CN201295224Y - Multi-mode confocal imaging device - Google Patents
Multi-mode confocal imaging device Download PDFInfo
- Publication number
- CN201295224Y CN201295224Y CNU2008201550140U CN200820155014U CN201295224Y CN 201295224 Y CN201295224 Y CN 201295224Y CN U2008201550140 U CNU2008201550140 U CN U2008201550140U CN 200820155014 U CN200820155014 U CN 200820155014U CN 201295224 Y CN201295224 Y CN 201295224Y
- Authority
- CN
- China
- Prior art keywords
- light path
- dichroic beamsplitter
- object lens
- imaging
- signal harvester
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Fee Related
Links
Images
Landscapes
- Investigating, Analyzing Materials By Fluorescence Or Luminescence (AREA)
Abstract
The utility model discloses a multi-mode confocal imaging device, which comprises a reflected signal acquisition device and a fluorescence signal acquisition device; the two devices share optical paths of a first dichroic spectroscope, a scanning mirror and an objective; and the respective detection optical path of the first dichroic spectroscope, the scanning mirror and the objective comprises a filter plate, a lens, a confocal pinhole and a photoelectric detector, wherein, the photoelectric detector is connected with an imaging computer system. As the signals are collected from the same time point and the same location point by two sets of confocal systems; and meanwhile, the optical design is adopted to avoid mutual interference between a multi-path laser and a detection system. Therefore, the real-time and non-invasive three dimensional detection of the biological tissue can be completed.
Description
Technical field
This utility model also relates to a kind of device of optical imagery, relates in particular to a kind of device that utilizes reflection and fluorescence to carry out the imaging of multi-mode confocal optics.
Background technology
Formerly technology [1] (referring to Opt.Photonics News, P.Daucatas, 18,2007, the reflected light of the confocal reflective imaging device utilization tissue that pp.28-33) is proposed carries out imaging.Because reflected signal is the refractive index sensitivity only, therefore can not realize the selective imaging of specific biological molecules.
Formerly technology [2] (referring to J.Microsc., A.L.Carlson et al., 228,2007, described in pp.11-24) is confocal reflection and fluorescent dual module formula formation method.Its ultimate principle is by switched laser wavelength and different filtering systems, respectively tissue is carried out confocal catoptric imaging and confocal fluorescent imaging.Because these two kinds of patterns are not to gather simultaneously, therefore two kinds of resulting information of pattern can't directly be compared by the histokinesis of breathing, heart beating brings.
Functional imaging refers to the imaging pattern that is used to analyze its biochemical function by the Biochemical Information of extracting biological tissue.Structural imaging refers to and utilizes tissue biological's physical characteristic, extracts tissue reflection of light, scattering isostructuralism signal are used for imaging of tissue.At present, adopt the burnt reflected signal of copolymerization to extract melanin and keratin information, and utilize fluorescence signal to extract biological metabolism information to have obtained preliminary study.
In the multi-modal imaging of biological tissue, a very big problem is influence how to avoid histokinesis to cause, extracts multimode information and it is stacked up in organizing micro-process.Existing technology formerly all can not reach above purpose.
The utility model content
Technical problem to be solved in the utility model provides the imaging of a kind of multi-mode reflection-fluorescent confocal and carries out with method and the device thereof of putting multi-modal imaging, this method and device can focus on multi-modal imaging the combination of three-dimensional imaging technology together, utilize the real-time noinvasive of method of optics ground that biological tissue is carried out three-dimensional and detect.
This utility model is to solve the problems of the technologies described above to adopt following technical scheme:
A kind of multi-mode co-focusing imaging device, this device comprise reflected signal harvester and fluorescence signal harvester,
Wherein the reflected signal harvester comprises first LASER Light Source, prism polarizer, quarter-wave plate, first dichroic beamsplitter, scanning mirror and the object lens that are provided with along the light path order, be sequentially set with first filter plate, first lens, the burnt pin hole of first copolymerization and first photodetector on the reflected light path of the light path of being returned by object lens of prism polarizer, this first photodetector is connected with the imaging computer system;
This device also is provided with the fluorescence signal harvester simultaneously, and the public above-mentioned light path of fluorescence signal harvester and reflected signal harvester from first dichroic beamsplitter to object lens, it comprises: along second LASER Light Source of light path order setting, second dichroic beamsplitter, first dichroic beamsplitter, scanning mirror and object lens, second dichroic beamsplitter is arranged at the optical routing object lens and returns on the reflected light path of first dichroic beamsplitter, on the reflected light path of the light path of returning by object lens of second dichroic beamsplitter, be sequentially set with second filter plate, second lens, the burnt pin hole of second copolymerization and second photodetector, this second photodetector is connected with the imaging computer system.
