CN1268289C - Longitudinal scanning method and device in optical image system of coherent faults - Google Patents
Longitudinal scanning method and device in optical image system of coherent faults Download PDFInfo
- Publication number
- CN1268289C CN1268289C CN 200310110838 CN200310110838A CN1268289C CN 1268289 C CN1268289 C CN 1268289C CN 200310110838 CN200310110838 CN 200310110838 CN 200310110838 A CN200310110838 A CN 200310110838A CN 1268289 C CN1268289 C CN 1268289C
- Authority
- CN
- China
- Prior art keywords
- prism
- prism group
- optical fiber
- movable
- group
- 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
- 239000013307 optical fiber Substances 0.000 claims abstract description 45
- 238000012014 optical coherence tomography Methods 0.000 claims abstract description 38
- 238000000034 method Methods 0.000 claims abstract description 21
- 238000006073 displacement reaction Methods 0.000 claims abstract description 15
- 230000003068 static effect Effects 0.000 claims abstract 5
- 239000000835 fiber Substances 0.000 claims description 16
- 230000033001 locomotion Effects 0.000 claims description 7
- 230000003287 optical effect Effects 0.000 abstract description 18
- 238000003754 machining Methods 0.000 abstract description 7
- 239000006185 dispersion Substances 0.000 abstract description 5
- 238000003672 processing method Methods 0.000 abstract description 5
- 230000002349 favourable effect Effects 0.000 abstract 1
- 238000003384 imaging method Methods 0.000 description 15
- 238000012545 processing Methods 0.000 description 14
- 229910052573 porcelain Inorganic materials 0.000 description 11
- 238000005516 engineering process Methods 0.000 description 10
- 230000011514 reflex Effects 0.000 description 8
- 238000005481 NMR spectroscopy Methods 0.000 description 5
- 230000005540 biological transmission Effects 0.000 description 3
- 239000000919 ceramic Substances 0.000 description 3
- 238000003745 diagnosis Methods 0.000 description 3
- 239000011248 coating agent Substances 0.000 description 2
- 238000000576 coating method Methods 0.000 description 2
- 230000008878 coupling Effects 0.000 description 2
- 238000010168 coupling process Methods 0.000 description 2
- 238000005859 coupling reaction Methods 0.000 description 2
- 238000011161 development Methods 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 239000003292 glue Substances 0.000 description 2
- 238000004519 manufacturing process Methods 0.000 description 2
- 238000011160 research Methods 0.000 description 2
- 230000004044 response Effects 0.000 description 2
- 238000003325 tomography Methods 0.000 description 2
- 102000001554 Hemoglobins Human genes 0.000 description 1
- 108010054147 Hemoglobins Proteins 0.000 description 1
- 206010028980 Neoplasm Diseases 0.000 description 1
- 208000017442 Retinal disease Diseases 0.000 description 1
- 238000001574 biopsy Methods 0.000 description 1
- 210000004556 brain Anatomy 0.000 description 1
- 201000011510 cancer Diseases 0.000 description 1
- 238000003759 clinical diagnosis Methods 0.000 description 1
- 238000002591 computed tomography Methods 0.000 description 1
- 238000013170 computed tomography imaging Methods 0.000 description 1
- 239000013078 crystal Substances 0.000 description 1
- 230000007547 defect Effects 0.000 description 1
- 230000002950 deficient Effects 0.000 description 1
- 238000013461 design Methods 0.000 description 1
- 230000001627 detrimental effect Effects 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 201000010099 disease Diseases 0.000 description 1
- 208000037265 diseases, disorders, signs and symptoms Diseases 0.000 description 1
- 230000005684 electric field Effects 0.000 description 1
- 239000012467 final product Substances 0.000 description 1
- 238000010438 heat treatment Methods 0.000 description 1
- 208000015181 infectious disease Diseases 0.000 description 1
- 238000002329 infrared spectrum Methods 0.000 description 1
- 208000032839 leukemia Diseases 0.000 description 1
- 238000005259 measurement Methods 0.000 description 1
- 230000007096 poisonous effect Effects 0.000 description 1
- 230000010287 polarization Effects 0.000 description 1
- 238000011084 recovery Methods 0.000 description 1
- 238000002310 reflectometry Methods 0.000 description 1
- 238000013519 translation Methods 0.000 description 1
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 1
Images
Landscapes
- Investigating Or Analysing Materials By Optical Means (AREA)
Abstract
The present invention relates to a longitudinal scanning method and a device in an optical coherence tomography (OCT) system. The method adopts a prism system which is composed of a movable prism group and a static prism group to be used in a longitudinal scanning device; moreover, the movable prism group can be driven by a micro-displacement device to realize linear longitudinal scanning with high speed and high accuracy. The device comprises a light source, an optical fiber, an optical fiber coupler, a lens, the prism system, the micro-displacement device, etc., wherein the prism system is composed of the movable prism group and the static prism group which are respectively composed of a plurality of small reflecting type prisms, plane reflectors and light holes. The present invention has the advantages of compact and simple structure, favorable symmetry and high speed scanning. A traditional optical element processing method can be used to process prisms so that machining accuracy is high, and an angle error of the prisms can be controlled within 1 DEG. The present invention adopts reflecting devices and can avoid errors brought by luminous beam chromatic dispersion.
