CN103033464B - Photoacoustic-fluorescence flow cytometer - Google Patents
Photoacoustic-fluorescence flow cytometer Download PDFInfo
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- CN103033464B CN103033464B CN201210574122.2A CN201210574122A CN103033464B CN 103033464 B CN103033464 B CN 103033464B CN 201210574122 A CN201210574122 A CN 201210574122A CN 103033464 B CN103033464 B CN 103033464B
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Abstract
The invention discloses a photoacoustic-fluorescence flow cytometer. The flow cytometer comprises an optical excitation system, a fluorescence signal receiving system, a photoacoustic signal receiving system, a sample platform and a computer display controlling system, wherein the optical excitation system is connected with the fluorescence signal receiving system, the sample platform and the computer display controlling system; the photoacoustic signal receiving system is connected with the sample platform and the computer display controlling system; the fluorescence signal receiving system is connected with the computer display controlling system; the computer display controlling system is electrically connected with the optical excitation system, the fluorescence signal receiving system and the photoacoustic signal receiving system. According to the flow cytometer, as a pulse laser is adopted as a single excitation light source, a photoacoustic signal and a fluorescence signal of a substance to be detected are excited simultaneously, and simultaneously acquired through an upper passage and a lower passage, the photoacoustic signal and the fluorescence signal are detected in real time, and more information about a single cell and granules is acquired.
Description
Technical field
The invention belongs to flow cytometer detection technical field, particularly a kind of Photoacoustic-fluoreflowce flowce cytometer and detection method thereof and application.
Background technology
Flow cytometry is the technology that the seventies grows up, it integrates computer technology, laser technology, fluid mechanics, cytochemistry, cellular immunology, have the function of analysis and sorting cells, this technology is a kind of detection means of unicellular or particle being carried out to quantitative test and sorting on functional level simultaneously.
At present, what FCM analysis method was the most frequently used is fluorescence flow cytometry art, it irradiates under flow at high speed state by the cell of fluorescent dyeing or particle with continuous laser, measure the intensity of its emitting fluorescence, thus reach a kind of cell analysis technology of cell or particle being carried out to qualitative or quantitative determination and analysis.Fluorescence flow cytometry instrument is widely used at present in the fields such as biomedicine, molecular biology.But owing to relying on the fluoroscopic examination of extrinsic fluorescence dyestuff, its method has some limitations: (1) cannot be detected dark matter (non-fluorescence material); (2) fluorescent dye may degrade with the physiological status change of cell, decompose or the phenomenon such as cancellation in cell, thus fluorescence cannot be detected and undetected.
When optoacoustic effect refers to that short light pulse irradiates certain absorber, absorber absorbs luminous energy and produces transient temperature rise, and temperature rise causes the volume dilational of absorber, thus gives off ultrasound wave.Optoacoustic effect produces the absorption coefficient of light depending on exciting light parameter and irradiation object, as long as there is the material of light absorption to be effectively converted into ultrasonic signal and to be detected, does not need to depend on fluorescent material.The such as non-fluorescence material of the band such as red blood cell endogenous pigment molecule, by photo-acoustic excitation, detects radiate ultrasonic and just can realize optoacoustic flow cytometer detection, and without the need to marking the fluorchrome of external source again.Therefore, by the methods combining that optoacoustic flow cytometer detection and fluorescence flow detect, utilize same light source to excite optoacoustic and fluorescence simultaneously, and detect the signal of two kinds of energy models simultaneously, just can realize the flow cytometer detection art of optoacoustic-fluorescent dual module state, effectively can make up the deficiency of fluorescence flow detection method, realize bimodal, multiparameter, complementary flow cytometer detection new technology.
Summary of the invention
Primary and foremost purpose of the present invention is that the shortcoming overcoming prior art is with not enough, provides a kind of Photoacoustic-fluoreflowce flowce cytometer.The advantage of this flow cytometer uses pulse laser as single excitation source, the simultaneously optoacoustic of excitation-detection material and fluorescence signal, then by upper and lower two paths, gather optoacoustic and the fluorescence signal of tested substance respectively simultaneously, realize two kinds of multi-functional flow cytometer detections of mode.
