Sample analyzer

Abstract

The utility model relates to a sample analyzer and relates to the technical field of biochemical analysis. The sample analyzer provided by the utility model 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. The detection unit includes a photodiode having different lower limit optical power values or lower limit optical power values for different wavelengths. The optical power and / or the light current of the photodiode has different lower limit optical power values or lower limit optical power values according to different wavelengths, and when biochemical detection is carried out, the optical performance index of the optical module is far higher than the industrial standard.

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 utility model relates to biochemical analysis technical field, 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 injected into a reaction cup for reaction incubation, and after incubation, the reaction cup is detected to obtain various parameters of the sample.

[0005] The light source used for detection by the 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 the sample analyzer often has to frequently replace the halogen lamp when it reaches the end of its lifespan, resulting in high maintenance costs. SUMMARY

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

[0007] It is known that in the prior art, there have been considerations to replace halogen lamps with LED lamps as light sources, but all have only remained at the scheme level, and there is no sample analyzer in actual products that uses LED lamps as light sources. The main reason for this situation is that the corresponding wavelength light required by the sample analyzer for sample detection has requirements, and if an LED lamp is selected as the light source of the sample analyzer, it cannot meet the detection requirements, so there is no sample analyzer in actual products that uses LED lamps as light sources.

[0008] Industry standards require that optical modules need to meet certain optical performance indicators, including stray light, absorbance linear range, absorbance accuracy, absorbance stability, and absorbance repeatability. The existing biochemical detector can only simply meet the lower limit of several optical performance indicators required by industry standards, so its detection performance needs to be improved.

[0009] The utility model provides a sample analyzer, which is used to solve at least one of the above technical problems.

[0010] The utility model provides a sample analyzer, comprising:

[0011] A sample module for carrying a sample;

[0012] a sample dispensing module for sucking and discharging the sample;

[0013] a reagent module for carrying reagents;

[0014] a reagent dispensing module for sucking and discharging the reagents;

[0015] a reaction assembly comprising a cuvette for biochemical detection, the sample dispensing module discharges the sucked sample to the cuvette, and the reagent dispensing module discharges the sucked reagents to the cuvette;

[0016] a mixing module for mixing the reagents and the sample in the cuvette; and

[0017] an optical module for detecting the sample in the cuvette;

[0018] the optical module comprises a light source unit, a combining unit, a light splitting unit and a detection unit;

[0019] the light source unit is an LED lamp group composed of multiple LED lamps, the LED lamp group comprises 340 nm LED lamps, wide-spectrum LED lamps and 405 nm LED lamps; the combining unit can combine the light emitted by the multiple LED lamps; the light splitting unit can sort the composite light combined by the combining unit into monochromatic light of corresponding wave bands for detection by the detection unit;

[0020] the composite light can cover the wavelengths required for biochemical detection; and the detection unit is used for optical detection of the monochromatic light;

[0021] when performing optical detection, the minimum light power of the 340 nm monochromatic light received by the detection unit is lower than the minimum light power of the 405 nm monochromatic light.

[0022] In some embodiments, the number of detection units is the same as the number of monochromatic light sorted by the light splitting unit; the detection unit is a photodiode, and the photodiode can receive the monochromatic light sorted by the light splitting unit.

[0023] In some embodiments, the lower limit of the light power value of the photodiode at a wavelength of 340 nm is 5.28×10 -2 μw.

[0024] In some embodiments, the lower limit of the photocurrent of the photodiode at a wavelength of 340 nm is 10.98 nA.

[0025] In some embodiments, when the detection unit measures the 340 nm wavelength provided by the 340 nm LED lamp, the absorbance repeatability is: coefficient of variation CV≤0.4%.

[0026] In some embodiments, the detection unit has a linear range of absorbance when measuring 340nm provided by the 340nm LED lamp and any one of 450nm-520nm provided by the wide spectrum LED lamp, with a maximum absorbance of >4.0 within a relative bias of ±5%.

[0027] In some embodiments, the detection unit has stray light of absorbance A>5 when measuring 340nm provided by the 340nm LED lamp.

[0028] In some embodiments, the detection unit has absorbance accuracy of an absorbance value of 0.5Abs±0.025 or 1.0Abs±0.07 when measuring 340nm provided by the 340nm LED lamp.

[0029] In some embodiments, the detection unit has absorbance stability of a change in absorbance of no more than 0.01 when measuring 340nm provided by the 340nm LED lamp and any one of 600nm-700nm provided by the wide spectrum LED lamp.

[0030] In some embodiments, the plurality of LED lamps each has a corresponding lower limit light power value; the lower limit light power value P1 of the 340nm LED lamp is the smallest among the lower limit light power values of the plurality of LED lamps.

[0031] In some embodiments, the plurality of LED lamps each has a corresponding standard use light power value, and the standard light power value of the 340nm LED lamp is lower than the standard light power value of the wide spectrum LED lamp.

[0032] In some embodiments, the standard use light power value of the 340nm LED lamp is not less than 1.2mW.

[0033] In some embodiments, the standard use light power value of the 340nm LED lamp is 1.2mW-2.5mW.

[0034] In some embodiments, the lower limit light power value P1 of the 340nm LED lamp is 0.06mW.

[0035] In some embodiments, the LED lamp set further comprises a 380nm LED lamp, and the lower limit light power value P1 of the 380nm LED lamp is the largest among the lower limit light power values of the plurality of LED lamps.

[0036] In some embodiments, the lower limit light power value P3 of the 380nm LED lamp is 0.7mW.

[0037] In some embodiments, the lower limit light power value of the plurality of LED lamps satisfies the following relationship: P1

[0038] P1 is the lower limit light power value of the 340 nm LED lamp;

[0039] P2 is the lower limit light power value of the wide spectrum LED lamp;

[0040] P3 is the lower limit light power value of the 380 nm LED lamp;

[0041] P4 is the lower limit light power value of the 405 nm LED lamp.

[0042] In some embodiments, at least one of the plurality of LED lamps and the colorimetric cup are arranged in a straight line when the colorimetric cup is in a detection position.

[0043] In some embodiments, the wide spectrum LED lamp, the combining unit and the colorimetric cup are arranged in a straight line when the colorimetric cup is in a detection position.

[0044] In some embodiments, the optical module further comprises a collimating device arranged between the light source unit and the combining unit; the collimating device is used to collimate the light beams emitted by each of the LED lamps to adjust the divergent light emitted by each of the LED lamps to parallel light.

[0045] In some embodiments, at least one of the plurality of LED lamps is configured to have a maximum divergence angle of no more than 30°.

[0046] In some embodiments, one or two of the plurality of LED lamps have a variable divergence angle of 0°-30°.

[0047] In some embodiments, one of the plurality of LED lamps has a variable divergence angle of 0°-15°.

[0048] In some embodiments, the collimating device comprises a plano-convex lens.

[0049] In some embodiments, the curvature radius and diameter of the plano-convex lens are matched with the corresponding LED lamp.

[0050] In some embodiments, the plano-convex lens on the light path of one of the plurality of LED lamps is compatible with a variable divergence angle of 20°-30° LED lamp.

[0051] In some embodiments, the plano-convex lens on the light path of one of the plurality of LED lamps is compatible with a variable divergence angle of 20°-30° LED lamp.

[0052] In some embodiments, the optical path of the optical module is designed such that the light emitted from each LED lamp has the same optical path distance from the collimating device to the cuvette.

[0053] In some embodiments, at least one of the light combining dichroic mirrors is arranged in one-to-one correspondence with at least one of the collimating devices and is located on the optical path of the corresponding collimating device.

[0054] In some embodiments, the cuvette has a light receiving surface and a light emitting surface, and the composite light converged by the light combining unit passes through the light receiving surface and the light emitting surface of the cuvette in sequence and then is split by the light splitting unit.

[0055] In some embodiments, a front diaphragm and a rear diaphragm are separately arranged at the positions corresponding to the light receiving surface and the light emitting surface, respectively; the front diaphragm is used to filter stray light irradiating the sample in the cuvette; and the rear diaphragm is used to filter the emergent light after the composite light passes through the sample.

[0056] The light splitting unit can sort the light filtered by the rear diaphragm into monochromatic light of corresponding wave bands for detection by the detection unit.

[0057] In some embodiments, when the sample is being detected, the front diaphragm, the cuvette and the rear diaphragm are arranged in a straight line, and the center of the front diaphragm and the center of the rear diaphragm are on the same straight line.

[0058] In some embodiments, the light passing area of the rear diaphragm is smaller than the light passing area of the front diaphragm.

[0059] In some embodiments, the front diaphragm and the rear diaphragm each have a circular light passing surface, and the diameter of the light passing surface of the front diaphragm is 1-3 times the diameter of the light passing surface of the rear diaphragm.

[0060] In some embodiments, the upper top of the light passing surface of the front diaphragm does not exceed the liquid level of the liquid in the cuvette when the sample analyzer is performing detection of the minimum reaction amount.

[0061] In some embodiments, the size of the parallel light spot entering the cuvette assembly is 2-3 mm.

[0062] In some embodiments, the size of the light spot entering the light splitting unit after passing through the cuvette assembly is 1-1.5 mm.

[0063] In some embodiments, the diameter D1 of the light passing surface of the front diaphragm satisfies 2 mm≤D1≤3 mm.

[0064] In some embodiments, the diameter D2 of the light passage surface of the rear diaphragm satisfies: 1mm≤D2≤1.5mm.

[0065] In some embodiments, the colorimetric assembly further comprises an incubation slot front window sheet and an incubation slot rear window sheet respectively located on two sides of the colorimetric cup, the front diaphragm is located on the side of the incubation slot front window sheet away from the colorimetric cup, and the rear diaphragm is located on the side of the incubation slot rear window sheet away from the colorimetric cup.

[0066] In some embodiments, the light combining unit comprises a lenticular lens, and the lenticular lens is arranged on the side of the rear diaphragm away from the incubation slot rear window sheet.

[0067] In some embodiments, the number of light combining dichroic mirrors is less than or equal to the number of LED lamps.

[0068] 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 wide-spectrum LED lamp, and one of the plurality of light combining dichroic mirrors can transmit the light of the 405nm LED lamp.

[0069] In some embodiments, when the LED lamp group further comprises a 380nm LED lamp, one of the plurality of light combining dichroic mirrors can reflect the light of the 380nm LED lamp.

[0070] In some embodiments, the transmittance T ave of the light combining dichroic mirror in the transmissive region is greater than or equal to 90%; or the reflectance T ave of the light combining dichroic mirror in the reflective region is less than or equal to 5%.

[0071] In some embodiments, the composite light formed by the light combining unit is expanded before irradiating the colorimetric cup; and the expanded composite light irradiates the sample in the colorimetric cup to complete the optical detection of the sample.

[0072] In some embodiments, an expander is arranged between the light combining unit and the colorimetric cup, and the diameter of the composite light is expanded by the expander.

[0073] The expander is configured to expand the composite light aggregated by the light combining unit, and the light emitted by each LED lamp has the same optical path distance from the flat light device to the expander.

[0074] In some embodiments, the composite light subjected to expansion is composite parallel light formed by combining parallel light obtained by flat light processing of the flat light device by the light combining unit.

[0075] The beam expander comprises a Galilean beam expander or a Keplerian beam expander; when the beam expander comprises a Galilean beam expander, the Galilean beam expander comprises a plano-concave lens and a double convex lens arranged in sequence; when the beam expander comprises a Keplerian beam expander, the Keplerian beam expander comprises two double convex lenses.

