CN112229780A - An improved flow cytometer based on fiber-optic integrated microfluidic chip - Google Patents
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- G01N15/00—Investigating characteristics of particles; Investigating permeability, pore-volume or surface-area of porous materials
- G01N15/10—Investigating individual particles
- G01N15/14—Optical investigation techniques, e.g. flow cytometry
- G01N15/1434—Optical arrangements
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N15/00—Investigating characteristics of particles; Investigating permeability, pore-volume or surface-area of porous materials
- G01N15/10—Investigating individual particles
- G01N15/14—Optical investigation techniques, e.g. flow cytometry
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Abstract
The invention provides an improved flow cytometer based on an optical fiber integrated microfluidic chip. The method is characterized in that: the system consists of five modules, namely an optical fiber integrated microfluidic chip, a light source, a fluid control system, a photoelectric detection system and a waste liquid collection system. A fluid control system in the system controls a cell sample and sheath fluid to form a cell flow, the cell flow flows into a cell flow guide pipe of the microfluidic chip, the cell flow guide pipe is connected with the hollow annular core optical fiber, and cells in the cell flow are irradiated by a self-focusing light beam of the hollow annular core optical fiber to generate scattered light. The micro-flow chip is embedded with scattered light collecting optical fibers which are distributed on two sides of the micro-flow channel. Scattered signal light in different directions is collected through the optical fiber and transmitted to the photoelectric detection system for light splitting detection. The invention can be used for cell analysis.
Description
(I) technical field
The invention relates to an improved flow cytometer based on an optical fiber integrated microfluidic chip, which can be used for automatic analysis and sorting of cells and belongs to the technical field of cell detection and analysis.
(II) background of the invention
The flow cytometry principle of operation is the multiparameter, rapid quantitative analysis of single cells or other biological particles by monoclonal antibodies at the cellular molecular level. The method can analyze tens of thousands of cells at high speed, can simultaneously measure a plurality of parameters from one cell, has the advantages of high speed, high precision and good accuracy, and is one of the most advanced cell quantitative analysis techniques in the present generation. It was first used to measure cell volume in the 50's of the 20 th century and can be detected when cells are passed straight through a sight hole with a fast flowing fluid. In flow cytometry, cells in solution are detected by passing the laser beam of the instrument at a rate of 10,000 cells (or more) per second. Today's flow cytometers have more detectable fluorescence parameters (from 1 or 2 up to around 30) and can measure all parameters on the same cell simultaneously.
The flow cytometry has the following characteristics: (1) single cell analysis: the object of flow cytometry analysis is single cell or particle-like substance, and various samples need to be processed appropriately to prepare single cell suspension before being used for flow analysis; (2) multi-parameter analysis: the flow cytometry can obtain physical parameters of cells or particle-like substances, and can analyze DNA content, antigen expression, enzyme activity and the like of the cells by a fluorescein labeling technology; (3) high flux: the flow cytometry can analyze the physicochemical characteristics of thousands of cells every second, and the total number of the analyzed cells in the sample to be tested can reach millions, so that the characteristic identification and counting of the cells are more accurate; (4) the sorting function: cells having a particular trait or function can be isolated from a mixed population of cells. Cell sorting, especially single cell sorting, is of great value in studying the structure and function of cells.
A Flow cytometer (Flow cytometer) is a device that automatically analyzes and sorts cells. It can quickly measure, store and display a series of important biophysical and biochemical characteristic parameters of dispersed cells suspended in liquid, and can select specified cell subsets according to the preselected parameter range. Flow cytometry consists essentially of four parts. They are: a flow chamber and a fluid flow system; a laser source and an optical system; a photoelectric tube and a detection system; the patent CN110687034A of computer and analysis system discloses a laser irradiation type loss cell analyzer, which has complicated optical path and spatial structure and high manufacturing cost to ensure its stability and independence of each module. Patent CN111024592A discloses an optical path device of a flow cytometer, which has a large optical path volume and a complicated light receiving structure. .
The traditional flow cytometer adopts a spatial light path, which has high requirements on the spatiality and stability of the light path, and needs to precisely adjust the light path, and the optical elements are greatly interfered by external environments such as vibration, temperature, humidity and the like. Moreover, these space optical elements are bulky and are not flexible enough in assembly. More importantly, the traditional spatial light path system adopts a microscope objective as a light receiving medium, and the size of the objective is large, so that the use number of the objective and the light path integration are limited.
