Analyser with multiple detection light paths

Abstract

This application discloses an analyzer with multiple detection optical paths, comprising a body, a microfluidic detection chip, and detection components. The microfluidic detection chip has a first detection slot and multiple second detection slots. The first detection slot contains at least one detection reagent for blood gas detection, and different second detection slots contain at least one detection reagent for biochemical detection, immunological detection, and coagulation detection. The detection components include a first detection element and a second detection element. The first detection element is configured to emit a signal to the first detection slot and receive the signal reflected from the first detection slot, to perform blood gas detection on the sample in the first detection slot. The second detection element is configured to emit different signals to different second detection slots and receive the signals reflected from the second detection slots, to perform biochemical detection and / or immunological detection and / or coagulation detection on the sample. This application solves the problem of limited detection function in related technologies' analyzers.

Description

Technical Field

[0001] This application relates to the field of medical device technology, and more specifically, to an analyzer with multiple detection optical paths. Background Technology

[0002] In related technologies, analyzers are typically equipped with different microfluidic detection chips to perform single-item tests on samples, such as blood gas analysis, biochemistry analysis, immunology analysis, and coagulation analysis. However, existing analyzers offer only one detection function when performing different tests on blood. Summary of the Invention

[0003] The main objective of this application is to provide an analyzer with multiple detection optical paths to solve the problem that analyzers in related technologies have limited detection functions when performing different tests on blood.

[0004] According to one aspect of this application, an analyzer having multiple detection optical paths is provided, comprising: Organism; A microfluidic detection chip is rotatably and replaceably disposed on the body. The microfluidic detection chip has a first detection slot and a plurality of second detection slots. The first detection slot contains at least a detection reagent for blood gas detection, and different second detection slots contain at least a detection reagent for biochemical detection, immune detection and coagulation detection. A detection component is disposed on the body. The detection component includes a first detection component and a second detection component. The first detection component is configured to transmit a signal to a first detection slot and receive a signal reflected from the first detection slot to perform blood gas detection on a sample in the first detection slot. The second detection component is configured to transmit different signals to different second detection slots and receive signals reflected from the second detection slots to perform biochemical and / or immunological and / or coagulation detection on the sample. The first detection component includes a first emitting part and a first receiving part. The first emitting part is disposed on the top of the microfluidic detection chip and includes multiple first light sources, each of which emits light with a different wavelength. The first receiving part is disposed on the top of the first emitting part. The first detection component is configured such that when a sample is injected into the microfluidic detection chip and the microfluidic detection chip is not rotated, each of the first light sources emits a light signal to the first detection slot, and the first receiving part is used to receive the light signal reflected in the first detection slot to perform different blood gas detections on the sample. The second detection component includes a second emitting part and a second receiving part. The second emitting part is disposed at the bottom of the microfluidic detection chip and includes multiple second light sources, each emitting light with a different wavelength. The second receiving part is disposed at the top of the microfluidic detection chip. The second detection component is configured such that, after a sample is injected into the microfluidic detection chip, during the rotation of the microfluidic detection chip, each of the second detection slots sequentially passes through each of the second light sources along the rotation direction of the microfluidic detection chip; when a second detection slot corresponds to a second light source, the second light source emits a light signal to the second detection slot, and the second receiving part is used to receive the light signal reflected from the second detection slot for biochemical and / or immunological and / or coagulation detection of the sample.

[0005] In some embodiments, the first detection slot is disposed at the center of the microfluidic detection chip, and a plurality of second detection slots are disposed at the edge of the microfluidic detection chip, and the plurality of second detection slots are spaced apart along the circumferential direction of the microfluidic detection chip; Along the height direction of the analyzer, the first detection component is disposed on the body and located at the top of the first detection slot, the second detection component is disposed on opposite sides of the microfluidic detection chip, and the microfluidic detection chip has the ability to rotate to a detection position that corresponds to the second detection slot and the second detection component.

[0006] In some embodiments, the first detection component further includes a detection body, which is connected to the first transmitting unit and located between the first receiving unit and the microfluidic detection chip. The detection body has a plurality of detection channels spaced apart, and each detection channel is disposed on the top of the first detection slot. The first light source is disposed in the detection channel in a corresponding manner. The detection channel is used to transmit the light signal emitted by the first light source to the first detection slot and to transmit the light signal reflected by the first detection slot to the first receiving unit.

[0007] In some embodiments, the detection channel includes a first channel and a second channel, a first end of the first channel is connected to the second channel, a first end of the second channel is located at the top of the first detection slot, and the second channel is used to transmit the light signal reflected in the first detection slot to the first detection component; The first emitting part is disposed at the second end of the first channel. The first emitting part is used to emit light of different wavelengths to different channels of the first channel and to allow the light to enter the first detection slot through the first channel and the second channel.

[0008] In some embodiments, the second detection component further includes a first support portion, which is disposed between the microfluidic detection chip and a plurality of second light sources. The first support portion has a plurality of emission channels, and the plurality of second light sources are disposed in the plurality of emission channels in a corresponding manner. The second detection component includes a second support portion, which is disposed on the top of the microfluidic detection chip. The second support portion has multiple receiving channels, which are arranged one-to-one with the transmitting channels along the height direction of the analyzer. The second receiving portion is disposed on the top of the second transmitting portion, and the first detection component is disposed on the second support portion.

[0009] In some embodiments, the analyzer further includes a dustproof component disposed between the microfluidic detection chip and the emission channel, and the dustproof component covers the side of the emission channel closest to the microfluidic detection chip.

[0010] In some embodiments, the body has a mounting cavity, and the analyzer with multiple detection optical paths further includes a first driving component, a bracket component, and a position detection component. The bracket component has a first position received in the mounting cavity and a second position protruding from the mounting cavity by a predetermined distance. The first driving component is connected to the bracket component to drive the bracket component to switch between the first position and the second position. The microfluidic detection chip is rotatably and replaceably disposed in the bracket component. The position detection component is disposed in the mounting cavity and is electrically connected to the first driving component. When the position detection component detects that the bracket assembly has reached the second position, the position detection component transmits a signal to the first drive component to cause the first drive component to stop driving the bracket assembly.

[0011] In some embodiments, the analyzer having multiple detection optical paths further includes a second driving component and a tray, the second driving component being disposed on the body, the tray being disposed on the second driving component, the second driving component driving the tray to rotate, and the microfluidic detection chip being detachably disposed on the tray; The microfluidic detection chip includes a transparent microfluidic detection chip, and the tray has a plurality of first clearance holes, which are arranged one-to-one with a plurality of second detection slots.

