Blood analyzer

Abstract

The utility model discloses a blood analyzer. The blood analyzer comprises a light source module; the light source module is used for emitting a light source light beam to a sample in the flow chamber to generate a forward light beam; the first light splitting module is used for carrying out light splitting processing on the forward light beam to generate a first scattered light beam and a second scattered light beam, and the direction of the central light path of the first scattered light beam is different from the direction of the central light path of the second scattered light beam; a diaphragm module; the first scattered light beam penetrates through the first optical processing unit of the diaphragm module and is emitted to the low-angle sensing module; the second scattered light beam passes through a second optical processing unit of the diaphragm module and is emitted to the middle angle sensing module; the first interval and the second interval are partially overlapped. Based on the mode, the accuracy of sample detection can be effectively improved.

Description

Technical Field

[0001] The present application relates to the field of detection technology, and in particular to a blood analyzer. Background Art

[0002] In the prior art, by using the light source module in the blood analyzer to emit a light source beam to the sample in the flow chamber, it can stimulate the generation of a corresponding forward scattered beam. By collecting the detection information of the low-angle scattered beam with a low divergence angle and the medium-angle scattered beam with a medium divergence angle in all the forward scattered beams and processing them, it is possible to detect the relevant information of the sample.

[0003] The defect of the prior art is that when a blood analyzer is used to detect platelets, the maximum value of the angle interval of the low-angle scattered light beam collected is usually close to the minimum value of the angle interval of the medium-angle scattered light beam. In this case, if the maximum value of the angle interval of the low-angle scattered light beam is small, it is easy to make the intensity of the platelet-related signal in the detection signal corresponding to the low-angle scattered light beam low, while the intensity of the platelet-related signal in the detection signal corresponding to the medium-angle scattered light beam meets the requirement, or if the maximum value of the angle interval of the low-angle scattered light beam is large, it is easy to make the intensity of the platelet-related signal in the detection signal corresponding to the medium-angle scattered light beam low, while the intensity of the platelet-related signal in the detection signal corresponding to the low-angle scattered light beam meets the requirement. In summary, when the existing blood analyzer is used to detect platelets, it is easy to fail to identify some platelets in the sample due to the insufficient intensity of the platelet-related signal in the detection signal corresponding to the scattered light beam at some angles, or cause the signal intensity of some platelets in the sample to be less than the noise intensity and be submerged. Therefore, the accuracy of sample detection of the existing blood analyzer is low. Utility Model Content

[0004] The main technical problem solved by this application is how to improve the accuracy of sample detection by a blood analyzer.

[0005] In order to solve the above technical problems, the technical solution adopted in the present application is: a blood analyzer, comprising: a light source module; a flow chamber, the light source module is used to emit a light source beam to the sample in the flow chamber to generate a forward beam; a first spectrometer module, the first spectrometer module is used to perform spectroscopic processing on the forward beam to generate a first scattered beam and a second scattered beam, the direction of the central light path of the first scattered beam is different from the direction of the central light path of the second scattered beam; an aperture module; a low-angle sensing module, the first scattered beam passes through the first optical processing unit of the aperture module to be emitted to the low-angle sensing module; a medium-angle sensing module, the second scattered beam passes through the second optical processing unit of the aperture module to be emitted to the medium-angle sensing module; the first interval partially overlaps the second interval; the first interval is the interval of the angle between the beam corresponding to the first scattered beam in all the forward beams and the central light path of the forward beam; the second interval is the interval of the angle between the beam corresponding to the second scattered beam in all the forward beams and the central light path of the forward beam.

[0006] The minimum value of the first interval is smaller than the minimum value of the second interval, and the maximum value of the first interval is smaller than the maximum value of the second interval.

[0007] The first interval is 1-12 degrees, and the second interval is 5-20 degrees.

[0008] Among them, the light source module is used to emit a light source beam to the sample in the flow chamber to generate a lateral beam; the blood analyzer also includes: a second spectroscopic module, the second spectroscopic module is used to perform spectroscopic processing on the lateral beam to generate a third scattered beam and a fluorescent beam, the direction of the central light path of the third scattered beam is different from the direction of the central light path of the fluorescent beam; a high-angle sensing module, the third scattered beam is emitted to the high-angle sensing module; a fluorescent sensing module, the fluorescent beam is emitted to the fluorescent sensing module.

[0009] The third interval is 60-120 degrees; the third interval is the interval of the angle between the central light path of the lateral light beam and the central light path of the forward light beam.

