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. According to the utility model, a plurality of LED lamps are used as light sources, the LED lamps replace the existing halogen lamps, and as the service life of the LED lamps is longer, the problems of short service life, frequent maintenance, long preheating time during use and the like of the halogen lamps can be completely solved; and the light beam of the LED lamp can meet the requirement of light power, so that the accuracy and reliability of detection are ensured.

Description

[0001] Cross Reference to Related Applications

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

[0003] The 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. 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. Therefore, the sample analyzer often has to frequently replace the halogen lamp due to the expiration of the halogen lamp's 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 light of the corresponding wavelength 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] The utility model provides a kind of sample analyzer, for solving at least one technical problem described above.

[0009] The utility model provides a kind of sample analyzer, comprising:

[0010] Sample module, for carrying sample;

[0011] Sample dispensing module, for sucking and discharging the sample;

[0012] Reagent module, for carrying reagent;

[0013] Reagent dispensing module, for sucking and discharging the reagent;

[0014] a reaction assembly including a cuvette for biochemical detection, the sample dispensing module discharges the aspirated sample to the cuvette; the reagent dispensing module discharges the aspirated reagent to the cuvette;

[0015] a mixing module for mixing the reagent and sample in the cuvette; and

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

[0017] The optical module comprises a light source unit, a combining unit, a light splitting unit and a detection unit.

[0018] The light source unit is an LED lamp group composed of multiple LED lamps, the LED lamp group comprises a 340 nm LED lamp, a wide-spectrum LED lamp and a 405 nm LED lamp; the combining unit can combine the light emitted by 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.

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

[0020] The multiple LED lamps each have a corresponding lower limit light power; 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.

[0021] 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, which can receive the monochromatic light sorted by the light splitting unit.

[0022] In some embodiments, the lower limit light power value of the photodiode at a wavelength of 340 nm is 5.28 x 10 -2 μw.

[0023] In some embodiments, the lower limit value of the photocurrent of the photodiode at a wavelength of 340 nm is 10.98 nA.

[0024] 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%.

[0025] In some embodiments, when the detection unit measures any wavelength of 340 nm provided by the 340 nm LED lamp and 450 nm-520 nm provided by the wide-spectrum LED lamp, the absorbance linear range is: the maximum absorbance with a relative bias within ±5% is ≥4.0.

[0026] In some embodiments, the stray light is A>5 when the detection unit measures the 340nm wavelength provided by the 340nm LED lamp.

[0027] In some embodiments, the absorbance accuracy is 0.5Abs±0.025 or 1.0Abs±0.07 when the detection unit measures the 340nm wavelength provided by the 340nm LED lamp.

[0028] In some embodiments, the absorbance stability is not more than 0.01 when the detection unit measures any wavelength of 340nm provided by the 340nm LED lamp and 600nm-700nm provided by the wide-spectrum LED lamp.

[0029] In some embodiments, the plurality of LED lamps respectively have corresponding standard use optical powers, and the standard optical power of the 340nm LED lamp is lower than that of the wide-spectrum LED lamp.

[0030] In some embodiments, the standard use optical power of the 340nm LED lamp is not less than 1.2mW.

[0031] In some embodiments, the standard use optical power of the 340nm LED lamp is 1.2mW-2.5mW.

[0032] In some embodiments, the lower limit optical power value P1 of the 340nm LED lamp is 0.06mW.

[0033] In some embodiments, the LED lamp set further comprises a 380nm LED lamp, and the lower limit optical power value P1 of the 380nm LED lamp is the largest among the lower limit optical power values of the plurality of LED lamps.

[0034] In some embodiments, the lower limit optical power value P3 of the 380nm LED lamp is 0.7mW.

[0035] In some embodiments, the lower limit optical power values of the plurality of LED lamps satisfy the following relationship: P1

[0036] wherein P1 is the lower limit optical power value of the 340nm LED lamp;

[0037] P2 is the lower limit optical power value of the wide-spectrum LED lamp;

[0038] P3 is the lower limit optical power value of the 380nm LED lamp;

[0039] P4 is a lower light power value of the 405 nm LED lamp.

[0040] In some embodiments, at least one of the plurality of LED lamps is arranged in a straight line with the cuvette when the cuvette is in the detection position.

[0041] In some embodiments, the wide-spectrum LED lamp is arranged in a straight line with the combining unit and the cuvette when the cuvette is in the detection position.

[0042] In some embodiments, the optical module further comprises flat light devices arranged between the light source unit and the combining unit; the flat light devices are used to perform flat light processing on the light beams emitted by each of the LED lamps to adjust the divergent light emitted by each of the LED lamps into parallel light.

[0043] 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°.

[0044] In some embodiments, one or two of the plurality of LED lamps have a variable divergence angle of 0°-30°.

[0045] In some embodiments, one of the plurality of LED lamps has a variable divergence angle of 0°-15°.

[0046] In some embodiments, the flat light devices comprise plano-convex lenses.

[0047] In some embodiments, the curvature radius and diameter of the plano-convex lenses are matched with the corresponding LED lamps.

[0048] In some embodiments, the plano-convex lens on the light path of one of the plurality of LED lamps is capable of being compatible with an LED lamp having a variable divergence angle of 20°-30°.

[0049] In some embodiments, the plano-convex lens on the light path of one of the plurality of LED lamps is capable of performing flat light processing on an LED lamp having a variable divergence angle of less than 20°.

[0050] In some embodiments, the optical module is designed such that the light emitted by each of the LED lamps has the same light path distance from the flat light devices to the cuvette. In some embodiments, the combining unit comprises a plurality of light combining dichroic mirrors and / or a combination of a plurality of light combining dichroic mirrors.

[0051] In some embodiments, at least one of the light combining dichroic mirrors is arranged one-to-one with at least one of the flat light devices and is located on the light path of the corresponding flat light device.

[0052] In some embodiments, the cuvette has a light receiving surface and a light emitting surface, and the composite light gathered by the combining unit passes through the light receiving surface and the light emitting surface of the cuvette in sequence and then is split by the splitting unit.

[0053] In some embodiments, a front diaphragm and a rear diaphragm are respectively arranged at positions corresponding to the light receiving surface and the light emitting surface, the front diaphragm is used to filter stray light irradiating the sample in the cuvette, and the rear diaphragm is used to filter emergent light after the composite light passes through the sample.

[0054] The splitting unit can sort the emergent light filtered by the rear diaphragm into monochromatic light of corresponding wave bands for detection by the detection unit.

[0055] 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.

[0056] In some embodiments, the light passing area of the rear diaphragm is smaller than the light passing area of the front diaphragm.

[0057] 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.

[0058] 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 detecting the minimum reaction amount.

[0059] In some embodiments, the size of the parallel light spot entering the cuvette assembly is 2-3 mm.

[0060] In some embodiments, the size of the light spot entering the splitting unit after passing through the cuvette assembly is 1-1.5 mm.

[0061] In some embodiments, the diameter D1 of the light passing surface of the front diaphragm satisfies 2 mm≤D1≤3 mm.

[0062] In some embodiments, the diameter D2 of the light passing surface of the rear diaphragm satisfies 1 mm≤D2≤1.5 mm.

[0063] In some embodiments, the cuvette assembly further comprises a pre-incubation slot front window piece and a pre-incubation slot rear window piece respectively located on two sides of the cuvette, the front diaphragm is located on the side of the pre-incubation slot front window piece away from the cuvette, and the rear diaphragm is located on the side of the pre-incubation slot rear window piece away from the cuvette.

[0064] In some embodiments, the beam combining unit comprises a lenticular lens, which is disposed on the side of the rear aperture away from the rear window of the incubation tank.

[0065] In some embodiments, the number of light combining dichroic mirrors is less than or equal to the number of LED lamps.

[0066] In some embodiments, one of the plurality of light combining dichroic mirrors can reflect the light of the 340 nm 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 405 nm LED lamp.

[0067] In some embodiments, when the LED lamp set further comprises a 380 nm LED lamp, one of the plurality of light combining dichroic mirrors can reflect the light of the 380 nm LED lamp.

[0068] In some embodiments, the transmittance T of the light combining dichroic mirror in the transmission region is greater than or equal to 90%; or the transmittance T of the light combining dichroic mirror in the reflection region is less than or equal to 5%. ave ave

[0069] In some embodiments, the composite light formed by the beam combining unit is expanded before irradiating the colorimetric cup; the expanded composite light irradiates the sample in the colorimetric cup to complete the optical detection of the sample.

[0070] In some embodiments, an expander is arranged between the beam combining unit and the colorimetric cup, and the diameter of the composite light is expanded by the expander.

[0071] The expander is used to expand the composite light aggregated by the beam combining unit; the light emitted by each LED lamp has the same optical path distance from the flat light device to the expander.

[0072] In some embodiments, the expanded composite light is the composite parallel light obtained by the beam combining unit after the flat light device is flat light processed.

[0073] The expander comprises a Galilean expander or a Kepler expander; when the expander comprises a Galilean expander, the Galilean expander comprises a flat-concave lens and a lenticular lens arranged in sequence; when the expander comprises a Kepler expander, the Kepler expander comprises two lenticular lenses.

[0074] In some embodiments, the Galilean expander can expand the diameter of the composite light passing therethrough to m times the original diameter.​​12 times;

[0075] wherein m 12 = f2 / f1; f1 is the focal length of the plano-concave lens in the Galilean expander, and f2 is the focal length of the convex lens in the double Galilean expander.

[0076] In some embodiments, the divergence angle of the composite light after being expanded by the Galilean expander is m 12 times smaller than the divergence angle of the composite light before entering the Galilean expander.

[0077] wherein m 12 = f2 / f1; f1 is the focal length of the plano-concave lens in the Galilean expander, and f2 is the focal length of the convex lens in the double Galilean expander.

