Sample analyzer

Abstract

The invention relates to a sample analyzer, and relates to the technical field of biochemical analysis. The sample analyzer provided by the invention comprises an optical module for performing optical detection on a sample reagent mixed solution in the cuvette. The optical module comprises a light source unit, the light source unit comprises a light source, the wavelength of light emitted by the light source can cover the wavelength required by biochemical detection, and the light source comprises a plurality of LED lamps. A plurality of LED lamps are used as light sources, the LED lamps replace existing halogen lamps, and due to the fact that the service life of the LED lamps is longer, the problems that the halogen lamps are short in service life, frequent in maintenance, long in preheating time in use and the like can be completely solved; and the light beam of the LED lamp can meet the requirement of light power, so that the accuracy and reliability of detection are ensured.

Description

[0001] Cross Reference to Related Applications

[0002] This application claims priority to Chinese Patent Application CN202411209963.2, filed on August 30, 2024, entitled “Sample Analyzer”, the contents of which are incorporated herein by reference. TECHNICAL FIELD

[0003] The present application relates to the technical field of biochemical analysis, in particular to a sample analyzer. BACKGROUND

[0004] A sample analyzer refers to an instrument used for biochemical performance analysis of biological samples such as blood. During analysis, the sample is usually injected into a reaction cup for incubation, and after incubation, the reaction cup is detected to obtain various parameters of the sample.

[0005] The light source for detection of a sample analyzer is generally a halogen lamp to ensure that certain light power requirements are met. However, the biggest problem with halogen lamps is their short lifespan, so at the later stage of use of a sample analyzer, the halogen lamp often has to be replaced frequently due to expiration of its lifespan, resulting in high maintenance costs. SUMMARY

[0006] -Problem to be solved by the solution-

[0007] In a scheme considering replacing a halogen lamp with an LED lamp as a light source, during optical design, all optical elements are usually laid flat on a plane for ease of observation and calculation, but if the positions of the optical structure are designed completely according to this optical scheme, problems such as light source lamp panel interference and large area occupied by the optical structure may occur. For example, in optical design for 3 or 4 LED lamps, in order to balance the light path design and energy, two LED lamps are usually arranged with a small interval between the same direction lamp axes, if the bases of the two LED lamps are in the same plane, the two LED lamps can be arranged by being welded on the same circuit board; if the bases of the two LED lamps are in different planes, a separate circuit board needs to be welded for each LED lamp, at this time, the circuit board is prone to interfere with other structures.

[0008] The present application provides a sample analyzer for solving at least one of the above technical problems.

[0009] The present application provides a sample analyzer, comprising:

[0010] a sample module for carrying a sample;

[0011] a sample dispensing module for aspirating and dispensing the sample;

[0012] a reagent module for carrying reagents;

[0013] a reagent dispensing module for aspirating and dispensing the reagents;

[0014] a reaction assembly comprising cuvettes for biochemical detection, the sample dispensing module dispenses the aspirated sample to the cuvettes, and the reagent dispensing module dispenses the aspirated reagents to the cuvettes;

[0015] a mixing module for mixing the reagents and sample in the cuvettes; and

[0016] an optical module for detecting the sample in the cuvettes;

[0017] the optical module comprises a light source unit, a combining unit, a light splitting unit and a detection unit;

[0018] the light source unit is an LED lamp group composed of multiple LED lamps, the LED lamp group comprises a 340 nm LED lamp, a wide-spectrum LED lamp and a 405 nm LED lamp; wherein the light emitting surface of the LED lamps faces the combining unit; the combining unit combines the light emitted by the multiple LED lamps to form composite light; the composite light combined by the combining unit passes through the sample in the cuvette to reach the light splitting unit; the light splitting unit sorts the combined composite light into monochromatic light of corresponding wavebands for detection by the detection unit;

[0019] the composite light can cover the wavelengths required for biochemical detection; the detection unit is used for optical detection of the monochromatic light;

[0020] the 340 nm LED lamp, the wide-spectrum LED lamp and the 405 nm LED lamp are arranged in different planes respectively.

[0021] In one embodiment, the planes in which the LED lamps are arranged are perpendicular to each other.

[0022] In one embodiment, when the LED lamp group comprises the 340 nm LED lamp, the wide-spectrum LED lamp and the 405 nm LED lamp, at least one LED lamp, the combining unit and the cuvette in the detection position are arranged in a straight line.

[0023] In one embodiment, the wide-spectrum LED lamp, the combining unit and the cuvette in the detection position are arranged in a straight line.

[0024] In one embodiment, the LED lamp group further comprises a 380 nm LED lamp, and the light emitting surface of each LED lamp faces the combining unit.

[0025] In one embodiment, the 380nm LED is arranged on a different plane from the 340nm LED, the broadband LED, and the 405nm LED; wherein the plane containing one of the 340nm LED, the broadband LED, the 405nm LED, and the 380nm LED is perpendicular to the plane containing the other LEDs.

[0026] In one embodiment, at least two of the multiple LEDs have their bulbs in the same height plane or in the same cross-section.

[0027] In one embodiment, at least one of the multiple LEDs is located in a plane parallel to the height plane or the cross-section.

[0028] In one embodiment, the wave combiner unit has at least two light-receiving surfaces, and the wave combiner unit receives light emitted by a corresponding LED through the light-receiving surfaces;

[0029] The beam combining unit converges the light emitted individually from multiple LEDs; the beam splitting unit sorts the converged composite light into monochromatic light of corresponding wavelengths for detection by the detection unit.

[0030] In one embodiment, the light-receiving surface is capable of reflecting and / or transmitting light of different wavelengths; the light emitted by the LED light group is combined into composite light after being reflected or transmitted by at least two light-receiving surfaces.

[0031] In one embodiment, the wave combiner unit includes a beam combining dichroic mirror mounting base and a plurality of beam combining dichroic mirrors. The beam combining dichroic mirror mounting base is used to integrate the plurality of beam combining dichroic mirrors, and the plurality of beam combining dichroic mirrors are respectively used as light-receiving surfaces of the wave combiner unit.

[0032] In one embodiment, the dichroic combining mirrors are respectively installed at different mounting positions on different sides of the dichroic combining mirror mounting base.

[0033] In one embodiment, the dichroic combining mirror mounting base has multiple inclined surfaces, the number of which corresponds one-to-one with the number of dichroic combining mirrors, and each dichroic combining mirror is mounted on the corresponding inclined surface.

[0034] In one embodiment, the number of the multiplexing units is less than the number of LEDs in the LED group.

[0035] In one embodiment, the LED light group is equipped with a temperature maintenance module, which is able to maintain each LED light in the LED light group within a preset temperature range.

[0036] In one embodiment, the optical module further includes a light combining device, which includes an optical mount, in which the LED lamp is mounted, and the temperature maintenance module is capable of cooling the LED lamp.

[0037] In one embodiment, the temperature maintenance module includes a cooling channel for cooling the LED.

[0038] In one embodiment, an incubation module is further included, the incubation module being used to contain cuvettes and provide an incubation environment for samples and reagents within the cuvettes; the cooling channel is in fluid communication with the incubation module and is used to receive incubation water from the incubation module.

[0039] In one embodiment, the temperature fluctuation of the incubation water is ±0.1°C.

[0040] In one embodiment, the beam combining unit combines the light emitted individually from multiple LEDs to form composite light; the composite light formed by the beam combining unit passes through the sample in the cuvette to form outgoing light, and the beam splitting unit sorts the outgoing light into monochromatic light of corresponding wavelengths for detection by the detection unit.

[0041] In one embodiment, the number of monochromatic lights sorted by the spectral unit is the same as the number of corresponding wavelengths required for biochemical detection.

[0042] In one embodiment, the beam splitting unit includes a first dichroic mirror, which is capable of splitting the emitted light into two beams of light in different directions; the wavelengths of the two beams of light in different directions do not overlap.

[0043] In one embodiment, the beam splitting unit further includes a plurality of dichroic mirrors disposed on one of the optical paths after the beam splitting by the first beam splitting dichroic mirror and a plurality of dichroic mirrors disposed on the other optical path after the beam splitting by the first beam splitting dichroic mirror.

[0044] In one embodiment, when the first dichroic mirror splits the emitted light into two beams of light in different directions, the first dichroic mirror can split the emitted light into two beams of light that are perpendicular to each other through transmission and refraction.

[0045] In one embodiment, the multiple dichroic mirrors arranged on either of the two optical paths after the first dichroic mirror has split the light have the same deflection direction.

[0046] In one embodiment, the optical module is equipped with a reflector on the light-emitting side of the cuvette; the reflector can convert the emitted light from its propagation direction.

[0047] In one embodiment, the light-receiving surface is capable of reflecting and / or transmitting light of different wavelengths; the light emitted by the LED light group is reflected or transmitted through multiple light-receiving surfaces and then converges into composite light.

[0048] In one embodiment, the wave combiner unit includes a beam combining dichroic mirror mounting base and a plurality of beam combining dichroic mirrors. The beam combining dichroic mirror mounting base is used to integrate the plurality of beam combining dichroic mirrors. The beam combining dichroic mirrors serve as the light-receiving surface of the wave combiner unit.

[0049] In one embodiment, the number of the dichroic mirrors is less than or equal to the number of LEDs in the LED group.

[0050] In one embodiment, the cooling channels correspond one-to-one with the number of LEDs in the LED light group, so as to achieve individual cooling for each LED in each LED light group.

[0051] In one embodiment, the cooling channel passes through the optical mount to cool each LED in the LED assembly individually.

[0052] In one embodiment, the cooling channel includes an outlet and an inlet, and the number of the outlet and the inlet is one or more.

[0053] In one embodiment, at least one LED is arranged in a straight line with the beam combiner and the cuvette rotated to the detection position; the reflector adjusts the emitted light to a direction perpendicular to the line containing the LED, the beam combiner, and the cuvette, which is perpendicular to the placement surface of the sample analyzer.

[0054] In one embodiment, a corresponding focusing unit is configured in the optical path from the emitted light to the reflector; the focusing unit is used to focus the emitted light, which includes transmitted light, refracted light and reflected light; a flat mirror is configured between the reflector and the beam splitter; the flat mirror is used to flatten the focused emitted light; after being flattened by the flat mirror, the emitted light is separated into monochromatic light of the corresponding wavelength band by the beam splitter for detection by the detection unit.

[0055] In one embodiment, the first dichroic mirror and the dichroic mirror have a transmittance Tave ≥ 90% in the transmission region or a transmittance Tave ≤ 5% in the reflection region.

[0056] In one embodiment, the beam splitting unit further includes a plurality of narrowband filters, each of which is respectively disposed in correspondence with a dichroic mirror.

[0057] In one embodiment, the wave combiner unit includes a beam combining dichroic mirror mounting base and a plurality of beam combining dichroic mirrors. The beam combining dichroic mirror mounting base is used to integrate the plurality of beam combining dichroic mirrors. The beam combining dichroic mirrors serve as the light-receiving surface of the wave combiner unit.

[0058] In one embodiment, the emitted light is sorted into monochromatic light of corresponding wavelengths by the beam splitting unit for detection by the detection unit.

[0059] In one embodiment, the cooling channels correspond one-to-one with the number of LEDs in the LED group, so as to achieve individual cooling for each LED in the LED group.

[0060] In one embodiment, the cooling channel passes through the optical mount to cool each LED in the LED assembly.

[0061] In one embodiment, at least two of the multiple LEDs have their bulbs in the same height plane or in the same cross-section.

[0062] In one embodiment, the light source unit is an LED lamp group composed of multiple LEDs, including 340nm LEDs, broadband LEDs, and 405nm LEDs; the beam combining unit can combine the light emitted individually by multiple LEDs; the beam splitting unit can separate the composite light combined by the beam combining unit into monochromatic light of corresponding wavelengths for detection by the detection unit.

[0063] The composite light can cover the wavelengths required for biochemical detection; the detection unit is used for optical detection of the monochromatic light;

[0064] During optical detection, the detection unit can receive monochromatic light with a wavelength of 340nm at a minimum power lower than that with a wavelength of 405nm.

[0065] In some embodiments, the number of detection units is the same as the number of monochromatic lights separated by the beam splitting unit; the detection unit is a photodiode, which is capable of receiving the monochromatic light separated by the beam splitting unit.

[0066] In some embodiments, the lower limit optical power of the photodiode at a wavelength of 340 nm is 5.28 × 10⁻⁶. -2 μw.

[0067] In some embodiments, the lower limit of the photocurrent of the photodiode at a wavelength of 340 nm is 10.98 nA.

[0068] In some embodiments, when the detection unit measures the 340nm wavelength provided by the 340nm LED, the absorbance repeatability is: coefficient of variation CV ≤ 0.4%.

[0069] In some embodiments, when the detection unit measures any wavelength from 340nm provided by the 340nm LED lamp to 450nm-520nm provided by the broadband LED lamp, the linear range of absorbance is: the maximum absorbance with a relative bias within ±5% is ≥4.0.

