CN108514404A - Optical coherence tomography system - Google Patents
Optical coherence tomography system Download PDFInfo
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- A61B5/0066—Optical coherence imaging
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- A61B5/0073—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence by tomography, i.e. reconstruction of 3D images from 2D projections
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- A—HUMAN NECESSITIES
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- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0075—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence by spectroscopy, i.e. measuring spectra, e.g. Raman spectroscopy, infrared absorption spectroscopy
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Abstract
The present invention relates to a kind of optical coherence tomography systems.The system includes light source, fiber coupler, reference arm, sample arm, signal acquisition module and signal processing module.Light source provides initial light；Initial light is divided into reference light and sample light by fiber coupler；The reflected light of reference light is transmitted back to fiber coupler by reference arm；Sample arm utilizes sample light detection sample to be tested, sample light to generate rear orientation light in sample to be tested and be transmitted back to fiber coupler；Rear orientation light interferes to form interference light with reflected light in fiber coupler；Interference light is divided into multipath interference spectrum by fiber coupler；Signal acquisition module acquires each interference spectrum respectively；Signal processing module generates the detection image of the sample to be tested according to the spectral line signal of each road interference spectrum.Above system can eliminate virtual image interference and optical signal noise interference, so that the imaging effect of above system is preferable.
Description
Technical field
The present invention relates to technical field of optical detection, more particularly to a kind of optical coherence tomography system.
Background technology
Means of optical coherence tomography (Optical CoherenceTomography, abbreviation OCT) is 90 years last century
The lossless optical detective technology that generation grows up.Optical signal delay and phase of the OCT based on optics low coherence interferometer become
Change measuring system, the back scattering and reflection signal for sample interior different depth are measured indirectly.OCT is according in sample
The different refractive index in portion (optical diffusion characteristic inside representative sample) generates the signal of different contrast, to realize to sample
Internal cross section is imaged.Since OCT image technology has non-radiative, non-contact, axial direction resolution ratio to test sample
Height, it is lossless, it is easy to interior and peeps integrated and moderate characteristic, thus be a kind of optical imaging tools of great future.Currently,
OCT technology has been widely used for the medical diagnostic fields such as ophthalmology, skin histology, intravascular sight glass, orthopaedics.OCT technology is in work
Industry application field is also gradually applied, such as drug coating, material thickness measure, the spraying of vehicle paint.
OCT technology is divided into time domain OCT according to the difference that it is delayed with phase measurement indirectly for sample scattering light, how general
Strangle OCT, frequency sweep OCT, spectrum OCT etc..Wherein, it is swept without using mechanical scanning component progress axial depth since spectrum OCT has
It retouches, the information by different level of sample axial direction can be directly obtained by the Fourier transform of spectrum, it is thus possible to greatly improve system
Image taking speed, and the noise for avoiding mechanical movement Scan Architecture from introducing.Meanwhile the hydrone of wavelength that spectrum OCT is used absorbs
It is minimum, thus in ophthalmic medical and diagnostic field, achieve great success.
However, traditional spectrum OCT still is based on the Michelson interferometers of two-beam interference, (interferometer two-arm has
Fixed π phase differences).Spectrum OCT can introduce the empty signal of zero optical path difference position both sides when handling interference spectrum, this
Sample has virtual image interference in spectrum OCT image.In addition, the interference of scattering light, reference light, DC terms etc., will also result in interference
The noise of spectral line signal is larger.Therefore, the interference of traditional spectrum OCT is larger, causes effect in imaging results bad.
Invention content
Based on this, it is necessary to which the interference for traditional spectrum OCT is larger, leads in imaging results that effect is bad to ask
Topic, provides a kind of optical coherence tomography system.
A kind of optical coherence tomography system, including：
Light source provides initial light；
Fiber coupler, the fiber coupler receives the initial light, and the initial light is divided into multiple-channel output light,
The multiple-channel output light includes reference light and all the way sample light all the way；
Reference arm is transmitted back to the fiber coupler for receiving the reference light, and by the reflected light of the reference light；
Sample arm, for receiving the sample light；The sample arm utilizes the sample light detection sample to be tested, the sample
Product light scatters at the sample to be tested, generates rear orientation light, and the rear orientation light is transmitted back to the fiber coupling
Device；The rear orientation light is interfered with the reflected light in the fiber coupler, forms interference light；The interference light
Multipath interference spectrum is divided by the fiber coupler, often exporting respectively all the way in the multipath interference spectrum；
Signal acquisition module acquires each interference spectrum respectively；
Signal processing module generates the detection figure of the sample to be tested according to the spectral line signal of interference spectrum described in each road
Picture, the imaging to eliminate the sample to be tested are interfered.
Above-mentioned optical coherence tomography system, first, reference light form reflected light by reference to arm and return to fiber coupling
Device.Sample light forms rear orientation light by sample arm and is back to fiber coupler.Secondly, fiber coupler receives back scattering
Light and reflected light.Rear orientation light and reflected light interfere in fiber coupler, form interference light.Also, fiber coupling
Interference light is divided into multipath interference spectrum by device.Then, signal acquisition module acquires each road interference spectrum, the interference of the roads Bing Jiangge respectively
The spectral line signal transmission of spectrum is to signal processing module.The spectral line signal of each road interference spectrum is handled by signal processing module, and
Obtain the image information of sample to be tested Depth Stratification time.Since interference light has been divided into multipath interference spectrum, institute by fiber coupler
Image procossing is carried out according to each road interference spectrum with signal processing module, virtual image interference can be eliminated and optical signal noise is dry
It disturbs, so that the imaging effect of above system is preferable.