[0012] In some embodiments, the body is provided with an installation cavity, and an opening is provided on a first side of the body along a first direction. The opening communicates with the installation cavity, and the microfluidic detection chip enters the installation cavity through the opening. The first detection component and the second detection component are both disposed on the second side of the body opposite to the first side. The analyzer also includes a first heat dissipation component, which is located on top of the first detection component and the second detection component, and is used at least to dissipate heat from the first detection component.

[0013] In some embodiments, the body is provided with an installation cavity, and an opening is provided on a first side of the body along a first direction. The opening communicates with the installation cavity, and the microfluidic detection chip enters the installation cavity through the opening. The second detection component includes a second transmitting part disposed in the mounting cavity, and a second heat dissipation component is disposed at the opening. The second heat dissipation component is used to dissipate heat from the second driving assembly and the second transmitting part.

[0014] Unlike related technologies, the analyzer of this application is equipped with a first detection slot and multiple second detection slots. The first detection slot contains reagents for blood gas analysis, and different second detection slots contain at least reagents for biochemical analysis, immunoassay, and coagulation analysis. The analyzer also includes a first detection component and a second detection component. The first detection component transmits signals to the first detection slot and receives signals reflected from it, enabling blood gas analysis on at least the sample within the first detection slot. In other words, the first detection component can simultaneously transmit multiple different signals to the first detection slot and receive multiple different signals reflected from it, allowing the analyzer to perform different blood gas analysis on the sample at the same time. Furthermore, the second detection component transmits different signals to different second detection slots and receives signals reflected from them, enabling biochemical analysis and / or immunoassay and / or coagulation analysis on the sample. Therefore, the arrangement of the second detection component and multiple second detection slots allows the analyzer to perform at least one of the following tests on the sample, in addition to blood gas analysis: biochemical analysis, immunoassay, and coagulation analysis. Compared to related technologies, the analyzer in this application has rich detection functions and can quickly perform multiple tests on samples. Attached Figure Description

[0015] The accompanying drawings, which are included to provide a further understanding of this application and form part of this application, are illustrative and descriptive, serving to explain this application and do not constitute an undue limitation thereof. In the drawings: Figure 1 This is a connection diagram of an analyzer with multiple detection optical paths disclosed in an embodiment of this application; Figure 2This is a partial structural diagram of an analyzer with multiple detection optical paths disclosed in an embodiment of this application (with the second heat dissipation component and the first driving component removed). Figure 3 for Figure 2 Enlarged schematic diagram of region I in the middle; Figure 4 This is an exploded structural diagram of the detection subject disclosed in the embodiments of this application; Figure 5 This is a cross-sectional view of the detection subject disclosed in the embodiments of this application; Figure 6 This is a partial structural schematic diagram of an analyzer with multiple detection optical paths disclosed in an embodiment of this application (with the first detection component removed). Figure 7 This is a structural diagram of the second base of the analyzer with multiple detection optical paths disclosed in an embodiment of this application; Figure 8 This is a structural diagram of the microfluidic detection chip of the analyzer with multiple detection optical paths disclosed in the embodiments of this application; Figure 9 This is a structural diagram of the first base of the analyzer with multiple detection optical paths disclosed in an embodiment of this application; Figure 10 This is a structural diagram of the analyzer housing with multiple detection optical paths disclosed in an embodiment of this application; Figure 11 for Figure 9 Enlarged view of region I in the middle; Figure 12 This is a partial cross-sectional view of a structure with multiple detection optical paths disclosed in an embodiment of this application; Figure 13 This is a schematic diagram of the structure of the tray disclosed in an embodiment of this application.

[0016] The above figures include the following reference numerals: 10. Body; 11. Second base; 20. Microfluidic detection chip; 21. First detection slot; 22. Second detection slot; 30. First detection component; 31. Detection body; 32. First transmitter; 33. First receiver; 40. Second detection component; 41. Second transmitter; 42. Second receiver; 43. First support; 44. Second support; 50. Reagent kit; 61. First heat dissipation component; 62. Second heat dissipation component; 70. Dustproof component; 71. Dustproof part; 72. Light-transmitting part; 80. Bracket assembly; 81. Frame; 82. First base 83. Base; 91. Tray; 92. First drive assembly; 93. Second drive assembly; 94. Position detection assembly; 101. Mounting cavity; 301. Detection channel; 311. First block; 312. Second block; 431. Transmitting channel; 432. Receiving channel; 501. Second clearance hole; 711. Third clearance hole; 831. First clearance hole; 3011. First channel; 3012. Second channel; 4311. First branch channel; 4312. Second branch channel; 4411. Fourth filter; 30121. First segment; 30122. Second segment. Detailed Implementation

[0017] It should be noted that, unless otherwise specified, the embodiments and features described in this application can be combined with each other. This application will now be described in detail with reference to the accompanying drawings and embodiments.

[0018] It should be noted that the terminology used herein is for the purpose of describing particular embodiments only and is not intended to limit the exemplary embodiments according to this application. As used herein, the singular form is intended to include the plural form as well, unless the context clearly indicates otherwise. Furthermore, it should be understood that when the terms "comprising" and / or "including" are used in this specification, they indicate the presence of features, steps, operations, devices, components, and / or combinations thereof.

[0019] Unless otherwise specifically stated, the relative arrangement, numerical expressions, and values ​​of the components and steps described in these embodiments do not limit the scope of this application. It should also be understood that, for ease of description, the dimensions of the various parts shown in the drawings are not drawn to actual scale. Techniques, methods, and devices known to those skilled in the art may not be discussed in detail, but where appropriate, such techniques, methods, and devices should be considered part of the specification. In all examples shown and discussed herein, any specific values ​​should be interpreted as merely exemplary and not as limitations. Therefore, other examples of exemplary embodiments may have different values. It should be noted that similar reference numerals and letters in the following drawings denote similar items; therefore, once an item is defined in one drawing, it need not be further discussed in subsequent drawings.

[0020] As described in the background section, in related technologies, due to the structural design of the analyzer and its microfluidic detection chip, the analyzer can only perform one of the following tests on a blood sample (blood) at a time: blood gas, biochemistry, immunology, and coagulation. When at least two of these tests are required, the microfluidic detection chip needs to be constantly replaced during the testing process. Furthermore, the detection optical path on the analyzer may be insufficient for the tests, necessitating the use of an additional detection optical path. This means that analyzers in related technologies have limited detection capabilities.

