CN217717432U - Optical detection component and optical detection system - Google Patents

Abstract

The utility model provides an optical detection component and an optical detection system, which belong to the field of optical detection equipment. an optical detection assembly, comprising: a light detector for detecting light signals; a light collection unit for collecting light signals and projecting the collected light signals on the light detector; a blocking diaphragm, arranged before the light collection unit; The aperture diaphragm is arranged between the light collection unit and the light detector; wherein, the light collection unit is an aspherical lens. An optical detection system, including: a flow chamber for the detected blood cells to pass through; a front light assembly for generating a laser beam and focusing it on the flow chamber to form forward scattered light, side scattered light and side fluorescence; side detection a component for detecting side scattered light and side fluorescence; and a forward detection component, which is the above-mentioned optical detection component, for detecting forward scattered light. The utility model can avoid the problems of spherical aberration and astigmatism, and improve the detection accuracy of blood cells.

Description

An optical detection component and an optical detection system

technical field

The utility model belongs to the field of optical detection equipment, in particular to an optical detection component and an optical detection system.

Background technique

In existing hematology analyzers, the laser light scattering fluorescence staining method is usually used to classify and count the cells. It uses a laser as a light source, collimates and focuses the lens to irradiate the fluorescently labeled cells in the flow chamber to generate forward scattered light, side scattered light and side fluorescence.

Forward scattered light reflects the size of the cell, forward scattered light reflects the complexity of the cell, and side fluorescence reflects the content of nucleic acid in the cell. Nucleic acid includes deoxyribonucleic acid and ribonucleic acid. The scattered light is converted into an electrical signal by the optical detection component, and the analysis of the electrical signal can realize the classification of blood cells. At present, most optical detection components use spherical lenses or spherical lens groups to collect and converge forward scattered light signals, and then detect them. Due to its own structure, the spherical lens is prone to problems such as spherical aberration and astigmatism when converging forward scattered light.

Utility model content

In view of the above-mentioned shortcomings of the prior art, the purpose of this utility model is to provide an optical detection component and an optical detection system, which are used to solve the problems of spherical aberration and astigmatism in the optical detection component in the prior art.

In order to achieve the above purpose and other related purposes, the utility model provides an optical detection component, including:

a light detector for detecting light signals;

a light collecting unit for collecting light signals and projecting the collected light signals onto the light detector;

a straight blocking diaphragm, arranged before the light collection unit, for screening the light signal entering the light collection unit;

A small aperture diaphragm, arranged between the light collection unit and the photodetector, is used to filter the light signal projected by the light collection unit on the photodetector;

Wherein, the light collecting unit is an aspheric lens.

Optionally, the light collecting unit has an incident surface and an outgoing surface, the incident surface is a plane or a convex surface, and the outgoing surface is a convex surface.

Optionally, the surface reflectance of the incident surface is ≤0.1%.

Optionally, the surface reflectance of the incident surface is ≤0.05%.

Optionally, the focal length of the light collection unit is 5mm-13mm.

Optionally, the focal length of the light collection unit is 7mm-11mm.

Optionally, the clear aperture of the light collection unit is >3mm, and the numerical aperture of the light collection unit is >0.2.

Optionally, the clear aperture of the light collection unit is >5mm, and the numerical aperture of the light collection unit is >0.25.

Optionally, the light collecting unit is an even-order aspheric lens.

Optionally, the distance between the light collecting unit and the straight blocking diaphragm is <1mm.

Optionally, the straight blocking diaphragm screens light signals whose incident angles are between an upper limit and a lower limit to enter the light collection unit, the lower limit being 1°, and the upper limit ≥ 5°.

Optionally, the upper limit ≥ 9°.

Optionally, the aperture diaphragm has a first through hole and a second through hole, the first through hole and the second through hole are elongated, the first through hole and the second through hole Two through holes intersect each other, the length of the first through hole is ≥3 mm, and the width of the first through hole is ≤1.5 mm.

