CN1170142C - High-speed optical interference chromatographic imaging apparats - Google Patents
High-speed optical interference chromatographic imaging apparats Download PDFInfo
- Publication number
- CN1170142C CN1170142C CNB021044570A CN02104457A CN1170142C CN 1170142 C CN1170142 C CN 1170142C CN B021044570 A CNB021044570 A CN B021044570A CN 02104457 A CN02104457 A CN 02104457A CN 1170142 C CN1170142 C CN 1170142C
- Authority
- CN
- China
- Prior art keywords
- interference
- photoelectric sensor
- imaging
- light
- semi
- 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
Landscapes
- Investigating Or Analysing Materials By Optical Means (AREA)
Abstract
The present invention relates to a microscopic imaging instrument, particularly to a medical interference microscopic imaging instrument. In order to solve the problems of low imaging speed, etc. in the prior art, the present invention has the technical scheme that a confocal structure is applied to a system, namely that an object to be imaged is on the focal line of an objective lens; a photoelectric sensor is on the focal line of an imaging objective lens, and the objective lens makes one-dimensional scanning in the axial direction or the radial direction; the object to be imaged can be on the focus of the objective lens, and the photoelectric sensor can be on the focus of the imaging objective lens; the objective lens adopts a cylindrical mirror, the photoelectric signal sensor adopts linear array CCD elements, and the light source adopts a laser device in the infrared wave band. The microscopic imaging instrument has the characteristics of high speed, small volume, simple structure, etc.
Description
Technical field
The present invention relates to a kind of microscopic imaging apparatus, especially relate to a kind of medical intervention microscopic imaging apparatus.
Background technology
Interference of light tomography (OCT, Optical Coherence Tomography) technology be first kind with relevant be the medical imaging technology of characteristic, its theoretical foundation is early stage white light interferometric method, originate from initial optical coherence domain reflectometry measurement technology (OCDR, Optical Coherence-Domain Reflectometry) as the network failure detection.OCDR is used to detect the flaw of optical cable originally, but people just recognize that it has the ability of surveying eyes and other biological tissue soon.The proposition first of OCT notion is in 1991, and the D.Huang of masschusetts, u.s.a Polytechnics and J.G.Fujimoto etc. adopt the OCT technology successfully to human eye retina's fine structure and arterial wall imaging.As the illustration of imaging in transparent, slight scattering medium and strong scattering medium, the optical fiber Michelson interferometer of 830nm SLD light source is used in this research, reaches the axial resolution of 10 μ m.1993, demonstrated the live body optical coherent chromatographic imaging of human retina.Nineteen ninety-five, the clinical research of beginning ophthalmology.During the decade short, OCT develops rapidly, on resolution and performance, be greatly improved, and expand out multiple imaging pattern thus, as Doppler OCT (ODT), Polarization-Sensitive type OCT (PS-OCT), spectrum OCT, Difference Absorption type OCT, with the OCT technology of two-photon fluorescence or combination of ultrasound, and in mode, realized fault imaging to the internal with the endoscope combination.These different modes be imaged as from the microcosmic tissues observed structure better, understanding its physiological function provides means.
Yet up to now, all there is a great shortcoming in existing OCT system: image taking speed is too slow.In these OCT systems, each constantly can only obtain a picture element, wishes to get a complete image, needs pointwise to finish the scanning of both direction.Because OCT system imaging resolution is high, in order to obtain high-resolution image, its sweep velocity is difficult to improve.
It as number of patent application 99240337.5 invention, adopted one group of replaceable combinations of pairs of forming by exciter filter, double color reflection mirror, inhibition filter, advantage such as make not only that system has kept original light path simplification, compact conformation, volume is little and with low cost, the system that also makes has realized the 3-D view test to various fluorescence and non-fluorescent samples; Another number of patent application is 99113633.0 invention, discloses a kind of self-align fiber-optic confocal scanning microscope that has, and comprises fiber-optic confocal scanning microscope and accurate confocal small field of view microscope.That is to say that a microscope of this invention has two kinds of microscopical functions, the function of existing microscan tomography, the function of imaging once promptly is to carry out self-align function to measuring target again.But these systems speed when realizing the microscan tomography is slower, especially when human body being carried out at the body real time imagery, because arteriocapillary vibrations make that imaging is difficult to realize.