[0078] In some embodiments, the Kepler expander is capable of expanding the diameter of the composite light passing therethrough to m 12 times.

[0079] wherein m 12 = f2 / f1; f1 is the focal length of the double convex lens closer to the combining unit in the Kepler expander, and f2 is the focal length of the double convex lens farther from the combining unit in the Kepler expander.

[0080] In some embodiments, the divergence angle of the composite light after being expanded by the Kepler expander is m 12 times smaller than the divergence angle of the composite light before entering the Kepler expander.

[0081] wherein m 12 = f2 / f1; f1 is the focal length of the double convex lens closer to the combining unit in the Kepler expander, and f2 is the focal length of the double convex lens farther from the combining unit in the Kepler expander.

[0082] In some embodiments, a screening unit is arranged between the combining unit and the cuvette; the screening unit is used to screen the composite light formed by the combining unit; wherein 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.

[0083] In some embodiments, the overlapping area at least includes the light emitted by the 340 nm LED lamp and the light emitted by the wide-spectrum LED lamp.

[0084] In some embodiments, the LED lamp set further comprises a 405 nm LED lamp; the overlapping region comprises light emitted by the 340 nm LED lamp, light emitted by the wide-spectrum LED lamp, and light emitted by the 405 nm LED lamp.

[0085] In some embodiments, the distance from the flat light device corresponding to each LED lamp to the beam combining device is different; the light path length inside the beam combining unit for light emitted by each LED lamp is different; the light path distance from the flat light device to the output position of the beam combining unit for light emitted by each LED lamp is the same.

[0086] In some embodiments, the flat light device is arranged between the LED lamp and the beam combining unit.

[0087] In some embodiments, the wide-spectrum LED lamp, the beam combining unit, and the colorimetric cup in the detection position are arranged in a straight line.

[0088] In some embodiments, the wavelengths of light emitted by the plurality of LED lamps can cover the wavelengths required for biochemical detection.

[0089] When performing optical detection, the minimum light power of 340 nm monochromatic light that can be received by the detection unit is lower than the minimum light power of 405 nm monochromatic light.

[0090] In some embodiments, the light screened by the screening unit is parallel composite light after flat light processing by the flat light device.

[0091] In one embodiment, the light emitting surface of the LED lamp faces the beam combining unit; the beam combining unit combines light emitted by a plurality of LED lamps to form composite light; the composite light combined by the beam combining unit passes through a sample in the colorimetric cup to reach the light splitting unit; the light splitting unit sorts the combined composite light into monochromatic light of corresponding wavebands for detection by the detection unit; 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.

[0092] In one embodiment, the 340 nm LED lamp, the wide-spectrum LED lamp, and the 405 nm LED lamp are arranged in different planes, respectively.

[0093] In one embodiment, the planes in which the LED lamps are arranged are perpendicular to each other.

[0094] 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 of the LED lamps, the beam combining unit, and the colorimetric cup in the detection position are arranged in a straight line.

[0095] In one embodiment, the wide spectrum LED lamp, the combining unit and the colorimetric cup in the detecting position are arranged in a straight line.

[0096] In one embodiment, the LED lamp set further comprises a 380nm LED lamp, and the light emitting surface of each LED lamp faces the combining unit.

[0097] In one embodiment, the 380nm LED lamp is arranged in a different plane from the 340nm LED lamp, the wide spectrum LED lamp and the 405nm LED lamp; wherein the plane in which one of the 340nm LED lamp, the wide spectrum LED lamp, the 405nm LED lamp and the 380nm LED lamp is arranged is perpendicular to the plane in which the other LED lamps are arranged.

[0098] 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.

[0099] 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.

[0100] 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.

[0101] 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.

[0102] 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 combined into composite light after being reflected or transmitted by at least two light receiving surfaces.

[0103] In one embodiment, the combining unit comprises a combining dichroic mirror mounting base and a plurality of combining dichroic mirrors, the combining dichroic mirror mounting base 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.

[0104] In one embodiment, the combining dichroic mirrors are respectively mounted on mounting positions of different sides of the combining dichroic mirror mounting base.

[0105] In one embodiment, the combining dichroic mirror mounting base has a plurality of inclined surfaces, the number of the inclined surfaces respectively corresponds to the number of the combining dichroic mirrors, and each combining dichroic mirror is respectively mounted on the corresponding inclined surface.

[0106] In one embodiment, the number of the light combining units is less than the number of the LED lamps in the LED lamp group.

[0107] In one embodiment, the LED lamp group is configured with a temperature maintaining module, which is capable of maintaining each LED lamp in the LED lamp group at a preset temperature range.

[0108] In one embodiment, the optical module further comprises a light combining device, which comprises an optical seat, the LED lamp is installed in the optical seat, and the temperature maintaining module is capable of cooling the LED lamp.

[0109] In one embodiment, the temperature maintaining module comprises a cooling flow channel for cooling the LED lamp.

[0110] In one embodiment, an incubation module is further included, which is 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.

[0111] In one embodiment, the temperature fluctuation of the incubation water is ±0.1℃.

[0112] In one embodiment, the light combining unit combines the light emitted by multiple 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 sorting unit sorts the outgoing light into monochromatic light of corresponding wave bands for detection by the detection unit.

[0113] In one embodiment, the number of the monochromatic light sorted by the light sorting unit is the same as the number of the corresponding wavelengths required by the biochemical detection.

[0114] In one embodiment, the light sorting unit comprises a first light sorting dichroic mirror, which is capable of dividing the outgoing light into two beams of light in different directions; the two beams of light have non-overlapping wavelengths.

[0115] In one embodiment, the light sorting unit further comprises a plurality of dichroic mirrors arranged on one of the light paths after the light is sorted by the first light sorting dichroic mirror and a plurality of dichroic mirrors arranged on the other light path after the light is sorted by the first light sorting dichroic mirror.

[0116] In one embodiment, when the first light sorting dichroic mirror divides the outgoing light into two beams of light in different directions, the first light sorting dichroic mirror is capable of dividing the outgoing light into two beams of light perpendicular to each other by transmission and refraction.

[0117] In one embodiment, the deflection directions of the plurality of dichroic mirrors arranged on any one of the two light paths after the first light-splitting dichroic mirror are the same.

[0118] In one embodiment, the optical module is configured with a mirror on the light-emitting side of the cuvette; the mirror can change the propagation direction of the emitted light.

[0119] In one embodiment, the light-receiving surfaces can reflect and / or transmit 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.

[0120] In one embodiment, the light-combining unit comprises a light-combining dichroic mirror mounting base and the plurality of light-combining dichroic mirrors, the light-combining dichroic mirror mounting base 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.

[0121] 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.

[0122] 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 achieve individual cooling for each LED lamp in the LED lamp group.

[0123] In one embodiment, the cooling flow channel runs through the optical seat to individually cool each LED lamp in the LED lamp group.

[0124] In one embodiment, the cooling flow channel comprises one or more water outlets and one or more water inlets.

[0125] 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 emitted light to be perpendicular to the straight line where the LED lamp, the light-combining unit and the cuvette are located, which is perpendicular to the placement surface of the sample analyzer.

[0126] In one embodiment, a corresponding focusing unit is arranged on the light path of the emitted light to the mirror; the focusing unit is used to focus the emitted 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 emitted light; the emitted light is flattened by the flat mirror and then sorted into monochromatic light of corresponding wavebands by the light-splitting assembly for detection by the detection unit.

[0127] In one embodiment, the first beam splitter and the dichroic mirror have a transmittance Tave≥90% in the transmissive region or a transmittance Tave≤5% in the reflective region.

[0128] In one embodiment, the beam splitting unit further comprises a plurality of narrowband filters, each of which is arranged in one-to-one correspondence with each dichroic mirror.

[0129] In one embodiment, the beam combining unit comprises a beam combining dichroic mirror mounting seat and a plurality of beam combining dichroic mirrors, the beam combining dichroic mirror mounting seat being used to integrate the plurality of beam combining dichroic mirrors; the beam combining dichroic mirror serving as a light receiving surface of the beam combining unit.

[0130] In one embodiment, the exiting light is sorted by the beam splitting unit into monochromatic light of corresponding wavebands for detection by the detection unit.

[0131] 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.

[0132] In one embodiment, the cooling flow channel penetrates through the optical seat to cool each LED lamp in the LED lamp group, respectively.

[0133] 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.

[0134] Compared with the prior art, the utility model has the advantages that the utility model uses a plurality of LED lamps as light sources, the LED lamps replace the existing halogen lamps, since the LED lamps have a longer service life, the problems of short service life, frequent maintenance and long preheating time during use of the halogen lamps can be completely solved; and the light beam of the LED lamp can meet the requirement of optical power, thereby ensuring the accuracy and reliability of detection. BRIEF DESCRIPTION OF DRAWINGS

[0135] Hereinafter, the utility model will be described in more detail based on the embodiments and with reference to the drawings.

[0136] Figure 1 is a structural schematic view of a chemical analyzer in an embodiment of the utility model;

[0137] Figure 2 is a relative spectral radiation diagram of a wide-spectrum LED lamp;

[0138] Figure 3 is a light source light path plane schematic view of a chemical analyzer in an embodiment of the utility model;

[0139] Figure 4 is a structure diagram of a Galileo type beam expander in one of the embodiments of the present application;

[0140] Figure 5 is a structure diagram of a Kepler type beam expander in another embodiment of the present application;

[0141] Figure 6 is a light source light path three-dimensional structure diagram of a chemical analyzer in the embodiment of the present application;

[0142] Figure 7 is a three-dimensional structure diagram of a light combination dichroic mirror mounting seat in the embodiment of the present application;

[0143] Figure 8 is a three-dimensional structure diagram of an optical seat in the embodiment of the present application;

[0144] Figure 9 is a structure diagram of a cooling flow channel in the embodiment of the present application;

[0145] Figure 10 is a light path diagram of a first LED lamp in the embodiment of the present application;

[0146] Figure 11 is a light path diagram of a second LED lamp in the embodiment of the present application;

[0147] Figure 12 is a light path diagram of a third LED lamp or a fourth LED lamp in the embodiment of the present application;

[0148] Figure 13 is a structure diagram of a colorimetric assembly in the embodiment of the present application;

[0149] Figure 14 is a structure diagram of a reflected light beam after aggregation in the embodiment of the present application;

[0150] Figure 15 is a structure diagram of a light splitting unit in one of the embodiments of the present application;

[0151] Figure 16 is a structure diagram of a light splitting unit in another embodiment of the present application;

[0152] Figure 17 is a structure diagram of a light splitting unit of a sample analyzer in the preferred embodiment of the present application;

[0153] Figure 18 is a structure diagram of a light splitting unit in another embodiment of the present application;

[0154] Figure 19The structure of the light splitting unit of another embodiment of the utility model is intended.