The interference light is divided into three road interference spectrums by the fiber coupler in one of the embodiments,；Wherein, institute
The light intensity stated in three road interference spectrums between arbitrary two-way interference spectrum is equal, and the phase between the interference spectrum of three road is in
Equiphase difference arranges.
The system also includes optical fiber circulators in one of the embodiments,；The optical fiber circulator has first end
Mouth, second port and third port；
There are three input terminals for the fiber coupler tool；Three input terminals are respectively first input end, the second input
End, third input terminal；
Wherein, the first port is connect with the light source, for receiving the initial light；The second port with it is described
First input end connects, and the second port is used to the initial light that the optical fiber circulator is received being transmitted to the light
Fine coupler；Interference spectrum is passed by first input end transmission, the second port and the third port successively all the way
Transport to the signal acquisition module；Interference spectrum described in another way is transmitted to the signal acquisition mould by second input terminal
Block；Also the interference spectrum is transmitted to the signal acquisition module by the third input terminal all the way.
In one of the embodiments, the system also includes light path selecting module, the light path selecting module selection exists
Different moments receive interference spectrum described in each road, and interference spectrum is transmitted separately to the signal acquisition module described in the roads Bing Jiangge.
The light path selecting module is electric control optical switch in one of the embodiments,.
The reference arm includes the first collimation lens and speculum, the speculum and institute in one of the embodiments,
The optical axis for stating the first collimation lens is vertical；The reference light is changed into directional light by first collimation lens；The directional light
It is incident to the speculum, and incidence angle is 0 °；The directional light is reflected to form the reflected light by the speculum.
The speculum is adjustable relative to the distance of first collimation lens in one of the embodiments,.
The sample arm includes the second collimation lens and detection object lens, second collimation in one of the embodiments,
Lens and the detection object lens constitute confocal optical path；The sample light is changed into directional light by second collimation lens；This is flat
Row light forms detection light via the detection object lens and converges on the sample to be tested, and the detection light is on the sample to be tested
The rear orientation light that scattering is formed is transmitted back to the fiber coupler by the confocal optical path.
The optical axis of second collimation lens and the detection object lens is vertical in one of the embodiments,；
The sample arm further includes scanning galvanometer；The scanning galvanometer is set to second collimation lens and described simultaneously
On the optical axis for detecting object lens；The directional light of the second collimation lens outgoing reflexes to the detection object by the scanning galvanometer
Mirror；The directional light of second collimation lens is adjustable relative to the incidence angle of the scanning galvanometer.
The light source is ultra broadband light source in one of the embodiments, and the initial light is low-coherent light；The signal
Acquisition module is spectrometer.
Description of the drawings
Fig. 1 is the structural schematic diagram of the optical coherence tomography system of an embodiment；
Fig. 2 is the operation block diagram of the signal processing module of an embodiment.
Specific implementation mode
In order to make the foregoing objectives, features and advantages of the present invention clearer and more comprehensible, below in conjunction with the accompanying drawings to the present invention
Specific implementation mode be described in detail.
Fig. 1 is the structural schematic diagram of the optical coherence tomography system 100 of an embodiment.The optical coherence tomography
System 100 includes at light source 110, fiber coupler 120, reference arm 130, sample arm 140, signal acquisition module 150 and signal
Manage module 160.In the present embodiment, the propagation of the optical signal between each device in optical coherence tomography system 100 is all
Pass through spread fiber.
Light source 110 is for providing initial light.
Fiber coupler 120 includes several input terminals and several output ends.The fiber coupler 120 is described defeated by one
Enter end and receives the initial light.The initial light is divided into the multichannel exported from the corresponding output end by fiber coupler 120
Output light.Wherein have all the way output light be reference light, also all the way output light be sample light.
Reference arm 130 receives the reference light, and the reflected light of the reference light is passed along the corresponding output end
It is back to the fiber coupler 120.As shown in Figure 1, reference arm 130 includes the first collimation lens 131 and speculum 132.It is described
Speculum 132 is vertical with the optical axis of first collimation lens 131.First collimation lens 131 changes the reference light
For directional light.The directional light is incident to the speculum 132, and incidence angle is 0 °.The speculum 132 is by the directional light
Reflect to form the reflected light.Therefore, reflected light is back to fiber coupler 120 along the light path of reference light.
Sample arm 140 receives the sample light.The sample arm 140 utilizes the sample light detection sample to be tested 200.Institute
It states sample light and back scattering occurs at the sample to be tested 200, generate rear orientation light.The rear orientation light along with institute
The output end for stating sample photophase is transmitted back to the fiber coupler 120.Wherein, rear orientation light refers to from the direction of sample light
The scattered wave of (i.e. the direction of incident light) observation.As shown in Figure 1, sample arm 140 includes the second collimation lens 141 and detection object lens
142, second collimation lens 141 and the detection object lens 142 constitute confocal optical path.Wherein, confocal optical path refers to light path
Light path between two collimation lenses 141 and detection object lens 142 is reversible.The application of confocal optical path can to avoid the interference of stray light,
Ensure the return of the second collimation lens 141 is the back scattering optical signal of sample.Second collimation lens 141 is by the sample
Light is changed into directional light.The directional light forms detection light via the detection object lens 142.Detection light converges to the sample to be tested
On 200.The detection light scatters on the sample to be tested 200 and forms rear orientation light.Rear orientation light is by described confocal
Light path is transmitted back to the fiber coupler 120.