Therefore, image taking speed is slow, just becomes important disadvantages of confocal scan microscope.Particularly be used for biomedicine in bulk measurement the time, image taking speed has seriously limited the application of interfering tomography apparatus slowly.
Summary of the invention
The objective of the invention is to overcome deficiency of the prior art, a kind of high speed OCT is provided system.
In order to overcome the deficiencies in the prior art, the technical solution used in the present invention is: interference of light tomography apparatus is by LASER Light Source, catoptron, object lens, semi-transparent semi-reflecting lens, imaging len, slit and photoelectric sensor constitute, after photoelectric sensor changes into data with the light signal of receiving, send data collector, entering computing machine handles, system adopts confocal arrangement, the object of promptly desiring imaging is on the focal line of object lens, photoelectric sensor is on the focal line of imaging len, the light beam that LASER Light Source is sent is through collimator objective, be split into the two-way light beam by semi-transparent semi-reflecting lens, the one tunnel through first catoptron 3, returns to second catoptron 2 again, pass through semi-transparent semi-reflecting lens, through imaging len, behind slit 8, pass through enlarging objective again; Another road light beam becomes a focal line through object lens in the internal focus of observed object body, after the object tissue reflection that is in focal line, be focused into a linear beam through object lens, semi-transparent semi-reflecting lens, imaging len again, behind slit, pass through enlarging objective again, above-mentioned two-way light beam interferes, and the interference signal of generation is received by photoelectric sensor, and described object lens are made one-dimensional scanning vertically or radially by additional control device control; The object of desiring imaging also can be on the focus of object lens; Photoelectric sensor also can be on the focus of imaging len; Described object lens adopt two gummed cylindrical mirrors; Described imaging len adopts two gummed cylindrical mirrors; Described photoelectric sensor adopts line array CCD device or other linear some array photoelectric sensor; Described LASER Light Source adopts the wideband laser of infrared band, also can adopt the wideband laser of visible light wave range (as red light).
The present invention can make the speed of OCT improve hundred times, can simplify the structure of confocal scan microscope simultaneously, reduces volume, has expanded the usable range of OCT widely.
Description of drawings
Fig. 1 is the system construction drawing of confocal scan microscope.
Wherein: the 1st, object lens; 2 and 3 is catoptrons; The 4th, semi-transparent semi-reflecting lens; The 5th, collimator objective; The 6th, LASER Light Source; The 7th, imaging len; The 8th, slit; The 9th, enlarging objective; The 10th, photoelectric sensor; The 11st, data collector; The 12nd, computing machine.
Embodiment
Below in conjunction with the drawings and specific embodiments the present invention is described in further detail:
Fig. 1 illustrates this system construction drawing.Wherein: the 1st, object lens; 2 and 3 is catoptrons; The 4th, semi-transparent semi-reflecting lens; The 5th, collimator objective; The 6th, LASER Light Source; The 7th, imaging len; The 8th, slit; The 9th, enlarging objective; The 10th, photoelectric sensor; The 11st, data collector; The 12nd, computing machine.