Description
One, technical field
The present invention relates to the optical coherence tomography technology, particularly relate to optical coherence tomography system high speed longitudinal scanning method and device thereof.
Two, background technology
The comparatively sophisticated tomography technology of development mainly contains three kinds now: computed tomography imaging (Computedtomography), ultra sonic imaging (Ultrasonic imaging) and NMR (Nuclear Magnetic Resonance)-imaging (Nuclear magneticresonance).These three kinds of technology respectively have characteristics, such as when it is used for human body and checks to aspect the infringement of human body, though diagnosis has reduced many with the dosage of X ray in these years, exist less detrimental effect but still have many data to show, may increase human infection some diseases such as cancer, leukemia and cataractous probability.Yet most data show that all magnetic field strong relatively in used now ultrasonic diagnosis dosage or the nuclear magnetic resonance, NMR is without any poisonous effect.But these three kinds of tomography technologies can't satisfy scientific research and the clinical diagnosis requirement (resolution of these three kinds of faultage images is about about 100 μ m～1mm) to real-time, Noninvasive and high-resolution imaging fully.
1991 the Massachusetts Institute of Technology (MIT) yellow David people such as (David Huang) principle of low-coherent light reflectometer (Low-coherence reflectometry) and confocal microscope is applied in the biomedical fault imaging field, optical coherence tomography (Optical Coherence Tomography) has been proposed, in this ten years development, optical coherence tomography (OCT) is with advantage such as its not damaged imaging, imaging resolution height, system structure be simple, cheap and enjoy attracting attention of science and engineering research person.
Optical coherence tomography (OCT) can be applied in many fields that there is potential defect in other imaging technique, provides reference data in particular for meticulous surgical operation.For example, in the operation of brain section, traditional tissue biopsy is breakneck, and other imaging technique has brought a lot of limitation owing to resolution is too low; And for example, need the imaging technique of micron dimension to the diagnosis of early stage retinal diseases, so far, also not than optical coherence tomography (OCT) imaging technique more suitably.
The ultimate principle of optical coherence tomography (OCT) is the rear orientation light that makes the organism to be measured on the signal arm by the optical fiber type Michelson interferometer, interfere with the reference light that is reflected by total reflective mirror on the reference arm, detect the information that this interference signal can obtain organism to be measured.Wherein realize scanning to organism depth direction to be measured by the reference arm total reflective mirror along the back and forth movement of optical axis direction, i.e. longitudinal scanning is by realizing the transversal scanning to organism to be measured along the vertical direction movable signal of optical axis arm.Because light source uses low-coherence light source, its coherence length is short, so the difference of the length of reference arm and signal arm just can interfere phenomenon in coherence length the time, and therefore, the longitudinal resolution of organism imaging to be measured depends on the coherence length l of light
c:
Wherein, λ
0Be centre wavelength, Δ λ is the bandwidth (Bandwidth FWHM) of light source.Because optical signal comes and goes, so the imaging longitudinal resolution is l
cHalf.As, use centre wavelength to be 830nm, when bandwidth was the superluminescent diode (SLD) of 25nm, the longitudinal resolution of imaging was 12 μ m, if use image-recovery technique resolution can be risen to micron even sub-micrometer scale.
Critical component in optical coherence tomography (OCT) system can be classified as three parts: light source, interferometer and scanning means.
