Optical system of full-automatic five-classification blood analyzer

Abstract

The utility model discloses a full-automatic five-classification blood analyzer optical system which comprises a fixed seat fixedly connected with the upper side surface of a base, a flow chamber is arranged on the upper side surface of the fixed seat, an irradiation box body is arranged on one side of the flow chamber and fixedly connected with the base, and the irradiation box body is arranged on the other side of the flow chamber. And a front light assembly is arranged in the irradiation box body. According to the utility model, through the circular light barrier arranged in the center of the diaphragm I, direct laser light spots and small-angle scattered light signals can be shielded, the signal-to-noise ratio is improved, the sensitivity of a low-angle scattered light receiving assembly to left-right position deviation is reduced, the overall optical stability is improved, and the accuracy of a detection result is guaranteed.

Description

Technical Field

[0001] This utility model relates to the technical field of blood testing instruments, and in particular to an optical system for a fully automatic five-part differential blood analyzer. Background Technology

[0002] Blood analyzers, also known as blood cell analyzers, hematology analyzers, or blood cell counters, are among the most widely used instruments in clinical testing at hospitals at all levels. They assist doctors in making more accurate judgments and analyses of patients' disease characteristics. With the development of computer technology in recent years, blood cell analysis techniques have shifted from trichotomy to quinchotomy, and from two-dimensional space to three-dimensional space, resulting in various blood analyzers based on sheath flow technology.

[0003] Existing patent publication number CN212658587U discloses an optical system, which includes a front light device, a flow chamber device, and a light detection device arranged sequentially. The front light device is used to provide a collimated and shaped laser beam. The flow chamber device is the area where the detected blood cells are irradiated by the laser beam. The light detection device includes a low-to-medium angle detection device and a high-angle detection device. The high-angle detection device includes a high-angle aperture, a high-angle converging lens, and a high-angle photodetector. The low-to-medium angle detection device includes a low-angle photodetector. This utility model also provides a blood cell counter including such an optical system. This optical system has a simple structure, is easy to install and maintain, and has a good ability to identify and detect lymphocytes, monocytes, neutrophils, basophils, and eosinophils.

[0004] Existing high-angle detection devices are composed of a large number of components and require repeated adjustments during use. This results in complex assembly and adjustment of existing high-angle detection devices, poor consistency of detection signals, and affects the detection effect. Utility Model Content

[0005] The purpose of this section is to outline some aspects of embodiments of the present invention and to briefly describe some preferred embodiments. Simplifications or omissions may be made in this section, as well as in the abstract and title of this application, to avoid obscuring the purpose of these documents; however, such simplifications or omissions should not be construed as limiting the scope of the present invention.

[0006] In view of the problems existing in the optical system of the current fully automatic five-part differential blood analyzer, this utility model is proposed.

[0007] Therefore, the purpose of this utility model is to provide an optical system for a fully automatic five-part differential blood analyzer, which aims to solve the problem that "existing high-angle detection devices are composed of a large number of components and require repeated adjustments during use, resulting in complex assembly and adjustment of existing high-angle detection devices, poor consistency of detection signals, and affecting detection results".

[0008] To solve the above-mentioned technical problems, this utility model provides the following technical solution:

[0009] An optical system for a fully automated five-part differential blood analyzer includes: a main unit, an analysis unit, and a receiving unit, characterized in that:

[0010] The main unit includes a base;

[0011] The analysis unit includes a fixed base that is fixedly connected to the upper surface of the base, and a flow chamber is provided on the upper surface of the fixed base. An irradiation box is provided on one side of the flow chamber and is fixedly connected to the base. A front light component is provided inside the irradiation box.

[0012] The receiving unit includes a mounting base that is slidably connected to the base, and a connecting seat is slidably connected to the upper surface of the mounting base. A first receiving component, a second receiving component, and a third receiving component are provided on one side of the connecting seat.

[0013] As a preferred embodiment of the optical system of the fully automatic five-part differential blood analyzer described in this utility model, the front light assembly includes a laser installed inside the irradiation chamber, and a lens 1, a lens 2 and a lens 3 are provided on one side of the laser. The lens 1, lens 2 and lens 3 are all concentrically arranged with the laser's light output axis as the center.