[0076] In some embodiments, the Galilean beam expander is capable of expanding the diameter of the composite light passing therethrough to m 12 times the original diameter;

[0077] In some embodiments, the Galilean beam expander is capable of expanding the diameter of the composite light passing therethrough to m 12 times the original diameter;

[0078] In some embodiments, the Galilean beam expander is capable of expanding the diameter of the composite light passing therethrough to m 12 times the original diameter;

[0079] In some embodiments, the Galilean beam expander is capable of expanding the diameter of the composite light passing therethrough to m 12 times the original diameter;

[0080] In some embodiments, the Keplerian beam expander is capable of expanding the diameter of the composite light passing therethrough to m 12 times the original diameter;

[0081] In some embodiments, the Keplerian beam expander is capable of expanding the diameter of the composite light passing therethrough to m 12 times the original diameter;

[0082] In some embodiments, the Keplerian beam expander is capable of expanding the diameter of the composite light passing therethrough to m 12 times the original diameter;

[0083] In some embodiments, the Keplerian beam expander is capable of expanding the diameter of the composite light passing therethrough to m 12 times the original diameter;

[0084] In some embodiments, a screening unit is arranged between the combining unit and the cuvette; the screening unit is configured to screen the composite light formed by the combining unit; and the screening range of the screening unit is the overlapping area of the composite light after the light emitted by the plurality of LED lamps passes through the combining unit.

[0085] In some embodiments, the overlapping area includes at least the light emitted by the 340 nm LED lamp and the light emitted by the wide-spectrum LED lamp.

[0086] In some embodiments, the LED lamp set further includes a 405 nm LED lamp; and the overlapping area includes the light emitted by the 340 nm LED lamp, the light emitted by the wide-spectrum LED lamp, and the light emitted by the 405 nm LED lamp.

[0087] In some embodiments, the distance from the corresponding flat light device of each LED lamp to the combining device is different; the light path length of each LED lamp inside the combining unit is different; and the light path distance from the flat light device to the output position of the combining unit for the light emitted by each LED lamp is the same.

[0088] In some embodiments, the flat light device is arranged between the LED lamps and the combining unit.

[0089] In some embodiments, the wide-spectrum LED lamp, the combining unit, and the cuvette in the detection position are arranged in a straight line.

[0090] In some embodiments, the wavelengths of the light emitted by the plurality of LED lamps can cover the wavelengths required for biochemical detection.

[0091] In some embodiments, the light screened by the screening unit is the parallel composite light after the flat light processing of the flat light device.

[0092] In one embodiment, the light emitting surface of the LED lamp faces the combining unit; the combining unit combines the light emitted by the plurality of 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 wave bands for detection by the detection unit; the composite light can cover the wavelengths required for biochemical detection; and the detection unit is configured to perform optical detection on the monochromatic light.

[0093] In some embodiments, the 340 nm LED lamp, the wide-spectrum LED lamp, and the 405 nm LED lamp are arranged in different planes, respectively.

[0094] In one embodiment, the planes in which the LED lamps are arranged are perpendicular to each other.

[0095] In one embodiment, when the LED lamp set 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.

[0096] In one embodiment, the wide-spectrum LED lamp, the combining unit and the cuvette in the detection position are arranged in a straight line.

[0097] In one embodiment, the LED lamp set further comprises a 380 nm LED lamp, and the light emitting surface of each LED lamp faces the combining unit.

[0098] In one embodiment, the 380 nm LED lamp is arranged in a different plane from the 340 nm LED lamp, the wide-spectrum LED lamp and the 405 nm LED lamp; wherein 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 located is perpendicular to the plane in which the other LED lamps are located.

[0099] In one embodiment, the lamp beads of at least two LED lamps of the plurality of LED lamps are in the same height plane or in the same cross section.

[0100] In one embodiment, at least one other LED lamp of the plurality of LED lamps is in a plane parallel to the height plane or the cross section.

[0101] In one embodiment, the combining unit has at least two light receiving surfaces, and the combining unit receives light emitted by the corresponding LED lamp through the light receiving surfaces.

[0102] The combining unit converges the light emitted by the plurality of 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.

[0103] In one embodiment, the light receiving surfaces can reflect and / or transmit light of different wavelengths; and the light emitted by the LED lamp set is converged into composite light after being reflected or transmitted by at least two light receiving surfaces.

[0104] In one embodiment, the combining unit comprises a combining dichroic mirror mounting seat and a plurality of combining dichroic mirrors, the combining dichroic mirror mounting seat is used to integrate the plurality of combining dichroic mirrors, and the plurality of combining dichroic mirrors are respectively used as light receiving surfaces of the combining unit.

[0105] In one embodiment, the combining dichroic mirrors are respectively mounted on mounting positions of different sides of the combining dichroic mirror mounting seat.

[0106] In one embodiment, the light combining dichroic mirror mounts have a plurality of inclined surfaces, the number of the inclined surfaces corresponding to the number of the light combining dichroic mirrors respectively, each of the light combining dichroic mirrors being mounted on a corresponding inclined surface.

[0107] In one embodiment, the number of the light combining units is less than the number of the LED lamps in the LED lamp group.

[0108] In one embodiment, the LED lamp group is provided with a temperature maintaining module, which is capable of maintaining each of the LED lamps in the LED lamp group within a preset temperature range.

[0109] In one embodiment, the optical module further comprises a light combining device, the light combining device comprising an optical mount, the LED lamps being mounted in the optical mount, the temperature maintaining module being capable of cooling the LED lamps.

[0110] In one embodiment, the temperature maintaining module comprises a cooling flow channel for cooling the LED lamps.

[0111] In one embodiment, an incubation module is further included, the incubation module being used for accommodating a cuvette, and providing an incubation environment for a sample and a reagent 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.

[0112] In one embodiment, the temperature fluctuation of the incubation water is ±0.1℃.

[0113] In one embodiment, 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 a sample in the cuvette to form outgoing light, and the light separating unit separates the outgoing light into monochromatic light of corresponding wave bands for detection by the detection unit.

[0114] In one embodiment, the number of the monochromatic light separated by the light separating unit is the same as the number of the corresponding wavelengths required by the biochemical detection.

[0115] In one embodiment, the light separating unit comprises a first light separating dichroic mirror, the first light separating dichroic mirror being capable of separating the outgoing light into two beams of light in different directions; the two beams of light have non-overlapping wavelengths.

[0116] In one embodiment, the light separating unit further comprises a plurality of dichroic mirrors arranged on one of the light paths after the light is separated by the first light separating dichroic mirror, and a plurality of dichroic mirrors arranged on the other light path after the light is separated by the first light separating dichroic mirror.

[0117] In one embodiment, the first light-splitting dichroic mirror is capable of splitting the emergent light into two beams of light in perpendicular directions by means of transmission and refraction when the first light-splitting dichroic mirror splits the emergent light into two beams of light in different directions.

[0118] In one embodiment, the deflection directions of the plurality of dichroic mirrors arranged on any one of the two light paths after the splitting of the first light-splitting dichroic mirror are the same.

[0119] In one embodiment, the optical module is configured with a mirror on the light-emitting side of the cuvette; the mirror is capable of changing the propagation direction of the emergent light.

[0120] In one embodiment, the light-receiving surface is capable of reflecting and / or transmitting light of different wavelengths; the light emitted by the LED lamp group converges into composite light after being reflected or transmitted by the plurality of light-receiving surfaces.

[0121] In one embodiment, the light-combining unit comprises a light-combining dichroic mirror mounting seat and the plurality of light-combining dichroic mirrors, the light-combining dichroic mirror mounting seat is used to integrate the plurality of light-combining dichroic mirrors; the light-combining dichroic mirror serves as the light-receiving surface of the light-combining unit.

[0122] In one embodiment, the number of light-combining dichroic mirrors is less than or equal to the number of LED lamps in the LED lamp group.

[0123] In one embodiment, the cooling flow channel corresponds to the number of LED lamps in the LED lamp group one-to-one, so as to realize individual cooling for each LED lamp in the LED lamp group.

[0124] In one embodiment, the cooling flow channel penetrates through the optical seat to individually cool each LED lamp in the LED lamp group.

[0125] In one embodiment, the cooling flow channel comprises one or more water outlets and one or more water inlets.

[0126] In one embodiment, at least one LED lamp is arranged in a straight line with the light-combining unit and the cuvette rotated to the detection position; the mirror adjusts the emergent light to be in a direction perpendicular to the straight line in which the LED lamp, the light-combining unit and the cuvette are arranged, and the direction is perpendicular to the placement surface of the sample analyzer.

[0127] In one embodiment, a corresponding focusing unit is arranged in the light path of the exit light to the mirror; the focusing unit is used to focus the exit light containing transmitted light, refracted light and reflected light; a flat mirror is arranged between the mirror and the light splitting assembly; the flat mirror is used to flatten the focused exit light; and the exit light is sorted into monochromatic light of corresponding wave bands by the light splitting assembly for detection by the detection unit.

[0128] In one embodiment, the first light splitting dichroic mirror and the dichroic mirror have a transmittance Tave≥90% in the transmission region or a transmittance Tave≤5% in the reflection region.

[0129] In one embodiment, the light splitting unit further comprises a plurality of narrowband filters, which are respectively arranged in one-to-one correspondence with each dichroic mirror.

[0130] In one embodiment, the light combining unit comprises a light combining dichroic mirror mounting seat and a plurality of light combining dichroic mirrors, the light combining dichroic mirror mounting seat is used to integrate the plurality of light combining dichroic mirrors; and the light combining dichroic mirror serves as a light receiving surface of the light combining unit.

[0131] In one embodiment, the exit light is sorted into monochromatic light of corresponding wave bands by the light splitting unit for detection by the detection unit.

[0132] In one embodiment, the cooling flow channel corresponds to the number of LED lamps in the LED lamp group in one-to-one correspondence, so as to realize individual cooling for each LED lamp in the LED lamp group.

[0133] In one embodiment, the cooling flow channel penetrates through the optical seat to cool each LED lamp in the LED lamp group, respectively.

[0134] In one embodiment, the lamp beads of at least two LED lamps in the plurality of LED lamps are in the same height plane or in the same cross section.

[0135] Compared with the prior art, the photodiode has different lower limit optical power values or lower limit optical power values for different wavelengths, and the optical performance index of the optical module is much higher than the industry standard when biochemical detection is performed. BRIEF DESCRIPTION OF DRAWINGS

[0136] In the following, the utility model will be described in more detail based on the embodiments and with reference to the drawings.

[0137] Figure 1 is a structural schematic view of a chemical analyzer in the embodiments of the utility model;

[0138] Figure 2 is the relative spectral radiation diagram of the wide-spectrum LED lamp;

[0139] Figure 3 is the light source light path plane schematic diagram of the chemical analyzer in the embodiment of the utility model;

[0140] Figure 4 is the structural schematic diagram of the galileo type beam expander in one of the embodiments of the utility model;

[0141] Figure 5 is the structural schematic diagram of the kepler type beam expander in another embodiment of the utility model;

[0142] Figure 6 is the light source light path three-dimensional structure diagram of the chemical analyzer in the embodiment of the utility model;

[0143] Figure 7 is the three-dimensional structure schematic diagram of the light combiner dichroic mirror mounting seat in the embodiment of the utility model;

[0144] Figure 8 is the three-dimensional structure schematic diagram of the optical seat in the embodiment of the utility model;

[0145] Figure 9 is the structural schematic diagram of the cooling flow channel in the embodiment of the utility model;

[0146] Figure 10 is the optical path schematic diagram of the first LED lamp in the embodiment of the utility model;

[0147] Figure 11 is the optical path schematic diagram of the second LED lamp in the embodiment of the utility model;

[0148] Figure 12 is the optical path schematic diagram of the third LED lamp or the fourth LED lamp in the embodiment of the utility model;

[0149] Figure 13 is the structural schematic diagram of the colorimetric assembly in the embodiment of the utility model;

[0150] Figure 14 is the structural diagram of the reflected light beam after gathering in the embodiment of the utility model;

[0151] Figure 15 is the structural diagram of the light splitting unit in one of the embodiments of the utility model;

[0152] Figure 16 is the structural diagram of the light splitting unit in another embodiment of the utility model;

[0153] Figure 17The structure of the spectrometer unit of the sample analyzer in the preferred embodiment of the utility model is intended.