Light source must satisfy three primary conditions: near infrared spectrum, short-phase dry length, high irradiance.Because during light frequency higher (blue light or higher), average scattering length is shorter, so optical coherence tomography (OCT) needs the long wave light source, but at 2 μ m or longer wave band, the absorptance of water increases, and therefore can only select the wave band of wavelength below 1.8 μ m.On the other hand, if wavelength is short more, resolution is high more, accordingly, if wavelength increases, for keeping same resolution, the bandwidth of light source must increase with the trend of 2 powers, therefore, select light source for convenience, should select the shortwave light source as far as possible, yet because hemoglobin is bigger at the following absorptance of 700nm, and consider and generally optical source wavelength is chosen in the relation of scattering length near the 850nm.
Interferometer is based on the structure of Michelson interferometer, common optical coherence tomography (OCT) system all uses optical fiber structure, though connecting, optical fiber makes that light path is flexible, it is a lot of to have simplified, but also brought the restriction of system effectiveness, because what use is wideband light source, so CHROMATIC DISPERSION IN FIBER OPTICS will make longitudinal resolution reduce greatly.
The longitudinal scanning speed of scanning means and resolution are in status of equal importance in optical coherence tomography (OCT).For high-resolution imaging system, the minute movement of organism to be measured just may cause the fuzzy of image, therefore has only the scanning speed of raising just can overcome this disadvantage.Existing longitudinal scanning technology probably is divided into following 6 kinds:
1, the step motor drive reflecting mirror is realized scanning.Advantage: linear, control convenience, cheap; Shortcoming: speed is slow, positioning accuracy is poor when moving back and forth.
2, realize scanning with piezoquartz.Advantage: at a high speed, approximately linear, control be convenient, cheap; Shortcoming: displacement is less, crystal is frangible.
3, stretching optical fiber is realized scanning.Advantage: simple in structure, control convenience, cheap; Shortcoming: non-linear, light polarization changes.
4, realize scanning with rotary prism.Advantage: at a high speed, control is convenient, cheap; Shortcoming: non-linear, dutycycle is low, light beam has chromatic dispersion by prism.
5, optical delay line is realized scanning.Advantage: at a high speed, approximately linear; Shortcoming: certain dutycycle, complex structure are arranged.
6, realize scanning with the spiral mirror.Advantage: at a high speed, linear, simple in structure, reflection-type; Shortcoming: machining accuracy is difficult to guarantee.
As can be seen, these longitudinal scanning technology respectively have its pluses and minuses, and wherein the step motor drive reflecting mirror realizes that scanning is the longitudinal scanning technology of the first generation, is replaced by other multiple technologies.
Optical delay line realizes that longitudinal scanning is the more method of using at present, and its structure is comparatively complicated, and is to realize longitudinal scanning by the angle swinging of galvanometer, therefore, can only be on low-angle approximately linear.
Realize that with the spiral mirror longitudinal scanning has at a high speed, advantage such as linear, simple for structure, owing to be the element of direct reflection-type, so light beam do not have chromatic dispersion problem, just can't use traditional method for manufacturing optical element, so have to adopt mechanical processing tools.Because its structural characteristics are necessary for its required machining tool of configuration separately, and are difficult to polish required optical surface, promptly are difficult to reach the precision of micron dimension.
Utilize the electrostriction effect of piezoelectric ceramics, can realize the micrometric displacement of sub-micrometer scale positioning accuracy and nanometer scale resolution, though also there is sluggish shortcoming, but owing to the reason of sluggishness is the dielectric constant of medium and relevant the causing of variation history of electric field intensity, if therefore adopt the method for direct control electrode intensity, under open loop situations, can effectively solve the hysteresis phenomenon of piezoelectric ceramics, also can realize that closed loop control solves the hysteresis phenomenon of piezoelectric ceramics by increasing micro-displacement sensor.But existing piezoelectric/electrostrictive porcelain can only be realized the displacement from several microns to more than 100 microns, its displacement is less, for example utilizes piezoelectric/electrostrictive porcelain to drive reflecting mirror and all can not satisfy the requirement that needs in optical coherence tomography (OCT) system reach 2mm to the 3mm longitudinal scanning degree of depth.
Three, summary of the invention
Purpose of the present invention is just in order to overcome the existing defective of above-mentioned existing longitudinal scanning technology, provide a kind of in the optical coherence tomography system method and the device thereof of longitudinal scanning, having solved existing micro positioner drives reflecting mirror and can not satisfy the requirement that needs in the optical coherence tomography system reach 2mm to the 3mm longitudinal scanning degree of depth, and can directly utilize the required optical prism of high-precision traditional optical element processing method processing, thereby realize the linear scanning of high-speed, high precision, and then improve the accuracy of measuring.
