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WO2014084556A1 - Dispositif de tomographie à cohérence optique (oct) pour traitement de données oct tridimensionnelles - Google Patents

Dispositif de tomographie à cohérence optique (oct) pour traitement de données oct tridimensionnelles Download PDF

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Publication number
WO2014084556A1
WO2014084556A1 PCT/KR2013/010701 KR2013010701W WO2014084556A1 WO 2014084556 A1 WO2014084556 A1 WO 2014084556A1 KR 2013010701 W KR2013010701 W KR 2013010701W WO 2014084556 A1 WO2014084556 A1 WO 2014084556A1
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data
oct
scan line
processing
cores
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Korean (ko)
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엄태중
김창석
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Gwangju Institute of Science and Technology
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Gwangju Institute of Science and Technology
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/06—Devices, other than using radiation, for detecting or locating foreign bodies ; Determining position of diagnostic devices within or on the body of the patient
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N21/47—Scattering, i.e. diffuse reflection
    • G01N21/4795—Scattering, i.e. diffuse reflection spatially resolved investigating of object in scattering medium
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • 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
    • A61B5/0062—Arrangements for scanning
    • A61B5/0066—Optical coherence imaging
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00—Measuring instruments characterised by the use of optical techniques
    • G01B9/02—Interferometers
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00—Measuring instruments characterised by the use of optical techniques
    • G01B9/02—Interferometers
    • G01B9/02001—Interferometers characterised by controlling or generating intrinsic radiation properties
    • G01B9/02002—Interferometers characterised by controlling or generating intrinsic radiation properties using two or more frequencies
    • G01B9/02004—Interferometers characterised by controlling or generating intrinsic radiation properties using two or more frequencies using frequency scans
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00—Measuring instruments characterised by the use of optical techniques
    • G01B9/02—Interferometers
    • G01B9/02083—Interferometers characterised by particular signal processing and presentation
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00—Measuring instruments characterised by the use of optical techniques
    • G01B9/02—Interferometers
    • G01B9/0209—Low-coherence interferometers
    • G01B9/02091—Tomographic interferometers, e.g. based on optical coherence
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated

Definitions

  • the present invention relates to an optical coherent tomography (OCT) apparatus for processing a 3D image at high speed. More particularly, the present invention relates to a high speed processing of a 3D image using a 64-bit-based dynamic memory allocation method. The present invention relates to an optical interference tomography apparatus.
  • OCT optical coherent tomography
  • tomography imaging techniques such as X-ray CT, MRI, and ultrasound imaging are widely used in the medical field. These techniques are used for diagnosis in specific fields according to different physical properties, resolutions, penetration depths, and the like. Recently, research on the development of a medical diagnostic apparatus using light is being actively conducted.
  • OCT optical coherence tomography apparatus
  • Optical coherence tomography is a technology based on OCDR (Optical Coherence Domain Tomography), and Duguay and Matic first presented the possibility of 'seeing through skin' in the early 1970s.
  • This technique uses the low coherence characteristics of the laser to cross-sectional imaging the non-invasive and non-contact method of the internal structure of the biological tissue by measuring optical reflection. To do.
  • OCT researches to complement the human hazard, price, and measurement resolution problems of existing measurement equipment such as X-ray computed tomography (CT), ultrasound imaging, and magnetic resonance imaging. It is becoming.
  • CT computed tomography
  • ultrasound imaging ultrasound imaging
  • magnetic resonance imaging It is becoming.
  • the imaging technique of the OCT is based on a Michelson interferometer, and the output of a light source having low coherence is divided into two directions of an interferometer arm.
  • the reflected light returned from the reference stage and the back scattered light from the sample stage meet again to cause interference and are imaged through signal processing.
  • the interference properties of light reflected from biological tissues have time-of-flight information about the microstructures derived from the reflective boundaries and back-scattering of the tissues.
  • the optical coherence tomography apparatus uses light, so it is harmless to use it for diagnosing the human body.
  • the most representative diagnostic field is diagnosis of the retina of the eye.
  • OCT has higher resolution (resolution) than conventional ultrasound images, and can take many advantages such as non-incision imaging of the inside of an object, real-time tomography imaging, and the manufacture of small and low-cost devices. Have.
  • An object of the present invention is to provide a user by processing in real time a large amount of data of several gigabytes or more generated when configuring a real-time three-dimensional image using the OCT.
