation drive mechanism is used to drive the detection disk and the light shielding disk to perform synchronous rotation around the rotation axis in a plane perpendicular to the same optical path, so that the combined incident light beam passes through the corresponding groups of light-transmitting holes and the detection holes in sequence to obtain each combined outgoing light beam;

[0021] The first detection module is configured to detect a pulse signal of the first light beam based on each of the combined outgoing light beams, and send the pulse signal of the first light beam to the control device;

[0022] The second detection module is used to detect the energy of the preset spectral band based on each of the combined output light beams, and send the energy of each of the preset spectral bands to the control device;

[0023] The control device is used to determine the sample to be tested contained in each of the detection holes according to the pulse signal of the first light beam, and to determine the concentration of each of the sample to be tested according to the energy of each of the preset spectral segments.

[0024] In the technical solutions provided in the embodiments of the present application, a shading disc is used in conjunction with a microfluidic disc, and the detection holes on the microfluidic disc are positioned using the first light beam transmitted through the light-transmitting hole on the shading disc. This not only eliminates the positioning holes on the microfluidic disc, allowing the microfluidic disc of the same volume to expand with more detection holes, but also utilizes the detection signal of the first light beam to locate each detection hole, eliminating the need to locate the detection hole using the positioning hole. This avoids the influence of the error tolerance between the positioning hole and the detection hole, and improves the accuracy of the correlation between the detection items and the detection results. BRIEF DESCRIPTION OF THE DRAWINGS

[0025] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the following briefly introduces the drawings required for use in the embodiments or the description of the prior art. Obviously, the drawings described below are only some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying any creative work.

[0026] FIG1a is a schematic structural diagram of a conventional microfluidic disc;

[0027] FIG1b is a schematic diagram of a scheme for positioning colorimetric wells in an existing centrifugal microfluidic biochemical analyzer;

[0028] Figures 2-4 are schematic diagrams of three structures of centrifugal microfluidic biochemical analyzers provided in the embodiments of the present application;

[0029] FIG5 is a schematic diagram of a structure of a microfluidic disc provided in an embodiment of the present application;

[0030] FIG6 is a schematic structural diagram of an aperture disk provided in an embodiment of the present application;

[0031] FIG7 a is a schematic diagram of a pulse signal of a first light beam provided in an embodiment of the present application;

[0032] FIG7 b is a schematic diagram of a solution for determining the correspondence between each detection item and the energy of each preset spectral segment using the pulse signal of the first light beam provided in an embodiment of the present application. DETAILED DESCRIPTION

[0033] The following will clearly and completely describe the technical solutions in the embodiments of the present invention in conjunction with the accompanying drawings. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without making creative efforts are within the scope of protection of the present invention.

[0034] To facilitate understanding, the working principle of the centrifugal microfluidic biochemical analyzer is first explained.

[0035] The centrifugal microfluidic biochemical analyzer can control the microfluidic disc to rotate to generate centrifugal motion. Centrifugal force is used to achieve the flow and mixing of samples and diluents within the microfluidic disc, resulting in a diluted sample. The diluted sample is then filled into each detection well through a separation channel and reacts with the reagents in the detection well to obtain the test sample. The centrifugal microfluidic biochemical analyzer has two optical paths: a detection optical path and a positioning optical path. The former is used to detect the concentration of the test sample in each detection well to obtain the test result; different detection wells are used to detect different items, and the latter is used to determine the detection well associated with each test result, that is, to determine the test item to which each test result belongs. In other words, the latter is used to determine the test result corresponding to each test item.

[0036] In response to the technical defect that the existing positioning optical path is not accurate enough in positioning the detection holes, the embodiment of the present application provides a centrifugal microfluidic biochemical analyzer. By using a shading optical disc and a microfluidic disc in combination, the detection optical path and the positioning optical path are integrated into the same optical path to accurately determine the correlation between the detection holes and the detection results. Compared with the existing detection scheme, the present application scheme adds a shading optical disc and a microfluidic disc to complete the coordinated detection. It should be noted that the microfluidic disc in the present application scheme omits the processing and manufacturing of the positioning holes compared to the existing microfluidic disc shown in Figure 1a, thereby simplifying the disc structure and manufacturing cost, and allowing the microfluidic disc to have more space to expand the number of detection holes.

[0037] See Figures 2-4, which show three different structures of centrifugal microfluidic biochemical analyzers. The specific structure of the centrifugal microfluidic biochemical analyzer is described below in conjunction with Figures 2-4.

[0038] Example 1

[0039] The structure of the centrifugal microfluidic biochemical analyzer 10 is shown in FIG2 , and includes a first light source assembly 100 , a second light source assembly 200 , a first color separation assembly 300 , a rotation drive mechanism 400 , a first detection module 500 , a second detection module 600 and a control device (not shown).

[0040] The first light source assembly 100 and the second light source assembly 200 are first described below.

[0041] Specifically, the first light source assembly can emit a light beam, and the second light source assembly can also emit a light beam. For ease of distinction, the light beam emitted by the first light source assembly is referred to as the first light beam, and the light beam emitted by the second light source assembly is referred to as the second light beam. It should be noted that the first light source assembly is used in conjunction with the first detection module, that is, the first detection module is used to detect the pulse signal of the first light beam; the second light source assembly is used in conjunction with the second detection module, that is, the second detection module uses the second light beam to detect the concentration of the test sample. The specific detection process is described in detail below.

[0042] In one specific implementation, the first light source assembly 100 includes an infrared light source and a second light-collecting assembly. The infrared light source is configured to emit an initial infrared beam. The second light-collecting assembly is configured to reduce the divergence of the initial infrared beam to produce a first light beam. Specifically, the second light-collecting assembly is positioned in the optical path of the initial infrared beam. The initial infrared beam is then limited by the second light-collecting assembly to produce the first light beam. It is understood that in this implementation, the first light beam is an infrared beam. As shown in FIG2 , the first light source assembly 100 includes an infrared light source 101, an infrared signal aperture 102, and an infrared shaping lens 103. It is understood that the combination of the infrared signal aperture 102 and the infrared shaping lens 103 can improve the light source utilization of the initial infrared beam. However, the second light-collecting assembly is not limited to the structure shown in FIG2 . For example, the infrared shaping lens 103 can be omitted, and the initial infrared beam can be limited to the infrared signal aperture 102 alone to produce the first light beam. Alternatively, the second light-collecting assembly can include any optical device or combination of optical devices that can be considered by those skilled in the art for limiting the divergence of an infrared beam. For example, the infrared shaping lens can be replaced with an infrared light-collecting lens.