[0070] In some embodiments, when the detection unit measures the 340nm wavelength provided by the 340nm LED, the stray light has an absorbance A > 5.

[0071] In some embodiments, when the detection unit measures the 340nm wavelength provided by the 340nm LED, the absorbance accuracy is: absorbance value of 0.5Abs±0.025 or 1.0Abs±0.07.

[0072] In some embodiments, when the detection unit measures any wavelength between 340nm provided by the 340nm LED lamp and 600nm-700nm provided by the broadband LED lamp, the absorbance stability is: the change in absorbance is no greater than 0.01.

[0073] In some embodiments, each of the plurality of LEDs has a corresponding lower limit luminous power; the lower limit luminous power value P1 of the 340nm LED is the smallest among the lower limit luminous power values ​​of the plurality of LEDs.

[0074] In some embodiments, the plurality of LEDs each have a corresponding standard operating light power, and the standard light power of the 340nm LED is lower than that of the broadband LED.

[0075] In some implementations, the standard operating power of the 340nm LED lamp is not less than 1.2mW.

[0076] In some implementations, the standard operating power of the 340nm LED lamp ranges from 1.2mW to 2.5mW.

[0077] In some embodiments, the lower limit luminous power value P1 of the 340nm LED lamp is 0.06mW.

[0078] In some embodiments, the LED light group further includes a 380nm LED, wherein the lower limit luminous power value P1 of the 380nm LED is the largest among the lower limit luminous power values ​​of the multiple LEDs.

[0079] In some embodiments, the lower limit luminous power value P3 of the 380nm LED lamp is 0.7mW.

[0080] In some embodiments, the lower limit luminous power values ​​of the plurality of LEDs satisfy the following relationship: P1 < P2 < P4 < P3,

[0081] Wherein, P1 is the lower limit optical power value of the 340nm LED lamp;

[0082] P2 is the lower limit luminous power value of the broadband LED lamp;

[0083] P3 is the lower limit luminous power value of the 380nm LED lamp;

[0084] P4 is the lower limit luminous power value of the 405nm LED lamp.

[0085] In some embodiments, at least one of the plurality of LEDs is arranged in a straight line with the cuvette at the detection position.

[0086] In some embodiments, when the cuvette is in the detection position, the broadband LED lamp is arranged in a straight line with the multiplexing unit and the cuvette.

[0087] In some embodiments, the optical module further includes a beam leveling device disposed between the light source unit and the beam combining unit; the beam leveling device is used to perform beam leveling on the light beams emitted by each of the LEDs, so as to adjust the divergent light emitted by each of the LEDs into parallel light.

[0088] In some embodiments, at least one of the plurality of LEDs is configured such that the maximum divergence angle does not exceed 30°.

[0089] In some embodiments, the variable divergence angle of one or two of the multiple LEDs is 0°-30°.

[0090] In some embodiments, the variable divergence angle of one of the multiple LEDs is 0°-15°.

[0091] In some embodiments, the plano optical device includes a plano-convex lens.

[0092] In some embodiments, the radius of curvature and diameter of the plano-convex lens are matched to the corresponding LED light.

[0093] In some embodiments, the plano-convex lens in the optical path of one of the multiple LEDs is compatible with LEDs with a variable divergence angle of 20°-30°.

[0094] In some embodiments, the plano-convex lens in the optical path of one of the multiple LEDs can provide flat light for LEDs with a variable divergence angle of less than 20°.

[0095] In some embodiments, the optical path of the optical module is designed such that the light emitted by each LED travels the same distance from the planar light device to the cuvette. In some embodiments, the beam combining unit includes multiple dichroic mirrors and / or a combination of multiple dichroic mirrors.

[0096] In some embodiments, at least one of the light-combining dichroic mirrors is disposed in a one-to-one correspondence with at least one of the light-planing devices and is located in the optical path of the respective light-planing device.

[0097] In some embodiments, the cuvette has a light-receiving surface and a light-emitting surface, and the composite light converged by the beam combining unit passes through the light-receiving surface and the light-emitting surface of the cuvette in sequence and is then split by the beam splitting unit.

[0098] Specifically, a front aperture and a rear aperture are separately configured at corresponding positions on the light-receiving surface and the light-emitting surface; the front aperture is used to filter stray light illuminating the sample in the cuvette; the rear aperture is used to filter the outgoing light after the composite light passes through the sample;

[0099] The beam splitting unit can separate the excellent light filtered by the rear aperture into monochromatic light of the corresponding wavelength for detection by the detection unit.

[0100] In some embodiments, during sample testing, the front aperture, the cuvette, and the rear aperture are arranged in a straight line, wherein the center of the front aperture and the center of the rear aperture are on the same straight line.

[0101] In some embodiments, the light-transmitting area of ​​the rear aperture is smaller than that of the front aperture.

[0102] In some embodiments, both the front aperture and the rear aperture have circular light-transmitting surfaces; wherein the diameter of the light-transmitting surface of the front aperture is 1-3 times the diameter of the light-transmitting surface of the rear aperture.

[0103] In some embodiments, the top of the light-transmitting surface of the front aperture does not exceed the liquid level in the cuvette when the sample analyzer is performing a minimum reaction quantity detection.

[0104] In some embodiments, the size of the parallel light spot entering the colorimetric component is 2mm to 3mm.

[0105] In some embodiments, the size of the light spot entering the spectral unit after passing through the colorimetric component is 1 mm to 1.5 mm.

[0106] In some embodiments, the diameter D1 of the light-transmitting surface of the front aperture satisfies: 2mm ≤ D1 ≤ 3mm.

[0107] In some embodiments, the diameter D2 of the light-transmitting surface of the rear aperture satisfies: 1mm ≤ D2 ≤ 1.5mm.

[0108] In some embodiments, the colorimetric assembly further includes a front incubation window and a rear incubation window located on opposite sides of the colorimetric cup, with the front aperture located on the side of the front incubation window away from the colorimetric cup and the rear aperture located on the side of the rear incubation window away from the colorimetric cup.

[0109] In some embodiments, the beam combining unit includes a biconvex lens disposed on the side of the rear aperture away from the rear window of the incubation tank.

[0110] In some embodiments, the number of the dichroic mirrors is less than or equal to the number of the LEDs.

[0111] In some embodiments, one of the plurality of light-combining dichroic mirrors can reflect the light of the 340nm LED lamp, one of the plurality of light-combining dichroic mirrors can transmit the light of the broadband LED lamp, and one of the plurality of light-combining dichroic mirrors can transmit the light of the 405nm LED lamp.

[0112] In some embodiments, when the LED light group further includes a 380nm LED, one of the multiple light-combining dichroic mirrors can reflect the light from the 380nm LED.

[0113] In some embodiments, the transmittance T of the combining dichroic mirror in the transmission region is... ave Greater than or equal to 90%; or the transmittance T of the dichroic mirror in the reflection region. ave Less than or equal to 5%.

[0114] In some embodiments, the composite light formed by the beam combining unit is expanded before illuminating the cuvette; the expanded composite light then illuminates the sample in the cuvette to complete the optical detection of the sample.

[0115] In some embodiments, a beam expander is disposed between the beam combiner and the cuvette to enlarge the diameter of the composite light.

[0116] The beam expander is used to expand the composite light aggregated by the beam combiner unit; the light emitted by each LED lamp has the same optical path distance from the flat light device to the beam expander.

[0117] In some embodiments, the composite light for beam expansion is a composite parallel light formed by combining the parallel light obtained after the beam combining unit performs flat beam processing on the flat beam device.

[0118] The beam expander includes a Galilean beam expander or a Keplerian beam expander; when the beam expander includes a Galilean beam expander, the Galilean beam expander includes a plano-concave lens and a biconvex lens arranged in sequence; when the beam expander includes a Keplerian beam expander, the Keplerian beam expander includes two biconvex lenses.

[0119] In some embodiments, the Galilean beam expander is capable of increasing the diameter of the composite light passing through it to m times its original diameter. 12 times;

[0120] Where, m 12 =f2 / f1; f1 is the focal length of the plano-concave lens in the Galilean beam expander, and f2 is the focal length of the convex lens in the double Galilean beam expander.

[0121] In some embodiments, the divergence angle of the composite light after being expanded by the Galilean beam expander is m smaller than the divergence angle of the composite light before entering the Galilean beam expander. 12 times;

[0122] Where, m 12 =f2 / f1; f1 is the focal length of the plano-concave lens in the Galilean beam expander, and f2 is the focal length of the convex lens in the double Galilean beam expander.

[0123] In some embodiments, the Keplerian beam expander is capable of increasing the diameter of the composite light passing through it to m times its original diameter. 12 times;

[0124] Where, m 12 = f2 / f1; f1 is half the focal length of the biconvex lens closer to the beam combiner in the Keplerian beam expander, and f2 is half the focal length of the biconvex lens farther from the beam combiner in the Keplerian beam expander.

[0125] In some embodiments, the divergence angle of the composite light after being expanded by the Keplerian beam expander is m smaller than the divergence angle of the composite light before entering the Galerian beam expander. 12 times;

[0126] Where, m 12 = f2 / f1; f1 is half the focal length of the biconvex lens closer to the beam combiner in the Keplerian beam expander, and f2 is half the focal length of the biconvex lens farther from the beam combiner in the Keplerian beam expander.

[0127] In some embodiments, a filtering unit is disposed between the beam combining unit and the colorimetric cup; the filtering unit is used to filter the composite light formed by the beam combining unit; wherein, the filtering range of the filtering unit is the overlapping area of ​​the composite light after the light emitted by the multiple LEDs is combined by the beam combining unit.

[0128] In some embodiments, the overlapping region includes at least the light emitted by the 340nm LED and the light emitted by the broadband LED.

[0129] In some embodiments, the LED light assembly further includes a 405nm LED; the overlapping region includes the light emitted by the 340nm LED, the light emitted by the broadband LED, and the light emitted by the 405nm LED.

[0130] In some embodiments, the distance from the flat device to the multiplexing device is different for each of the LEDs; the optical path length of each LED inside the multiplexing unit is different; and the optical path length from the flat device to the output position of the multiplexing unit is the same for the light emitted by each LED.

[0131] In some embodiments, the flat light device is disposed between the LED lamp and the multiplexing unit.

[0132] In some embodiments, the broadband LED lamp, the multiplexing unit, and the cuvette at the detection position are arranged in a straight line.

[0133] In some embodiments, the wavelengths of light emitted by the multiple LEDs can cover the wavelengths required for biochemical detection.

[0134] In some embodiments, the light filtered by the filtering unit is parallel composite light after the flat light processing by the flat light device.

[0135] Compared with the prior art, the advantages of the present invention are that the 340nm LED, broadband LED and 405nm LED in the LED lamp group of the present invention are arranged on different planes, that is, the LED lamp of the present invention has a three-dimensional layout, thus avoiding the interference between lamp boards or between lamp boards and other structures in the prior art; and the three-dimensional layout of each LED lamp can reduce the volume of the entire optical structure, thereby facilitating the miniaturization of the sample analyzer. Attached Figure Description

[0136] The invention will now be described in more detail with reference to embodiments and the accompanying drawings.

[0137] Figure 1 This is a schematic diagram of the structure of the chemical analyzer in an embodiment of the present invention;

[0138] Figure 2 This is the relative spectral radiation diagram of broadband LED lights;

[0139] Figure 3 This is a schematic diagram of the light source optical path of the chemical analyzer in an embodiment of the present invention;

[0140] Figure 4 This is a schematic diagram of the structure of a Galilean beam expander in one embodiment of the present invention;

[0141] Figure 5 This is a schematic diagram of the structure of a Kepler beam expander in another embodiment of the present invention;

[0142] Figure 6 This is a schematic diagram of the three-dimensional structure of the light source optical path of the chemical analyzer in an embodiment of the present invention;

[0143] Figure 7 This is a three-dimensional structural schematic diagram of the light-combining dichroic mirror mounting base in an embodiment of the present invention;

[0144] Figure 8 This is a three-dimensional structural diagram of the optical mount in an embodiment of the present invention;

[0145] Figure 9 This is a schematic diagram of the cooling channel structure in an embodiment of the present invention;

[0146] Figure 10 This is a schematic diagram of the optical path of the first LED lamp in an embodiment of the present invention;

[0147] Figure 11 This is a schematic diagram of the optical path of the second LED lamp in an embodiment of the present invention;

[0148] Figure 12 This is a schematic diagram of the optical path of the third or fourth LED lamp in an embodiment of the present invention;

[0149] Figure 13 This is a schematic diagram of the colorimetric component in an embodiment of the present invention;

[0150] Figure 14 This is a schematic diagram of the structure of the reflected light beam after focusing in an embodiment of the present invention;

[0151] Figure 15 This is a schematic diagram of the structure of a beam splitter component according to one embodiment of the present invention;

[0152] Figure 16 This is a structural schematic of a beam splitter component according to another embodiment of the present invention;

[0153] Figure 17 This is a schematic diagram of the structure of the spectrometer component in a preferred embodiment of the present invention;

[0154] Figure 18 This is a structural schematic diagram of a beam splitter component according to another embodiment of the present invention;

[0155] Figure 19 This is a structural schematic of a beam splitter component according to yet another embodiment of the present invention;

[0156] Figure 20 This is a schematic diagram of the optical module of the sample analyzer in an embodiment of the present invention.

