CN117297555B - Spectrum processing system based on parallel light calculation and application of spectrum processing system in OCT - Google Patents
Spectrum processing system based on parallel light calculation and application of spectrum processing system in OCT Download PDFInfo
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Abstract
The invention relates to a spectrum processing system based on parallel light calculation and application thereof in OCT, in particular to a spectrum processing system based on parallel light calculation and application thereof in an OCT imaging system, belonging to the technical fields of light calculation and biomedical optical imaging, in particular to application thereof in an OCT imaging system. The OCT imaging system based on parallel light calculation is different from the conventional OCT system which uses an electronic computer to process spectrum data, adopts the parallel light calculation system to perform fractional order/integer order Fourier transform on spectrum signals output by an OCT interferometer, and can directly obtain structural information of a sample in a full-light mode, so that the imaging system can greatly improve the imaging speed.
Description
Technical Field
The invention relates to a spectrum processing system based on parallel light calculation and application thereof in OCT, in particular to a spectrum processing system based on parallel light calculation and application thereof in an OCT imaging system, belonging to the technical fields of light calculation and biomedical optical imaging, in particular to application thereof in an OCT imaging system.
Background
Optical coherence tomography (optical coherence tomography, OCT) technology has undergone many changes since the beginning of the 90 s of the last century, and one of the most significant impetus to promote continued innovation is the pursuit of OCT imaging speed. The high-speed real-time OCT can enable people to know the deep structure of organisms in time, and can provide guarantee for quick judgment in the biological detection, medical diagnosis and operation process. However, the prior OCT technology still has a series of problems in terms of speed, mainly embodied in a back-end photodetection system, a data acquisition system, and a data processing system.
Firstly, the OCT imaging of the biological sample has a requirement on the detection bandwidth of the system, under the condition of a certain detection depth, the higher the scanning frequency of a light source line is, the higher the bandwidth of a required photoelectric detector is, and the price of the photoelectric detector with high bandwidth is also very expensive; second, data acquisition systems are subject to greater pressure relative to photodetection systems. As known from the sampling law, the information of the analog signal can be accurately recovered only when the data acquisition system has a sampling rate which is more than twice the highest bandwidth of the photoelectric detection system. However, high sampling rate data acquisition cards have not been domesticated and the imported products are very expensive; finally, the difficulties faced by data processing systems are most troublesome compared to photodetection systems and data acquisition systems. There are two aspects to consider for a data processing system. On the one hand, the data collected by the data collection system needs to be transmitted to the computer cache through the transmission bus, and the transmission bandwidth of the bus interface is limited, which brings great difficulty to the real-time data transmission of the ultra-high-speed OCT system. On the other hand, even if data is smoothly transmitted into an electronic computer, the reconstruction of OCT images is difficult to accomplish in time by using the existing electronic computer to perform real-time data processing on mass data. For example, in the data processing of conventional swept OCT systems, the fast fourier transform operation is a decisive factor limiting the processing speed. Although the fast fourier transform algorithm is used as a fast algorithm for fourier transform processing, the data processing efficiency of a computer is improved to a great extent, but the speed of the fast fourier transform algorithm still cannot meet the current requirements in the face of a large amount of spectrum data brought by an ultra-high-speed sweep OCT system.
In view of the above, the existing spectrum data processing system has a certain limitation, so a new spectrum processing method is needed to overcome the current difficulties.
Disclosure of Invention
The technical solution of the invention is as follows: the system is used for carrying out real-time high-speed processing on spectrum big data.
The technical scheme of the invention is as follows:
the spectrum processing system is used for acquiring sample structure information in OCT, acquiring complex spectrum and spectrum phase information, acquiring spectrum for eliminating a base line and distinguishing a near characteristic peak, acquiring integral of the spectrum and acquiring a filtered spectrum;
the spectrum processing system comprises a two-dimensional space template, a dispersive element and an area array camera;
the two-dimensional space template is used for carrying out two-dimensional space modulation on the spectrum signal to be processed and outputting the optical signal subjected to the two-dimensional space modulation to the dispersive element;
the dispersion element is used for dispersing the optical signal subjected to two-dimensional spatial modulation and outputting the optical signal to the area array camera;
the area array camera is used for receiving the dispersed light;
when the spectrum processing system is used for acquiring sample structure information in OCT, the two-dimensional space template is used for acquiring the sample structure information in OCTxThe direction adopts a chirp function (i.e. a chirp function) as the shape of the transmission function;
when the spectrum processing system is used for acquiring complex spectrum and spectrum phase information, the two-dimensional space template is formed in the following wayxThe direction takes the shape of the following formula (1) as a transmission function:
（1）
wherein α is the fractional order, sgn (x) is a sign function, ε and x 0 Is a parameter;
when the spectrum processing system is used for acquiring the spectrum of the elimination base line and distinguishing the characteristic peaks close to each other, the two-dimensional space template adopts the following formula (2) as the shape of the transmission function in the x direction:
（2）
wherein,for fractional order, ++>Is a fractional derivative operator, σ is a parameter;
when the spectrum processing system is used to acquire the integral of the spectrum, the two-dimensional spatial template takes the shape of the following equation (3) as a transmission function in the x-direction:
（3）
wherein,γfor fractional order, H (x) is a step function, x 1 Is a parameter;
when the spectral processing system is used to obtain the filtered spectrum, the two-dimensional spatial template takes the inverse fourier transform of the filtered frequency response function in the x-direction as the shape of the transmission function.