Optionally, the length of the first through hole is ≥5 mm, and the width of the first through hole is ≤1 mm.

Optionally, the aspheric lens is one

The utility model also provides an optical detection system, comprising:

a flow chamber for the passage of blood cells to be tested;

The front light assembly is used to generate a laser beam and focus the laser beam on the flow chamber along a first direction, form forward scattered light along the first direction, and form side scattered light and side fluorescence along the second direction , the first direction intersects the second direction;

a side detection component for detecting the side scattered light and the side fluorescence; and

The forward detection component is the above-mentioned optical detection component, which is used to detect the forward scattered light.

As mentioned above, an optical detection component and an optical detection system provided by the utility model have the following beneficial effects: since the light collection unit is provided, and the light collection unit is an aspheric lens, compared with the spherical lens, the aspheric lens can avoid The spherical lens converges the spherical aberration and astigmatism caused by the scattered light to improve the detection accuracy of blood cells. The straight blocking diaphragm is arranged before the light collection unit, and can filter the light signal entering the light collection unit, reduce the direct light, and prevent the direct light from entering the light detector to cause signal saturation. At the same time, the small aperture diaphragm is arranged between the light collection unit and the light detector, which can filter the light signal projected by the light collection unit on the light detector, and avoid the interference of stray light on the light detector , to improve the detection quality of the photodetector.

Description of drawings

Fig. 1 is a schematic structural diagram of an optical detection system in an embodiment of the present invention.

Fig. 2 is a schematic structural diagram of a straight stop diaphragm in an embodiment of the present invention.

Fig. 3 is the first structural diagram of the light collection unit in the embodiment of the present invention.

Fig. 4 is the second structural diagram of the light collection unit in the embodiment of the present invention.

Fig. 5 is a schematic structural diagram of the aperture diaphragm in the embodiment of the present invention.

Explanation of reference signs:

Laser 1, collimating mirror 2, shaping lens group 3, straight stop diaphragm 4, light collection unit 5, pinhole diaphragm 6, light detector 7, side collection lens 8, dichromatic mirror 9, side scatter detection Component 10, side fluorescence detection component 11, front light component 101, light isolation component 102, flow chamber 103, forward detection component 104 and side detection component 105, light blocking strip 401, aperture hole 402, incident surface 501, The exit surface 502 , the first through hole 601 , and the second through hole 602 .

Detailed ways

The implementation of the present utility model is illustrated by specific specific examples below, and those skilled in the art can easily understand other advantages and effects of the present utility model from the content disclosed in this specification.

See Figures 1 through 5. It should be noted that the structures, proportions, sizes, etc. shown in the drawings attached to this specification are only used to match the content disclosed in the specification, for those who are familiar with this technology to understand and read, and are not used to limit the implementation of the utility model Therefore, it has no technical substantive meaning. Any modification of structure, change of proportional relationship or adjustment of size shall still fall within the scope of The technical content disclosed by the utility model must be within the scope covered. At the same time, terms such as "upper", "lower", "left", "right", "middle" and "one" quoted in this specification are only for the convenience of description and are not used to limit this specification. The applicable scope of the utility model and the change or adjustment of its relative relationship shall also be regarded as the applicable scope of the utility model if there is no substantial change in the technical content.

As shown in FIGS. 1 to 5 , the present embodiment provides an optical detection assembly, including a photodetector 7 , a light collection unit 5 , a straight blocking diaphragm 4 and a straight blocking diaphragm 4 . The light detector 7 is used to detect the light signal, and the light collection unit 5 is an aspheric lens, used to collect the light signal and project the collected light signal on the light detector 7 . The straight blocking diaphragm 4 is arranged in front of the light collecting unit 5 for filtering the light signal entering the light collecting unit 5 . The aperture diaphragm 6 is disposed between the light collecting unit 5 and the light detector 7 , and is used for filtering the light signal projected on the light detector 7 by the light collecting unit 5 .