[0157] Figure label:

[0158] 1. Sample module; 11. Sample rack; 12. Sample tube;

[0159] 2. Sample dispensing module;

[0160] 3. Reagent module; 31. Reagent compartment; 32. Reagent kit;

[0161] 4. Reagent dispensing module; 6. Mixing module;

[0162] 7. Optical module; 71. Dichroic mirror mounting base; 711. Mounting slot; 72. Optical base; 721. Receiving cavity; 73. Water outlet; 74. Water inlet; 75. Plug;

[0163] 8. Incubation module; 9. Cleaning module; 10. ISE analysis components; 15. Reagent kit;

[0164] 100. First LED light; 101. Second LED light; 102. Third LED light; 103. Fourth LED light;

[0165] 104. First plano-convex lens; 105. Second plano-convex lens; 106. Third plano-convex lens; 107. Fourth plano-convex lens;

[0166] 110. First combining dichroic mirror; 108. Second combining dichroic mirror; 109. Third combining dichroic mirror;

[0167] 111. Plano-concave lens;

[0168] 112, 118: Biconvex lenses;

[0169] 113. Front aperture; 114. Front window of incubator; 115. Cuvette; 116. Rear window of incubator; 117. Rear aperture;

[0170] 119. Reflector; 120. Fifth plano-convex lens; 121. Plano aperture; 122. First dichroic mirror;

[0171] 123, 124, 125, 126, 127, 128, 142, 143, 144, 145, 146, 147: Spectrophotometers;

[0172] 136, 137, 138, 139, 140, 141, 129, 130, 131, 132, 133, 134, 135: Narrowband filters;

[0173] 150. Detector; 160. Concave diffraction grating. Detailed Implementation

[0174] The invention will now be further described with reference to the accompanying drawings.

[0175] This invention provides a sample analyzer (or biochemical analyzer), which is an instrument used to detect and analyze biochemical substances, thereby providing information for clinical diagnosis, treatment, prognosis, and health status. Figure 1 As shown, the sample analyzer includes a sample module 1 for carrying samples, a sample dispensing module 2 for aspirating and dispensing samples, a reagent module 3 for carrying reagents, a reagent dispensing module 4 for aspirating and dispensing reagents, a reaction assembly including cuvettes 5, a mixing module 6 for mixing the reagents and samples in the cuvettes 5, an incubation module 8 for incubating the reagents and samples in the cuvettes 5, a cleaning module 9 for cleaning the cuvettes 5, and an optical module 7 for detection. Furthermore, the sample analyzer may also include a module for detecting Na in patient samples. + K + Cl - The ISE analysis component 10, namely the electrolyte module, is used for ion concentration detection. In addition, the sample analyzer is equipped with multiple reagent kits for holding different reagents.

[0176] like Figure 1 As shown, sample module 1 includes a sample rack 11 and sample tubes 12 located on the sample rack 11. A track system is used to transport the sample tubes containing samples via a sample infeed track 13, perform sampling during transport, and retrieve the sample rack via a retrieval track 14 after sampling is completed. Reagent module 3 includes a reagent compartment 31 and reagent kits 32 located within the reagent compartment 31.

[0177] The optical module 7 of the sample analyzer generally includes a light source unit, a beam combining unit, a beam splitting unit, and a detection unit. The detection principle of the optical module 7 is based on Beer-Lambert's law to detect absorbance at different wavelengths. According to Beer-Lambert's law, when a beam of parallel monochromatic light passes perpendicularly through a uniform, non-scattering absorbing material, its absorbance A is directly proportional to the concentration c of the absorbing material and the thickness L of the absorption layer, and inversely proportional to the transmittance T. That is, absorbance A satisfies the following expression:

[0178] A=lg(1 / T)=Kbc=lg(Io / It);

[0179] Where A represents absorbance, abbreviated as Abs / OD, which has no unit;

[0180] T is the transmittance;

[0181] K is the absorption coefficient, L / (g·cm);

[0182] b is the solution thickness, in cm;

[0183] c represents the solution concentration, in g / L;

[0184] Io is the intensity of transmitted light, and cd is the candela / new candle.

[0185] It represents the incident light intensity, expressed in cd.

[0186] In biochemical tests, absorbance is converted into concentration results. Optical module 7 calculates absorbance by detecting changes in light intensity (beam transmission) of the analyte. Therefore, the stability of the light source energy is crucial for the accuracy of test results in biochemical testing. Biochemical detection requires polychromatic light within the 340nm-800nm ​​wavelength range, specifically wavelengths of 340nm, 380nm, 405nm, 450nm, 480nm, 505nm, 546nm, 570nm, 600nm, 660nm, 700nm, 750nm, and 800nm. In particular, 340nm is an extremely commonly used wavelength in biochemical detection and serves as the primary wavelength for many detection parameters in result calculations.

[0187] The optical module 7 includes multiple light source units, each consisting of an LED light group composed of multiple LEDs. This invention achieves a polychromatic light effect by combining multiple LEDs. The number of LEDs can be, for example, two, three, four, or more. Further, the multiple LEDs can be a combination of multiple monochromatic LEDs and one or more broadband LEDs. For example, the LED light group includes 340nm LEDs, broadband LEDs, 405nm LEDs, and 380nm LEDs. A beam combining unit can combine the light emitted individually from multiple LEDs; a beam splitting unit can sort the composite light combined by the beam combining unit into monochromatic light of corresponding wavelengths for detection by the detection unit. The composite light can cover the wavelengths required for biochemical detection; the detection unit is used for optical detection of the monochromatic light.

[0188] Industry standards require optical module 7 to meet certain optical performance indicators, including five aspects: stray light, absorbance linear range, absorbance accuracy, absorbance stability, and absorbance repeatability. Each indicator has corresponding absorbance requirements, and the various optical performance indicators of the industry standards and instrument design are shown in Table 1 below.

[0189] Table 1. List of optical performance indicators required by industry standards

[0190]

[0191] The lower limit of optical energy required for biochemical detection needs to consider multiple factors, such as light source parameters, instrument optical performance parameters, the lower limit range of the light signal received by the detector, detection sensitivity, noise level, and the signal-to-noise ratio of the data acquisition system. Existing biochemical analyzers can only simply meet the lower limits of a few of the optical performance indicators required by the aforementioned industry standards; therefore, their detection performance needs further improvement.

[0192] In some embodiments of the present invention, the optical performance parameters of the optical module 7 satisfy at least one of the following conditions:

[0193] When measuring the 340nm wavelength provided by the 340nm LED lamp, the stray light is: absorbance A > 5;

[0194] When measuring any wavelength from 340nm provided by a 340nm LED lamp and from 450nm to 520nm provided by a broadband LED lamp, the linear range of absorbance is: the maximum absorbance with a relative bias of ±5% is ≥4.0.

[0195] When measuring the 340nm wavelength provided by a 340nm LED lamp, the absorbance accuracy is: absorbance value of 0.5Abs±0.025 or 1.0Abs±0.07;

[0196] When measuring any wavelength within the 340nm range provided by a 340nm LED and the 600nm-700nm range provided by a broadband LED, the absorbance stability is: the absorbance change is no greater than 0.01; and

[0197] When measuring the absorbance at a wavelength of 340nm provided by a 340nm LED lamp, the repeatability of absorbance is: coefficient of variation CV ≤ 0.4%.

[0198] The optical performance indicators of the optical module 7 of the present invention are shown in Table 2 below.

[0199] Table 2 lists the optical performance indicators of the optical module 7 of the present invention.

[0200]

[0201] As can be seen from Tables 1 and 2, the optical performance indicators of the optical module 7 of the present invention are far higher than the requirements of industry standards, and its detection performance is greatly improved.

[0202] In some embodiments, the linear range of absorbance when the optical module 7 of the present invention measures each wavelength is shown in Table 3.

[0203] Table 3 lists the linear range of absorbance for optical module 7.

[0204]

[0205]

[0206] As shown in Table 3, when the optical module 7 of the present invention measures the 340nm wavelength provided by the 340nm LED lamp, the absorbance linear range is: maximum absorbance ≥ 4.18 with a relative bias of -1.03%; when measuring the 450nm wavelength provided by the broadband LED lamp, the absorbance linear range is: maximum absorbance ≥ 4.13 with a relative bias of 1.52%; when measuring the 480nm wavelength provided by the broadband LED lamp, the absorbance linear range is: maximum absorbance ≥ 4.13 with a relative bias of 3.64%; and when measuring the 505nm wavelength provided by the broadband LED lamp, the absorbance linear range is: maximum absorbance ≥ 4.17 with a relative bias of 0.33%.

[0207] Therefore, the linear range of absorbance of the optical module 7 of the present invention far exceeds the industry standard requirements for this parameter.

[0208] During optical detection, the lowest optical power of monochromatic light at a wavelength of 340nm that the detection unit can receive is lower than the lowest optical power of monochromatic light at a wavelength of 405nm. The number of detection units is the same as the number of monochromatic lights separated by the beam splitting unit.

[0209] The detection unit of optical module 7 includes a detector, which includes a photodiode (PD). The photodiode can receive monochromatic light separated by the beam splitter. Different photodiodes have different photosensitivity coefficients for different wavelengths. These photosensitivity coefficients can be used to convert optical power values ​​into photocurrent values. The photosensitivity coefficients of the photodiodes corresponding to these wavelengths also directly affect the lower limit of their detection range.

[0210] The lower limit requirement for the light energy value of each wavelength of the photodiode of the present invention is characterized by the light power and / or photocurrent of the photodiode.

[0211] Specifically, the optical power and / or photocurrent of the photodiode of the present invention satisfy the following conditions:

[0212] When measuring the 340nm wavelength provided by a 340nm LED, the photodiode's optical power is greater than or equal to 5.28 × 10⁻⁶. -2 μW (i.e., the lower limit of optical power is 5.28 × 10⁻⁶) -2 μw), and / or the photocurrent of the photodiode is greater than or equal to 10.98 nA (i.e., the lower limit of the photocurrent is 10.98 nA).

[0213] Furthermore, when measuring other wavelengths, the lower limits of the photodiode's optical power and photocurrent are shown in Table 4 below.

[0214] Table 4 Summary of photocurrent lower limits for photodiodes that meet biochemical detection requirements

[0215]

[0216] The absorbance linear range in Table 3 above is a particularly important parameter. This is because the absorbance linear range represents the upper limit of absorbance that the sample analyzer can detect. A higher absorbance value indicates a weaker intensity of transmitted light through the analyte, meaning the solution absorbs that wavelength more strongly. This indirectly reflects the lower limit of light intensity that the photodiode can measure, thus allowing us to determine the lower limit of the photodiode's light energy values ​​for each wavelength.

[0217] Therefore, it can be understood that when the absorbance linear range of the optical module 7 of the present invention meets the requirements of Table 3 above, the optical power and / or the lower limit value of the photodiode of the present invention meets the requirements of Table 4 above; or conversely, when the optical power and / or the lower limit value of the photodiode of the present invention meets the requirements of Table 4 above, the absorbance linear range of the optical module 7 of the present invention meets the requirements of Table 3 above.

[0218] Furthermore, it should be noted that the dark current of a photodiode is generally less than 50 pA; the low-noise dark current introduced by the circuit and external environment to the photodiode does not exceed 100 pA (1 pA = 10 pA). -12 A).

[0219] Table 5 shows the corresponding values ​​of maximum noise floor photocurrent and optical power for photodiodes of different wavelengths. The maximum noise floor is calculated when the circuit amplification factor is at its maximum adjustable value.

[0220] Table 5. Corresponding Maximum Noise Floor Power and Photocurrent Values ​​of Photodiodes at Different Wavelengths

[0221]

[0222] When selecting a photodiode, its optical power and / or photocurrent must be at least greater than the maximum noise floor optical power and photocurrent values ​​in Table 5 above; or the dark current of the photodiode must be less than 50pA.

[0223] In summary, the optical performance indicators of the optical module 7 of the present invention are far superior to the industry standards, and the present invention proposes that the photodiode of the optical module 7 needs to meet the lower limit values ​​of optical power and / or photocurrent.

[0224] Existing sample analyzers typically use halogen lamps as the light source to obtain the required wavelength, or a combination of halogen lamps and LED lamps. However, these existing solutions cannot solve the problems of short lifespan, frequent maintenance, and long warm-up time of halogen lamps.