[0043] In one specific implementation, the second light source assembly 200 includes a xenon lamp light source and a third light-collecting assembly. The xenon lamp light source is configured to emit an initial xenon lamp beam. The third light-collecting assembly is configured to reduce the divergence of the initial xenon lamp beam to produce a second light beam. Specifically, the third light-collecting assembly is disposed in the optical path of the initial xenon lamp beam. The initial xenon lamp beam is confined by the third light-collecting assembly to generate a second light beam. It is understood that in this implementation, the second light beam is a xenon lamp beam. As shown in FIG2 , the second light source assembly 200 includes a xenon lamp light source 201, a xenon lamp signal aperture 202, and a xenon lamp shaping lens 203. It is understood that the combination of the xenon lamp signal aperture 202 and the xenon lamp shaping lens 203 can improve the light source utilization of the initial xenon lamp beam. However, the third light-collecting assembly is not limited to the structure shown in FIG2 . For example, the xenon lamp shaping lens 203 can be omitted, and the xenon lamp signal aperture 202 alone can be used to confine the initial xenon lamp beam to produce the second light beam. Alternatively, the third light collecting component includes any optical device or combination of multiple optical devices that can be thought of by those skilled in the art for limiting the divergence of the xenon lamp light beam, such as the xenon lamp shaping lens can also be replaced by a xenon lamp light collecting lens.

[0044] The first color separation component 300 will be described below.

[0045] The first color separation component 300 is used to integrate the optical path of the first light beam and the optical path of the second light beam into the same optical path to obtain a combined incident light beam. The first color separation component 300 can integrate two light beams with different optical paths into the same optical path. As shown in Figure 2, the first color separation component 300 transmits the first light beam and reflects the second light beam. The first light beam and the second light beam are symmetrically incident with respect to the first color separation component 300, and the incident angles are both 45 degrees. The first light beam and the second light beam passing through the first color separation component 300 are integrated into the same optical path. The light beam irradiated along this optical path can be called a combined incident light beam. In a specific implementation, the first color separation component includes a dichroic mirror, a grating, or a dispersion prism. In addition, it should be noted that the relative positions of the first light beam and the second light beam and the first color separation component 300 are not limited to those shown in FIG2 , and may also be other forms that can integrate the optical paths of the first light beam and the second light beam, such as the second light source component 200 is flipped to the right side of the integrated optical path with the integrated optical path as the symmetry line, and the first color separation component 300 is rotated 90 degrees clockwise with the intersection of the two light beams as the center.

[0046] First, the rotation drive mechanism 400 will be described below.

[0047] The rotation drive mechanism 400 includes a rotation shaft, which is used to mount the microfluidic disk and the light shielding disk.

[0048] The microfluidic disk has multiple detection holes circumferentially defined. These holes can include colorimetric holes or other types of holes for accommodating test samples. Figure 5 shows a schematic diagram of one configuration of colorimetric holes on a microfluidic disk. Sixteen colorimetric holes are evenly spaced along the circumference of the disk. Of course, the number of colorimetric holes can be greater or less than that shown in Figure 5.

[0049] The optical shielding disc has multiple light-transmitting holes formed along its circumference, and the size of one of the multiple light-transmitting holes is different from the sizes of the other light-transmitting holes. For ease of description, the light-transmitting hole of different size is referred to as the target light-transmitting hole. It should be noted that the size of the target light-transmitting hole can be larger or smaller than the sizes of the other light-transmitting holes, as long as the sizes can be distinguished. In one specific implementation, the light-transmitting holes are circular, and the multiple light-transmitting holes are evenly distributed along the circumference of the optical shielding disc; the size of the target light-transmitting hole is larger than the sizes of the other light-transmitting holes, and the sizes of the other light-transmitting holes are consistent. Furthermore, each light-transmitting hole on the optical shielding disc is larger than the size of the detection hole on the corresponding microfluidic disc.

[0050] In one specific implementation, the light-blocking disc can be an aperture disc, and the light-transmitting aperture is an aperture. See Figure 6, which shows a schematic structural diagram of an aperture disc, in which one aperture is slightly larger than the other apertures. The aperture disc is fixedly or removably mounted to the rotating shaft of the rotary drive mechanism, and the microfluidic disc is removably mounted on the side of the aperture disc away from the rotating shaft. For ease of understanding, the relative positions of the microfluidic disc and the aperture disc are illustrated in conjunction with Figures 2-4. Microfluidic disc 800 is removably mounted to the rotating shaft of the rotary drive mechanism, and aperture disc 700 is removably mounted on the side of the microfluidic disc away from the rotating shaft. With reference to the up-and-down viewing direction of Figures 2-4, the microfluidic disc is mounted below the aperture disc. In another specific implementation, with reference to the up-and-down viewing direction of Figures 2-4, the microfluidic disc can also be mounted above the aperture disc. The microfluidic disc is removable, and the aperture disc can be fixed to the rotating shaft or removably mounted to the rotating shaft.

[0051] When the microfluidic disc and the optical shielding plate are mounted on the rotating shaft, each detection hole corresponds to each light-transmitting hole. As shown in FIG2-4, the aperture 701 corresponds to the position of the colorimetric hole 801. The rotary drive mechanism 400 is used to drive the rotating shaft to rotate the microfluidic disc to prepare the test samples required for the detection project, wherein the test samples required for each detection project are placed in the corresponding detection holes. The rotary drive mechanism 400 drives the microfluidic disc and the optical shielding plate to perform synchronous rotational motion around the rotating shaft in a plane perpendicular to the same optical path, so that the combined incident light beam passes through each corresponding group of light-transmitting holes and detection holes in sequence to obtain each combined output light beam. As shown in FIG2-4, the rotary drive mechanism 400 drives the microfluidic disc and the optical shielding plate to rotate counterclockwise. Each combined incident light beam is irradiated downward from the top of the figure, and after passing through the light-transmitting holes and detection holes, a combined output light beam is obtained.

[0052] The first detection module 500 is used to detect the pulse signal of the first light beam based on each combined output light beam, and send the pulse signal of the first light beam to the control device; the second detection module 600 is used to detect the energy of the preset spectral segment based on each combined output light beam, and send the energy of each preset spectral segment to the control device; the control device is used to determine the detection item corresponding to each pulse waveform in the pulse signal of the first light beam, and determine the detection result of the sample to be tested under each detection item according to the detection item corresponding to each pulse waveform and the energy of each preset spectral segment.

[0053] The first detection module 500 is described below.

[0054] The first detection module 500 first separates the first light beam from the combined outgoing light beam and then uses a detector to detect the signal of the first light beam. It is understood that when the optical shielding plate and the microfluidic disk are mounted on the rotating shaft, the light-transmitting holes and detection holes at corresponding positions become a group of holes. During the synchronous rotation of the optical shielding plate and the microfluidic disk, the combined incident light beam sequentially illuminates each group of holes, and the combined light beam emerging from each group of holes is called the combined outgoing light beam. The first detection module continuously detects the combined outgoing light beam. It is understood that the first detection module detects the combined outgoing light beam only when the combined incident light beam passes through each group of holes. When the combined incident light beam illuminates other opaque positions of the optical shielding plate, the combined incident light beam is blocked and the first detection module does not detect the combined outgoing light beam. Therefore, the first light beam detected by the first detection module based on each combined outgoing light beam is a pulse signal, and the pulse position of the pulse signal indicates that the combined incident light beam has passed through a group of holes.