The objective of the invention is to be achieved through the following technical solutions:
The method of longitudinal scanning in the optical coherence tomography of the present invention system, adopt a kind of prism system that constitutes by movable prism group and stationary prism group, the longitudinal scan device that is used for optical coherence tomography of the present invention system, utilize the movable prism group in the micro positioner driving prism system again, realize the longitudinal scanning of high-speed, high precision by the translational motion of high accuracy micro positioners such as piezoelectric/electrostrictive porcelain.
Longitudinal scan device in the optical coherence tomography of the present invention system, include light source, optical fiber, fiber coupler, lens, data collecting system, components and parts such as data terminal, light source is connected with optical fiber, optical fiber is connected with fiber coupler, fiber coupler is connected with two optical fiber respectively again, the light that promptly passes through fiber coupler is divided into two-beam and enters two optical fiber respectively, the light beam that one optical fiber is drawn enters two lens and realizes arriving organism to be measured again after collimation and the focusing, also comprise a prism system that constitutes by stationary prism group and movable prism group and in order to drive the micro positioner of movable prism group according to the said device of the present invention, the stationary prism group places the rear of collimation lens, movable prism group in the prism system is fixed on the micro positioner, and placing stationary prism group rear, movable prism group and stationary prism group must be used in pairing.
Movable prism group in this device prism system and stationary prism group are made of a plurality of little reflection-type prisms, plane mirror and light hole respectively again.The structure of prism system has difference with movable prism group and stationary prism group structural parameters different.The concrete structure parameter of movable prism group and stationary prism group comprises: the prismatical length of each little reflection-type, width and height; The length of prism group and width; The prismatical number of little reflection-type of prism group length direction; The prismatical number of little reflection-type of prism group width; The position of light hole; The position whether plane mirror and plane mirror are arranged.
The present invention compared with prior art has following advantage:
1, the prism system of the present invention's employing is assembled by many little reflection-type prisms, therefore can use traditional method for manufacturing optical element processing prism, its machining accuracy height, the prism angular error can be controlled in 1 " in.
2, the present invention uses high accuracy micro positioner such as piezoelectric/electrostrictive porcelain to drive movable prism group in the prism system, because piezoelectric/electrostrictive porcelain has very high response speed (tens microseconds), just because of its response speed is fast, the speed that its electromechanical Coupling is carried out is also just very fast, have little time and heat exchange with outside, therefore there is not heating problem, can reaches at a high speed, not have the longitudinal scanning that machinery rubs, do not have noise simultaneously.
3, the piezoelectric/electrostrictive porcelain micro positioner that uses of the present invention, its volume is generally very little, is used with prism system of the present invention, has compact conformation, advantage that volume is little.
4, movable prism group simple in structure in the prism system that adopts of the present invention, symmetry is good, has therefore reduced the unstable factor in the motion, and then improves certainty of measurement.
5, the prism system of the present invention's employing is a kind of total reflection element, has avoided chromatic dispersion problem.
Four, description of drawings
Fig. 1 is the connection diagram that prism system of the present invention is used for the optical coherence tomography system.
Fig. 2 be in the prism system of the present invention with the paired structural representation of Fig. 3 with the movable prism group in 4 * 4 zones.
Fig. 3 is the structural representation that has the stationary prism group in 4 * 4 zones in the prism system of the present invention.
Fig. 4 be in the prism system of the present invention with the paired structural representation of Fig. 5 with the movable prism group in 6 * 6 zones.
Fig. 5 is the structural representation that has the stationary prism group in 6 * 6 zones in the prism system of the present invention.
Fig. 6 be in the prism system of the present invention with the paired structural representation of Fig. 7 with the movable prism group in 4 * 4 zones.
Fig. 7 is the structural representation that has 4 * 4 zones in the prism system of the present invention and comprise the stationary prism group of two light holes.
Fig. 8 is the two-dimentional equivalent index path that the present invention uses prism system.
Five, the specific embodiment
Below in conjunction with accompanying drawing, the present invention is further illustrated by embodiment.But content of the present invention is not limited only to content related among the embodiment.
Longitudinal scanning method in the optical coherence tomography of the present invention system, the prism system that employing is made of movable prism group 112 and stationary prism group 111, the longitudinal scan device that is used for the optical coherence tomography system, utilize the movable prism group 112 in the piezoelectric/electrostrictive porcelain micro positioner 113 driving prism systems again, realize the linear longitudinal scanning of high-speed, high precision by the translational motion of piezoelectric/electrostrictive porcelain micro positioner 113.