[0010] Among them, the blood analyzer includes DIFF detection channel, BASO detection channel and RBC / PLT / RET detection channel; the DIFF detection channel, BASO detection channel and RBC / PLT / RET detection channel share the sensor module in the blood analyzer, and the low-angle sensor module, medium-angle sensor module, high-angle sensor module and fluorescence sensor module are all sensor modules.

[0011] Among them, the blood analyzer also includes: a front light module, which is located between the light source module and the flow chamber, and is used to focus the light source light beam; and / or a forward collecting component, which is used to collect the forward light beam so that the forward light beam is emitted to the first splitting module.

[0012] The distance between the side of the front light module close to the flow chamber and the sample flow of the flow chamber is in the range of 25-35 mm.

[0013] The front light module includes a collimating lens and a shaping lens; the focal length of the shaping lens ranges from 30 to 45 mm.

[0014] The aperture module further includes a third optical processing unit; the third optical processing unit is located between the flow chamber and the first light splitting module, and the third optical processing unit is located on the central optical path of the forward light beam.

[0015] The beneficial effect of the present application is that, different from the prior art, in the technical solution of the present application, the light source module is used to emit a light source beam to the sample in the flow chamber to generate a forward beam, the first spectroscopic module is used to perform spectroscopic processing on the forward beam to generate a first scattered beam and a second scattered beam, the first scattered beam passes through the first optical processing unit of the aperture module to be emitted to the low-angle sensor module, the second scattered beam passes through the second optical processing unit of the aperture module to be emitted to the medium-angle sensor module, the first interval of the first scattered beam partially overlaps with the second interval of the second scattered beam, based on the above method, the total intensity of the signal corresponding to the first scattered beam received by the low-angle sensor module can be at a similar order of magnitude to the total intensity of the signal corresponding to the second scattered beam received by the medium-angle sensor module, which can The signal corresponding to the first scattered light beam received by the low-angle sensing module retains its characteristic of reflecting the particle diameter, and can also have the characteristic of reflecting the material particle size and density of the signal corresponding to the second scattered light beam received by the medium-angle sensing module, and the total intensity of the signal collected by the low-angle sensing module and the total intensity of the signal collected by the medium-angle sensing module can reach a similar and sufficiently high level, thereby reducing the possibility of platelets not being identified due to insufficient signal intensity, thereby achieving the ability to detect the particle diameter, material particle size and density of platelets based on the low-angle sensing module and the medium-angle sensing module, while also improving the accuracy of the number of platelet particles detected based on the low-angle sensing module and the medium-angle sensing module, thereby improving the accuracy of sample detection by the blood analyzer. BRIEF DESCRIPTION OF THE DRAWINGS

[0016] In order to more clearly illustrate the technical solutions in the embodiments of the present application, the drawings required for use in the description of the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of the present application. For ordinary technicians in this field, other drawings can be obtained based on these drawings without creative work.

[0017] Figure 1 It is a structural schematic diagram of an embodiment of the blood analyzer of the present application;

[0018] Figure 2 This is one of the waveform diagrams of one embodiment of the present application showing the relationship between light intensity and particle diameter;

[0019] Figure 3 This is the second waveform diagram of the light intensity and particle diameter of an embodiment of the present application;

[0020] Figure 4 is a scatter diagram of an embodiment of platelets and red blood cells of the present application;

[0021] Figure 5 It is a scatter diagram of an embodiment of the white blood cells of the present application.

[0022] The figures are marked as: light source module 101, flow chamber 102, first spectroscopic module 103, aperture module 104, first optical processing unit 1041, second optical processing unit 1042, third optical processing unit 1043, low-angle sensing module 105 and medium-angle sensing module 106, second spectroscopic module 107, high-angle sensing module 108, fluorescence sensing module 109, front light module 110, collimating lens 1101, shaping lens 1102, forward collecting component 111, and lateral collecting component 112. DETAILED DESCRIPTION

[0023] The technical solutions in the embodiments of the present application will be clearly and completely described below in conjunction with the drawings in the embodiments of the present application. It will be appreciated that the specific embodiments described herein are only used to explain the present application, rather than to limit the present application. It should also be noted that, for ease of description, only some but not all structures related to the present application are shown in the drawings. Based on the embodiments in the present application, all other embodiments obtained by ordinary technicians in the art without making creative work are within the scope of protection of the present application.

