CN117825279A - Full-field sweep-frequency optical coherence tomography system capable of achieving parallel acquisition - Google Patents
Full-field sweep-frequency optical coherence tomography system capable of achieving parallel acquisition Download PDFInfo
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Abstract
The invention relates to a parallel acquisition full-field sweep-frequency optical coherence tomography system, which comprises a beam splitter, wherein four sides of the beam splitter are respectively connected with a light source input light path, a reference arm light path, a sample arm light path and a camera acquisition light path, and the light source input light path comprises a light source, a first reflection type grating, a first double-cemented lens, a DMD digital micromirror, a second double-cemented lens, a second reflection type grating, a beam expander and a first lens; the camera acquisition light path comprises a second lens, a reflecting mirror, a transmission type grating, a third double-cemented lens and a camera; parallel light rays output by the light source input light path enter the first surface of the beam splitter through the first lens, enter the reference arm light path and the sample arm light path through the second surface and the third surface of the beam splitter respectively, light reflected by the reference arm light path and the sample arm light path returns along the original light path, interference occurs after exiting through the fourth surface of the beam splitter, and the light is captured by the camera acquisition light path. The system of the invention has high imaging speed.
Description
Technical Field
The invention relates to a full-field sweep-frequency optical coherence tomography system for parallel acquisition, belonging to the technical field of biomedical holographic microscopic imaging.
Background
The sweep source optical coherence tomography (SS-OCT) system is based on the relation that the interference spectrum of a measuring arm and a reference arm and the back reflection light intensity information of different depths of a sample are exactly a pair of Fourier transform pairs, and after the light beams representing the information of the different depths of the sample are collected uniformly, the intensity information of the depth of the sample can be calculated through inverse Fourier transform, and the system is a three-dimensional tomography technology which can reconstruct images in the depth direction through the acquisition of the interference spectrum and the inverse Fourier transform. Compared with other medical imaging methods, the SS-OCT technology has the advantages of higher receiving sensitivity, non-contact, noninvasive measurement, low cost, simple system and the like. The core element of the SS-OCT system is a sweep laser source, a Michelson interferometer and a spectrum detector. However, the traditional sweep source optical coherence tomography adopts a point sweeping mode, a vibrating mirror needs to be moved to carry out transverse scanning to reconstruct a three-dimensional tomographic image of a sample, imaging efficiency is affected, and the transverse resolution is affected by the fact that a focus cannot be dynamically adjusted according to the measured depth of the sample, so that the limitations of low imaging efficiency and low transverse resolution exist, in addition, if one thousand wavelengths are required to be scanned, one thousand pictures are required to be taken, namely, one thousand frames are required to be continuously taken by a camera, and imaging speed is greatly affected.
Disclosure of Invention
The invention aims to provide a Full-field swept-source optical coherence tomography (FF-Field Parallel Swept Source Optical Coherence Tomography, FF-PSS-OCT) system for parallel acquisition, so as to overcome the limitations of low imaging efficiency and low transverse resolution of the traditional swept-source optical coherence tomography technology.
In order to achieve the technical purpose, the invention adopts the following scheme:
the full-field sweep-frequency optical coherence tomography system comprises a beam splitter, wherein four sides of the beam splitter are respectively connected with a light source input light path, a reference arm light path, a sample arm light path and a camera acquisition light path, and the light source input light path sequentially comprises a light source, a first reflection type grating, a first double-cemented lens, a DMD digital micromirror, a second double-cemented lens, a second reflection type grating, a beam expander and a first lens along the light path;
the camera acquisition light path sequentially comprises a second lens, a reflecting mirror, a transmission type grating, a third double-cemented lens and a camera along the light path;
parallel light rays output by a light source input light path enter a first surface of a beam splitter through a first lens, enter a reference arm light path and a sample arm light path through a second surface and a third surface of the beam splitter respectively, light reflected by the reference arm light path and the sample arm light path returns along an original light path, interference occurs after exiting through a fourth surface of the beam splitter, and the interference light is captured by a camera after passing through a second lens, a reflecting mirror, a transmission type grating and a third double-cemented lens in sequence.
As a preferred embodiment, the light source is a broadband laser light source.
As a preferred embodiment, the camera is a two-dimensional camera.
As a preferred embodiment, the reference arm optical path and the sample arm optical path have the same optical path length.
As a preferred embodiment, the optical path elements of the reference arm optical path and the sample arm optical path have the same composition.