[0225] To address the aforementioned problems, this invention proposes that the optical module 7 includes multiple light source units, the wavelengths of light emitted by these units being able to cover the wavelengths required for biochemical detection. The light sources include multiple LEDs. This invention achieves the effect of polychromatic light by using a combination of multiple LEDs. The number of LEDs can be, for example, two, three, four, or more. Furthermore, the multiple LEDs can be a combination of multiple monochromatic LEDs and one or more broadband LEDs.

[0226] For LED light sources, the light beam at the wavelength used for biochemical detection also needs to meet certain optical power requirements to ensure the accuracy and reliability of the detection. In particular, the linear range of absorbance needs to be considered for all detection wavelengths, because the linear range of absorbance represents the upper limit of absorbance that the instrument can detect. The higher the absorbance value, the weaker the intensity of the transmitted light through the analyte, meaning that the stronger the absorption of that wavelength by the analyte solution. This indirectly reflects the lower limit of the light intensity that the optical module 7 can measure, thus obtaining the lower limit of the energy at the light source end.

[0227] During optical inspection, the detection unit can receive a minimum optical power of 340nm wavelength monochromatic light that is lower than the minimum optical power of 405nm wavelength monochromatic light. Each LED has a corresponding lower limit optical power, and the lower limit optical power value P1 of the 340nm LED is the smallest among the multiple LEDs. Furthermore, each LED has a corresponding standard operating optical power, and the standard optical power of the 340nm LED is lower than that of the broadband LED. The standard operating optical power range of the 340nm LED is 1.2mW-2.5mW.

[0228] Furthermore, broadband LED lights provide wavelengths from 450nm to 800nm, using 450nm as the excitation light to excite other wavelengths. Therefore, the relative radiant intensity is not consistent across different wavelengths. The relative spectral radiance diagram of a broadband LED light is shown below. Figure 2 As shown, Figure 2 The horizontal axis represents wavelength, and the vertical axis represents relative radiation intensity. From Figure 2 It can be seen that 450nm, as the peak wavelength, has a relative radiant intensity of 100%, while the relative radiant intensities of 480nm and 660nm are the lowest, at 9.5% and 5% respectively. Therefore, the lower limit of broadband light energy needs to focus on wavelengths with lower relative radiant intensity, that is, the light intensity of the wavelength with the lowest relative radiant intensity needs to meet the requirements in order to carry out the biochemical detection of the corresponding items.

[0229] The lower limit of the energy value of the light source in this invention is required to be characterized by optical power value.

[0230] Furthermore, the lower limit optical power value P1 of the present invention that can provide a 340nm LED lamp with a wavelength of 340nm is the smallest, that is, it is less than the lower limit optical power value of LED lamps that provide other wavelengths.

[0231] Furthermore, the lower limit optical power value P3 of the present invention that can provide a 380nm LED lamp with a wavelength of 380nm is the largest, that is, it is greater than the lower limit optical power value of LED lamps that provide other wavelengths.

[0232] Furthermore, the present invention provides a lower limit luminous power value P1 of 0.06mW for a 340nm LED lamp with a wavelength of 340nm. The present invention provides a lower limit luminous power value P3 of 0.7mW for an LED lamp with a wavelength of 380nm.

[0233] Furthermore, the present invention provides a lower limit luminous power value P4 of 0.5mW for a 405nm LED lamp with a wavelength of 405nm. The present invention provides a lower limit luminous power value P2 of 0.16mW for a broadband LED lamp with a wavelength of 450nm-800nm.

[0234] The lower limit luminous power values ​​of the LED of the present invention are shown in Table 6 below.

[0235] Table 6 List of lower limit luminous power values ​​for LEDs

[0236]

[0237] The lower limit luminous power value of the LED of the present invention satisfies the following condition: P1 < P2 < P4 < P3.

[0238] Furthermore, since each LED has its own supply current range, the optical power of each LED varies linearly with respect to the available supply current. Therefore, the optical power of each LED can be adjusted accordingly based on usage. For example, selecting a larger optical power value combined with a smaller amplification factor to obtain a digital signal as the initial detection value allows the optical module 7 to have a larger adjustable range (adjustable supply current and adjustable circuit amplification factor), thereby improving the lifespan of the optical module 7.

[0239] Therefore, it can be understood that when the absorbance linear range of the optical module 7 of the present invention meets the requirements of Table 3 above, the lower limit of the light power of the LED lamp of the present invention meets the requirements of Table 6 above; or conversely, when the lower limit of the light power of the LED lamp of the present invention meets the requirements of Table 6 above, the absorbance linear range of the optical module 7 of the present invention meets the requirements of Table 3 above.

[0240] In summary, this invention proposes a technical solution using multiple LED lamps as the light source. The lifespan of these LED lamps can reach 20,000 to 50,000 hours, or even longer. Therefore, it completely solves the problems of short lifespan, frequent maintenance, and long warm-up times associated with halogen lamps. This provides an effective solution for sample analyzers to achieve or even exceed the precision levels when using halogen lamps as the light source in clinical testing. Furthermore, this invention proposes that the lower limit optical power value P1 of the 340nm LED lamp is minimal, for example, 0.06mW, and its optical performance indicators far exceed industry standards.

[0241] As described above, the plurality of LED lights of the present invention include a plurality of monochrome LED lights and one or more broadband LED lights. Specifically, the plurality of LED lights include a combination of three monochrome LED lights and one broadband LED light.

[0242] like Figure 3 The example shown illustrates four LED lights. These four LED lights are LED 100, LED 101, LED 102, and LED 103. One of these LED lights is a broadband LED, while the others are monochrome LEDs. The wavelength range of the light emitted by these LED lights is 340nm-800nm.

[0243] More specifically, the second LED 101 is a broadband LED that provides wavelengths of 450nm-800nm. The first LED 100 provides a wavelength of 340nm, the third LED 102 provides a wavelength of 380nm, and the fourth LED 103 provides a wavelength of 405nm, thus satisfying the requirement of covering the wavelengths required for the above-mentioned biochemical detection.

[0244] Furthermore, at least one LED light and the cuvette 115 are arranged in a straight line at the detection position. Specifically, as shown... Figure 3 As shown, the broadband LED lamp and the cuvette 115 are arranged in a straight line at the detection position. When the cuvette 115 is in the detection position, the broadband LED lamp 101, the multiplexing unit, and the cuvette 115 are arranged in a straight line.

[0245] Understandably, other wavelength LEDs can also be selected for combination, as long as they can cover the wavelength range of 340nm-800nm ​​required for biochemical detection.

[0246] In order to meet the requirements of covering the wavelengths required for the above-mentioned biochemical detection, the present invention adopts different combinations of LED lights. However, when different combinations of LED lights are used, they will have different divergence angles, resulting in non-uniformity after light combination. This problem may directly affect the test results of clinical items of the sample analyzer, leading to a decrease in the precision of the whole machine.

[0247] To address the aforementioned problems, this invention proposes a broadband light source optical path scheme that can meet the wavelength requirements of 340nm-800nm ​​for sample analyzers, aiming to solve the problem of poor beam uniformity caused by different LED lights having varying divergence angles.

[0248] Specifically, the optical module 7 of the present invention includes a beam leveling device, which is used to perform beam leveling on the light beams emitted by each LED lamp, so as to adjust the divergent light emitted by each LED lamp into parallel light. The beam leveling device is respectively arranged in a one-to-one correspondence with each LED lamp, and each beam leveling device is arranged in the optical path of the corresponding LED lamp, for performing beam leveling on the light beams emitted by LED lamps with a certain emission angle.

[0249] Furthermore, a plano-optical device can be, for example, a plano-convex lens.

[0250] like Figure 3 As shown, the plano-convex lenses are a first plano-convex lens 104 in the optical path of the first LED 100, a second plano-convex lens 105 in the optical path of the second LED 101, a third plano-convex lens 106 in the optical path of the third LED 102, and a fourth plano-convex lens 107 in the optical path of the fourth LED 103. The radius of curvature and diameter of each plano-convex lens are matched to the corresponding LED.

[0251] At least one of the aforementioned LEDs is configured with a maximum divergence angle not exceeding 30°, and one or two of the aforementioned LEDs have a variable divergence angle of 0°-30°, or one of the aforementioned LEDs has a variable divergence angle of 0°-15°.

[0252] Furthermore, in order to achieve the principle of minimizing the types of optical elements in the optical path, the variable divergence angle of each LED lamp satisfies one or more of the following conditions:

[0253] The variable divergence angle of the first LED light 100 is 0°-30°;

[0254] The variable divergence angle of the second LED 101 is 0°-30°; and

[0255] The variable divergence angles of the third LED light 102 and the fourth LED light 103 are both 0°-15°.

[0256] The variable divergence angle of the four LED lights mentioned above can be selected within a certain range, thus making the selection of LED lights more flexible and replaceable.

[0257] Furthermore, the radius of curvature and diameter of the plano-convex lens should be matched with the corresponding LED to achieve plano-convex beams over a certain optical path distance. For example, the second plano-convex lens 105 in the optical path of the second LED 101 is compatible with LEDs with variable divergence angles in the range of 20°-30°. The third plano-convex lens 106 and the fourth plano-convex lens 107 in the optical paths of the second plano-convex lens 105 for the third LED 102 and the fourth LED 103 can perform small-angle beam parallelization.

[0258] Furthermore, the performance of the first plano-convex lens 104 and the second plano-convex lens 105 is superior to that of the third plano-convex lens 106 and the fourth plano-convex lens 107. Since both the second LED lamp 101 and the first LED lamp 100 are products resulting from technological breakthroughs, there may be significant batch-to-batch variations. That is, the divergence angles of different second LED lamps 101 may differ considerably, and the divergence angles of different first LED lamps 100 may also differ considerably. Since plano-convex lenses are used to flatten the light emitted by the corresponding LED lamps, if the plano-convex lens can only receive light with a small divergence angle (e.g., 20°), but the divergence angle of the light source is large (e.g., 30°), then the plano-convex lens cannot collect and flatten all the light emitted by the LED lamp, resulting in reduced light energy utilization. Therefore, it is necessary to make the divergence angle that the plano-convex lens can receive relatively large, so as to accommodate the instability of the LED lamp's divergence angle as much as possible.

[0259] In summary, by employing a flat-light device to flatten the light beams emitted by each LED lamp with a certain emission angle, this invention can ensure the uniformity of the combined light and avoid affecting the test results of clinical items in the sample analyzer.

[0260] As mentioned above, this invention uses a plano-convex lens to flatten the light beams emitted by each LED. However, since the direction and angle of the light emitted by each LED are different, the direction and angle of the flattened light beams are also different. Therefore, it is necessary to combine the light beams from different directions and angles into one beam during testing.

[0261] To address the aforementioned problems, the optical module 7 of this invention further includes a beam combiner. The beam combiner utilizes the principle of semi-reflection and semi-transparency to combine and filter beams of different wavelengths, thereby achieving the purpose of converging beams from different directions and angles into a single beam.

[0262] Furthermore, the light combining device includes a light combining dichroic mirror and / or a combination of light combining dichroic mirrors, wherein the number of light combining dichroic mirrors is less than or equal to the number of LED lights.

[0263] like Figure 3 In the example shown, the light-combining dichroic mirrors are a first light-combining dichroic mirror 110, a second light-combining dichroic mirror 108, and a third light-combining dichroic mirror 109, and each light-combining dichroic mirror satisfies one or more of the following conditions:

[0264] The first dichroic mirror 110 can reflect the light emitted by the first LED lamp 100 and transmit the light reflected and transmitted by the second dichroic mirror 108 (i.e., the first dichroic mirror 110 transmits in the 370nm~812nm wavelength band and reflects in the 330nm~350nm wavelength band).

[0265] The second dichroic mirror 108 can transmit light emitted by the second LED lamp 101 and reflect light reflected and transmitted by the third dichroic mirror 109 (i.e., the second dichroic mirror 108 transmits light in the 439nm-812nm wavelength range and reflects light in the 369nm-416nm wavelength range); and

[0266] The third dichroic mirror 109 can reflect the light emitted by the third LED lamp 102 and transmit the light emitted by the fourth LED lamp 103 (that is, the third dichroic mirror 109 transmits in the 398nm~812nm wavelength band and reflects in the 368nm~387nm wavelength band).

[0267] Furthermore, the transmittance Tave of the aforementioned dichroic mirror is ≥90% in the transmission region and ≤5% in the reflection region (i.e., the reflectance is ≥95%).

[0268] like Figure 3 As shown, the light beam emitted by the first LED lamp 100 is flattened by the first plano-convex lens 104 and then directed towards the first dichroic mirror 110. Since the first LED lamp 100 emits a light beam with a wavelength of 340nm, the light beam is reflected by the first dichroic mirror 110.

