CN201101518Y - Common channel type endoscopic optical coherent chromatography imaging system - Google Patents
Common channel type endoscopic optical coherent chromatography imaging system Download PDFInfo
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- CN201101518Y CN201101518Y CNU200720111514XU CN200720111514U CN201101518Y CN 201101518 Y CN201101518 Y CN 201101518Y CN U200720111514X U CNU200720111514X U CN U200720111514XU CN 200720111514 U CN200720111514 U CN 200720111514U CN 201101518 Y CN201101518 Y CN 201101518Y
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Abstract
The utility model discloses a common-channel-type optical endoscopic coherence tomography imaging system. The light emitted from a broadband light source is connected with the port (a) of a first optical circulator, the light emitted from a port (b) reaches a sample through a first collimating lens, a two-dimensional scanning galvanometer, a microobjective, an optical fiber image-transmitting bundle and a Green lens, and the light returning to the port (b) is connected with the port (d) of a second optical circulator through the port (c) of the first optical circulator. The light emitted from the port (e) reaches a reflector arranged on an electric-control translational platform through a second collimating lens and a flat light-splitting sheet. The light returning to the port (e) is shot out from the port (f) of the second optical circulator and then reaches a linear array CCD detector through a third collimating lens, a diffraction grating and an imaging lens. The two-dimensional scanning galvanometer, the electric-control translational platform and the linear array CCD detector are all connected with a control system. Light circulators are adopted to improve the energy utilization rate of the system, and the spectral detection technology is adopted to increase the imaging speed. The imaging quality of the system is free from the environmental impact, the endoscopic sensor is convenient to be processed and installed and the energy utilization rate of the system is high.
Description
Technical field
This utility model relates to based endoscopic imaging technology and Optical Coherence Tomography Imaging Technology, especially relates to a kind of common channel type endoscopic optical coherent chromatography imaging system of spying upon head in the optical fiber image transmission beam conduct that adopts.
Background technology
Only carrying out pathological changes diagnosis according to the metamorphosis of tissue surface has very big subjectivity and limitation, and the faultage image of organization internal can provide more objective basis for doctor's diagnosis.Many chromatography imaging techniques as: Computerized chromatographic (CT), nuclear magnetic resonance, NMR (MRI), X ray, ultrasonic etc., are extensively applied to clinical diagnosis.Yet above-mentioned technology can only provide the resolution of 0.1～1mm, reaches the detection tissue abnormalities far away, the desired level of resolution of the mechanics of biological tissue during as early-stage cancer.
Optical coherent chromatographic imaging (Optical Coherence Tomography is called for short OCT) is a kind of emerging optical image technology, can non-invasively carry out visual observation to internal structure, physiological function and even the molecular information of biological tissue.It possesses the required high-resolution of histopathological analysis (reaching 1～20 μ m), can bring into play clinical function such as pathological changes early diagnosis, process monitoring and operation mediation.OCT also have fast, the radiationless damage of image taking speed, information diversification, moderate cost, with the compatible advantage such as good of existing Medical Instruments, be at present by extensive imaging tool good, that can on clinical medicine, play a significant role.Especially the OCT technology endoscopic OCT technology that combines with the based endoscopic imaging technology and form can be carried out imaging to the histoorgan of organism inside, has greatly expanded the utilization scope of OCT, can provide diagnosis basis more accurately for the doctor.Endoscopic OCT has obtained utilization at aspects such as gastronintestinal system, respiratory system, blood vessel imagings.
In existing endoscopic OCT system, (the Guillermo J.Tearney of Fujimoto group as U.S. MIT, et al., In vivo endoscopic optical biopsy with optical coherence tomography, Science, 276,2037～2039,1997), the Chen group of University of California (Tuqiang Xie, et al., Fiber-optic-bundle-based optical coherence tomography, Optics Letters, 30 (14), 1803～1805,2005) etc., generally as in spy upon head and pass on the optical fiber of optical device or the sample arm that optical fiber image transmission beam places interference structure.Because the inner-cavity structure of intracorporeal organ is very irregular, the optical fiber or the optical fiber image transmission beam that enter in it exist bending and twisted phenomena inevitably, cause changing by the polarization state of optical fiber or optical fiber image transmission beam transmitting beam, add the influence of the chromatic dispersion that causes by them, image quality is significantly descended.Therefore, must in reference arm, accurately mate, thereby make the formation of system and adjusting become complicated unusually above-mentioned factor.And, in spy upon each replacing of head, all need carry out the complex operations such as light path coupling, dispersion compensation and polarization state adjusting of big stroke range.