[0014] As a preferred embodiment of the optical system of the fully automatic five-part differential blood analyzer described in this utility model, the first receiving component includes a structural base one disposed on one side surface of the connecting seat, and a photocell one disposed inside the structural base one. An aperture one is disposed on one side surface of the structural base one, the aperture one is circular in shape, and a circular light-blocking plate is disposed in the center of the aperture one.

[0015] As a preferred embodiment of the optical system of the fully automatic five-part differential blood analyzer described in this utility model, the second receiving component includes a second photocell, a second structural base, and a second aperture. The second photocell is disposed inside the second structural base, and the second aperture is disposed on one side surface of the second structural base.

[0016] As a preferred embodiment of the optical system of the fully automatic five-part differential blood analyzer described in this utility model, the third receiving component includes a structural seat three disposed on one side surface of a structural seat three, a photocell three disposed inside the structural seat three, and an aperture three disposed on one side surface of the structural seat three.

[0017] As a preferred embodiment of the optical system of the fully automatic five-part differential blood analyzer described in this utility model, the laser is a red laser diode, the first lens is a plano-convex or biconvex aspherical lens, and the second and third lenses are both cylindrical lenses or a combination of lenses.

[0018] The beneficial effects of this utility model are:

[0019] 1. A laser is emitted by a laser. After collimation and optimization by lens one, the laser spot is shaped by lenses two and three. The shaped laser irradiates a flow chamber and an aperture to form a direct spot of a specified size, which can completely envelop a single blood cell. In the flow chamber, sheath flow technology allows cells to pass through the laser-irradiated area one by one. Each cell generates scattered light signals in various directions as it passes through the irradiated area. The generated scattered light signals are collected by the receiving unit. The first, second, and third receiving components collect scattered light signals in three ranges: low angle, medium angle, and high angle, forming a three-dimensional coordinate system. Each point in the coordinate system is composed of pulse signals generated by cells passing through the laser-irradiated area. The number of sample cells in each test constitutes the total number in the three-dimensional coordinate system. A circular light-blocking plate set in the center of aperture one can block the direct laser spot and small-angle scattered light signals, improve the signal-to-noise ratio, and reduce the sensitivity of the low-angle scattered light receiving component to left and right position shifts, thereby improving the overall optical stability and ensuring the accuracy of the detection results.

[0020] 2. By setting up structural base one, structural base two and structural base three, the position can be adjusted independently, which reduces the difficulty of assembly and adjustment, reduces the overall size of the optical system and improves practicality. Attached Figure Description

[0021] To more clearly illustrate the technical solutions of the embodiments of this utility model, the drawings used in the description of the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this utility model. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort. Among them:

[0022] Figure 1 The diagram shows a three-dimensional structural schematic of the optical system of a fully automatic five-part differential blood analyzer proposed in this utility model.

[0023] Figure 2 This is a schematic diagram of the three-dimensional structure of the analysis unit;

[0024] Figure 3 This is a schematic diagram of the three-dimensional structure of the receiving unit;

[0025] Figure 4 This is a schematic diagram of the three-dimensional structure of aperture one.

[0026] In the diagram: 100, Main unit; 101, Base; 200, Analysis unit; 201, Fixing seat; 202, Flow chamber; 203, Irradiation box; 204, Front light assembly; 204a, Laser; 204b, Lens 1; 204c, Lens 2; 204d, Lens 3; 300, Receiving unit; 301, Mounting seat; 302, Connecting seat; 303, First receiving assembly; 303a, Photovoltaic cell 1; 303b, Structural seat 1; 303c, Aperture 1; 303d, Circular light-blocking plate; 304, Second receiving assembly; 304a, Photovoltaic cell 2; 304b, Structural seat 2; 304c, Aperture 2; 305, Third receiving assembly; 305a, Photovoltaic cell 3; 305b, Structural seat 3; 305c, Aperture 3. Detailed Implementation

[0027] To make the above-mentioned objectives, features and advantages of this utility model more apparent and understandable, the specific embodiments of this utility model will be described in detail below with reference to the accompanying drawings.

[0028] Many specific details are set forth in the following description in order to provide a full understanding of the present invention. However, the present invention may also be implemented in other ways different from those described herein. Those skilled in the art can make similar extensions without departing from the spirit of the present invention. Therefore, the present invention is not limited to the specific embodiments disclosed below.