[0154] Figure 18 The structure of the spectrometer unit of the another embodiment of the utility model is intended.

[0155] Figure 19 The structure of the spectrometer unit of the still another embodiment of the utility model is intended.

[0156] Figure 20 The structure of the optical module of the sample analyzer in the embodiment of the utility model is intended.

[0157] Reference signs:

[0158] 1, sample module; 11, sample rack; 12, sample tube;

[0159] 2, sample dispensing module;

[0160] 3, reagent module; 31, reagent bin; 32, reagent box;

[0161] 4, reagent dispensing module; 6, mixing module;

[0162] 7, optical module; 71, light-combining dichroic mirror mounting seat; 711, mounting groove; 72, optical seat; 721, containing cavity; 73, water outlet; 74, water inlet; 75, plug;

[0163] 8, incubation module; 9, cleaning module; 10, ISE analysis assembly; 15, reagent box;

[0164] 100, first LED lamp; 101, second LED lamp; 102, third LED lamp; 103, fourth LED lamp;

[0165] 104, first plano-convex lens; 105, second plano-convex lens; 106, third plano-convex lens; 107, fourth plano-convex lens;

[0166] 110, first light-combining dichroic mirror; 108, second light-combining dichroic mirror; 109, third light-combining dichroic mirror;

[0167] 111, plano-concave lens;

[0168] 112, 118: double convex lens;

[0169] 113, front diaphragm; 114, incubation groove front window piece; 115, colorimetric cup; 116, incubation groove rear window piece; 117, rear diaphragm;

[0170] 119, reflector; 120, fifth plano-convex lens; 121, plano-photodiaphragm; 122, first light-splitting dichroic mirror;

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

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

[0173] 150, detector; 160, concave diffraction grating. DETAILED DESCRIPTION

[0174] The utility model will be further described below with reference to the drawings.

[0175] The utility model provides a sample analyzer (or can be called biochemical analyzer), it is a kind of instrument for detecting, analyzing life chemical substance, to provide information basis for the diagnosis, treatment and prognosis and health status of disease in clinic.For example Figure 1 As shown, sample analyzer includes the sample module 1 for carrying sample, the sample dispensing module 2 for sucking and discharging sample, the reagent module 3 for carrying reagent, the reagent dispensing module 4 for sucking and discharging reagent, the reaction assembly including cuvette 5, the mixing module 6 for mixing reagent and sample in cuvette 5, the incubation module 8 for incubating reagent and sample in cuvette 5, the cleaning module 9 for cleaning cuvette 5 and the optical module 7 for detection.In addition, sample analyzer can also include ISE analysis assembly 10, i.e. electrolyte module, for detecting the concentration of Na + , K + , Cl - Ion in patient sample.In addition, a plurality of reagent boxes are arranged in sample analyzer for containing different reagents.

[0176] As shown in Figure 1 , sample module 1 includes sample holder 11 and sample tube 12 on sample holder 11. Among them, track system is used to carry sample tube containing sample through sample track 13, and sampling is carried out during carrying, and sample holder is recycled through recovery track 14 after sampling is completed.Reagent module 3 includes reagent bin 31 and reagent box 32 in reagent bin 31.

[0177] The optical module 7 of the sample analyzer generally includes a light source unit, a combination unit, a light splitting unit, and a detection unit. The detection principle of the optical module 7 is based on the Lambert-Beer law to detect the absorbance of different wavelengths. According to the Lambert-Beer law, when a parallel monochromatic light passes through a uniform non-scattering absorbent substance vertically, the absorbance A is proportional to the concentration c and the absorption layer thickness L of the absorbent substance, and inversely proportional to the transmittance T, that is, the absorbance A satisfies the following expression:

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

[0179] Wherein, A is the absorbance, abbreviated as Abs / OD, unitless;

[0180] T is the transmittance;

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

[0182] b is the solution thickness, cm;

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

[0184] Io is the transmitted light intensity, cd (Candela / New Candle);

[0185] It is the incident light intensity, cd.

[0186] When performing biochemical tests, the absorbance is converted into a concentration result. The optical module 7 calculates the absorbance by detecting the light intensity change (light beam transmission) of the measured object. Therefore, it can be known that the stability of the light source energy is crucial for the accuracy of the test results when performing biochemical tests. Because biochemical detection requires complex light in the wavelength range of 340nm-800nm, specifically, wavelengths of 340nm, 380nm, 405nm, 450nm, 480nm, 505nm, 546nm, 570nm, 600nm, 660nm, 700nm, 750nm and 800nm are required. In particular, the 340nm wavelength is extremely common in biochemical detection, and is used as the main wavelength for many detection projects to calculate the results.

[0187] The optical module 7 comprises a plurality of light source units, and the light source unit is an LED lamp group composed of a plurality of LED lamps, and the effect of complex light can be achieved by using the combination of a plurality of LED lamps. The number of LED lamps may be, for example, 2, 3, 4 or more. Further, the plurality of LED lamps are a combination of a plurality of single-color LED lamps and one or more wide-spectrum LED lamps. For example, the LED lamp group comprises 340nm LED lamps, wide-spectrum LED lamps, 405nm LED lamps and 380nm LED lamps. The beam combining unit can combine the light emitted by the plurality of LED lamps; the beam splitting unit can sort the composite light combined by the beam combining unit into single-color light of the corresponding wave band for the detection unit to detect. The composite light can cover the required wavelength for biochemical detection; and the detection unit is used for optical detection of the single-color light.

[0188] The industry standard requires that the optical module 7 needs to meet certain optical performance indicators, including stray light, absorbance linear range, absorbance accuracy, absorbance stability and absorbance repeatability. Each indicator has a corresponding absorbance requirement, and the industry standard and the optical performance indicators of the instrument design are shown in Table 1.

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

[0190]

[0191] The lower limit of the light energy value required for biochemical detection needs to consider multiple factors, such as light source parameters, instrument optical performance indicator parameters, lower limit range of the light signal received by the detector, detection sensitivity, noise level, signal-to-noise ratio of the data acquisition system, etc. The existing biochemical detector can only simply meet the lower limit of several optical performance indicators required by the above industry standard, and the detection performance needs to be improved.

[0192] In some embodiments of the present application, the optical performance indicator parameters of the optical module 7 at least meet 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 one of the 340nm wavelength provided by the 340nm LED lamp and the 450nm-520nm wavelength provided by the wide-spectrum LED lamp, the absorbance linear range is: the maximum absorbance with a relative bias within ±5% is ≥4.0;

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

[0196] The absorbance stability is that the change of absorbance is not more than 0.01 when measuring any one of 340nm and 600nm-700nm provided by a 340nm LED lamp and a wide-spectrum LED lamp respectively; and

[0197] The absorbance repeatability is that the coefficient of variation CV is less than or equal to 0.4% when measuring the 340nm wavelength provided by a 340nm LED lamp.

[0198] The optical performance indexes of the optical module 7 of the utility model are shown in Table 2 below.

[0199] Table 2: Optical performance index list of the optical module 7 of the utility model

[0200] .

[0201] According to Table 1 and Table 2, the optical performance indexes of the optical module 7 of the utility model are much higher than the requirements of the industry standard, and the detection performance is greatly improved.

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

[0203] Table 3: Absorbance linear range list of the optical module 7

[0204]

[0205]

[0206] According to Table 3, when the optical module 7 of the utility model measures the 340nm wavelength provided by a 340nm LED lamp, the absorbance linear range is that the maximum absorbance with a relative bias of-1.03% is greater than or equal to 4.18; when measuring the 450nm wavelength provided by a wide-spectrum LED lamp, the absorbance linear range is that the maximum absorbance with a relative bias of 1.52% is greater than or equal to 4.13; when measuring the 480nm wavelength provided by a wide-spectrum LED lamp, the absorbance linear range is that the maximum absorbance with a relative bias of 3.64% is greater than or equal to 4.13; when measuring the 505nm wavelength provided by a wide-spectrum LED lamp, the absorbance linear range is that the maximum absorbance with a relative bias of 0.33% is greater than or equal to 4.17.

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

[0208] When performing optical detection, the minimum light power of the monochromatic light of 340nm wavelength that the detection unit can receive is lower than the minimum light power of the monochromatic light of 405nm wavelength. The number of detection units is the same as the number of monochromatic light divided by the light splitting unit.

[0209] The detection unit of the optical module 7 includes a detector, which includes a photodiode (PD). The photodiode can receive monochromatic light sorted by the light sorting unit. Different photodiodes have different photosensitivity coefficients for different wavelengths, and the photosensitivity coefficients of the photodiodes corresponding to the wavelengths also directly affect the lower limit values that can be detected by the photodiodes.

[0210] The lower limit requirement of the light energy values of the photodiode at different wavelengths is characterized by the optical power and / or the photocurrent of the photodiode.

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

[0212] When the 340nm wavelength provided by the 340nm LED lamp is measured, the optical power of the photodiode is greater than or equal to 5.28x10 -2 μw (i.e., the lower limit value of the optical power is 5.28x10 -2 μw), and / or the photocurrent of the photodiode is greater than or equal to 10.98nA (i.e., the lower limit value of the photocurrent is 10.98nA).

[0213] Further, when other wavelengths are measured, the lower limit values of the optical power and the photocurrent of the photodiode are shown in Table 4 below.

[0214] Table 4: Summary of the lower limit values of the photocurrent of the photodiode satisfying biochemical detection

[0215]

[0216] The absorbance linear range in the above Table 3 is an especially important parameter index. Because the absorbance linear range represents the upper limit value of the absorbance that can be detected by the sample analyzer, the greater the absorbance value, the weaker the light intensity of the transmitted light through the to-be-measured object, i.e., the stronger the absorption of the to-be-measured solution to the wavelength, which indirectly reflects the lower limit value of the light intensity that can be measured by the photodiode, so that the lower limit requirement of the light energy values of the photodiode at different wavelengths can be obtained.

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

[0218] In addition, it should be noted that the dark current value of the photodiode is generally less than 50pA; the bottom noise dark current brought by the circuit and the external environment to the photodiode is not more than 100pA (1pA = 10 -12 A).

[0219] As shown in Table 5, the maximum bottom noise photocurrent and optical power value corresponding table of photodiodes of different wavelengths is shown. Among them, the maximum bottom noise is the conversion obtained under the condition that the circuit amplification multiple is adjustable maximum.

[0220] Table 5 Maximum bottom noise optical power and photocurrent value corresponding table of photodiodes under different wavelengths

[0221]

[0222] In the selection of photodiodes, the optical power and / or photocurrent is at least greater than the maximum bottom noise optical power and photocurrent value in Table 5 above; or the dark current of the photodiode is less than 50pA.

[0223] In summary, the optical performance index of the optical module 7 of the utility model is far higher than the industry standard, and the utility model proposes that the photodiode of the optical module 7 needs to meet the lower limit value of optical power and / or photocurrent.

[0224] The existing sample analyzer generally uses a halogen lamp as a light source to obtain the required wavelength, or uses a combination of a halogen lamp and an LED lamp to obtain the required wavelength, but these existing solutions cannot solve the problems of short halogen lamp life, frequent maintenance and long preheating time when used.

[0225] In view of the above problems, the utility model provides: the optical module 7 includes a plurality of light source units, and the wavelengths of the light emitted by the plurality of light source units can cover the wavelengths required for biochemical detection, wherein the light source includes a plurality of LED lamps. The utility model can achieve the effect of polychromatic light by using the combination of a plurality of LED lamps. The number of LED lamps may be, for example, 2, 3, 4 or more. Further, the plurality of LED lamps are a combination of a plurality of single-color LED lamps and one or more wide-spectrum LED lamps.