[0055] In order to ensure sufficient light transmission so that the first detection module 500 can detect the trapezoidal pulse signal of the first light beam, the target light transmission hole on the shading disk can be larger than the other light transmission holes, and the size of the light transmission hole can be larger than the size of the detection hole at the corresponding position.

[0056] Taking the microfluidic disk shown in Figure 5 and the aperture disk shown in Figure 6 as examples, the pulse signal of the first light beam detected by the first detection module is shown in Figure 7a. The first light beam is detected 16 times within one rotational cycle, so the pulse signal within one rotational cycle includes 16 trapezoidal pulses. The pulse signal of the first light beam can be transmitted to the control device. The pulse signal of the first light beam is related to the size of the light transmission aperture. If the light transmission aperture is small, the pulse signal of the first light beam may not be a trapezoidal pulse signal, but a sawtooth pulse signal.

[0057] In a specific implementation, as shown in FIG2 , the first detection module 500 includes: a second color separation component 501 , a first light collection component 502 and a detector 503 .

[0058] The second color separation component 501 includes a dichroic mirror, a grating, or a dispersion prism. The second color separation component is arranged on the optical path from the combined outgoing light beam to the detector 503, and is specifically used to separate the first light beam and the second light beam from each combined outgoing light beam. As shown in Figure 2, the angle between the second color separation component 501 and the first color separation component 300 is 90 degrees. The second color separation component 501 transmits the first light beam (the transmitted first light beam is detected by the detector 503) and reflects the second light beam (the reflected second light beam reaches the second detection module 600). Alternatively, the angle between the second color separation component 501 and the first color separation component 300 is 0 degrees, that is, the two color separation components are parallel to each other, so that the second color separation component 501 can be reflected by the second light beam to the other side of the combined outgoing light path (the right side in Figure 2).

[0059] The first light-collecting component 502 is disposed on the optical path from the separated first light beam to the detector, and is used to reduce the divergence of the separated first light beam. For example, the first light-collecting component 502 may specifically include an infrared collection aperture. In some embodiments, the first light-collecting component 502 may be omitted, and the first light beam separated by the second color separation component 501 directly reaches the detector 503. The detector 503 is used to receive each separated first light beam and generate a pulse signal of the first light beam, and transmit the pulse signal of the first light beam to the control device. In some embodiments, the light-collecting diameter of the first light-collecting component 502 is smaller than the diameter of the detection hole of the microfluidic disk. This can filter out stray light from other paths, such as ambient light and surface reflected light, so that the light signals detected by the detector 503 all come from the detection hole, thereby ensuring the accuracy of the waveform signal of the first light beam.

[0060] The second detection module 600 is described below.

[0061] During the synchronous rotation of the optical shielding plate and the microfluidic disk, the second detection module 600 detects the energy of the preset spectral segments from the separated second light beam and transmits the energy of each preset spectral segment to the control device. The control device then calculates the concentration of the test sample in each detection well based on the energy of the preset spectral segments. Specifically, after the combined incident light beam passes through the test sample in the detection well, a portion of its spectral energy is absorbed by the test sample. The second detection module 600 detects the energy of the separated second light beam in the preset spectral segments. The control device uses the energy of the preset spectral segments to calculate the concentration of the test sample.

[0062] Specifically, the control device can pre-store the energy of the second light beam in the same preset spectral band when the second light beam passes through an empty detection hole (a detection hole that does not contain a test sample). The control device uses the ratio of the energy of the preset spectral band when the test sample is present in the detection hole to the energy of the preset spectral band when the test sample is not present in the detection hole as the absorbance of the preset spectral band, and then calculates the absorbance using the Lambert-Beer law to obtain concentration information. The test sample can be a test sample of various samples such as body fluids, blood, urine, etc.

[0063] It should be noted that the spectral range of the first light beam does not overlap with the preset spectral range in the second light beam used to detect the concentration of the test sample. This allows the first detection module and the second detection module to process the preset spectral ranges of the first and second light beams, respectively. As shown in Figure 2, the second detection module 600 is specifically configured to receive each second light beam separated by the second color separation component 501, detect the energy of the preset spectral range from each second light beam, and transmit the energy of each preset spectral range to the control device.

[0064] In addition, the preset spectral segment that the second detection device 600 can detect can be a continuous spectral segment or a plurality of preset spectral segments of different ranges. As shown in Figures 2-4, the second detection module 600 may include a plurality of dichroic mirrors 601 arranged in sequence along the same optical path. The function of the dichroic mirrors is to separate a light beam of a preset spectral segment from the separated second light beam again, and the energy of the separated light beam of the preset spectral segment is detected by the corresponding detector 602. The second detection device 600 sends the energy of the plurality of preset spectral segments to the control device. The control device can pre-store the correspondence between the type of the sample to be tested and the preset spectral segment. After receiving the energy of the plurality of preset spectral segments, the energy of the preset spectral segment corresponding to the type of the current sample to be tested can be selected from the energies of the plurality of preset spectral segments according to the type of the current sample to be tested, and then the concentration of the current sample to be tested can be calculated using the energy of the selected preset spectral segment.

[0065] The second detection device 600 shown in Figures 2-4 has the ability to detect the concentration of multiple types of samples to be tested due to including multiple color separation mirrors and detectors, and is more applicable. Of course, the specific structure of the second detection device 600 is not limited to that shown in Figures 2-4. It can be used to set the number of color separation mirrors and detectors in order to detect the concentration of more or fewer types of samples to be tested. The application does not specifically limit the number of color separation mirrors and detectors. In addition, the shaping lens 603 of the second detection device 600 can shape the separated second light beam, and the shaped second light beam is split by the color separation mirror 601. Of course, the setting of the shaping lens 603 can also be omitted. Furthermore, splitting is not limited to being realized by the color separation mirror, but can also be realized by other optical spectroscopic devices such as gratings and dispersion prisms.

[0066] Next, the control device will be described.

[0067] The control device is a device with computing capabilities, such as a controller, which can communicate with the first and second detection modules via wired or wireless communication. The control device can collect two types of data: the pulse signal of the first light beam transmitted by the first detection device 500, and the energy of each preset spectral segment transmitted by the second detection device 600. It should be noted that the energy of each preset spectral segment corresponds to the energy of the preset spectral segment corresponding to the different detection apertures.

[0068] The control device determines the test items corresponding to each pulse waveform based on the pulse signal of the first light beam, and determines the test results of the test sample under each test item based on the energy of each preset spectral band. The test items include, but are not limited to, CRP (C-reactive protein) and erythrocyte sedimentation rate.