[0029] Secondly, the term "an embodiment" or "embodiment" as used herein refers to a specific feature, structure, or characteristic that may be included in at least one implementation of the present invention. The phrase "in one embodiment" appearing in different places in this specification does not necessarily refer to the same embodiment, nor is it a single or selective embodiment that excludes other embodiments.

[0030] Secondly, this utility model is described in detail with reference to the schematic diagrams. When describing the embodiments of this utility model, for ease of explanation, the cross-sectional views illustrating the device structure may be partially enlarged, not adhering to the usual scale. Furthermore, the schematic diagrams are merely examples and should not limit the scope of protection of this utility model. In addition, actual manufacturing should include the three-dimensional spatial dimensions of length, width, and depth.

[0031] Reference Figure 1-4. This utility model provides an optical system for a fully automated five-part differential blood analyzer, comprising a main unit 100, an analysis unit 200, and a receiving unit 300, characterized in that:

[0032] The main unit 100 includes a base 101, which supports the main body of the equipment;

[0033] The analysis unit 200 includes a fixed base 201 fixedly connected to the upper surface of the base 101, and a flow chamber 202 is provided on the upper surface of the fixed base 201. An irradiation box 203 is provided on one side of the flow chamber 202, and the irradiation box 203 is fixedly connected to the base 101. A front light assembly 204 is provided inside the irradiation box 203. The flow chamber 202 allows cells to pass through one by one in sequence. The laser beam irradiates the individual cells that pass through in sequence, generating a scattered light signal. The flow chamber 202 can be selected from Corning 7980 to ensure laser transmittance.

[0034] The receiving unit 300 includes a mounting base 301 that is slidably connected to the base 101 and can slide left and right. A connecting base 302 is slidably connected to the upper surface of the mounting base 301 and can slide back and forth. A first receiving component 303, a second receiving component 304 and a third receiving component 305 are provided on one side of the connecting base 302.

[0035] The front light assembly 204 includes a laser 204a installed inside the irradiation box 203, and a lens 204b, a lens 204c, and a lens 204d are provided on one side of the laser 204a. The lens 204b, lens 204c, and lens 204d are all concentrically arranged with the laser 204a's output optical axis as the center to ensure the stability of the laser beam direction.

[0036] Furthermore, the first receiving component 303 includes a structural base 303b disposed on one side surface of the connecting base 302, and a photocell 303a disposed inside the structural base 303b. An aperture 303c is disposed on one side surface of the structural base 303b. The aperture 303c is circular in shape, and a circular light-blocking plate 303d is disposed in the center of the aperture 303c. This plate is used to block direct light spots and small-angle scattered light signals. The receiving angle range is set to 2 to 5°. The aperture 303c is disposed on the surface of the photocell 303a and is as close as possible to reduce the influence of direct light and stray light. This component is used to receive low-angle scattered light signals, which can reflect the size of the cell to be detected.

[0037] Furthermore, the second receiving component 304 includes a second photovoltaic cell 304a, a second structural base 304b, and a second aperture 304c. The second photovoltaic cell 304a is disposed inside the second structural base 304b, and the second aperture 304c is disposed on one side surface of the second structural base 304b. The second aperture 304c is disposed on the surface of the second photovoltaic cell 304a and is as close as possible to reduce the influence of direct light and stray light. The second structural base 304b and the first structural base 303b are simplified into the same structural base, saving space and reducing the overall system volume. The second aperture 304c and the first aperture 303c are merged into one aperture surface, simplifying the assembly process and reducing stray light interference. The second aperture 304c has an arc-shaped design and the receiving angle is set to 5-25°. This component is used to receive mid-angle scattered light signals, which can reflect the internal complexity of cells.

[0038] Furthermore, the third receiving component 305 includes a third structural base 305b disposed on one side surface of the first structural base 303b. A third photovoltaic cell 305a is disposed inside the third structural base 305b. An aperture 305c is disposed on one side surface of the third structural base 305b. The aperture 305c is disposed on the surface of the third photovoltaic cell 305a and is as close as possible to reduce the influence of direct light and stray light. An aperture 2 304c is disposed on the surface of the second photovoltaic cell 304a and is as close as possible to reduce the influence of direct light and stray light. The aperture 305c has a square design and the receiving angle is set to 30-55°. This component is used to receive high-angle scattered light signals, which can reflect the particle size inside the cell.