[0024] The terms "first", "second", "third" in this application are only used for descriptive purposes, and cannot be understood as indicating or implying relative importance or implicitly indicating the number of indicated technical features. Thus, the features defined as "first", "second", "third" can expressly or implicitly include at least one of the features. In the description of this application, the meaning of "multiple" is at least two, such as two, three, etc., unless otherwise clearly and specifically defined. In the embodiments of this application, all directional indications (such as up, down, left, right, front, back...) are only used to explain the relative position relationship, movement, etc. between the components under a certain specific posture (as shown in the accompanying drawings). If the specific posture changes, the directional indication also changes accordingly. In addition, the terms "including" and "having" and any of their variations are intended to cover non-exclusive inclusions. For example, a process, method, system, product or device comprising a series of steps or units is not limited to the steps or units listed, but optionally also includes steps or units that are not listed, or optionally also includes other steps or units inherent to these processes, methods, products or devices.

[0025] Reference to "embodiments" herein means that a particular feature, structure, or characteristic described in conjunction with the embodiments may be included in at least one embodiment of the present application. The appearance of the phrase in various locations in the specification does not necessarily refer to the same embodiment, nor is it an independent or alternative embodiment that is mutually exclusive with other embodiments. It is explicitly and implicitly understood by those skilled in the art that the embodiments described herein may be combined with other embodiments.

[0026] This application proposes a blood analyzer, see Figure 1 , Figure 1 FIG. 1 is a schematic diagram of the structure of an embodiment of the blood analyzer of the present application. Figure 1 As shown, the blood analyzer includes a light source module 101 , a flow chamber 102 , a first light splitting module 103 , an aperture module 104 , a low-angle sensing module 105 and a mid-angle sensing module 106 .

[0027] The light source module 101 is used to emit a light source beam to the sample in the flow chamber 102 to generate a forward beam.

[0028] The light source module 101 may be a laser light source for generating a laser with a specific wavelength as a light source beam, and emitting the light source beam to sample particles in the sample flow in the flow chamber 102, thereby scattering and generating a forward light beam.

[0029] It should be noted that the forward light beam may include a forward scattered light beam, which is scattered light generated when the light source light beam is irradiated on the sample particles. A corresponding signal can be generated by photoelectric conversion of the forward scattered light beam, and the detection result of the sample particles can be obtained based on the processing of the information contained in the signal.

[0030] The first light splitting module 103 is used to perform light splitting processing on the forward light beam to generate a first scattered light beam and a second scattered light beam. The direction of the central light path of the first scattered light beam is different from the direction of the central light path of the second scattered light beam.

[0031] Among them, the first splitting module 103 can specifically be a half-reflective half-mirror, which can be used to transmit a part of the forward light beam and reflect another part of the forward light beam, so that the forward scattered light beam in the forward light beam is divided into two parts, which are emitted in different directions respectively.

[0032] In one example, the first light splitting module 103 can specifically make the direction of the light beam reflected by it and the direction of the light beam transmitted by it to be 90 degrees, 70 degrees, 80 degrees, or other angles.

[0033] The first scattered light beam passes through the first optical processing unit 1041 of the aperture module 104 and is emitted toward the low-angle sensing module 105. The second scattered light beam passes through the second optical processing unit 1042 of the aperture module 104 and is emitted toward the middle-angle sensing module 106.

[0034] The first interval partially overlaps with the second interval.

[0035] The first interval is the interval of the angle between the beam corresponding to the first scattered beam in all forward beams and the central light path of the forward beam. The second interval is the interval of the angle between the beam corresponding to the second scattered beam in all forward beams and the central light path of the forward beam.

[0036] Among the forward scattered light beams emitted in different directions, a part of the light beams, after being transmitted, is screened by the first optical processing unit 1041, which can block the light beams except the first scattered light beam, and only transmit the first scattered light beam; at the same time, another part of the light beams, after being reflected, is screened by the second optical processing unit 1042, which can block the light beams except the second scattered light beam, and only transmit the second scattered light beam.

[0037] The first interval is the interval of the angle between the first scattered light beam generated by the light source beam scattered on the sample particles and which has not changed the emission direction, and the central light path of the forward light beam; and the second interval is the interval of the angle between the second scattered light beam generated by the light source beam scattered on the sample particles and which has not changed the emission direction, and the central light path of the forward light beam.