[0226] For LED light sources, the light beam of the wavelength used for biochemical detection also needs to meet a certain optical power 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 the absorbance that the instrument can detect. The greater the absorbance value, the weaker the transmitted light intensity through the measured object, i.e. the stronger the absorption of the measured solution to the wavelength, which indirectly reflects the lower limit of the light intensity that the optical module 7 can measure, so that the lower limit of the energy at the light source end can be obtained.

[0227] When optical detection is performed, the minimum light power of monochromatic light of 340 nm wavelength received by the detection unit is lower than the minimum light power of monochromatic light of 405 nm wavelength. The plurality of LED lamps respectively have corresponding lower limit light powers, and the lower limit light power value P1 of the 340 nm LED lamp is the smallest among the lower limit light power values of the plurality of LED lamps. In addition, the plurality of LED lamps respectively have corresponding standard use light powers, and the standard light power of the 340 nm LED lamp is lower than the standard light power of the wide spectrum LED lamp. The standard use light power of the 340 nm LED lamp ranges from 1.2 mW to 2.5 mW.

[0228] In addition, the wide spectrum LED lamp provides wavelengths of 450 nm-800 nm, which are excited by 450 nm as excitation light to excite other wavelengths. Therefore, the relative radiation intensity of different wavelengths is not consistent, and the relative spectral radiation diagram of the wide spectrum LED lamp is as shown in Figure 2 Figure 2 The abscissa is wavelength, and the ordinate is relative radiation intensity. As can be seen from Figure 2 , the peak wavelength is 450 nm, the relative radiation intensity is 100%, and the relative radiation intensities of the wavelengths of 480 nm and 660 nm are the lowest, being 9.5% and 5% respectively. Therefore, the lower limit of the wide spectrum light energy needs to focus on the wavelengths with low relative radiation intensity, that is, the light intensity of the wavelength with the lowest relative radiation intensity needs to meet the requirements, so that the corresponding biochemical detection can be performed.

[0229] The lower limit requirement of the energy value of the light source is characterized by the light power value.

[0230] Further, the lower limit light power value P1 of the 340 nm LED lamp providing a wavelength of 340 nm is the smallest, that is, smaller than the lower limit light power values of the LED lamps providing other wavelengths.

[0231] Further, the lower limit light power value P3 of the 380 nm LED lamp providing a wavelength of 380 nm is the largest, that is, larger than the lower limit light power values of the LED lamps providing other wavelengths.

[0232] Further, the lower limit light power value P1 of the 340 nm LED lamp providing a wavelength of 340 nm is 0.06 mW. The lower limit light power value P3 of the LED lamp providing a wavelength of 380 nm is 0.7 mW.

[0233] Further, the lower limit light power value P4 of the 405 nm LED lamp providing a wavelength of 405 nm is 0.5 mW. The lower limit light power value P2 of the wide spectrum LED lamp providing wavelengths of 450 nm-800 nm is 0.16 mW. ​

[0234] The lower limit light power value of the LED is shown in Table 6 below.

[0235] Table 6: List of lower limit light power values of the LED

[0236]

[0237] The lower limit light power value of the LED satisfies the following conditions: P1 < P2 < P4 < P3.

[0238] Further, since each LED lamp has its own power supply current range, the light power of each LED lamp linearly changes with respect to the available power supply current. Therefore, the light power of each LED lamp can be adjusted accordingly according to the usage. For example, selecting a larger light power value and combining a small amplification factor to obtain a digital signal as the initial value of detection can make the optical module 7 have a larger adjustable space (adjustable power supply current and adjustable circuit amplification factor), thereby achieving the purpose of improving the service life of the optical module 7.

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

[0240] In summary, the utility model proposes a technical scheme of using multiple LED lamps as light sources. The service life of the LED lamp can reach 20,000 to 50,000 hours or even longer, so it can completely solve the problems of short service life, frequent maintenance and long preheating time of halogen lamps, thereby providing an effective solution for the precision level of the sample analyzer in the clinical detection project test process to reach or even exceed that of the halogen lamp as a light source. Moreover, the utility model proposes that the lower limit light power value P1 of the 340 nm LED lamp is the smallest, for example, it can be 0.06 mW, and its optical performance index is much higher than the industry standard.

[0241] As described above, the multiple LED lamps of the utility model include multiple monochromatic LED lamps and one or more wide-spectrum LED lamps. Specifically, the multiple LED lamps include a combination of three monochromatic LED lamps and one wide-spectrum LED lamp.

[0242] As Figure 3As shown, an example of four LED lamps is shown. Among them, the four LED lamps are respectively a first LED lamp 100, a second LED lamp 101, a third LED lamp 102 and a fourth LED lamp 103, wherein one LED lamp is a wide-spectrum LED lamp, and the other LED lamps are single-color LED lamps; the wavelength range of the light emitted by the plurality of LED lamps includes 340nm-800nm.

[0243] More specifically, the second LED lamp 101 is a wide-spectrum LED lamp, and can provide a wavelength of 450nm-800nm. The first LED lamp 100 can provide a wavelength of 340nm, the third LED lamp 102 can provide a wavelength of 380nm, and the fourth LED lamp 103 can provide a wavelength of 405nm, so as to meet the requirement of being able to cover the wavelength required for the above biochemical detection.

[0244] Further, at least one LED lamp is arranged in a straight line with the cuvette 115 at the detection position. Specifically, as shown in Figure 3 As shown, the wide-spectrum LED lamp is arranged in a straight line with the cuvette 115 at the detection position. The wide-spectrum LED lamp 101 is arranged in a straight line with the combining unit and the cuvette 115 at the detection position of the cuvette 115.

[0245] It can be understood that other waveband LED lamps can also be selected for combination, as long as they can cover the wavelength of 340nm-800nm required for biochemical detection.

[0246] The utility model discloses in order to meet the requirement of covering the wavelength required for the above biochemical detection, adopt the mode of different LED lamp combination, but different LED lamp combination uses, and each will have different divergence angle, therefore there is the problem of non-uniformity after light combination, and this problem can directly influence the test result of the clinical project of sample analyzer, and lead to the precision of complete machine to be poor.

[0247] In view of the above problem, the utility model provides a kind of broadband light source optical path scheme capable of meeting 340nm-800nm wavelength of sample analyzer, which aims at solving the problem of poor light beam uniformity caused by different LED lamps due to different divergence angles.

[0248] Specifically, the optical module 7 of the utility model includes flat light device, and the light device is used to carry out flat light processing on the light beam emitted by each LED lamp, to adjust the divergent light emitted by each LED lamp into parallel light. Flat light device is respectively arranged in one-to-one correspondence with each LED lamp, and each flat light device is arranged on the light path of the corresponding LED lamp, for carrying out flat light processing on the light beam emitted by the LED lamp with a certain light-emitting angle.

[0249] Further, the flat light device can be a plano-convex lens, for example.

[0250] AsFigure 3 As shown, the flat light devices are respectively a first flat convex lens 104 on the light path of the first LED lamp 100, a second flat convex lens 105 on the light path of the second LED lamp 101, a third flat convex lens 106 on the light path of the third LED lamp 102, and a fourth flat convex lens 107 on the light path of the fourth LED lamp 103. The curvature radius and diameter of each flat convex lens are matched with the corresponding LED lamp.

[0251] At least one of the plurality of LED lamps has a maximum divergence angle of no more than 30°, one or two of the plurality of LED lamps has a variable divergence angle of 0°-30°, or one of the plurality of LED lamps has a variable divergence angle of 0°-15°.

[0252] Further, in order to achieve the principle of reducing the types of optical elements on the light path as much as possible, 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 lamp 100 is 0°-30°;

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

[0255] The variable divergence angle of the third LED lamp 102 and the fourth LED lamp 103 is 0°-15°.

[0256] The variable divergence angle of the above-mentioned four LED lamps is selected within a certain variable range, so that the selection of LED lamps is more flexible and has replaceability.

[0257] Further, the curvature radius and diameter of the flat light device should be matched with the corresponding LED lamp to perform flat light within a certain optical path distance. For example, the second flat convex lens 105 on the light path of the second LED lamp 101 can be compatible with LED lamps with a variable divergence angle within the range of 20°-30°. The third flat convex lens 106 and the fourth flat convex lens 107 on the light path of the second flat convex lens 105 for the third LED lamp 102 and the fourth LED lamp 103 can perform small-angle beam parallel processing.

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

[0260] As mentioned above, this utility model 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 issues, the optical module 7 of this invention also 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 goal 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 light-combining dichroic mirror 108 can transmit the light emitted by the second LED lamp 101 and reflect and transmit the light reflected by the third light-combining dichroic mirror 109 (i.e., the second light-combining dichroic mirror 108 transmits light in the wavelength band of 439 nm to 812 nm and reflects light in the wavelength band of 369 nm to 416 nm).

[0266] The third light-combining 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 (i.e., the third light-combining dichroic mirror 109 transmits light in the wavelength band of 398 nm to 812 nm and reflects light in the wavelength band of 368 nm to 387 nm).

[0267] In addition, the above-mentioned light-combining dichroic mirror has a transmittance Tave≥90% in the transmission region and a Tave≤5% (i.e., a reflectance of 95% or more) in the reflection region.

[0268] As shown in FIG. 1, for the light beam emitted by the first LED lamp 100, after the light beam passes through the flat light of the first plano-convex lens 104, the light beam is directed to the first light-combining dichroic mirror 110. Since the first LED lamp 100 emits a light beam with a wavelength of 340 nm, the light beam is reflected by the first light-combining dichroic mirror 110. Figure 3

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

[0270] For the light beam emitted by the third LED lamp 102, after the light beam passes through the flat light of the third plano-convex lens 106, the light beam is directed to the third light-combining dichroic mirror 109. Since the third LED lamp 102 emits a light beam with a wavelength of 380 nm, the light beam is reflected by the third light-combining dichroic mirror 109; the reflected light beam is directed to the first light-combining dichroic mirror 110, and thus the light beam is transmitted by the first light-combining dichroic mirror 110.

[0271] For the light beam emitted by the fourth LED lamp 103, after the light beam passes through the flat light of the fourth plano-convex lens 107, the light beam is directed to the third light-combining dichroic mirror 109. Since the fourth LED lamp 103 emits a light beam with a wavelength of 405 nm, the light beam is transmitted by the third light-combining dichroic mirror 109; the transmitted light beam is directed to the first light-combining dichroic mirror 110, and thus the light beam is transmitted by the first light-combining dichroic mirror 110.

[0272] ​It can be understood that as the light source for detection, the LED lamp capable of covering the wave band of 340nm-800nm can be selected for combination, and the light combining dichroic mirror with the wave band range selected according to the wave band of the LED lamp can still achieve the same effect of the utility model.

[0273] In summary, the utility model discloses a light combining dichroic mirror, which can combine the parallel light of four LED lamps into the same light beam after shaping, thereby obtaining the complex color light of 340nm-800nm wave band required for biochemical detection.

[0274] In addition, the mutual combination of the LED lamps with variable divergence angles, the short light path flat light processing and the beam combining can avoid the problem that the angle error is introduced when the light beam with angle enters the light combining dichroic mirror, thereby affecting the quality of the beam combining.

[0275] As described above, the utility model obtains the complex color light of 340nm-800nm wave band required for biochemical detection through the light combining device. However, the light beam aperture after flat light is different due to the different light emitting angles of the LED lamps, and if the light beams with different apertures are directly imaged, the light beam uniformity cannot be guaranteed, the degree of light quantity change of different wavelengths is obviously different, and the precision of the double-wavelength test project in the sample analyzer can be seriously affected, so the selection of the complex color light needs to be considered.

[0276] The utility model discloses a light beam uniformity after the light combining of different LED lamps and the degree of light quantity change are equivalent, so that the whole machine test can achieve the detection effect of the halogen lamp as the light source, and the utility model concept of the beam expansion design is proposed. Through the beam expansion design, the light beam of the parallel light after shaping of different paths can be expanded, so that the light beams with different aperture sizes have a larger overlapping area, and then the light beam size suitable for the sample analyzer is selected in the completely overlapping area and detected, at this time, for the measured object, the collimation degree of the received light beam is close to the ideal light beam, so the uniformity can also be optimal.