The light collection unit 5 adopts an aspheric lens. Compared with a spherical lens, the aspheric lens can avoid spherical aberration and astigmatism caused by the convergence of scattered light, and improve the detection accuracy of blood cells.

In some embodiments, the light collecting unit 5 uses two or more aspheric lenses, or a combination of spherical lenses and aspheric lenses. In this embodiment, the light collection unit 5 is used to collect scattered light signals in the forward low angle and focus them on the position of the forward detector. The light collection unit 5 is an aspheric lens, and the number is one. Compared with the embodiment of the spherical lens, this embodiment uses an aspheric lens, which can effectively improve the problems of spherical aberration and astigmatism caused by the spherical lens, and is more conducive to the adjustment of the forward optical path, making it easier for the optical detection system to reach an ideal state. At the same time, the use of a single aspheric mirror makes the optical path system relatively simple, which is beneficial to the miniaturization of the optical detection system on the basis of saving costs. Moreover, after adopting a single aspherical lens, the mechanical structure of the optical detection component is simpler, and the requirements for mechanical structure accuracy and optical path adjustment are lower.

In this embodiment, the straight blocking diaphragm 4 is arranged before the light collection unit 5, which can filter the light signal entering the light collection unit 5, reduce the direct light, and prevent the direct light signal from entering the light detector 7 to cause signal saturation. . At the same time, the aperture diaphragm 6 is arranged between the light collection unit 5 and the light detector 7, and can filter out the stray light in the light signal projected from the light collection unit 5 to the light detector 7, The interference of stray light to the photodetector 7 is avoided, and the detection quality of the photodetector 7 is improved.

As shown in FIG. 3 , the light collecting unit 5 has an incident surface 501 and an outgoing surface 502 . The surface reflectance of the incident surface 501 is ≤0.1%, so as to reduce the reflection of the incident light signal, thereby reducing the influence of the reflected light on the stability of the light source. In this embodiment, the surface reflectance of the incident surface 501 is ≤0.05%, such as 0.04%, so as to further reduce the influence of reflected light on the stability of the light source.

In some embodiments, the incident surface 501 is a plane, and the outgoing surface 502 is a convex surface. The straight blocking diaphragm 4 cooperates with the incident surface 501 , and the filtered optical signal enters the light collection unit 5 from the incident surface 501 . Compared with the convex surface, the thickness of the light collecting unit 5 whose incident surface 501 is a plane is smaller, which is beneficial to reduce the size of the optical detection component. At the same time, the light collection unit 5 is usually fixed by glue transfer, and the glue is usually coated on the light collection unit 5 first, and then bonded and fixed. When the glue is squeezed on the incident surface 501, if the incident surface 501 is a convex surface, the glue will flow away easily, and if the incident surface 501 is a plane, then the glue can stay on the incident surface 501 better, which is convenient for the light collecting unit 5 installation.

As shown in Figure 4, in another embodiment, both the incident surface 501 and the outgoing surface 502 are convex. When the incident surface 501 is convex, when light is incident, most of the reflected light generated by the convex surface will deviate from the incident direction, and the less reflected light will be along the The incident direction returns to the front light assembly 101 in the same way, thereby reducing the influence of reflected light on the stability of the light source.

In order to shorten the size of the optical path of the optical detection component, the focal length of the aspheric lens is between 5 mm and 13 mm. In this embodiment, the focal length of the aspheric lens ranges from 7 mm to 11 mm. At the same time, the distance between the incident surface 501 of the aspheric lens and the straight stop diaphragm 4 is less than 1mm. carried out to further reduce the optical path size of the optical detection assembly.

Specifically, in this embodiment, the focal length of the light collection unit 5 is between 7 mm and 11 mm, for example, 8 mm.