In addition, the reflected light of fibre bundle end face can form background signal on the detector image planes, is non-expectation light beam, must make it deflect away from image planes, so need optical fiber image transmission beam end surface grinding Cheng Yuqi axis is become the inclined-plane at 8 ° of inclination angles.When adopting Green lens (GRIN lens, when gradient-index lens) output beam being focused on, also need the mutually bonding face of Green lens and optical fiber image transmission beam also is processed into the inclined-plane at 8 ° of inclination angles, should accomplish when the two is bonding that the orientation is accurate, make that the processing of optical fiber image transmission beam and Green lens and mounting process are complicated.The existence of this angle, the light path that makes light beam be experienced when the diverse location transmission of optical fiber image transmission beam there are differences, and causes the interference signal intensity of whole image planes inhomogeneous.
Summary of the invention
In order to overcome disadvantages of background technology, the purpose of this utility model provides a kind of common channel type endoscopic optical coherent chromatography imaging system.This system as in spy upon the end face reflection light of optical fiber image transmission beam of head as reference light, it and transmit by same optical fiber image transmission beam from the flashlight of sample, constitute the interference structure road, that play the sensing effect altogether, the optical path difference between reference light and the flashlight is compensated by another common path interference structure.
The technical scheme that its technical problem that solves this utility model adopts is:
The light that wideband light source sends meets the first optical circulator port a, the light that sends by the first optical circulator port b successively through first collimating lens, two-dimensional scan galvanometer, microcobjective, optical fiber image transmission beam and Green lens to sample, the light that is back to port b meets the second optical circulator port d by the first optical circulator port c; The light that sends by the second optical circulator port e after second collimating lens, broadband beam split plain film to the reflecting mirror that is contained on the electronic control translation stage; The light that is back to port e by the second optical circulator port f outgoing after, successively through the 3rd collimating lens, diffraction grating, imaging len to the line array CCD detector; Two-dimensional scan galvanometer, electronic control translation stage and line array CCD detector all are connected with control system.
Described control system comprises image pick-up card, computer, functional generator and controllor for step-by-step motor, the line array CCD detector is through image acquisition clamping computer, computer output two paths of signals, one the tunnel connects the two-dimensional scan galvanometer through functional generator, and another road connects electronic control translation stage through controllor for step-by-step motor.
The described light that is sent by the first optical circulator port b behind first collimating lens, two-dimensional scan galvanometer, microcobjective, optical fiber image transmission beam and Green lens, connects corner cube prism to sample successively again.
The length of described optical fiber image transmission beam is greater than 1000mm, and two end faces are processed to the plane perpendicular with its axis, and front end face places on the focal plane of microcobjective.
The transmittance/reflectance of described broadband beam split plain film approaches 62/38.
Described reflecting mirror is the broadband high reflection mirror, is specially metal-dielectric film broadband high reflection mirror.
The photosurface of described line array CCD detector is positioned on the back focal plane of imaging len, and the groove direction of the length direction of photosurface and diffraction grating is perpendicular.
Between described first optical circulator and wideband light source, first collimating lens, second optical circulator, and between second optical circulator and second collimating lens, the 3rd collimating lens, connect with single-mode fiber.