Said apparatus has used the multichannel exciting light simultaneously, and its common focus point is overlapped in tissue, adopts optical design to avoid interfering with each other of multi-path laser and detection system simultaneously; Like this, because two cover confocal system collections is signal from same time point and location point, so the displacement of biological tissue is consistent to two cover systems, promptly do not have relative displacement.Since different mode simultaneously, with point focusing in sample, therefore the motion of tissue can not influence the coupling of two kinds of pattern measuring-signals, the image information that obtains like this is exactly the multi-modal imaging that has structure and function information simultaneously; Thereby finish the three-dimensional of carrying out biological tissue in real-time noinvasive ground and detect the influence that its histokinesis of having eliminated biological tissue fully brings the multi-modality imaging binding analysis.
Description of drawings
For above-mentioned purpose of the present utility model, feature and advantage can be become apparent, below in conjunction with accompanying drawing the specific embodiment of the present utility model is elaborated, wherein:
Fig. 1 is the structural representation of this utility model multi-mode co-focusing imaging device.
Among the figure:
101. first LASER Light Source, 102. prism polarizer, 103. quarter-wave plates
104. first dichroic beamsplitter, 105. scanning mirrors, 106. object lens
107. target sample 108. first filter plates 109. first lens
110. burnt pin hole 111. first photodetectors of first copolymerization 113. computer systems
201. second LASER Light Source, 202. second dichroic beamsplitters, 203. second optical filters
204. burnt pin hole 206. second photodetectors of second lens, 205. second copolymerization
The specific embodiment
Accompanying drawing 1 shows a kind of multi-mode co-focusing imaging device, and this device comprises that this device comprises reflected signal harvester and fluorescence signal harvester,
Wherein the reflected signal harvester comprises first LASER Light Source 101 that is provided with along the light path order, prism polarizer 102, quarter-wave plate 103, first dichroic beamsplitter 104, scanning mirror 105 and object lens 106, second dichroic beamsplitter 202 is arranged at optical routing object lens 106 and returns on the reflected light path of first dichroic beamsplitter 104, on the reflected light path of the light path of returning by object lens 106 of prism polarizer 102, be sequentially set with first filter plate 108, first lens 109, the burnt pin hole 110 of first copolymerization and first photodetector 111, this first photodetector 111 is connected with imaging computer system 113;
This device also is provided with the fluorescence signal harvester simultaneously, and the public above-mentioned light path of fluorescence signal harvester and reflected signal harvester from first dichroic beamsplitter 104 to object lens 106, it comprises: along second LASER Light Source 201 of light path order setting, second dichroic beamsplitter 202, first dichroic beamsplitter 104, scanning mirror 105 and object lens 106, on the reflected light path of the light path of returning by object lens 106 of second dichroic beamsplitter 202, be sequentially set with second filter plate 203, second lens 204, the burnt pin hole 205 of second copolymerization and second photodetector 206, this second photodetector 206 is connected with imaging computer system 113.
At first, the LASER Light Source 101 that the burnt exciting light of reflective copolymerization adopts is near-infrared 808nm, through prism polarizer (Glan-Taylor prism) 102 partially after, through quarter-wave plate 103, transfer line polarized light to circularly polarized light, formed circularly polarized light sees through first dichroic beamsplitter 104, arrives a pair of inspection streaming confocal scanning mirror 105.Scanning mirror reflects light to object lens 106, and is converged to focus by object lens, shines on the sample 107; Scanning mirror 105 and object lens 106 are finished horizontal and vertical the moving that detects optical focus respectively by computer system 113 controls.