As a preferred embodiment, the sample arm light path includes a first microscope objective, an object to be imaged; the reference arm light path comprises a second micro objective and a plane mirror.
As a preferred embodiment, the beam splitter is a 50/50 beam splitter.
As a preferred embodiment, the DMD digital micromirror controls the on and off of the micromirror by loading pixel maps of different widths at different positions.
As a preferred embodiment, the beam expander is a light beam expander lens group composed of two lenses.
As a preferred embodiment, the system further comprises a terminal, wherein after the multi-wavelength interference image captured by the camera is acquired through the terminal, the depth information of the sample at each wavelength is reconstructed by using an inverse fourier transform method, and a three-dimensional depth information image of the sample is acquired.
The beneficial effects of the invention are as follows:
1. the invention realizes the reconstruction multispectral parallel acquisition imaging by utilizing the DMD digital micromirror. The DMD filter is used for obtaining any multi-wavelength spectrum, the interval between adjacent multi-wavelength spectrums is adjustable, and the width of a single-wavelength spectrum is adjustable. The beams are dispersed in a horizontal direction using a diffraction grating, the beams having different carriers are spatially separated, and each beam is projected in the horizontal direction to a different area of the two-dimensional camera. Each beam with one carrier does not overlap with the other beam when two-dimensional microscopic imaging is performed, and the resolution of the image of each carrier is improved.
2. The invention adopts a parallel acquisition mode, filters out the wavelength with the interval of 20nm and the bandwidth of 0.1nm of five different wave bands by using the DMD, and can acquire and shoot five or ten pictures without crosstalk between each other by a single frame, so that only two hundred frames or one hundred frames need to be shot, and compared with Shan Zhenshan pictures, the speed is improved by five times or ten times, the imaging speed is greatly improved, and the invention can be applied to the field of ophthalmology for carrying out ultra-fast volume-rate stable retina imaging.
3. The invention uses a full-field illumination mode to replace the traditional point focusing mode illumination, uses a two-dimensional camera to replace a one-dimensional linear array camera, omits transverse scanning, can adopt an objective lens with high numerical aperture, and improves the imaging efficiency and the transverse resolution.
4. The sample arm light path and the reference arm light path are identical, so that the dispersion difference of the two light paths is effectively reduced; and the same light path can ensure the spatial consistency of the two beams of light, and finally the formed interference fringes can realize imaging under high resolution.
Drawings
Fig. 1 is a schematic structural view of embodiment 1 of the present invention.
Fig. 2 is a schematic diagram of the optical path of the present invention.
FIG. 3 is a schematic diagram of a multi-wavelength fringe image output by the system of the present invention.
In the figure: 110. a light source; 120. a first reflective grating; 130. a first doublet lens; 140. DMD digital micromirror; 150. a second double cemented lens; 160. a second reflective grating; 170. a third lens; 180. a fourth lens; 190. a first lens; 200. a beam splitter; 210. a second face; 220. a first microobjective; 230. an object to be imaged; 310. a third face; 320. a neutral density filter; 330. a second microobjective; 340. a plane mirror; 410. a fourth face; 420. a second lens; 430. a reflecting mirror; 440. a transmissive grating; 450. a third doublet lens; 460. a camera; 470. and (5) a terminal.
Detailed Description
The technical scheme of the invention is further described below with reference to the attached drawings and specific embodiments.
Example 1
Referring to fig. 1, a full field swept optical coherence tomography system for parallel acquisition, comprising: beam splitter 200, light source input optical path, reference arm optical path, sample arm optical path, camera acquisition optical path. The beam splitter in this embodiment is a 50/50 beam splitter.
The light source input light path includes: a light source 110, a first reflective grating 120, a first doublet 130, a DMD digital micromirror 140, a second doublet 150, a second reflective grating 160, a beam expander, a first lens 190.
In the light source input optical path, the order of light emitted by the light source 110 passing through the instrument is sequentially a first reflective grating 120, a first double-cemented lens 130, a DMD digital micromirror 140, a second double-cemented lens 150, a second reflective grating 160, a beam expander, and a first lens 190.