[0069] The specific implementation method includes: since the shading disk is in a rotating state, and the size of the target light-transmitting hole on the shading disk is different from the size of other light-transmitting holes, the pulse signal of the first light beam is a periodic signal, and the waveform of one pulse in the pulse signal is different from the other pulse waveforms, so that the control device can determine that the light-transmitting hole corresponding to the pulse waveform of different size is the target light-transmitting hole, and then according to the rotation direction of the light-transmitting hole and the arrangement relationship between the other light-transmitting holes and the target light-transmitting hole, the light-transmitting holes corresponding to the other pulse waveforms can be determined in sequence. Furthermore, since the positions of the light-transmitting holes and the detection holes correspond one to one, the control device can determine the detection holes corresponding to each pulse waveform in the pulse signal of the first light beam. Furthermore, the detection items corresponding to each detection hole can be pre-set, for example, detection hole 01 corresponds to detection item A, and detection hole 02 corresponds to detection item B, and then the control device can determine the detection item corresponding to each pulse waveform. Since the energy of the preset spectral segment and the pulse signal of the first light beam are detected at the same time, there is a one-to-one temporal correspondence between each pulse waveform and each energy in the pulse signal of the first light beam. The control device can use the correspondence between the pulse waveform and the energy, as well as the correspondence between the pulse waveform and the detection item to determine the correspondence between the energy and the detection item. After obtaining the concentration information using the energy, the concentration information of the sample to be tested under each detection item can be determined, and the detection results of the detection items can be obtained based on the concentration information.

[0070] The above process is explained in conjunction with Figures 5, 6 and 7b. Assuming that the aperture disk and microfluidic disk in Figures 5 and 6 rotate counterclockwise, the control device receives the waveform signal of the first light beam. After analyzing the waveform signal, it can determine the colorimetric aperture corresponding to each pulse waveform, such as the widest trapezoidal pulse corresponds to colorimetric aperture No. 01, and the other trapezoidal pulses in one rotation cycle correspond to colorimetric apertures No. 02-16 in sequence. Since there is a correspondence between the colorimetric apertures and the detection items, it is also possible to determine the detection item corresponding to each pulse waveform, such as the widest trapezoidal pulse corresponds to detection item 1, and the subsequent ones in one rotation cycle correspond to items 2-16 in sequence. In addition, based on the temporal correspondence between the various energies of the preset spectral segments and the trapezoidal pulses, the detection items corresponding to the various energy values ​​can be determined, such as the energy value corresponding to detection item 16 is E1, the energy value corresponding to detection item 1 is E2, the energy value corresponding to detection item 2 is E3, and so on.

[0071] As can be seen from the above description, each light-transmitting hole is larger than the size of its corresponding detection hole. Therefore, the pulse signal of the first light beam is a trapezoidal pulse signal. Therefore, when the control device determines the detection items corresponding to each pulse waveform in the pulse signal of the first light beam, it is specifically used to: first, based on the width of each trapezoidal pulse in the trapezoidal pulse signal, distinguish the target pulse waveform corresponding to the target light-transmitting hole and the other pulse waveforms corresponding to each other light-transmitting hole in each trapezoidal pulse. Then, according to the rotation direction of the rotating shaft and the sorting of the detection items corresponding to the rotation direction, determine the detection item corresponding to the target pulse waveform and the detection item corresponding to each other pulse waveform. Furthermore, based on the detection items corresponding to each pulse waveform and the energy of each preset spectral segment, determine the detection results of the test sample under each detection item.

[0072] In summary, one of the functions of the pulse signal of the first light beam is to locate the position of the detection hole on the microfluidic disk, so the first light beam can also be called a positioning beam; based on the energy of the preset spectral band in the second light beam, the detection result of the test sample can be obtained, so the second light beam can also be called a detection beam.

[0073] In some embodiments, the pulse signal of the first light beam can be used not only to locate the position of the detection hole on the microfluidic disk, but also as a trigger signal for the second light source component to emit the second light beam, that is, the control device is also used to control the first light source component to emit the first light beam, and when the first detection module detects the pulse signal of the first light beam, it controls the second light source component to emit the second light beam, so that the first color separation component can integrate the optical path of the first light beam and the optical path of the second light beam into the same optical path to obtain a combined incident light beam. It can be seen that in this embodiment, the first light source component continuously emits the first light beam. When the first detection module detects a pulse waveform of the first light beam, it means that the detection hole moves to the bottom of the combined light beam, thereby triggering the second light source component to emit the second light beam, and the second light source component immediately stops emitting the second light beam until the first detection module detects the next pulse waveform of the first light beam and then continues to emit the second light beam based on the trigger signal.

[0074] As can be seen, the second light source assembly emits the second light beam discontinuously. For example, the flash duration of the second light beam is generally about 1 μs. This reduces the energy consumption of the second light source assembly. Furthermore, it should be noted that when the pulse signal of the first light beam is a trapezoidal wave, the control device can more easily identify the trapezoidal pulse from the pulse signal, thereby accurately sending a trigger signal to the first light source assembly and using the trigger signal to control the first light source assembly.

[0075] Example 2

[0076] The structure of the centrifugal microfluidic biochemical analyzer 20 is shown in Figure 3, which includes a first light source assembly 100, a second light source assembly 200, a first color separation assembly 300, a rotation drive mechanism 400, a first detection module 500, a second detection module 600 and a control device (not shown).

[0077] The structures of the centrifugal microfluidic biochemical analyzer 20 in this embodiment are similar to those of the centrifugal microfluidic biochemical analyzer 10 in the first embodiment. Only the differences in the structures are described in detail below. For the same structures, please refer to the description of the corresponding contents above and will not be repeated here.

[0078] First, the second detection module 600 is set in a different position. In this embodiment, the second detection module 600 is set on the optical path from the combined output light beam to the second color separation component 501, and is specifically used to receive each combined output light beam, separate the light beams of the preset spectral segment from each combined output light beam to form a residual light beam, detect the energy of each separated light beam, and send the energy of each preset spectral segment to the control device; and the second color separation component 501 is set on the optical path from the residual light beam to the detector, and is specifically used to separate the first light beam from each residual light beam. It should be noted that in this embodiment, the second detection module 600 can use a color separation mirror to separate the light beam of the preset spectral segment from the combined output light beam. The color separation mirror is used to separate a light beam of a preset spectral segment. The second detection module 600 can include one or more color separation mirrors, and different color separation mirrors separate light beams of different preset spectral segments.

[0079] Second, the physical characteristics of the second color separation component are different. Unlike the second color separation component 501 of the centrifugal microfluidic biochemical analyzer 10, which transmits the first light beam, the second color separation component 501 of the centrifugal microfluidic biochemical analyzer 20 reflects the first light beam. It should be noted that the second color separation component 501 in this embodiment can transmit the first light beam.

[0080] Third, the angle between the second color separation component 501 and the first color separation component 300 is 0 degrees (i.e., they are parallel to each other). Of course, the angle between the second color separation component 501 and the first color separation component 300 can also be 90 degrees, so that the first light beam separated by the second color separation component 501 is flipped to the other side of the combined beam output light path (the left side in Figure 3).