  • an optical coherence tomography may be disclosed.
  • the optical coherence tomography apparatus is configured to receive an electric light source for generating coherent light, an interferometer for generating an interference fringe from a sample measured by receiving light emitted from the light source, and an interference fringe irradiated from the interferometer.
  • the obtained three-dimensional OCT data includes a total of l * m * n data including l data along the A-scan line, m along the B-scan line, and n data along the C-scan line. Defined, and a data address may be defined for each of the l * m * n data.
  • the obtained three-dimensional OCT data is grouped into a plurality of data sets along a scan line direction of one of the A-scan line, the B-scan line, or the C-scan line, and the plurality of data sets are the processing unit.
  • parallel processing By parallel processing.
  • the processing unit may include a multi-core processor (central processing unit, CPU), and the plurality of data sets may be parallelized by being divided by the number of cores (threads) of the multi-core processor.
  • CPU central processing unit
  • the display apparatus may further include a display unit configured to display data imaged by the processor, wherein the receiving unit converts the interference fringe into the electrical signal in one of the cores of the multi-core processor.
  • the display is executed on one core not used by the receiver of the cores of the multi-core processor, and the processor is configured to perform the plurality of data sets on cores not used by the processor and the receiver among the cores of the multi-core processor.
  • the number of cores used in the processing unit may be two or more.
  • the apparatus may further include a rendering unit for rendering the obtained 3D OCT data, wherein the processing unit processes the plurality of data sets in cores not used in the processing unit and the receiving unit among the cores of the multi-core processor.
  • a plurality of data sets may be processed in parallel to form a 2D cross-sectional image, and the rendering unit may render the 2D cross-sectional image to image in 3D.
  • a method for processing three-dimensional OCT data obtained by an optical coherence tomography is disclosed.
  • the method may include defining a data address for each of the obtained data using a 64-bit dynamic memory allocation scheme.
  • the obtained three-dimensional OCT data includes a total of l * m * n data including l data along the A-scan line, m along the B-scan line, and n data along the C-scan line. Defined, and a data address may be defined for each of the l * m * n data.
  • the obtained three-dimensional OCT data is grouped into a plurality of data sets along a scan line direction of one of the A-scan line, B-scan line or C-scan line, the plurality of data sets are multi-core It can be processed in parallel by processing in a plurality of cores of the processor.
  • a computer-readable recording medium including program code for causing at least one computer to process three-dimensional OCT data obtained from an optical coherence tomography (OCT) device.
  • OCT optical coherence tomography
  • the computer-readable recording medium may include program code for causing at least one computer to define a data address using a 64-bit based dynamic memory allocation scheme for each of the obtained three-dimensional OCT data.
  • the obtained three-dimensional OCT data includes a total of l * m * n data including l data along the A-scan line, m along the B-scan line, and n data along the C-scan line. Defined, and a data address may be defined for each of the l * m * n data.
  • the obtained three-dimensional OCT data is grouped into a plurality of data sets along a scan line direction of one of the A-scan line, B-scan line or C-scan line, the plurality of data sets are multi-core It can be processed in parallel by processing in a plurality of cores of the processor.
  • addressing and parallel processing the three-dimensional OCT data by 64-bit-based dynamic memory allocation method can increase the data processing speed 3 Real-time dimensional OCT images can be implemented.
  • OCT optical coherence tomography apparatus
  • Figure 2 shows a schematic diagram when the OCT is SS-OCT using a two-dimensional camera according to an embodiment of the present invention.
  • FIG 3 illustrates a data set of scanning one three-dimensional volume image of the human eye in accordance with one embodiment of the present invention.
  • FIG. 4 illustrates a parallel processing method of a plurality of data sets according to an embodiment of the present invention.
  • FIG. 5 is a schematic diagram of an operation process of obtaining, processing, and outputting an interference signal in an OCT according to an embodiment of the present invention.
  • FIG. 6 is a schematic diagram of an operation process of obtaining, processing, rendering, and outputting an interference signal in an OCT according to an embodiment of the present invention.
  • FIG. 7 is a flowchart of a method for processing 3D OCT data obtained in an optical coherence tomography apparatus according to an embodiment of the present invention.