Another object of the present invention is to provide the detection method using above-mentioned Photoacoustic-fluoreflowce flowce cytometer.
Another object of the present invention is to provide the application of described Photoacoustic-fluoreflowce flowce cytometer.
Object of the present invention is achieved through the following technical solutions: a kind of Photoacoustic-fluoreflowce flowce cytometer, comprises optical excitation system, fluorescence signal receiving system, photoacoustic signal receiving system, sample stage and computing machine (PC) display control program; Optical excitation system is connected with fluorescence signal receiving system, sample stage, Computer display control system respectively, photoacoustic signal receiving system is connected with sample stage, Computer display control system respectively, and fluorescence signal receiving system is connected with Computer display control system; Computer display control system is electrically connected with optical excitation system, fluorescence signal receiving system, photoacoustic signal receiving system respectively;
Described optical excitation system comprises excitation source, diaphragm, cylindrical lens, slit A, achromat A, catoptron, dichroic beam splitter A and microcobjective; Excitation source and Computer display control system are electrically connected; Diaphragm, cylindrical lens, slit A, achromat A, catoptron, dichroic beam splitter A and microcobjective are mechanically connected successively; Microcobjective and described sample stage are mechanically connected; Optical excitation system device is all fixed in camera bellows, and diaphragm, cylindrical lens, slit A, achromat A all can move in camera bellows track, carries out optical shaping to output light;
Described camera bellows is the camera bellows covering whole light path;
Described fluorescence signal receiving system comprises the dichroic beam splitter B, optical filter, achromat B, slit B and the photomultiplier that are mechanically connected successively; Dichroic beam splitter B is arranged between catoptron and dichroic beam splitter A, and photomultiplier and Computer display control system are electrically connected;
Described fluorescence signal receiving system becomes confocal arrangement with optical excitation system, and the slit B namely in fluorescence signal receiving system and sample stage lay respectively in the focus of achromat B corresponding to front and microcobjective;
Described photoacoustic signal receiving system comprises the focus supersonic detector and amplifier that connect successively; Focus supersonic detector is connected with sample stage, and Amplifier And Computer display control program is electrically connected;
The optical focus of the microcobjective in the acoustic focus of described focus supersonic detector and optical excitation system is confocal;
Described excitation source is preferably short pulse excitation light source, and the effect of excitation source is exciting light acoustical signal and fluorescence signal; The excitation wavelength of described excitation source is preferably 400 ~ 2500nm, and pulse duration range is preferably 1 ~ 50ns, and repetition frequency is preferably 1Hz ~ 15KHz;
Preferred, the excitation wavelength of described excitation source is 532nm, and pulse duration range is 10ns, and repetition frequency is 15Hz;
The effect of described focus supersonic detector is to receive photoacoustic signal; The effect of described photomultiplier is to receive fluorescence signal;
Described Computer display control system is configured with binary channels parallel acquisition card and gathers control software design, and fluorescence signal and photoacoustic signal are by the card collection of binary channels parallel acquisition and be stored into gathering the computing machine of control software design;
Use above-mentioned Photoacoustic-fluoreflowce flowce cytometer to detect the detection method of cell or particle number, comprise the following steps:
(1) sample fixed placement is central at sample stage, microcobjective is placed on directly over sample, focus supersonic detector is placed in immediately below sample, fluorescence light-emitting window place that photomultiplier is placed in microcobjective oblique upper, photomultiplier transit tube outside camera bellows is closed;
(2) excitation source sends pulse laser, successively after diaphragm, cylindrical lens, slit A, achromat A, catoptron and microcobjective, forms a focal line hot spot and is across on detected sample, and vertical with the flow direction of sample; The size of focal line hot spot is preferably 5 μm × 60 μm;