Disclosure of the invention
The invention aims to provide an improved flow cytometer based on an optical fiber integrated microfluidic chip.
The purpose of the invention is realized as follows:
an improved flow cytometer based on an optical fiber integrated microfluidic chip is shown in fig. 1. The system consists of five modules, namely an optical fiber integrated microfluidic chip 1, a light source 2, a fluid control system 6, photoelectric detection systems 7-1 and 7-2 and a waste liquid collection system 9. A fluid control system 6 in the system controls a cell sample and sheath fluid to form a cell flow, the cell flow flows into a cell flow guide pipe 10 of a microfluidic chip, the cell flow guide pipe 10 is connected with a hollow annular core optical fiber 4, the hollow annular core optical fiber 4 uses a hollow part 4-5 of the optical fiber as a single cell flow channel, the output end of the hollow annular core optical fiber 4 is manufactured into a frustum structure by an optical fiber grinding technology and used for focusing and irradiating exciting light, and cells 11 in the cell flow can only pass through one self-focusing position at each time due to the self-focusing effect of light beams at the output end of the hollow annular core optical fiber. The cells 11 in the cell flow are irradiated with an excitation light source and then collected by the waste liquid collection system 9. Scattered light collecting optical fibers 8-1 and 8-2 are embedded on the microfluidic chip and distributed on two sides of the microfluidic channel. Scattered signal light in different directions is collected through optical fibers and respectively transmitted to photoelectric detection systems 7-1 and 7-2 for light splitting detection.
The optical fiber integrated microfluidic chip comprises a cell flow conduit 10, a hollow annular core optical fiber 4 and two scattered light collecting optical fibers 8-1 and 8-2. The fluid control system 6 controls sheath fluid and a cell sample to form a single cell flow, the single cell flow is transmitted to the hollow annular core optical fiber 4 through the cell fluid guide pipe 10, the hollow annular core optical fiber 4 takes a hollow part 4-5 thereof as a single cell flow channel, the hollow annular core optical fiber 4 leads exciting light of the light source 2 out by utilizing the fiber core 4-2 and irradiates on cells to generate scattered light, the output end of the hollow annular core optical fiber 4 is manufactured into a frustum structure by the optical fiber grinding technology, and the cells 11 in the cell flow can only pass through one at a self-focusing position due to the self-focusing effect of light beams at the output end of the hollow annular core optical fiber. The scattered light is collected by scattered light collection fibers 8-1, 8-2 located on both sides of the hollow annular core fiber 4, and then the cell flow enters a waste liquid treatment system 9 for corresponding harmless treatment.
As shown in FIG. 2, one side of the hollow annular core optical fiber 4 on the integrated microfluidic chip is perforated by a precision drilling technology, and the micro-hole 4-4 is used for connecting the hollow annular core optical fiber 4 with the cell flow conduit 10. When the cell flow reaches the hollow annular core fiber 4, the hollow annular core fiber 4 takes the hollow part 4-5 as a microfluidic channel, and the excitation light generated by the light source 2 is transmitted through the fiber core 4-2. The output end of the hollow annular core optical fiber 4 is made into a frustum structure by an optical fiber grinding technology and used for focusing and irradiating an excitation light source.
After the scattered light is generated, the scattered light is collected by scattered light collecting optical fibers 8-1 and 8-2 and respectively transmitted to photoelectric detection systems 7-1 and 7-2. Alternatively, the scattered light collecting fibers 8-1 and 8-2 can be both pure quartz core fluorine-doped cladding fibers with large numerical aperture and large core diameter, and can collect scattered light well. The scattered light collection fibers 8-1 and 8-2 are respectively positioned at two sides of the hollow annular core fiber 4 and are at 90 degrees with the hollow annular core fiber 4, and the two scattered light collection fibers 8-1 and 8-2 are positioned on the same straight line.
As shown in fig. 3, 4 and 5, the scattered light is transmitted to the photodetection systems 7-1 and 7-2 via scattered light collecting fibers 8-1 and 8-2, respectively. The photoelectric detection systems 7-1 and 7-2 have the same structure and are composed of a light splitting module 12 and a photoelectric detection module 13, wherein the light splitting module 12 is composed of a plurality of different dichromatic mirrors 12-1-12-4, the dichromatic mirrors 12-1-12-4 can be selected according to the number of different fluorescent markers on cells and the spectrum band width of a light source, and correspondingly, the number of the photoelectric detectors 13-1-13-4 in the photoelectric detection module 13 can also be selected according to the number of different dichroic lenses 12-1-12-4. The photodetector may be a single photon detector, a photomultiplier tube, or other photodetectors.