In this embodiment, a broadband laser source is used, the light emitted by the broadband laser source is firstly directed onto the first reflection-type grating 120, then the spectrum is dispersed in different angles through the grating, then the spectrum is focused and is applied onto the DMD through the lens, then the on-off of the micromirror is controlled by loading pixel patterns with different widths at different positions of the DMD, the pixel patterns are changed into white pixels at certain positions in the black background pattern to control the micromirror, the deflection of the white pixel bar is +12° to indicate the wavelength required by the on-state reflection, and the deflection angle is-12 °And dump the unwanted spectrum. The spectrum impinging on the DMD is passed through the grating equationThe calculated angle can obtain a wide spectrum range, so that the light wavelength corresponding to the position of each micromirror which coincides with the spectrum line in the DMD is different, and the width of a single micromirror also represents the line width of a fixed value in space wavelength, so that the micromirror at the required position can reflect the required wavelength by only deflecting +12°. The reflected wavelength is converged into a light spot by the second double-cemented lens 150 and the second reflection type grating 160, and then is expanded by the beam expander, and finally is focused by the first lens 190 and directed to the first face of the beam splitter.
In the present embodiment, the beam expander is a light beam expander lens group composed of the third lens 170 and the fourth lens 180.
The sample arm light path includes: a second face 210 of the beam splitter, a first microscope objective 220, an object 230 to be imaged. The light emitted from the second face 210 of the beam splitter sequentially passes through the first microscope objective 220 and the object 230 to be imaged in sequence. The light is split into two beams by the beam splitter after passing through the 50/50 beam splitter, wherein fifty percent of the light is emitted by the second face 210 of the beam splitter 200 (the other fifty percent of the light is emitted by the third face 310 of the beam splitter), and is emitted to the first microscope objective 220, and after passing through the beam converging light spot of the first microscope objective 220, the light with different wavelengths is emitted to the object 230 to be imaged, so that scanning imaging of the object is realized; after striking the object to be imaged, the light reflected back by the object is directed back towards the second face 210 of the beam splitter.
The reference arm optical path includes: a third face 310 of the beam splitter, a neutral density filter 320, a second microscope objective 330, a plane mirror 340. The light emitted from the third face 310 of the beam splitter sequentially passes through the neutral density filter 320, the second microscope objective 330 and the plane mirror 340 in sequence. The light emitted from the third face 310 of the beam splitter passes through the neutral density filter 320 to adjust the light power, then passes through the second micro objective lens 330, and passes through the beam-converging light spot of the second micro objective lens 330 to be emitted to the plane mirror 340; after striking the mirror 340, the light is reflected back from the mirror 340 and back toward the third face 310 of the beam splitter.
A neutral density filter 320 is provided in the reference arm path to reduce the optical power, but does not affect the spatial properties of the light, and the optical path lengths of the reference arm path and the sample arm path are consistent. Similarly, a neutral density filter can be added in the sample arm light path, so that the elements of the reference arm light path and the sample arm light path are completely consistent.
The camera acquisition light path includes: a fourth face 410 of the beam splitter, a second lens 420, a mirror 430, a transmissive grating 440, a third doublet 450, a camera 460, a terminal 470. The light emitted from the fourth surface 410 of the beam splitter sequentially passes through the second lens 420, the reflecting mirror 430, the transmissive grating 440, the third double-cemented lens 450, the camera 460 and the terminal 470 in the order of the instrument, wherein the terminal is a computer in this embodiment, and the camera 460 is a two-dimensional camera. The light reflected by the reference arm light path is emitted to the third face 310 of the beam splitter 200 and then emitted by the fourth face 410 of the beam splitter, the light reflected by the sample arm light path is emitted to the second face 210 of the beam splitter 200 and then emitted by the fourth face 410 of the beam splitter, two light beams interfere and are emitted to the second lens 420 to form a whole parallel light beam, the light beams with different wavelengths are emitted to the transmission type grating 440 through the reflecting mirror 430, the light beams with different wavelengths are separated after passing through the transmission type grating 440, the separated light beams are further emitted to the third double-cemented lens 450, the light beams are focused after passing through the third double-cemented lens, a colorful rainbow line appears on the two-dimensional camera plane after focusing, and finally a plurality of parallel interference images without crosstalk can be displayed on each other through the computer terminal.
Example 2
Referring to fig. 2, this is an imaging principle optical path of a full-field swept-frequency optical coherence tomography system acquired in parallel, comprising: a first lens 190, a beam splitter 200, a first micro-objective 220, a second lens 420, a transmission grating 440, a third doublet 450, a camera 460, a terminal 470.