[0155] Figure 20 The structure of the optical module of the sample analyzer in the embodiment of the utility model is intended.

[0156] Reference signs:

[0157] 1, sample module; 11, sample rack; 12, sample tube;

[0158] 2, sample dispensing module;

[0159] 3, reagent module; 31, reagent bin; 32, reagent box;

[0160] 4, reagent dispensing module; 6, mixing module;

[0161] 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;

[0162] 8, incubation module; 9, cleaning module; 10, ISE analysis assembly; 15, reagent box;

[0163] 100, first LED lamp; 101, second LED lamp; 102, third LED lamp; 103, fourth LED lamp;

[0164] 104, first plano-convex lens; 105, second plano-convex lens; 106, third plano-convex lens; 107, fourth plano-convex lens;

[0165] 110, first light combining dichroic mirror; 108, second light combining dichroic mirror; 109, third light combining dichroic mirror;

[0166] 111, plano-concave lens;

[0167] 112, 118: double convex lens;

[0168] 113, front diaphragm; 114, incubation groove front window piece; 115, colorimetric cup; 116, incubation groove rear window piece; 117, rear diaphragm;

[0169] 119, reflector; 120, fifth plano-convex lens; 121, plano-optical diaphragm; 122, first light splitting dichroic mirror;

[0170] 123, 124, 125, 126, 127, 128, 142, 143, 144, 145, 146, 147: light splitting dichroic mirror;

[0171] 136, 137, 138, 139, 140, 141, 129, 130, 131, 132, 133, 134, 135: narrow-band filter;

[0172] 150: detector; 160: concave diffraction grating. DETAILED DESCRIPTION

[0173] The utility model will be further described below with reference to the drawings.

[0174] 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.

[0175] As shown, 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 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.

[0176] Optical module 7 of sample analyzer generally includes light source unit, mixing unit, light splitting unit and detection unit.The detection principle of optical module 7 is based on Lambert Beer law to detect absorbance of different wavelengths.According to Lambert Beer law, when a parallel monochromatic light is vertically through a uniform non-scattering absorbent material, its absorbance A is proportional to the concentration c of absorbent material and the thickness L of absorption layer, and is inversely proportional to transmittance T, that is, absorbance A satisfies the following expression:

[0177] A=lg (1 / T)=Kbc=lg (Io / It);

[0178] Wherein, A is absorbance, abbreviation Abs / OD, unitless;

[0179] T is transmittance;

[0180] K is absorption coefficient, L / (g-cm);

[0181] b is the solution thickness, cm;

[0182] c is the solution concentration, g / L;

[0183] Io is the transmitted light intensity, cd (Candela / New Candlepower);

[0184] It is the incident light intensity, cd.

[0185] 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 object to be measured. 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 band 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 commonly used in biochemical detection, and as the main wavelength of many detection projects, it participates in the calculation of the results.

[0186] The optical module 7 includes a plurality of light source units, and the light source unit is an LED lamp group composed of a plurality of LED lamps. The combination of a plurality of LED lamps can achieve the effect of complex light. The number of LED lamps may, for example, be 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 includes 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 complex light combined by the beam combining unit into single-color light of the corresponding wavelength band for the detection unit to detect. The complex light can cover the wavelengths required for biochemical detection; and the detection unit is used for optical detection of the single-color light.

[0187] Industry standards require that the optical module 7 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 standards and instrument design of each optical performance indicator are shown in Table 1 below.

[0188] Table 1 list of optical performance index required by industry standard

[0189]

[0190] The lower limit of light energy required for biochemical detection needs to consider multiple factors, such as light source parameters, optical performance index parameters of the instrument, lower limit range of 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 indexes required by the above industry standard requirements, and its detection performance needs to be improved.

[0191] In some embodiments of the utility model, the optical performance index parameters of the optical module 7 at least meet one of the following conditions:

[0192] When measuring the 340nm wavelength provided by the 340nm LED lamp, the stray light is: absorbance A>5;

[0193] When measuring any one of 340nm provided by the 340nm LED lamp and 450nm-520nm provided by the wide spectrum LED lamp, the absorbance linear range is: the maximum absorbance with a relative bias within ±5% is greater than or equal to 4.0;

[0194] 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;

[0195] When measuring any one of 340nm provided by the 340nm LED lamp and 600nm-700nm provided by the wide spectrum LED lamp, the absorbance stability is: the change of absorbance is not greater than 0.01; and

[0196] When measuring the 340nm wavelength provided by the 340nm LED lamp, the absorbance repeatability is: the coefficient of variation CV≤0.4%.

[0197] The optical performance index of the optical module 7 of the utility model is shown in Table 2.

[0198] Table 2 list of optical performance index of the optical module 7 of the utility model

[0199]

[0200] According to Table 1 and Table 2, the optical performance index of the optical module 7 of the utility model is much higher than the requirement of the industry standard, and the detection performance is greatly improved.

[0201] In some embodiments, the optical module 7 of the utility model has the absorbance linear range as shown in Table 3 when measuring each wavelength.

[0202] Table 3: List of absorbance linear range of optical module 7

[0203]

[0204]

[0205] According to Table 3, when the optical module 7 of the utility model measures the 340nm wavelength provided by the 340nm LED lamp, the absorbance linear range is: 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 the wide-spectrum LED lamp, the absorbance linear range is: 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 the wide-spectrum LED lamp, the absorbance linear range is: 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 the wide-spectrum LED lamp, the absorbance linear range is: the maximum absorbance with a relative bias of 0.33% is greater than or equal to 4.17.

[0206] Therefore, the absorbance linear range of the optical module 7 of the utility model far exceeds the requirement of the industry standard for this parameter.

[0207] When performing optical detection, the minimum light power of the monochromatic light of 340nm wavelength received by the detection unit is lower than that of the monochromatic light of 405nm wavelength. The number of detection units is the same as the number of monochromatic light separated by the light splitting unit.

[0208] The detection unit of the optical module 7 includes a detector, and the detector includes a photodiode (PD). The photodiode can receive the monochromatic light separated by the light splitting unit. Different photodiodes have different photosensitivity coefficients for different wavelengths, and the photosensitivity coefficient of the photodiode corresponding to these wavelengths can convert the light power value into the photocurrent value, and the photosensitivity coefficient of the photodiode corresponding to these wavelengths also directly affects the lower limit value that can be detected.

[0209] The lower limit of the light energy value of each wavelength of the photodiode of the utility model is characterized by the light power and / or photocurrent of the photodiode.

[0210] Specifically, the light power and / or photocurrent of the photodiode of the utility model satisfy the following conditions:

[0211] When measuring the 340nm wavelength provided by the 340nm LED lamp, the light power of the photodiode is greater than or equal to 5.28x10 -2 μw (i.e. the lower limit of the light power is 5.28x10-2 μw), and / or the photocurrent of the photodiode is greater than or equal to 10.98 nA (i.e., the lower limit of the photocurrent is 10.98 nA).

[0212] Further, when the other wavelengths are measured, the lower limit of the optical power and the lower limit of the photocurrent of the photodiode are shown in Table 4 below.

[0213] Table 4 Summary of the lower limit of the photocurrent of the photodiode meeting the biochemical detection

[0214]

[0215] The absorbance linear range in Table 3 above is an especially important parameter index. Because the absorbance linear range represents the upper limit 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 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 can be measured by the photodiode, so that the lower limit requirement of the light energy value of each wavelength of the photodiode can be obtained.

[0216] Therefore, it can be understood that when the absorbance linear range of the optical module 7 of the utility model meets the requirements of Table 3 above, then the optical power of the photodiode and / or the lower limit of the photodiode of the utility model meet the requirements of Table 4 above; or conversely, when the optical power of the photodiode and / or the lower limit of the photodiode of the utility model meet the requirements of Table 4 above, then the absorbance linear range of the optical module 7 of the utility model meets the requirements of Table 3 above.

[0217] In addition, it should be noted that the dark current value of the photodiode is generally less than 50 pA; the bottom noise dark current brought by the circuit and the external environment to the photodiode is not more than 100 pA (1 pA = 10 -12 A).

[0218] As shown in Table 5, the maximum bottom noise photocurrent and optical power value corresponding table of the photodiode of different wavelengths is shown. Among them, the maximum bottom noise is obtained by conversion under the condition that the circuit amplification multiple is adjustable maximum.

[0219] Table 5 Maximum bottom noise optical power and photocurrent value corresponding table of the photodiode under different wavelengths

[0220]

[0221] When selecting the photodiode, the optical power and / or the photocurrent thereof 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 50 pA.

[0222] In summary, the optical performance index of the optical module 7 is much higher than the industry standard, and the photodiode of the optical module 7 needs to meet the lower limit value of optical power and / or optical current.

[0223] 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 service life of the halogen lamp, frequent maintenance, and long preheating time during use.

[0224] To solve 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 a 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.