[0269] Similarly, the light beam emitted by the second LED lamp 101, after being flattened by the second plano-convex lens 105, is directed towards the second dichroic combining mirror 108. Since the second LED lamp 101 emits a light beam with a wavelength of 450nm-800nm, the light beam is transmitted through the second dichroic combining mirror 108. The transmitted light beam is then directed towards the first dichroic combining mirror 110, and thus the light beam is transmitted through the first dichroic combining mirror 110.

[0270] The light beam emitted by the third LED lamp 102 is flattened by the third plano-convex lens 106 and then directed towards the third dichroic mirror 109. Since the third LED lamp 102 emits a light beam with a wavelength of 380nm, the light beam is reflected by the third dichroic mirror 109. The reflected light beam is directed towards the first dichroic mirror 110, and thus the light beam is transmitted through the first dichroic mirror 110.

[0271] The light beam emitted by the fourth LED lamp 103, after being flattened by the fourth plano-convex lens 107, is directed towards the third dichroic mirror 109. Since the fourth LED lamp 103 emits a light beam with a wavelength of 405nm, the light beam is transmitted through the third dichroic mirror 109. The reflected light beam is directed towards the first dichroic mirror 110, and thus the light beam is transmitted through the first dichroic mirror 110.

[0272] Understandably, the LED lamps used as the detection light source can be selected from LED lamps that can cover the wavelength range of 340nm-800nm ​​and combined with a dichroic mirror that matches the wavelength range of the LED lamps, so as to achieve the same effect as the present invention.

[0273] In summary, the present invention, through the aforementioned dichroic mirror, can combine the parallel light from four LED lights after shaping into a single beam, thereby obtaining polychromatic light in the 340nm-800nm ​​wavelength range required for biochemical detection.

[0274] Furthermore, by combining individual LEDs with variable divergence angles, performing short-path flattening treatment, and then combining them, the problem of angled beams introducing angular errors when entering the dichroic combining mirror can be avoided, thus preventing the beam combining quality from being affected.

[0275] As described above, this invention obtains polychromatic light in the 340nm-800nm ​​wavelength range required for biochemical detection using a light combining device. However, due to the different emission angles of each LED, the aperture of the flattened beam varies. If beams with different apertures are directly imaged, beam uniformity cannot be guaranteed, resulting in significant aberrations due to variations in light intensity at different wavelengths. This may seriously affect the precision of dual-wavelength testing in the sample analyzer. Therefore, the selection of polychromatic light needs to be considered.

[0276] To achieve uniform light beams and consistent light intensity variations after combining different LED lights, enabling the overall testing to achieve the same detection effect as halogen lamps, this invention proposes a beam expansion design. By expanding the beams, the parallel light beams after different path shaping can be enlarged, resulting in a larger overlap area for beams of different aperture sizes. Then, within the fully overlapping area, a beam size suitable for the sample analyzer is selected for detection. At this point, the collimation of the received beam for the test object is close to that of an ideal beam, thus achieving optimal uniformity.

[0277] Specifically, the optical module 7 includes a beam expander located in the optical path after beam combining. The beam expander can amplify different beams in the flat portion, thereby providing collimated light for the object under test. More specifically, the beam expander is located between the first dichroic mirror 110 and the object under test; in other words, the beam expanded by the beam expander can illuminate the object under test for detection.

[0278] Preferably, in such Figure 4 In the example shown, the beam expander is a Galilean beam expander. The Galilean beam expander includes a plano-concave lens 111 and a biconvex lens 112 arranged sequentially in the optical path after beam combining. It can amplify beams of different thicknesses, thus significantly increasing the overlapping area of ​​the four LEDs.

[0279] like Figure 4 As shown, the focal length of the plano-concave lens 111 is f1, and the focal length of the biconvex lens 112 is f2. Therefore, the beam passing through the Galilean beam expander will be enlarged to its original focal length m. 12 times (where m) 12 =f2 / f1). The divergence angle of the beam after expansion by a Galilean beam expander will be smaller by m than the divergence angle when it enters the Galilean beam expander. 12 The beam incident on the Galilean beam expander is a parallel beam that has been shaped and combined. Therefore, for the object under test, the collimation of the parallel beam received in the overlapping area will be close to that of the ideal beam, and the uniformity can also be optimized.

[0280] Optionally, in such Figure 5 In the example shown, the beam expander is a Keplerian beam expander. A Keplerian beam expander includes two biconvex lenses, namely... Figure 5 The numbers 111-1 and 112-1 are shown.

[0281] If one of the biconvex lenses has a focal length of f1 and the other biconvex lens 112 has a focal length of f2, then the beam passing through the Keplerian beam expander will also be amplified to its original size m. 12 times (where m) 12=f2 / f1). The divergence angle of the beam after expansion by the Keplerian beam expander will be smaller by m than the divergence angle when it enters the Keplerian beam expander. 12 The beam incident on the Keplerian beam expander is a parallel beam that has been shaped and combined. Therefore, for the object under test, the collimation of the parallel beam received in the overlapping area will be close to that of the ideal beam, and the uniformity can also be optimized.

[0282] In summary, by setting a beam expander in the optical path after light combining, the present invention can expand the beam of parallel light after shaping, thereby increasing the overlap area of ​​beams of different aperture sizes. This makes the collimation of the beam illuminating the test object close to the ideal beam, thus ensuring the uniformity of the beam and improving the precision of dual-wavelength test items in the sample analyzer.

[0283] As mentioned above, based on the inventive concept of beam combining and beam expanding, this invention obtains a uniform beam for detection using a beam combining device and a beam expander. However, in optical design, for ease of observation and calculation, all optical elements are typically laid flat on a single plane. But if the position of the optical structure is designed entirely according to this optical scheme, problems such as light source interference and large area occupied by the optical structure may occur.

[0284] For example, in the optical design of 3 or 4 LEDs, in order to balance the optical path design and energy, two LEDs are usually arranged with a small distance between their axes, facing the same direction. If the bases of the two LEDs are on the same plane, they can be arranged by soldering the two LEDs onto the same circuit board. If the bases of the two LEDs are on different planes, a separate circuit board needs to be soldered to each LED. In this case, interference between circuit boards or between the circuit board and other structures can easily occur.

[0285] Therefore, in order to solve this problem, this invention proposes a three-dimensional layout of each LED light and other optical components to achieve the goal of structural miniaturization.

[0286] In this invention, the number of LEDs is greater than or equal to 3. Each LED's light panel is located on a different plane in a Cartesian coordinate system; for example, the light panels of three LEDs are located on three mutually perpendicular planes in the Cartesian coordinate system.

[0287] Furthermore, at least two of the LEDs may be located in the same height plane or in the same cross section; even further, at least one additional LED may be located in a plane parallel to the height plane or the cross section.

[0288] like Figure 6The example shown illustrates a three-dimensional optical path diagram for four LEDs. Figure 4 As shown, the first LED light 100, the second LED light 101, the third LED light 102, and the fourth LED light 103 are located on the rear plane, the left plane, the front plane, and the bottom plane in a rectangular coordinate system, respectively. Furthermore, the first LED light 100, the second LED light 101, and the third LED light 102 are all located in the same height plane.

[0289] This arrangement avoids interference between lamp boards or between lamp boards and other structures, as is common in existing technologies. Furthermore, the three-dimensional arrangement of each LED light reduces the footprint of the entire optical structure, thus facilitating the miniaturization of the sample analyzer.

[0290] In summary, by arranging the LEDs in a three-dimensional manner, this invention not only avoids interference problems but also reduces the size, thereby enabling the sample analyzer to meet the requirements of miniaturization.

[0291] Once all optical components are arranged in a three-dimensional configuration, the specific installation method of the dichroic combining mirror needs to be considered.

[0292] like Figure 7 As shown, the optical module 7 also includes a beam combiner unit, which has at least two light-receiving surfaces. The beam combiner unit receives light emitted by the corresponding LED light through the light-receiving surfaces, which can reflect and / or transmit light of different wavelengths. The light emitted by the LED light group is combined into composite light after being reflected or transmitted by at least two light-receiving surfaces.

[0293] The wave combiner unit includes the aforementioned dichroic mirrors and / or combinations thereof, and also includes a beam combining structure for integrating the aforementioned dichroic mirrors. Each of the multiple dichroic mirrors serves as a light-receiving surface of the wave combiner unit.

[0294] Specifically, the light-combining structure includes a light-combining dichroic mirror mounting base 71, with a first light-combining dichroic mirror 110, a second light-combining dichroic mirror 108, and a third light-combining dichroic mirror 109 respectively mounted on different sides of the mounting base 71. Specifically, one mounting position of the light-combining structure allows the first light-combining dichroic mirror 110 to reflect the light emitted by the first LED lamp 100 and transmit the light reflected and transmitted by the second light-combining dichroic mirror 108; another mounting position of the light-combining structure allows the second light-combining dichroic mirror 108 to transmit the light emitted by the second LED lamp 101 and reflect the light reflected and transmitted by the third light-combining dichroic mirror 109; and another mounting position of the light-combining structure allows the third light-combining dichroic mirror 109 to reflect the light emitted by the third LED lamp 102 and transmit the light emitted by the fourth LED lamp 103.

[0295] Furthermore, the dichroic combining mirror mounting base 71 has multiple inclined surfaces, the number of which corresponds one-to-one with the number of dichroic combining mirrors. Each inclined surface is provided with a mounting groove 711 for mounting the corresponding dichroic combining mirror. Figure 7 As shown, the first dichroic mirror 110 is disposed on the inclined surface on the right side of the dichroic mirror mounting base 71, the second dichroic mirror 108 is disposed on the inclined surface on the left side of the dichroic mirror mounting base 71, and the third dichroic mirror 109 is disposed on the inclined surface on the upper side of the dichroic mirror mounting base 71.

[0296] The inner edge of each mounting slot 711 can be tightly attached to the outer edge of the corresponding dichroic combining mirror. Each dichroic combining mirror can be fixed in the corresponding mounting slot 711 by one or more of the following methods: sliding installation, snap-fit ​​installation, and adhesive installation.

[0297] Furthermore, such as Figure 8 As shown, the light combining device also includes an optical base 72. The optical base 72 has an overall columnar structure, and its rear, left, front and bottom sides are used to mount the first LED 100, the second LED 101, the third LED 102 and the fourth LED 103, respectively.

[0298] Specifically, fasteners are provided on the rear, left, front and bottom sides of the optical base 72 for fixing to the corresponding LED light panel; LED bead holes are also provided on the rear, left, front and bottom sides of the optical base 72 for installing the corresponding LED beads.

[0299] In addition, the optical base 72 is provided with a receiving cavity 721 for mounting the dichroic combining mirror mounting base 71. The dichroic combining mirror mounting base 71 can be fixed in the receiving cavity 721 by one or more of the following methods: sliding mounting, snap-fit ​​mounting, and adhesive mounting.

[0300] Therefore, this invention achieves the goal of combining the beams of four independent LEDs located in different orientations into a single beam using only two structural components: the dichroic mirror mounting base 71 and the optical base 72. The structure of the dichroic mirror mounting base 71 and the optical base 72 facilitates high-precision manufacturing to ensure the positional accuracy of each optical element.

[0301] In addition, since each LED light generates a certain amount of heat when it is working, the cooling method of the optical module 7 also needs to be considered.

[0302] This invention proposes a concept of cooling the light source of the optical module 7 by using the incubation water in the incubation module 8 described above.

[0303] Specifically, such as Figure 9As shown, the optical mount 72 is provided with cooling channels, which surround each light source.

[0304] In some embodiments, the cooling fluid in the cooling channel is a liquid, that is, the cooling channel dissipates heat from each light source by water cooling.

[0305] The cooling channel includes an outlet 73 and an inlet 74, which are connected by a flow path inside the optical mount 72. The flow path can be a water pipe or other pipe separately installed in the optical mount 72, or it can be a machining path directly machined in the optical mount 72.

[0306] The pipe between the outlet 73 and the inlet 74 bypasses the location of the light source of the optical module 7, or surrounds the light source of the optical module 7.

[0307] The number of cooling channels corresponds one-to-one with the number of light sources, enabling individual cooling for each light source. In other words, each LED has its own dedicated cooling channel. These cooling channels can be fluidly connected to each other, or each channel can be fluidly connected to the incubation water supply pipes in incubation module 8.

[0308] For example, the inlet 74 of each cooling channel is connected to the incubation water supply pipeline in the incubation module 8, so the incubation water in the incubation module 8 can enter the optical base 72 through the inlet 74 to cool the light source; the cooled incubation water flows out from the outlet 73, which can be connected to the recycling system.