[0021] To address the issues in the relevant technologies, see [link / reference]. Figures 1 to 13 As shown in the figure, this application embodiment provides an analyzer with multiple detection optical paths. The analyzer includes a body 10, a microfluidic detection chip 20, and detection components.

[0022] The microfluidic detection chip 20 is rotatably and replaceably mounted on the body 10. The microfluidic detection chip 20 has a first detection slot 21 and multiple second detection slots 22. The first detection slot 21 contains at least one reagent for blood gas detection, and different second detection slots 22 contain at least one reagent for biochemical detection, immunological detection, and coagulation detection. A detection assembly is mounted on the body 10 and includes a first detection component 30 and a second detection component 40. The first detection component 30 is configured to emit signals to the first detection slot 21 and receive signals reflected from the first detection slot 21, to perform blood gas detection on the sample in at least the first detection slot 21. The second detection component 40 is configured to emit different signals to different second detection slots 22 and receive signals reflected from the second detection slots 22, to perform biochemical and / or immunological and / or coagulation detection on the sample.

[0023] It should be noted that "performing biochemical and / or immunological and / or coagulation tests on the sample" refers to one of the following: performing biochemical tests on the sample, performing immunological tests on the sample, performing coagulation tests on the sample, performing both biochemical and immunological tests on the sample, performing both biochemical and coagulation tests on the sample, performing both immunological and coagulation tests on the sample, and performing either biochemical, immunological, or coagulation tests on the sample.

[0024] Furthermore, the first detection component 30 includes a first emitting part 32 and a first receiving part 33. The first emitting part 32 is disposed on top of the microfluidic detection chip 20, and includes multiple first light sources, each emitting light with a different wavelength. The first receiving part 33 is disposed on top of the first emitting part 32. The first detection component 30 is configured such that when a sample is injected into the microfluidic detection chip 20 and the microfluidic detection chip 20 is not rotated, each of the first light sources emits an optical signal to the first detection slot 21, and the first receiving part 33 receives the optical signal reflected from the first detection slot 21 to perform different blood gas detections on the sample.

[0025] Specifically, after the sample is injected into the microfluidic detection chip 20, multiple first light sources emit light signals to the first detection slot 21. The light from different first light sources has different wavelengths. After the sample in the first detection slot 21 receives light signals of different wavelengths, it will release excitation light of different wavelengths. After the excitation light of different wavelengths is received by the first detection component 30, multiple blood gas detection parameters of the sample can be measured.

[0026] Meanwhile, the second detection component 40 includes a second emitting part 41 and a second receiving part 42. The second emitting part 41 is disposed at the bottom of the microfluidic detection chip 20 and includes multiple second light sources, each emitting light with a different wavelength. The second receiving part 42 is disposed at the top of the microfluidic detection chip 20. The second detection component 40 is configured such that, after a sample is injected into the microfluidic detection chip 20, during the rotation of the microfluidic detection chip 20, each second detection slot 22 passes sequentially through each second light source along the rotation direction of the microfluidic detection chip 20; when a second detection slot 22 corresponds to a second light source, the second light source emits a light signal to the second detection slot 22, and the second receiving part 42 receives the light signal reflected from the second detection slot 22 for biochemical and / or immunological and / or coagulation detection of the sample.

[0027] It should be noted that the phrase "each second detection slot 22 passes through each second light source sequentially along the rotation direction of the microfluidic detection chip 20" in this application means that during the rotation of the microfluidic detection chip 20, the first second detection slot 22 will rotate first to correspond with the first second light source, completing the precise docking between the two; after the microfluidic detection chip 20 continues to rotate a certain angle, the first second detection slot 22 will leave the illumination area of ​​the first second light source and gradually rotate to correspond with the second second light source. At the same time, the second second detection slot 22 will rotate synchronously to correspond with the first second light source, and so on. That is to say, the first second detection slot 22 will sequentially complete the docking with the first second light source, the second second light source, ... up to the Nth second light source, where N is the total number of second light sources. Each subsequent second detection slot 22 will pass through each second light source sequentially along the rotation direction of the microfluidic detection chip 20 in the exact same order as the first second detection slot 22, achieving precise correspondence.

[0028] Specifically, when the microfluidic chip rotates, the sample enters each of the second detection slots 22 under centrifugal force and mixes with the reagents in the second detection slots 22. When the second light source excites the sample in the second detection slot 22, the sample in the second detection slot 22 will release light of a specific wavelength, which is ultimately received by the second receiving unit 42. In this embodiment, since there are multiple second light sources, and the light emitted by different second light sources has different wavelengths, the excitation light generated in the second detection slot 22 will have different wavelengths after different wavelengths of light irradiate it. After receiving different excitation light, the second receiving unit 42 can obtain different parameters to perform at least one of the following tests on the sample: biochemical, immunological, or coagulation. In this embodiment, the second light source can be an LED lamp. Furthermore, it is known that biochemical detection, immunological detection, and coagulation detection all include multiple items. For example, biochemical tests include tests for potassium ions, sodium ions, chloride ions, base excess, blood glucose, lactate, blood urea nitrogen, creatine kinase, and hemoglobin in a sample. Immunological tests include tests for C-reactive protein and atrial natriuretic peptide in a sample. Coagulation tests include tests for prothrombin time, fibrinogen, activated partial thromboplastin time, and D-dimer in a sample.

[0029] Unlike related technologies, the analyzer of this application is provided with a first detection slot 21 and multiple second detection slots 22. The first detection slot 21 contains test reagents for blood gas detection, and different second detection slots 22 contain at least test reagents for biochemical detection, immunological detection, and coagulation detection. Simultaneously, the analyzer of this application has a first detection component 30 and a second detection component 40. The first detection component 30 is used to transmit signals to the first detection slot 21 and receive signals reflected from the first detection slot 21, so as to perform blood gas detection on at least the sample in the first detection slot 21. That is, the first detection component 30 can simultaneously transmit multiple different signals to the first detection slot 21 and receive multiple different signals reflected from the first detection slot 21, so that the analyzer can detect different blood gas items of the sample at the same time. Furthermore, the second detection component 40 is used to transmit different signals to different second detection slots 22 and receive signals reflected from the second detection slots 22, so as to perform biochemical detection and / or immunological detection and / or coagulation detection on the sample. In other words, the arrangement of the second detection component 40 and multiple second detection slots 22 enables the analyzer to perform at least one of the following tests on samples: biochemical, immunological, and coagulation tests, in addition to blood gas analysis. Therefore, compared to related technologies, the analyzer of this application has richer detection functions and can quickly perform multiple tests on samples.