[0225] 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 light intensity of the transmitted light 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.

[0226] During optical detection, the minimum optical power of the monochromatic light of 340nm wavelength received by the detection unit is lower than that of the monochromatic light of 405nm wavelength. The plurality of LED lamps respectively have corresponding lower limit optical powers, and the lower limit optical power value P1 of the 340nm LED lamp is the smallest among the lower limit optical power values of the plurality of LED lamps. In addition, the plurality of LED lamps respectively have corresponding standard use optical powers, and the standard optical power of the 340nm LED lamp is lower than that of the wide-spectrum LED lamp. The standard use optical power of the 340nm LED lamp ranges from 1.2mW to 2.5mW.

[0227] In addition, the wide-spectrum LED lamp provides a wavelength of 450nm-800nm, which is excited by 450nm 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 wherein the abscissa represents the wavelength, and the ordinate represents the relative radiation intensity. From Figure 2It can be seen that, among them, 450nm is taken as the peak wavelength, the relative radiation intensity is 100%, and the relative radiation intensities of 480nm and 660nm are the lowest, which are 9.5% and 5% respectively. Therefore, the lower limit of the wide spectrum band light energy needs to focus on the wavelength with lower relative radiation intensity, that is, the light intensity of the wavelength with the lowest relative radiation intensity needs to meet the requirements, so as to carry out the corresponding biochemical detection.

[0228] The lower limit of the energy value of the light source is characterized by the light power value.

[0229] Further, the lower limit light power value P1 of the 340nm LED lamp providing a wavelength of 340nm is the smallest, that is, smaller than the lower limit light power value of the LED lamp providing other wavelengths.

[0230] Further, the lower limit light power value P3 of the 380nm LED lamp providing a wavelength of 380nm is the largest, that is, larger than the lower limit light power value of the LED lamp providing other wavelengths.

[0231] Further, the lower limit light power value P1 of the 340nm LED lamp providing a wavelength of 340nm is 0.06mW. The lower limit light power value P3 of the LED lamp providing a wavelength of 380nm is 0.7mW.

[0232] Further, the lower limit light power value P4 of the 405nm LED lamp providing a wavelength of 405nm is 0.5mW. The lower limit light power value P2 of the wide spectrum LED lamp providing a wavelength of 450nm-800nm is 0.16mW.

[0233] The lower limit light power value of the LED of the utility model is shown in the following table 6.

[0234] Table 6: Lower limit light power value list of LED

[0235]

[0236] The lower limit light power value of the LED of the utility model satisfies the following conditions: P1 < P2 < P4 < P3.

[0237] 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 use. 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 (power supply current adjustable and circuit amplification factor adjustable), so as to achieve the purpose of improving the service life of the optical module 7.

[0238] Therefore, it can be understood that when the optical absorbance linear range of the optical module 7 of the utility model meets the requirements of the above table 3, the lower limit value of the optical power of the LED lamp of the utility model meets the requirements of the above table 6; or conversely, when the lower limit value of the optical power of the LED lamp of the utility model meets the requirements of the above table 6, the optical absorbance linear range of the optical module 7 of the utility model meets the requirements of the above table 3.

[0239] In summary, the utility model provides the technical scheme of taking 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 that the problems of short service life, frequent maintenance and long preheating time of halogen lamps can be completely solved, thereby providing an effective solution for the precision level of the sample analyzer in the clinical detection project test process to reach or exceed that of the halogen lamp as a light source. Moreover, the utility model proposes that the lower limit optical power value P1 of the LED lamp of 340nm is minimum, for example, it can be 0.06mW, and its optical performance index is much higher than the industry standard.

[0240] 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.

[0241] As shown in the above table 1, the wavelength range of the LED lamp is 340nm-800nm. Figure 3 As shown in the above table 1, the wavelength range of the LED lamp is 340nm-800nm.

[0242] More specifically, the second LED lamp 101 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, so as to meet the requirement of covering the wavelength required for the above biochemical detection.

[0243] Further, at least one LED lamp is arranged in a straight line with the cuvette 115 at the detection position. Specifically, as shown in the above table 2, the wide-spectrum LED lamp is arranged in a straight line with the cuvette 115 at the detection position. Figure 3 Further, at least one LED lamp is arranged in a straight line with the cuvette 115 at the detection position. Specifically, as shown in the above table 2, the wide-spectrum LED lamp is arranged in a straight line with the cuvette 115 at the detection position.

[0244] It can be understood that other waveband LED lamps can also be selected for combination as long as the wavelengths required for biochemical detection of 340nm-800nm can be covered.

[0245] The utility model discloses in order to satisfy the requirement of covering the wavelength required for above-mentioned biochemical detection, has adopted 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 clinical project of sample analyzer, causes the precision of complete machine to be poor.

[0246] In view of the above problem, the utility model provides a kind of broadband light source light path scheme capable of satisfying the 340nm-800nm wavelength of sample analyzer, it aims at solving the problem of poor beam uniformity caused by different LED lamp due to different divergence angle.

[0247] 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 to the light beam emitted by each LED lamp, to adjust the divergent light emitted by each LED lamp into parallel light.The 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 to the light beam emitted by the LED lamp with certain light-emitting angle.

[0248] Further, the flat light device can be a plano-convex lens, for example.

[0249] As shown in Figure 3 The flat light device is respectively a first plano-convex lens 104 on the light path of the first LED lamp 100, a second plano-convex lens 105 on the light path of the second LED lamp 101, a third plano-convex lens 106 on the light path of the third LED lamp 102 and a fourth plano-convex lens 107 on the light path of the fourth LED lamp 103. The curvature radius and diameter of each plano-convex lens are matched with the corresponding LED lamp.

[0250] At least one of the plurality of LED lamps has a maximum divergence angle of not 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°.

[0251] Further, in order to realize 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:

[0252] The variable divergence angle of the first LED lamp 100 is 0°-30°;

[0253] The variable divergence angle of the second LED lamp 101 is 0°-30°; and

[0254] The variable divergence angles of the third LED lamp 102 and the fourth LED lamp 103 are both 0°-15°.

[0255] The variable divergence angles of the four LED lamps described above are selected in a certain variable range, so that the selection of the LED lamps is more flexible and replaceable.

[0256] Further, the curvature radius and the diameter of the flat light device should be matched with the corresponding LED lamp to perform flat light of a certain optical path distance. For example, the second plano-convex lens 105 on the light path of the second LED lamp 101 can be compatible with the LED lamp with a variable divergence angle in the range of 20°-30°. The third plano-convex lens 106 and the fourth plano-convex lens 107 on the light path of the second plano-convex lens 105 of the third LED lamp 102 and the fourth LED lamp 103 can perform small-angle beam parallel processing.

[0257] Further, the performance of the first plano-convex lens 104 and the second plano-convex lens 105 is better than that of the third plano-convex lens 106 and the fourth plano-convex lens 107. Since the second LED lamp 101 and the first LED lamp 100 are both products generated by new technical breakthroughs, the batch difference of the products can be large, that is, the divergence angles of different second LED lamps 101 can differ greatly, and the divergence angles of different first LED lamps 100 can also differ greatly. The plano-convex lens is used to perform flat light on the light emitted by the corresponding LED lamp. If the plano-convex lens can only receive light with a small range of divergence angles (for example, 20°), but the divergence angle of the light source is large (for example, 30°) at this time, the plano-convex lens cannot collect and perform flat light on all the light emitted by the LED lamp, which will reduce the utilization rate of light energy. Therefore, the divergence angle that can be received by the plano-convex lens needs to be relatively large, so as to accommodate the unstable divergence angle of the LED lamp as much as possible.

[0258] In summary, the utility model discloses a flat light device for performing flat light processing on the light beams emitted by each LED lamp with a certain light-emitting angle, which can ensure the uniformity of the combined light and avoid affecting the test results of the clinical items of the sample analyzer.

[0259] As described above, the utility model discloses a plano-convex lens for performing flat light processing on the light beams emitted by each LED lamp, but the directions and angles of the light beams emitted by each LED lamp are different, so the directions and angles of the light beams after flat light are also different. When detecting, the light beams with different directions and angles need to be combined into one beam.

[0260] To solve the above problems, the optical module 7 further comprises a light combining device. The light combining device combines and filters light beams of different wave bands by using the principle of half reflection and half transmission, so as to combine light beams of different directions and different angles into one beam.

[0261] Further, the light combining device comprises light combining dichroic mirrors and / or a combination of light combining dichroic mirrors, and the number of light combining dichroic mirrors is less than or equal to the number of LED lamps.

[0262] As shown in the example, Figure 3 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:

[0263] 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 (i.e., the first light combining dichroic mirror 110 transmits light in the wave band of 370nm-812nm and reflects light in the wave band of 330nm-350nm);

[0264] The second light combining dichroic mirror 108 can transmit the light emitted by the second LED lamp 101 and reflect the light reflected and transmitted by the third light combining dichroic mirror 109 (i.e., the second light combining dichroic mirror 108 transmits light in the wave band of 439nm-812nm and reflects light in the wave band of 369nm-416nm); and

[0265] 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 wave band of 398nm-812nm and reflects light in the wave band of 368nm-387nm).

[0266] In addition, the transmittance Tave of the light combining dichroic mirror in the transmission region is greater than or equal to 90%, and the Tave in the reflection region is less than or equal to 5% (i.e., the reflectivity is greater than 95%).

[0267] As shown in the example, Figure 3 for the light beam emitted by the first LED lamp 100, after passing through the flat light of the first plano-convex lens 104, it is incident on the first light combining dichroic mirror 110. Since the first LED lamp 100 emits a light beam with a wavelength of 340nm, the light beam is reflected at the first light combining dichroic mirror 110.

