Optical module of fluorescence immunoassay analyzer

Abstract

The utility model discloses an optical module of a fluorescence immunoassay analyzer, which simplifies the structure, reduces the cost and improves the detection efficiency. The device comprises an optical circuit board, an LED, a PD, an excitation shell, a receiving shell, an optical fiber, a plano-convex lens, an optical filter and a dichroscope, the optical circuit board is provided with a row of LEDs and a row of PDs, and the number of the LEDs is equal to that of the PDs; the excitation shell and the receiving shell respectively cover the LED and the PD; the excitation shell is provided with an output hole, and the receiving shell is provided with an input hole for connecting an optical fiber; a first channel communicated to the output hole is arranged in the excitation shell corresponding to the LED, and a second channel communicated to the input hole is arranged in the receiving shell corresponding to the PD; plano-convex lenses are arranged at the output hole and the input hole; each LED and each PD are correspondingly provided with a pair of plano-convex lenses and an optical filter; a plurality of dichroscopes are arranged in the first channel and the second channel, light concentration is achieved between the LED and the output hole through the dichroscopes, and light dispersion is achieved between the input hole and the PD through the dichroscopes.

Description

Technical Field

[0001] The utility model relates to the technical field of fluorescence immunoassay, in particular to an optical module of a fluorescence immunoassay analyzer. Background Art

[0002] A fluorescence immunoassay analyzer is an instrument capable of measuring and quantitatively analyzing trace substances, which can convert the structure and characteristics of substances into visible and measurable spectral signals. The fluorescence immunoassay analyzer has the characteristics of high detection sensitivity, fast and accurate, convenient operation, etc., and is not affected by the nature of the detected substance itself, and is one of the most important technologies in current analysis and detection technologies.

[0003] According to the currently commonly used optical path design on the market, when different detection waves are required for sampling, mainly a single-channel photometric module is driven by a motor to drive a mechanical structure to align it with different detection wave emitters for individual detection. Although this solution has the advantage of simple structural design, the software control is relatively complex, and there are a large number of modules, a large volume. At the same time, the photometric accuracy is also affected by the mechanical movement accuracy, and there are many interference factors; moreover, since the inside of the optical fiber used for transmitting signals is composed of multiple strands of ultra-fine quartz glass optical fibers, long-term and frequent movement may cause the fine optical fibers inside the optical fiber to break. Summary of the Utility Model

[0004] The purpose of the utility model is to provide an optical module of a fluorescence immunoassay analyzer, solve the problems existing in the prior art, simplify the structure, reduce the cost, and improve the detection efficiency.

[0005] In order to achieve the above object, the solution of the utility model is:

[0006] An optical module of a fluorescence immunoassay analyzer, comprising an optical circuit board, LEDs, PDs, an excitation housing, a receiving housing, optical fibers, plano-convex lenses, filter plates, and dichroic mirrors; a row of LEDs and a row of PDs arranged side by side are provided on the optical circuit board, and the number of LEDs is equal to the number of PDs; the excitation housing and the receiving housing respectively cover the LEDs and PDs; the excitation housing is provided with an output hole, and the receiving housing is provided with an input hole, and both the output hole and the input hole are used to connect optical fibers; a first channel is provided in the excitation housing corresponding to each LED, and each first channel communicates with the output hole; a second channel is provided in the receiving housing corresponding to each PD, and each second channel communicates with the input hole; plano-convex lenses are provided at the output hole and the input hole; a pair of plano-convex lenses and filter plates are respectively provided corresponding to each LED and PD, and the plano-convex lens is located between the LED / PD and the filter plate; a plurality of dichroic mirrors are provided in the first channel and the second channel, and the dichroic mirror is used to concentrate the light from each first channel to the output hole between the LED and the output hole, and the dichroic mirror is used to disperse the light from the input hole to each second channel between the input hole and the PD.

[0007] A reflecting mirror is provided in each of the excitation housing and the receiving housing.

[0008] It further includes a shielding cover provided on the optical circuit board and covering the PD.

[0009] The optical module of the fluorescence immunoassay analyzer further includes a support plate provided at the bottoms of the excitation housing and the receiving housing, and the optical circuit board is vertically connected to the support plate.

[0010] After adopting the above technical solution, the present utility model has the following technical effects:

[0011] By respectively concentrating a plurality of first channels and second channels in the excitation housing and the receiving housing, and transmitting the excitation light and the emission light through optical fibers, the present utility model can greatly reduce the volume of the product. The overall structure is fixed, without a moving mechanical structure. Only software control is required to collect signals from the corresponding channels of the LEDs and PDs, eliminating mechanical movement actions, reducing wear on the optical fibers and other accessories, and greatly improving the service life of the product; at the same time, since the channel switching is controlled by pure software, the time for mechanical movement to switch channels is saved, and the detection efficiency can be greatly improved; the excitation and receiving parts of the present utility model are independent of each other, and the maintenance is simpler; because the present utility model is no longer interfered by mechanical movement, the detection accuracy is improved, and in an actual product, the photometric fluctuation CV can reach within 0.1%. Description of the Drawings