[0277] Specifically, the optical module 7 includes a beam expander in the light path after light combining. The beam expander can perform beam expansion processing on different light beams of the flat light part, thereby providing collimated light for the measured object. More specifically, the beam expander is located between the first light combining dichroic mirror 110 and the measured object, in other words, the light beam after beam expansion by the beam expander can irradiate the measured object for detection.

[0278] Preferably, in the example as shown in the figure, Figure 4 The Galilean beam expander includes a flat-concave lens 111 and a double-convex lens 112 arranged in sequence in the light path after light combining, which can amplify the light beams with different thicknesses, so that the overlapping area of the four LED lamps is significantly improved.

[0279] As Figure 4 shown, the focal length of the plano-concave lens 111 is f1, and the focal length of the double convex lens 112 is f2, so the light beam passing through the Galilean beam expander is expanded to m 12 times (wherein m 12 =f2 / f1) of the original. The divergence angle of the light beam after the Galilean beam expander is m 12 times smaller than the divergence angle entering the Galilean beam expander, and since the light beam entering the Galilean beam expander is parallel light after shaping and combining, the collimation of the parallel light received by the object to be measured in the overlapping area is close to the ideal light beam, and the uniformity can also be optimal.

[0280] Optionally, in the example as Figure 5 shown, the beam expander is a Keplerian beam expander. The Keplerian beam expander includes two double convex lenses, namely Figure 5 111-1 and 112-1 as shown.

[0281] The focal length of one of the double convex lenses is f1, and the focal length of the other double convex lens 112 is f2, so the light beam passing through the Keplerian beam expander is also expanded to m 12 times (wherein m 12 =f2 / f1) of the original. The divergence angle of the light beam after the Keplerian beam expander is m 12 times smaller than the divergence angle entering the Keplerian beam expander, and since the light beam entering the Keplerian beam expander is parallel light after shaping and combining, the collimation of the parallel light received by the object to be measured in the overlapping area is close to the ideal light beam, and the uniformity can also be optimal.

[0282] In summary, by setting a beam expander in the light path after combining, the light beam of the parallel light after shaping can be expanded to increase the overlapping area of light beams of different aperture sizes, so that the collimation of the light beam irradiated onto the object to be measured is close to the ideal light beam, that is, the uniformity of the light beam is ensured, thereby improving the precision of the double-wavelength test project in the sample analyzer.

[0283] As described above, according to the utility model concept of combining and expanding, the utility model obtains a uniform light beam for detection through the combining device and the beam expander. When designing the optical structure, all optical elements are usually laid out on a plane for the convenience of observation and calculation, but if the positions of the optical structure are designed according to this optical scheme, problems such as light source lamp panel interference and large occupied area of the optical structure may occur.

[0284] For example, in the optical design of 3 or 4 LED lights, in order to balance the light path design and energy, two LED lights are arranged with small distance between the same direction lamp shafts, if the bases of the two LED lights are in the same plane, the two LED lights can be arranged by welding on the same circuit board; if the bases of the two LED lights are in different planes, a circuit board needs to be welded for each LED light, at this time, the circuit board and the circuit board or the circuit board and other structures are easy to interfere with each other.

[0285] Therefore, in order to solve this problem, the utility model discloses the utility model concept of the three-dimensional layout of each LED light for the specific layout of each LED light and other optical elements, so as to achieve the purpose of miniaturization.

[0286] In the utility model, the number of LED lights is greater than or equal to 3. Wherein, the lamp panels of each LED light are respectively on different planes in the rectangular space coordinate system, for example, the lamp panels of three LED lights are respectively on three mutually perpendicular planes in the rectangular space coordinate system.

[0287] Further, the lamp beads of at least two LED lights can be in the same height plane or in the same section; further, at least one other LED light is in a plane parallel to the height plane or the section.

[0288] As shown in the example of Fig. Figure 6 As shown in Fig. Figure 4 The first LED light 100, the second LED light 101, the third LED light 102 and the fourth LED light 103 are respectively on the back plane, the left plane, the front plane and the bottom plane in the rectangular space coordinate system. And wherein, the first LED light 100, the second LED light 101 and the third LED light 102 are respectively in the same height plane.

[0289] Through this arrangement, the interference between the lamp panels or the lamp panels and other structures in the prior art is avoided; and the LED lights are arranged in three dimensions, so that the occupied area of the entire optical structure is smaller, thereby facilitating the miniaturization of the sample analyzer.

[0290] In summary, the utility model arranges each LED light in three dimensions, which not only avoids interference problems, but also reduces the volume, so that the sample analyzer meets the miniaturization requirements.

[0291] When all the optical elements are arranged in three dimensions, the specific installation method of the light combining dichroic mirror needs to be considered.

[0292] As shown in Fig. Figure 7As shown, the optical module 7 further comprises a light combining unit, the light combining unit has at least two light receiving surfaces, the light combining unit receives light emitted by corresponding LED lamps through the light receiving surfaces, and the light receiving surfaces 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 the at least two light receiving surfaces.

[0293] The light combining unit comprises the light combining dichroic mirrors described above and / or combinations thereof, and further comprises a light combining structure for integrating the light combining dichroic mirrors described above. The plurality of light combining dichroic mirrors are respectively used as light receiving surfaces of the light combining unit.

[0294] Specifically, the light combining structure comprises a light combining dichroic mirror mounting seat 71, the first light combining dichroic mirror 110, the second light combining dichroic mirror 108 and the third light combining dichroic mirror 109 are respectively mounted on mounting positions on different sides of the light combining dichroic mirror mounting seat 71. Among them, one of the mounting positions on the light combining structure is such that the first light combining dichroic mirror 110 can 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; one of the mounting positions on the light combining structure is such that the second light combining dichroic mirror 108 can transmit the light emitted by the second LED lamp 101, and reflect and transmit the light reflected and transmitted by the third light combining dichroic mirror 109; one of the mounting positions on the light combining structure is such that the third light combining 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.

[0295] Further, the light combining dichroic mirror mounting seat 71 has a plurality of inclined surfaces, the number of inclined surfaces respectively corresponds to the number of light combining dichroic mirrors. Each inclined surface is provided with a mounting groove 711 for mounting a corresponding light combining dichroic mirror. As Figure 7 As shown, the first light combining dichroic mirror 110 is arranged on the inclined surface on the right side of the light combining dichroic mirror mounting seat 71, the second light combining dichroic mirror 108 is arranged on the inclined surface on the left side of the light combining dichroic mirror mounting seat 71, and the third light combining dichroic mirror 109 is arranged on the inclined surface on the upper side of the light combining dichroic mirror mounting seat 71.

[0296] The inner side edge of each mounting groove 711 can be in close contact with the outer side edge of the corresponding light combining dichroic mirror. Each light combining dichroic mirror can be fixed in the corresponding mounting groove 711 in one or more of the following ways: sliding installation, clamping and mounting, and adhesive installation.

[0297] Further, as Figure 8 As shown, the light combining device further comprises an optical seat 72. The optical seat 72 is integrally configured as a columnar structure, and the rear side, the left side, the front side and the bottom side thereof are respectively used for mounting the first LED lamp 100, the second LED lamp 101, the third LED lamp 102 and the fourth LED lamp 103.

[0298] Specifically, fasteners are arranged on the rear side, the left side, the front side and the bottom side of the optical seat 72 respectively for fixing the lamp panels of the corresponding LED lamps; and lamp bead holes are also arranged on the rear side, the left side, the front side and the bottom side of the optical seat 72 respectively for installing the lamp beads of the corresponding LED lamps.

[0299] In addition, the optical seat 72 is further provided with a containing cavity 721 for installing the combining dichroic mirror mounting seat 71. The combining dichroic mirror mounting seat 71 can be fixed in the containing cavity 721 by one or more of sliding installation, clamping and installation and adhesive installation.

[0300] Therefore, the light beams of four independent LED lamps located in different directions can be combined into one light beam only by two structural members, i.e. the combining dichroic mirror mounting seat 71 and the optical seat 72. The structures of the combining dichroic mirror mounting seat 71 and the optical seat 72 are convenient for high-precision machining to ensure the position accuracy of each optical element.

[0301] In addition, since each LED lamp generates a certain amount of heat during operation, the cooling mode of the optical module 7 also needs to be considered.

[0302] The utility model provides, through using the incubation water in the incubation module 8 described above to cool the light source of the optical module 7.

[0303] Specifically, as shown in Figure 9 The optical seat 72 is provided with a cooling flow channel, and the cooling flow channel surrounds each light source respectively.

[0304] In some embodiments, the cooling fluid in the cooling flow channel is a liquid, i.e. the cooling flow channel cools each light source by water cooling.

[0305] The cooling flow channel includes a water outlet 73 and a water inlet 74, and the two are connected by a flow path inside the optical seat 72. The flow path can be a pipe or the like pipeline arranged separately in the optical seat 72, or can be a machining passage directly machined in the optical seat 72.

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

[0307] The number of cooling flow channels corresponds to the number of light sources one-to-one to facilitate individual cooling of each light source. That is, each LED lamp has a cooling flow channel for cooling it. The cooling flow channels can be in fluid communication with each other, or each cooling flow channel is in fluid communication with the incubation water supply pipeline in the 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] In addition, the optical seat 72 is further provided with a plug 75. An opening is formed on the side wall of the optical seat 72 when the cooling flow channel is machined, and therefore the opening is plugged by the plug 75 after the cooling flow channel is obtained. In summary, the optical module 7 is individually cooled by the cooling flow channel using incubation water as the cooling medium, so that the light source can be ensured to be at a normal working temperature.

[0314] As described above, when detecting, the light intensity of different wavelength light beams and the uniformity of light beam mixing need to be ensured. Therefore, the utility model provides, through corresponding optical path design, that is, through the mode that the light paths of different LED lamps are the same when reaching the measured object after flat light, light mixing and beam expansion, the light intensity of different wavelength light beams and the uniformity of light beam mixing are ensured, so as to improve the accuracy of sample analyzer project detection.

[0315] According to the above, the second LED lamp 101 of the utility model is a wide-spectrum LED lamp, which can provide a wavelength of 450nm-800nm. The first LED lamp 100 can provide a wavelength of 340nm, the third LED lamp 102 can provide a wavelength of 380nm, and the fourth LED lamp 103 can provide a wavelength of 405nm. The light emitting angles of different LED lamps are different, and the strengths of light energy are not completely consistent, so the design distribution needs to take into account the light emitting angles, light intensity and optical element loss.

[0316] Specifically, the light source of the utility model comprises a plurality of light emitting elements, and the plurality of light emitting elements are each provided with a flat light device, which is used for flat light of the corresponding light emitting element; the optical path design of the optical module is that the light emitted by each LED lamp has the same light path distance from the flat light device to the colorimetric cup 115. The flat light device is arranged between the LED lamp and the light mixing unit. The optical module further comprises a beam expander; wherein the beam expander is used for expanding the composite light aggregated by the light mixing unit; the light emitted by each LED lamp has the same light path distance from the flat light device to the beam expander.

[0317] The following will be described taking the light emitting element as an example. As shown in Figure 3 Each LED lamp is provided with a flat light device, which can be a flat convex lens, for example.

[0318] Figure 3 A plane schematic diagram of the light path of the light source of the utility model is shown. Specifically, in order to improve the light beam intensity and the light beam uniformity, the light path distances of the light beams of the plurality of LED lamps are the same when the light beams enter the beam expander after flat light. More specifically, the light path distances of the light beams of the plurality of LED lamps are the same when the light beams enter the beam expander from appropriate positions after flat light. The appropriate positions after flat light can be the best positions after flat light, for example.