The dispersion element is a dispersion prism, a reflection grating or a transmission grating, and is used for performing all-optical convolution operation (namely convolution between a spectrum signal and a modulation function) on the optical signal after spatial modulation; preferably, when a dispersion prism is used as the dispersion element, an incident angle of incident light into the dispersion prism is a set value, so that an angle at which light of a center wavelength exits from the dispersion prism is equal to the incident angle, and an angle at which light of the center wavelength is deflected by the dispersion prism is minimized;
the application of a spectrum processing system based on parallel light calculation in an OCT imaging system is provided, wherein the spectrum processing system is applied to the OCT imaging system;
the OCT imaging system comprises a light source, an OCT interferometer, a spectrum processing system based on parallel light calculation and a computer;
the light source is used for outputting parallel broadband light to the OCT interferometer;
the OCT interferometer is used for receiving the parallel broadband light output by the light source, dividing the received parallel broadband light into two paths, and outputting interference light to a spectrum processing system based on parallel light calculation after interference occurs;
the OCT interferometer comprises a first cylindrical lens, a second cylindrical lens, a beam splitting prism, a first convex lens, a second convex lens, a third convex lens, a reference lens and a sample to be detected;
the parallel broadband light output by the light source is output to the first cylindrical lens, the first cylindrical lens converges the parallel broadband light in one direction and then converges the parallel broadband light through the first convex lens, and then the converged light is divided into two paths by the beam splitting prism, wherein one path of the converged light is output to the second convex lens, and the other path of the converged light is output to the third convex lens. The second convex lens converges the received converged light to a line on the sample surface, and the third convex lens converges the received converged light to a line on the reference mirror. The first convex lens and the second convex lens form a 4f system, the first convex lens and the third convex lens form a 4f system, and the design of the cylindrical lens and the two 4f systems is adopted, so that a plurality of points on a sample can be scanned simultaneously, and two paths of return light are ensured to be coherent in space. The return light of the reference lens and the return light of the sample are interfered at the beam splitting prism and then output to the second lens, and the second lens converts the return light into parallel light and outputs the parallel light to a spectrum processing system based on parallel light calculation;
the spectrum processing system based on parallel light calculation is used for receiving interference light output by the OCT interferometer, acquiring sample structure information according to the interference light and outputting the sample structure information to the computer;
the computer is used for receiving and displaying the sample structure information.
Advantageous effects
(1) The spectrum processing system based on parallel light calculation carries out full-light real-time high-speed operation on the spectrum signals by using the optical path, and the OCT imaging system based on parallel light calculation uses a parallel light calculation method to process a large amount of data spectrums generated by the OCT imaging system in real time, so that the structural information of a sample can be directly obtained in a full-light mode;
(2) The system can operate on the spectrum signals at an ultra-high speed, and the speed is far higher than that of the existing method for processing the spectrum signals based on the electronic computer, so that the system not only utilizes the one-dimensional distribution of light in space, but also utilizes the other space dimension, and can process multiple paths of spectrum signals at the same time.
(3) The OCT imaging system based on the parallel optical computing method is different from the conventional OCT for scanning the sample point by point, but adopts a parallel imaging mode to collect light on one line on the surface of the sample, can complete line scanning for hundreds to thousands times at one time, and then adopts the parallel optical computing system to perform fractional order/integer order Fourier transform on a spectrum signal output by an OCT interferometer, so that the structural information of the sample can be directly obtained in a full-light mode, and the imaging speed of the imaging system can be greatly improved.
Drawings
FIG. 1 is a schematic diagram of a spectral processing system based on parallel light computing according to the present invention;
fig. 2 is a schematic diagram of an OCT imaging system of the present invention based on a spectral processing system of parallel light computation.