First collimation lens 131 and the second collimation lens 141 are all fiber collimating lenses.Fiber collimating lenses are with light
The non-spherical lens of fine pigtail coupling.It is parallel that the broadband diverging light that optical fiber inputs can be collimated into free space by fiber collimating lenses
Light output.The operating wavelength range of fiber collimating lenses should match the centre wavelength and spectrum width of aforementioned wideband light source 110.Further
Ground, aberration and aberration of the fiber collimating lenses in entire operating wavelength range are answered as small as possible.It in this way can be to ensure not
The output light component of co-wavelength can become same collimated light beam.It simultaneously also can not sharing the same light the reflected in parallel light received point
Amount is back to same coupling efficiency in optical fiber.In addition, fiber collimating lenses and detection object lens 142 can be convex lenses.
After rear orientation light is back to reflected light in fiber coupler 120, their hairs in the fiber coupler 120
Raw interference, forms interference light.The interference light is divided by the fiber coupler 120 for multipath interference spectrum, every interference light all the way
Spectrum is exported by corresponding input terminal.
Signal acquisition module 150 acquires each interference spectrum respectively.Signal acquisition module 150 obtains each road interference spectrum
Spectral line signal.
Signal processing module 160 generates the inspection of the sample to be tested 200 according to the spectral line signal of interference spectrum described in each road
Altimetric image is eliminated the imaging to the sample to be tested 200 with interference spectrum described in each road and is interfered.
Above-mentioned optical coherence tomography system 100, first, reference light form reflected light return light by reference to arm 130
Fine coupler 120.Sample light forms rear orientation light by sample arm 140 and is back to fiber coupler 120.Secondly, optical fiber coupling
Clutch 120 receives rear orientation light and reflected light.Rear orientation light and reflected light interfere in fiber coupler 120, shape
At interference light.Also, interference light is divided into multipath interference spectrum by fiber coupler 120.Then, signal acquisition module 150 is distinguished
Each road interference spectrum is acquired, the spectral line signal transmission of the roads Bing Jiangge interference spectrum is to signal processing module 160.By signal processing mould
Block 160 handles the spectral line signal of each road interference spectrum, and obtains the image information of sample to be tested 200 Depth Stratification time.Due to light
Interference light has been divided into multipath interference spectrum by fine coupler 120, so signal processing module 160 is carried out according to each road interference spectrum
Image procossing can eliminate virtual image interference and optical signal noise interference, so that the imaging effect of above system is preferable.
In the present embodiment, light source 110 is ultra broadband light source 110.The initial light is low-coherent light.The ultra-wideband-light
Source 110 refers to the light source 110 based on semiconductor laser or light emitting diode.According to the difference of detection sample, 110 light of light source
The centre wavelength of spectrum can be selected in 850nm, 1310nm, the different locations such as 1550nm.But the centre wavelength of 110 spectrum of light source is not
It is confined to this, different centre wavelength can be selected according to sample to be tested 200.For example, the wave band of initial light can be near-infrared
Wave band.Since near infrared band transmissivity is higher, so system is higher to the imaging effect to sample to be tested 200, can reach
The lossless three-dimensional imaging of high-resolution.Ultra broadband light source 110 is characterized in：Spectrum spectrum width it is larger (full width at half maximum FWHM >=50nm,
Middle FWHM is the abbreviation of full width at half maximum), total Output optical power is up to 20mW (continuous light) or more.Light
The spectrum spectrum width in source 110 is wider, and the axial resolution of the scattered information of the sample different depth position of system detection is finer.And
Luminous power is bigger, then the scattering light of sample arm 140 is stronger, and the signal received by signal acquisition module 150 is stronger, imaging effect
Better.Further, the light intensity of light source 110 has smaller fluctuation in entire spectrum width range planted agent.For example, light source 110 can be with
It is integrated with optical fiber collimator.In this way, light source 110 is by the free space optical coupled into optical fibres of transmitting, to facilitate follow-up connection.
In the present embodiment, there are three input terminal and three output ends for the tool of fiber coupler 120.The reference light and the sample
The light intensity of product light is equal.The interference light is divided into three road interference spectrums, arbitrary two-way interference spectrum by the fiber coupler 120
Light intensity it is equal, and the phase of three road interference spectrum in equiphase difference arrange.In the present system, sample light to three export
The splitting ratio at end is 1：1：1.The splitting ratio of interference light to three input terminals is also 1：1：1.It may insure three tunnel interference lights in this way
The phase of spectrum is arranged in equiphase difference.That is the tolerance of the phase of three road interference spectrums isThe spy of 3 × 3 fiber couplers 120
Property may insure that the fixed skew of generated 3 interference spectrums is respectively：0,
In the present embodiment, fiber coupler 120 is 3 × 3 fiber couplers 120.In this way, it is dry to can effectively improve any road
The signal-to-noise ratio of spectrum is related to, so that the signal amplitude for the sample depth information that signal processing module 160 recovers is most strong.3×3
Fiber coupler 120 is a kind of optical fibre device of six ports.Each port is attached by optical fiber pigtail and external circuits.Light
Fine coupler 120 has first input end c1, the second input terminal c2, third input terminal c3, the first output end c4, second output terminal
C5 and third output end c6.As shown in Figure 1, six ports of 3 × 3 couplers are divided into two groups of left and right, the three of one group of the left side on Fig. 1
A port is all input terminal (being respectively first input end c1, the second input terminal c2, third input terminal c3).The three of the right on Fig. 2
A port is all output end (being respectively the first output end c4, second output terminal c5, third output end c6).Any one input terminal
It can be used as light input port.The light inputted from input terminal can be exported by any one output end.The two groups of ports in left and right have
Reciprocity.The operating wavelength range of coupler should match the centre wavelength and spectrum width of aforementioned wideband light source 110.Input terminal extremely exports
The excess loss at end is as small as possible.The splitting ratio of fiber coupler 120 is consistent as far as possible in entire operating wavelength range.