[0319] AsFigure 10 As shown in FIG. 6, a light path schematic diagram of the first LED lamp 100 is shown, wherein L1 is the light path distance of the light beam of the first LED lamp 100 after passing through the flat light from the flat light best position to the first light combining dichroic mirror 110, L3 is the light path distance of the light beam of the first LED lamp 100 after passing through the first light combining dichroic mirror 110 to the focal point of the flat-concave lens 111, f1 is the focal length of the flat-concave lens 111, and f2 is the focal length of the double-convex lens 112. Therefore, the light path distance of the light beam of the first LED lamp 100 after passing through the flat light from the flat light best position to the expander is L1+L3.

[0320] As shown in FIG. 7, a light path schematic diagram of the second LED lamp 101 is shown, wherein L2 is the light path distance of the light beam of the second LED lamp 101 after passing through the flat light from the flat light best position to the first light combining dichroic mirror 110, L3 is the light path distance of the light beam of the second LED lamp 101 after passing through the first light combining dichroic mirror 110 to the focal point of the flat-concave lens 111, f1 is the focal length of the flat-concave lens 111, and f2 is the focal length of the double-convex lens 112. Therefore, the light path distance of the light beam of the second LED lamp 101 after passing through the flat light from the flat light best position to the expander is L2+L3. Figure 11 As shown in FIG. 8, a light path schematic diagram of the third LED lamp 102 or the fourth LED lamp 103 is shown, wherein L2 is the light path distance of the light beam of the third LED lamp 102 or the fourth LED lamp 103 after passing through the flat light from the flat light best position to the first light combining dichroic mirror 110, L3 is the light path distance of the light beam of the third LED lamp 102 or the fourth LED lamp 103 after passing through the first light combining dichroic mirror 110 to the focal point of the flat-concave lens 111, f1 is the focal length of the flat-concave lens 111, and f2 is the focal length of the double-convex lens 112. Therefore, the light path distance of the light beam of the third LED lamp 102 or the fourth LED lamp 103 after passing through the flat light from the flat light best position to the expander is L2+L3.

[0321] Figure 12 As shown in FIG. 8, a light path schematic diagram of the third LED lamp 102 or the fourth LED lamp 103 is shown, wherein L2 is the light path distance of the light beam of the third LED lamp 102 or the fourth LED lamp 103 after passing through the flat light from the flat light best position to the first light combining dichroic mirror 110, L3 is the light path distance of the light beam of the third LED lamp 102 or the fourth LED lamp 103 after passing through the first light combining dichroic mirror 110 to the focal point of the flat-concave lens 111, f1 is the focal length of the flat-concave lens 111, and f2 is the focal length of the double-convex lens 112. Therefore, the light path distance of the light beam of the third LED lamp 102 or the fourth LED lamp 103 after passing through the flat light from the flat light best position to the expander is L2+L3.

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

[0323] In summary, the utility model makes different LED lamps combined in the light path at the appropriate position for the design idea of the same light path distance, which not only can make the light beams of different wavelengths better combined to a certain extent, make the selection of LED lamps more flexible, and the combination mode more various, but also can ensure the consistency of the light quantity of the light beams of different wavelengths.

[0324] ​When detecting in the sample analyzer, it is hoped that parallel light is incident into the colorimetric assembly, so that the detection can be more in line with the application conditions of the Lambert-Beer law, because the law requires that the parallel monochromatic light is vertically incident, and such an incident condition is more beneficial to the accuracy of the biochemical detection result. In addition, the establishment of the Lambert-Beer law also needs the following conditions:

[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 the radiation and the substance is limited to the process of light absorption, and there is no fluorescence and photochemistry.

[0328] However, the incident light condition of the existing sample analyzer is a light beam with a certain angle, that is, the light source light beam is focused by a focusing lens to be imaged and focused on a certain position of the to-be-detected substance in the colorimetric assembly, and is not parallel light, nor is it vertically incident. Therefore, for the biochemical detection system with focused incident, the front and rear light beams of the colorimetric assembly have great limitations, and the front and rear light beams cannot be adapted, and the selectivity is low.

[0329] In view of the above problems, the utility model provides a colorimetric assembly which can improve the spot matching mode of biochemical detection performance. Specifically, the utility model is based on parallel light incidence, and the colorimetric assembly can match the sizes of the front and rear light spots. In other words, the size of the light spot incident into the colorimetric assembly has a certain range of selectivity, and the size of the transmitted light beam entering the spectrometer unit also has a corresponding range of selectivity. Such light spot size matching not only makes the test result of the non-uniform scattering system project in biochemical detection more accurate, but also can select different optical detection systems according to different precision models of the biochemical detector, which is more flexible, and at the same time, will not cause great changes in the structure and light path, and can also make the light source selection space wider. At the same time, the different matching conditions of the front and rear light spots can meet the performance requirements of the whole machine, and the precision index far exceeds the industry standard.

[0330] In the sample analyzer, most detection projects adopt a double-wavelength determination method, that is, the concentration result of the to-be-detected object is determined by simultaneously measuring the light signal change of two wavelengths. Specifically, the incident light is incident into the colorimetric assembly, the light beam passing through the colorimetric assembly enters the spectrometer unit, the spectrometer unit divides the received complex light into the required monochromatic light, the signal of the monochromatic light beam is detected by the detector, the circuit system performs photoelectric conversion, and finally outputs in the form of digital signal, so that the absorbance value of the to-be-detected substance can be calculated and obtained, and then the concentration result is converted.

[0331] In the method, the two wavelengths are regarded as the main wavelength and the secondary wavelength of the test item respectively, the better the synchronization of the main-secondary wavelength optical signal change is, the better the quantification is, and the more accurate and reliable the test result is; then no matter the uniform determination object or the non-uniform scattering system determination object, the smaller the divergence angle of the incident light beam is, the better, that is, the parallel light incidence is the best, which is more beneficial to the determination of different systems. Therefore, the matching of the front and rear light spot sizes of the colorimetric assembly can greatly reduce the influence of interference on the test result, reduce the influence of the scattered light generated by the interference substances in the reaction on the transmitted light beam, such as bubbles, unknown interference substances in the reaction liquid and the like, so as to ensure the precision and accuracy of the 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; the size matching of the front and rear diaphragms of the parallel light incidence greatly improves the synchronization of the main-secondary wavelength change, and thus the dual-wavelength detection can be more accurate.

[0333] As shown in Figure 13 The incubation module 8 of the utility model includes a colorimetric assembly, the colorimetric assembly includes a colorimetric cup 115, incubation groove front window sheet 114 and incubation groove rear window sheet 116 located on both sides of the colorimetric cup 115, and front diaphragm 113 located in front of the incubation groove front window sheet 114 and rear diaphragm 117 located behind the incubation groove rear window sheet 116.

[0334] The size of the parallel light spot entering the colorimetric assembly needs to consider the minimum reaction volume of the colorimetric cup 115, because the liquid level of different to-be-measured substances in the colorimetric cup 115 can be different; in addition, the light beam emitted by the LED lamp with the smallest divergence angle can also enter the colorimetric assembly.

[0335] The colorimetric cup 115 has a light receiving surface and a light emitting surface, and the composite light of the beam combining unit passes through the light receiving surface and the light emitting surface of the colorimetric cup 115 in turn and then is spectrally divided by the light splitting unit. The front diaphragm 113 and the rear diaphragm 117 are separately arranged at the corresponding positions of the light receiving surface and the light emitting surface, the front diaphragm 113 is used for filtering stray light irradiating the sample in the colorimetric cup 115, and the rear diaphragm 117 is used for filtering the emergent light after the composite light passes through the sample. The light splitting unit can sort the emergent light filtered by the rear diaphragm 117 into monochromatic light of the corresponding wave band for detection by the detection unit.

[0336] When the sample is detected, the front diaphragm 113, the colorimetric cup 115 and the rear diaphragm 117 are arranged in a straight line. The center of the front diaphragm 113 and the center of the rear diaphragm 117 are on the same straight line.

[0337] The light passing area of the rear diaphragm 117 is smaller than that of the front diaphragm 113. Both the front diaphragm 113 and the rear diaphragm 117 have a circular light passing area, and the diameter of the light passing area of the front diaphragm 113 is 1-3 times that of the rear diaphragm 117.

[0338] The upper top of the light passing area of the front diaphragm 113 does not exceed the liquid level of the liquid in the cuvette 115 when the sample analyzer is detecting the minimum reaction amount.

[0339] The size of the parallel light spot entering the cuvette assembly is 2-3 mm. The size of the light spot entering the spectrometer unit after passing through the cuvette assembly is 1-1.5 mm.

[0340] Preferably, the size of the parallel light spot entering the cuvette assembly, i.e. the diameter D1 of the light passing area of the front diaphragm 113, satisfies: 2 mm≤D1≤3 mm; and the size of the light spot entering the spectrometer system after passing through the cuvette assembly, i.e. the diameter D2 of the light passing area of the rear diaphragm 117, satisfies: 1 mm≤D2≤1.5 mm.

[0341] The matching relationship between the diameter D1 of the light passing area of the front diaphragm 113 and the diameter D2 of the light passing area of the rear diaphragm 117 is shown in Table 7.

[0342] Table 7 Matching list of the diameter of the light passing area of the front diaphragm 113 and the diameter of the light passing area of the rear diaphragm 117

[0343]

[0344] Further, in the case where the diameter D2 of the light passing area of the rear diaphragm 117 matches the diameter of the light passing area of the front diaphragm 113, the smaller the diameter D1 of the light passing area of the front diaphragm 113, the greater the coefficient of variation CV.

[0345] For example, according to Table 7, one matching mode is that the diameter D1 of the light passing area of the front diaphragm 113 is 2 mm, and the diameter D2 of the light passing area of the rear diaphragm 117 matched therewith is 1.5 mm; and another matching mode is that the diameter D1 of the light passing area of the front diaphragm 113 is 3 mm, and the diameter D2 of the light passing area of the rear diaphragm 117 matched therewith is 1.5 mm. Compared with each other, the coefficient of variation CV of the concentration result of the former matching mode is greater, and therefore the precision of the latter matching mode is better.

[0346] This is because when considering the influence of stray light caused by interference, the greater the amount of incident light received by the measurement object, the more accurate the interference signal that can be measured, and the higher the quantification, so when the diameter of the light passing area of the front diaphragm 113 is small and matches the diameter of the light passing area of the rear diaphragm 117, the probability of stray light caused by interference in the measured object entering the spectrometer unit is relatively greater, and the influence on the test result is more obvious, so the coefficient of variation CV result will be relatively larger.

[0347] Similarly, if the diameter D1 of the light passing surface of the front light barrier 113 is selected as 1mm or 1.5mm, the influence of the interference will be smaller, and the coefficient of variation CV will be smaller, the precision will be higher, and the deviation will be smaller.

[0348] For example, in biochemical detection, the within-run precision of clinical items is a necessary determination procedure of the instrument. According to the industry standard in the art, the determination items include alanine aminotransferase (ALT), urea (UREA), and total protein (TP). The ALT item of the three clinical items is mainly targeted. The determination reactivity of the low concentration sample of the item is small, the main wavelength of the item is 340nm, the auxiliary wavelength is 405nm, the reactivity change is small, and the precision of the detection system is more tested. The degree of synchronization of the double-wavelength light quantity change is also more tested. The smaller the CV of the concentration result indicates that the instrument detection is more precise, and the larger the CV indicates that the instrument detection precision is lower. Therefore, the precision result of the item with small reactivity can be used to determine the performance of the light spot after matching. The determination concentration of ALT in the industry standard is 30U / L-50U / L, and CV<5%.

[0349] The utility model discloses the corresponding ALT reagent, calibrant and corresponding determination process are used, normal value quality control serum or fresh patient serum is used as sample, and the ALT item under the concentration range is repeatedly tested, each item is repeatedly tested 20 times, and the coefficient of variation (CV) of 20 results is calculated, and is respectively summarized as shown in table 8 and table 9.