[0030] It is worth mentioning that blood gas analysis includes multiple detection items, such as pH value detection, O2 concentration detection, and CO2 concentration detection. When the sample and reagents are mixed in the first detection tank 21, different signals emitted by the first detection component 30 irradiate the mixed solution, causing the mixed solution to emit different signals. When the first detection component 30 receives these different signals, it can obtain the pH value, O2 partial pressure value, and CO2 partial pressure value of the sample based on these signals.

[0031] In some embodiments, a first detection groove 21 is disposed at the center of the microfluidic detection chip 20, and a plurality of second detection grooves 22 are disposed at the edges of the microfluidic detection chip 20, with the plurality of second detection grooves 22 spaced apart along the circumferential direction of the microfluidic detection chip 20. Along the height direction of the analyzer (as shown in the attached figure) Figure 2 (in the Z direction), the first detection component 30 is disposed on the body 10 and located on the top of the first detection slot 21, the second detection component 40 is disposed on opposite sides of the microfluidic detection chip 20, and the microfluidic detection chip 20 has the ability to rotate to a detection position that corresponds to the second detection slot 22 and the second detection component 40.

[0032] Specifically, the first detection component 30 and the second detection component 40 of this application are spatially offset, which can, to a certain extent, avoid interference between the signals emitted by the first detection component 30 and the signals emitted by the second detection component 40, thereby preventing inaccurate detection results from the analyzer. Simultaneously, the first detection slot 21 is located at the center of the microfluidic detection chip 20, and the first detection component 30 is located on top of the first detection slot 21. This arrangement is to meet the requirements for blood gas detection. It is known that blood gas detection is usually a static detection. After high-speed centrifugation, O2 and CO2 gases in the sample may escape, ultimately leading to inaccurate blood gas detection results. Therefore, the first detection slot 21 is located at the center of the microfluidic detection chip 20, enabling static detection of the sample. Furthermore, blood gas detection requires high precision. If the signal emitted by the first detection slot 21 needs to undergo multiple refractions before reaching the first detection component 30, this may result in excessive signal loss, leading to inaccurate detection results. Therefore, the first detection component 30 of this application is located directly above the first detection slot 21, allowing the first detection component 30 to quickly release or receive signals. On the other hand, after the microfluidic detection chip 20 rotates, it aligns multiple second detection slots 22 with the second detection component 40. In other words, after the microfluidic detection chip 20 rotates, the sample is drawn into the multiple second detection slots 22 by centrifugal force. When it is necessary to detect the sample in the second detection slot 22, rotating the microfluidic detection chip 20 allows the second detection slot 22 to receive the signal released by the second detection component 40, thereby transmitting a signal to the second detection component 40 to complete the detection.

[0033] In some embodiments, the first detection component 30 further includes a detection body 31, which is connected to the first transmitting unit 32 and located between the first receiving unit 33 and the microfluidic detection chip 20. The detection body 31 has a plurality of detection channels 301 spaced apart, each detection channel 301 being disposed on the top of the first detection slot 21. A first light source is correspondingly disposed in each detection channel 301. The detection channel 301 is used to transmit the light signal emitted by the first light source to the first detection slot 21 and to transmit the light signal reflected by the first detection slot 21 to the first receiving unit 33.

[0034] To prevent interference between the light from the various first light sources, this embodiment provides multiple detection channels 301 on the detection body 31. Each first light source is correspondingly positioned within a detection channel 301, ensuring that the light signals emitted by each light source to the first detection slot 21 are independent. Furthermore, the detection channels 301 can also transmit the light signals reflected from the first detection slot 21 to the first receiving unit 33. That is, when the first receiving unit 33 receives the light signals reflected from the first detection slot 21, the multiple detection channels 301 also prevent interference between the multiple light signals reflected from the first detection slot 21.

[0035] In some embodiments, the detection channel 301 includes a first channel 3011 and a second channel 3012. A first end of the first channel 3011 communicates with the second channel 3012, and a first end of the second channel 3012 is located at the top of the first detection groove 21. The second channel 3012 is used to transmit the light signal reflected within the first detection groove 21 to the first detection component 30. A first emitting part 32 is disposed at the second end of the first channel 3011. The first emitting part 32 is used to emit light of different wavelengths to different first channels 3011, and to allow the light to enter the first detection groove 21 through the first channel 3011 and the second channel 3012.

[0036] Specifically, when different blood gas tests need to be performed simultaneously, multiple first light sources are activated. Since each first light source emits light of different wavelengths, when light of different wavelengths enters the first detection slot 21 through different first channels 3011 and second channels 3012, the light of different wavelengths acts on the sample in the first detection slot 21, causing the sample to reflect different light signals. These different light signals then reach the first receiving unit 33 through the second channel 3012, allowing the first receiving unit 33 to analyze the detection parameters of different blood gas tests in the sample. Furthermore, when only a single blood gas test is needed, the first light source can be selectively activated to excite the sample with an appropriate wavelength. In some embodiments, the first light source includes an LED lamp.

[0037] In some embodiments, the detection body 31 includes a first block 311 and a second block 312 that are detachably connected, with the first block 311 located on top of the second block 312. A first channel 3011 is formed in the second block 312, and the second channel 3012 includes a first segment 30121 and a second segment 30122 that are interconnected. The first segment 30121 penetrates the first block 311 along the height direction of the analyzer, and the second segment 30122 penetrates the second block 312 along the height direction of the analyzer.

[0038] Specifically, the first block 311 and the second block 312 can be detachably connected by bolts, and when the first block 311 and the second block 312 are connected, the first segment 30121 and the second segment 30122 form the second channel 3012. It is understood that after long-term use, dust may accumulate in the first channel 3011 or the second channel 3012, thus requiring regular cleaning to prevent a decrease in the analyzer's detection accuracy. In this embodiment, since the first block 311 and the second block 312 are detachably connected, and the second channel 3012 includes the first segment 30121 and the second segment 30122, with the first segment 30121 located on the first block 311 and the second segment 30122 located on the second block 312, and the first channel 3011 located in the second block 312, this design facilitates separate cleaning of the first channel 3011 and the second channel 3012. On the other hand, if either the first block 311 or the second block 312 is damaged, the first block 311 or the second block 312 can be replaced separately, avoiding the need to replace the entire detection body 31, thus reducing the maintenance cost of the analyzer to some extent.

[0039] In some embodiments, a first filter (not shown in the figure) is provided in the first channel 3011. The first filter is used to prevent light other than a specific wavelength emitted by the first light source from entering the first channel 3011, so as to avoid astigmatism or other light interfering with the detection results of the analyzer.