Detailed Description
The invention will now be described in detail by way of example with reference to the accompanying drawings.
Examples
As shown in fig. 1, in the spectrum processing system based on parallel light calculation, input light is modulated by a two-dimensional space template 1, then dispersed by a dispersion element 2, and finally received by an area camera 3, which is the whole parallel light calculation process.
Wherein, the two-dimensional space template 1 can be a printed transparent film.
The dispersive element 2 may be a dispersive prism. When the dispersing element 2 is a dispersing prism, as a preferred embodiment, the incident angle of the incident light into the dispersing prism is a set value, so that the angle of the light with the central wavelength exiting from the dispersing prism is equal to the incident angle. At this time, the angle at which the light of the center wavelength is deflected by the prism is minimized. The area camera 3 may be replaced by a white screen for observing the light calculation result.
In the system, the incident light of the two-dimensional space template 1 has no spectrum change in the x direction, and consists of multiple paths of light to be processed in the y direction, wherein the spectrum of each path is a signal to be processed, and x and y are two orthogonal directions in the plane of the two-dimensional space template 1. The distribution of the transmission function of the two-dimensional space template 1 in the x-direction is a set function (determined by the required calculations performed on the spectrum) and does not change in the y-direction. After the dispersion by the dispersion prism, the divergent light is irradiated onto the area camera 3. The distribution of the data collected by the area camera 3 in the x 'direction is the result of the calculation of a certain path of optical signals, and the results of the calculation of multiple paths of light are arranged side by side in the y' direction, wherein x 'and y' are two orthogonal directions (two sides parallel to the rectangular photosensitive target surface of the camera) in the plane of the area camera 3. The result of the light calculation is the convolution between the spectral signal and the transmission function of the two-dimensional space template. As a preferred embodiment, the following details are provided: the y direction of the two-dimensional space template 1, the axial direction of the dispersive element 2 and one side (y' direction) of the photosensitive target surface of the area array camera 3 are parallel; the incident light direction of the two-dimensional space template 1 is vertical to the x and y directions; when the incident light reaches the area camera 3, the incident direction of the central wavelength is vertical to the x ', y' directions; the dispersive element 2 will only disperse light in the x 'direction and not in the y' direction.
Since there are 1024 columns of pixels of a typical area camera 3, the speed of parallel light computation is three orders of magnitude higher than that of single-pass light computation. The current high-speed 1024 x 1024 pixel area-array camera has a frame rate of 20KHz, so the operation speed of parallel light calculation can reach 20MHz, and the traditional method for processing spectrum data is difficult to realize the high speed.
As shown in fig. 2, the OCT imaging system of the spectral processing system based on parallel light calculation, in which parallel broadband light output from the light source 4 enters the OCT interferometer, is converged in one direction by the first cylindrical lens 5, and is then converged by the first convex lens 6. The light is then split by the beam splitting prism 7 into two paths, into the sample arm and the reference arm of the interferometer, respectively. In the sample arm of the interferometer, a second convex lens 8 concentrates the light onto a line on the surface of the sample 9. Likewise, at the reference arm of the interferometer, the third convex lens 10 converges the light on a line on the reference mirror 11. Here, the first convex lens 6 and the second convex lens 8 constitute a 4f system, and the first convex lens 6 and the third convex lens 10 constitute a 4f system. The design of cylindrical lenses and two 4f systems is adopted because one ensures that several points on the sample are scanned simultaneously and the other ensures that the two-arm return light is spatially coherent. After the return light of both arms interferes at the beam splitting prism 7, the return light is converted into parallel light by the second lens 12, and enters a spectrum processing system based on parallel light calculation.
The spectrum processing system based on parallel light calculation consists of a two-dimensional space template 1, a dispersion element 2 and an area array camera 3, wherein input light is modulated by the two-dimensional space template 1, dispersed by the dispersion element 2 and finally received by the area array camera 3, and the whole parallel light calculation process is realized. Finally, the computer 13 collects and displays the light calculation result via the data line. Preferably, the transmission function of the two-dimensional space template 1 is selected as follows: the chirp function (i.e., chirping function) is in the x direction and is unchanged in the y direction. The two-dimensional space template 1 can be a printed transparent film. The transmittance change interval of the two-dimensional space template 1 is from T 1 To T 2 . Wherein T is 1 For the minimum transmittance, T, provided by the two-dimensional space template 1 2 The intrinsic transmittance of the transparent material used for the two-dimensional space template 1. In the x-direction, the transmission function of the two-dimensional space template is in the shape of a chirp function at T 1 To T 2 Oscillating in between. The dispersive element 2 may be a dispersive prism. When the dispersing element 2 is a dispersing prism, the incident angle of the incident light entering the dispersing prism is a set value, so that the emergent angle of the light with the central wavelength from the dispersing prism is equal to the incident angle. At this time, the angle at which the light of the center wavelength is deflected by the prism is minimized. The area camera 3 may be replaced by a white screen for observing the light calculation result. The focal lengths of the first cylindrical lens 5, the second cylindrical lens 12, the first convex lens 6, the second convex lens 8, and the third convex lens 10 are the same or close. The splitting ratio of the splitting prism 7 may be 5:5, 4:6, 3:7, 2:8, 1:9. The OCT interferometer may employ a fiberized optical path.