As an example, the wavelength range of the broadband laser light source in this embodiment is 535 to 625nm, and five wavelengths with a 20nm bandwidth of 0.1nm interval are loaded by the DMD.
The light emitted by the first lens 190 sequentially passes through the beam splitter 200, the first micro objective 220, the second lens 420, the transmission grating 440, the third double-cemented lens 450, the camera 460 and the terminal 470 in sequence.
The parallel light rays pass through the first lens 190, are focused on the beam splitter, are irradiated onto the first micro objective 220 through the beam splitter 200 and multiple reflections, pass through the first micro objective 220, and are irradiated onto a sample plane in parallel; after being reflected from the sample plane, the light returns in the original path in the sample arm, after passing through the first micro objective 220, the light is expanded through the second lens 420, and then is irradiated onto the transmission type grating 440 through the reflecting mirror 430, interference waves with different wavelengths are separated in the transverse direction due to the spatial dispersion of the grating, pass through the transmission type grating 440, then are directed to the third double-cemented lens 450, are converged through the third double-cemented lens 450, then the light shows a colorful rainbow line in the transverse direction of the two-dimensional camera, finally five parallel interference images with the wavelength interval of 20nm and without crosstalk can be displayed through the computer terminal, and the three-dimensional depth information image of the sample is obtained by reconstructing the depth information of the sample at each wavelength by combining an inverse Fourier transform method. Referring to fig. 3, five interference fringe images without crosstalk between each other can be captured simultaneously by loading five white pixel strips through the DMD to filter out wavelengths with intervals of 20nm and bandwidths of 0.1nm, 600nm, 580nm, 560nm and 540nm, and combining imaging principle single frames collected in parallel, then the positions of the white pixel strips are controlled by a computer to change, and the next frame can capture interference fringe images without crosstalk between each other in different wave bands of 621nm, 601nm, 581nm, 561nm and 541nm simultaneously, so that the imaging speed is greatly improved.
Example captured fringeyIn the axial direction, when the sample has a three-dimensional profile, the power spectral density of the light is exemplified by an interference imageObeying Gaussian distribution->After the collected interference image filters out the direct current term and the self-coherent term, the light intensity of the interference image is +.>Therein, whereinI r AndI s the reflected light intensity of the reference mirror and the back reflected light intensity of the sample are shown respectively,k 0 for the center wavelength of the light, 2σ is the standard deviation bandwidth of the power spectrum, and the light emitted by the light source filtering light path is divided into reference light and sample light, the power ratio is +.> (0<α<1). The back reflection light intensity information based on the interference spectrum of the measuring arm and the reference arm and different depths of the sample is the relation of a pair of Fourier transformation pairsI c (k) Performing inverse Fourier transform->Depth information of the sample is obtained.
Although the embodiments of the present invention have been specifically described above, the present invention is not limited thereto, and the scope of the present invention is not limited thereto. Various equivalent modifications and substitutions and other embodiments will occur to those skilled in the art without departing from the spirit and scope of the present invention.
Claims (10)
1. The full-field sweep-frequency optical coherence tomography system for parallel acquisition comprises a beam splitter (200), four sides of which are respectively connected with a light source input light path, a reference arm light path, a sample arm light path and a camera acquisition light path,
the light source input optical path sequentially comprises a light source (110), a first reflection type grating (120), a first double-cemented lens (130), a DMD digital micro-mirror (140), a second double-cemented lens (150), a second reflection type grating (160), a beam expander and a first lens (190) along the optical path;
the camera acquisition optical path sequentially comprises a second lens (420), a reflecting mirror (430), a transmission type grating (440), a third double-cemented lens (450) and a camera (460) along the optical path;
parallel light rays output by a light source input light path enter a first surface of a beam splitter (200) through a first lens (190), enter a reference arm light path and a sample arm light path through a second surface (210) and a third surface (310) of the beam splitter respectively, light reflected by the reference arm light path and the sample arm light path returns along an original light path, interference occurs after the light rays exit through a fourth surface (410) of the beam splitter, and the interference light rays are captured by a camera (460) after passing through a second lens (420), a reflecting mirror (430), a transmission type grating (440) and a third double-cemented lens (450) in sequence.
2. The system of claim 1, wherein the light source (110) is a broadband laser light source.
3. The system of claim 1, wherein the camera (460) is a two-dimensional camera.
4. The system of claim 1, wherein the reference arm optical path and the sample arm optical path have the same optical path length.