[0040] In some embodiments, a second filter (not shown) is provided in the first segment 30121. In some embodiments, a third filter (not shown) is provided in the second segment 30122. Similarly, providing a second filter in the first segment 30121 can prevent stray light from entering the first detection slot 21, or prevent stray light reflected from the first detection slot 21 from entering the first segment 30121. Providing a third filter in the second segment 30122 can prevent stray light from shining onto the first receiving unit 33, thereby preventing stray light from interfering with the detection results. That is, by using the first filter, the second filter, and the third filter, the detection accuracy of the analyzer can be improved.

[0041] In some embodiments, a connection port (not shown in the figure) is provided between the first end and the second end of the second channel 3012, the first end of the first channel 3011 is connected to the connection port, and a reflector (not shown in the figure) is provided at the connection port.

[0042] Specifically, in this embodiment, the second channel 3012 is perpendicularly connected to the first channel 3011. Therefore, in order for the light energy in the first channel 3011 to pass through the second channel 3012 and enter the first detection slot 21, a reflector needs to be installed at the connection port to reflect the light in the first channel 3011 and allow it to pass through the second channel 3012 into the first detection slot 21. In this embodiment, the reflector is tilted at the connection port.

[0043] In some embodiments, the first detection slot 21 includes a plurality of first detection slots 21, each corresponding to a detection channel 301, wherein each first detection slot 21 is provided with a different fluorescent reagent.

[0044] In one specific embodiment, the first detection cell 21 includes three cells, each containing a different fluorescent reagent. Specifically, one cell contains a pH fluorescent dye, one cell contains a CO2 fluorescent dye, and the other cell contains an O2 fluorescent dye. When the analyzer is operating, the samples in the three cells react with the pH, CO2, and O2 fluorescent dyes respectively, and after receiving light of a predetermined wavelength incident through the second channel 3012, they reflect light of a specific wavelength that passes through the second channel 3012 and enters the first detection component 30. This allows the analyzer to simultaneously detect the sample's pH value, carbon dioxide partial pressure, and oxygen partial pressure.

[0045] In some embodiments, the same fluorescent reagent is disposed in some of the first detection cells 21. It is understood that since the light emitted by each light-emitting element has a different wavelength, when the same fluorescent reagent is disposed in some of the first detection cells 21, different wavelengths of light will reflect different light signals after irradiating the first detection cells 21 containing the same fluorescent reagent. Analyzing and comparing these light signals can be used to calibrate the analyzer's detection results. In other words, the blood gas detection performed by the first detection component 30 on the first detection cells 21 containing the same fluorescent reagent is the same detection, but different wavelengths of light are used for excitation. Analyzing the difference between the reflected light can be used to calibrate the analyzer's detection accuracy.

[0046] When different second detection slots 22 contain different biochemical reagents, light of different wavelengths excites the samples in these second detection slots 22, enabling the second detection component 40 to simultaneously perform multiple biochemical tests on the samples. Similarly, the analyzer of this application can also simultaneously detect multiple coagulation items or multiple immune items. Of course, the analyzer of this application can also simultaneously detect multiple coagulation items, multiple immune items, and multiple biochemical items.

[0047] In some embodiments, the second detection component 40 further includes a first support portion 43, which is disposed between the microfluidic detection chip 20 and a plurality of second light sources. The first support portion 43 has a plurality of emission channels 431, and the plurality of second light sources are correspondingly disposed within the plurality of emission channels 431. The second detection component 40 also includes a second support portion 44, which is disposed on the top of the microfluidic detection chip 20. The second support portion 44 has a plurality of receiving channels 432, which are correspondingly disposed with the emission channels 431 along the height direction of the analyzer. The first detection component 30 is disposed on the second support portion 44.

[0048] Specifically, the first support part 43 includes a first support block connected to the body 10. Multiple emission channels 431 are provided on the first support block, and multiple second light sources are correspondingly arranged within the multiple emission channels 431. This is to prevent mutual interference between the light emitted by the multiple second light sources, which would ultimately affect the detection results. Similarly, the second support part 44 includes a second support block connected to the body 10. Multiple receiving channels 432 are provided on the second support block to prevent mutual interference between the light signals emitted from different second detection slots 22, which would lead to inaccurate detection results from the second detection component 40. Furthermore, in this embodiment, the first detection component 30 is disposed on the second support part 44. This arrangement makes the analyzer structure more compact to a certain extent. That is, there is no need to set additional support components on the frame; the first detection component 30 can be fixed by the second support part 44.

[0049] In some embodiments, the emission channel 431 includes a first branch channel 4311 and a second branch channel 4312 that are interconnected. The cross-section of the first branch channel 4311 is larger than the cross-section of the second branch channel 4312, and the second light source is disposed within the first branch channel 4311. It should be noted that, in this application, "the cross-section of the first branch channel 4311" refers to the cross-section obtained by cutting the first branch channel 4311 along a direction perpendicular to its length; similarly, "the cross-section of the second branch channel 4312" refers to the cross-section obtained by cutting the second branch channel 4312 along a direction perpendicular to its length.

[0050] Understandably, when the second light source emits a light signal within the first channel 4311, the larger cross-section of the first channel 4311 provides a stable accommodating space for the second light source. This also facilitates the full diffusion and convergence of the emitted light signal into the connected second channel 4312, preventing scattering and disorder of the light signal due to limited space during the initial emission phase. Meanwhile, the smaller cross-section of the second channel 4312 precisely guides and converges the light signal, further focusing the light signal transmitted from the first channel 4311, reducing signal loss and diffusion during transmission, and allowing the light signal to act more concentratedly and precisely within the second detection slot 22, which has rotated to the corresponding position in the channel.

[0051] In some embodiments, the analyzer further includes a dustproof component 70 disposed between the microfluidic detection chip 20 and the emission channel 431, and the dustproof component 70 covers the side of the emission channel 431 closest to the microfluidic detection chip 20.

[0052] Specifically, to prevent dust and other impurities from easily entering the emission channel 431, this embodiment covers the end of the emission channel 431 near the microfluidic detection chip 20 with a dustproof component 70. This effectively blocks external dust and other impurities from entering the interior of the emission channel 431, effectively preventing impurities from adhering to the inner wall of the emission channel 431 and affecting the transmission of optical signals. This prevents stray light interference or increased optical signal loss, ensuring that the optical signal emitted by the second light source can be accurately transmitted to the second detection slot 22 through the emission channel 431, effectively guaranteeing the accuracy of the detection results.