In some embodiments, the numerical aperture of the light collecting unit 5 needs to be > 0.2, and the clear aperture of the light collecting unit 5 > 3 mm, so as to ensure that the scattered light passing through the straight blocking diaphragm 4 is effectively received and focused to the light detector 7 position. In this embodiment, the numerical aperture of the light collecting unit 5 is >0.25, for example, 0.3, and the clear aperture of the light collecting unit 5 is >5 mm, for example, 6 mm. In order to further increase the scattered light receiving range of the light collecting unit 5 .

In some embodiments, the light collecting unit 5 adopts an even-order aspheric lens. Compared with an odd-order aspheric lens, the processing of the even-order aspheric lens is simpler, which effectively reduces the processing cost of the aspheric lens.

The straight blocking diaphragm 4 can filter the light signals whose incident angles are between the upper limit and the lower limit into the light collecting unit 5 . In some embodiments, the lower limit is 1°, the upper limit ≥ 5° and the optical signal within the lower limit is direct light. If the direct light enters the light collection unit 5, it will cause saturation of the optical signal of the photodetector 7 and affect the detection result. The upper limit should be as high as possible, at least not less than 5°. In this embodiment, the upper limit is greater than or equal to 9°, such as 10°, so as to increase the reception of optical signals other than direct light as much as possible.

Specifically, as shown in Figure 2, the straight stop diaphragm 4 includes a circular diaphragm hole 402 and a light blocking strip 401 arranged in the middle of the diaphragm hole 402. The forward scattered light signal is selectively received, for example, the scattered light within 10° is selectively received. The light blocking strip 401 can block direct light in a low-angle direction, such as within 1°, after the laser beam irradiates the flow chamber 103, so as to prevent forward signal saturation. At the same time, the light blocking strip 401 is matte blackened to absorb or diffusely reflect the direct light, preventing the direct light from returning to the front light assembly 101 and affecting the stability of the optical detection system.

As shown in Figure 5, the aperture diaphragm 6 has a first through hole 601 and a second through hole 602, both of which are elongated, and the first through hole 601 is connected to the second through hole 602. The two through holes 602 intersect, and the light signal collected by the first light collecting component can pass through the first through hole 601 and the second through hole 602 and project on the photodetector 7, and the impurities outside the first through hole 601 and the second through hole 602 Light is filtered. In this embodiment, both the first through hole 601 and the second through hole 602 are waist holes, and the first through hole 601 and the second through hole 602 intersect each other at midpoints and are perpendicular to each other. In some embodiments, the first through hole 601 is elongated, the length of the first through hole 601 is ≥ 3 mm, and the width of the first through hole 601 is ≤ 1.5 mm, so that all the required low-angle scattered light can pass through the small hole light Diaphragm 6 serves the purpose of blocking stray light at the same time, so as to ensure the effective identification of tiny forward light signals. In this embodiment, the length of the first through hole 601 is greater than or equal to 5 mm, such as 6 mm. The width of the first through hole 601 is ≤1 mm, for example, 0.7 mm. In order to further improve the screening and filtering ability of the first through hole 601 for the light signal collected by the first light collection component.

As shown in FIG. 1 , this embodiment also provides an optical detection system, including a flow chamber 103 , a front light assembly 101 , a side detection assembly, and a front detection assembly.

The flow chamber 103 is used for the blood cells to be detected to pass through, and the blood cells pass through the flow chamber 103 one by one, which is convenient for analysis and detection. The front light assembly 101 is used to generate a laser beam and focus the laser beam on the flow chamber 103 along the first direction. Scattered light and side fluorescence. In some embodiments, the first direction intersects the second direction. In this embodiment, the first direction is perpendicular to the second direction. The side detection component is used to detect side scattered light and side fluorescence. The forward detection component is the above-mentioned optical detection component for detecting forward scattered light.