[0309] On the one hand, since the temperature fluctuation of the incubation water in the incubation module 8 is only ±0.1℃, the incubation water is a relatively constant cooling medium. Therefore, when using incubation water to cool the light source, the stability of the beam of different LED lamps can be ensured. On the other hand, since the incubation water is used in the incubation module 8 to incubate the mixture formed by the sample and reagent in the color cup 5, the incubation water is already an existing medium in the sample analyzer. Introducing it into the cooling channel to cool the light source can reduce the external medium supply structure and medium source of the sample analyzer, ensuring the miniaturization of the sample analyzer.

[0310] Optionally, there can be multiple outlets 73 and inlets 74. For example, one outlet 73 and one inlet 74 can be provided for each light source; correspondingly, there can also be multiple cooling channels. Since different light sources have different power, different heat generation, and different temperature sensitivities, configuring an outlet 73, an inlet 74, and a cooling channel separately for each light source allows for individual control of the flow rate of the cooling channel for each light source, thereby achieving different levels of heat dissipation for each light source.

[0311] Preferably, there is only one outlet 73 and one inlet 74, and the cooling channel runs through the entire optical base 72 to provide heat dissipation for each light source. The advantage of this design is that it allows for a smaller and more compact structure of the optical module 7, thus meeting miniaturization requirements. The outlet 73 and inlet 74 can be located on the same sidewall of the optical base 72.

[0312] like Figure 9 As shown, the cooling channel of the first LED lamp 100 will be used as an example for explanation. An outlet 73 and an inlet 74 are respectively provided on the outer surface of the rear sidewall of the optical base 72. The outlet 73 and inlet 74 penetrate the lamp plate of the first LED lamp 100 and are fluidly connected through a processing passage (not shown) in the rear sidewall of the optical base 72. The pipeline is arranged around the first LED lamp 100, thereby cooling it.

[0313] Furthermore, a plug 75 is also provided on the optical mount 72. During the fabrication of the cooling channel, an opening is formed on the side wall of the optical mount 72; therefore, after obtaining the cooling channel, this opening is sealed by the plug 75. In summary, this invention provides separate cooling for the light source of the optical module 7 by using incubation water as the cooling medium in the cooling channel, ensuring that the light source remains at its normal operating temperature.

[0314] As mentioned above, during testing, it is necessary to ensure the uniformity of light intensity and beam mixing of different wavelength beams. Therefore, this invention proposes to improve the accuracy of sample analyzer testing by designing the optical path accordingly, that is, by ensuring that the optical path lengths of different LED lights are the same when they reach the test object after flattening, combining, and expanding the beams.

[0315] As described above, the second LED lamp 101 of this invention is a broadband LED lamp, providing a wavelength of 450nm-800nm. The first LED lamp 100 provides a wavelength of 340nm, the third LED lamp 102 provides a wavelength of 380nm, and the fourth LED lamp 103 provides a wavelength of 405nm. Different LED lamps have different emission angles and their light energy intensity is not entirely consistent; therefore, the design must consider the emission angle, light intensity, and optical component losses when designing the distribution.

[0316] Specifically, the light source of this invention includes multiple light-emitting elements, each equipped with a beam-flattening device. The beam-flattening device flattens the light emitted by the respective light-emitting element. The optical path design of the optical module ensures that the light emitted by each LED travels the same distance from the beam-flattening device to the cuvette 115. The beam-flattening device is positioned between the LED and the beam combiner unit. The optical module also includes a beam expander, which expands the composite light combined by the beam combiner unit. The light emitted by each LED travels the same distance from the beam-flattening device to the beam expander.

[0317] The following explanation uses an LED light as an example. Figure 3 As shown, each LED is equipped with a plano-optical device, which can be, for example, a plano-convex lens.

[0318] Figure 3 A planar schematic diagram of the light source optical path of the present invention is shown. Specifically, in order to improve beam intensity and beam uniformity, the optical path distances of the beams from multiple LED lamps are the same when they enter the beam expander after passing through the flat beam. More specifically, the optical path distances of the beams from multiple LED lamps are the same when they enter the beam expander from a suitable position after passing through the flat beam. This suitable position after passing through the flat beam can be, for example, the optimal position after passing through the flat beam.

[0319] like Figure 10 The diagram shows the optical path of the first LED lamp 100. L1 represents the optical path distance from the optimal position of the flat light beam after passing through the flat light source to the first dichroic mirror 110. L3 represents the optical path distance from the first dichroic mirror 110 to the focal point of the plano-concave lens 111. f1 is the focal length of the plano-concave lens 111, and f2 is the focal length of the biconvex lens 112. Therefore, the optical path distance from the optimal position of the flat light beam after passing through the flat light source to the beam expander is L1 + L3.

[0320] like Figure 11 The diagram shows the optical path of the second LED lamp 101. L2 represents the optical path distance from the optimal position of the flat light beam after passing through the flat light source to the first dichroic mirror 110. L3 represents the optical path distance from the first dichroic mirror 110 to the focal point of the plano-concave lens 111. f1 is the focal length of the plano-concave lens 111, and f2 is the focal length of the biconvex lens 112. Therefore, the optical path distance from the optimal position of the flat light source to the beam expander after passing through the flat light source is L2 + L3.

[0321] like Figure 12The diagram illustrates the optical path of either the third LED 102 or the fourth LED 103. L2 represents the optical path distance from the optimal position of the flat light beam after passing through the flat light source to the first dichroic mirror 110. L3 represents the optical path distance from the first dichroic mirror 110 to the focal point of the plano-concave lens 111. f1 is the focal length of the plano-concave lens 111, and f2 is the focal length of the biconvex lens 112. Therefore, the optical path distance from the optimal position of the flat light beam after passing through the flat light source to the beam expander is L2 + L3.

[0322] The optical path distance of each LED beam after passing through the flat light satisfies L1+L3=L2+L3, that is, L1=L2.

[0323] In summary, the present invention, by placing different LED combinations at appropriate positions in the optical path with the same optical path distance, not only improves the beam combining of different wavelengths of light to a certain extent and makes the selection of LEDs more flexible and the combination methods more diverse, but also ensures the consistency of light quantity of different wavelength beams.

[0324] When performing tests in a sample analyzer, it is desirable for parallel light to be incident on the colorimetric component. This ensures that the detection conforms more closely to the application conditions of Beer-Lambert's Law, as this law requires parallel monochromatic light to be incident perpendicularly. Such incident conditions are more conducive to the accuracy of biochemical test results. In addition, the Beer-Lambert's Law also requires the following conditions to hold true:

[0325] 1. The light-absorbing substance is a non-scattering system;

[0326] 2. There is no interaction between the light-absorbing particles;

[0327] 3. The interaction between radiation and matter is limited to the process of light absorption; no fluorescence or photochemical phenomena occur.

[0328] However, the incident light conditions of existing sample analyzers are all beams with a certain angle, that is, the light source beam is focused by a focusing lens so that it is focused on a certain position of the analyte in the colorimetric component, rather than parallel light or perpendicular incident light. Therefore, for biochemical detection systems with focused incident light, the design of the front and rear beams of the colorimetric component will have great limitations, and it cannot achieve front and rear beam adaptation, resulting in low selectivity.

[0329] To address the aforementioned problems, this invention proposes a colorimetric component with a spot matching method that improves biochemical detection performance. Specifically, this invention is based on parallel light incidence, and the colorimetric component can match the sizes of the incident and transmitted light beams. In other words, the size of the light spot incident on the colorimetric component has a certain range of selectivity, and the corresponding size of the transmitted light beam entering the beam splitter also has a corresponding selectable range. This spot size matching not only makes the test results of non-uniform scattering systems in biochemical detection more accurate, but also allows for the matching and selection of different optical detection systems for different precision models of biochemical analyzers, offering greater flexibility without significantly altering the structure and optical path, and broadening the selection space for light sources. Furthermore, the different matching conditions for the sizes of the incident and transmitted light spots all meet the performance requirements of the entire instrument, with precision indicators far exceeding industry standards.

[0330] In sample analyzers, most detection items employ a dual-wavelength measurement method, which determines the concentration of the analyte by simultaneously measuring the changes in light signals at two wavelengths. Specifically, incident light enters the colorimetric component, and the beam passing through the component enters the subsequent spectrometer. The spectrometer separates the received polychromatic light into the desired monochromatic light, which is then detected by a detector. The circuit system performs photoelectric conversion and outputs the result as a digital signal, allowing the calculation of the absorbance value of the analyte, which is then converted into a concentration result.

[0331] In this method, the two wavelengths are considered as the primary and secondary wavelengths of the test item, respectively. The better the synchronicity of the changes in the primary and secondary wavelength light signals, the better the quantification, and the more accurate and reliable the test results. Therefore, regardless of whether the measured object is uniform or non-uniform scattering system, the smaller the divergence angle of the incident beam, the better; that is, parallel light incidence is best, which is more conducive to the measurement of different systems. Thus, the matching of the spot size before and after the colorimetric component of this invention can greatly reduce the influence of interference on the test results and reduce the influence of scattered light generated by interfering substances in the reaction on the transmitted beam, such as bubbles, unknown interfering substances in the reaction solution, etc., thereby ensuring the precision and accuracy of biochemical detection performance.

[0332] It should be noted that the principle of dual-wavelength detection is to eliminate noise interference, reduce the influence of stray light, and reduce the interference of the sample itself on light absorption. Matching the size of the front and rear apertures of parallel light incidence greatly improves the synchronization of the main and secondary wavelength changes, thus making dual-wavelength detection more accurate.

[0333] like Figure 13As shown, the incubation module 8 of the present invention includes a colorimetric component, which includes a colorimetric cup 115, an incubation tank front window 114 and an incubation tank rear window 116 located on both sides of the colorimetric cup 115, a front aperture 113 located in front of the incubation tank front window 114 and a rear aperture 117 located behind the incubation tank rear window 116.

[0334] The size of the parallel light spot entering the colorimetric component needs to take into account the minimum reaction volume of the cuvette 115, because the liquid level of different analytes in the cuvette 115 may be different; in addition, it is also necessary to consider that the light beam emitted by the LED lamp with the minimum divergence angle can enter the colorimetric component.

[0335] The cuvette 115 has a light-receiving surface and a light-emitting surface. The composite light beam combined by the beam combining unit passes through the light-receiving surface and the light-emitting surface of the cuvette 115 in sequence and is then split by the beam splitting unit. A front aperture 113 and a rear aperture 117 are separately configured at corresponding positions on the light-receiving surface and the light-emitting surface, respectively. The front aperture 113 is used to filter stray light illuminating the sample in the cuvette 115; the rear aperture 117 is used to filter the outgoing light after the composite light passes through the sample. The beam splitting unit can separate the bright light filtered by the rear aperture 117 into monochromatic light of the corresponding wavelength band for detection by the detection unit.

[0336] During sample testing, the front aperture 113, cuvette 115, and rear aperture 117 are arranged in a straight line. The center of the front aperture 113 and the center of the rear aperture 117 are on the same straight line.

[0337] The light-transmitting area of ​​the rear aperture 117 is smaller than that of the front aperture 113. Both the front aperture 113 and the rear aperture 117 have circular light-transmitting surfaces, and the diameter of the light-transmitting surface of the front aperture 113 is 1-3 times the diameter of the light-transmitting surface of the rear aperture 117.

[0338] The top of the light-transmitting surface of the front aperture 113 shall not exceed the liquid level in the cuvette 115 when the sample analyzer is performing the minimum reaction quantity detection.

[0339] The size of the parallel light spot entering the colorimetric component is 2mm to 3mm. After passing through the colorimetric component, the size of the light spot entering the spectrometer is 1mm to 1.5mm.

[0340] Preferably, the size of the parallel light spot entering the colorimetric component, i.e. the diameter D1 of the light-transmitting surface of the front aperture 113, satisfies: 2mm≤D1≤3mm; and the size of the light spot entering the beam splitting system after passing through the colorimetric component, i.e. the diameter D2 of the light-transmitting surface of the rear aperture 117, satisfies: 1mm≤D2≤1.5mm.

[0341] The matching relationship between the diameter D1 of the light-transmitting surface of the front aperture 113 and the diameter D2 of the light-transmitting surface of the rear aperture 117 is shown in Table 7 below.

[0342] Table 7 lists the matching results of the diameter of the light-transmitting surface of the front aperture 113 and the diameter of the light-transmitting surface of the rear aperture 117.

[0343]

[0344] Furthermore, when the diameter D2 of the light-transmitting surface of the rear aperture 117, which matches the diameter of the light-transmitting surface of the front aperture 113, is the same, the smaller the diameter D1 of the light-transmitting surface of the front aperture 113, the larger the coefficient of variation CV.

[0345] For example, according to Table 7, one matching method is as follows: the diameter D1 of the light-transmitting surface of the front aperture 113 is 2 mm, and the diameter D2 of the light-transmitting surface of the matching rear aperture 117 is 1.5 mm; another matching method is as follows: the diameter D1 of the light-transmitting surface of the front aperture 113 is 3 mm, and the diameter D2 of the light-transmitting surface of the matching rear aperture 117 is 1.5 mm. Compared with the former, the coefficient of variation (CV) of the concentration result of the former matching method is larger, therefore the latter matching method has better precision.