[0350] Table 8 shows the ALT precision (unfiltered biochemical composite quality control product) of the diameter of the light passing surface of the front light barrier 113 and the diameter of the light passing surface of the rear light barrier 117 matched therewith; and table 9 shows the ALT precision (filtered biochemical composite quality control product) of the diameter of the light passing surface of the front light barrier 113 and the diameter of the light passing surface of the rear light barrier 117 matched therewith.

[0351] Table 8 shows the ALT precision (unfiltered biochemical composite quality control product) of the diameter of the light passing surface of the front light barrier 113 and the diameter of the light passing surface of the rear light barrier 117 matched therewith; and table 9 shows the ALT precision (filtered biochemical composite quality control product) of the diameter of the light passing surface of the front light barrier 113 and the diameter of the light passing surface of the rear light barrier 117 matched therewith.

[0352]

[0353] According to table 8, under the condition that the diameter of the light passing surface of the rear light barrier 117 is the same, the smaller the diameter of the light passing surface of the front light barrier 113, the greater the coefficient of variation CV. However, the diameter D1 of the light passing surface of the front light barrier 113 satisfies 2mm≤D1≤3mm, and the diameter D2 of the light passing surface of the rear light barrier 117 satisfies 1mm≤D2≤1.5mm. The actual measured coefficient of variation CV is less than 3.5%, and therefore the performance index of the sample analyzer of the utility model is far above the industry standard.

[0354] Table 9 ALT intra-batch precision of filtration quality control

[0355]

[0356] According to Table 9, in the case that the diameter of the light passing surface of the rear diaphragm 117 is the same, the smaller the diameter of the light passing surface of the front diaphragm 113 is, the greater the coefficient of variation CV is. However, the diameter D1 of the light passing surface of the front diaphragm 113 satisfies: 2mm≤D1≤3mm; the diameter D2 of the light passing surface of the rear diaphragm 117 satisfies: 1mm≤D2≤1.5mm, and the actually measured coefficient of variation CV is less than 2.2%, so the performance index of the sample analyzer of the utility model is far above the industry standard.

[0357] In addition, from the data of Table 8 and Table 9, it can be seen that the precision result of the test object is better than that of the determination object containing the interference, but through the light spot matching mode proposed by the utility model, for the project with small reaction degree such as ALT, the precision CV result far exceeding the industry standard can be obtained without filtering the sample during instrument determination.

[0358] It can be understood that the selection of the diameter D1 of the light passing surface of the front diaphragm 113 and the diameter D1 of the light passing surface of the rear diaphragm 117 is not limited to the data listed in Table 8 and Table 9, as long as 2mm≤D1≤3mm and 1mm≤D2≤1.5mm are satisfied.

[0359] In summary, the utility model discloses a front diaphragm 113 and a rear diaphragm 117 with a diameter range of the light passing surface matched, so that the test result is more accurate.

[0360] As described above, the utility model discloses a parallel incident light is incident into a colorimetric assembly, and the light beam passing through the colorimetric assembly needs to be split, that is, it is split into the required monochromatic light, and then detection and calculation are carried out, and this mode is called "post-splitting" optical detection of the sample analyzer.

[0361] In some embodiments, the sample analyzer of the utility model uses dichroic mirror splitting for splitting. Dichroic mirror splitting is widely used because of its advantages of simple debugging, high accuracy, etc.

[0362] Specifically, as shown in Figure 14 The optical module 7 also includes a combination unit, and the number of the combination unit is less than the number of the LED lamps in the LED lamp group. The combination unit includes a double convex lens 118. The optical module 7 also includes a reflector 119, a fifth plano-convex lens 120, a flat light diaphragm 121 and a light splitting unit arranged in sequence.

[0363] As shown in Figure 14As shown, the light beam is emitted from the rear stop 117 and enters the lenticular lens 118. The lenticular lens 118 focuses the light beam emitted from the rear stop 117. The focused light beam is reflected by the mirror 119, thereby changing the original light path direction so that the light path is not too large in one direction, thereby saving space. The reflected light beam enters the fifth plano-convex lens 120, and the fifth plano-convex lens 120 collimates the reflected light beam. The collimation distance of the fifth plano-convex lens 120 is about 120 mm. The collimated light beam enters the light splitting unit through the flat light stop 121, and the flat light stop 121 can eliminate the edge stray light.

[0364] As shown in Figure 15 and Figure 16 , two forms of the sample analyzer using dichroic mirrors for light splitting are shown. Figure 15 and Figure 16 The light splitting mode shown in the above two manners is a straight light path light splitting mode.

[0365] As shown in Figure 15 , the light path of the light splitting unit is in the transverse direction. The light splitting unit includes a mirror 119, a plurality of dichroic mirrors, and a narrow-band filter corresponding to each dichroic mirror.

[0366] It can be understood that the number of dichroic mirrors is the same as the number of types of wavelengths required by the sample analyzer. Because the sample analyzer requires 13 wavelengths, the number of dichroic mirrors is 13. The dichroic mirrors can be represented by 123, 124, 125, 126, 127, 128, 142, 143, 144, 145, 146, 147, and 148. The number of narrow-band filters is also 13, and the narrow-band filters are represented by 136, 137, 138, 139, 140, 141, 129, 130, 131, 132, 133, 134, and 135, respectively.

[0367] The light beam passing through the flat light stop 121 is reflected by the mirror 119 and reflected to the dichroic mirror 123 (which is the first dichroic mirror in the light path). The dichroic mirror 123 reflects the 340 nm light to the narrow-band filter 136 to become monochromatic light, and the monochromatic light is irradiated onto the corresponding detector (which can be a photodetector) of the narrow-band filter 136. The light with a wavelength greater than 340 nm is transmitted through the dichroic mirror 123 to the next dichroic mirror 124, and the light is transmitted and split in this way.

[0368] According to Figure 15 , in this light splitting mode, the length b1 of the light 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] As Figure 16 shown, the light path of the light splitting unit is along the vertical direction. The light splitting unit comprises a plurality of dichroic mirrors and a narrow-band filter corresponding to each dichroic mirror.

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

[0371] The light beam after collimating by the collimating diaphragm 121 enters the dichroic mirror 123 (which is the first dichroic mirror in the light path), and the dichroic mirror 123 reflects the 340nm light to the narrow-band filter 136 to become monochromatic light, which is then irradiated onto the corresponding detector (which can be a photodetector, for example) of the narrow-band filter 136, and the light with a wavelength greater than 340nm is transmitted through the dichroic mirror 123 to the next dichroic mirror 124, and so on to the next dichroic mirror to perform light splitting.

[0372] According to Figure 16 It can be seen that in this light splitting mode, the length b2 of the light splitting unit is: b2=N×a. Wherein, N is the number of dichroic mirrors (i.e.

[0373] In a preferred embodiment, the utility model provides a layout mode of dichroic mirrors, which reduces the length of the vertical light path by half by reasonably utilizing space, thereby achieving the purposes of reducing the occupied space and reducing the loss of optical energy.

[0374] As Figure 17 shown, the light splitting unit of the preferred embodiment of the utility model is shown. The light splitting unit comprises a first light splitting dichroic mirror 122 located after the collimating diaphragm 121.

[0375] As Figure 17As shown, the first light-splitting dichroic mirror 122 splits the light beam into two beams in different directions, for example, one beam in the horizontal direction and one beam in the vertical direction, so the light-splitting unit further includes a plurality of dichroic mirrors arranged in the horizontal direction and a plurality of dichroic mirrors arranged in the vertical direction. Among them, the first light-splitting dichroic mirror 122 and other dichroic mirrors reflect the wavelength band of 335nm-510nm in the reflection area and transmit the wavelength band of 541nm-805nm in the transmission area; the transmittance T ave ≥90% in the transmission area and T ave ≤5% (i.e. the reflectivity is above 95%) in the reflection area. Therefore, the reflection wavelength band of the first light-splitting dichroic mirror 122 and other dichroic mirrors is 340nm, 380nm, 405nm, 450nm, 480nm and 505nm, and the transmission wavelength band is 546nm, 570nm, 600nm, 660nm, 700nm, 750nm and 800nm.

[0376] As Figure 17 shown, the light-splitting unit further includes a plurality of dichroic mirrors after the first light-splitting dichroic mirror 122, among which the plurality of dichroic mirrors in the horizontal direction can be represented by 123, 124, 125, 126, 127 and 128; and the plurality of dichroic mirrors in the vertical direction can be represented by 142, 143, 144, 145, 146, 147 and 148.

[0377] Preferably, the difference between the number of dichroic mirrors in the two different directions is as small as possible, so that the size difference between the two directions is small.

[0378] Because the sample analyzer needs to detect 13 wavelengths (340nm, 380nm, 405nm, 450nm, 480nm, 505nm, 546nm, 570nm, 600nm, 660nm, 700nm, 750nm and 800nm), 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 light-splitting unit further includes a plurality of narrowband filters, which are arranged one-to-one corresponding to the plurality of dichroic mirrors in the horizontal direction and the plurality of dichroic mirrors in the vertical direction. For example, the narrowband filters corresponding to each dichroic mirror in the horizontal direction are represented by 136, 137, 138, 139, 140 and 141, and the narrowband filters corresponding to each dichroic mirror in the vertical direction are represented by 129, 130, 131, 132, 133, 134 and 135.

[0380] As Figure 17As shown, the first light-splitting dichroic mirror 122 can split the light beam into two beams of different directions according to the required wavelength, and then split the two beams into monochromatic light in turn. The 13 wavelengths commonly used in biochemical analysis are 340nm-800nm, and the middle wavelengths such as 505nm and 546nm are taken for splitting, so that the first light-splitting dichroic mirror 122 reflects the light of 340nm-505nm to the dichroic mirror 123, the dichroic mirror 123 reflects the light of 340nm to the narrow-band filter 136 to become monochromatic light, and the monochromatic light irradiates the corresponding detector 150 (for example, a photodetector) of the narrow-band filter 136, and the light with a wavelength greater than 340nm is transmitted to the next dichroic mirror 124 through the dichroic mirror 123 and is transmitted to the next dichroic mirror in turn for splitting; and the light beam of 546nm-800nm is transmitted through the first light-splitting dichroic mirror 122 to the dichroic mirror 142, and similarly, the dichroic mirror 142 reflects the light of 340nm to the narrow-band filter 129 to become monochromatic light, and the monochromatic light irradiates the corresponding detector 150 (for example, a photodetector) of the narrow-band filter 129, and the light with a wavelength greater than 340nm is transmitted to the next dichroic mirror 143 through the dichroic mirror 142 and is transmitted to the next dichroic mirror in turn for splitting.

[0381] Therefore, it can be known that by arranging a plurality of dichroic mirrors in the transverse direction, the optical path in the vertical direction is transferred by half to the transverse direction, so that the length of the optical path in the vertical direction is reduced by half, thereby achieving the purposes of reducing the occupied space and reducing the loss of light energy.

[0382] As shown in the figure, Figure 17 The length of the light-splitting unit is D+l1, and the width is C+l2. Wherein, D=N1x a, C=N2x a, l1=l2, N 1＝ =N1+N2, N1 is the number of dichroic mirrors in the vertical direction, N2 is the number of dichroic mirrors (i.e. the number of wavelengths) in the transverse direction, l1 is the distance between two dichroic mirrors in the vertical direction, and l2 is the distance between two dichroic mirrors in the transverse direction.

[0383] When N1=N2, the length D of the light-splitting unit in the preferred embodiment of the utility model is b1 / 2 or D=b2 / 2, that is, the length of the light-splitting unit in the preferred embodiment of the utility model in the vertical direction is only Figure 15 or Figure 16 half of the length of the light-splitting unit in the embodiment shown in the figure, and the remaining optical path of the light-splitting unit in the preferred embodiment of the utility model is transferred to the horizontal direction, thereby greatly reducing the occupied space, effectively reducing the loss of light energy, reducing the degree of light divergence, and maximizing the use of space.