Principle of work of the present invention is as follows: LASER Light Source 6 is the laser instrument of near-infrared band, its broad band light beam that sends is extended to even, the parallel beam of 1 millimeter to several millimeters of diameter through collimator objective 5, be split into the two-way light beam through semi-transparent semi-reflecting lens 4: the one tunnel through catoptron 3, after returning to catoptron 2 again, by semi-transparent semi-reflecting lens 4, be focused into a linear beam through imaging len 7, behind slit 8, be imaged on the photoelectric sensor 10 by enlarging objective 9; Another road light beam becomes a focal line through object lens 1 in observed object internal focus, after the observed object reflection that is in focal line, pass through object lens 1, semi-transparent semi-reflecting lens 4 again, be focused into a linear beam through imaging len 7, behind slit 8, by enlarging objective imaging 9 on photoelectric sensor 10.When the optical path difference of two-way light beam less than interference of light apart from the time, photoelectric sensor 10 can receive the interference signal of two-way light beam.Because the pixel on the photoelectric sensor 10 has one-to-one relationship with the observed object that is in focal line, therefore, can obtain being in hundreds if not thousands of pixels of observed object of focal line this moment.Along with cylindrical mirror 1 and catoptron 2 move at directions X or Y direction, can obtain the high-definition picture of X-Z plane or Y-Z plane observing object soma.Owing to only need to do scanning motion, so this device can high speed imaging in a direction.The signal of photoelectric sensor 10 outputs is sent into computing machine 12 through data collector 11, through obtaining the tomographic map of observed object after the COMPUTER CALCULATION.
Claims (7)
1. interference of light tomography apparatus, its formation comprises: LASER Light Source, catoptron, object lens, semi-transparent semi-reflecting lens, imaging len, slit and photoelectric sensor, described photoelectric sensor send data collector after the light signal of receiving is changed into data, enters computing machine and handles; It is characterized in that, system adopts confocal arrangement, and the object of both having desired imaging is on the focal line of object lens, and photoelectric sensor is on the focal line of imaging len, the light beam that wideband laser sends is through collimator objective, be split into the two-way light beam by semi-transparent semi-reflecting lens, the one tunnel through first catoptron (3), return to second catoptron (2) again, pass through semi-transparent semi-reflecting lens, through imaging len, behind slit (8), pass through enlarging objective again; Another road light beam becomes a focal line through object lens in the internal focus of testee, after the object tissue reflection that is in focal line, be focused into a linear beam through object lens, semi-transparent semi-reflecting lens, imaging len again, behind slit, pass through enlarging objective again, above-mentioned two-way light beam interferes, and the interference signal of generation is received by photoelectric sensor, and described object lens are made one-dimensional scanning vertically or radially by additional control device control.
2. interference of light tomography apparatus according to claim 1 is characterized in that, system adopts confocal arrangement, and the object of desire imaging is on the focus of object lens.
3. interference of light tomography apparatus according to claim 1 is characterized in that, system adopts confocal arrangement, and photoelectric sensor is on the focus of imaging len.
4. interference of light tomography apparatus according to claim 1 is characterized in that: described object lens adopt two gummed cylindrical mirrors.
5. interference of light tomography apparatus according to claim 1 is characterized in that: described imaging len adopts two gummed cylindrical mirrors.
6. interference of light tomography apparatus according to claim 1 is characterized in that: described photoelectric sensor adopts the line array CCD device.