The irradiated cell flow enters a waste liquid collection system 9 for corresponding harmless treatment.
Alternatively, the light source 2 may be a single-wavelength laser light source, or may be multiple light sources with different wavelengths, and the excitation light is coupled into the optical fiber 3 in the light source 2 via the optical fiber wavelength division multiplexer 14 for transmission, as shown in fig. 7. The optical fiber 3 is connected to the hollow ring-core optical fiber 4 by a coupler 15 or by core alignment, as shown in fig. 8a and 8 b. This is similar to the common-path excitation system in conventional flow cytometers, i.e., multiple wavelengths of laser light are simultaneously applied to each cell passing through the beam.
Optionally, the optical fiber 3 in the light source 2 may be a single-mode optical fiber or a multimode optical fiber
Compared with the traditional flow cytometer, the invention has the following advantages:
(1) compared with the traditional nozzle type microfluidic channel, the microfluidic chip has the advantages of various preparation methods, various material types, rich design diversity of the fluid channel, high integration level of the chip, small dimension and high design flexibility.
(2) The optical fiber is adopted to replace the traditional space optical path, so that the fine adjustment of the space optical path when a device is replaced is avoided. The optical fiber is directly embedded into the microfluidic chip, the chip can be integrally replaced, and the whole system is high in stability and is slightly influenced by external environments such as temperature, humidity and vibration. And the optical fiber has excellent flexibility and can be bent arbitrarily, which is extremely advantageous for integration and miniaturization of the system.
(3) The microfluidic chip can be used for analyzing cells with different sizes by replacing hollow annular core optical fibers with different sizes. For tiny cells, the micro-lens at the end of the optical fiber realizes the output of a light beam with a micron size, and ensures the measurement resolution when the cells pass through.
(IV) description of the drawings
Fig. 1 is a schematic diagram of an improved flow cytometer based on an optical fiber integrated microfluidic chip.
Fig. 2 is a schematic diagram of a hollow annular core optical fiber structure.
Fig. 3 is a schematic diagram of a structure of a photo-detection system.
Fig. 4 is a schematic structural diagram of a light splitting module of the photodetection system.
Fig. 5 is a schematic diagram of a photodetection module of the photodetection system.
Fig. 6 is a schematic diagram of a wavelength division multiplexing device of a light source.
FIG. 7 is a schematic diagram of the connection of a light source fiber to a hollow annular core fiber, FIG. 7(a) is a coupler connection type, and FIG. 7(b) is a core alignment type.
FIG. 8 is a schematic diagram of a hollow ring-core optical fiber with a hollow portion as a microfluidic channel and focused excitation light source to irradiate a cell sample.
(V) detailed description of the preferred embodiments
The invention is further illustrated with reference to the following figures and specific examples.
Example 1:
fig. 1 is a system diagram of an improved flow cytometer based on an optical fiber integrated microfluidic chip. The system consists of five modules, namely an optical fiber integrated microfluidic chip 1, a light source 2, a fluid control system 6, a photoelectric detection system 7 and a waste liquid collection system 9. A fluid control system 6 in the system controls a cell sample and sheath fluid to form single cell flow, the single cell flow flows into a cell flow guide pipe 10 of a microfluidic chip 1, and the cell flow guide pipe 10 is connected with a hollow annular core optical fiber 4. The hollow annular core optical fiber 4 is connected with the optical fiber 3 to introduce the exciting light of the light source 2, and the hollow annular core optical fiber 4 can be connected with the optical fiber 3 in a coupler mode, as shown in fig. 8(a), or in a fiber core alignment mode, as shown in fig. 8 (b). The hollow ring-shaped core optical fiber 4 uses the hollow part 4-5 as a micro-flow channel for the cell flow to pass through. The output end of the hollow annular core optical fiber 4 is made into a frustum structure through an optical fiber grinding technology for focusing and irradiating exciting light, and the cells 11 in the cell flow can only pass through one self-focusing position at each time due to the self-focusing function of the light beam at the output end of the hollow annular core optical fiber 4, as shown in fig. 8. The cells 11 in the cell flow are irradiated with an excitation light source and then collected by the waste liquid collection system 9. Scattered light generated by irradiation is collected by scattered light collection optical fibers 8-1 and 8-2 and respectively transmitted to photoelectric detection systems 7-1 and 7-2 for corresponding detection and analysis.