[0268] Similarly, for the light beam emitted by the second LED lamp 101, after passing through the flat light of the second plano-convex lens 105, the light beam is incident on the second light combining dichroic mirror 108, since the second LED lamp 101 emits a light beam with a wavelength of 450nm-800nm, the light beam is transmitted at the second light combining dichroic mirror 108; the transmitted light beam is incident on the first light combining dichroic mirror 110, and thus the light beam is transmitted at the first light combining dichroic mirror 110.

[0269] For the light beam emitted by the third LED lamp 102, after passing through the flat light of the third plano-convex lens 106, the light beam is incident on the third light combining dichroic mirror 109, since the third LED lamp 102 emits a light beam with a wavelength of 380nm, the light beam is reflected at the third light combining dichroic mirror 109; the reflected light beam is incident on the first light combining dichroic mirror 110, and thus the light beam is transmitted at the first light combining dichroic mirror 110.

[0270] For the light beam emitted by the fourth LED lamp 103, after passing through the flat light of the fourth plano-convex lens 107, the light beam is incident on the third light combining dichroic mirror 109, since the fourth LED lamp 103 emits a light beam with a wavelength of 405nm, the light beam is transmitted at the third light combining dichroic mirror 109; the reflected light beam is incident on the first light combining dichroic mirror 110, and thus the light beam is transmitted at the first light combining dichroic mirror 110.

[0271] It can be understood that as the detection light source, the LED lamp can be selected to cover the wavelength range of 340nm-800nm, and the light combining dichroic mirror with an adaptive wavelength range is selected according to the wavelength range of the LED lamp, and the same effect of the utility model can still be achieved.

[0272] In summary, the light combining dichroic mirror can combine the parallel light of the four LED lamps into the same light beam, and thus the complex color light with a wavelength range of 340nm-800nm required for biochemical detection can be obtained.

[0273] In addition, the mutual combination of the LED lamps with variable divergence angles, the short light path parallel light processing, and the light beam combining can avoid the problem that the angle error is introduced when the light beam with an angle enters the light combining dichroic mirror, thereby affecting the quality of the light beam combining.

[0274] As described above, the utility model obtains the complex color light with a wavelength range of 340nm-800nm required for biochemical detection through the light combining device. However, since the light emitting angles of the LED lamps are different, the light beam diameters after the parallel light processing are different, and if the light beams with different diameters are directly imaged, the light beam uniformity cannot be guaranteed, the degree of variation of the light quantity of different wavelengths is obviously different, and the precision of the double-wavelength test project in the sample analyzer can be seriously affected, and thus the selection of the complex color light needs to be considered.

[0275] To achieve uniform light beams and consistent light intensity variations after combining different LED lights, enabling the overall testing to achieve the same detection effect as halogen lamps, this invention proposes a beam expansion design. By expanding the beams, the parallel light beams after different path shaping can be enlarged, resulting in a larger overlap area for beams of different aperture sizes. Then, within the fully overlapping area, a beam size suitable for the sample analyzer is selected for detection. At this point, the collimation of the received beam for the test object is close to that of an ideal beam, thus achieving optimal uniformity.

[0276] Specifically, the optical module 7 includes a beam expander located in the optical path after beam combining. The beam expander can amplify different beams in the flat portion, thereby providing collimated light for the object under test. More specifically, the beam expander is located between the first dichroic mirror 110 and the object under test; in other words, the beam expanded by the beam expander can illuminate the object under test for detection.

[0277] Preferably, in such Figure 4 In the example shown, the beam expander is a Galilean beam expander. The Galilean beam expander includes a plano-concave lens 111 and a biconvex lens 112 arranged sequentially in the optical path after beam combining. It can amplify beams of different thicknesses, thus significantly increasing the overlapping area of ​​the four LEDs.

[0278] like Figure 4 As shown, the focal length of the plano-concave lens 111 is f1, and the focal length of the biconvex lens 112 is f2. Therefore, the beam passing through the Galilean beam expander will be enlarged to its original focal length m. 12 times (where m) 12 =f2 / f1). The divergence angle of the beam after expansion by a Galilean beam expander will be smaller by m than the divergence angle when it enters the Galilean beam expander. 12 The beam incident on the Galilean beam expander is a parallel beam that has been shaped and combined. Therefore, for the object under test, the collimation of the parallel beam received in the overlapping area will be close to that of the ideal beam, and the uniformity can also be optimized.

[0279] Optionally, in such Figure 5 In the example shown, the beam expander is a Keplerian beam expander. A Keplerian beam expander includes two biconvex lenses, namely... Figure 5 The numbers 111-1 and 112-1 are shown.

[0280] If one of the biconvex lenses has a focal length of f1 and the other biconvex lens 112 has a focal length of f2, then the beam passing through the Keplerian beam expander will also be amplified to its original size m. 12 times (where m) 12= f2 / f1). The beam divergence angle after the beam expander is smaller than the beam divergence angle entering the beam expander by m 12 times, and since the light beam entering the beam expander is parallel light after shaping and combining, the collimation of the parallel light received by the object to be measured is close to an ideal light beam, and the uniformity is also optimal.

[0281] In summary, the utility model discloses a beam expander arranged in the light path after combining, which can expand the light beam of the parallel light after shaping to increase the overlapping area of the light beams of different diameters, so that the collimation of the light beam irradiated to the object to be measured is close to an ideal light beam, i.e., the uniformity of the light beam is ensured, thereby improving the precision of the double-wavelength test project in the sample analyzer.

[0282] 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. In optical design, 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, the light source lamp panel may interfere, and the optical structure may occupy a large area.

[0283] For example, in the optical design of 3 or 4 LED lamps, two LED lamps are usually arranged with a small distance between the same directional lamp axes in order to consider the light path design and energy, and if the bases of the two LED lamps are in the same plane, the two LED lamps can be arranged by welding on the same circuit board; if the bases of the two LED lamps are in different planes, a circuit board needs to be welded for each LED lamp, and at this time, the circuit board may interfere with the circuit board or other structures.

[0284] Therefore, in order to solve this problem, the utility model discloses a three-dimensional arrangement of LED lamps according to the specific arrangement of each LED lamp and other optical elements, so as to achieve the purpose of miniaturization.

[0285] In the utility model, the number of LED lamps is greater than or equal to 3. The lamp panels of the LED lamps are respectively arranged on different planes in a rectangular space coordinate system, for example, the lamp panels of three LED lamps are respectively arranged on three mutually perpendicular planes in a rectangular space coordinate system.

[0286] Further, the lamp beads of at least two LED lamps can be arranged in the same height plane or in the same section plane, and further, at least one other LED lamp is arranged in a plane parallel to the height plane or the section plane.

[0287] For example, the lamp panels of the three LED lamps are respectively arranged on three mutually perpendicular planes in a rectangular space coordinate system. Figure 6In the shown example, a stereoscopic ray diagram of 4 LED lamps is shown. Figure 4 As shown, the first LED lamp 100, the second LED lamp 101, the third LED lamp 102 and the fourth LED lamp 103 are respectively located on the back plane, the left plane, the front plane and the bottom plane in the rectangular coordinate system. And wherein the first LED lamp 100, the second LED lamp 101 and the third LED lamp 102 are respectively located in the same height plane.

[0288] Through such a setting mode, the interference between the lamp panel and the lamp panel or the lamp panel and other structures in the prior art is avoided. And the stereoscopic layout of each LED lamp makes the land occupation area of the whole optical structure smaller, thereby facilitating the miniaturization of the sample analyzer.

[0289] In summary, the utility model discloses a stereoscopic layout of each LED lamp, which can not only avoid interference problems, but also reduce the volume, so that the sample analyzer meets the miniaturization requirement.

[0290] When all the optical elements are stereoscopically arranged, the specific mounting mode of the combining dichroic mirror needs to be considered.

[0291] As shown in the figure, Figure 7 The optical module 7 also includes a combining unit, and the unit has at least two light receiving surfaces. The combining unit receives the light emitted by the corresponding LED lamp through the light receiving surface, and the light receiving surface can reflect and / or transmit light of different wavelengths. The light emitted by the LED lamp group is combined into composite light after being reflected or transmitted by at least two light receiving surfaces.

[0292] The combining unit includes the above-mentioned combining dichroic mirrors and / or combinations thereof, and also includes a combining structure for integrating the above-mentioned combining dichroic mirrors. A plurality of the combining dichroic mirrors are respectively used as the light receiving surface of the combining unit.

[0293] Specifically, the combining structure includes a combining dichroic mirror mounting seat 71, and the first combining dichroic mirror 110, the second combining dichroic mirror 108 and the third combining dichroic mirror 109 are respectively installed on the mounting positions of different sides of the combining dichroic mirror mounting seat 71. Among them, one of the mounting positions on the combining structure makes the first combining dichroic mirror 110 capable of reflecting the light emitted by the first LED lamp 100 and transmitting the light reflected and transmitted by the second combining dichroic mirror 108. One of the mounting positions on the combining structure makes the second combining dichroic mirror 108 capable of transmitting the light emitted by the second LED lamp 101 and reflecting the light reflected and transmitted by the third combining dichroic mirror 109. One of the mounting positions on the combining structure makes the third combining dichroic mirror 109 capable of reflecting the light emitted by the third LED lamp 102 and transmitting the light emitted by the fourth LED lamp 103.

[0294] Further, the light combining dichroic mirror mounting base 71 has a plurality of inclined surfaces, the number of the inclined surfaces respectively corresponds to the number of the light combining dichroic mirrors. Each of the inclined surfaces is provided with a mounting groove 711 for mounting a corresponding light combining dichroic mirror. Figure 7 As shown in the figure, the first light combining dichroic mirror 110 is arranged on the inclined surface on the right side of the light combining dichroic mirror mounting base 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 base 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 base 71.

[0295] The inner side edge of each of the mounting grooves 711 can be close to the outer side edge of the corresponding light combining dichroic mirror. Each of the light combining dichroic mirrors can be fixed in the corresponding mounting groove 711 by one or more of sliding mounting, clamping and mounting, and adhesive mounting.