[0053] In some embodiments, the dustproof component 70 includes a light-transmitting element 72, and multiple light-transmitting elements 72 are disposed one-to-one at one end of the emission channel 431 near the microfluidic detection chip 20. In some embodiments, the light-transmitting element 72 includes a glass sheet.

[0054] Specifically, in this embodiment, by installing the light-transmitting element 72 at one end of the emission channel 431 near the microfluidic detection chip 20, it not only covers the ports of each emission channel 431, effectively blocking external dust and other impurities from entering the interior of the emission channel 431 and preventing impurities from adhering to the inner wall of the channel and affecting the transmission of light signals, but also, thanks to the light-transmitting characteristics of the light-transmitting element 72 itself, allows the light signal emitted by the second light source to be accurately transmitted to the second detection slot 22 through the emission channel 431 and the light-transmitting element 72, ensuring lossless light signal transmission and no stray light interference. Optionally, the light-transmitting element 72 in this application can be set to two, three, or more, and this application does not make a specific limitation.

[0055] In some embodiments, the housing 10 has a mounting cavity 101. The analyzer with multiple detection optical paths further includes a first drive assembly 91, a bracket assembly 80, and a position detection assembly 93. The bracket assembly 80 has a first position housed in the mounting cavity 101 and a second position protruding from the mounting cavity 101 by a predetermined distance. The first drive assembly 91 is connected to the bracket assembly 80 to drive the bracket assembly 80 to switch between the first and second positions. The microfluidic detection chip 20 is rotatably and replaceably disposed in the bracket assembly 80. The position detection assembly 93 is disposed in the mounting cavity 101 and is electrically connected to the first drive assembly 91. When the position detection assembly 93 detects that the bracket assembly 80 has reached the second position, the position detection assembly 93 transmits a signal to the first drive assembly 91 to stop the first drive assembly 91 from driving the bracket assembly 80.

[0056] Specifically, the position detection component 93 can be a laser displacement sensor or a wire displacement sensor. The first drive component 91 includes a first motor and a lead screw. The bracket component 80 includes a tray 83 and a frame 81. The frame 81 is mounted on the lead screw, and the tray 83 is mounted on the frame 81. The microfluidic detection chip 20 is rotatably and replaceably mounted on the tray 83. When the bracket component 80 moves from the first position to the second position, if the distance by which the bracket component 80 protrudes from the mounting cavity 101 is greater than a predetermined distance, this may cause the bracket component 80 to collide with an object outside the analyzer, resulting in damage to the bracket component 80 or the microfluidic detection chip 20. Therefore, to prevent damage to the bracket component 80 or the microfluidic detection chip 20 caused by movement, this application provides a position detection component 93 on the frame to detect the distance the bracket component 80 moves from the first position to the second position. When the bracket component 80 moves a predetermined distance, the position detection component 93 transmits a signal to the first motor, thereby stopping the first motor.

[0057] In some embodiments, the analyzer with multiple detection optical paths further includes a second driving component 92, which is disposed on the body 10. A tray 83 is disposed on the second driving component 92, and the second driving component 92 drives the tray 83 to rotate. The microfluidic detection chip 20 includes a transparent microfluidic detection chip 20. The tray 83 has multiple first clearance holes 831, each corresponding to a multiple second detection slot 22. Specifically, the microfluidic detection chip 20 includes a transparent microfluidic detection chip 20, and the tray 83 has multiple first clearance holes 831 to allow the light signal emitted by the second light source to enter the second detection slot 22 through the emission channel 431.

[0058] In some embodiments, a first base 82 is further provided on the frame 81, and the microfluidic detection chip 20 is disposed on the first base 82, with the transmission channel 431 passing through the first base 82. It can be understood that the first base 82 in this embodiment provides a stable mounting foundation for the microfluidic detection chip 20, ensuring that the microfluidic detection chip 20 will not shift or shake during rotation, thus ensuring the stability of the detection process.

[0059] Specifically, during the rotation of the microfluidic detection chip 20, each of the second detection slots 22 on the microfluidic detection chip 20 will pass through each emission channel 431 in sequence along the rotation direction. When the second detection slot 22 rotates to correspond to a certain emission channel 431, the light signal emitted by the second light source through the emission channel 431 can be accurately transmitted to the second detection slot 22. The emission channel 431 can not only further concentrate the light signal and reduce the diffusion loss of the light signal during the transmission process, but also block external stray light interference, ensuring that the light signal accurately acts on the mixture in the second detection slot 22. In some embodiments, a fourth filter 4411 is provided in the receiving channel 432. It is understood that the fourth filter 4411 is used to prevent light other than the specific wavelength emitted by the second detection slot 22 from entering the receiving channel 432, so as to avoid astigmatism or other light from interfering with the detection results of the analyzer.

[0060] In some embodiments, the second transmitting part 41 and the second receiving part 42 are located on opposite sides of the microfluidic detection chip 20 along the height direction of the body 10, and the microfluidic detection chip 20 includes a transparent microfluidic detection chip 20. It is understood that in this embodiment, the second transmitting part 41 may be located below the microfluidic detection chip 20, and the second receiving part 42 may be located above the microfluidic detection chip 20; alternatively, the second transmitting part 41 may be located above the microfluidic detection chip 20, and the second receiving part 42 may be located below the microfluidic detection chip 20. With this configuration, when the microfluidic detection chip 20 rotates to align a certain second detection groove 22 with the corresponding second light source, the second transmitting part 41 located on one side of the microfluidic detection chip 20 emits a light signal towards the second detection groove 22. The transparent microfluidic detection chip 20 allows the light signal to penetrate the body of the microfluidic detection chip 20 without obstruction and precisely act on the mixture in the second detection groove 22 to excite the mixture to generate a feedback light signal. At this time, the second receiving unit 42, which is located on the other side of the chip and is opposite to the second transmitting unit 41, can receive the light signal fed back after penetrating the chip. There is no need to adjust the direction of light signal transmission, thus avoiding problems such as light signal loss and conduction obstruction caused by component position offset or chip opacity.

[0061] In other words, the relative arrangement of the second transmitting unit 41 and the second receiving unit 42 in this embodiment, together with the transparent microfluidic detection chip 20, allows the emission, penetration, excitation and reception of light signals to form a continuous vertical transmission path, effectively improving the transmission efficiency and accuracy of light signals, while avoiding mutual interference between light signals of different detection items.