  • OCT optical coherence tomography apparatus
  • the OCT includes a light source unit 10 generating coherent light, an interferometer unit generating an interference fringe from a sample measured by receiving the emitted light from the light source unit 10, and the interferometer unit It may include a receiver 50 for receiving the interference fringe to be irradiated into an electrical signal, and a processor 60 for imaging the data obtained by the receiver.
  • the light source unit 10 may generate coherent light.
  • the light source unit 10 includes a superluminescent LED (SLD) that emits light and optical band dividing means (e.g., a prism or the like) for emitting light from the SLD as broadband light. ) May be included.
  • SLD superluminescent LED
  • optical band dividing means e.g., a prism or the like
  • the light source unit 10 may include a tunable laser and an SOA.
  • the OCT is a full field OCT (FF-OCT)
  • an appropriate broadband light source may be used accordingly.
  • the light generated from the light source unit 10 of the OCT should be broadband, and should have an intensity that is not harmful when irradiated to the human body.
  • the interferometer includes a beam splitter 20 for splitting the coherent light generated from the light source unit 10 into a first light incident to the reference stage 30 and a second light incident to the sample stage.
  • a reference stage 30 including a mirror or the like for reflecting one light back to the beam splitter 20 and a sample stage for scanning the sample using the incident second light and reflecting it back to the beam splitter 20 40 may include.
  • the beam splitter 20 splits the light from the light source unit 10 into a first light to the reference stage 30 and a second light to the sample stage 40 and from the reference stage 30 and the sample stage 40. It combines and interferes with the incoming light.
  • the beam splitter 20 should be able to divide the broadband light from the light source unit 10 into the first light and the second light accurately at a predetermined ratio without loss.
  • the beam splitter 20 mainly divides the first light and the second light by a ratio of 50:50, and may include, for example, an optical coupler.
  • the reference stage 30 may include, for example, a mirror or the like to reflect light incident from the beam splitter 20.
  • the reference stage 30 is for generating reference light for generating an interference signal with light incident from the sample stage 40 to the beam splitter 20, and according to the optical path of the sample stage 40.
  • the optical path length of (30) shall be adjusted accordingly.
  • the sample stage 40 includes, for example, a galvanometer or the like, and is a portion for scanning a sample (for example, an eye of a human body) using light incident from the beam splitter 20.
  • the light reflected from the sample may be incident to the beam splitter 20 again to be combined with the light from the reference stage 30 to generate an interference signal.
  • the OCT may include a receiver 50 for receiving the interference signal generated by combining the light reflected from the reference stage 30 and the sample stage 40 in the beam splitter 20 and converting the interference signal into an electrical signal.
  • the receiver 50 may include a digitizer (1 GSample / second or more) capable of acquiring high speed signals, and in the case of SD-OCT, the receiver 50 may use a high speed frame grabber.
  • the OCT is a global full field OCT (FF-OCT)
  • FF-OCT full field OCT
  • an appropriate optical signal detecting element may be used accordingly.
  • the interference signal data may be acquired at a speed capable of realizing a sample image in real time.
  • Figure 2 shows a schematic diagram when the OCT is SS-OCT using a two-dimensional camera according to an embodiment of the present invention.
  • the light source unit 10 may include a wavelength tunable laser 101 and an SOA 102 for optical signal amplification. .
  • the interferometer is a beam splitter 20 for splitting the coherent light generated from the wavelength tunable laser light source unit 10 into a first light incident to the reference stage 30 and a second light incident to the sample stage, Scanning a sample using a reference stage 30 including a mirror or the like for reflecting the incident first light back to the beam splitter 20 and the incident second light and reflecting it back to the beam splitter 20 It may include a sample stage 40 for.
  • the beam splitter 20 splits the light from the light source unit 10 into a first light to the reference stage 30 and a second light to the sample stage 40 and from the reference stage 30 and the sample stage 40. It combines and interferes with the incoming light.
  • the beam splitter 20 mainly divides the first light and the second light in a ratio of 50:50 in free space.
  • the reference stage 30 may include, for example, a mirror or the like to reflect light incident from the beam splitter 20.
  • the sample stage 40 is a portion for scanning a sample using light incident from the beam splitter 20, for example, by including a galvanometer or a moving stay.
  • the light scattered from the sample is not scattered at one point, but scattered from a sample of a certain area.
  • the light scattered from the sample may be incident to the beam splitter 20 and may be combined with the light from the reference stage 30 to generate an optical interference signal corresponding to each area of the sample.