As shown in Figure 1, optical coherence tomography system 100 further includes optical fiber circulator 170.The optical fiber circulator
170 have first port p1, second port p2 and third port p3.Second port is connect with first input end optical fiber.Described
Single port receives the initial light.Initial light is transmitted to second port by first port.The initial light passes through the second end
An input terminal of the fiber coupler 120 is transported in oral instructions.In the present embodiment, it is defeated that initial light by second port p2 is transmitted to first
Enter to hold c1.In three road interference spectrums, the interference spectrum is transmitted to by the first input end c1 by second port p2 all the way
The signal acquisition module 150.Interference spectrum described in another way is transmitted to the signal acquisition mould by the second input terminal c2
Block 150.Also the interference spectrum is transmitted to the signal acquisition module 150 by the third input terminal c3 all the way.
In optical fiber circulator 170, initial light is inputted by first port p1, is exported by second port p2.Second port p2
The light (interference spectrum) of input is exported by third port p3.And the light of third port p2 input is isolated without being back to the
Single port p1.Initial light can be not only introduced in fiber coupler 120 in this way, but also can be by certain interference spectrum signal taking-up all the way
And light source 110 is protected not interfered by interference spectrum.
It should be noted that the second output terminal c5 of fiber coupler 120 is not used, can be prevented by modes such as knottings
The end face light reflection back into optical fibers coupler 120 of second output terminal c5 introduces interference.
In the present embodiment, in reference arm 130, speculum 132 is adjustable relative to the distance of first collimation lens 131
Section.Specifically, speculum 132 is a kind of plane mirror, is mounted on optical regulation lens frame, by adjusting the pitching of speculum 132
And deflection angle, reference light is reflected back the first collimation lens 131 and again coupled back into optical fibers.Further, in order to avoid anti-
Penetrate light intensity power it is excessive cause signal acquisition module 150 receive occur saturation even damage, can by the pitching of speculum 132 and partially
Corner is transferred from best angle of reflection.Also diaphragm (operation wavelength matches the centre wavelength and spectrum width of light source 110) may be selected as anti-
Penetrate mirror 132.Reflected light is formed using the mirror-reflection between air and diaphragm.Preferably, speculum 132 and pH effect mirror
Frame can be fixed on an one-dimensional linear mobile platform, by adjusting mobile platform, change speculum 132 and the first collimation lens
The distance between 131, to change the light path of 130 light path of reference arm.Therefore, speculum 132 is for adjusting the anti-of reference arm 130
Penetrate the optical path difference of light and the scattering light of sample arm 140, it is ensured that its optical path difference is located in interference distance.
As shown in Figure 1, in sample arm 140, second collimation lens 141 is vertical with the detection optical axis of object lens 142.
The sample arm 140 further includes scanning galvanometer 143.The scanning galvanometer 143 is set to 141 He of the second collimation lens simultaneously
On the optical axis of the detection object lens 142.The directional light that second collimation lens 141 is emitted is reflected by the scanning galvanometer 143
To the detection object lens 142.The directional light of second collimation lens 141 can relative to the incidence angle of the scanning galvanometer 143
It adjusts.Specifically, scanning galvanometer 143 is that a kind of metal-coated membrane plane that can quickly change deflection angle by electric current driving is anti-
Penetrate mirror 132.Plane mirror 132 has zero color difference and aberration.In systems, scanning galvanometer 143 is mounted on 140 light path of sample arm
In.The reflecting surface normal and 141 optical axis of the second collimation lens of the original state of scanning galvanometer 143 are at 45 degree of angles.By quickly changing
The angle for becoming normal and 141 optical axis of the second collimation lens plays the role of light beam scanning, different horizontal to obtain sample to be tested 200
To the axial depth optical information at position.The scan frequency of scanning galvanometer 143 is within 100Hz.Refer to laterally herein waiting for test sample
Product 200 are perpendicular to the direction of detection 142 optical axis of object lens.It refer to axially the side that sample to be tested 200 is parallel to detection 142 optical axis of object lens
To.
Detect object lens 142 be the collimated light beam that will be emitted by the second collimation lens 141 and scanning galvanometer 143, converge to by
Detect sample surfaces.Since the wave-length coverage of input light is larger, achromatic lens group need to be selected to constitute.Detect object lens 142
Operating wavelength range should match the centre wavelength and spectrum width of light source 110.The focal length of detection object lens 142 is answered smaller, and bore is then
The scattering light for detecting sample can should be received as much as possible more so.Meanwhile larger bore is it is also possible that converge
The spot size of accumulation reduces, and is advantageously implemented the detection of 200 lateral resolution of high sample to be tested.In this system, because second
Collimation lens 141 and detection object lens 142 constitute confocal optical path, need to will detect stringent place of sample and be put down with the coke of detection object lens 142
Face position, so that detection is accurate.
Optical coherence tomography system 100 further includes light path selecting module 180.The light path selecting module 180 selects
Interference spectrum described in each road is received in different moments, interference spectrum is transmitted separately to the signal acquisition module described in the roads Bing Jiangge
150.Light path selecting module 180 plays the work of gate intervention spectrum between fiber coupler 120 and signal acquisition module 150
With.It in this way can be to avoid the interference of each road interference spectrum.