[0081] Example 3

[0082] The structure of the centrifugal microfluidic biochemical analyzer 30 is shown in FIG4 , and includes a first light source assembly 100 , a second light source assembly 200 , a first color separation assembly 300 , a rotation drive mechanism 400 , a first detection module 500 , a second detection module 600 and a control device (not shown).

[0083] The structures of the centrifugal microfluidic biochemical analyzer 30 in this embodiment are similar to those of the centrifugal microfluidic biochemical analyzer 10 in the first embodiment. Only the differences in the structures are described in detail below. For the same structures, please refer to the description of the corresponding contents above and will not be repeated here.

[0084] First, the physical characteristics of the first color separation component differ. The first color separation component 300 of the centrifugal microfluidic biochemical analyzer 10 transmits the first light beam and reflects the second light beam, while the first color separation component 300 of the centrifugal microfluidic biochemical analyzer 20 reflects the first light beam and transmits the second light beam. As shown in Figure 4, the first and second light beams are symmetrically incident on the first color separation component, and both have an incident angle of 45 degrees.

[0085] Second, the second detection module 600 is positioned differently. In this embodiment, the second detection module 600 is positioned on the optical path from the combined outgoing light beam to the second color separation component 501, specifically for receiving each combined outgoing light beam, separating a light beam of a preset spectral segment from each combined outgoing light beam to form a residual light beam, detecting the energy of each separated light beam, and sending the energy of each preset spectral segment to the control device; and the second color separation component 501 is positioned on the optical path from the residual light beam to the detector, specifically for separating the first light beam from each residual light beam. It should be noted that in this embodiment, the second detection module 600 can use a color separation mirror to separate a light beam of a preset spectral segment from the combined outgoing light beam. The color separation mirror is used to separate a light beam of a preset spectral segment. The second detection module 600 can include one or more color separation mirrors, and different color separation mirrors separate light beams of different preset spectral segments.

[0086] Third, the physical characteristics of the second color separation component differ. The second color separation component 501 of the centrifugal microfluidic biochemical analyzer 10 transmits the first light beam, while the second color separation component 501 of the centrifugal microfluidic biochemical analyzer 20 reflects the first light beam. It should be noted that the second color separation component 501 in this embodiment can transmit the first light beam.

[0087] Fourth, the angle between the second color separation component 501 and the first color separation component 300 is 0 degrees (i.e., they are parallel to each other). Of course, the angle between the second color separation component 501 and the first color separation component 300 can also be 90 degrees, so that the first light beam separated by the second color separation component 501 is flipped to the other side of the combined beam output light path (the left side in Figure 3).

[0088] From the above embodiments, it can be seen that the first detection module detects the pulse signal of the first light beam based on each combined output light beam. For example, as shown in FIG2 , the second color separation component is used to separate the first light beam from the combined output light beam and then detect the pulse signal of the first light beam. Alternatively, as shown in FIG3-4 , the second color separation component is used to separate the first light beam from the remaining light beam of the combined output light beam and then detect the pulse signal of the first light beam. The second detection module can detect the energy of a preset spectral band based on each combined output light beam. For example, as shown in FIG2 , the second light beam is separated from the combined output light beam and then the energy of the preset spectral band is detected from the separated second light beam. Alternatively, as shown in FIG3-4 , the energy of the preset spectral band is directly detected from the combined output light beam.

[0089] As can be seen from the above embodiments, the centrifugal microfluidic biochemical analyzer provided by the present application uses a light-shielding disc in conjunction with a microfluidic disc, and uses the first light beam transmitted through the light-transmitting hole on the light-shielding disc to position the detection holes on the microfluidic disc. This not only eliminates the positioning holes on the microfluidic disc, allowing the microfluidic disc of the same volume to expand with more detection holes, but also uses the detection signal of the first light beam to locate each detection hole, eliminating the need to use the positioning holes to locate the detection holes. Therefore, the influence of the error tolerance between the positioning holes and the detection holes is avoided, and the accuracy of the correlation between the detection holes (detection items) and the detection results is improved.

[0090] In other embodiments, the light-shielding disc can be integrated with the microfluidic disc. The light-shielding disc is formed by coating a light-shielding material on one side of the microfluidic disc, and the light-transmitting hole is the area of ​​the microfluidic disc that is not coated with the light-shielding material.

[0091] In other embodiments, the light shielding disc is a light shielding film made of a light shielding material, and the light-transmitting hole is a through hole opened in the light shielding film; the light shielding film is fixedly or detachably attached to one side of the microfluidic disc.

[0092] In addition, the present application also provides a concentration detection system, which can be applied to various medical devices that use light beams to detect the concentration of a sample to be tested, such as a liquid chromatograph.

[0093] Specifically, the concentration detection system includes: a first light source component, a second light source component, a first color separation component, a rotation drive mechanism, a first detection module, a second detection module and a control device.

[0094] The first light source assembly is used to emit a first light beam, and the second light source assembly is used to emit a second light beam, wherein the spectral range of the first light beam does not overlap with the preset spectral range in the second light beam used to detect the concentration of the sample to be tested.

[0095] The first color separation component is used to integrate the optical path of the first light beam and the optical path of the second light beam into the same optical path to obtain a combined incident light beam.

[0096] The rotary drive mechanism includes a rotating shaft for mounting a detection disk and a light shielding plate. The detection disk is provided with a plurality of detection holes along a circumferential direction, the detection holes being used to accommodate samples to be tested. The light shielding plate is provided with a plurality of light-transmitting holes along a circumferential direction, and the size of a target light-transmitting hole among the plurality of light-transmitting holes is different from the sizes of the other light-transmitting holes. When the detection disk and the light shielding plate are mounted on the rotating shaft, each detection hole corresponds to each light-transmitting hole position. The detection disk may be a microfluidic disk or other form of detection disk for accommodating samples to be tested. Different detection holes can accommodate different samples to be tested.

[0097] The rotary drive mechanism is used to drive the detection disk and the light shielding disk to perform synchronous rotation around the rotation axis in a plane perpendicular to the same optical path, so that the combined incident light beam passes through the corresponding groups of light-transmitting holes and detection holes in sequence to obtain each combined output light beam.

[0098] The first detection module is used to detect the pulse signal of the first light beam based on each combined output light beam, and send the pulse signal of the first light beam to the control device.

[0099] The second detection module is used to detect the energy of the preset spectral segments based on each combined output light beam, and send the energy of each preset spectral segment to the control device.