  • the OCT receiver receives the interference signal generated by combining the light reflected from the reference stage 30 and the sample stage 40 in the beam splitter 20 and converts the interference signal into an electrical signal by using the two-dimensional CCD camera 501. 50 may be included. Unlike the photodetector which acquires the optical interference signal scattered at one point, the 2D CCD camera 501 may detect the optical interference signal scattered in a predetermined region at one time.
  • the receiver 50 as described above may obtain the interference signal data at a speed capable of realizing a 3D image of a predetermined region of a sample in real time.
  • the receiver 50 may include a frame grabber 502 for digitizing the electrical signal received from the 2D CCD camera.
  • the OCT may include a processor 60 for processing the 3D OCT data obtained by the receiver 50 to implement an image of a sample.
  • the processor 60 processes the 3D OCT data based on the 64-bit dynamic memory allocation method of the obtained 3D OCT data.
  • the maximum declarable data capacity is limited to about 3 gigabytes.
  • at least 8 gigabytes of data are required. Therefore, the conventional 32-bit data processing method cannot process data of more than 8 gigabytes at once. Therefore, in the 32-bit base, the size of the initial image must be reduced or large data must be stored separately and processed separately.
  • FIG 3 illustrates a data set of scanning one three-dimensional volume image of the human eye in accordance with one embodiment of the present invention.
  • three-dimensional OCT data is defined using a 64-bit-based dynamic memory allocation scheme. Declare the first of three-dimensional OCT data as a specific address in memory (xxxx), the second as the next address (xxxx + 1), and the last data as (xxxx + (l- 1) Declare as * (m-1) * (n-1)) address.
  • This dynamic memory allocation method uses a 64-bit data format, which allows you to declare addresses larger than 3 gigabytes. Specifically, when processing in the 64-bit data format, theoretically, it is possible to process data of 2 ⁇ 64 size, and in the current 64-bit operating system, the address can be declared up to about 8 terabytes. Therefore, three-dimensional OCT data of more than several gigabytes can be defined at one time, and signal processing can be performed.
  • the data declaration using the existing array uses the static memory allocation method so that the physical copy of the data occurs in the memory area when the data is copied and the operation occurs, so the time required to copy the data becomes more complicated. Also lengthens.
  • the dynamic memory allocation method since data is processed using only the start address and the last address of a memory area in which data exists without copying the entire data, copying of data takes little time.
  • FIG. 4 illustrates a parallel processing method of a plurality of data sets according to an embodiment of the present invention.
  • a data set includes a plurality of m * n vectorized data sets of l * m * n data along each A-scan line. Are separated by).
  • n data sets in the A-scan line direction are vectorized based on the A-scan line.
  • Vectorization of data can be implemented using, for example, Intel's IPP data processing language.
  • the data obtained by the receiver 50 may be classified according to various conditions, thereby vectorizing the data. For example, data can be vectorized based on B-scan lines or C-scan lines rather than A-scan lines.
  • the processor 60 may include a multicore processor 310.
  • the multicore processor 310 may include, for example, k + 2 cores (or threads).
  • the l data is m * n vectored plurality of data sets along each A-scan line described in FIG. After dividing by), it is divided into k bundles and distributed to k cores 310 2 , 310 3 ,..., 310 k + 1 ).
  • m * n vectorized plurality of data sets ( ) May be divided by k and evenly distributed to k cores 310 1 , 310 2 ,..., 310 k .
  • the multi-core processor 310 simultaneously processes the data set allocated to each core according to the OCT data processing instruction, and when data processing is completed in all cores, the multi-core processor 310 collects one data and displays the image corresponding to one screen on the computer monitor. You can make it visible.
  • the two remaining cores 310 1 and 310 k + 2 may be used for data acquisition and image display, respectively, as described later in connection with FIG. 6.
  • the number of the plurality of data sets and the number of cores are only examples, and the number of the plurality of data sets may be distributed to an appropriate number according to the number of the plurality of data sets and the number of cores, and processed in the plurality of cores.
  • processing multiple vectorized data sets using multiple cores reduces the number of copies of data and the number of operations required, as compared to the case where data is read out point by point and processed by a processing device. You can save time.
  • the processing of core-specific data can be implemented using, for example, a data code set called OpenMP.