(3) when sample flows through linear light spot region, produce optoacoustic and fluorescence signal due to exciting of laser simultaneously;
(4) fluorescence signal produced is received by photomultiplier after microcobjective, dichroic beam splitter B, optical filter, achromat B and slit B;
(5) photoacoustic signal produced is received by the focus supersonic detector below sample stage simultaneously;
(6) photoacoustic signal and fluorescence signal are respectively simultaneously by binary channels parallel acquisition card collection signal intensity and time waveform, after be stored in computing machine;
(7) to be collected complete after, by the signal analysis and processing of computing machine, obtain that optoacoustic flow cytometer detection and fluorescence flow in sample detect respectively by the cell of linear light spot or the counting of particle;
The receive mode of the fluorescence signal described in step (4) adopts reverse confocal receiving mode; The fluorescence that what described reverse confocal receiving mode referred to that photomultiplier receives is in excitation-emission light path, and photomultiplier becomes confocal conjugate relation with detected material, the slit namely before photomultiplier and sample are placed on respectively and receive with on the optical focus on excitation light path;
The receive mode of the photoacoustic signal described in step (5) adopts the confocal receiving mode of subtend; The confocal receiving mode of described subtend refers to that the microcobjective in optical excitation system and the focus supersonic detector in photoacoustic signal receiving system are in pairs to placement, and the optical focus of microcobjective overlaps with the acoustic focus of focus supersonic detector; Sample is adjusted on confocal point by sample stage and is realized confocal exciting and reception;
Described Photoacoustic-fluoreflowce flowce cytometer can be applicable to quantitative test and the monitoring of cell or particle.
Principle of work of the present invention: pulse laser can absorb luminous energy and produce photoacoustic signal or fluorescence signal by absorbate body, or produces optoacoustic and fluorescence signal simultaneously.By single excitation source, produce two kinds of signal modes simultaneously, and realize flow cytometer detection simultaneously, utilize the complementarity of optoacoustic and fluorescence signal to realize high detection efficiency.The present invention adopts and excites and receive photon excited, and photoacoustic signal and fluorescence signal divide upper and lower two passages simultaneously collected.Pulse laser becomes focal line hot spot after optical shaping, and this linear light spot respectively with focus supersonic detector and photomultiplier before linear slots be in confocal position, substantially increase the detection efficiency of photoacoustic signal and fluorescence signal.
The present invention has following advantage and effect relative to prior art:
(1) optoacoustic and fluorescence flow detection method combine by the present invention, produce optoacoustic and fluorescence signal under the excitation of single excitation source simultaneously, optics and the parameters,acoustic of detected material can be obtained simultaneously, realize the detection of the size of cell (or particle), density, number etc.
(2) Photoacoustic-fluoreflowce flowce cytometer of the present invention utilizes optoacoustic and fluorescence signal to provide complementary information, as dark matter can utilize its photoacoustic signal to analyze, makes up existing fluorescence flow and detects the problem depending on fluorochrome label.
(3) the present invention adopts and excites and receive photon excited, eliminates non-confocal signal, only accepts target place signal, improve systems axiol-ogy sensitivity.
Accompanying drawing explanation
Fig. 1 is the structural representation of the Photoacoustic-fluoreflowce flowce cytometer of embodiment 1, and wherein: 1 is excitation source, 2 is diaphragm, and 3 is cylindrical lens, 4 is slit A, and 5 is achromat A, and 6 is catoptron, 7 is dichroic beam splitter B, and 8 is optical filter, and 9 is achromat B, 10 is slit B, and 11 is photomultiplier, and 12 is dichroic beam splitter A, 13 is charge coupled cell, and 14 is microcobjective, and 15 is sample stage, 16 is focus supersonic detector, and 17 is amplifier, and 18 is Computer display control system.
Fig. 2 is the focal line hot spot figure of embodiment 1.