[0296] Further, as shown in the figure, Figure 8 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.

[0297] Specifically, the rear side, the left side, the front side and the bottom side of the optical seat 72 are respectively provided with fasteners for fixing the lamp panels of the corresponding LED lamps, and are respectively provided with lamp bead holes for mounting the lamp beads of the corresponding LED lamps.

[0298] In addition, the optical seat 72 is further provided with a containing cavity 721 for mounting the light combining dichroic mirror mounting base 71. The light combining dichroic mirror mounting base 71 can be fixed in the containing cavity 721 by one or more of sliding mounting, clamping and mounting, and adhesive mounting.

[0299] Therefore, the utility model only needs two structural members, i.e. the light combining dichroic mirror mounting base 71 and the optical seat 72, to achieve the purpose of combining the light beams of four independent LED lamps located in different directions into one light beam. The structures of the light combining dichroic mirror mounting base 71 and the optical seat 72 are convenient for high-precision machining, so as to ensure the position accuracy of each optical element.

[0300] In addition, since each of the LED lamps generates a certain amount of heat during operation, the cooling mode of the optical module 7 also needs to be considered.

[0301] The utility model discloses that the utility model concept of cooling the light source of the optical module 7 by using the incubation water in the incubation module 8 described above is proposed.

[0302] Specifically, as shown in the figure, Figure 9As shown, the optical seat 72 is provided with cooling flow channels, which respectively surround the light sources.

[0303] In some embodiments, the cooling fluid in the cooling flow channels is liquid, i.e. the cooling flow channels cool the light sources by water cooling.

[0304] The cooling flow channels include a water outlet 73 and a water inlet 74, which are connected by a flow path inside the optical seat 72. The flow path can be a pipe or the like arranged separately in the optical seat 72, or can be a machining passage directly machined in the optical seat 72.

[0305] The pipe between the water outlet 73 and the water inlet 74 bypasses or surrounds the light sources of the optical module 7.

[0306] The number of cooling flow channels corresponds to the number of light sources, so as to achieve individual cooling for 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 an incubation water supply pipe in the incubation module 8.

[0307] For example, the water inlet 74 of each cooling flow channel is in communication with the incubation water supply pipe in the incubation module 8, so that the incubation water in the incubation module 8 can enter the optical seat 72 through the water inlet 74 to cool the light sources; the cooled incubation water flows out from the water outlet 73, which can be connected to a recycling system.

[0308] 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, so that the stability of the light beams of different LED lamps can be ensured when the incubation water is used to cool the light sources; on the other hand, since the incubation water is used to incubate the mixture of the sample and the reagent in the colorimetric cup 5 in the incubation module 8, the incubation water is already an existing medium in the sample analyzer, and introducing it into the cooling flow channel to cool the light sources can reduce the medium providing structure and medium source outside the sample analyzer, and ensure the miniaturization of the sample analyzer.

[0309] Optionally, the number of water outlets 73 and water inlets 74 can be multiple. For example, for each light source, one water outlet 73 and one water inlet 74 can be provided; correspondingly, the number of cooling flow channels can also be multiple. Since the power of different light sources is different, the heat generated by them is also different, and their sensitivity to temperature is also different, so that the water outlet 73, the water inlet 74 and the cooling flow channel are respectively configured for each light source, which can achieve the control of the flow of the cooling flow channel of each light source, so as to take different degrees of heat dissipation for each light source.

[0310] Preferably, the number of water outlets 73 and water inlets 74 is one, and the cooling flow channel runs through the whole optical seat 72, thereby providing heat dissipation for each light source. The advantage of this scheme is that it can make the structure of the optical module 7 smaller and more compact, thereby meeting the miniaturization requirement. The water outlet 73 and the water inlet 74 can be located on the same side wall of the optical seat 72.

[0311] As shown in Figure 9 The cooling flow channel of the first LED lamp 100 is taken as an example for description. The water outlet 73 and the water inlet 74 are respectively arranged on the outer surface of the rear side wall of the optical seat 72, and the water outlet 73 and the water inlet 74 run through the lamp panel of the first LED lamp 100 and are in fluid communication through the machining passage (not shown) in the rear side wall of the optical seat 72. The pipeline is arranged around the first LED lamp 100, thereby cooling the first LED lamp 100.

[0312] In addition, the optical seat 72 is also provided with a plug 75. When the cooling flow channel is machined, an opening will be formed on the side wall of the optical seat 72, 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, thereby ensuring that the light source can be at a normal working temperature.

[0313] As described above, when detection is performed, it is necessary to ensure the light intensity of different wavelength light beams and the uniformity of light beam mixing. Therefore, the present application proposes that the light path is designed, that is, the light path of different LED lamps after flat light, light mixing and beam expansion is made the same, so as to ensure the light intensity of different wavelength light beams and the uniformity of light beam mixing, thereby improving the accuracy of sample analyzer project detection.

[0314] According to the above, the second LED lamp 101 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 light energy strengths are also not completely consistent, so the light emitting angle, light quantity strength and optical element loss are considered in the design distribution.

[0315] Specifically, the light source comprises a plurality of light emitting elements, and each of the plurality of light emitting elements is provided with a flat light device, and the flat light device 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 optical path distance from the flat light device to the colorimetric cup 115. The flat light device is arranged between the LED lamp and the combining unit. The optical module further comprises a beam expander; wherein the beam expander is used for expanding the combined light aggregated by the combining unit; the light emitted by each LED lamp has the same optical path distance from the flat light device to the beam expander.

[0316] The following takes the light emitting element as an LED lamp as an example for description. As shown in Figure 3 each LED lamp is provided with a flat light device, and the flat light device may be, for example, a flat convex lens.

[0317] 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 after flat light and entering the beam expander are the same. More specifically, the light path distances of the light beams of the plurality of LED lamps after flat light and entering the beam expander from the appropriate positions after flat light are the same. Wherein, the appropriate positions after flat light may be, for example, the best positions after flat light.

[0318] As shown in Figure 10 , 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 flat light and entering the first light combining dichroic mirror 110 from the best position after flat light, 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 flat light and entering the beam expander from the best position after flat light is L1+L3.

[0319] As shown in Figure 11 , 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 flat light and entering the first light combining dichroic mirror 110 from the best position after flat light, 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 flat light and entering the beam expander from the best position after flat light is L2+L3.

[0320] As shown in Figure 12As shown, the 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 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.

[0321] 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.

[0322] In summary, the utility model makes different LED lamps combined in the light path at appropriate positions for the same light path distance design idea, which not only can make different wavelength light beams better combined and make the selection of LED lamps more flexible, but also can ensure the consistency of the light quantity of different wavelength light beams.

[0323] 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 biochemical detection results. In addition, the establishment of the Lambert-Beer law also needs the following conditions:

[0324] 1. The light-absorbing substance is a non-scattering system;

[0325] 2. There is no interaction between light-absorbing particles;

[0326] 3. The interaction between radiation and the substance is limited to the process of light absorption, and there is no fluorescence and photochemical phenomenon.

[0327] However, the incident light conditions of the existing sample analyzer are all 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 measured object in the colorimetric assembly, which is not parallel light, nor vertical incidence. Therefore, for the biochemical detection system with focused incidence, the front and rear light beam design of the colorimetric assembly has great limitations, and the front and rear light beams cannot be adapted, and the selectivity is low.

[0328] To solve the above problems, the utility model provides a colorimetric assembly which can improve the light 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 front and rear light spots. In other words, the size of the light spot incident to 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 results of the non-uniform scattering system 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 will not cause great changes in structure and light path. It can also make the light source selection space wider. At the same time, the different matching conditions of the front and rear light spot sizes can meet the performance requirements of the whole machine, and the precision index far exceeds the industry standard.

[0329] In the sample analyzer, most detection items adopt a double-wavelength determination method, that is, the concentration result of the object to be measured is determined by simultaneously measuring the light signal change at two wavelengths. Specifically, the incident light is incident into the colorimetric assembly, and the light beam transmitted through the colorimetric assembly enters the subsequent spectrometer unit. The spectrometer unit divides the received complex light into the required monochromatic light, and then detects the signal of the monochromatic light beam through the detector. The circuit system performs photoelectric conversion, and finally outputs in the form of digital signal, so that the absorbance value of the measured object can be calculated, and then converted into the concentration result.

[0330] In this method, the two wavelengths are regarded as the main wavelength and the auxiliary wavelength of the test item respectively. The better the synchronization of the main and auxiliary wavelength light signals, the better the quantification, and the more accurate and reliable the test result. Therefore, whether it is a uniform determination object or a non-uniform scattering system determination object, the smaller the divergence angle of the incident light beam, the better, that is, the parallel light incidence is the best, which is more conducive to the determination of different systems. Therefore, the matching of the sizes of the front and rear light spots of the colorimetric assembly of the utility model can greatly reduce the influence of interference on the test result, reduce the influence of scattered light generated by interfering substances in the reaction, such as bubbles and unknown interfering substances in the reaction solution, on the transmitted light beam, so as to ensure the precision and accuracy of the biochemical detection performance.

[0331] It should be noted that the principle of double-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 and auxiliary wavelengths, thereby making the double-wavelength detection more accurate.

[0332] For example, Figure 13As shown, the incubation module 8 of the utility model includes a colorimetric assembly, the colorimetric assembly includes a colorimetric cup 115, incubation groove front window piece 114 and incubation groove rear window piece 116 located at both sides of the colorimetric cup 115, and front diaphragm 113 located in front of the incubation groove front window piece 114 and rear diaphragm 117 located behind the incubation groove rear window piece 116.

[0333] 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.