  • FIG. 5 is a schematic diagram of a parallel operation process of obtaining, processing, and outputting an interference signal in an OCT according to an embodiment of the present invention.
  • the time required for acquiring the data is shortened because the OCT data processing time is sufficiently short (high-speed digitizer). Or OCT data acquisition time of the frame grabber or display time on a computer monitor. In this case, it is possible to escape from the time-series structure of acquiring, processing and displaying data, and again acquiring, processing and displaying data.
  • a data acquisition step of acquiring an OCT interference signal in a high-speed digitizer or frame grabber a data processing step of processing the acquired data through a series of processes (signal domain conversion, noise filtering, inverse Fourier transform, etc.), and a computer monitor
  • a series of processes signal domain conversion, noise filtering, inverse Fourier transform, etc.
  • a computer monitor In order to output an image to the image file, three calculation processes are performed, which are converted into an image file and a display step of transmitting data to a graphics card.
  • the data acquisition step is determined by the limiting factors of external devices (light source, digitizer, frame grabber, etc.) such as the repetition rate of the OCT laser light source and the data acquisition speed of the digitizer, and the display step is the format of the already processed data.
  • external devices light source, digitizer, frame grabber, etc.
  • the cores are allocated one by one, and a plurality of cores are distributed in a processing step with a relatively high processing load.
  • the data processing speed increases proportionally.
  • a core (core 1) used for data acquisition, cores (cores 2 to 5) used for data processing, and a core (core 6) used for display are separately designated and used for data acquisition.
  • the core (core 1) passes the data to the cores (cores 2 to 5) used for data processing after the longest data acquisition, and does not wait for the completion of all data processing and display. Perform the acquisition.
  • the cores (cores 2 to 5) used for data processing receive and process the OCT interference signal data obtained by the cores (core 1) used for data acquisition, and use the processed data for display. To the core (core 6). After waiting for data to flow from the core (core 1) used for data acquisition, a series of processes are repeated.
  • cores (cores 6) used for display also pass the OCT image data after the cores (cores 2 to 5) used for data processing, the received cores are displayed on the monitor and the cores used for data processing ( Core 2 to 5) waits until the processed image data is over, and then a series of processes are repeated.
  • the temporal parallel structuring method can be implemented using, for example, an MFC based multi-threading technique.
  • FIG. 6 is a schematic diagram of an operation process of obtaining, processing, rendering, and outputting an interference signal in an OCT according to an embodiment of the present invention.
  • the data may be sent to a rendering unit including a graphic card computing unit (GPU) to form a 3D image.
  • a rendering unit including a graphic card computing unit (GPU) to form a 3D image.
  • GPU graphic card computing unit
  • GPU operations can be very fast performing the same operations over and over again, but the built-in memory is limited and they are basically inadequate for large data processing based on 32-bit operations.
  • the processing unit copies the processed data to the graphic card and displays the data on the monitor after performing the task of rendering the processed data into a 3D image.
  • the OCT data processing time can be shortened sufficiently to be equal to or less than the time required for data acquisition (OCT data acquisition time of the high-speed digitizer or frame grabber) or the display time to the computer monitor. In this case, it is possible to escape from the time-series structure of acquiring, processing and displaying data, and again acquiring, processing and displaying data.
  • a core used for data acquisition (core 1), cores used for data processing (cores 2 to 5), a GPU used for 3D image rendering, and a core used for display (core 6)
  • the core used for data acquisition (core 1) passes the data to the cores (cores 2 to 5) used for data processing after the longest data acquisition, and all data processing and display Do not wait until the end of the data acquisition immediately.
  • the cores used for data acquisition receive and process the received two-dimensional OCT images. Pass the data to form to the GPU. After waiting for data to flow from the core (core 1) used for data acquisition, a series of processes are repeated.
  • the GPU used for 3D image rendering transfers the processed 2D OCT image data to the cores (cores 2 to 5) used for data processing, receives it, renders it into 3D image, and renders it.
  • the 3D OCT image data is passed to the core (core 6) used for display.
  • cores 2 to 5 In the core used for data processing (cores 2 to 5), a series of processes are repeated after waiting until the processed image data is transferred.
  • the core used for display (core 6) also receives the 3D OCT image data after the GPU renders it, displays it on the monitor, and then processes the processed 3D OCT image data on the GPU used for 3D image rendering. Wait until you get over, then repeat the process.