Fig. 3 is the photoacoustic signal figure of the cell that the fluorescent dye FITC of embodiment 2 marks, and wherein: (a) is photoacoustic signal figure, (b) is the partial enlarged drawing of photoacoustic signal figure.
Fig. 4 is the fluorescence signal figure of the cell that the fluorescent dye FITC of embodiment 2 marks, and wherein: (a) is fluorescence signal figure, (b) is the partial enlarged drawing of fluorescence signal figure.
Fig. 5 is the erythrocytic photoacoustic signal figure of embodiment 3.
Fig. 6 is the erythrocytic fluorescence signal figure of embodiment 3.
Embodiment
Below in conjunction with embodiment and accompanying drawing, the present invention is described in further detail, but embodiments of the present invention are not limited thereto.
Embodiment 1
A kind of Photoacoustic-fluoreflowce flowce cytometer, as shown in Figure 1, comprises optical excitation system, fluorescence signal receiving system, photoacoustic signal receiving system, sample stage and Computer display control system; Optical excitation system is connected with fluorescence signal receiving system, sample stage, Computer display control system respectively, photoacoustic signal receiving system is connected with sample stage, Computer display control system respectively, and fluorescence signal receiving system is connected with Computer display control system; Computer display control system is electrically connected with optical excitation system, fluorescence signal receiving system, photoacoustic signal receiving system respectively;
Described optical excitation system comprises excitation source 1, diaphragm 2, cylindrical lens 3, slit A4, achromat A5, catoptron 6, dichroic beam splitter A12 and microcobjective 14; Excitation source 1 and Computer display control system 18 are electrically connected; Diaphragm 2, cylindrical lens 3, slit A4, achromat A5, catoptron 6, dichroic beam splitter A12 and microcobjective 14 are mechanically connected successively; Microcobjective 14 and sample stage 15 are mechanically connected;
Described fluorescence signal receiving system comprises the dichroic beam splitter B7, optical filter 8, achromat B9, slit B10 and the photomultiplier 11 that connect successively; Dichroic beam splitter B7 is arranged between catoptron 6 and dichroic beam splitter A12, and photomultiplier 11 and Computer display control system 18 are mechanically connected;
Described photoacoustic signal receiving system comprises the focus supersonic detector 16 and amplifier (ZFL-500) 17 that are mechanically connected successively; Focus supersonic detector 16 and sample stage 15 are mechanically connected, and amplifier 17 and Computer display control system 18 are mechanically connected;
Described excitation source 1, diaphragm 2, cylindrical lens 3, slit A4, achromat A5, optical filter 8, achromat B9, slit B10 and photomultiplier 11 are fixed in camera bellows with strictly coaxial structure; Diaphragm 2, cylindrical lens 3, slit A4, achromat A5, achromat B9 and slit B10 can move in camera bellows track, carry out optical shaping to output light;
Described excitation source is short pulse excitation light source;
Described Computer display set-up of control system has binary channels parallel acquisition card and gathers control software design; Fluorescence signal and photoacoustic signal respectively simultaneously by binary channels parallel acquisition card collection signal intensity and time waveform, after be stored in computing machine;
The laser that excitation source 1 sends focuses on and forms line spot after cylindrical lens 3, again through slit A4, achromat A5, reflected by catoptron 6, then focus on through dichroic beam splitter A12 and microcobjective 14, be irradiated on sample, the size of focal beam spot is 5 μm × 60 μm, as shown in Figure 2; Linear light spot is across on detected sample, and vertical with the flow direction of sample, thus linear light spot can cover the xsect of whole sample, so can excited sample through all cells (particle) of this hot spot; The photoacoustic signal that cell (particle) produces is focused ultrasonic detector 16 and receives, the fluorescence signal produced is received by photomultiplier 11 after dichroic beam splitter B7, optical filter 8, achromat B9 and slit B10, two kinds of signals, respectively simultaneously by binary channels parallel acquisition card collection signal intensity and time waveform, are stored in computing machine and carry out aftertreatment.