[0038] The first interval of the first scattered light beam received by the low-angle sensing module 105 is a low-angle interval, and the second interval of the second scattered light beam received by the medium-angle sensing module 106 is a medium-angle interval. The low-angle interval partially overlaps with the medium-angle interval. Based on the above method, the characteristics of the particle diameter of the sample can be obtained by analyzing the signal corresponding to the received first scattered light beam, and the characteristics of the material particle size and density of the sample can be obtained by analyzing the signal corresponding to the received second scattered light beam. The low-angle sensing module 105 and the medium-angle sensing module 106 can also be used simultaneously to detect the light beam corresponding to the interval portion overlapping with the above portion in the forward light beam, so that the total intensity of the signal corresponding to all the light beams received by the low-angle sensing module 105 and the total intensity of the signal corresponding to all the light beams received by the medium-angle sensing module 106 can reach a similar and sufficiently high level, thereby reducing the possibility that the platelets in the sample cannot be identified due to insufficient signal intensity generated by the low-angle sensing module 105 or the medium-angle sensing module 106, thereby improving the accuracy of sample detection of platelets based on the blood analyzer.

[0039] Different from the prior art, in the technical solution of the present application, the light source module is used to emit a light source beam to the sample in the flow chamber to generate a forward beam, the first spectroscopic module is used to perform spectroscopic processing on the forward beam to generate a first scattered beam and a second scattered beam, the first scattered beam passes through the first optical processing unit of the aperture module to be emitted to the low-angle sensor module, and the second scattered beam passes through the second optical processing unit of the aperture module to be emitted to the medium-angle sensor module, and the first interval of the first scattered beam partially overlaps with the second interval of the second scattered beam. Based on the above method, the total intensity of the signal corresponding to the first scattered beam received by the low-angle sensor module can be at a similar order of magnitude to the total intensity of the signal corresponding to the second scattered beam received by the medium-angle sensor module, which can make the low-angle sensor module The signal corresponding to the first scattered light beam received by the sensing module retains its characteristic of reflecting the particle diameter, and can also have the characteristic of reflecting the material particle size and density of the signal corresponding to the second scattered light beam received by the medium-angle sensing module, and the total intensity of the signal collected by the low-angle sensing module and the total intensity of the signal collected by the medium-angle sensing module can reach a similar and sufficiently high level, thereby reducing the possibility of platelets not being identified due to insufficient signal intensity, thereby achieving the ability to detect the particle diameter, material particle size and density of platelets based on the low-angle sensing module and the medium-angle sensing module, while also improving the accuracy of the number of platelet particles detected based on the low-angle sensing module and the medium-angle sensing module, thereby improving the accuracy of sample detection of the blood analyzer.

[0040] In one embodiment, the minimum value of the first interval is smaller than the minimum value of the second interval, and the maximum value of the first interval is smaller than the maximum value of the second interval.

[0041] Specifically, the values ​​in the first interval and the second interval are both positive values, the minimum value of the first interval is smaller than any value in the second interval, the maximum value of the first interval is within the second interval, the maximum value of the second interval is larger than any value in the first interval, and the minimum value of the second interval is within the first interval.

[0042] Based on the above method, the first interval and the second interval can have overlapping parts but not completely overlapping, that is, based on the above setting, the first scattered light beam corresponding to the first interval in all the received forward light beams can have the characteristics of reflecting the particle diameter, and the second scattered light beam corresponding to the second interval in all the received forward light beams can have the characteristics of reflecting the particle size and density of the material. At the same time, both the first scattered light beam and the second scattered light beam can be converted into signals with sufficiently high total intensity under the premise of having the above characteristics because the angle intervals covered are wide enough, so as to perform corresponding processing and analysis to obtain the detection results of platelets, thereby reducing the possibility of platelets not being identified due to too low signal intensity and improving the accuracy of sample detection.

[0043] Optionally, the first interval is 1-12 degrees, and the second interval is 5-20 degrees.

[0044] Specifically, for the first scattered light beam received by the low-angle sensor module 105, based on the Mie scattering principle, a light source beam can be emitted to particles of different particle sizes, and the light intensity of the first scattered light beam in different first intervals can be detected to obtain a waveform diagram of the relationship between the corresponding light intensity and the particle diameter, see Figure 2 , Figure 2 is one of the waveform diagrams of an embodiment of the light intensity and particle diameter of the present application, such as Figure 2 As shown, the horizontal axis is the particle diameter of the particles in the sample in the flow chamber, and the vertical axis is the light intensity of the first scattered light beam in the first interval generated by the light source beam irradiating the particles in the sample flow in the flow chamber. Figure 2 In the figure, the first interval corresponding to curve ① is 1-12 degrees, the first interval corresponding to curve ② is 1-10 degrees, the first interval corresponding to curve ③ is 1-8 degrees, and the first interval corresponding to curve ④ is 1-5 degrees.