PE-TxRed is selected as a fluorescent marker of a cell sample, and the wavelength of an excitation light source of the PE-TxRed is 488 nm. After the PE-TxRed attached to the cells in the single cell flow is irradiated by an excitation light source, the wavelength of the generated scattered excitation light is 620nm, and scattered light is collected by scattered light collection optical fibers 8-1 and 8-2 and respectively transmitted to photoelectric detection systems 7-1 and 7-2. The photoelectric detection system 7-2 is taken as an example to illustrate the light splitting and detecting process of the scattered light.
The scattered light collection fiber 8-2 collects two wavelengths of scattered light, respectively: the wavelength is 488nm light source exciting light and 620nm excited light. The scattered light collection optical fiber 8-2 transmits the collected scattered light to the photoelectric detection system 7-2, and the photoelectric detection system 7-2 comprises a light splitting module 12 and a photoelectric detection module 13. The light splitting surfaces of the light splitters 12-1 and 12-2 of the light splitting module 12 are respectively coated with a long wave-passing dichroscope and a short wave-passing dichroscope of 500 nm. Correspondingly, the single photon detectors 13-1 and 13-2 in the photodetection module 13 are respectively used for detecting the scattered light with the wavelength of 488nm and the scattered light with the wavelength of 620 nm.
Example 2:
FITC and APC-Cy7 are selected as markers of cells in the single cell flow, and the excitation light wavelengths are respectively as follows: 488nm and 635nm, the wavelengths of the generated excited light are 530nm and 780nm respectively.
The light sources 2-1 and 2-2 are 488nm and 635nm laser light sources respectively, the light sources are combined by a wavelength division multiplexer 14 and then transmitted to the hollow annular core optical fiber 4 through the optical fiber 3. The cells 11 in the cell flow generate scattered light after being irradiated, and the scattered light is collected by scattered light collecting optical fibers 8-1 and 8-2 and respectively transmitted to photoelectric detection systems 7-1 and 7-2. The scattered light contains 4 wavelengths of light, excitation light with wavelengths of 488nm and 635nm, and excited light with wavelengths of 530nm and 780 nm. The photoelectric detection system 7-2 is taken as an example to illustrate the light splitting and detection conditions of the scattered light.
Four scattered light wavelengths entering the photoelectric detection system, wherein a short wave passing dichroscope with the spectral wavelength of 700nm is plated on the spectral surface of the spectral interface 12-1, the photoelectric detection module 13 is firstly entered for scattering with the wavelength of 780nm, the single photon detector 13-1 carries out corresponding detection processing, a short wave passing dichroscope with the spectral wavelength of 600nm is plated on the spectral surface of the spectral interface 12-2, the single photon detector 13-2 enters the photoelectric detection module 13 through the spectral interface 12-2 with the wavelength of 635nm, the single photon detector 13-2 carries out corresponding detection processing, a short wave passing dichroscope with the wavelength of 500nm is plated on the spectral surface of the spectral interface 12-3, the scattered light with the wavelength of 530nm enters the photoelectric detection module 13 through the spectral interface 12-3, the single photon detector 13-3 carries out corresponding detection processing, and finally, a long wave passing dichroscope with the wavelength of 500nm is plated on the spectral interface of the spectral interface 12-4, scattered light with the wavelength of 488nm enters the photoelectric detection module 13 through the light splitting interface 12-4, and corresponding detection processing is carried out by the single-photon detector 13-4.
Claims (6)
1. An improved flow cytometer based on an optical fiber integrated microfluidic chip is characterized in that: it comprises five modules of integrated miniflow chip of optic fibre, light source, fluid control system, photoelectric detection system, waste liquid collecting system, fluid control system control cell sample and sheath liquid form the cell stream in the system, flow into the cell stream pipe of miniflow chip, the cell stream pipe is connected with cavity annular core optic fibre, the cell in the cell stream is through cavity annular core self-focusing light beam irradiation back, collect the processing by waste liquid collecting system, it collects optic fibre to inlay the scattered light on the miniflow chip, distribute in the both sides of miniflow passageway, the scattered signal light of equidirectional is collected via the optic fibre, transmit to photoelectric detection system and carry out the beam split and survey.