Embodiment 2
Use the Photoacoustic-fluoreflowce flowce cytometer of embodiment 1 to detect the detection method of number of cells, comprise the following steps:
(1) rhodamine sample is placed in sample stage central authorities, microcobjective is placed on directly over sample stage, focus supersonic detector is placed in immediately below sample stage, fluorescence light-emitting window place that photomultiplier is placed in microcobjective oblique upper, photomultiplier transit tube outside camera bellows is closed;
(2) start Photoacoustic-fluoreflowce flowce cytometer, adopt Ti∶Sapphire laser pulsed laser as excitation source, Output of laser wavelength is 532nm, and pulsewidth is 10ns, and repetition frequency is 15Hz; By the pulse laser that above-mentioned laser instrument produces, focus on after cylindrical lens and form linear light spot, then reflected by catoptron after slit A, achromat A, be then focused to a focal beam spot through dichroic beam splitter A and microcobjective; The size of focal beam spot is 5 μm × 60 μm;
(3) mobile example platform, when rhodamine sample flows through linear light spot region, make rhodamine sample blur-free imaging on a display screen, and the focal beam spot making excitation light path be formed runs through corresponding rhodamine example cross section, wherein major axis crosses the diameter of rhodamine sample, and vertical with the flow direction of FITC labeled cell in rhodamine sample, when the cell of FITC mark in rhodamine sample is by focal beam spot, rhodamine sample will be inspired corresponding photoacoustic signal and fluorescence signal;
(4) fluorescence signal produced is received by photomultiplier after microcobjective, dichroic beam splitter B, optical filter, achromat B and slit B;
(5) photoacoustic signal produced is received by focus supersonic detector after ultrasonic coupling liquid;
(6) photoacoustic signal and fluorescence signal are respectively simultaneously by binary channels parallel acquisition card collection signal intensity and time waveform, after be stored in computing machine;
(7) to be collected complete after, by the signal analysis and processing program of computing machine, obtain the cell count by linear light spot that optoacoustic flow cytometer detection and fluorescence flow detection statistics go out respectively;
As shown in Figure 3, wherein: (a) is photoacoustic signal figure, (b) is the partial enlarged drawing of photoacoustic signal figure to the photoacoustic signal figure of the cell that fluorescent dye FITC marks; As shown in Figure 4, wherein: (a) is fluorescence signal figure, (b) is the partial enlarged drawing of fluorescence signal figure to the fluorescence signal figure of the cell that fluorescent dye FITC marks; Optoacoustic flow cytometer detection and fluorescence flow detection statistics can be realized by Fig. 3 and Fig. 4 this system known and go out cell count by linear light spot; Partial enlarged drawing can find out the number of the cell by linear light spot clearly.