[0045] Platelets are usually 1-4 microns in size and consist of Figure 2 It can be seen that when the particle size is 1-4 microns, the light intensity of the first scattered light beam in the first interval of 1-12 degrees is higher than the light intensity of the first scattered light beam in other first intervals, and the following table can be obtained through experiments:

[0046] The first interval is 1-5 degrees The first interval is 1-8 degrees The first interval is 1-12 degrees Platelet particle count of sample 1 1984 2081 2162 Platelet particle count of sample 2 2998 3883 3559 Platelet particle count of sample 3 2842 3396 3392 Platelet particle count of sample 4 2261 2519 2678 Platelet particle count of sample 5 2376 2559 2696

[0047] It can be seen from the above table that, through experiments, when the platelet particles in the same sample in the flow chamber are counted based on the first scattered light beams in different first intervals, the number of platelet particles counted based on the first scattered light beam in the first interval of 1-12 degrees is usually the largest. It can be seen that when the number of platelet particles is detected based on the first scattered light beam in the first interval of 1-12 degrees, due to the higher light intensity of the first scattered light beam, the possibility of platelets not being identified due to noise is lower, thereby improving the accuracy of sample detection.

[0048] For the second scattered light beam received by the mid-angle sensor module 106, based on the Mie scattering principle, a light source beam can be emitted to particles of different particle sizes, and the light intensity of the second scattered light beam in different second intervals can be detected to obtain a waveform diagram of the relationship between the corresponding light intensity and the particle diameter, see Figure 3 , Figure 3 This is the second waveform diagram of an embodiment of the light intensity and particle diameter of the present application. Figure 3As shown, the horizontal axis is the particle diameter of the particles in the sample in the flow chamber, and the vertical axis is the light intensity of the second scattered light beam in the second interval generated by the light source beam irradiating the particles in the sample flow in the flow chamber. Figure 3 In the figure, the second interval corresponding to curve ① is 5-20 degrees, the second interval corresponding to curve ② is 6-20 degrees, the second interval corresponding to curve ③ is 8-20 degrees, and the second interval corresponding to curve ④ is 10-20 degrees.

[0049] Platelets are usually 1-4 microns in size and consist of Figure 3 It can be seen that when the particle size is 1-4 microns, the light intensity of the second scattered light beam in the second interval of 5-20 degrees is higher than the light intensities of the second scattered light beams in other second intervals. Therefore, when the number of platelet particles is detected based on the second scattered light beam in the second interval of 5-20 degrees, due to the higher light intensity of the second scattered light beam, the possibility of platelets not being identified due to noise is lower, thereby improving the accuracy of sample detection.

[0050] See also Figure 4 , Figure 4 is a scatter diagram of an embodiment of platelets and red blood cells of the present application, such as Figure 4 As shown in the figure, the vertical axis is the light intensity of the first scattered light beam in the first interval of 1-12 degrees when the particle is identified, and the horizontal axis is the light intensity of the second scattered light beam in the second interval of 5-20 degrees when the particle is identified. By collecting the first scattered light beam and the second scattered light beam, it is possible to construct Figure 4 The two-dimensional scatter plot shown in the figure, based on the setting of the first interval and the second interval, can make a separation gap as shown at the dotted line X appear in the two-dimensional scatter plot, the scatter points of platelets are on the left of the dotted line X, and the scatter points of red blood cells are on the right of the dotted line X. According to the Mie scattering principle, the formation of the separation gap is related to the different contents of platelets and red blood cells, which leads to the difference in their absorption rate and refractive index of light. The morphology of the isolation gap can be affected by reasonably setting the first interval and the second interval.

[0051] like Figure 4 As shown, under the premise of setting the above-mentioned first interval and the second interval, the platelets and red blood cells in the sample can be more clearly separated in the two-dimensional scatter diagram constructed based on the first scattered light beam and the second scattered light beam, that is, the above-mentioned separation gap is more obvious, which is more convenient for distinguishing platelets and red blood cells, so as to improve the accuracy of counting or other types of detection of platelets or red blood cells.

[0052] In one embodiment, if Figure 1 As shown, the light source module 101 is used to emit a light source beam to the sample in the flow chamber 102 to generate a lateral light beam.