Compare with background technology, the beneficial effect that the utlity model has is:
1, the utlity model has image quality characteristics little, simple to operate affected by environment: reference light and flashlight are by same optical fiber image transmission beam transmission, and the optical path difference between the two is by another common path interference structure compensation, and whole system is the common path interference structure.The chromatic dispersion of optical fiber image transmission beam, polarization state change, and factors such as variation of ambient temperature, vibration are little to the imaging results influence, need not to consider especially they are mated, and make the formation of system and adjusting become simply;
2, this utility model can be changed as required to use and spy upon head in different, and need not system is carried out complex operations such as chromatic dispersion coupling and polarization state adjusting, and the light path coupling that only need carry out little stroke range gets final product;
3, the utlity model has compact conformation, characteristics safe in utilization: the probe that enters the organism inner chamber only plays sensing, all operations all carries out in the probe outside, make the inner device usage quantity of probe be reduced to minimum, be convenient to realize the miniaturization of popping one's head in, thereby easilier enter various organs and carry out imaging; The inside of probe does not have any moving component and drive current, and system has very high safety in utilization;
4, spying upon the processing and the mounting process of head in this utility model makes oversimplifies: the reflected light of optical fiber image transmission beam rear end face is utilized as reference light, so needn't be processed into the inclined-plane at 8 ° of inclination angles to optical fiber image transmission beam and Green lens end face, installs also much easier;
5, the utlity model has the high characteristics of capacity usage ratio: the energy loss of two optical circulators of employing almost can be ignored, and the capacity usage ratio of system is higher than the OCT system that adopts the beam splitting device.
Description of drawings
Fig. 1 is a system schematic of the present utility model.
Fig. 2 for this utility model be used for the imaging of tract wall in spy upon a sketch map.
Fig. 3 is a control system sketch map of the present utility model.
Among the figure: 1. wideband light source, 2. first optical circulator, 3. first collimating lens, 4. two-dimensional scan galvanometer, 5. microcobjective, 6. optical fiber image transmission beam, 7. Green lens, 8. corner cube prism, 9. sample, 10. second optical circulator, 11. second collimating lens, 12. broadband beam split plain film, 13. reflecting mirrors, 14. electronic control translation stages, 15. the 3rd collimating lens, 16. diffraction grating, 17. imaging lens, 18. line array CCD detectors, 19. image pick-up card, 20. computer, 21. functional generators, 22. controllor for step-by-step motor.
The specific embodiment
Below in conjunction with drawings and Examples this utility model is further described:
The common channel type endoscopic optical coherent chromatography imaging system that the utility model proposes as shown in Figure 1, the light that wideband light source 1 sends meets first optical circulator, 2 port a, again by first optical circulator, 2 port b outgoing to the first collimating lens 3, the parallel incident two-dimensional scan galvanometer 4 in collimation back, light beam after the reflection is focused on back coupled into optical fibres coherent fiber bundle 6 by microcobjective 5, and light beam is divided into back reflected laser and transillumination when transferring to rear end face.Transillumination is focused on sample 9 by Green lens 7.The probe that uses among Fig. 1, can adopt and spy upon head in the side direction type when needs carry out imaging to the tract wall as spying upon head in the forward-type.
Spy upon head in the side direction type as shown in Figure 2, it is formed by the bonding again corner cube prism 8 of another side of the bonding Green lens 7 of the rear end face of optical fiber image transmission beam 6, Green lens 7.Use when spying upon in the side direction type, focused on the back, changed after the directions incident sample 9 from the side by corner cube prism 8 again by Green lens 7 by the light of optical fiber image transmission beam 6 rear end face transmissions.
In above-mentioned two kinds of forms, spy upon in front, two end faces of optical fiber image transmission beam 6 are processed to the plane perpendicular with its axis, and front end face places on the focal plane of microcobjective 5 to be collected into irradiating light beam, and rear end face is the plane of reference of interference system, it and sample 9 constitute one and approach interferometer common road, that play the sensing effect together.Because optical fiber image transmission beam 6 is not a single-mode fiber, with the various modes transmission, wherein the formed image of light beam that only transmits in the basic mode mode is only the true picture of sample to light beam therein.Along with the increase of optical fiber image transmission beam length, the image that forms by higher order mode and spatially can separate by the image that basic mode forms.When optical fiber image transmission beam length is about 1000mm, the image that is formed by higher order mode can deflect away from from show image planes fully, and only show the sample image that forms by basic mode, thereby guaranteed that imaging depth that system can reach this sample is not subjected to the influence of multimode transmission.Therefore, should make the length of optical fiber image transmission beam 6 greater than 1000mm.
By sample 9 reflection or backward scattered light with by the light of optical fiber image transmission beam 6 rear end faces reflection, after Yan Yuanlu turns back to first optical circulator 2, again by port c outgoing to the second optical circulator 10.By the light beam of second optical circulator, 10 port e outgoing by second collimating lens, 11 collimations after, parallel reflected light and the transillumination of being divided into when being incident to broadband beam split plain film 12.The parallel incidence reflection mirror 13 of transillumination, reflecting mirror 13 is fixed on the electronic control translation stage 14.The transmittance/reflectance of broadband beam split plain film 12 should approach 62/38, and the intensity of feasible two light beams that obtain after its beam splitting is complementary.For making system have high energy utilization rate, reflecting mirror 13 adopts broadband high reflectance minute surface, is specially metal-dielectric film broadband high reflection mirror.