Light path selecting module 180 is electric control optical switch.Electric control optical switch is a kind of light path using electric signal triggering control
Break-make selecting module.The operating wavelength range of electric control optical switch should match the centre wavelength and spectrum width of aforementioned wideband light source 110.Electricity
1ns can be less than by controlling the break-make handoff response time of photoswitch, and operating wavelength range can reach 100nm or more.Therefore electricity
Photoswitch is controlled to be suitble to carry out the channel signal switching of high speed in the present system.In this way can when component selections receive by way of
The quantity of signal acquisition module 150 is saved, it is cost-effective.Specifically, electric control optical switch carries optical fiber pigtail connector, to share the same light
Fine coupler 120 is connected with fiber optical circulator.
Signal acquisition module 150 is spectrometer.Further, rapid spectrometer can be used in spectrometer.Rapid spectrometer is
A kind of equipment of the relative power strength of the different wave length component of detection input optical signal.Its wave-length coverage that can be responded is answered
Centre wavelength with light source 110 and spectrum width.Specifically, spectrometer can be based on high speed alignment CMOS (Complementary
Metal Oxide Semiconductor) camera framework.I.e. by collimation lens, (partial picture need to increase to be expanded input light
Mirror) it is changed into free space parallel light emergence.Free space parallel light emergence has certain spot size.Directional light, which is incident to, to spread out
Penetrate grating (can be reflection-type or transmission-type grating).Directional light is by grating according to Bragg diffraction by the light of different wave length component
Signal is detached by the different angles of diffraction.The maximum incident angle of incidence angle selection diffraction efficiency of grating of directional light.Go out
The diffraction light penetrated is converged to by achromatism condenser lens on the receiving plane of alignment CMOS cameras.Each of CMOS cameras connects
Reproduced image member (according to operation wavelength, pixel can be the photosensitive materials such as Si, AlGaAs or InGaAs) enters corresponding to rapid spectrometer
Penetrate a certain wavelength component of light.According to the photosensitive intensity of each pixel, you can obtain the spectral information of incident light.Specifically,
Rapid spectrometer carries fiber coupling interface.The spectra collection rate of rapid spectrometer can reach 100k spectral lines/second.Spectrometer has
There are the data of high speed to read interface and large capacity cache, to be provided in a large amount of spectral line datas of high speed acquisition at signal in real time
It manages module 160 and carries out data processing.Using rapid spectrometer, the spectral line data per interference spectrum all the way can be accurately obtained.
Rapid spectrometer obtains three road interference spectrums by electric control optical switch.This three roads interference spectrum luminous intensity is denoted as respectively
I1(k), I2(k), I3(k) (first input end c1, the second input terminal c2 and the third input of fiber coupler 120 are corresponded respectively to
Hold c3).From the characteristic of 3 × 3 fiber couplers 120, it is assumed that I1(k) proper phase isI2(k) proper phase
It is 0, I3(k) proper phase is
Fig. 2 is the operation block diagram of the signal processing module 160 of an embodiment.It is quick that signal processing module 160 receives three tunnels
Spectrometer spectral line.Signal processing module 160 with etc. three phase algorithms recover image.The virtual image is eliminated first, then passes through coefficient
DC terms and interference noise item are eliminated in operation, to obtain comprising the scattered signal range value a at sample interior different depth
(z).Every treated that spectral line corresponds to the axial information at a certain position, i.e., so-called A-Scan spectral lines.Again by and scanning
Galvanometer 143 synchronizes, and forms the axial depth hum pattern of tested article difference lateral position.Sample to be tested is just constituted in this way
200 cross section scattering amplitude image, i.e., it is so-called to obtain B-Scan images.Equal three phase algorithms of system are as follows：
First, according to the data processing method of traditional SD-OCT systems, 3 interference spectrums that rapid spectrometer is obtained
Spectral line Si(λ) is converted into wave-number domain S from wavelength domaini(k).Mapping mode is：(i=1,2,3 are every spectral lines to k=2 π/λ
Mark；Si(k) a pair of with the first input end c1 of 3 × 3 fiber couplers 120, the second input terminal c2 and third input terminal c3 mono-
It answers).By Si(k) spline interpolation for carrying out wave-number domain, obtains the spectral line signal I of wave-number domain uniform samplingi(k), according to SD-OCT
Matter has：
In formula (1), ERIt is reference light light intensity, the back scattering information of 200 inside points level of a (z) samples to be tested, k is wave
Number independent variable, n is sample refractive index,The corresponding phase component of as three spectral lines (is followed successively by0,), i is void
Number unit.
Secondly, as shown in Fig. 2, for Ii(k) such as inferior three-phase position algorithm operation is executed：
Hi(z)=FT [Ii(k)], (i=1,2,3) (2)
In formula (2), FT indicates Fourier transform.
By the operation of formula (3) and formula (4), the virtual image of sample to be tested 200 can be eliminated.
DC terms interference and the noise jamming of three road interference spectrums can be eliminated by formula (5).
An elimination DC terms, the virtual image and the optimization of noise jamming spectrum can be obtained from three interference spectrums from above-mentioned operation
Line H (z).Back scattering information a (z) is proportional to H (z), i.e. A-Scan spectral lines to sample interior by different level.Pass through scanning galvanometer 143
Move back and forth, the A-Scan spectral lines at the laterally different position of sample surfaces can be obtained, finally, by all A-Scan spectral line groups
It closes, you can obtain the cross section B-Scan images of sample.