With reference to Fig. 1, longitudinal scan device in the optical coherence tomography of the present invention system, include light source 11, optical fiber 12,14,15, fiber coupler 13, lens 16,17, data collecting system 115, data terminal 116 components and parts such as grade, light source 11 is connected with optical fiber 12, optical fiber 12 is connected with fiber coupler 13, fiber coupler 13 is connected with optical fiber 15 with optical fiber 14 respectively again, the light that promptly passes through fiber coupler is divided into two-beam and enters optical fiber 14 and optical fiber 15 respectively, the light beam of drawing by optical fiber 14 enter lens 16 and lens 17 realize collimation and focus on after again to organism 18 to be measured, also comprise a prism system that constitutes by movable prism group 112 and stationary prism group 111 according to the said device of the present invention, and in order to drive the piezoelectric/electrostrictive porcelain micro positioner 113 of movable prism group 112, the light beam of being drawn by optical fiber 15 enters collimating lens 110, stationary prism group 111 places the rear of collimating lens 110, movable prism group 112 is fixed on the micro positioner 113, and placing stationary prism group rear, movable prism group and stationary prism group must be used in pairing.
The process that realizes scanning is: the light beam coupling of sending from light source 11 is to optical fiber 12, and light beam enters 2 * 2 fiber couplers 13 through behind the optical fiber 12, is divided into two bundles then and enters optical fiber 14 and optical fiber 15 respectively.
The first bundle light is through optical fiber 14 transmission back scioptics 16 collimations, focus on the organism 18 to be measured through lens 17 again, be transferred to lens 16 focusing after the rear orientation light of organism 18 to be measured is collected by lens 17 again and be coupled into optical fiber 14, enter 2 * 2 fiber couplers 13 by optical fiber 14 again, and be transferred to detector 114.Wherein move the integral body of forming by optical fiber 14, lens 16 and lens 17 19 and realize transversal scanning organism 18 to be measured by the direction of arrow among the figure.
The second bundle light passes through collimating lens 110 collimations through optical fiber 15 transmission backs, enter the stationary prism group 111 of prism system again, stationary prism group 111 by prism system and movable prism group 112 come back reflective after, again by stationary prism group 111 outgoing in the prism system, the light beam of outgoing is still collected by collimating lens 110, and be coupled in the optical fiber 15, be transferred to detector 114 by 2 * 2 fiber couplers 13 again.Wherein realize longitudinal scanning by the movable prism group 112 in the direction of arrow translation prism system among the figure by piezoelectric/electrostrictive porcelain 113.
Detector 114 is converted to the signal of telecommunication with the interference light signal of this two-beam and enters data collecting system 115, enters data terminal 116 at last and handles and draw faultage image.
The structure of the prism system of the present invention's design has difference with the difference of structural parameters, Fig. 2, Fig. 3, Fig. 4, Fig. 5, Fig. 6, Fig. 7 are exactly the movable prism group under the different structure parameter and the structure of stationary prism group, the representative of the part of black has plated reflectance coating among the figure, white line above the black part is the boost line of doing for outstanding three dimensional structure, does not have any physical significance; The light hole of reflectance coating is not plated in the white portion representative, and the black line above the white portion is the boost line of doing for outstanding three dimensional structure, does not have any physical significance.
The concrete structure parameter of prism system comprises: the prismatical length d of each little reflection-type
i, width d '
iWith height h
i(wherein the i subscript is represented the prismatical numbering of each little reflection-type); The length l of prism group and width w; The prismatical number N of little reflection-type of prism group length direction
lThe prismatical number N of little reflection-type of prism group width
wThe position of light hole; The position whether plane mirror and plane mirror are arranged.
Can select as required with the different example description architecture parameters of Fig. 2, Fig. 3, Fig. 4, Fig. 5, Fig. 6, Fig. 7 below.
Fig. 2 is the movable prism group that is used with Fig. 3, Fig. 3 is the stationary prism group, the two prisms group all can be considered 4 * 4 zones, a little reflection-type prism or plane mirror both can have been placed in each zone, also can be used as light hole, wherein each regional length and width are prismatical length of each little reflection-type and width, are d
i=d '
i=d (wherein the i subscript is represented the prismatical numbering of each little reflection-type), the prismatical height of each little reflection-type is h
i=d; Length l=the 4d of prism group, width w=4d; The prismatical number N of little reflection-type of prism group length direction
l=l/d=4; The prismatical number N of little reflection-type of prism group width
w=w/d=4; The position of light hole is 31 zones among Fig. 3, is the incident and the exit window of light beam; 316 zones of the position of plane mirror in Fig. 3.