7. interference of light tomography apparatus according to claim 1 is characterized in that: described LASER Light Source adopts the wideband laser of infrared band.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CNB021044570A CN1170142C (en) | 2002-03-19 | 2002-03-19 | High-speed optical interference chromatographic imaging apparats |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CNB021044570A CN1170142C (en) | 2002-03-19 | 2002-03-19 | High-speed optical interference chromatographic imaging apparats |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN1369702A CN1369702A (en) | 2002-09-18 |
| CN1170142C true CN1170142C (en) | 2004-10-06 |
Family
ID=4740105
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CNB021044570A Expired - Fee Related CN1170142C (en) | 2002-03-19 | 2002-03-19 | High-speed optical interference chromatographic imaging apparats |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN1170142C (en) |
Families Citing this family (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6944322B2 (en) * | 2001-03-28 | 2005-09-13 | Visiongate, Inc. | Optical tomography of small objects using parallel ray illumination and post-specimen optical magnification |
| CN1321322C (en) * | 2004-08-30 | 2007-06-13 | 浙江大学 | Differential interference chromatography for measuring three dimension refractive index |
| CN101744607A (en) * | 2008-12-17 | 2010-06-23 | 中国科学院西安光学精密机械研究所 | Imaging system of compressed state light field |
| CN110854045A (en) * | 2019-11-20 | 2020-02-28 | 西北电子装备技术研究所(中国电子科技集团公司第二研究所) | Method for adjusting parallelism between chip sucker and substrate sucker by using collimation light path |
| CN111413070A (en) * | 2020-04-13 | 2020-07-14 | 蔚海光学仪器（上海）有限公司 | Brightness detection device and detection method thereof |
-
2002
- 2002-03-19 CN CNB021044570A patent/CN1170142C/en not_active Expired - Fee Related
Also Published As
| Publication number | Publication date |
|---|---|
| CN1369702A (en) | 2002-09-18 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN101869466B (en) | Confocal scanning and optical coherence tomograph based on self-adaptive optical technology | |
| JP3553451B2 (en) | Optical coherence tomographic observation system | |
| CN105147241B (en) | Method and system based on double space carrier frequency technique extension OCT image depth | |
| US5465147A (en) | Method and apparatus for acquiring images using a ccd detector array and no transverse scanner | |
| CN100455253C (en) | Endoscopic imaging system in bulk optics biopsy spectral coverage OCT | |
| CN101884524B (en) | Wide view field optical coherence tomographic instrument based on adaptive optical technology | |
| CN100488440C (en) | Common channel type endoscopic optical coherent chromatography imaging method and system | |
| CN101427911B (en) | Method and system for detecting ultra-broadband optical spectrum of ultrahigh-resolution spectrum field OCT | |
| CN108742511A (en) | Spectral coverage OCT and the confocal synchronous scanning system of line | |
| JP2002505434A (en) | Confocal microscope using multispectral coding | |
| CN201019719Y (en) | Spectrum region OCT endoscopic image pick-up device used for in situ optical biopsy | |
| CN102525406A (en) | Three-dimensional imaging device for retina | |
| CN104224117B (en) | It is a kind of optical spectrum encoded confocal imaging method and system to be cooperateed with optical coherence tomography | |
| CN102944521A (en) | Non-contact photoacoustic and optical coherence tomography dual-imaging device and detection method thereof | |
| CN202568206U (en) | Retina three-dimensional imaging device | |
| CN108784644A (en) | A kind of opticianry parameter measurement system | |
| CN102578993A (en) | Endoscopic OCT (optical coherence tomography) imaging apparatus and endoscopic OCT imaging method | |
| CN108567410A (en) | Optical coherence tomography and the confocal synchronous imaging system of spot scan | |
| CN110013212A (en) | Multi-parameter, multi-functional eyes measuring instrument based on optical coherence tomography | |
| CN100479737C (en) | Paralleled imaging method and system for common path type endoscopic OCT of hard tube model | |
| CN1170142C (en) | High-speed optical interference chromatographic imaging apparats | |
| CN209236115U (en) | Spectral coverage OCT and the confocal synchronous scanning system of line | |
| CN100346739C (en) | Real-time imaging optical coherent endoscope system | |
| WO2002084259A1 (en) | High-speed optical delay generating method by rotation reflector in optical coherence tomography and optical coherence tomography device | |
| CN111053531A (en) | Handheld oral angiography device and method based on sweep frequency optical coherence tomography |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C06 | Publication | ||
| PB01 | Publication | ||
| C10 | Entry into substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| C10 | Entry into substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| C14 | Grant of patent or utility model | ||
| GR01 | Patent grant | ||
| C19 | Lapse of patent right due to non-payment of the annual fee | ||
| CF01 | Termination of patent right due to non-payment of annual fee |