The refractive index of biological sample does not match and has caused the reflection of sample to signal, is collected by object lens 106 through the signal of sample reflection, is seeing through first dichroic beamsplitter, 104 back arrival quarter-wave plates 103.Because reflected light has kept circular polarization, therefore behind the process wave plate, become the polarization states that become 90 degree with incident illumination.This polarized light is reflected through behind prism 102, arrives on first filter plate (plated film wave plate) 108, and this wave plate is a band pass filter, only can make 808nm laser by and have the height of OD5 to absorb to other light especially 375nm laser.
After focusing on through first lens 109 again, the burnt pin hole 110 of aperture first copolymerization that single mode fiber system is used as confocal system.Through behind the optical fiber, utilize first photodetector (PMT photo-detector) 111 to survey its intensity at reflected signal, and 113 imagings of input computer system;
The laser instrument 201 of acquisition function signal is a 375nm laser instrument, is used to excite biological tissue's autofluorescence.Laser is reflexed on the inspection streaming scanning mirror 105 by first dichroic beamsplitter 104 by behind the second dichroic filter plate 202.By adjusting the direction of laser instrument, can guarantee the light path conjugation of two laser instrument.
Collected by object lens 106 from the fluorescence that sample excitation goes out, by first, second dichroic beamsplitter 104,202 reflections.By 400-500nm second wave filter (band filter) 203, but 375nm laser that filtering reflects and 800nm laser are only surveyed the fluorescence signal of 400-500nm.Equally, burnt pin hole 204 of aperture first copolymerization that single mode fiber system is used as confocal system.Through behind the optical fiber, utilize second photodetector (PMT photo-detector) 205 to survey its intensity at reflected signal, and 113 imagings of input computer system;
Import computer after the signals collecting of above-mentioned dual mode simultaneously, imaging processing just can obtain the superimposed image of the multimode information of same same time of target sample simultaneously, detects thereby finish the three-dimensional of carrying out biological tissue in real-time noinvasive ground.
Claims (1)
1. multi-mode co-focusing imaging device, it is characterized in that: this device comprises reflected signal harvester and fluorescence signal harvester,
Wherein the reflected signal harvester comprises first LASER Light Source, prism polarizer, quarter-wave plate, first dichroic beamsplitter, scanning mirror and the object lens that are provided with along the light path order, be sequentially set with first filter plate, first lens, the burnt pin hole of first copolymerization and first photodetector on the reflected light path of the light path of being returned by object lens of prism polarizer, this first photodetector is connected with the imaging computer system;
This device also is provided with the fluorescence signal harvester simultaneously, and the public above-mentioned light path of fluorescence signal harvester and reflected signal harvester from first dichroic beamsplitter to object lens, it comprises: along second LASER Light Source of light path order setting, second dichroic beamsplitter, first dichroic beamsplitter, scanning mirror and object lens, second dichroic beamsplitter is arranged at the optical routing object lens and returns on the reflected light path of first dichroic beamsplitter, on the reflected light path of the light path of returning by object lens of second dichroic beamsplitter, be sequentially set with second filter plate, second lens, the burnt pin hole of second copolymerization and second photodetector, this second photodetector is connected with the imaging computer system.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CNU2008201550140U CN201295224Y (en) | 2008-11-07 | 2008-11-07 | Multi-mode confocal imaging device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CNU2008201550140U CN201295224Y (en) | 2008-11-07 | 2008-11-07 | Multi-mode confocal imaging device |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN201295224Y true CN201295224Y (en) | 2009-08-26 |
Family
ID=41041182
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CNU2008201550140U Expired - Fee Related CN201295224Y (en) | 2008-11-07 | 2008-11-07 | Multi-mode confocal imaging device |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN201295224Y (en) |
Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101919686A (en) * | 2010-09-21 | 2010-12-22 | 华中科技大学 | Multi-mode imaging system for observing cerebral cortex functions of moving animals |
| CN102297854A (en) * | 2011-05-23 | 2011-12-28 | 公安部第一研究所 | High-efficiency multi-mode laser-induced fluorescence optical path exciting system |
| CN107037048A (en) * | 2016-09-28 | 2017-08-11 | 华中科技大学 | Imaging device, method and the imaging system of reflected signal and fluorescence signal are obtained simultaneously |
| CN108375560A (en) * | 2017-10-25 | 2018-08-07 | 南京大学 | A kind of laser co-focusing-two-photon-goes up changing multi state fluoroscopic imaging systems and its application |
| CN109288489A (en) * | 2018-10-17 | 2019-02-01 | 中国科学院苏州生物医学工程技术研究所 | A kind of imaging scope |
-
2008
- 2008-11-07 CN CNU2008201550140U patent/CN201295224Y/en not_active Expired - Fee Related
Cited By (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101919686A (en) * | 2010-09-21 | 2010-12-22 | 华中科技大学 | Multi-mode imaging system for observing cerebral cortex functions of moving animals |
| CN102297854A (en) * | 2011-05-23 | 2011-12-28 | 公安部第一研究所 | High-efficiency multi-mode laser-induced fluorescence optical path exciting system |
| CN107037048A (en) * | 2016-09-28 | 2017-08-11 | 华中科技大学 | Imaging device, method and the imaging system of reflected signal and fluorescence signal are obtained simultaneously |
| CN107037048B (en) * | 2016-09-28 | 2019-08-20 | 华中科技大学 | Imaging device, method and the imaging system of reflection signal and fluorescence signal are obtained simultaneously |
| CN108375560A (en) * | 2017-10-25 | 2018-08-07 | 南京大学 | A kind of laser co-focusing-two-photon-goes up changing multi state fluoroscopic imaging systems and its application |
| CN109288489A (en) * | 2018-10-17 | 2019-02-01 | 中国科学院苏州生物医学工程技术研究所 | A kind of imaging scope |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN101401722B (en) | Multi-mode co-focusing imaging method and apparatus | |
| CN100498421C (en) | Optical coherence tomography system using microlens or microprism array for scanning | |
| CN201295224Y (en) | Multi-mode confocal imaging device | |
| CN101869466B (en) | Confocal scanning and optical coherence tomograph based on self-adaptive optical technology | |
| CN201110835Y (en) | Laser scattering detection device for large-caliber neodymium glass surface defects | |
| CN109839732B (en) | Cage structure laser scanning confocal microscopic imaging system and method | |
| CN106290284A (en) | The two-photon fluorescence microscopic system of Structured Illumination and method | |
| CN103499562B (en) | Confocal laser optical tweezers Raman spectroscopy test device capable of being used in upright and inverted manners | |
| CN101135653A (en) | Laser scattering detection system for optical plane surface defects | |
| CN110367941A (en) | A kind of detection light fusion Noncontact optoacoustic-optical coherence tomography double-mode imaging system | |
| CN206757171U (en) | Novel multiple angle doughnut-like optical illuminates micro imaging system | |
| CN110118726A (en) | A kind of method and apparatus of parallel detecting fluorescent emission difference micro-imaging | |
| CN102735670B (en) | Double pinhole based super-resolution microscopy method and device | |
| JP6241858B2 (en) | Confocal microscope | |
| CN101904737A (en) | Living body fluorescent endoscopic spectrum imaging device | |
| CN103940796A (en) | Novel multi-angle and multi-mode quick switching circular optical illumination microscopic imaging system | |
| US20140218794A1 (en) | Confocal Fluorescence Microscope | |
| CN202568206U (en) | Retina three-dimensional imaging device | |
| CN113267252A (en) | Staring type confocal microscopic morphology spectrum four-dimensional detection system | |
| CN105510347A (en) | Optical material defect real-time imaging apparatus based on photothermal detection and optical microscopy | |
| CN112924389A (en) | Multi-mode imaging system and method based on photoacoustic and optical coherence tomography technology | |
| CN108982443A (en) | Two area's fluorescent scanning micro imaging system of near-infrared of multiphoton excitation | |
| CN116256377A (en) | Dark field confocal microscopic measurement device and method based on circular dichroism | |
| CN209542943U (en) | A kind of cage construction laser scanning co-focusing micro imaging system | |
| CN114353947A (en) | micro-Raman spectrometer based on light field imaging |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| CF01 | Termination of patent right due to non-payment of annual fee |
Granted publication date: 20090826 Termination date: 20171107 |
|
| CF01 | Termination of patent right due to non-payment of annual fee |