2. The improved flow cytometer based on optical fiber integrated microfluidic chip as described in claim 1, wherein: the hollow annular core optical fiber is perforated on the side surface thereof by a precise perforation technology and is used for connecting cell flow conduits, the hollow part of the optical fiber is used as a single cell flow channel, the output end of the hollow annular core is manufactured into a frustum structure by the optical fiber grinding technology and is used for focusing and irradiating exciting light, and cells in the cell flow can only pass through one self-focusing position at each time due to the self-focusing effect of light beams at the output end of the hollow annular core optical fiber.
3. The improved flow cytometer based on optical fiber integrated microfluidic chip as described in claim 1, wherein: the optical fiber integrated microfluidic chip comprises a cell flow guide pipe, a hollow annular core optical fiber and two scattered light collecting optical fibers.
4. The improved flow cytometer based on optical fiber integrated microfluidic chip as described in claim 1, wherein: the two scattered light collecting optical fibers are positioned on two sides of the output end of the hollow annular core optical fiber and form an angle of 90 degrees with the hollow annular core optical fiber, and the two optical fibers are positioned on the same straight line of the microfluidic chip. The two scattered light collecting optical fibers are large-numerical aperture and large-core diameter optical fibers.
5. The improved flow cytometer based on optical fiber integrated microfluidic chip as described in claim 1, wherein: the photoelectric detection system comprises a light splitting module and a photoelectric detection module, wherein the light splitting module consists of a plurality of dichromatic mirrors and is used for splitting the collected scattered light and transmitting the split light to the photoelectric detection module, the photoelectric detection module consists of a plurality of photoelectric detectors, and the used photoelectric detectors can be single photon detectors, photomultiplier tubes and other photoelectric detectors.
6. The improved flow cytometer based on optical fiber integrated microfluidic chip as described in claim 1, wherein: the excitation light source can be a single-wavelength laser light source or a plurality of light sources with different wavelengths, and is coupled into the hollow annular core optical fiber through the optical fiber wavelength division multiplexer for transmission.
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Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN114137654A (en) * | 2021-11-12 | 2022-03-04 | 中国工程物理研究院激光聚变研究中心 | Grating preparation method and grating preparation monitoring system for annular waveguide fiber |
Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4702598A (en) * | 1985-02-25 | 1987-10-27 | Research Corporation | Flow cytometer |
| CN2821565Y (en) * | 2005-06-19 | 2006-09-27 | 中国海洋大学 | Single cell algae flow type analysis microflow control chip |
| TW201319627A (en) * | 2011-11-09 | 2013-05-16 | Univ Nat Taiwan | Optical head |
| CN103191791A (en) * | 2013-03-01 | 2013-07-10 | 东南大学 | Integrated chip system for high-throughput sorting and counting detection of biological particles, and application |
| KR20190023438A (en) * | 2017-08-29 | 2019-03-08 | 피엠씨씨 주식회사 | Flow cytometry using optical fiber |
-
2020
- 2020-09-07 CN CN202010931452.7A patent/CN112229780A/en active Pending
Patent Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4702598A (en) * | 1985-02-25 | 1987-10-27 | Research Corporation | Flow cytometer |
| CN2821565Y (en) * | 2005-06-19 | 2006-09-27 | 中国海洋大学 | Single cell algae flow type analysis microflow control chip |
| TW201319627A (en) * | 2011-11-09 | 2013-05-16 | Univ Nat Taiwan | Optical head |
| CN103191791A (en) * | 2013-03-01 | 2013-07-10 | 东南大学 | Integrated chip system for high-throughput sorting and counting detection of biological particles, and application |
| KR20190023438A (en) * | 2017-08-29 | 2019-03-08 | 피엠씨씨 주식회사 | Flow cytometry using optical fiber |
Non-Patent Citations (1)
| Title |
|---|
| 叶晓兰等: "小型微流控芯片流式细胞仪的研制", 《分析化学》 * |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN114137654A (en) * | 2021-11-12 | 2022-03-04 | 中国工程物理研究院激光聚变研究中心 | Grating preparation method and grating preparation monitoring system for annular waveguide fiber |
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