5. The system of claim 4, wherein the optical path components of the reference arm optical path and the sample arm optical path are identical in composition.
6. The system of claim 1, wherein the sample arm optical path comprises a first microscope objective (220), an object (230) to be imaged; the reference arm light path comprises a second microscope objective (330) and a plane mirror (340).
7. The system of claim 1, wherein the beam splitter is a 50/50 beam splitter.
8. The system of claim 1, wherein the DMD digital micromirror (140) controls the turning on and off of the micromirror by loading a pattern of pixels of different widths at different locations.
9. The system of claim 1, wherein the beam expander is a beam expander lens group consisting of two lenses.
10. The system of claim 1, further comprising a terminal (470), wherein the three-dimensional depth information image of the sample is obtained by reconstructing the depth information of the sample at each wavelength using an inverse fourier transform method after the multi-wavelength interference image captured by the camera (460) is obtained via the terminal (470).
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Citations (9)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101427911A (en) * | 2008-12-22 | 2009-05-13 | 浙江大学 | Method and system for detecting ultra-broadband optical spectrum of ultrahigh-resolution spectrum field OCT |
| CN103256981A (en) * | 2013-04-18 | 2013-08-21 | 中国科学院长春光学精密机械与物理研究所 | Optical system of miniature cylindrical mirror multi-grating spectrum analysis |
| CN103616074A (en) * | 2013-11-21 | 2014-03-05 | 中国科学院长春光学精密机械与物理研究所 | Wavelength calibration method for digital micromirror grating spectrometer |
| CN103743702A (en) * | 2013-12-16 | 2014-04-23 | 中国科学院长春光学精密机械与物理研究所 | Spectrum two-dimensional folding Hadamard conversion near infrared spectrometer |
| CN104066370A (en) * | 2011-12-30 | 2014-09-24 | 威孚莱有限公司 | An integrated device for ophthalmology |
| CN106770145A (en) * | 2017-03-10 | 2017-05-31 | 上海理工大学 | Multi-path frequency-division duplicating fluorescence microscopy detection method is realized based on DMD |
| CN113317784A (en) * | 2021-06-08 | 2021-08-31 | 南京师范大学 | Micron-scale linear focusing scanning microspectrum optical coherence tomography system |
| CN115639198A (en) * | 2022-11-15 | 2023-01-24 | 南京理工大学 | Full-field optical space-time coherent coding dynamic volume imaging device and method |
| CN115937080A (en) * | 2022-09-30 | 2023-04-07 | 浙大宁波理工学院 | Hexagonal lattice illumination super-resolution microscopic system and image reconstruction method |
-
2024
- 2024-03-04 CN CN202410240540.0A patent/CN117825279B/en active Active
Patent Citations (9)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101427911A (en) * | 2008-12-22 | 2009-05-13 | 浙江大学 | Method and system for detecting ultra-broadband optical spectrum of ultrahigh-resolution spectrum field OCT |
| CN104066370A (en) * | 2011-12-30 | 2014-09-24 | 威孚莱有限公司 | An integrated device for ophthalmology |
| CN103256981A (en) * | 2013-04-18 | 2013-08-21 | 中国科学院长春光学精密机械与物理研究所 | Optical system of miniature cylindrical mirror multi-grating spectrum analysis |
| CN103616074A (en) * | 2013-11-21 | 2014-03-05 | 中国科学院长春光学精密机械与物理研究所 | Wavelength calibration method for digital micromirror grating spectrometer |
| CN103743702A (en) * | 2013-12-16 | 2014-04-23 | 中国科学院长春光学精密机械与物理研究所 | Spectrum two-dimensional folding Hadamard conversion near infrared spectrometer |
| CN106770145A (en) * | 2017-03-10 | 2017-05-31 | 上海理工大学 | Multi-path frequency-division duplicating fluorescence microscopy detection method is realized based on DMD |
| CN113317784A (en) * | 2021-06-08 | 2021-08-31 | 南京师范大学 | Micron-scale linear focusing scanning microspectrum optical coherence tomography system |
| CN115937080A (en) * | 2022-09-30 | 2023-04-07 | 浙大宁波理工学院 | Hexagonal lattice illumination super-resolution microscopic system and image reconstruction method |
| CN115639198A (en) * | 2022-11-15 | 2023-01-24 | 南京理工大学 | Full-field optical space-time coherent coding dynamic volume imaging device and method |
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