[0053] The blood analyzer further includes a second light splitting module 107 , a high-angle sensing module 108 and a fluorescence sensing module 109 .

[0054] The second light splitting module 107 is used to perform light splitting processing on the lateral light beam to generate a third scattered light beam and a fluorescent light beam. The direction of the central light path of the third scattered light beam is different from the direction of the central light path of the fluorescent light beam.

[0055] The third scattered light beam is emitted toward the high-angle sensing module 108 .

[0056] The fluorescent light beam is emitted toward the fluorescent sensing module 109 .

[0057] Specifically, the second light splitting module 107 can be a dichroic mirror, which can be used to reflect the third scattered beam of the lateral light beam and transmit the fluorescent beam of the lateral light beam, so that the third scattered beam and the fluorescent beam in the lateral light beam are emitted in different directions respectively.

[0058] In one example, the second light splitting module 107 can specifically make the direction of the light beam reflected by it and the direction of the light beam transmitted by it to be 90 degrees, 70 degrees, 80 degrees, or other angles.

[0059] Based on the analysis and processing of the signal generated by the first received scattered light beam, low-angle information can be obtained; based on the analysis and processing of the signal generated by the second received scattered light beam, medium-angle information can be obtained; based on the analysis and processing of the signal generated by the third received scattered light beam, high-angle information can be obtained; based on the analysis and processing of the signal generated by the received fluorescent light beam, fluorescent information can be obtained.

[0060] By combining at least two of the low-angle information, medium-angle information, high-angle information and fluorescence information, the above-mentioned sample detection of platelets, or sample detection of other types of cells, or sample detection of other types of cells can be achieved, which is not limited here.

[0061] Based on the above method, an optical system can be constructed to simultaneously obtain low-angle information, medium-angle information, high-angle information and fluorescence information of the sample, thereby improving the applicability and efficiency of sample detection.

[0062] Optionally, the third interval is 60-120 degrees.

[0063] The third interval is the interval of the angle between the central light path of the side light beam and the central light path of the forward light beam.

[0064] Specifically, the angle interval between the lateral light beam generated by scattering and / or excitation of the light source beam on the sample particles and which has not changed its emission direction and the central light path of the forward light beam is the third interval.

[0065] By making the third interval 60-120 degrees, the lateral light beam can include a third scattered light beam generated by the light source beam being scattered on the sample and a fluorescent light beam generated by excitation, thereby improving the application range and efficiency of sample detection of the optical system.

[0066] Optionally, the blood analyzer includes a DIFF detection channel, a BASO detection channel and a RBC / PLT / RET detection channel.

[0067] The DIFF detection channel, the BASO detection channel and the RBC / PLT / RET detection channel share the sensor module in the blood analyzer, and the low-angle sensor module 105, the middle-angle sensor module 106, the high-angle sensor module 108 and the fluorescence sensor module 109 are all sensor modules.

[0068] Specifically, the first interval may be 1-12 degrees, and the second interval may be 5-20 degrees.

[0069] When using the RBC / PLT / RET detection channel, first, you can choose not to pre-dye the sample in the flow chamber with RET dye, and at this time, based on the detection of the first scattered light beam and the second scattered light beam, you can distinguish and count the platelets (PLT) and red blood cells (RBC) in the sample. Second, you can also choose to pre-dye the sample in the flow chamber with RET dye, and at this time, based on the detection of the first scattered light beam, the second scattered light beam, the third scattered light beam and the fluorescent light beam, you can detect reticulocytes (RET).

[0070] When the first interval is 1-12 degrees and the second interval is 5-20 degrees, the first scattered light beam, the second scattered light beam, the third scattered light beam and the fluorescent light beam can all meet the requirements of RET detection.

[0071] When using the DIFF detection channel, the sample in the flow chamber needs to be pre-dyed with DIFF dye, and then the DIFF detection is mainly realized based on the detection of the third scattered light beam and the fluorescent light beam, and the range of the angles corresponding to the first scattered light beam and the second scattered light beam is not required to be high.

[0072] When the first interval is 1-12 degrees and the second interval is 5-20 degrees, both the third scattered light beam and the fluorescent light beam can meet the requirements of RET detection.

[0073] When using the BASO detection channel, BASO (basophil) cells are usually detected, and the detection of BASO cells is carried out by shrinking white blood cells other than BASO cells, thereby making BASO cells different in volume from other types of white blood cells. Therefore, the information on the particle size contained in the first scattered light beam is more important for the detection of BASO cells, that is, BASO detection is mainly achieved based on the detection of the first scattered light beam and the fluorescent light beam.