[0346] This is because when considering the influence of stray light caused by interference, the greater the amount of incident light received by the test object, the more accurate the interference signal can be measured and the higher the quantification. Therefore, when the diameter of the light transmission surface of the small front aperture 113 is matched with the diameter of the light transmission surface of the large rear aperture 117, the probability of stray light caused by interference in the test object entering the spectrometer is relatively greater, and the influence on the test results is more obvious. Therefore, the coefficient of variation (CV) result will be relatively larger.

[0347] Similarly, if the diameter D1 of the light-transmitting surface of the front aperture 113 is chosen to be 1mm or 1.5mm, the influence of interference will be smaller, resulting in a smaller coefficient of variation CV, higher accuracy, and smaller deviation.

[0348] For example, in biochemical testing, intra-assay precision for clinical tests is a necessary procedure for instruments. According to industry standards, these tests include alanine aminotransferase (ALT), urea (UREA), and total protein (TP). Focusing primarily on ALT, a clinical test, low-concentration samples show low reactivity. Furthermore, the dominant wavelength is 340nm and the secondary wavelength is 405nm, resulting in very small changes in reactivity. This places greater emphasis on the precision of the detection system and the synchronization of changes in the intensity of the dual-wavelength light. A smaller CV (volume response ratio) indicates higher instrument precision, while a larger CV indicates lower precision. Therefore, the precision result of a test with low reactivity can be used to determine the performance after spot matching. Industry standards specify ALT concentrations of 30U / L to 50U / L with a CV < 5%.

[0349] This invention uses corresponding ALT reagents, calibrators, and corresponding measurement procedures. Normal value quality control serum or fresh patient serum is used as samples to perform repeatability tests on ALT items within the concentration range. Each item is tested 20 times, and the coefficient of variation (CV) of the 20 results is calculated and summarized in Tables 8 and 9.

[0350] Table 8 shows the summary of ALT precision (unfiltered biochemical composite quality control) for the diameter of the light-transmitting surface of the randomly selected front aperture 113 and the diameter of the light-transmitting surface of its matching rear aperture 117; Table 9 shows the summary of ALT precision (filtered biochemical composite quality control) for the diameter of the light-transmitting surface of the randomly selected front aperture 113 and the diameter of the light-transmitting surface of its matching rear aperture 117.

[0351] Table 8. Intra-batch precision of ALT without filtration and quality control.

[0352]

[0353] As shown in Table 8, when the diameter of the light-transmitting surface of the rear aperture 117 is the same, the smaller the diameter of the light-transmitting surface of the front aperture 113, the larger its coefficient of variation (CV). However, the diameter D1 of the light-transmitting surface of the front aperture 113 satisfies: 2mm ≤ D1 ≤ 3mm; and the diameter D2 of the light-transmitting surface of the rear aperture 117 satisfies: 1mm ≤ D2 ≤ 1.5mm. The actual measured coefficients of variation (CV) are both less than 3.5%. Therefore, the performance indicators of the sample analyzer of this invention far exceed the industry standards.

[0354] Table 9. Intra-batch precision of ALT for filtration quality control

[0355]

[0356] As shown in Table 9, when the diameter of the light-transmitting surface of the rear aperture 117 is the same, the smaller the diameter of the light-transmitting surface of the front aperture 113, the larger its coefficient of variation (CV). However, the diameter D1 of the light-transmitting surface of the front aperture 113 satisfies: 2mm ≤ D1 ≤ 3mm; and the diameter D2 of the light-transmitting surface of the rear aperture 117 satisfies: 1mm ≤ D2 ≤ 1.5mm. The actual measured coefficients of variation (CV) are both less than 2.2%. Therefore, the performance indicators of the sample analyzer of this invention far exceed the industry standards.

[0357] Furthermore, as can be seen from the data in Tables 8 and 9, the more uniform test objects have better precision results than the test objects containing interfering substances. However, with the spot matching method proposed in this invention, for items with relatively low reactivity such as ALT, the instrument can obtain precision CV results far exceeding industry standards without filtering the sample during measurement.

[0358] Understandably, the selection of the diameter D1 of the light-transmitting surface of the front aperture 113 and the diameter D1 of the light-transmitting surface of the rear aperture 117 is not limited to the data listed in Tables 8 and 9, as long as 2mm≤D1≤3mm and 1mm≤D2≤1.5mm are satisfied.

[0359] In summary, the present invention makes the test results more accurate by setting the front aperture 113 and rear aperture 117 with matching diameter ranges of the light-transmitting surface.

[0360] As described above, the present invention involves directing a parallel incident light beam into a colorimetric component. The light beam passing through the colorimetric component then needs to be split into the required monochromatic light before detection and calculation. This method is known as "post-splitting" optical detection in sample analyzers.

[0361] In some embodiments, the sample analyzer of the present invention uses a dichroic mirror for spectral dispersion. Dichroic mirror spectral dispersion is widely used due to its advantages such as ease of adjustment and high accuracy.

[0362] Specifically, such as Figure 14 As shown, the optical module 7 also includes a beam combiner unit, the number of which is less than the number of LEDs in the LED light group. The beam combiner unit includes a biconvex lens 118. The optical module 7 also includes a reflector 119, a fifth plano-convex lens 120, a plano aperture 121, and a beam splitter unit arranged sequentially.

[0363] like Figure 14 As shown, the light beam exits from the rear aperture 117 and enters the biconvex lens 118. The function of the biconvex lens 118 is to focus the light beam exiting from the rear aperture 117. The focused light beam is reflected by the reflecting mirror 119, thereby changing the original direction of the light path and preventing the light path from being too large in one direction, thus saving space. The reflected light beam enters the fifth plano-convex lens 120, which collimates the reflected light beam. The collimation distance of the fifth plano-convex lens 120 can reach about 120mm. The collimated light beam enters the beam splitter unit through the plano-aperture 121, which can eliminate stray light at the edges.

[0364] like Figure 15 and Figure 16 As shown, two forms of spectral dispersion using a dichroic mirror are illustrated in the sample analyzer of the present invention. Figure 15 and Figure 16 The methods shown are all direct optical path beam splitting methods.

[0365] like Figure 15 As shown, the optical path of the beam splitter unit is in the lateral direction. The beam splitter unit includes a reflector 119, multiple dichroic mirrors, and a narrowband filter corresponding to each dichroic mirror.

[0366] Understandably, the number of dichroic mirrors is the same as the number of wavelengths required by the sample analyzer. Since the sample analyzer requires 13 wavelengths, there are 13 dichroic mirrors. These dichroic mirrors can be represented as 123, 124, 125, 126, 127, 128, 142, 143, 144, 145, 146, 147, and 148. Similarly, there are 13 narrowband filters, represented as 136, 137, 138, 139, 140, 141, 129, 130, 131, 132, 133, 134, and 135.

[0367] The light beam, after being flattened by the flat aperture 121, enters the reflector 119 and is reflected at the reflector 119 to the dichroic mirror 123 (the first dichroic mirror in the optical path). The dichroic mirror 123 reflects the 340nm light to the narrowband filter 136, turning it into monochromatic light. The monochromatic light then illuminates the detector (e.g., a photodetector) corresponding to the narrowband filter 136. Light with wavelengths greater than 340nm passes through the dichroic mirror 123 to the next dichroic mirror 124, and so on, for further beam splitting.

[0368] according to Figure 15 It can be seen that in this beam splitting method, the length b1 of the beam splitting unit is: b1 = N × a. Where N is the number of dichroic mirrors (i.e., the number of wavelengths), and a is the distance between two dichroic mirrors.

[0369] like Figure 16 As shown, the optical path of the beam splitter unit is vertical. The beam splitter unit includes multiple dichroic mirrors and narrowband filters corresponding to each dichroic mirror.

[0370] Similarly, the number of dichroic mirrors is the same as the number of wavelengths required by the sample analyzer. Since the sample analyzer requires 13 wavelengths, there are 13 dichroic mirrors. These mirrors can be designated as 123, 124, 125, 126, 127, 128, 142, 143, 144, 145, 146, 147, and 148. The number of narrowband filters is also 13, designated as 136, 137, 138, 139, 140, 141, 129, 130, 131, 132, 133, 134, and 135.

[0371] After being flattened by the flat aperture 121, the light beam enters the dichroic mirror 123 (the first dichroic mirror in the optical path). The dichroic mirror 123 reflects the 340nm light onto the narrowband filter 136, turning it into monochromatic light. The monochromatic light then illuminates the detector (e.g., a photodetector) corresponding to the narrowband filter 136. Light with wavelengths greater than 340nm passes through the dichroic mirror 123 and is transmitted to the next dichroic mirror 124, and so on, for further beam splitting.

[0372] according to Figure 16 It can be seen that in this beam splitting method, the length b2 of the beam splitting unit is: b2 = N × a. Where N is the number of dichroic mirrors (i.e., the number of wavelengths), and a is the distance between two dichroic mirrors.

[0373] In a preferred embodiment, the present invention proposes a layout for a dichroic mirror that, by making reasonable use of space, reduces the vertical optical path length by half, thereby reducing the space occupied and the loss of light energy.

[0374] like Figure 17 The diagram illustrates a beam-splitting unit in a preferred embodiment of the present invention. The beam-splitting unit includes a first dichroic mirror 122 located after the planar aperture 121. Specifically, the first dichroic mirror 122 is a dichroic mirror that splits the polychromatic light after it has passed through the planar aperture 121 into two.

[0375] like Figure 17 As shown, the first dichroic mirror 122 splits the light beam into two beams in different directions, for example, splitting the beam into a beam in the horizontal direction and a beam in the vertical direction. Therefore, the beam splitting unit also includes multiple dichroic mirrors arranged in the horizontal direction and multiple dichroic mirrors arranged in the vertical direction. The first dichroic mirror 122 and the other dichroic mirrors reflect wavelengths in the 335nm–510nm band in the reflection region and transmit wavelengths in the 541nm–805nm band in the transmission region; the transmittance T in the transmission region... ave ≥90%, in the T of the reflection zone ave ≤5% (i.e., reflectivity above 95%). Therefore, the reflective bands of the first dichroic mirror 122 and other dichroic mirrors are 340nm, 380nm, 405nm, 450nm, 480nm and 505nm, and the transmittance bands are 546nm, 570nm, 600nm, 660nm, 700nm, 750nm and 800nm.

[0376] like Figure 17As shown, the beam splitting unit also includes multiple dichroic mirrors after the first dichroic mirror 122. The multiple dichroic mirrors in the horizontal direction can be represented by 123, 124, 125, 126, 127 and 128; the multiple dichroic mirrors in the vertical direction can be represented by 142, 143, 144, 145, 146, 147 and 148.

[0377] Ideally, the difference in the number of dichroic mirrors in the two different directions should be minimized, so that the dimensions in the two directions are not significantly different.

[0378] Because the sample analyzer requires 13 wavelengths (340nm, 380nm, 405nm, 450nm, 480nm, 505nm, 546nm, 570nm, 600nm, 660nm, 700nm, 750nm, and 800nm) for detection and analysis, the number of dichroic mirrors in the horizontal direction can be 6, and the number of dichroic mirrors in the vertical direction can be 7.

[0379] In addition, the beam splitting unit also includes multiple narrowband filters, which are respectively arranged in a one-to-one correspondence with multiple dichroic mirrors in the horizontal direction and multiple dichroic mirrors in the vertical direction. For example, the narrowband filters corresponding to each dichroic mirror in the horizontal direction are denoted as 136, 137, 138, 139, 140 and 141, respectively, and the narrowband filters corresponding to each dichroic mirror in the vertical direction are denoted as 129, 130, 131, 132, 133, 134 and 135, respectively.

[0380] like Figure 17As shown, the first dichroic mirror 122 can split a light beam into two beams emitted in different directions according to the desired wavelength, and then sequentially split the two beams into monochromatic light. In biochemical analysis, 13 wavelengths are commonly used from 340nm to 800nm. Using intermediate wavelengths such as 505nm and 546nm for spectral splitting, the first dichroic mirror 122 reflects the 340nm to 505nm light to the dichroic mirror 123. The dichroic mirror 123 then reflects the 340nm light to the narrowband filter 136, converting it into monochromatic light. This monochromatic light then illuminates the detector 150 (e.g., a photodetector) corresponding to the narrowband filter 136. Light with wavelengths greater than 340nm passes through the dichroic mirror 123 and is transmitted to… The next dichroic mirror 124 is used for further beam splitting; while the beam of light in the 546nm to 800nm ​​range passes through the first dichroic mirror 122 and reaches the dichroic mirror 142. Similarly, the dichroic mirror 142 reflects the 340nm light onto the narrowband filter 129 and turns it into monochromatic light. The monochromatic light then illuminates the detector 150 (e.g., a photodetector) corresponding to the narrowband filter 129. The light with a wavelength greater than 340nm passes through the dichroic mirror 142 and is passed to the next dichroic mirror 143, and so on for further beam splitting.