Each technical characteristic of embodiment described above can be combined arbitrarily, to keep description succinct, not to above-mentioned reality
It applies all possible combination of each technical characteristic in example to be all described, as long as however, the combination of these technical characteristics is not deposited
In contradiction, it is all considered to be the range of this specification record.
Several embodiments of the invention above described embodiment only expresses, the description thereof is more specific and detailed, but simultaneously
It cannot therefore be construed as limiting the scope of the patent.It should be pointed out that coming for those of ordinary skill in the art
It says, without departing from the inventive concept of the premise, various modifications and improvements can be made, these belong to the protection of the present invention
Range.Therefore, the protection domain of patent of the present invention should be determined by the appended claims.
Claims (10)
1. a kind of optical coherence tomography system, which is characterized in that including：
Light source provides initial light；
Fiber coupler, the fiber coupler receives the initial light, and the initial light is divided into multiple-channel output light, described
Multiple-channel output light includes reference light and all the way sample light all the way；
Reference arm is transmitted back to the fiber coupler for receiving the reference light, and by the reflected light of the reference light；
Sample arm, for receiving the sample light；The sample arm utilizes the sample light detection sample to be tested, the sample light
It is scattered at the sample to be tested, generates rear orientation light, the rear orientation light is transmitted back to the fiber coupler；Institute
It states rear orientation light to interfere in the fiber coupler with the reflected light, forms interference light；The interference light is by institute
It states fiber coupler and is divided into multipath interference spectrum, often exporting respectively all the way in the multipath interference spectrum；
Signal acquisition module acquires each interference spectrum respectively；
Signal processing module generates the detection image of the sample to be tested according to the spectral line signal of interference spectrum described in each road, with
Eliminate the imaging interference of the sample to be tested.
2. system according to claim 1, which is characterized in that the interference light is divided into three tunnels by the fiber coupler to be done
Relate to spectrum；Wherein, the light intensity in the interference spectrum of three road between arbitrary two-way interference spectrum is equal, and three tunnel interference light
Phase between spectrum is arranged in equiphase difference.
3. system according to claim 2, which is characterized in that the system also includes optical fiber circulators；The fiber optic loop
Shape utensil has first port, second port and third port；
There are three input terminals for the fiber coupler tool；Three input terminals are respectively first input end, the second input terminal,
Three input terminals；
Wherein, the first port is connect with the light source, for receiving the initial light；The second port and described first
Input terminal connects, and the second port is used to the initial light that the optical fiber circulator is received being transmitted to the optical fiber coupling
Clutch；Interference spectrum is transmitted to by first input end transmission, the second port and the third port successively all the way
The signal acquisition module；Interference spectrum described in another way is transmitted to the signal acquisition module by second input terminal；Also
Have all the way the interference spectrum signal acquisition module is transmitted to by the third input terminal.
4. system according to claim 1, which is characterized in that further include light path selecting module, the light path selecting module
Selection receives interference spectrum described in each road in different moments, and interference spectrum is transmitted separately to the signal acquisition described in the roads Bing Jiangge
Module.
5. system according to claim 4, which is characterized in that the light path selecting module is electric control optical switch.
6. system according to claim 1, which is characterized in that the reference arm includes the first collimation lens and speculum,
The speculum is vertical with the optical axis of the first collimation lens；The reference light is changed into parallel by first collimation lens
Light；The directional light is incident to the speculum, and incidence angle is 0 °；The speculum reflects to form the directional light described
Reflected light.
7. system according to claim 6, which is characterized in that the speculum relative to first collimation lens away from
From adjustable.
8. system according to claim 1, which is characterized in that the sample arm includes the second collimation lens and detection object
Mirror, second collimation lens and the detection object lens constitute confocal optical path；Second collimation lens turns the sample light
Become directional light；The directional light forms detection light via the detection object lens and converges on the sample to be tested, the detection light
The rear orientation light that formation is scattered on the sample to be tested is transmitted back to the fiber coupler by the confocal optical path.
9. system according to claim 8, which is characterized in that the optical axis of second collimation lens and the detection object lens
Vertically；
The sample arm further includes scanning galvanometer；The scanning galvanometer is set to second collimation lens and the detection simultaneously
On the optical axis of object lens；The directional light of the second collimation lens outgoing reflexes to the detection object lens by the scanning galvanometer；Institute
The directional light for stating the second collimation lens is adjustable relative to the incidence angle of the scanning galvanometer.
10. system according to claim 1, which is characterized in that the light source is ultra broadband light source, and the initial light is low
Coherent light；The signal acquisition module is spectrometer.