[0100] The control device is used to determine the test samples contained in each detection hole according to the pulse signal of the first light beam, and to determine the concentration of each test sample according to the energy of each preset spectral segment. Specifically, the pulse waveform corresponding to the target detection hole and the pulse waveform corresponding to other detection holes can be distinguished according to the pulse signal of the first light beam. And because each pulse waveform in the pulse signal of the first light beam and the energy of each preset spectral segment have a one-to-one correspondence in time, the energy of the preset spectral segment corresponding to each detection hole is determined. Furthermore, since different detection holes contain different detection samples, the test sample contained in each detection hole can be determined according to the pre-recorded correspondence between the detection holes and the test samples. After combining the energy of the preset spectral segment corresponding to each detection hole, the energy of the preset spectral segment corresponding to each test sample can be determined. After converting the energy of the preset spectral segment into concentration information, the concentration information of each test sample can be obtained.

[0101] In a specific implementation, the first detection module includes: a second color separation component and a detector; the second color separation component is used to separate the first light beam based on each combined output light beam; the detector is used to receive each separated first light beam, generate a pulse signal of the first light beam, and send the pulse signal of the first light beam to the control device.

[0102] In a specific implementation, the second color separation component is arranged on the optical path from the combined output light beam to the detector, and is specifically used to separate the first light beam and the second light beam from each combined output light beam; the second detection module is specifically used to receive each separated second light beam, detect the energy of a preset spectral segment from each second light beam, and send the energy of each preset spectral segment to the control device.

[0103] In a specific implementation, the first color separation component transmits the first light beam and reflects the second light beam, the first light beam and the second light beam are symmetrically incident on the first color separation component, and the incident angles are both 45 degrees; the second color separation component transmits the first light beam and reflects the second light beam, and the angle between the second color separation component and the first color separation component is 90 degrees or 0 degrees.

[0104] In a specific implementation, the second detection module is arranged on the optical path from the combined output light beam to the second color separation component, and is specifically used to receive each combined output light beam, separate the light beam of a preset spectral segment from each combined output light beam to form a residual light beam, detect the energy of each separated light beam, and send the energy of each preset spectral segment to the control device; the second color separation component is arranged on the optical path from the residual light beam to the detector, and is specifically used to separate the first light beam from each residual light beam.

[0105] In one specific implementation, the first color separation component transmits the first light beam and reflects the second light beam, the first light beam and the second light beam are symmetrically incident on the first color separation component, and the incident angles are both 45 degrees; the second color separation component reflects the first light beam, and the angle between the second color separation component and the first color separation component is 90 degrees or 0 degrees.

[0106] In one specific implementation, the first color separation component reflects the first light beam and transmits the second light beam, the first light beam and the second light beam are symmetrically incident on the first color separation component, and the incident angles are both 45 degrees; the second color separation component reflects the first light beam, and the angle between the second color separation component and the first color separation component is 90 degrees or 0 degrees.

[0107] In a specific implementation, the light shielding disc is an aperture disc, and the light-transmitting hole is an aperture.

[0108] In one specific implementation, the aperture disk is fixedly or detachably mounted on the rotating shaft of the rotary drive mechanism, and the detection disk is detachably mounted on the side of the aperture disk away from the rotating shaft; or, the detection disk is detachably mounted on the rotating shaft of the rotary drive mechanism, and the aperture disk is detachably mounted on the side of the detection disk away from the rotating shaft.

[0109] In one specific implementation, the light shielding disc is a light shielding film formed by coating a light shielding material on one side of the detection disc, and the light transmission hole is an area of ​​the detection disc not coated with the light shielding material. Alternatively, the light shielding disc is a light shielding film made of the light shielding material, and the light transmission hole is a through hole formed in the light shielding film; the light shielding film is fixedly or removably attached to one side of the detection disc.

[0110] In a specific implementation, the pulse signal of the first light beam is a trapezoidal pulse signal; when the control device determines the samples to be tested contained in each detection hole based on the pulse signal of the first light beam, it is specifically used to distinguish the target detection hole corresponding to the target light-transmitting hole and the other detection holes corresponding to each other light-transmitting hole in each detection hole according to the width of each trapezoidal pulse in the trapezoidal pulse signal; according to the rotation direction of the rotating shaft and the sorting of each sample to be tested corresponding to the rotation direction, determine the sample to be tested corresponding to the target detection hole and the sample to be tested corresponding to each other detection hole.

[0111] In a specific implementation, the second light source component discontinuously emits the second light beam; the control device is also used to control the first light source component to emit the first light beam, and when the first detection module detects the pulse signal of the first light beam, controls the second light source component to emit the second light beam, so that the first color separation component integrates the optical path of the first light beam and the optical path of the second light beam into the same optical path to obtain a combined incident light beam.

[0112] For the description of other structures, please refer to the relevant description of the centrifugal microfluidic biochemical analyzer mentioned above, which will not be repeated here. It should be noted that the color separation components in each embodiment of the present application can include positional spectroscopic devices such as gratings and prisms, and can also include components (assemblies) that use coatings to achieve spectroscopic effects.

[0113] It should be noted that the various embodiments in this specification are described in a progressive manner, and each embodiment focuses on the differences from other embodiments. The same or similar parts between the various embodiments can be referred to in detail. With respect to the above description of the disclosed embodiments, the features described in the various embodiments in this specification can be replaced or combined with each other, so that professional and technical personnel in this field can implement or use this application.

[0114] It should also be noted that, in this document, relational terms such as first and second, etc., are used only to distinguish one entity or operation from another entity or operation, and do not necessarily require or imply any such actual relationship or order between these entities or operations. Moreover, the terms "comprises," "comprising," or any other variations thereof are intended to cover non-exclusive inclusion, such that a process, method, article, or device comprising a series of elements includes not only those elements, but also other elements not explicitly listed, or elements inherent to such process, method, article, or device. In the absence of further limitations, an element defined by the phrase "comprising a ..." does not exclude the presence of additional identical elements in the process, method, article, or device comprising the aforementioned elements.

[0115] The above description of the disclosed embodiments is intended to enable one skilled in the art to implement or use the present invention. Various modifications to these embodiments will be readily apparent to one skilled in the art, and the general principles defined herein may be implemented in other embodiments without departing from the spirit or scope of the present invention. Therefore, the present invention is not limited to the embodiments shown herein but is intended to conform to the widest scope consistent with the principles and novel features disclosed herein.