[0039] Furthermore, laser 204a is a red laser diode with a long service life and high stability. Lens 204b is a plano-convex or biconvex aspherical lens used to collimate the laser beam. Lens 204c and lens 204d are both cylindrical lenses or combinations of lenses used to shape the laser beam.

[0040] During use, laser 204a emits a laser beam. After collimation and optimization by lens 204b, the laser beam is shaped by lenses 204c and 204d. The shaped laser beam irradiates the flow chamber 202 and aperture 303c, forming a designated direct beam size that can completely envelop a single blood cell. In the flow chamber 202, the sheath flow technology allows cells to pass through the laser-irradiated area of ​​the flow chamber 202 one by one. Each cell generates scattered light signals in various directions when passing through the irradiated area. The generated scattered light signals are collected by the receiving unit 300. The first receiving component 303, the second receiving component 304, and the third receiving component 305 collect scattered light signals in three ranges: low angle, medium angle, and high angle, forming a three-dimensional coordinate system. Each point in the coordinate system is composed of pulse signals generated by the cells passing through the laser-irradiated area. The number of sample cells in each test constitutes the total number in the three-dimensional coordinate system.

[0041] It should be noted that the above embodiments are only used to illustrate the technical solution of this utility model and are not intended to limit it. Although this utility model has been described in detail with reference to preferred embodiments, those skilled in the art should understand that modifications or equivalent substitutions can be made to the technical solution of this utility model without departing from the spirit and scope of the technical solution of this utility model, and all such modifications or substitutions should be covered within the scope of the claims of this utility model.

Claims

1. An automatic five-classification blood analyzer optical system, comprising a main unit (100), an analysis unit (200) and a receiving unit (300), characterized in that: the main unit (100) comprises a base (101); the analysis unit (200) comprises a fixed seat (201) fixedly connected with the upper surface of the base (101), and the upper surface of the fixed seat (201) is provided with a flow chamber (202), one side of the flow chamber (202) is provided with an irradiation box (203), and the irradiation box (203) is fixedly connected with the base (101), and the inside of the irradiation box (203) is provided with a front light assembly (204); the receiving unit (300) comprises a mounting seat (301) slidingly connected with the base (101), and the upper surface of the mounting seat (301) is slidingly connected with a connecting seat (302), one side of the connecting seat (302) is provided with a first receiving assembly (303), a second receiving assembly (304) and a third receiving assembly (305).

2. The optical system of a fully automatic five-classification hematology analyzer according to claim 1, characterized in that: The front light assembly (204) comprises a laser (204a) mounted in the irradiation box (203), and one side of the laser (204a) is provided with a lens one (204b), a lens two (204c) and a lens three (204d), the lens one (204b), the lens two (204c) and the lens three (204d) are concentrically arranged with the laser (204a) light axis as the center.

3. The optical system of a fully automatic five-partition hematology analyzer according to claim 2, characterized in that: The first receiving assembly (303) comprises a structure seat one (303b) provided on one side surface of the connecting seat (302), and the inside of the structure seat one (303b) is provided with a photocell one (303a), one side surface of the structure seat one (303b) is provided with a diaphragm one (303c), the diaphragm one (303c) is circular in shape, and the center of the diaphragm one (303c) is provided with a circular light shield (303d).

4. The optical system of a fully automatic five-classification hematology analyzer according to claim 3, characterized in that: The second receiving assembly (304) comprises a photocell two (304a), a structure seat two (304b) and a diaphragm two (304c), the inside of the structure seat two (304b) is provided with the photocell two (304a), and one side surface of the structure seat two (304b) is provided with the diaphragm two (304c).

5. The optical system of a fully automatic five-partition hematology analyzer according to claim 4, characterized in that: The third receiving assembly (305) comprises a structure seat three (305b) provided on one side surface of the structure seat one (303b), the inside of the structure seat three (305b) is provided with a photocell three (305a), and one side surface of the structure seat three (305b) is provided with a diaphragm three (305c).

6. The optical system of a fully automatic five-partition hematology analyzer according to claim 5, characterized in that: The laser (204a) is a red light laser diode, the lens one (204b) is a plano-convex or double-convex aspheric lens, and the lens two (204c) and the lens three (204d) are both cylindrical lenses or combined lenses.

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