It is apparent that the data acquired by the area camera 3 is a line structure (i.e. a-scan) of the sample in the x' direction. Unlike conventional OCT, which scans a sample point by point, optical computing OCT uses parallel imaging, i.e., focusing light onto a line on the surface of the sample 9. Thus, the optical signals originating from different locations of the sample are distributed exactly on the area camera 3 along the y' direction, and each frame of data acquired by the camera is then a B-scan image of the sample 9. If three-dimensional imaging is required, a galvanometer can be added to the sample arm for one-dimensional scanning in the other direction, which is omitted from the schematic. Finally, the result of the light calculation is entered into the computer 13 via the data line for collection and display on the screen. If an area camera with a 20KHz frame rate is used here, the operation speed of parallel light calculation can reach 20MHz (i.e., two tens of millions of times per second), which is a speed that is difficult to reach for conventional OCT.
In summary, the above embodiments are only preferred embodiments of the present invention, and are not intended to limit the scope of the present invention. Any modification, equivalent replacement, improvement, etc. made within the spirit and principle of the present invention should be included in the protection scope of the present invention.
Claims (9)
1. A spectral processing system based on parallel light computing, characterized by:
the spectrum processing system is used for acquiring sample structure information in OCT, acquiring complex spectrum and spectrum phase information, acquiring spectrum for eliminating a base line and distinguishing a near characteristic peak, acquiring integral of the spectrum and acquiring a filtered spectrum;
the spectrum processing system comprises a two-dimensional space template, a dispersive element and an area array camera;
the two-dimensional space template is used for carrying out two-dimensional space modulation on the optical signal to be processed and outputting the optical signal subjected to the two-dimensional space modulation to the dispersion element;
the dispersion element is used for dispersing the optical signal subjected to two-dimensional spatial modulation and outputting the optical signal to the area array camera;
the area camera is used for receiving the dispersed light.
2. A parallel light computing based spectral processing system according to claim 1, wherein:
when the spectral processing system is used to obtain sample structure information in OCT, the two-dimensional spatial template adopts the shape of the chirp function as a transmission function in the x-direction.
3. A parallel light computing based spectral processing system according to claim 1, wherein:
when the spectrum processing system is used for acquiring complex spectrum and spectrum phase information, the two-dimensional space template adopts the following formula (1) as the shape of the transmission function in the x direction:
wherein α is the fractional order, sgn (x) is a sign function, ε and x 0 Is a parameter.
4. A parallel light computing based spectral processing system according to claim 1, wherein:
when the spectrum processing system is used for acquiring the spectrum of the elimination base line and distinguishing the characteristic peaks close to each other, the two-dimensional space template adopts the following formula (2) as the shape of the transmission function in the x direction:
wherein beta is fractional order, D β For fractional derivative operators, σ is a parameter.
5. A parallel light computing based spectral processing system according to claim 1, wherein:
when the spectrum processing system is used to acquire the integral of the spectrum, the two-dimensional spatial template takes the shape of the following equation (3) as a transmission function in the x-direction:
H(x)(x+x 1 ) γ-1 (3)
wherein, gamma is fractional order, H (x) is step function, x 1 Is a parameter.
6. A parallel light computing based spectral processing system according to claim 1, wherein:
when the spectral processing system is used to obtain the filtered spectrum, the two-dimensional spatial template takes the inverse fourier transform of the filtered frequency response function in the x-direction as the shape of the transmission function.
7. A parallel light computing based spectral processing system according to claim 1, wherein:
the dispersive element is a dispersive prism, a reflective grating or a transmissive grating, and is used for providing dispersion for the spatially modulated optical signal, and can be mathematically regarded as full optical convolution operation, namely convolution between the spectral signal and the modulation function.