In some embodiments, the front light assembly 101 includes a laser 1, a collimating mirror 2, and a shaping lens group 3. The laser light generated by the laser 1 passes through the collimating mirror 2 to form parallel light, and then passes through the shaping lens group 3 to make the laser beam The blood cells to be detected are irradiated by the flow chamber 103, and then forward scattered light, side scattered light and side fluorescence are generated.

The laser 1 of the front light assembly 101 has an output laser wavelength of 620nm-650nm, and the shape of the output laser spot is elliptical. The laser output from the laser 1 passes through the collimating lens to form parallel light with an elliptical spot. The parallel light is incident on the shaping lens group 3, and through the action of the shaping lens, the light spot at the position of the flow chamber 103 reaches a suitable size and shape.

Specifically, the incident direction of the parallel light is the Z direction, the emission direction of the side scattered light and the side fluorescent light is the Y direction perpendicular to the Z direction, and the direction perpendicular to the Y direction and the Z direction is the X direction. In this embodiment, the first through hole 601 of the pinhole diaphragm 6 is arranged along the X direction, and the second through hole 602 of the pinhole diaphragm 6 is arranged along the Y direction. When the cells in the flow chamber 103 pass through the detection area, the spot size of the parallel light can ensure that the sample in the flow chamber 103 is covered in the X direction, and scattered light is generated when a single cell is irradiated in the Y direction. In this embodiment, the size of the light spot of the parallel light at the position of the flow chamber 103 in the Y direction is between 5 μm˜20 μm, for example, 12 μm. The size in the X-direction is >150 μm, for example 175 μm.

In some embodiments, between the front optical assembly 101 and the flow chamber 103, an optical isolation assembly 102, that is, an optical isolator, is installed. The optical isolation component 102 can prevent the reflected light from the surface of the flow chamber 103 and other devices from returning to the laser 1 by changing the deflection state of the incident light and reflected light, affecting the stability of the laser 1 and reducing the sensitivity of the optical detection system.

The side detection component includes a side collection lens 8 , a dichromatic mirror 9 , a side scatter detection component 10 and a side fluorescence detection component 11 , and the side detection component can detect and collect side scattered light and side fluorescence. The side scatter detection component and the side fluorescence detection component 11 share the side collection lens 8, so that high-angle scattered light and fluorescence are focused to the detection component after passing through the collection lens to complete the detection. The dichromatic mirror 9 is used to distinguish the side scattered light from the side fluorescence. Specifically, the optical signal incident on the dichroic mirror 9 includes side scattered light and side fluorescence, wherein the side scattered light is consistent with the wavelength of the light source laser , the side fluorescence is longer than the wavelength of laser light generated by the source laser 1. Thus, the dichroic mirror 9 is able to reflect the side scatter light into the side scatter detection assembly 10 . The side scatter detection component 10 can obtain information reflecting the complexity of the cell according to the magnitude of the side scatter light signal and the pulse width parameters. At the same time, the dichromatic mirror 9 allows the side fluorescence to pass through and enter the side fluorescence detection component. The side fluorescence detection component can obtain information reflecting the nucleic acid content in the cell according to the size, intensity and pulse width of the fluorescence signal.

To sum up, in the optical detection component and optical detection system provided by this embodiment, the straight stop 4 is arranged in front of the light collection unit 5, which can filter the light signals entering the light collection unit 5, reduce direct light, and avoid A direct light signal entering the photodetector causes the light signal to saturate. Simultaneously, the pinhole aperture 6 is arranged between the light collection unit 5 and the photodetector 7, can filter out the stray light in the optical signal projected by the light collection unit 5 on the photodetector 7, and avoid stray light from affecting the photodetector. 7 to improve the detection quality of the photodetector 7. The light collection unit 5 is an aspheric lens, which can avoid spherical aberration and astigmatism caused by the convergence of scattered light by the spherical lens, and improve the detection accuracy of blood cells. At the same time, the optical path system using the aspheric mirror is relatively simple, which is conducive to the miniaturization of the optical detection system on the basis of saving costs. Moreover, after adopting a single aspheric lens, the mechanical structure of the optical detection component is simpler, and the requirements for mechanical structure precision and optical path adjustment are lower, which is more conducive to forward optical path adjustment, making it easier for the optical detection system to reach the ideal state.