Claims

1. A centrifugal microfluidic biochemical analyzer, characterized in that: include: A first light source assembly, a second light source assembly, a first color separation assembly, a rotation drive mechanism, a first detection module, a second detection module, and a control device; The first light source assembly is used to emit a first light beam, and the second light source assembly is used to emit a second light beam, wherein a spectral range of the first light beam does not overlap with a preset spectral range of the second light beam used for detecting the sample to be tested; The first color separation component is used to integrate the optical path of the first light beam and the optical path of the second light beam into the same optical path to obtain a combined incident light beam; The rotary drive mechanism includes a rotating shaft, and the rotating shaft is used to mount the microfluidic disk and the optical shielding plate, wherein the microfluidic disk is provided with a plurality of detection holes along a circumferential direction, and the optical shielding plate is provided with a plurality of light-transmitting holes along a circumferential direction, and the size of a target light-transmitting hole among the plurality of light-transmitting holes is different from the sizes of the other light-transmitting holes other than the target light-transmitting hole, and when the microfluidic disk and the optical shielding plate are mounted on the rotating shaft, the positions of the detection holes and the light-transmitting holes correspond one-to-one; The rotary drive mechanism is used to drive the rotation axis to rotate so as to drive the microfluidic disc to rotate, so as to prepare the test samples required for the detection items, wherein the test samples required for each detection item are placed in the corresponding detection holes, and to drive the microfluidic disc and the light shielding disc to perform synchronous rotational motion around the rotation axis in a plane perpendicular to the same optical path, so that the combined incident light beam passes through each group of the light-transmitting holes and the detection holes having a corresponding relationship in sequence to obtain each combined output light beam; The first detection module is configured to detect a pulse signal of the first light beam based on each of the combined outgoing light beams, and send the pulse signal of the first light beam to the control device; The second detection module is used to detect the energy of the preset spectral band based on each of the combined output light beams, and send the energy of each of the preset spectral bands to the control device; The control device is used to determine the detection item corresponding to each pulse waveform in the pulse signal of the first light beam, and determine the detection result of the sample to be tested under each detection item according to the detection item corresponding to each pulse waveform and the energy of each preset spectral segment.

2. The centrifugal microfluidic biochemical analyzer according to claim 1, characterized in that: The first detection module includes: a second color separation component and a detector; The second color separation component is used to separate the first light beam based on each of the combined output light beams; The detector is used to receive each separated first light beam, generate a pulse signal of the first light beam, and send the pulse signal of the first light beam to the control device.

3. The centrifugal microfluidic biochemical analyzer according to claim 2, characterized in that: The second color separation component is arranged on the optical path from the combined outgoing light beam to the detector, and is specifically used to separate the first light beam and the second light beam from each of the combined outgoing light beams; The second detection module is specifically configured to receive each separated second light beam, detect energy of a preset spectrum segment from each second light beam, and send the energy of each preset spectrum segment to the control device.

4. The centrifugal microfluidic biochemical analyzer according to claim 3, characterized in that: The first color separation component transmits the first light beam and reflects the second light beam, the first light beam and the second light beam are symmetrically incident on the first color separation component, and the incident angles are both 45 degrees; The second color separation component transmits the first light beam and reflects the second light beam, and an angle between the second color separation component and the first color separation component is 90 degrees or 0 degrees.

5. The centrifugal microfluidic biochemical analyzer according to claim 2, characterized in that: The second detection module is disposed on an optical path from the combined outgoing light beam to the second color separation component, and is specifically configured to receive each of the combined outgoing light beams, separate light beams of preset spectral segments from each of the combined outgoing light beams to form residual light beams, detect the energy of each separated light beam, and send the energy of each of the preset spectral segments to the control device; The second color separation component is arranged on the optical path from the remaining light beams to the detector, and is specifically used to separate the first light beam from each of the remaining light beams.

6. The centrifugal microfluidic biochemical analyzer according to claim 5, characterized in that: The first color separation component transmits the first light beam and reflects the second light beam, the first light beam and the second light beam are symmetrically incident on the first color separation component, and the incident angles are both 45 degrees; The second color separation component reflects the first light beam, and an included angle between the second color separation component and the first color separation component is 90 degrees or 0 degrees.

7. The centrifugal microfluidic biochemical analyzer according to claim 5, characterized in that: The first color separation component reflects the first light beam and transmits the second light beam, the first light beam and the second light beam are symmetrically incident on the first color separation component, and the incident angles are both 45 degrees; The second color separation component reflects the first light beam, and an included angle between the second color separation component and the first color separation component is 90 degrees or 0 degrees.

8. The centrifugal microfluidic biochemical analyzer according to claim 2, characterized in that: The first detection module further includes a first light collecting component; The first light collecting component is arranged on the optical path from the separated first light beam to the detector, and is used to reduce the divergence of the separated first light beam.

9. The centrifugal microfluidic biochemical analyzer according to claim 2, characterized in that: The first color separation component includes a dichroic mirror, a grating or a dispersion prism; the second color separation component includes a dichroic mirror, a grating or a dispersion prism.

10. The centrifugal microfluidic biochemical analyzer according to claim 1, characterized in that: The light shielding disc is an aperture disc, and the light-transmitting hole is an aperture.

11. The centrifugal microfluidic biochemical analyzer according to claim 10, characterized in that: The aperture disk is fixedly or detachably mounted on the rotation axis of the rotation drive mechanism, and the microfluidic disk is detachably mounted on a side of the aperture disk away from the rotation axis.

12. The centrifugal microfluidic biochemical analyzer according to claim 10, characterized in that: The microfluidic disk is detachably mounted on the rotating shaft of the rotary drive mechanism, and the aperture disk is detachably mounted on a side of the microfluidic disk away from the rotating shaft.

13. The centrifugal microfluidic biochemical analyzer according to claim 1, characterized in that: The light shielding disc is a light shielding film formed by coating a light shielding material on one side of the microfluidic disc, and the light-transmitting hole is an area of ​​the microfluidic disc that is not coated with the light shielding material.

14. The centrifugal microfluidic biochemical analyzer according to claim 1, characterized in that: The light-shielding disc is a light-shielding film made of light-shielding material, and the light-transmitting hole is a through hole opened by the light-shielding film; the light-shielding film is fixedly or detachably attached to one side of the microfluidic disc.

15. The centrifugal microfluidic biochemical analyzer according to claim 1, characterized in that: The light-transmitting holes are circular light-transmitting holes, and the multiple light-transmitting holes are evenly distributed along the circumferential direction of the light-shielding disc; the size of the target light-transmitting hole is larger than the size of the other light-transmitting holes, and the sizes of the other light-transmitting holes are consistent.

16. The centrifugal microfluidic biochemical analyzer according to claim 15, characterized in that: Each of the light-transmitting holes is larger than the corresponding detection hole.

17. The centrifugal microfluidic biochemical analyzer according to claim 16, characterized in that: The pulse signal of the first light beam is a trapezoidal pulse signal; When determining the detection items corresponding to each pulse waveform in the pulse signal of the first light beam, the control device is specifically used to distinguish the target trapezoidal pulse corresponding to the target light-transmitting hole and the other trapezoidal pulses corresponding to each of the other light-transmitting holes in each trapezoidal pulse according to the width of each trapezoidal pulse in the trapezoidal pulse signal; and determine the detection items corresponding to the target trapezoidal pulse and the detection items corresponding to each of the other trapezoidal pulses according to the rotation direction of the rotating shaft and the sorting of the detection items corresponding to the rotation direction.

18. The centrifugal microfluidic biochemical analyzer according to claim 1, characterized in that: The second light source assembly emits the second light beam discontinuously; The control device is also used to control the first light source assembly to emit a first light beam, and when the first detection module detects the pulse signal of the first light beam, control the second light source assembly to emit the second light beam, so that the first color separation assembly integrates the light path of the first light beam and the light path of the second light beam into the same light path to obtain a combined incident light beam.