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|---|---|---|---|---|
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Citations (34)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1915164A (en) * | 2006-09-08 | 2007-02-21 | 浙江大学 | Method and system for expanding dynamic range in tomography of optical coherent |
| CN1915163A (en) * | 2006-09-08 | 2007-02-21 | 浙江大学 | Method and system for realizing axial super resolution in tomography of optical coherent |
| WO2007051292A1 (en) * | 2005-11-02 | 2007-05-10 | Oti Ophthalmic Technologies Inc. | En-face oct with parallel detector array |
| CN101513366A (en) * | 2009-03-18 | 2009-08-26 | 天津大学 | PS-OCT-based three dimension visual nonnasality decayed tooth checking device and checking method thereof |
| CN101608930A (en) * | 2009-07-09 | 2009-12-23 | 复旦大学 | A kind of implementation method of pi/2 phase bias of optical fiber interferometer |
| CN101617935A (en) * | 2009-08-06 | 2010-01-06 | 浙江大学 | Method and system for wide-spectrum and high-resolution detection based on space-time light splitting in OCT |
| WO2010063416A1 (en) * | 2008-12-02 | 2010-06-10 | Optopol Technology S.A. | Method and apparatus for eye movement tracking in spectral optical coherence tomography. (sd-oct) |
| WO2010131531A1 (en) * | 2009-05-11 | 2010-11-18 | Canon Kabushiki Kaisha | Information processing apparatus in oct system |
| US20110130652A1 (en) * | 2009-11-18 | 2011-06-02 | The Board Of Trustees Of The University Of Illinois | Apparatus for biomedical imaging |
| CN102104363A (en) * | 2011-03-01 | 2011-06-22 | 北京大学 | Tera-hertz silica-based quadrupler and frequency multiplier |
| CN102151121A (en) * | 2011-01-28 | 2011-08-17 | 浙江大学 | Method and system for calibrating spectrum based on interference spectrum phase information |
| CN102264279A (en) * | 2008-12-26 | 2011-11-30 | 佳能株式会社 | Optical tomographic imaging apparatus |
| US20120002214A1 (en) * | 2009-04-13 | 2012-01-05 | Canon Labushiki Kaisha | Optical tomographic imaging apparatus and control method therefor |
| CN102333477A (en) * | 2009-01-23 | 2012-01-25 | 佳能株式会社 | Optical tomographic imaging method and optical tomographic imaging apparatus |
| CN102438501A (en) * | 2009-05-22 | 2012-05-02 | 佳能株式会社 | Imaging device and imaging method |
| CN102499648A (en) * | 2011-11-16 | 2012-06-20 | 清华大学 | Spectral-domain optical coherence tomography imaging system based on Fresnel spectrometer |
| CN102670172A (en) * | 2012-05-07 | 2012-09-19 | 浙江大学 | AS-OCT-SD (Anterior Segment-Optical Coherence Tomography-Spectrum Domain) imaging system and AS-OCT-SD imaging method based on visibility function regulation |
| CN103090808A (en) * | 2013-01-22 | 2013-05-08 | 浙江大学 | High-precision wide-range gap measuring method and system based on spectrum phase |
| CN103784120A (en) * | 2014-02-26 | 2014-05-14 | 中国科学院光电技术研究所 | Tumor boundary intraoperative detection instrument based on sweep frequency OCT technology |
| CN103900798A (en) * | 2014-03-28 | 2014-07-02 | 哈尔滨工程大学 | Optical coherence domain polarization measurement device with optical distance scanning on-line correction function |
| CN104434037A (en) * | 2014-12-12 | 2015-03-25 | 中国计量学院 | Modified SD - OCT system based on multi-channel spectrometer |
| CN104545772A (en) * | 2014-12-19 | 2015-04-29 | 佛山市南海区欧谱曼迪科技有限责任公司 | Composite narrowband imaging endoscope imaging system |
| CN104655032A (en) * | 2015-02-06 | 2015-05-27 | 浙江大学 | High-precision distance measurement system and method based on orthogonal chromatic dispersion spectral domain interferometer |
| US9204800B2 (en) * | 2011-03-07 | 2015-12-08 | St. Jude Medical, Inc. | Low cost high efficiency signal interrogation for multi-channel optical coherence tomography |
| CN105147241A (en) * | 2015-07-03 | 2015-12-16 | 南京航空航天大学 | Method and system based on double-space carrier frequency technology for increasing OCT (optical coherence tomography) imaging depth |
| CN105342558A (en) * | 2015-09-30 | 2016-02-24 | 苏州大学 | Swept-source-based correction method of phase errors in optical coherence tomography |
| US20160120401A1 (en) * | 2014-10-30 | 2016-05-05 | Tomey Corporation | Optical Tomographic Imaging Apparatus |
| CN106308744A (en) * | 2015-06-15 | 2017-01-11 | 南京理工大学 | Handheld human body any surface position skin frequency sweeping optical coherence tomography imaging apparatus |
| CN106383087A (en) * | 2016-10-09 | 2017-02-08 | 福建师范大学 | Polarization optical coherence tomography/polarization multiphoton microscopy bimodal imaging system |
| WO2017035328A1 (en) * | 2015-08-26 | 2017-03-02 | University Of Houston System | Evaluation of dermal filler injections by optical coherence tomography and optical coherence elastography |
| CN106725285A (en) * | 2017-01-06 | 2017-05-31 | 东北大学秦皇岛分校 | Optical coherence human eye measurement apparatus and human eye measuring method |
| WO2017134536A1 (en) * | 2016-02-05 | 2017-08-10 | Synaptive Medical (Barbados) Inc. | System and method for providing surgical guidance based on polarization-sensitive optical coherence tomography |
| WO2018000036A1 (en) * | 2016-07-01 | 2018-01-04 | Cylite Pty Ltd | Apparatus and method for confocal microscopy using dispersed structured illumination |
| US20180035894A1 (en) * | 2016-08-05 | 2018-02-08 | Tomey Corporation | Optical coherence tomographic device |
-
2018