Fig. 4 is the movable prism group that is used with Fig. 5, Fig. 5 is the stationary prism group, the two prisms group all can be considered 6 * 6 zones, a little reflection-type prism or plane mirror both can have been placed in each zone, also can be used as light hole, wherein each regional length and width are prismatical length of each little reflection-type and width, are d
i=d '
i=d (wherein the i subscript is represented the prismatical numbering of each little reflection-type), the prismatical height of each little reflection-type is h
i=d; Length l=the 6d of prism group, width w=6d; The prismatical number N of little reflection-type of prism group length direction
l=l/d=6; The prismatical number N of little reflection-type of prism group width
w=w/d=6; The position of light hole is 51 zones among Fig. 5, is the incident and the exit window of light beam; 536 zones of the position of plane mirror in Fig. 5.
Fig. 6 is the movable prism group that is used with Fig. 7, Fig. 7 is the stationary prism group, the two prisms group all can be considered 4 * 4 zones, a little reflection-type prism or plane mirror both can have been placed in each zone, also can be used as light hole, wherein each regional length and width are prismatical length of each little reflection-type and width, are d
i=d '
i=d (wherein the i subscript is represented the prismatical numbering of each little reflection-type), the prismatical height of each little reflection-type is h
i=d; Length l=the 4d of prism group, width w=4d; The prismatical number N of little reflection-type of prism group length direction
l=l/d=4; The prismatical number N of little reflection-type of prism group width
wThe position of=w/d=4 light hole is zone of 71 among Fig. 7 and 716 zones, is respectively the incident and the exit window of light beam; There is not plane mirror.
Among Fig. 8,, can derive the structural parameters value of the prism system that needs by the two-dimentional equivalent structure of movable prism group 112 and stationary prism group 111.For the convenience of element processing, select the prismatical length of each little reflection-type, width and highly equal, i.e. d here
i=d '
i=h
i=d.
After the light beam incident between movable prism group 112 and stationary prism group 111 multiple reflection, the plane mirror 83 by the stationary prism group makes light beam return along original optical path at last.When movable prism group 112 displacement x, the optical path difference of light beam is
Δl＝2NΔx (2)
Wherein N is the prismatical number of little reflection-type of movable prism group 112, the displacement Δ x of movable prism group 112 is by the displacement decision of micro positioner, use piezoelectric/electrostrictive porcelain as micro positioner, displacement can be taken at about Δ x=100 μ m usually, re-use N=16 prism, optical path difference will reach about Δ l=3.2mm so, can satisfy the requirement that needs in the optical coherence tomography system reach 2mm to the 3mm longitudinal scanning degree of depth fully.
Select the prismatical length of each little reflection-type, width and height d
i=d '
i=h
iDuring the value of=d, need to consider that the traditional optical element processing method can high accuracy process prismatical span, select d=10mm here.After the value, can see like this, the length l=N of the two-dimentional equivalent structure of movable prism group 112 * d=16 * 10=160mm, and width is a prismatical width w=d=10mm of little reflection-type.
Among Fig. 2, movable prism group 112 is three dimensional structures that the two-dimentional equivalent structure spatial arrangement with the movable prism group 112 shown in Fig. 8 becomes, this three dimensional structure can effectively reduce the size of prism group, improve the symmetry of element, little reflection-type prism number N=16 as movable prism group, the prismatical length of each little reflection-type is d=10mm, and three dimensional structure so shown in Figure 2 only need be got the prismatical number of little reflection-type of prism group length direction and the prismatical number of little reflection-type of prism group width equates N
l=N
w=4, just can realize the prismatical number N=N of little reflection-type
l* N
w=16, and the length of movable prism group and width are l=w=4d=40mm.
From length l=160mm, width w=10mm is integrated into length and width and equates to be the structure of l=w=40mm the three dimensional structure of the present invention's use with movable prism group like this.Simplifying for the stability that improves movable prism group vibration processes of this structure has important effect, and particularly movable prism group need be with the frequency vibration greater than 100Hz, and its symmetric raising will effectively improve the stability of motion so.