[0334] The colorimetric cup 115 has a light-receiving surface and a light-emitting surface, and the composite light combined by 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 resolved by the spectral resolution 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 spectral resolution unit can sort the light filtered by the rear diaphragm 117 into monochromatic light of corresponding wave bands for detection by the detection unit.

[0335] 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.

[0336] The light transmission area of the rear diaphragm 117 is smaller than the light transmission area of the front diaphragm 113. The front diaphragm 113 and the rear diaphragm 117 both have a circular light transmission surface, and the diameter of the light transmission surface of the front diaphragm 113 is 1-3 times the diameter of the light transmission surface of the rear diaphragm 117.

[0337] The upper top of the light transmission surface of the front diaphragm 113 does not exceed the liquid level of the liquid in the colorimetric cup 115 when the sample analyzer performs detection of the minimum reaction amount.

[0338] The size of the parallel light spot entering the colorimetric assembly is 2mm-3mm. The size of the light spot entering the spectral resolution unit after passing through the colorimetric assembly is 1mm-1.5mm.

[0339] Preferably, the size of the parallel light spot entering the colorimetric assembly, that is, the diameter D1 of the light transmission surface of the front diaphragm 113 satisfies: 2mm≤D1≤3mm; and the size of the light spot entering the spectral resolution system after passing through the colorimetric assembly, that is, the diameter D2 of the light transmission surface of the rear diaphragm 117 satisfies: 1mm≤D2≤1.5mm.

[0340] The matching relationship between the diameter D1 of the light transmission surface of the front diaphragm 113 and the diameter D2 of the light transmission surface of the rear diaphragm 117 is shown in Table 7.

[0341] Table 7 List of matching cases of the diameter of the light passage surface of the front light barrier 113 and the diameter of the light passage surface of the rear light barrier 117

[0342]

[0343] Further, in the case where the diameter D2 of the light passage surface of the rear light barrier 117 is the same as the diameter of the light passage surface of the front light barrier 113, the smaller the diameter D1 of the light passage surface of the front light barrier 113, the greater the coefficient of variation CV.

[0344] For example, according to Table 7, one matching mode is that the diameter D1 of the light passage surface of the front light barrier 113 is 2 mm, and the diameter D2 of the light passage surface of the rear light barrier 117 matched therewith is 1.5 mm; another matching mode is that the diameter D1 of the light passage surface of the front light barrier 113 is 3 mm, and the diameter D2 of the light passage surface of the rear light barrier 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 thus the precision of the latter matching mode is better.

[0345] This is because when the stray light effect caused by interference is considered, 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 passage surface of the small front light barrier 113 is matched with the diameter of the light passage surface of the large rear light barrier 117, the probability of the stray light caused by interference in the measured object entering the light splitting unit is relatively greater, and the effect on the test result is more obvious, so the coefficient of variation CV result will be relatively greater.

[0346] Similarly, if the diameter D1 of the light passage surface of the front light barrier 113 is 1 mm or 1.5 mm, the effect caused by interference will be smaller, and thus the coefficient of variation CV will be smaller, the precision will be higher, and the deviation will be smaller.

[0347] For example, in biochemical detection, the within-run precision of clinical items is a necessary measurement procedure for instruments. According to the industry standard in the field, the measurement items include alanine aminotransferase (ALT), urea (UREA), and total protein (TP). The ALT item is mainly aimed at the three clinical items. The measurement reaction degree of the low-concentration sample of this item is small, and the main wavelength of this item is 340 nm, and the secondary wavelength is 405 nm. The reaction degree changes very little, and it tests the precision of the detection system and the synchronization degree of the double-wavelength light quantity change even more. The smaller the CV of the concentration result, the more precise the instrument detection, and the greater the CV, the lower the instrument detection precision. Therefore, the precision result of the item with small reaction degree can be used to determine the performance of the light spot after matching. The measurement concentration of ALT in the industry standard is 30 U / L-50 U / L, and CV<5%.

[0348] The utility model discloses a corresponding ALT reagent, calibrant and corresponding determination process are used, with normal value quality control serum or fresh patient serum as sample, the ALT project under this concentration range is repeatedly tested, and each project is repeatedly tested 20 times, and the coefficient of variation (CV) of 20 times results is calculated, and is respectively shown in table 8 and table 9.

[0349] Table 8 shows the ALT precision (unfiltered biochemical composite quality control product) of the diameter of the light transmission surface of the front light barrier 113 and the diameter of the light transmission 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 transmission surface of the front light barrier 113 and the diameter of the light transmission surface of the rear light barrier 117 matched therewith.

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

[0351]

[0352] According to table 8, under the condition that the diameter of the light transmission surface of the rear light barrier 117 is the same, the smaller the diameter of the light transmission surface of the front light barrier 113, the greater the coefficient of variation CV. However, the diameter D1 of the light transmission surface of the front light barrier 113 satisfies 2mm≤D1≤3mm; and the diameter D2 of the light transmission surface of the rear light barrier 117 satisfies 1mm≤D2≤1.5mm, and the actually measured coefficient of variation CV is less than 3.5%, so the performance index of the sample analyzer of the utility model is far above the industry standard.

[0353] Table 9 shows the ALT precision (unfiltered biochemical composite quality control product) of the diameter of the light transmission surface of the front light barrier 113 and the diameter of the light transmission 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 transmission surface of the front light barrier 113 and the diameter of the light transmission surface of the rear light barrier 117 matched therewith.

[0354]

[0355] According to table 9, under the condition that the diameter of the light transmission surface of the rear light barrier 117 is the same, the smaller the diameter of the light transmission surface of the front light barrier 113, the greater the coefficient of variation CV. However, the diameter D1 of the light transmission surface of the front light barrier 113 satisfies 2mm≤D1≤3mm; and the diameter D2 of the light transmission surface of the rear light barrier 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.

[0356] In addition, from the data of table 8 and table 9, it can be seen that the precision result of the more uniform test object is better than that of the determination object containing interference, but through the light spot matching mode proposed by the utility model, for the project with small reaction degree such as ALT, the instrument can obtain the precision CV result far above the industry standard without filtering the sample during determination.

[0357] It can be understood that the selection of the diameter D1 of the light passing surface of the front light barrier 113 and the diameter D1 of the light passing surface of the rear light barrier 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 met.

[0358] In summary, the front light barrier 113 and the rear light barrier 117 with the diameter range of the light passing surface matched are arranged, so that the test result is more accurate.

[0359] As described above, the utility model discloses a kind of by making a parallel incident light incident into colorimetric component, and the light beam that passes through colorimetric component needs to be spectrally resolved, i.e.

[0360] In some embodiments, the sample analyzer of the utility model uses dichroic mirror spectrally resolved.

[0361] Specifically, as shown in Figure 14 The optical module 7 further 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 lenticular lens 118. The optical module 7 further includes a mirror 119, a fifth plano-convex lens 120, a flat light barrier 121 and a spectrally resolved unit arranged in sequence.

[0362] As shown in Figure 14 The light beam is incident into the lenticular lens 118 after being emitted from the rear light barrier 117. The lenticular lens 118 focuses the light beam emitted from the rear light barrier 117. The reflected light beam is incident into the fifth plano-convex lens 120. The fifth plano-convex lens 120 collimates the reflected light beam. The collimated light beam passes through the flat light barrier 121 and enters the spectrally resolved unit. The flat light barrier 121 eliminates edge stray light.

[0363] As shown in Figure 15 And Figure 16 Two forms of spectrally resolved by dichroic mirror are shown. Figure 15 And Figure 16 The two forms are straight light path spectrally resolved.

[0364] As shown in Figure 15As shown, the optical path of the beam splitter unit is in the lateral direction. The beam splitter unit includes a reflector 119, multiple dichroic mirrors, and a narrowband filter corresponding to each dichroic mirror.

[0365] Understandably, the number of dichroic mirrors is the same as the number of wavelengths required by the sample analyzer. Since the sample analyzer requires 13 wavelengths, there are 13 dichroic mirrors. These dichroic mirrors can be represented as 123, 124, 125, 126, 127, 128, 142, 143, 144, 145, 146, 147, and 148. Similarly, there are 13 narrowband filters, represented as 136, 137, 138, 139, 140, 141, 129, 130, 131, 132, 133, 134, and 135.

[0366] The light beam, after being flattened by the flat aperture 121, enters the reflector 119 and is reflected at the reflector 119 to the dichroic mirror 123 (the first dichroic mirror in the optical path). The dichroic mirror 123 reflects the 340nm light to the narrowband filter 136, turning it into monochromatic light. The monochromatic light then illuminates the detector (e.g., a photodetector) corresponding to the narrowband filter 136. Light with wavelengths greater than 340nm passes through the dichroic mirror 123 to the next dichroic mirror 124, and so on, for further beam splitting.

[0367] according to Figure 15 It can be seen that in this beam splitting method, the length b1 of the beam splitting unit is: b1 = N × a. Where N is the number of dichroic mirrors (i.e., the number of wavelengths), and a is the distance between two dichroic mirrors.

[0368] like Figure 16 As shown, the optical path of the beam splitter unit is vertical. The beam splitter unit includes multiple dichroic mirrors and narrowband filters corresponding to each dichroic mirror.

[0369] Similarly, the number of dichroic mirrors is the same as the number of wavelengths required by the sample analyzer. Since the sample analyzer requires 13 wavelengths, there are 13 dichroic mirrors. These mirrors can be designated as 123, 124, 125, 126, 127, 128, 142, 143, 144, 145, 146, 147, and 148. The number of narrowband filters is also 13, designated as 136, 137, 138, 139, 140, 141, 129, 130, 131, 132, 133, 134, and 135.

[0370] The light beam after collimating by the collimating diaphragm 121 is incident to a dichroic mirror 123 (the dichroic mirror is the first dichroic mirror in the light path), the dichroic mirror 123 reflects the light of 340 nm to a narrow-band filter 136 to become monochromatic light, the monochromatic light is incident to a corresponding detector (for example, a photodetector) of the narrow-band filter 136, and the light with a wavelength greater than 340 nm is transmitted to the next dichroic mirror 124 and is transmitted to the next dichroic mirror to be split.