The above-mentioned embodiments only illustrate the principles and effects of the present utility model, but are not intended to limit the present utility model. Anyone familiar with this technology can modify or change the above-mentioned embodiments without departing from the spirit and scope of the present invention. Therefore, all equivalent modifications or changes made by those with ordinary knowledge in the technical field without departing from the spirit and technical ideas disclosed in the utility model should still be covered by the claims of the utility model.

Claims (16)

1. An optical inspection assembly, comprising:

a light detector for detecting a light signal;

a light collection unit for collecting light signals and projecting the collected light signals on the light detector;

the straight stopping diaphragm is arranged in front of the light collecting unit and used for screening the light signals entering the light collecting unit;

the aperture diaphragm is arranged between the light collection unit and the light detector and is used for filtering the light signal projected on the light detector by the light collection unit;

wherein the light collection unit is an aspheric lens.

2. The optical inspection assembly of claim 1, wherein: the light collection unit is provided with an incident surface and an emergent surface, wherein the incident surface is a plane or a convex surface, and the emergent surface is a convex surface.

3. The optical inspection assembly of claim 2, wherein: the surface reflectivity of the incident surface is less than or equal to 0.1 percent.

4. The optical inspection assembly of claim 2, wherein: the surface reflectivity of the incident surface is less than or equal to 0.05 percent.

5. The optical inspection assembly of claim 1, wherein: the focal length of the light collection unit is 5 mm-13 mm.

6. The optical inspection assembly of claim 5, wherein: the focal length of the light collection unit is 7 mm-11 mm.

7. The optical inspection assembly of claim 1, wherein: the clear aperture of the light collection unit is larger than 3mm, and the numerical aperture of the light collection unit is larger than 0.2.

8. The optical inspection assembly of claim 7, wherein: the clear aperture of the light collection unit is larger than 5mm, and the numerical aperture of the light collection unit is larger than 0.25.

9. The optical inspection assembly of claim 1, wherein: the light collection unit is an even aspheric lens.

10. The optical inspection assembly of claim 1, wherein: the distance between the light collecting unit and the straight blocking diaphragm is less than 1mm.

11. The optical inspection assembly of claim 1, wherein: the light signal with the straight blocking diaphragm screening incidence angle between the upper limit and the lower limit enters the light collecting unit, the lower limit is 1 degree, and the upper limit is larger than or equal to 5 degrees.

12. The optical detection assembly of claim 11, wherein: the upper limit is more than or equal to 9 degrees.

13. The optical inspection assembly of claim 1, wherein: the aperture diaphragm is provided with a first through hole and a second through hole, the first through hole and the second through hole are both in long strips, the first through hole is intersected with the second through hole, the length of the first through hole is larger than or equal to 3mm, and the width of the first through hole is smaller than or equal to 1.5mm.

14. The optical inspection assembly of claim 13, wherein: the length of the first through hole is more than or equal to 5mm, and the width of the first through hole is less than or equal to 1mm.

15. The optical inspection assembly of claim 1, wherein: the number of the aspheric lenses is 1.

16. An optical inspection system, comprising:

a flow cell for passage of the detected blood cells;

the front light assembly is used for generating a laser beam and focusing the laser beam on the flow chamber along a first direction, forming forward scattering light along the first direction, and forming side scattering light and side fluorescence along a second direction, wherein the first direction and the second direction are intersected;

a lateral detection assembly for detecting the lateral scattered light and the lateral fluorescence; and

a forward detection assembly, being an optical detection assembly as claimed in any one of claims 1 to 15, for detecting said forward scattered light.

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