- 2018-03-28 CN CN201810264524.XA patent/CN108514404B/en active Active
Patent Citations (34)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2007051292A1 (en) * | 2005-11-02 | 2007-05-10 | Oti Ophthalmic Technologies Inc. | En-face oct with parallel detector array |
| CN1915163A (en) * | 2006-09-08 | 2007-02-21 | 浙江大学 | Method and system for realizing axial super resolution in tomography of optical coherent |
| CN1915164A (en) * | 2006-09-08 | 2007-02-21 | 浙江大学 | Method and system for expanding dynamic range in tomography of optical coherent |
| WO2010063416A1 (en) * | 2008-12-02 | 2010-06-10 | Optopol Technology S.A. | Method and apparatus for eye movement tracking in spectral optical coherence tomography. (sd-oct) |
| CN102264279A (en) * | 2008-12-26 | 2011-11-30 | 佳能株式会社 | Optical tomographic imaging apparatus |
| CN102333477A (en) * | 2009-01-23 | 2012-01-25 | 佳能株式会社 | Optical tomographic imaging method and optical tomographic imaging apparatus |
| CN101513366A (en) * | 2009-03-18 | 2009-08-26 | 天津大学 | PS-OCT-based three dimension visual nonnasality decayed tooth checking device and checking method thereof |
| US20120002214A1 (en) * | 2009-04-13 | 2012-01-05 | Canon Labushiki Kaisha | Optical tomographic imaging apparatus and control method therefor |
| WO2010131531A1 (en) * | 2009-05-11 | 2010-11-18 | Canon Kabushiki Kaisha | Information processing apparatus in oct system |
| CN102438501A (en) * | 2009-05-22 | 2012-05-02 | 佳能株式会社 | Imaging device and imaging method |
| CN101608930A (en) * | 2009-07-09 | 2009-12-23 | 复旦大学 | A kind of implementation method of pi/2 phase bias of optical fiber interferometer |
| CN101617935A (en) * | 2009-08-06 | 2010-01-06 | 浙江大学 | Method and system for wide-spectrum and high-resolution detection based on space-time light splitting in OCT |
| US20110130652A1 (en) * | 2009-11-18 | 2011-06-02 | The Board Of Trustees Of The University Of Illinois | Apparatus for biomedical imaging |
| CN102151121A (en) * | 2011-01-28 | 2011-08-17 | 浙江大学 | Method and system for calibrating spectrum based on interference spectrum phase information |
| CN102104363A (en) * | 2011-03-01 | 2011-06-22 | 北京大学 | Tera-hertz silica-based quadrupler and frequency multiplier |
| US9204800B2 (en) * | 2011-03-07 | 2015-12-08 | St. Jude Medical, Inc. | Low cost high efficiency signal interrogation for multi-channel optical coherence tomography |
| CN102499648A (en) * | 2011-11-16 | 2012-06-20 | 清华大学 | Spectral-domain optical coherence tomography imaging system based on Fresnel spectrometer |
| CN102670172A (en) * | 2012-05-07 | 2012-09-19 | 浙江大学 | AS-OCT-SD (Anterior Segment-Optical Coherence Tomography-Spectrum Domain) imaging system and AS-OCT-SD imaging method based on visibility function regulation |
| CN103090808A (en) * | 2013-01-22 | 2013-05-08 | 浙江大学 | High-precision wide-range gap measuring method and system based on spectrum phase |
| CN103784120A (en) * | 2014-02-26 | 2014-05-14 | 中国科学院光电技术研究所 | Tumor boundary intraoperative detection instrument based on sweep frequency OCT technology |
| CN103900798A (en) * | 2014-03-28 | 2014-07-02 | 哈尔滨工程大学 | Optical coherence domain polarization measurement device with optical distance scanning on-line correction function |
| US20160120401A1 (en) * | 2014-10-30 | 2016-05-05 | Tomey Corporation | Optical Tomographic Imaging Apparatus |
| CN104434037A (en) * | 2014-12-12 | 2015-03-25 | 中国计量学院 | Modified SD - OCT system based on multi-channel spectrometer |
| CN104545772A (en) * | 2014-12-19 | 2015-04-29 | 佛山市南海区欧谱曼迪科技有限责任公司 | Composite narrowband imaging endoscope imaging system |
| CN104655032A (en) * | 2015-02-06 | 2015-05-27 | 浙江大学 | High-precision distance measurement system and method based on orthogonal chromatic dispersion spectral domain interferometer |
| CN106308744A (en) * | 2015-06-15 | 2017-01-11 | 南京理工大学 | Handheld human body any surface position skin frequency sweeping optical coherence tomography imaging apparatus |
| CN105147241A (en) * | 2015-07-03 | 2015-12-16 | 南京航空航天大学 | Method and system based on double-space carrier frequency technology for increasing OCT (optical coherence tomography) imaging depth |
| WO2017035328A1 (en) * | 2015-08-26 | 2017-03-02 | University Of Houston System | Evaluation of dermal filler injections by optical coherence tomography and optical coherence elastography |
| CN105342558A (en) * | 2015-09-30 | 2016-02-24 | 苏州大学 | Swept-source-based correction method of phase errors in optical coherence tomography |
| WO2017134536A1 (en) * | 2016-02-05 | 2017-08-10 | Synaptive Medical (Barbados) Inc. | System and method for providing surgical guidance based on polarization-sensitive optical coherence tomography |
| WO2018000036A1 (en) * | 2016-07-01 | 2018-01-04 | Cylite Pty Ltd | Apparatus and method for confocal microscopy using dispersed structured illumination |
| US20180035894A1 (en) * | 2016-08-05 | 2018-02-08 | Tomey Corporation | Optical coherence tomographic device |
| CN106383087A (en) * | 2016-10-09 | 2017-02-08 | 福建师范大学 | Polarization optical coherence tomography/polarization multiphoton microscopy bimodal imaging system |
| CN106725285A (en) * | 2017-01-06 | 2017-05-31 | 东北大学秦皇岛分校 | Optical coherence human eye measurement apparatus and human eye measuring method |
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