8. An application of a spectrum processing system based on parallel light calculation, which is characterized in that:
the spectrum processing system is applied to an OCT imaging system;
the OCT imaging system comprising a light source, an OCT interferometer, the parallel light calculation based spectral processing system of any of claims 1-7, and a computer;
the light source is used for outputting parallel broadband light to the OCT interferometer;
the OCT interferometer is used for receiving the parallel broadband light output by the light source, dividing the received parallel broadband light into two paths, and outputting interference light to a spectrum processing system based on parallel light calculation after interference occurs;
the spectrum processing system based on parallel light calculation is used for receiving interference light output by the OCT interferometer, acquiring sample structure information according to the interference light and outputting a corresponding result to a computer;
the computer is used for receiving and displaying the corresponding result.
9. The use of a parallel light computing based spectral processing system according to claim 8, wherein:
the OCT interferometer comprises a first cylindrical lens, a second cylindrical lens, a beam splitting prism, a first convex lens, a second convex lens, a third convex lens and a reference lens;
the parallel broadband light output by the light source is output to a first cylindrical lens, the first cylindrical lens converges the parallel broadband light in one direction and then converges the parallel broadband light through a first convex lens, then the converged light is divided into two paths by a beam splitting prism, one path of the converged light is output to a second convex lens, the other path of the converged light is output to a third convex lens, the second convex lens converges the received converged light to a line on the surface of a sample, the third convex lens converges the received converged light to a line on a reference lens, return light of the reference lens and return light of the sample interfere at the beam splitting prism and then are output to the second cylindrical lens, and the second cylindrical lens converts the parallel light into parallel light and outputs the parallel light to a spectrum processing system based on parallel light calculation.
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Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103271721A (en) * | 2013-05-17 | 2013-09-04 | 浙江大学 | Method and system for detecting parallel OCT based on spectrum coding and orthogonal light splitting |
| CN103976762A (en) * | 2014-05-22 | 2014-08-13 | 中国科学院高能物理研究所 | Full-automatic mammary gland biopsy puncture method and device |
| CN104688188A (en) * | 2015-03-12 | 2015-06-10 | 清华大学 | Spectral optical coherence imaging system based on optic computation |
| CN106691394A (en) * | 2017-02-17 | 2017-05-24 | 浙江大学 | high resolution long focal depth OCT imaging system based on optical path code and method thereof |
| CN113599672A (en) * | 2021-08-16 | 2021-11-05 | 合肥德铭电子有限公司 | Gastrointestinal surgical balloon navigation system with endoscopic visualization and pressure detection |
| CN116849625A (en) * | 2023-09-04 | 2023-10-10 | 北京理工大学 | Intensity modulation type optical coherence tomography system based on light calculation |
Family Cites Families (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6795199B2 (en) * | 2001-07-18 | 2004-09-21 | Avraham Suhami | Method and apparatus for dispersion compensated reflected time-of-flight tomography |
| EP2841875A4 (en) * | 2012-04-23 | 2016-01-20 | Univ Ben Gurion | True-spectroscopic dual mode high resolution full-field optical coherence tomography using liquid crystal devices |
| CN105559756B (en) * | 2016-02-05 | 2019-11-15 | 浙江大学 | Based on the compound microangiography method and system of total space modulation spectrum segmentation angle |
-
2023
- 2023-11-29 CN CN202311608802.6A patent/CN117297555B/en active Active
Patent Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103271721A (en) * | 2013-05-17 | 2013-09-04 | 浙江大学 | Method and system for detecting parallel OCT based on spectrum coding and orthogonal light splitting |
| CN103976762A (en) * | 2014-05-22 | 2014-08-13 | 中国科学院高能物理研究所 | Full-automatic mammary gland biopsy puncture method and device |
| CN104688188A (en) * | 2015-03-12 | 2015-06-10 | 清华大学 | Spectral optical coherence imaging system based on optic computation |
| CN106691394A (en) * | 2017-02-17 | 2017-05-24 | 浙江大学 | high resolution long focal depth OCT imaging system based on optical path code and method thereof |
| CN113599672A (en) * | 2021-08-16 | 2021-11-05 | 合肥德铭电子有限公司 | Gastrointestinal surgical balloon navigation system with endoscopic visualization and pressure detection |
| CN116849625A (en) * | 2023-09-04 | 2023-10-10 | 北京理工大学 | Intensity modulation type optical coherence tomography system based on light calculation |
Non-Patent Citations (1)
| Title |
|---|
| 并行谱域光学相干层析成像技术的研究进展;沈毅 等;中国激光;第1-9页 * |
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