[0371] According to Figure 16 It can be known that, in the light splitting mode, the length b2 of the light splitting unit is b2=N×a, wherein N is the number of the dichroic mirrors (that is, the number of the wavelengths), and a is the distance between two dichroic mirrors.

[0372] In a preferred embodiment, the utility model provides a layout mode of dichroic mirror, through reasonable use of space, the light path length in vertical direction is reduced by half, thereby the purpose of reducing the occupied space and reducing the loss of light energy is achieved.

[0373] As Figure 17 shown, the light splitting unit in the preferred embodiment of the utility model is shown. The light splitting unit comprises a first light splitting dichroic mirror 122 after the collimating diaphragm 121, specifically, the first light splitting dichroic mirror 122 is a one-to-two light splitting dichroic mirror, and its function is to split the polychromatic light after collimating by the collimating diaphragm 121 into two.

[0374] As Figure 17 shown, the first light splitting dichroic mirror 122 splits the light beam into two beams in different directions, for example, splits the light beam into one beam in horizontal direction and one beam in vertical direction, therefore, the light splitting unit further comprises a plurality of dichroic mirrors arranged in horizontal direction and a plurality of dichroic mirrors arranged in vertical direction. Wherein, the first light splitting dichroic mirror 122 and other dichroic mirrors reflect the wavelength band of 335 nm to 510 nm in the reflection area, and transmit the wavelength band of 541 nm to 805 nm in the transmission area; the transmittance T ave of the transmission area is greater than or equal to 90%, and the T ave of the reflection area is less than or equal to 5% (that is, the reflectivity is more than 95%). Therefore, the reflection wavelength band of the reflection area of the first light splitting dichroic mirror 122 and other dichroic mirrors is 340 nm, 380 nm, 405 nm, 450 nm, 480 nm and 505 nm, and the transmission wavelength band of the transmission area is 546 nm, 570 nm, 600 nm, 660 nm, 700 nm, 750 nm and 800 nm.

[0375] As Figure 17As shown, the light splitting unit further comprises a plurality of dichroic mirrors after the first dichroic mirror 122, wherein the plurality of dichroic mirrors in the horizontal direction can be represented by 123, 124, 125, 126, 127 and 128; the plurality of dichroic mirrors in the vertical direction can be represented by 142, 143, 144, 145, 146, 147 and 148.

[0376] 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.

[0377] 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.

[0378] In addition, the light splitting unit further comprises a plurality of narrowband filters, which are respectively arranged one-to-one with 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 respectively represented by 136, 137, 138, 139, 140 and 141, and the narrowband filters corresponding to each dichroic mirror in the vertical direction are respectively represented by 129, 130, 131, 132, 133, 134 and 135.

[0379] As shown in FIG. 1, the light splitting unit 120 is arranged between the light source 110 and the sample analyzer 130, and is used to split the light emitted by the light source 110 into light beams of different wavelengths. 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.

[0380] 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.

[0381] 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.

[0382] 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 half of the length of the light-splitting unit in the embodiment shown in the figure, Figure 15 or Figure 16 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.

[0383] Figure 15 , Figure 16 andFigure 17 In the illustrated light 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.

[0384] In some other embodiments, as Figure 18 illustrated, the sample analyzer of the utility model adopts the light splitting manner of optical fiber splitting. 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.

[0385] As Figure 18 illustrated, the light 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.

[0386] 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 in this way to be split.

[0387] In some other embodiments, as Figure 19 illustrated, the sample analyzer of the utility model adopts the light splitting manner of grating splitting.

[0388] As Figure 18 illustrated, the light 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 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.

[0389] As Figure 20 illustrated, the overall structure of the optical module 7 of one embodiment of the utility model is shown.

[0390] 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.

[0391] 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.

[0392] 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.

[0393] In some embodiments, the optical module 7 further comprises an expander, which can be the above-mentioned Galilean expander or Kepler expander.

[0394] 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.

[0395] 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.

[0396] In some embodiments, the optical module 7 further comprises, in sequence after the light combiner unit, a mirror 119, a fifth plano-convex lens 120 and a collimator diaphragm 121.

[0397] 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 In some embodiments, the optical module 7 further comprises a light splitting unit, which can comprise the above-mentioned 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

[0398] In some embodiments, the optical module 7 further comprises a light splitting unit, which can split light in the manner of one-to-many fiber bundles as shown in Figure 18 which can comprise 13 dichroic mirrors and corresponding narrowband filters.

[0399] In some embodiments, the optical module 7 further comprises a light splitting unit, which can comprise the above-mentioned concave diffraction grating 160 as shown in Figure 19

[0400] ​​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.

[0401] 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. The biochemical detection device comprises: a sample module for carrying a sample; a sample dispensing module for sucking and discharging the sample; a reagent module for carrying a reagent; a reagent dispensing module for sucking and discharging the reagent; a reaction assembly comprising a 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 split the combined light of the combining unit into monochromatic light of corresponding wave bands for detection by the detection unit, and the combined light can cover the required wave length for biochemical detection. The detection unit is used for optical detection of the monochromatic light. The multiple LED lamps have corresponding lower limit light powers respectively, and the lower limit light power value P1 of the 340 nm LED lamp is the minimum among the lower limit light power values of the multiple LED lamps.

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

3. The sample analyzer of claim 2, wherein, The standard use light power of the 340 nm LED lamp is not less than 1.2 mW.

4. The sample analyzer of claim 2, wherein, The lower limit light power value P1 of the 340 nm LED lamp is 0.06 mW.

5. The sample analyzer of claim 1, wherein, The LED lamp group further comprises a 380 nm LED lamp, and the lower limit light power value P1 of the 380 nm LED lamp is the maximum among the lower limit light power values of the multiple LED lamps.

6. The sample analyzer of claim 1, wherein, At least one LED lamp of the multiple LED lamps is arranged in a straight line with the colorimetric cup at a detection position.

7. The sample analyzer of claim 1, wherein, The wide-spectrum LED lamp is arranged in a straight line with the combining unit and the colorimetric cup at the detection position.

8. The sample analyzer of claim 1, wherein, When optical detection is performed, the minimum light power of the 340 nm monochromatic light received by the detection unit is lower than that of the 405 nm monochromatic light.

9. The sample analyzer of claim 8, wherein, The number of the detection units is the same as that of the monochromatic light split by the light splitting unit, and the detection unit is a photodiode which can receive the monochromatic light split by the light splitting unit.

10. The sample analyzer of claim 9, wherein, The lower limit light power value of the photodiode at a wavelength of 340 nm is 5.28 x 10 -2 μw; and / or The lower limit value of the photoelectric current of the photodiode at the wavelength of 340 nm is 10.98 nA.

11. The sample analyzer of claim 8, 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 of not more than 0.4%. When the detection unit measures the 340 nm wavelength provided by the 340 nm LED lamp and any one of the 450 nm-520 nm wavelengths provided by the wide-spectrum LED lamp, the absorbance linear range is that the maximum absorbance with a relative bias in the range of plus or minus 5% is not less than 4.

0. The stray light is: absorbance A>5 when the detection unit measures the 340nm wavelength provided by the 340nm LED lamp; or The absorbance accuracy is: absorbance value is 0.5Abs±0.025 or 1.0Abs±0.07 when the detection unit measures any one of the 340nm wavelength provided by the 340nm LED lamp and the 600nm-700nm wavelength provided by the wide-spectrum LED lamp.

12. The sample analyzer of claim 8, wherein, The absorbance stability is: the change of absorbance is not more than 0.01 when the detection unit measures any one of the 340nm wavelength provided by the 340nm LED lamp and the 600nm-700nm wavelength provided by the wide-spectrum LED lamp.

13. 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; the collimating device is used for collimating the light beams emitted by each LED lamp to adjust the divergent light emitted by each LED lamp into parallel light.

14. The sample analyzer of claim 13, wherein, The optical path design of the optical module is that the light emitted by each LED lamp has the same optical path distance from the collimating device to the cuvette.

15. The sample analyzer of claim 1, wherein, The composite light formed by the beam combining unit is expanded before irradiating the cuvette; the expanded composite light irradiates the sample in the cuvette to complete the optical detection of the sample.

16. The sample analyzer of claim 15, wherein, An expander is arranged between the beam combining unit and the cuvette, and the diameter of the composite light is expanded by the expander.

17. The sample analyzer of claim 16, wherein, The expander comprises a Galilean expander or a Kepler expander; when the expander comprises a Galilean expander, the Galilean expander comprises a flat-concave lens and a double-convex lens arranged in sequence; when the expander comprises a Kepler expander, the Kepler expander comprises two double-convex lenses.

18. The sample analyzer of claim 17, 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.

19. The sample analyzer of claim 17, 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.

20. 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.

21. The sample analyzer of claim 1, wherein, The cuvette has a light receiving surface and a light emitting surface, and the composite light combined 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; wherein, a front stop and a rear stop are separately arranged at the corresponding positions of the light receiving surface and the light emitting surface; the front stop is used for filtering the stray light irradiating the sample in the cuvette; and the rear stop is used for filtering the emergent light after the composite light passes through the sample; The light splitting unit can sort the monochromatic light of the corresponding waveband from the emergent light filtered by the rear stop for detection by the detection unit.

22. The sample analyzer of claim 1, wherein, A screening unit is arranged between the beam combining unit and the cuvette; the screening unit is used for screening the composite light formed by the beam 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 beam combining unit.

23. The sample analyzer of claim 22, wherein, The overlapping area includes the light emitted by the 340nm LED lamp, the light emitted by the wide-spectrum LED lamp, and the light emitted by the 405nm LED lamp.

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