Now use Fig. 2, prism system shown in Figure 3 is described the transmission course of light beam in prism system, light beam is incided on the little reflection-type prism 21 of movable prism group by the light hole 31 of stationary prism group, reflex on the little reflection-type prism 22 through little reflection-type prism 21, light beam reflexes on the little reflection-type prism 32 of stationary prism group through little reflection-type prism 22, reflex to little reflection-type prism 33 again, reflex to the little reflection-type prism 23 of movable prism group again by little reflection-type prism 33, reflex to little reflection-type prism 24 again, reflex to the little reflection-type prism 34 of stationary prism group again, because little reflection-type prism 34 is different with the direction of little reflection-type prism 35, after light beam reflexes to little reflection-type prism 35 by little reflection-type prism 34, next that will reflex to movable prism group arranged on the prismatical little reflection-type prism 25, thereby repeat the reflection process of front, at last by the plane mirror 316 of stationary prism group with the light hole 31 its concrete reflection process of back outgoing of light beam when former road turns back to incident. are by the light hole in movable prism group and the stationary prism group, the numbering of little reflection-type prism and plane speculum is described as: 31 → 21 → 22 → 32 → 33 → 23 → 24 → 34 → 35 → 25 → 26 → 36 → 37 → 27 → 28 → 38 → 39 → 29 → 210 → 310 → 311 → 211 → 212 → 312 → 313 → 213 → 214 → 314 → 315 → 215 → 216 → 316 → 216 → 215 → 315 → 314 → 214 → 213 → 313 → 312 → 212 → 211 → 311 → 310 → 210 → 29 → 39 → 38 → 28 → 27 → 37 → 36 → 26 → 25 → 35 → 34 → 24 → 23 → 33 → 32 → 22 → 21 → 31.
Though the structure of movable prism group shown in Figure 2 is by N
i=N
w=4; d
i=d '
i=h
iThe little reflection-type prism gummed of 4 * 4=16 of=d=10mm forms, but when using the traditional optical element processing method to make, and it can be considered as 3 prisms and process and glue together.The prism of the 1st need processing is the prism of 10mm * 40mm of being combined by little reflection-type prism 21, little reflection-type prism 28, little reflection-type prism 29, little reflection-type prism 216; The prism of the 2nd need processing is the prism of 20mm * 40mm of being combined by little reflection-type prism 22, little reflection-type prism 27, little reflection-type prism 210, little reflection-type prism 215, little reflection-type prism 23, little reflection-type prism 26, little reflection-type prism 211, little reflection-type prism 214; The prism of the 3rd need processing is the prism of 10mm * 40mm of being combined by little reflection-type prism 24, little reflection-type prism 25, little reflection-type prism 212, little reflection-type prism 213.Wherein the prism of the 1st need processing is all the same with the prismatical shape and size of the 3rd need processing, but batch machining.
Though the structure of stationary prism group shown in Figure 3 is by N
l=N
w=4; d
i=d '
i=h
i4 * 4=16 of=d=10mm zone formed, 14 on little reflection-type prism is wherein arranged, 1 of 1 of plane mirror and light hole, but when using the traditional optical element processing method to make can be considered as it 8 prisms and 1 plane mirror and process and glue together.Wherein there are the prismatical shape and size of 6 need processing all the same, promptly little reflection-type prism 34; Little reflection-type prism 35; Little reflection-type prism 312; Little reflection-type prism 313; Little reflection-type prism 38; The shape and size of little reflection-type prism 39 are all the same, but batch machining; The prism of the 7th need processing is the prism of 10mm * 40mm of being combined by little reflection-type prism 32, little reflection-type prism 37, little reflection-type prism 310, little reflection-type prism 315; The prism of the 8th need processing is the prism of 10mm * 40mm of being combined by little reflection-type prism 33, little reflection-type prism 36, little reflection-type prism 311, little reflection-type prism 314, the prism of the 7th need processing is all the same with the prismatical shape and size of the 8th need processing, but batch machining.Reprocess a plane mirror that is of a size of 10mm * 10mm, be glued at regional 316 positions and get final product.