[0012] Figure 1 It is a three-dimensional view of a specific embodiment of the present utility model;

[0013] Figure 2 It is the front view of the specific embodiment of the present utility model;

[0014] Figure 3 is Figure 2 the cross-sectional view in the A-A direction in

[0015] Figure 4 is Figure 2 the cross-sectional view in the B-B direction in

[0016] Figure 5 It is the usage schematic diagram of the specific embodiment of the present utility model;

[0017] Figure 6 It is the principle schematic diagram of the specific embodiment of the present utility model

[0018] Explanation of the reference numerals in the drawings:

[0019] 1 - Optical circuit board; 2 - LED; 3 - PD; 4 - Excitation housing; 41 - Output hole; 42 - First channel; 5 - Receiving housing; 51 - Input hole; 52 - Second channel; 6 - Optical fiber; 61 - Incident optical fiber; 62 - Receiving optical fiber; 7 - Planoconvex lens; 8 - Filter; 9 - Dichroic mirror; 10 - Reflecting mirror; 20 - Shielding cover; 30 - Support plate; 40 - Nucleic acid extraction and amplification chip; 401 - Amplification area. Specific embodiments

[0020] In order to further explain the technical solution of the present utility model, the present utility model will be elaborated in detail through specific embodiments below.

[0021] Referring to Figures 1 to 4 as shown, the present utility model discloses an optical module of a fluorescence immunoassay analyzer, including an optical circuit board 1, an LED 2, a PD 3 (photodiode), an excitation housing 4, a receiving housing 5, an optical fiber 6, a planoconvex lens 7, a filter 8 and a dichroic mirror 9;

[0022] A row of LEDs 2 and a row of PDs 3 are arranged side by side on the optical circuit board 1, and the number of LEDs 2 is equal to the number of PDs 3;

[0023] The excitation housing 4 and the receiving housing 5 are respectively covered on the LED 2 and the PD 3; the excitation housing 4 is provided with an output hole 41, and the receiving housing 5 is provided with an input hole 51. Both the output hole 41 and the input hole 51 are used to connect the optical fiber 6; a first channel 42 is provided in the excitation housing 4 corresponding to each LED 2, and each first channel 42 communicates with the output hole 41; a second channel 52 is provided in the receiving housing 5 corresponding to each PD 3, and each second channel 52 communicates with the input hole 51;

[0024] Plano-convex lenses 7 are provided at both the output hole 41 and the input hole 51; a pair of plano-convex lenses 7 and filters 8 are correspondingly provided for each LED 2 and PD 3, and the plano-convex lenses 7 are located between the LED 2 / PD 3 and the filter 8;

[0025] A number of dichroic mirrors 9 are provided in both the first channel 42 and the second channel 52. The dichroic mirrors 9 are used to concentrate the light from each first channel 42 to the output hole 41 between the LED 2 and the output hole 41, and the dichroic mirrors 9 are used to disperse the light from the input hole 51 to each second channel 52 between the input hole 51 and the PD 3.

[0026] Through the above solution, in the present utility model, by respectively concentrating a plurality of first channels 42 and second channels 52 in the excitation housing 4 and the receiving housing 5, and transmitting the excitation light and the emission light through the optical fiber 6, the volume of the product can be greatly reduced. The overall structure is fixed, without a moving mechanical structure. Only the software needs to control the LEDs 2 and PDs 3 of the corresponding channels for signal acquisition, eliminating the mechanical movement, reducing the wear on the optical fiber 6 and other accessories, and greatly improving the service life of the product. At the same time, since the channel switching is controlled by software only, the time for mechanically switching channels is saved, and the detection efficiency can be greatly improved. The excitation part and the receiving part of the present utility model are independent of each other, and the maintenance is simpler. Since the present utility model is no longer interfered by mechanical movement, the detection accuracy is improved. In an actual product, the photometric fluctuation CV can reach within 0.1%.

[0027] The following shows specific embodiments of the present utility model.

[0028] The above excitation housing 4 and receiving housing 5 are both provided with a mirror 10 to realize the reflection of light, so as to reflect the light in the direction of the output hole 41 or the end of the second channel 52.

[0029] The present utility model further includes a shielding cover 20 provided on the optical circuit board 1 and covering the PD 3, which can prevent signal interference.

[0030] The present utility model further includes a support plate 30 provided at the bottoms of the excitation housing 4 and the receiving housing 5. The optical circuit board 1 is vertically connected to the support plate 30, so that the optical circuit board 1, the excitation housing 4, the receiving housing 5 and the support plate 30 are assembled into a whole.

[0031] The above optical fiber 6 includes an incident optical fiber 61 and a receiving optical fiber 62. The output hole 41 and the input hole 51 are respectively connected to the amplification region 401 (i.e., the fluorescence detection region) of the nucleic acid extraction and amplification chip 40 through the incident optical fiber 61 and the receiving optical fiber 62.