[0384] Figure 15 , Figure 16 andFigure 17 In the illustrated splitting manner, the tilt directions of the dichroic mirrors in each direction are the same, and the narrowband filters corresponding to each dichroic mirror are arranged on the same side of the direction.

[0385] In some other embodiments, as Figure 18 illustrated, the sample analyzer of the utility model adopts the optical fiber splitting manner to split light. Specifically, the sample analyzer of the utility model adopts a one-to-many optical fiber bundle, for example, a one-to-13 optical fiber bundle to split light.

[0386] As Figure 18 illustrated, the splitting unit includes a plurality of dichroic mirrors and narrowband filters corresponding to each dichroic mirror, and the dichroic mirrors can be represented by 123, 124, 125, 126, 127, 128, 142, 143, 144, 145, 146, 147 and 148. The number of dichroic mirrors is 13, and the number of narrowband filters is also 13, and the narrowband filters are represented by 136, 137, 138, 139, 140, 141, 129, 130, 131, 132, 133, 134 and 135.

[0387] As Figure 18 illustrated, the tilt directions of the dichroic mirrors are approximately perpendicular, so that the narrowband filters corresponding to the adjacent two dichroic mirrors are located on the two sides of the optical path, respectively. The incident light after collimation is incident into the dichroic mirror 123 (which is the first dichroic mirror in the optical path), the dichroic mirror 123 reflects the light with a wavelength of 340 nm to the narrowband filter 136 to become monochromatic light, and the monochromatic light is incident on the detector 150 (which can be a photodetector, for example) corresponding to the narrowband filter 136, and the light with a wavelength greater than 340 nm is transmitted through the dichroic mirror 123 to the next dichroic mirror 124, and the light is transmitted to the next dichroic mirror and then split.

[0388] In some other embodiments, as Figure 19 illustrated, the sample analyzer of the utility model adopts the grating splitting manner to split light.

[0389] As Figure 18 illustrated, the splitting unit includes a concave diffraction grating 160. The light beam after collimation by the collimating diaphragm 121 is incident into the concave diffraction grating 160. The concave diffraction grating 160 includes a substrate (usually glass), an epoxy resin layer (or a metal layer) above the substrate for forming grooves, and a reflective coating. The concave diffraction grating 160 can also split and reflect light with a wavelength of 340 nm to 800 nm, and the monochromatic light is incident on the detector 150.

[0390] As Figure 20 illustrated, the overall structure of the optical module 7 of one embodiment of the utility model is shown.

[0391] In some embodiments, the optical module 7 comprises a light source, which can comprise the above-mentioned LED lamp and / or combination of LED lamps.

[0392] In some embodiments, the optical module 7 further comprises a collimator, which can comprise the above-mentioned plano-convex lens and / or combination of plano-convex lenses.

[0393] In some embodiments, the optical module 7 further comprises a light combiner, which can comprise the above-mentioned light combiner dichroic mirror and / or combination of light combiner dichroic mirrors.

[0394] In some embodiments, the optical module 7 further comprises an expander, which can be the above-mentioned Galilean expander or Kepler expander.

[0395] In some embodiments, the optical module 7 further comprises a colorimetric assembly, which can comprise the above-mentioned colorimetric cup 115, front window piece 114 of the incubation slot, rear window piece 116 of the incubation slot, front diaphragm 113 and rear diaphragm 117.

[0396] In some embodiments, the optical module 7 further comprises a light combiner unit after the colorimetric assembly, which can be the above-mentioned lenticular lens 118.

[0397] In some embodiments, the optical module 7 further comprises a mirror 119, a fifth plano-convex lens 120 and a collimator diaphragm 121 arranged in sequence after the light combiner unit.

[0398] In some embodiments, the optical module 7 further comprises a light splitting unit, which can comprise the above-mentioned dichroic mirror and corresponding narrowband filter as shown in Figure 15 and Figure 16 or the first light splitting dichroic mirror 122 and multiple dichroic mirrors in the horizontal direction, multiple dichroic mirrors in the vertical direction and corresponding narrowband filters as shown in Figure 17 .

[0399] In some embodiments, the optical module 7 further comprises a light splitting unit, which can split light in the manner of one-to-many optical fiber bundles as shown in Figure 18 , which can comprise 13 dichroic mirrors and corresponding narrowband filters.

[0400] In some embodiments, the optical module 7 further comprises a light splitting unit, which can comprise a concave diffraction grating 160 as shown in Figure 19 .

[0401] In some embodiments, the optical module 7 further comprises a detection unit comprising a detector 150 comprising a photoelectric converter, which can be, for example, a photodiode (PD) as described above.

[0402] Although the present application has been described with reference to the preferred embodiments, various modifications and changes can be made thereto without departing from the scope of the present application. In particular, the technical features mentioned in each of the embodiments can be combined in any manner as long as there is no structural conflict. The present application 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, comprising: 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 colorimetric cup for biochemical detection, wherein the sample dispensing module discharges the sucked sample to the colorimetric cup; the reagent dispensing module discharges the sucked reagent to the colorimetric cup; a mixing module for mixing the reagent and the sample in the colorimetric cup; and an optical module for detecting the sample in the colorimetric cup; 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 combining unit can combine the light emitted by the multiple LED lamps; the light splitting unit can sort the composite light combined by the combining unit into monochromatic light of corresponding wave bands for detection by the detection unit; the composite light can cover the wavelengths required by biochemical detection; the detection unit is used for optical detection of the monochromatic light; when optical detection is performed, the minimum light power of the 340 nm monochromatic light received by the detection unit is lower than the minimum light power of the 405 nm monochromatic light. The number of the detection units is the same as the number of the monochromatic light sorted by the light splitting unit; the detection unit is a photodiode, and the photodiode can receive the monochromatic light sorted by the light splitting unit.

2. The sample analyzer of claim 1, wherein, The lower limit value of the photocurrent of the photodiode at a wavelength of 340 nm is 10.98 nA.

3. The sample analyzer of claim 2, wherein, The lower limit light power value of the photodiode at a wavelength of 340 nm is 5.28 x 10 -2 μw.

4. The sample analyzer of claim 2, wherein, When the detection unit measures the 340 nm wavelength provided by the 340 nm LED lamp, the absorbance repeatability is: a coefficient of variation CV is less than or equal to 0.4%.

5. The sample analyzer of claim 1, wherein, When the detection unit measures any one of the 340 nm wavelength provided by the 340 nm LED lamp and the 450 nm-520 nm wavelength provided by the wide-spectrum LED lamp, the absorbance linear range is: the maximum absorbance with a relative bias in a range of plus or minus 5% is greater than or equal to 4.

0.

6. The sample analyzer of claim 1, wherein, When the detection unit measures the 340 nm wavelength provided by the 340 nm LED lamp, the stray light is: an absorbance A is greater than 5.

7. The sample analyzer of claim 1, wherein, When the detection unit measures the 340 nm wavelength provided by the 340 nm LED lamp, the absorbance accuracy is: an absorbance value is 0.5 Abs plus or minus 0.025 or 1.0 Abs plus or minus 0.

07.

8. The sample analyzer of claim 1, wherein, When the detection unit measures any one of the 340 nm wavelength provided by the 340 nm LED lamp and the 600 nm-700 nm wavelength provided by the wide-spectrum LED lamp, the absorbance stability is: the change of the absorbance is not greater than 0.

01.

9. The sample analyzer of claim 1, wherein, The multiple LED lamps respectively have corresponding lower limit light powers; the lower limit light power value P1 of the 340 nm LED lamp is the smallest among the lower limit light power values of the multiple LED lamps.

10. The sample analyzer of claim 1, wherein, The multiple LED lamps respectively have corresponding standard use light powers, and the standard light power of the 340 nm LED lamp is lower than the standard light power of the wide-spectrum LED lamp.

11. The sample analyzer of claim 10, wherein, ​ 12. The sample analyzer of claim 10, wherein, The LED lamp set further comprises a 380nm LED lamp, and a lower limit light power value P1 of the 380nm LED lamp is the maximum among lower limit light power values of the plurality of LED lamps.

13. The sample analyzer of claim 1, wherein, At least one of the plurality of LED lamps is arranged in a straight line with the cuvette at the detection position.

14. The sample analyzer of claim 1, wherein, At the detection position, the wide-spectrum LED lamp is arranged in a straight line with the beam combining unit and the cuvette.

15. The sample analyzer of claim 1, wherein, The optical module further comprises a collimating device arranged between the light source unit and the beam combining unit, and the collimating device is configured to collimate light beams emitted by the LED lamps to adjust the divergent light emitted by the LED lamps into parallel light.

16. The sample analyzer of claim 15, wherein, The optical path of the optical module is designed such that the light emitted by the LED lamps has the same optical path distance from the collimating device to the cuvette.

17. The sample analyzer of claim 15, wherein, The composite light formed by the beam combining unit is expanded before irradiating the cuvette, and the expanded composite light irradiates the sample in the cuvette to complete the optical detection of the sample.

18. The sample analyzer of claim 17, wherein, An expander is arranged between the beam combining unit and the cuvette, and the expander is configured to expand the diameter of the composite light.

19. The sample analyzer of claim 18, wherein, The expander comprises a Galilean expander or a Kepler expander, and when the expander comprises the Galilean expander, the Galilean expander comprises a flat-concave lens and a double-convex lens arranged in sequence, and when the expander comprises the Kepler expander, the Kepler expander comprises two double-convex lenses.

20. The sample analyzer of claim 19, wherein, The Galilean expander is capable of expanding the diameter of the composite light passing therethrough to m times the original diameter; and / or the divergence angle of the composite light after expansion by the Galilean expander is m times smaller than the divergence angle of the composite light before entering the Galilean expander. 12 12 ​​ wherein m 12 = f2 / f1; fi is the focal length of the plano-concave lens in the Galilean expander, and f2 is the focal length of the bi-convex lens in the Galilean expander.

21. The sample analyzer of claim 19, wherein, The Keplerian expander is capable of expanding the diameter of the compound light passing therethrough to m 12 times the original; and / or the divergence angle of the compound light after expansion by the Keplerian expander is m 12 times smaller than the divergence angle of the compound light before entering the Keplerian expander. wherein m 12 = f2 / f1 ; f1 is 1 / 2 of the focal length of the lenticular lens closer to the combining unit in the Keplerian expander, and f2 is 1 / 2 of the focal length of the lenticular lens farther from the combining unit in the Keplerian expander.

22. The sample analyzer of claim 1, wherein, The cuvette has a light-receiving surface and a light-emitting surface, and the composite light formed by the beam combining unit passes through the light-receiving surface and the light-emitting surface of the cuvette in sequence and then passes through the light-splitting unit. A front diaphragm and a rear diaphragm are separately arranged at positions corresponding to the light-receiving surface and the light-emitting surface, respectively, the front diaphragm is configured to filter stray light irradiating the sample in the cuvette, and the rear diaphragm is configured to filter emergent light after the composite light passes through the sample. The light-splitting unit can sort the monochromatic light filtered by the rear diaphragm into corresponding wavebands for detection by the detection unit.

23. The sample analyzer of claim 1, wherein, The beam combining unit comprises a plurality of beam combining dichroic mirrors and / or a combination of a plurality of beam combining dichroic mirrors, and the number of the beam combining dichroic mirrors is less than or equal to the number of the LED lamps.

24. The sample analyzer of claim 1, wherein, A screening unit is arranged between the beam combining unit and the cuvette, and the screening unit is configured to screen the composite light formed by the beam combining unit, and the screening range of the screening unit is an overlapping area of the composite light after the light emitted by the plurality of LED lamps passes through the beam combining unit.

25. The sample analyzer of claim 24, wherein, The overlapping area comprises light emitted by the 340nm LED lamp, light emitted by the wide-spectrum LED lamp, and light emitted by the 405nm LED lamp.

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