[0062] In some embodiments, a mounting cavity 101 is provided within the body 10, along a first direction (as shown in the attached figure). Figure 11 An opening is provided on the first side of the body 10 (in the X direction), and the opening communicates with the mounting cavity 101. The microfluidic detection chip 20 enters the mounting cavity 101 through the opening. The first detection component 30 and the second detection component 40 are both located on the second side of the body 10 opposite to the first side. The analyzer also includes a first heat dissipation component 61, which is located on top of the first detection component 30 and the second detection component 40, and is used at least to dissipate heat from the first detection component 30.

[0063] Specifically, both the first detection component 30 and the second detection component 40 are disposed on the second side of the body 10 opposite to the first side. This arrangement can, to some extent, prevent the first detection component 30 and the second detection component 40 from being disposed on the first side, thereby preventing obstruction of the microfluidic detection chip 20 from entering and exiting the mounting cavity 101 through the opening. Furthermore, the first heat dissipation component 61 is located on top of the first detection component 30 and the second detection component 40 to improve the space utilization of the analyzer. In this embodiment, the first heat dissipation component 61 includes a first cooling fan, which is used to deliver airflow to the first detection component 30, thereby dissipating heat from the first detection component 30.

[0064] In some embodiments, the second detection component 40 includes a second emitting part 41, which is disposed in the mounting cavity 101 and has a second heat dissipation component 62 at the opening. The second heat dissipation component 62 is used to dissipate heat from the second driving component 92 and the second emitting part 41.

[0065] Specifically, the second drive assembly 92 includes a second motor for rotating the tray 83, thereby rotating the microfluidic detection chip 20. The second emitting part 41 is used to emit light signals to the second detection slot 22. After the analyzer has been working for a long time, the second motor and the second emitting part will generate a lot of heat, which will cause the temperature inside the mounting cavity 101 to be too high, thus affecting the stability of the analyzer. Therefore, this embodiment provides a second heat dissipation component 62 at the opening. The second heat dissipation component 62 includes a second cooling fan, which is used to extract air from the mounting cavity 101 to dissipate heat from the second emitting part 41 and the second drive assembly 92.

[0066] In some embodiments, the analyzer further includes a reagent kit 50, which is disposed on the microfluidic detection chip 20. The reagent kit 50 is provided with a second clearance hole 501 corresponding to the first detection groove 21, and the second clearance hole 501 penetrates the reagent kit 50 along the height direction of the analyzer.

[0067] Specifically, the reagent kit 50 is used to release reagents into the microfluidic detection chip 20. In order to prevent the reagent kit 50 from blocking the first detection slot 21, a second clearance hole 501 is provided on the reagent kit 50 in this embodiment so that the light energy reflected in the first detection slot 21 can enter the second channel 3012 through the second clearance hole 501.

[0068] In some embodiments, the dustproof component 70 further includes a dustproof element 71, which is located on the side of the light-transmitting element 72 near the microfluidic detection chip 20. The dustproof element 71 has multiple third clearance holes 711, which are arranged one-to-one with the multiple light-transmitting elements 72. In this embodiment, the dustproof element 71 is installed on the side of the light-transmitting element 72 near the microfluidic detection chip 20, which can further block external dust and other impurities, preventing them from entering the interior of the emission channel 431 through the gap between the light-transmitting element 72 and the emission channel 431, thereby ensuring that the surface of the light-transmitting element 72 is clean and does not affect the penetration and transmission of the light signal. The one-to-one arrangement of the multiple third clearance holes 711 with the multiple light-transmitting elements 72 will not block the light-transmitting element 72, effectively ensuring that the light signal emitted by the second light source is accurately transmitted to the second detection slot 22 through the emission channel 431, the light-transmitting element 72, and the third clearance holes 711. Optionally, the third clearance hole 711 in this application may be set to two, three or more, and this application does not make a specific limitation.

[0069] In some embodiments, a second base 11 is provided on the body 10, a second support 44 is provided on the second base 11, and a receiving channel 432 passes through the second base 11.

[0070] Specifically, the second base 11 provides a stable mounting carrier for the second support part 44 of the receiving component, ensuring that the second support part 44 and the receiving plate and receiving channel 432 on it are fixed in position during the detection process, and avoiding the impact of component displacement on the accurate reception of optical signals.

[0071] For ease of description, spatial relative terms such as "above," "on top of," "on the upper surface of," "above," etc., are used herein to describe the spatial positional relationship of a device or feature as shown in the figures to other devices or features. It should be understood that spatial relative terms are intended to encompass different orientations in use or operation beyond the orientation of the device as described in the figures. For example, if the device in the figures were inverted, a device described as "above" or "on top of" other devices or structures would subsequently be positioned as "below" or "under" other devices or structures. Thus, the exemplary term "above" can include both "above" and "below." The device may also be positioned in other different ways (rotated 90 degrees or in other orientations), and the spatial relative descriptions used herein will be interpreted accordingly.

[0072] Furthermore, it should be noted that the use of terms such as "first" and "second" to define components is merely for the purpose of distinguishing the corresponding components. Unless otherwise stated, the above terms have no special meaning and therefore cannot be construed as limiting the scope of protection of this application.

[0073] The above are merely preferred embodiments of this application and are not intended to limit this application. Various modifications and variations can be made to this application by those skilled in the art. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of this application should be included within the protection scope of this application.

Claims

1. An analyzer with multiple detection optical paths, characterized in that, include: Body (10); A microfluidic detection chip (20) is rotatably and replaceably disposed on the body (10). The microfluidic detection chip (20) has a first detection slot (21) and a plurality of second detection slots (22). The first detection slot (21) contains at least a detection reagent for blood gas detection, and different second detection slots (22) contain at least a detection reagent for biochemical detection, immune detection and coagulation detection. A detection component is disposed on the body (10). The detection component includes a first detection component (30) and a second detection component (40). The first detection component (30) is configured to transmit a signal to the first detection slot (21) and receive a signal reflected from the first detection slot (21) to perform blood gas detection on the sample in the first detection slot (21). The second detection component (40) is configured to transmit different signals to different second detection slots (22) and receive a signal reflected from the second detection slot (22) to perform biochemical detection and / or immune detection and / or coagulation detection on the sample. The first detection component (30) includes a first emitting part (32) and a first receiving part (33). The first emitting part (32) is disposed on the top of the microfluidic detection chip (20). The first emitting part (32) includes a plurality of first light sources, each of which emits light with a different wavelength. The first receiving part (33) is disposed on the top of the first emitting part (32). The first detection component (30) is configured such that when a sample is injected into the microfluidic detection chip (20) and the microfluidic detection chip (20) is not rotated, each of the first light sources emits a light signal to the first detection slot (21). The first receiving part (33) is used to receive the light signal reflected in the first detection slot (21) to perform different blood gas detections on the sample. The second detection component (40) includes a second emitting part (41) and a second receiving part (42). The second emitting part (41) is disposed at the bottom of the microfluidic detection chip (20) and includes a plurality of second light sources. The wavelengths of the light emitted by each second light source are different. The second receiving part (42) is disposed at the top of the microfluidic detection chip (20). The second detection component (40) is configured such that: when a sample is injected into the microfluidic detection chip (20), during the rotation of the microfluidic detection chip (20), each of the second detection slots (22) passes through each of the second light sources in sequence along the rotation direction of the microfluidic detection chip (20); when the second detection slot (22) corresponds to the second light source, the second light source emits a light signal to the second detection slot (22), and the second receiving part (42) is used to receive the light signal reflected in the second detection slot (22) to perform biochemical detection and / or immune detection and / or coagulation detection on the sample.