Embodiment 3
Use the Photoacoustic-fluoreflowce flowce cytometer of embodiment 1 to detect the detection method of number of cells, comprise the following steps:
(1) mouse ear blood vessel is placed in sample stage central authorities; Microcobjective is placed on directly over sample stage, focus supersonic detector is placed in immediately below sample stage, fluorescence light-emitting window place that photomultiplier is placed in microcobjective oblique upper, photomultiplier transit tube outside camera bellows is closed;
(2) start Photoacoustic-fluoreflowce flowce cytometer, adopt Ti∶Sapphire laser pulsed laser as excitation source, Output of laser wavelength is 532nm, and pulsewidth is 10ns, and repetition frequency is 15Hz; By the pulse laser that above-mentioned laser instrument produces, focus on after cylindrical lens and form line spot, then reflected by catoptron after slit A, achromat A, be then focused to a focal beam spot through dichroic beam splitter A and object lens; The size of focal beam spot is 5 μm × 60 μm;
(3) mobile example platform, make mouse ear blood vessel blur-free imaging on a display screen, and the focal beam spot making excitation light path be formed is across corresponding blood vessel, wherein major axis is across the diameter of blood vessel, and it is vertical with the erythrocytic flow direction of Ink vessel transfusing, when red blood cell is by focal line hot spot, corresponding photoacoustic signal and fluorescence signal will be inspired;
(4) fluorescence signal produced is received by photomultiplier after microcobjective, dichroic beam splitter B, optical filter, achromat B and slit B;
(5) photoacoustic signal produced is received by focus supersonic detector after ultrasonic coupling liquid;
(6) photoacoustic signal and fluorescence signal are respectively simultaneously by binary channels parallel acquisition card collection signal intensity and time waveform, after be stored in computing machine;
(7) to be collected complete after, by the signal analysis and processing program of computing machine, obtain optoacoustic flow cytometer detection and fluorescence flow detection statistics respectively and go out cell count by linear light spot;
As shown in Figure 5, the erythrocytic fluorescence signal figure of mouse ear blood vessel as shown in Figure 6 for the erythrocytic photoacoustic signal figure of mouse ear blood vessel.Optoacoustic flow cytometer detection and fluorescence flow detection statistics can be realized by Fig. 5 and Fig. 6 this system known and go out cell count by linear light spot; Also embody the complementarity of optoacoustic flow cytometer detection and fluorescence flow detection simultaneously.
Above-described embodiment is the present invention's preferably embodiment; but embodiments of the present invention are not restricted to the described embodiments; change, the modification done under other any does not deviate from Spirit Essence of the present invention and principle, substitute, combine, simplify; all should be the substitute mode of equivalence, be included within protection scope of the present invention.
Claims (10)
1. a Photoacoustic-fluoreflowce flowce cytometer, is characterized in that comprising optical excitation system, fluorescence signal receiving system, photoacoustic signal receiving system, sample stage and Computer display control system; Optical excitation system is connected with fluorescence signal receiving system, sample stage, Computer display control system respectively, photoacoustic signal receiving system is connected with sample stage, Computer display control system respectively, and fluorescence signal receiving system is connected with Computer display control system; Computer display control system is electrically connected with optical excitation system, fluorescence signal receiving system, photoacoustic signal receiving system respectively;
Described optical excitation system comprises excitation source, diaphragm, cylindrical lens, slit A, achromat A, catoptron, dichroic beam splitter A and microcobjective; Excitation source and Computer display control system are electrically connected; Diaphragm, cylindrical lens, slit A, achromat A, catoptron, dichroic beam splitter A and microcobjective are mechanically connected successively; Microcobjective and described sample stage are mechanically connected;
Described fluorescence signal receiving system comprises the dichroic beam splitter B, optical filter, achromat B, slit B and the photomultiplier that are mechanically connected successively; Dichroic beam splitter B is arranged between catoptron and dichroic beam splitter A, and photomultiplier and Computer display control system are electrically connected;
Described photoacoustic signal receiving system comprises the focus supersonic detector and amplifier that connect successively; Focus supersonic detector is connected with sample stage, and Amplifier And Computer display control program is electrically connected;
The detection method of the Photoacoustic-fluoreflowce flowce cytometer described in utilization, comprises the following steps:
(1) sample fixed placement is central at sample stage, microcobjective is placed on directly over sample, focus supersonic detector is placed in immediately below sample, fluorescence light-emitting window place that photomultiplier is placed in microcobjective oblique upper, photomultiplier transit tube outside camera bellows is closed;
(2) excitation source sends pulse laser, successively after diaphragm, cylindrical lens, slit A, achromat A, catoptron and microcobjective, forms a focal line hot spot and is across on detected sample, and vertical with the flow direction of sample; The size of focal line hot spot is 5 μm × 60 μm;
(3) when sample flows through linear light spot region, produce optoacoustic and fluorescence signal due to exciting of laser simultaneously;
(4) fluorescence signal produced is received by photomultiplier after microcobjective, dichroic beam splitter B, optical filter, achromat B and slit B;
(5) photoacoustic signal produced is received by the focus supersonic detector below sample stage simultaneously;
(6) photoacoustic signal and fluorescence signal are respectively simultaneously by binary channels parallel acquisition card collection signal intensity and time waveform, after be stored in computing machine;
(7) to be collected complete after, by the signal analysis and processing of computing machine, obtain that optoacoustic flow cytometer detection and fluorescence flow in sample detect respectively by the cell of linear light spot or the counting of particle;
The receive mode of the fluorescence signal described in step (4) adopts reverse confocal receiving mode; The receive mode of the photoacoustic signal described in step (5) adopts the confocal receiving mode of subtend.