[0032] In the present utility model, both the excitation part and the receiving part are designed with six channels. See Figure 3 and Figure 4, in the order from top to bottom, the six first channels 42 in the excitation housing 4 are the CY5 channel, ROX channel, Quasar705 channel, ATTO425 channel, FAM channel, and HEX channel respectively. The specific models of the corresponding LEDs 2 are NSPR310S (Nichia), NSPA510BS (Nichia), W680-06 (Yinghai), W420R-06 (Yinghai), NSPB510AS (Nichia), and NSPG310B (Nichia), and the content in the brackets is the corresponding manufacturer; the photosensitive surface area of the PD 3 can use a photodiode of 2.5*2.5mm or even larger. In this embodiment, the photodiode S1133-01 of Hamamatsu, Japan is selected. In the order from top to bottom, the central wavelengths of the parameters of the six filters 8 in the excitation housing 4 are 625nm narrowband, 571nm narrowband, 682nm narrowband, 435nm narrowband, 485nm narrowband, and 520nm narrowband respectively. The central wavelengths of the parameters of the six filters 8 in the receiving housing 5 are 660nm narrowband, 612nm narrowband, 718nm narrowband, 480nm narrowband, 525nm narrowband, and 571nm narrowband respectively. In the order from top to bottom and from right to left, the specific models of the five dichroic mirrors 9 in the excitation housing 4 and the five dichroic mirrors 9 in the receiving housing 5 are respectively:

[0033]

[0034] Reference Figure 5 and Figure 6 As shown, the working principle of the present invention is:

[0035] (1) Since the light emitted by the LED 2 is relatively divergent, in order to ensure that the excitation of each LED 2 has sufficient excitation intensity and a narrow wavelength range, a plano-convex lens 7 is added to the rear end of each LED 2 for light focusing, and the light emitted by the LED is changed into parallel light through the plano-convex lens 7; moreover, the spectral wavelength range of the light emitted by the LED 2 is relatively wide and cannot meet the requirements of the PCR excitation light wavelength range. A narrowband filter 8 needs to be added to the rear end of each lens to filter out stray light of other wavelength bands.

[0036] (2) Since the intensity of the PCR emission light is weak, and the light emitted after the emission light enters the optical fiber 6 and is transmitted and then emitted is scattered at a certain angle, a plano-convex lens 7 needs to be added to the output end of the optical fiber 6 (i.e., the input hole 51) to converge into parallel light; in order to ensure that the emission light of each channel has sufficient fluorescence intensity when entering the PD 3 and is not affected by the excitation light, a narrowband filter 8 needs to be added to the front end of the PD 3 to prevent the light in the excitation wavelength band from entering the PD 3, which can avoid weak signal-to-noise ratio; at the same time, a plano-convex lens 7 also needs to be added to the rear end of the narrowband filter 8 for focusing to ensure that the fluorescence intensity of the emission light can be focused and enter the PD 3.

[0037] (3) During the experiment, the amplification area 401 of the nucleic acid extraction and amplification chip 40 contains amplification reagents. The software controls the activation of each LED 2 in the excitation housing 4 to energize and excite the fluorescent groups in the amplification area 401. After the fluorescent groups obtain sufficient energy, they release photons of different wavelengths. The photons are conducted through the receiving optical fiber 62 into the receiving housing 5, and then the software controls the PD 3 in each channel of the receiving housing 5 to work, detect the received light intensity, and convert it into an electrical signal to achieve fluorescence collection.

[0038] The above embodiments and drawings do not limit the product form and style of the present invention. Any appropriate changes or modifications made by those of ordinary skill in the art shall be regarded as not departing from the patent scope of the present invention.

Claims

1. An optical module of a fluorescence immunoassay analyzer, characterized in that: It includes an optical circuit board, LEDs, PDs, an excitation housing, a receiving housing, optical fibers, plano-convex lenses, filter plates, and dichroic mirrors; A row of LEDs and a row of PDs are arranged side by side on the optical circuit board, and the number of the LEDs is equal to the number of the PDs; The excitation housing and the receiving housing are respectively sleeved on the LEDs and PDs; the excitation housing is provided with an output hole, and the receiving housing is provided with an input hole, and both the output hole and the input hole are used to connect the optical fibers; a first channel is provided corresponding to each LED in the excitation housing, and each first channel communicates with the output hole; a second channel is provided corresponding to each PD in the receiving housing, and each second channel communicates with the input hole; Plano-convex lenses are provided at both the output hole and the input hole; a pair of plano-convex lenses and a filter plate are provided corresponding to each LED and PD, and the plano-convex lens is located between the LED / PD and the filter plate; A plurality of dichroic mirrors are provided in both the first channel and the second channel. The dichroic mirror is used to concentrate the light from each first channel to the output hole between the LED and the output hole, and the dichroic mirror is used to disperse the light from the input hole to each second channel between the input hole and the PD.

2. The optical module of the fluorescence immunoassay analyzer according to claim 1, characterized in that: A reflecting mirror is provided in both the excitation housing and the receiving housing.

3. The optical module of the fluorescence immunoassay analyzer according to claim 1, characterized in that: It further includes a shielding cover provided on the optical circuit board and covering the PD.

4. The optical module of the fluorescence immunoassay analyzer according to claim 1, characterized in that: It further includes a support plate provided at the bottom of the excitation housing and the receiving housing, and the optical circuit board is vertically connected to the support plate.

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