[0074] See also Figure 5 , Figure 5 is a scatter diagram of an embodiment of the white blood cells of the present application, such as Figure 5 As shown, the horizontal axis is the light intensity SFL of the fluorescent beam, and the vertical axis is the light intensity of the first scattered beam in the corresponding first interval. From left to right, they are respectively the white blood cell scatter plot between the light intensity of the first scattered beam in the first interval of 1-5 degrees and the light intensity of the fluorescent beam, the white blood cell scatter plot between the light intensity of the first scattered beam in the first interval of 1-8 degrees and the light intensity of the fluorescent beam, and the white blood cell scatter plot between the light intensity of the first scattered beam in the first interval of 1-12 degrees and the light intensity of the fluorescent beam.

[0075] Depend on Figure 5 It can be seen that the area Y( Figure 5 The cells in the circled area are BASO cells. Only in the leukocyte scatter plot corresponding to the first interval of 1-12 degrees, BASO cells can be effectively distinguished from other leukocytes. Figure 5 In all figures except the white blood cell scatter plot corresponding to the first interval of 1-12 degrees, BASO cells cannot be distinguished from other white blood cells and there is no obvious boundary. Therefore, when the first interval is 1-12 degrees and the second interval is 5-20 degrees, the first scattered light beam and the fluorescent light beam can meet the requirements of RET detection.

[0076] In summary, based on the above method, the optical system constructed from the light source module 101 to each sensor module can be used to perform corresponding types of sample detection when using the DIFF detection channel, the BASO detection channel and the RBC / PLT / RET detection channel respectively, and through the reasonable setting of the first interval and the second interval, the needs of the three detection channels can be met at the same time, thereby improving the applicability and reliability of the blood analyzer.

[0077] Optionally, the blood analyzer may further include a lateral collecting component 112 , which is used to collect the lateral light beams so that the lateral light beams are emitted toward the second light splitting module 107 .

[0078] Specifically, the lateral collecting component 112 may be a focusing lens or other types of optical devices with focusing capabilities, which is not limited here.

[0079] In one embodiment, if Figure 1 As shown, the blood analyzer further includes a front light module 110. The front light module 110 is located between the light source module 101 and the flow chamber 102. The front light module 110 is used to focus the light beam of the light source.

[0080] and / or,

[0081] The blood analyzer further includes a forward collecting component 111 , which is used to collect the forward light beam so that the forward light beam is emitted toward the first light splitting module 103 .

[0082] Specifically, the forward collecting component 111 can be a focusing lens or other types of optical devices with focusing capabilities, which is not limited here.

[0083] The front light module 110 can be specifically used to perform corresponding optical processing on the light source beam to form a more suitable light spot irradiated on the sample flow in the flow chamber.

[0084] Based on the above method, the reliability of sample detection can be improved.

[0085] Optionally, the distance between the side of the front light module 110 close to the flow chamber 102 and the sample flow of the flow chamber 102 is in the range of 25-35 mm.

[0086] Specifically, the distance between the front light module 110 and the sample flow of the flow chamber 102 can be 26 mm, that is, the working distance of the front light module 110 can be 26 mm, which can improve the rationality of the light intensity distribution of the light spot irradiated on the sample flow of the flow chamber, is more suitable for sample detection of small particles such as platelets, and is conducive to reducing the overall volume of the blood analyzer.

[0087] Alternatively, if Figure 1 As shown, the front light module 110 includes a collimating lens 1101 and a shaping lens 1102 .

[0088] The focal length of the shaping lens 1102 is in the range of 30-45 mm.

[0089] Specifically, by making the focal length of the shaping lens 1102 in the range of 30-45 mm, the width of the light spot irradiated on the sample flow in the flow chamber can be made less than or equal to 10 microns in the direction of the sample flow, thereby improving the rationality of the light intensity distribution of the light spot irradiated on the sample flow in the flow chamber, being more suitable for sample detection of small particles such as platelets, and being beneficial to reducing the overall volume of the blood analyzer.

[0090] Optionally, the numerical aperture of the forward collection assembly 111 is greater than 0.4.

[0091] Specifically, by making the numerical aperture of the forward collection component 111 greater than 0.4, it can be ensured that the mid-angle sensing module 106 can collect all the second scattered light beams in the required second interval, thereby improving the reliability of sample detection.