2. Photoacoustic-fluoreflowce flowce cytometer according to claim 1, is characterized in that: described optical excitation system device is all fixed in camera bellows, and diaphragm, cylindrical lens, slit A, achromat A can move in camera bellows track; Described camera bellows is the camera bellows covering whole light path.
3. Photoacoustic-fluoreflowce flowce cytometer according to claim 1, is characterized in that: described fluorescence signal receiving system becomes confocal arrangement with optical excitation system.
4. Photoacoustic-fluoreflowce flowce cytometer according to claim 3, is characterized in that: the slit B in described fluorescence signal receiving system and sample stage lay respectively in the focus of achromat B and microcobjective.
5. Photoacoustic-fluoreflowce flowce cytometer according to claim 1, is characterized in that: the optical focus of the microcobjective in the acoustic focus of described focus supersonic detector and optical excitation system is confocal.
6. Photoacoustic-fluoreflowce flowce cytometer according to claim 1, it is characterized in that: described excitation source is short pulse excitation light source, the excitation wavelength of described short pulse excitation light source is 400 ~ 2500nm, and pulse duration range is 1 ~ 50ns, and repetition frequency is 1Hz ~ 15KHz.
7. Photoacoustic-fluoreflowce flowce cytometer according to claim 6, is characterized in that: the excitation wavelength of described excitation source is 532nm, and pulse duration range is 10ns, and repetition frequency is 15Hz.
8. Photoacoustic-fluoreflowce flowce cytometer according to claim 1, is characterized in that: described Computer display control system is configured with binary channels parallel acquisition card and gathers control software design.
9. use the detection method of the Photoacoustic-fluoreflowce flowce cytometer described in any one of claim 1 ~ 8.
10. the application of the Photoacoustic-fluoreflowce flowce cytometer described in any one of claim 1 ~ 8, is characterized in that: described Photoacoustic-fluoreflowce flowce cytometer is applied to quantitative test and the monitoring of cell or particle.
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| CN104280327B (en) * | 2014-06-20 | 2017-01-04 | 博奥生物集团有限公司 | A kind of streaming phosphor collection optical system |
| CN104459975B (en) * | 2014-12-29 | 2016-08-24 | 中国科学院长春光学精密机械与物理研究所 | The micro-imaging optical system of imaging flow cytometer |
| CN105352931A (en) * | 2015-09-28 | 2016-02-24 | 周辉 | Multifunctional device and method for detecting tumor cells or other pathologic cells |
| CN108519329B (en) * | 2018-03-26 | 2021-01-15 | 华中科技大学 | Multi-channel scanning and detecting line confocal imaging device |
| CN112345502A (en) * | 2020-10-27 | 2021-02-09 | 天津市英贝特航天科技有限公司 | Detector for eliminating fluorescence noise in fluorescence immunoassay analyzer |
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| CN102087198A (en) * | 2010-11-18 | 2011-06-08 | 苏州生物医学工程技术研究所 | Flow cytometry |
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| CN101278829A (en) * | 2008-05-26 | 2008-10-08 | 上海理工大学 | Portable in vivo flow cytometry |
| CN102087198A (en) * | 2010-11-18 | 2011-06-08 | 苏州生物医学工程技术研究所 | Flow cytometry |
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