19. The centrifugal microfluidic biochemical analyzer according to claim 1, characterized in that: The first light source assembly includes an infrared light source and a second light collecting assembly; The infrared light source is used to emit an initial infrared light beam; the second light collecting component is used to reduce the divergence of the initial xenon lamp light beam to obtain the first light beam.

20. The centrifugal microfluidic biochemical analyzer according to claim 1, characterized in that: The second light source assembly includes a xenon lamp light source and a third light collecting assembly; The xenon lamp light source is used to emit an initial xenon lamp light beam; the third light collecting component is used to reduce the divergence of the initial xenon lamp light beam to obtain the second light beam.

21. A concentration detection system, characterized in that: include: A first light source assembly, a second light source assembly, a first color separation assembly, a rotation drive mechanism, a first detection module, a second detection module, and a control device; The first light source assembly is used to emit a first light beam, and the second light source assembly is used to emit a second light beam, wherein a spectral range of the first light beam does not overlap with a preset spectral range of the second light beam used to detect the concentration of the sample to be tested; The first color separation component is used to integrate the optical path of the first light beam and the optical path of the second light beam into the same optical path to obtain a combined incident light beam; The rotary drive mechanism includes a rotating shaft, and the rotating shaft is used to mount the detection disk and the optical shielding plate, wherein the detection disk is provided with a plurality of detection holes along the circumferential direction, and the detection holes are used to accommodate samples to be tested, and the optical shielding plate is provided with a plurality of light-transmitting holes along the circumferential direction, and the size of a target light-transmitting hole among the plurality of light-transmitting holes is different from the sizes of the other light-transmitting holes other than the target light-transmitting hole, and when the detection disk and the optical shielding plate are mounted on the rotating shaft, the positions of the detection holes and the light-transmitting holes correspond one-to-one; The rotation drive mechanism is used to drive the detection disk and the light shielding disk to perform synchronous rotation around the rotation axis in a plane perpendicular to the same optical path, so that the combined incident light beam passes through the corresponding groups of light-transmitting holes and the detection holes in sequence to obtain each combined outgoing light beam; The first detection module is configured to detect a pulse signal of the first light beam based on each of the combined outgoing light beams, and send the pulse signal of the first light beam to the control device; The second detection module is used to detect the energy of the preset spectral band based on each of the combined output light beams, and send the energy of each of the preset spectral bands to the control device; The control device is used to determine the sample to be tested contained in each of the detection holes according to the pulse signal of the first light beam, and to determine the concentration of each of the sample to be tested according to the energy of each of the preset spectral segments.

22. The concentration detection system according to claim 21, characterized in that: The first detection module includes: a second color separation component and a detector; The second color separation component is used to separate the first light beam based on each of the combined output light beams; The detector is used to receive each separated first light beam, generate a pulse signal of the first light beam, and send the pulse signal of the first light beam to the control device.

23. The concentration detection system according to claim 22, characterized in that: The second color separation component is arranged on the optical path from the combined outgoing light beam to the detector, and is specifically used to separate the first light beam and the second light beam from each of the combined outgoing light beams; The second detection module is specifically configured to receive each separated second light beam, detect energy of a preset spectrum segment from each second light beam, and send the energy of each preset spectrum segment to the control device.

24. The concentration detection system according to claim 23, characterized in that: The first color separation component transmits the first light beam and reflects the second light beam, the first light beam and the second light beam are symmetrically incident on the first color separation component, and the incident angles are both 45 degrees; The second color separation component transmits the first light beam and reflects the second light beam, and an angle between the second color separation component and the first color separation component is 90 degrees or 0 degrees.

25. The concentration detection system according to claim 22, characterized in that: The second detection module is disposed on an optical path from the combined outgoing light beam to the second color separation component, and is specifically configured to receive each of the combined outgoing light beams, separate light beams of preset spectral segments from each of the combined outgoing light beams to form residual light beams, detect the energy of each separated light beam, and send the energy of each of the preset spectral segments to the control device; The second color separation component is arranged on the optical path from the remaining light beams to the detector, and is specifically used to separate the first light beam from each of the remaining light beams.

26. The concentration detection system according to claim 25, characterized in that: The first color separation component transmits the first light beam and reflects the second light beam, the first light beam and the second light beam are symmetrically incident on the first color separation component, and the incident angles are both 45 degrees; The second color separation component reflects the first light beam, and an included angle between the second color separation component and the first color separation component is 90 degrees or 0 degrees.

27. The concentration detection system according to claim 25, characterized in that: The first color separation component reflects the first light beam and transmits the second light beam, the first light beam and the second light beam are symmetrically incident on the first color separation component, and the incident angles are both 45 degrees; The second color separation component reflects the first light beam, and an included angle between the second color separation component and the first color separation component is 90 degrees or 0 degrees.

28. The concentration detection system according to claim 21, characterized in that: The light shielding disc is an aperture disc, and the light-transmitting hole is an aperture.

29. The concentration detection system according to claim 28, characterized in that: The aperture disc is fixedly or detachably mounted on the rotating shaft of the rotary drive mechanism, and the detection disc is detachably mounted on a side of the aperture disc away from the rotating shaft; or, The detection disk is detachably mounted on the rotating shaft of the rotation drive mechanism, and the aperture disk is detachably mounted on a side of the detection disk away from the rotating shaft.

30. The concentration detection system according to claim 21, characterized in that: The light shielding disc is a light shielding film formed by coating a light shielding material on one side of the detection disc, and the light-transmitting hole is an area of ​​the detection disc that is not coated with the light shielding material.

31. The concentration detection system according to claim 21, characterized in that: The light shielding disc is a light shielding film made of light shielding material, and the light-transmitting hole is a through hole opened by the light shielding film; the light shielding film is fixedly or detachably attached to one side of the detection disc.

32. The concentration detection system according to claim 21, characterized in that: The pulse signal of the first light beam is a trapezoidal pulse signal; When the control device determines the samples to be tested contained in each of the detection holes based on the pulse signal of the first light beam, it is specifically used to distinguish the target detection holes corresponding to the target light-transmitting holes and the other detection holes corresponding to each of the other light-transmitting holes in the detection holes based on the width of each trapezoidal pulse in the trapezoidal pulse signal; and determine the samples to be tested corresponding to the target detection holes and the samples to be tested corresponding to each of the other detection holes based on the rotation direction of the rotating shaft and the sorting of the samples to be tested corresponding to the rotation direction.

33. The concentration detection system according to claim 21, characterized in that: The second light source assembly emits the second light beam discontinuously; The control device is also used to control the first light source assembly to emit a first light beam, and when the first detection module detects the pulse signal of the first light beam, control the second light source assembly to emit the second light beam, so that the first color separation assembly integrates the light path of the first light beam and the light path of the second light beam into the same light path to obtain a combined incident light beam.

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