After the light beam after 12 reflections of mirror 13 and broadband beam split plain film of being reflected turns back to second optical circulator 10 along former road, by port f outgoing to the three collimating lens 15, the parallel incident diffraction grating 16 in collimation back, the light beam that chromatic dispersion is come behind the diffraction is focused on the image planes of line array CCD detector 18 by imaging len 17.The perpendicular placement of groove direction of the image planes length direction of line array CCD detector 18 and diffraction grating 16.Between first optical circulator 2 and wideband light source 1, first collimating lens 3, second optical circulator 10, and between second optical circulator 10 and second collimating lens 11, the 3rd collimating lens 15, connect with single-mode fiber.Two-dimensional scan galvanometer 4, electronic control translation stage 14 and line array CCD detector 18 all are connected with control system.
Control system of the present utility model comprises image pick-up card 19, computer 20, functional generator 21 and controllor for step-by-step motor 22 as shown in Figure 3.Computer 20 carries out the interference signal collection by image pick-up card 19 control linear array ccd detectors 18, and the signal input computer 20 that collects is processed and displayed.Computer 20 output two path control signal: the one tunnel controls two-dimensional scan galvanometers 4 through functional generator 21 carries out transversal scanning, to realize the imaging to sample 9 diverse locations; One the tunnel through controllor for step-by-step motor 22 driving electronic control translation stages 14, be with reflecting mirror 13 to move axially by it, carry out the light path coupling between flashlight and the reference light, till best interference signal occurring, realized the optical path difference between flashlight and the reference light being compensated in the interior outside of spying upon head.
Line array CCD detector 18, image pick-up card 19 and functional generator 21 all can be bought from the market, and they are respectively as the AViiVA SM2CL line array CCD detector of U.S. Atmel company, the PCIe-1430 image pick-up card of America NI company and the DS345 type function generator of U.S. STANFORD RESEARCH SYSTEM company.Controllor for step-by-step motor 22 and electronic control translation stage 14 are auxiliary products, can buy together, as the TSA30-C electronic control translation stage and the SC3 controllor for step-by-step motor of Beijing Zolix Instrument Co., Ltd..
The common channel type endoscopic optical coherent chromatography imaging method that the utility model proposes, its concrete steps are as follows:
1) the electronic control translation stage band reflecting mirror and is moved axially, till best interference signal occurring;
2) gather interference signal by the line array CCD detector, obtain signal I (k) distribution of light intensity about wave number k, and through image pick-up card input computer;
3) by computer signal I (k) is carried out the one dimension inverse fourier transform along the spectral evolution direction, obtain signal I (z) distribution of light intensity about position z, I (z) is the image of sample along depth direction z;
4) computer is controlled the two-dimensional scan galvanometer along the continuous sweep of x direction by functional generator, to the difference of the each point on x direction execution in step 2) and 3), obtain the image of each point, can reconstruct the two dimensional image of sample along x direction and depth direction z by these images along depth direction z;
5) the two-dimensional scan galvanometer is along the continuous sweep of y direction, equal execution in step 4 during step pitch of every scanning) once, sample can be reconstructed the 3-D view of sample along the two dimensional image of x direction and depth direction z when obtaining corresponding each scanning step pitch respectively by these images.
The above-mentioned specific embodiment is used for this utility model of explaining; rather than this utility model limited; in the protection domain of spirit of the present utility model and claim, any modification and change to this utility model is made all fall into protection domain of the present utility model.