Claims (4)
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN 200310110838 CN1268289C (en) | 2003-11-03 | 2003-11-03 | Longitudinal scanning method and device in optical image system of coherent faults |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN 200310110838 CN1268289C (en) | 2003-11-03 | 2003-11-03 | Longitudinal scanning method and device in optical image system of coherent faults |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN1539376A CN1539376A (en) | 2004-10-27 |
| CN1268289C true CN1268289C (en) | 2006-08-09 |
Family
ID=34335758
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN 200310110838 Expired - Fee Related CN1268289C (en) | 2003-11-03 | 2003-11-03 | Longitudinal scanning method and device in optical image system of coherent faults |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN1268289C (en) |
Families Citing this family (9)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2010501877A (en) * | 2006-08-25 | 2010-01-21 | ザ ジェネラル ホスピタル コーポレイション | Apparatus and method for improving optical coherence tomography imaging capabilities using volumetric filtering techniques |
| JP5269809B2 (en) * | 2007-01-10 | 2013-08-21 | ライトラブ イメージング， インコーポレイテッド | Method and apparatus for optical coherence tomography using tunable light source |
| EP1962051A1 (en) * | 2007-02-21 | 2008-08-27 | Agfa HealthCare N.V. | System and method for optical coherence tomography |
| DE502007004384D1 (en) * | 2007-02-21 | 2010-08-26 | Agfa Healthcare Nv | System and method for optical coherence tomography |
| CN101199413B (en) * | 2007-12-21 | 2010-04-14 | 北京高光科技有限公司 | Optical coherence tomography method and equipment therefor |
| JP5645445B2 (en) * | 2009-05-22 | 2014-12-24 | キヤノン株式会社 | Imaging apparatus and imaging method |
| WO2013044932A1 (en) * | 2011-09-26 | 2013-04-04 | Wavelight Gmbh | Optical coherence tomography technique |
| CN106264579B (en) * | 2016-09-29 | 2023-03-17 | 四川大学 | Device capable of verifying influence of beam hardening on CBCT imaging quality |
| CN110954018A (en) * | 2019-11-25 | 2020-04-03 | 长春理工大学 | Optical coherence tomography scanning detection system |
-
2003
- 2003-11-03 CN CN 200310110838 patent/CN1268289C/en not_active Expired - Fee Related
Also Published As
| Publication number | Publication date |
|---|---|
| CN1539376A (en) | 2004-10-27 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US7555333B2 (en) | Integrated optical scanning image acquisition and display | |
| US8700134B2 (en) | Cantilever-based MEMS optical scanning apparatus, system and method | |
| US8526006B2 (en) | System and method for optical coherence tomography and method for calibrating said type of system | |
| Shin et al. | Fiber-optic confocal microscope using a MEMS scanner and miniature objective lens | |
| CN102428343B (en) | Optical tomography system with high-speed scanner | |
| US7616986B2 (en) | Optical fiber scanner for performing multimodal optical imaging | |
| CN100488440C (en) | Common channel type endoscopic optical coherent chromatography imaging method and system | |
| US8810797B2 (en) | System and method for optical coherence tomography | |
| US8330962B2 (en) | System and method for optical coherence tomography with modulated detector sensitivity | |
| US8665449B2 (en) | System and method for optical coherence tomography | |
| US8339610B2 (en) | System and method for optical coherence tomography with spectrally modulated light injected into optical fibre | |
| CN1639539A (en) | Apparatus for OCT Imaging with On-axis Focus for Improved Resolution and Depth of Field | |
| CN1268289C (en) | Longitudinal scanning method and device in optical image system of coherent faults | |
| CN1586402A (en) | Endoscopic optical tomographic imaging scanning probe device based on micro motor | |
| CN101617215A (en) | Systems and methods for optical coherence tomography | |
| CN104224117A (en) | Spectrally encoded confocal and optical coherence tomography cooperative imaging method and system | |
| CN208044186U (en) | Lighting device, pathological section imaging device based on white light linear light source and scanning system | |
| Pan et al. | A MEMS mirror-based confocal laser endomicroscope with image distortion correction | |
| CN209661612U (en) | Three-dimensional line scans micro-optical probe | |
| CN108852262A (en) | A kind of wide visual field Photoacoustic endoscope and imaging system for exempting from scanner | |
| CN101711666A (en) | Two-dimensional scan fiber optic probe for endoscopic optical coherence tomography | |
| CN101406391A (en) | OCT chromatography longitudinal scan device for measuring biological tissue | |
| CN110836869A (en) | An all-fiber high-speed optical coherence tomography scanning device | |
| CN205844575U (en) | A kind of big stroke height rate of scanning fibre delay line | |
| CN2682437Y (en) | Longitudinal scanning device in optical correlation fault imaging system |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| C06 | Publication | ||
| PB01 | Publication | ||
| 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 |