[0381] Therefore, it can be seen that by setting multiple dichroic mirrors in the horizontal direction, half of the light path in the vertical direction can be shifted to the horizontal direction, thereby reducing the length of the light path in the vertical direction by half, thus achieving the purpose of reducing the space occupied and reducing the loss of light energy.

[0382] like Figure 17 As shown, the length of the beam splitter is D+l1, and its width is C+l2. Where D = N1×a, C = N2×a, l1 = l2, N... 1＝ = N1 + N2, where N1 is the number of dichroic mirrors in the vertical direction, N2 is the number of dichroic mirrors in the horizontal direction (i.e., the number of wavelengths), l1 is the distance between two dichroic mirrors in the vertical direction, and l2 is the distance between two dichroic mirrors in the horizontal direction.

[0383] When N1 = N2, the length D of the beam-splitting unit in the preferred embodiment of the present invention is either b1 / 2 or D = b2 / 2, that is, the length of the beam-splitting unit in the vertical direction in the preferred embodiment of the present invention is only... Figure 15 or Figure 16 In the embodiment shown, half the length of the beam splitting unit is used. In the preferred embodiment of the present invention, the remaining optical path of the beam splitting unit is shifted to the horizontal direction, which can greatly reduce the space it occupies, effectively reduce the loss of light energy, reduce the degree of light divergence, and maximize the utilization of space.

[0384] Figure 15 , Figure 16 and Figure 17In the beam splitting method shown, the tilt direction of each dichroic mirror in each direction is the same, and the narrowband filter corresponding to each dichroic mirror is set on the same side in that direction.

[0385] In other implementations, such as Figure 18 As shown, the sample analyzer of the present invention uses optical fiber splitting for beam splitting. Specifically, the sample analyzer of the present invention uses a multi-fiber bundle splitting method, such as a 13-fiber bundle splitting method, for beam splitting.

[0386] like Figure 18 As shown, the beam splitter unit includes multiple dichroic mirrors and narrowband filters corresponding to each dichroic mirror. The dichroic mirrors can be represented by 123, 124, 125, 126, 127, 128, 142, 143, 144, 145, 146, 147, and 148. There are 13 dichroic mirrors and 13 narrowband filters, which are represented by 136, 137, 138, 139, 140, 141, 129, 130, 131, 132, 133, 134, and 135.

[0387] like Figure 18 As shown, the dichroic mirrors are tilted approximately vertically, thus placing the narrowband filters corresponding to two adjacent dichroic mirrors on opposite sides of the optical path. The incident light, after being flattened, enters the dichroic mirror 123 (the first dichroic mirror in the optical path). The dichroic mirror 123 reflects the 340nm light onto the narrowband filter 136, turning it into monochromatic light. The monochromatic light then illuminates the detector 150 (e.g., a photodetector) corresponding to the narrowband filter 136. Light with wavelengths greater than 340nm passes through the dichroic mirror 123 to the next dichroic mirror 124, and so on, for further beam splitting.

[0388] In some other implementations, such as Figure 19 As shown, the sample analyzer of the present invention uses grating spectral dispersion for spectral dispersion.

[0389] like Figure 18 As shown, the beam-splitting unit includes a concave diffraction grating 160. The beam, after being flattened by the planar aperture 121, enters the concave diffraction grating 160. The concave diffraction grating 160 includes a substrate (typically glass), an epoxy resin layer (or metal layer) located above the substrate to form the grooves, and a reflective coating. The concave diffraction grating 160 can also split and reflect wavelengths from 340 nm to 800 nm, with the monochromatic light then illuminating the detector 150.

[0390] like Figure 20 The diagram shows the overall structure of the optical module 7 according to one embodiment of the present invention.

[0391] In some embodiments, the optical module 7 includes a light source, which may include, for example, the individual LEDs and / or combinations of LEDs described above.

[0392] In some embodiments, the optical module 7 further includes a plano-optical device, which may include the plano-convex lenses and / or combinations of plano-convex lenses described above.

[0393] In some embodiments, the optical module 7 further includes a light combining device, which may include the light combining dichroic mirrors and / or combinations of the light combining dichroic mirrors described above.

[0394] In some embodiments, the optical module 7 also includes a beam expander, which may be a Galilean beam expander or a Keplerian beam expander as described above.

[0395] In some embodiments, the optical module 7 further includes a colorimetric component, which may include the colorimetric cup 115, the incubator front window 114, the incubator rear window 116, the front aperture 113, and the rear aperture 117 described above.

[0396] In some embodiments, the optical module 7 further includes a beam combiner unit following the colorimetric component, which may be the biconvex lens 118 described above.

[0397] In some embodiments, the optical module 7 further includes a reflector 119, a fifth plano-convex lens 120, and a plano-diaphragm 121 arranged sequentially after the wave combiner unit.

[0398] In some embodiments, the optical module 7 further includes a beam-splitting unit, which may include, for example... Figure 15 and Figure 16 Each dichroic mirror and the corresponding narrowband filter; or including, for example, Figure 17 The first dichroic mirror 122, as well as multiple dichroic mirrors in the horizontal direction, multiple dichroic mirrors in the vertical direction, and narrowband filters corresponding to each dichroic mirror.

[0399] In some embodiments, the optical module 7 further includes a beam-splitting unit, which can use, for example... Figure 18 The method shown is to split light into multiple fiber bundles, which can include 13 dichroic mirrors and corresponding narrowband filters.

[0400] In some embodiments, the optical module 7 further includes a beam-splitting unit, which may include, for example... Figure 19 The concave diffraction grating 160 shown is an example.

[0401] In some embodiments, the optical module 7 further includes a detection unit, which includes a detector 150 and a photoelectric converter, such as a photodiode (PD) as described above.

[0402] Although the invention has been described with reference to preferred embodiments, various modifications can be made and components can be replaced with equivalents without departing from the scope of the invention. In particular, the technical features mentioned in the various embodiments can be combined in any manner as long as there is no structural conflict. The invention is not limited to the specific embodiments disclosed herein, but includes all technical solutions falling within the scope of the claims.

Claims

1. A sample analyzer characterized by, The application relates to a biochemical detection device. The biochemical detection device comprises: a sample module for carrying a sample; a sample dispensing module for sucking and discharging the sample; a reagent module for carrying a reagent; a reagent dispensing module for sucking and discharging the reagent; a reaction assembly comprising a cuvette for biochemical detection, the sample dispensing module discharges the sucked sample to the cuvette; the reagent dispensing module discharges the sucked reagent to the cuvette; a mixing module for mixing the reagent and the sample in the cuvette; and an optical module for detecting the sample in the cuvette. The optical module comprises a light source unit, a combining unit, a light splitting unit and a detection unit. The light source unit is an LED lamp group composed of multiple LED lamps, the LED lamp group comprises a 340 nm LED lamp, a wide-spectrum LED lamp and a 405 nm LED lamp. The light emitting surface of the LED lamp faces the combining unit, the combining unit combines the light emitted by the multiple LED lamps to form composite light, the composite light combined by the combining unit passes through the sample in the cuvette to reach the light splitting unit, and the light splitting unit sorts the composite light combined into monochromatic light of corresponding wave bands for detection by the detection unit. The composite light can cover the required wavelength for biochemical detection, and the detection unit is used for optical detection of the monochromatic light. The 340 nm LED lamp, the wide-spectrum LED lamp and the 405 nm LED lamp are arranged in different planes respectively.

2. The sample analyzer of claim 1, wherein, The planes in which the LED lamps are arranged are perpendicular to each other.

3. The sample analyzer of claim 1, wherein, When the LED lamp group comprises the 340 nm LED lamp, the wide-spectrum LED lamp and the 405 nm LED lamp, at least one LED lamp, the combining unit and the cuvette in a detection position are arranged in a straight line.

4. The sample analyzer of claim 3, wherein, The wide-spectrum LED lamp, the combining unit and the cuvette in a detection position are arranged in a straight line.

5. The sample analyzer of claim 1, wherein, The LED lamp group further comprises a 380 nm LED lamp, and the light emitting surface of the 380 nm LED lamp faces the combining unit.

6. The sample analyzer of claim 5, wherein, The 380 nm LED lamp is arranged in a plane different from the planes of the 340 nm LED lamp, the wide-spectrum LED lamp and the 405 nm LED lamp, and the plane in which one of the 340 nm LED lamp, the wide-spectrum LED lamp, the 405 nm LED lamp and the 380 nm LED lamp is arranged is perpendicular to the planes in which the other LED lamps are arranged.

7. The sample analyzer of claim 1, wherein, The lamp beads of at least two LED lamps in the multiple LED lamps are in the same height plane or in the same section plane.

8. The sample analyzer of claim 7, wherein, At least one other LED lamp in the multiple LED lamps is in a plane parallel to the height plane or the section plane.

9. The sample analyzer of claim 1, wherein, The combining unit has at least two light receiving surfaces, and the combining unit receives the light emitted by the corresponding LED lamps through the light receiving surfaces. The combining unit converges the light emitted by the multiple LED lamps, and the light splitting unit sorts the converged composite light into monochromatic light of corresponding wave bands for detection by the detection unit.

10. The sample analyzer of claim 9, wherein, The light receiving surface can reflect and / or transmit light of different wavelengths; the light emitted by the LED lamp group is combined into composite light after being reflected or transmitted by at least two light receiving surfaces.

11. The sample analyzer of claim 9, wherein, The light combining unit comprises a light combining dichroic mirror mounting base and a plurality of light combining dichroic mirrors, the light combining dichroic mirror mounting base is used for integrating the plurality of light combining dichroic mirrors, and the plurality of light combining dichroic mirrors are respectively used as the light receiving surfaces of the light combining unit.

12. The sample analyzer of claim 11, wherein, The light combining dichroic mirrors are respectively installed at the mounting positions of different sides of the light combining dichroic mirror mounting base.

13. The sample analyzer of claim 12, wherein, The light combining dichroic mirror mounting base has a plurality of inclined surfaces, the number of the inclined surfaces respectively corresponds to the number of the light combining dichroic mirrors, and each light combining dichroic mirror is respectively installed on the corresponding inclined surface.

14. The sample analyzer of claim 1, wherein, The number of the light combining units is less than the number of the LED lamps in the LED lamp group.

15. The sample analyzer of claim 1, wherein, The LED lamp group is provided with a temperature maintaining module, which can maintain each LED lamp in the LED lamp group within a preset temperature range.

16. The sample analyzer of claim 15, wherein, The optical module further comprises a light combining device, the light combining device comprises an optical seat, the LED lamp is installed in the optical seat, and the temperature maintaining module can cool the LED lamp.

17. The sample analyzer of claim 16, wherein, The temperature maintaining module comprises a cooling flow channel for cooling the LED lamp.

18. The sample analyzer of claim 17, wherein, Further comprising an incubation module for accommodating a cuvette, and providing an incubation environment for samples and reagents in the cuvette; the cooling flow channel is in fluid communication with the incubation module, and the cooling flow channel is used for receiving incubation water in the incubation module.

19. The sample analyzer of claim 18, wherein, The temperature fluctuation of the incubation water is ±0.1℃.

20. The sample analyzer of claim 1, wherein, The light combining unit combines the light emitted by a plurality of LED lamps to form composite light; the composite light formed by the light combining unit passes through the sample in the cuvette to form outgoing light, the light sorting unit sorts the outgoing light into monochromatic light of corresponding wave bands for detection by the detection unit, and the number of the sorted monochromatic light of the light sorting unit is the same as the number of the corresponding wavelengths required by biochemical detection.

21. The sample analyzer of claim 20, wherein, The light sorting unit comprises a first light sorting dichroic mirror, which can divide the outgoing light into two beams of light in different directions; the two beams of light have non-overlapping wavelengths.

22. The sample analyzer of claim 21, wherein, The light sorting unit further comprises a plurality of dichroic mirrors arranged on one of the two light paths after the light is sorted by the first light sorting dichroic mirror, and a plurality of dichroic mirrors arranged on the other light path after the light is sorted by the first light sorting dichroic mirror.

23. The sample analyzer of claim 22, wherein, When the first light sorting dichroic mirror divides the outgoing light into two beams of light in different directions, the first light sorting dichroic mirror can divide the outgoing light into two beams of light perpendicular to each other by transmission and refraction.

24. The sample analyzer of claim 23, wherein, The plurality of dichroic mirrors arranged on any one of the two light paths after the light is sorted by the first light sorting dichroic mirror have the same deflection direction.

25. The sample analyzer of claim 20, wherein, The optical module is provided with a mirror on the light emitting side of the cuvette; the mirror can change the propagation direction of the outgoing light.

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