Claims (8)
1. common channel type endoscopic optical coherent chromatography imaging system, it is characterized in that: the light that wideband light source (1) sends meets first optical circulator (2) port a, the light that sends by first optical circulator (2) port b successively through first collimating lens (3), two-dimensional scan galvanometer (4), microcobjective (5), optical fiber image transmission beam (6) and Green lens (7) to sample (9), the light that is back to port b meets second optical circulator (10) port d by first optical circulator (2) port c; The light that sends by second optical circulator (10) port e after second collimating lens (11), broadband beam split plain film (12) to the reflecting mirror (13) that is contained on the electronic control translation stage (14); The light that is back to port e by second optical circulator (10) port f outgoing after, successively through the 3rd collimating lens (1 5), diffraction grating (16), imaging len (17) to line array CCD detector (18); Two-dimensional scan galvanometer (4), electronic control translation stage (14) and line array CCD detector (18) all are connected with control system.
2. common channel type endoscopic optical coherent chromatography imaging according to claim 1 system, it is characterized in that: described control system comprises image pick-up card (19), computer (20), functional generator (21) and controllor for step-by-step motor (22), line array CCD detector (18) connects computer (20) through image pick-up card (19), computer (20) output two paths of signals, one the tunnel connects two-dimensional scan galvanometer (4) through functional generator (21), and another road connects electronic control translation stage (14) through controllor for step-by-step motor (22).
3. common channel type endoscopic optical coherent chromatography imaging according to claim 1 system, it is characterized in that: the described light that is sent by first optical circulator (2) port b behind first collimating lens (3), two-dimensional scan galvanometer (4), microcobjective (5), optical fiber image transmission beam (6) and Green lens (7), connects corner cube prism (8) to sample (9) successively again.
4. common channel type endoscopic optical coherent chromatography imaging according to claim 1 system, it is characterized in that: the length of described optical fiber image transmission beam (6) is greater than 1000mm, two end faces are processed to the plane perpendicular with its axis, and front end face places on the focal plane of microcobjective (5).
5. common channel type endoscopic optical coherent chromatography imaging according to claim 1 system, it is characterized in that: the transmittance/reflectance of described broadband beam split plain film (12) approaches 62/38.
6. common channel type endoscopic optical coherent chromatography imaging according to claim 2 system, it is characterized in that: described reflecting mirror (13) is the broadband high reflection mirror, is specially metal-dielectric film broadband high reflection mirror.
7. common channel type endoscopic optical coherent chromatography imaging according to claim 1 system, it is characterized in that: the photosurface of described line array CCD detector (18) is positioned on the back focal plane of imaging len (17), and the groove direction of the length direction of photosurface and diffraction grating (16) is perpendicular.
8. common channel type endoscopic optical coherent chromatography imaging according to claim 1 system, it is characterized in that: between described first optical circulator (2) and wideband light source (1), first collimating lens (3), second optical circulator (10), and between second optical circulator (10) and second collimating lens (11), the 3rd collimating lens (15), connect with single-mode fiber.
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| Application Number | Priority Date | Filing Date | Title |
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| CNU200720111514XU CN201101518Y (en) | 2007-07-03 | 2007-07-03 | Common channel type endoscopic optical coherent chromatography imaging system |
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| CNU200720111514XU CN201101518Y (en) | 2007-07-03 | 2007-07-03 | Common channel type endoscopic optical coherent chromatography imaging system |
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Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101797146B (en) * | 2010-01-29 | 2011-09-14 | 浙江大学 | Scanning-free spectrum code-based endoscopic imaging method and system |
| CN102920438A (en) * | 2012-10-30 | 2013-02-13 | 电子科技大学 | High-resolution optical scanning holographic slice imaging method based on variable pupils |
| CN103190956A (en) * | 2013-02-27 | 2013-07-10 | 胡建明 | Laser therapeutic instrument based on OCT (optical coherence tomography) imaging system |
-
2007
- 2007-07-03 CN CNU200720111514XU patent/CN201101518Y/en not_active Expired - Lifetime
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101797146B (en) * | 2010-01-29 | 2011-09-14 | 浙江大学 | Scanning-free spectrum code-based endoscopic imaging method and system |
| CN102920438A (en) * | 2012-10-30 | 2013-02-13 | 电子科技大学 | High-resolution optical scanning holographic slice imaging method based on variable pupils |
| CN102920438B (en) * | 2012-10-30 | 2014-07-16 | 电子科技大学 | High-resolution optical scanning holographic slice imaging method based on variable pupils |
| CN103190956A (en) * | 2013-02-27 | 2013-07-10 | 胡建明 | Laser therapeutic instrument based on OCT (optical coherence tomography) imaging system |
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