2. The analyzer with multiple detection optical paths according to claim 1, characterized in that, The first detection groove (21) is disposed at the center of the microfluidic detection chip (20), and a plurality of second detection grooves (22) are disposed at the edge of the microfluidic detection chip (20), and the plurality of second detection grooves (22) are spaced apart along the circumferential direction of the microfluidic detection chip (20); Along the height direction of the analyzer, the first detection component (30) is disposed on the body (10) and located on top of the first detection slot (21), the second detection component (40) is disposed on opposite sides of the microfluidic detection chip (20), and the microfluidic detection chip (20) has the ability to rotate to a detection position that corresponds to the second detection slot (22) and the second detection component (40).

3. The analyzer with multiple detection optical paths according to claim 1, characterized in that, The first detection component (30) further includes a detection body (31), which is connected to the first transmitting part (32) and located between the first receiving part (33) and the microfluidic detection chip (20). The detection body (31) is provided with a plurality of detection channels (301) spaced apart, and each detection channel (301) is located on the top of the first detection groove (21). The first light source is disposed in the detection channel (301) in a corresponding manner. The detection channel (301) is used to transmit the light signal emitted by the first light source to the first detection slot (21) and to transmit the light signal reflected by the first detection slot (21) to the first receiving unit (33).

4. The analyzer with multiple detection optical paths according to claim 3, characterized in that, The detection channel (301) includes a first channel (3011) and a second channel (3012). The first end of the first channel (3011) is connected to the second channel (3012). The first end of the second channel (3012) is located at the top of the first detection slot (21). The second channel (3012) is used to transmit the light signal reflected in the first detection slot (21) to the first detection component (30). The first emitting part (32) is disposed at the second end of the first channel (3011). The first emitting part (32) is used to emit light of different wavelengths to different first channels (3011) and to allow the light to enter the first detection slot (21) through the first channel (3011) and the second channel (3012).

5. The analyzer with multiple detection optical paths according to claim 1, characterized in that, The second detection component (40) further includes a first support portion (43), which is disposed between the microfluidic detection chip (20) and the plurality of second light sources. The first support portion (43) has a plurality of emission channels (431) and the plurality of second light sources are disposed in the plurality of emission channels (431) in a corresponding manner. The second detection component (40) includes a second support part (44), which is disposed on the top of the microfluidic detection chip (20). The second support part (44) has multiple receiving channels (432). Along the height direction of the analyzer, the receiving channels (432) are arranged in a one-to-one correspondence with the transmitting channels (431). The second receiving part (42) is disposed on the top of the second transmitting part (41), and the first detection component (30) is disposed on the second support part (44).

6. The analyzer with multiple detection optical paths according to claim 5, characterized in that, The analyzer also includes a dustproof component (70) disposed between the microfluidic detection chip (20) and the emission channel (431), and the dustproof component (70) covers the side of the emission channel (431) near the microfluidic detection chip (20).

7. The analyzer with multiple detection optical paths according to any one of claims 1 to 6, characterized in that, The body (10) has an installation cavity (101). The analyzer with multiple detection optical paths also includes a first drive assembly (91), a bracket assembly (80), and a position detection assembly (93). The bracket assembly (80) has a first position that is received in the installation cavity (101) and a second position that protrudes from the installation cavity (101) by a predetermined distance. The first drive assembly (91) is connected to the bracket assembly (80) to drive the bracket assembly (80) to switch between the first position and the second position. The microfluidic detection chip (20) is rotatably and replaceably disposed in the bracket assembly (80). The position detection assembly (93) is disposed in the installation cavity (101) and is electrically connected to the first drive assembly (91). When the position detection component (93) detects that the bracket assembly (80) has reached the second position, the position detection component (93) transmits a signal to the first drive component (91) so that the first drive component (91) stops driving the bracket assembly (80).

8. The analyzer with multiple detection optical paths according to any one of claims 1 to 6, characterized in that, The analyzer with multiple detection optical paths further includes a second drive component (92) and a tray (83). The second drive component (92) is disposed on the body (10), and the tray (83) is disposed on the second drive component (92). The second drive component (92) drives the tray (83) to rotate, and the microfluidic detection chip (20) is detachably disposed on the tray (83). The microfluidic detection chip (20) includes a transparent microfluidic detection chip (20), and the tray (83) is provided with a plurality of first clearance holes (831), and the plurality of first clearance holes (831) are provided in a one-to-one correspondence with the plurality of second detection slots (22).

9. The analyzer with multiple detection optical paths according to claim 8, characterized in that, The body (10) is provided with an installation cavity (101). Along the first direction, an opening is provided on the first side of the body (10). The opening communicates with the installation cavity (101). The microfluidic detection chip (20) enters the installation cavity (101) through the opening. The first detection component (30) and the second detection component (40) are both disposed on the second side of the body (10) opposite to the first side. The analyzer also includes a first heat dissipation component (61), which is located on top of the first detection component (30) and the second detection component (40), and the first heat dissipation component (61) is used at least to dissipate heat from the first detection component (30).

10. The analyzer with multiple detection optical paths according to claim 8, characterized in that, The body (10) is provided with an installation cavity (101). Along the first direction, an opening is provided on the first side of the body (10). The opening communicates with the installation cavity (101). The microfluidic detection chip (20) enters the installation cavity (101) through the opening. The second detection component (40) includes a second transmitter (41), which is disposed in the mounting cavity (101). A second heat dissipation component (62) is disposed at the opening. The second heat dissipation component (62) is used to dissipate heat from the second drive assembly (92) and the second transmitter (41).

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