[0092] Alternatively, if Figure 1 As shown, the aperture module 104 also includes a third optical processing unit 1043 .

[0093] The third optical processing unit 1043 is located between the flow chamber 102 and the first light splitting module 103 , and the third optical processing unit 1043 is located on the central optical path of the forward light beam.

[0094] Specifically, the third optical processing unit 1043 can be a straightening aperture, which can be used to absorb the scattered light beam located on the central light path of the forward light beam, thereby preventing the scattered light beam from being reflected back to the light source module 101 along the original path in the subsequent pipeline, thereby reducing the possibility of damage to the light source module 101 and improving the reliability of the blood analyzer.

[0095] The above description is only an implementation method of the present application, and does not limit the patent scope of the present application. Any equivalent structure or equivalent process transformation made using the contents of the present application specification and drawings, or directly or indirectly used in other related technical fields, are also included in the patent protection scope of the present application.

Claims

1. A blood analyzer, characterized in that: include: Light source module; A flow chamber, wherein the light source module is used to emit a light source beam to the sample in the flow chamber to generate a forward light beam; a first light splitting module, the first light splitting module being used to perform light splitting processing on the forward light beam to generate a first scattered light beam and a second scattered light beam, wherein the direction of the central light path of the first scattered light beam is different from the direction of the central light path of the second scattered light beam; Aperture module; A low-angle sensing module, wherein the first scattered light beam passes through a first optical processing unit of the aperture module and is emitted toward the low-angle sensing module; A middle angle sensing module, wherein the second scattered light beam passes through the second optical processing unit of the aperture module and is emitted toward the middle angle sensing module; Wherein, the first interval partially overlaps with the second interval; The first interval is the interval of the angle between the light beam corresponding to the first scattered light beam in all the forward light beams and the central light path of the forward light beam; The second interval is an interval of angles between the light beam corresponding to the second scattered light beam in all forward light beams and the central light path of the forward light beam.

2. The blood analyzer according to claim 1, characterized in that: The minimum value of the first interval is smaller than the minimum value of the second interval, and the maximum value of the first interval is smaller than the maximum value of the second interval.

3. The blood analyzer according to claim 2, characterized in that: The first interval is 1-12 degrees, and the second interval is 5-20 degrees.

4. The blood analyzer according to any one of claims 1 to 3, characterized in that: The light source module is used to emit a light source beam to the sample in the flow chamber to generate a lateral light beam; The blood analyzer also includes: a second light splitting module, the second light splitting module being used to perform light splitting processing on the lateral light beam to generate a third scattered light beam and a fluorescent light beam, wherein the direction of the central light path of the third scattered light beam is different from the direction of the central light path of the fluorescent light beam; A high-angle sensing module, the third scattered light beam is emitted toward the high-angle sensing module; A fluorescence sensing module, the fluorescence light beam is emitted toward the fluorescence sensing module.

5. The blood analyzer according to claim 4, characterized in that: The third interval is 60-120 degrees; The third interval is the interval of the angle between the central light path of the side light beam and the central light path of the forward light beam.

6. The blood analyzer according to claim 4, characterized in that: The blood analyzer includes a DIFF detection channel, a BASO detection channel and an RBC / PLT / RET detection channel; The DIFF detection channel, the BASO detection channel and the RBC / PLT / RET detection channel share the sensor module in the blood analyzer, and the low-angle sensor module, the middle-angle sensor module, the high-angle sensor module and the fluorescence sensor module are all the sensor modules.

7. The blood analyzer according to any one of claims 1 to 3, characterized in that: The blood analyzer also includes: A front light module, the front light module is located between the light source module and the flow chamber, and the front light module is used to focus the light beam of the light source; And / or, a forward collecting component, wherein the forward collecting component is used to collect the forward light beam so that the forward light beam is emitted to the first light splitting module.

8. The blood analyzer according to claim 7, characterized in that: The distance between the side of the front light module close to the flow chamber and the sample flow of the flow chamber is in the range of 25-35 mm.

9. The blood analyzer according to claim 7, characterized in that: The front light module includes a collimating lens and a shaping lens; The focal length of the plastic surgery lens is in the range of 30-45 mm.

10. The blood analyzer according to any one of claims 1 to 3, characterized in that: The aperture module further includes a third optical processing unit; The third optical processing unit is located between the flow chamber and the first light splitting module, and the third optical processing unit is located on the central optical path of the forward light beam.

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