  • the temporal parallel structuring method can be implemented using, for example, an MFC based multi-threading technique.
  • FIG. 7 is a flowchart of a method for processing 3D OCT data obtained in an optical coherence tomography apparatus according to an embodiment of the present invention.
  • the method for processing 3D OCT data obtained by an optical coherence tomography apparatus includes: defining a data address for each of the obtained 3D OCT data using a 64-bit dynamic memory allocation method ( 601).
  • the obtained three-dimensional OCT data is a total of l * m * n data is defined, including l along the A-scan line, m along the B-scan line, and n along the C-scan line
  • a data address may be defined.
  • the method may then further comprise grouping 602 into a plurality of data sets along a scan line direction of one of an A-scan line, a B-scan line or a C-scan line. For example, when grouped along the A-scan line direction from Up to m * n vectorized data sets can be defined.
  • the method may then include a step 603 in which a plurality of data sets are processed in parallel by being processed in a plurality of cores of a multi-core processor.
  • m * n vectorized data sets can be processed by dividing the number equally to k cores of k + 2 cores of a multi-core processor.
  • the present invention can be applied to acquire and process three-dimensional OCT data in various kinds of OCT.
  • the speed of the fast wavelength variable laser is increased, so that the optical interference signal generated after the laser light source passes through the OCT interferometer is detected by the photodetector and the high-speed digitizer.
  • the 3D OCT image may be implemented using the detected data.
  • an embodiment of the present invention may be utilized to implement the detected data into a real-time three-dimensional image.
  • spectral domain OCT based on a broadband semiconductor light source
  • the speed of the CCD camera of the spectrometer increases, so that the optical interference signal generated after the broadband semiconductor light source passes through the OCT interferometer is framed with a high speed spectrometer and a frame.
  • Three-dimensional OCT images may be implemented using data detected through the grabber.
  • an embodiment of the present invention may be utilized to implement the detected data into a real-time three-dimensional image.
  • the spectral laser light source passes the optical interference signal generated after passing through the OCT interferometer using the free-space optical system.
  • the 4D OCT image may also be implemented using the data detected through the frame grabber. In this case, an embodiment of the present invention may be utilized to implement the detected data into a real-time three-dimensional image.
  • FF-OCT full-field OCT
  • three-dimensional data is detected in an FF-OCT structure in which a broadband light source passes through a free space interferometer and acquires depth image information at different plane phase differences.
  • OCT image can be implemented.
  • an embodiment of the present invention may be utilized to implement the detected data into a real-time three-dimensional image.
  • the functions presented herein may be implemented through hardware, software, firmware, or a combination thereof. If implemented in software, the functions may be stored on or transmitted over as one or more instructions or code on a computer-readable medium.
  • Computer-readable media includes computer storage media and communication media including any medium for facilitating the transfer of a computer program from one place to another.
  • a storage medium may be any available medium that can be accessed by a general purpose computer or a special computer.
  • such computer-readable media can be any program code means required in the form of RAM, ROM, EEPROM, CD-ROM or other optical disk storage media, magnetic disk storage media or other magnetic storage devices, or instructions or data structures.
  • any connecting means may be considered a computer readable medium.
  • the software is transmitted from a website, server, or other remote source through wireless technologies such as coaxial cable, fiber optic cable, twisted pair, digital subscriber line (DSL), or infrared radio, and microwave, such coaxial Wireless technologies such as cable, fiber optic cable, twisted pair, DSL, or infrared radio, and microwave may be included within the definition of such a medium.
  • wireless technologies such as coaxial cable, fiber optic cable, twisted pair, digital subscriber line (DSL), or infrared radio, and microwave
  • coaxial Wireless technologies such as cable, fiber optic cable, twisted pair, DSL, or infrared radio, and microwave may be included within the definition of such a medium.
  • Disks and discs used herein include compact discs (CDs), laser discs, optical discs, DVDs, floppy disks, and Blu-ray discs, where the disks magnetically reproduce data, but the discs are optically To play the data. Combinations of the above should also be included within the scope of computer-readable media.

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Abstract

La présente invention vise à accroître la vitesse de traitement de données dans une tomographie à cohérence optique à source balayée (SS-OCT) et une tomographie à cohérence optique dans le domaine de Fourier (FD-OCT) comprenant la SS-OCT et, en particulier, à traiter des données de grande dimension obtenues par une unité de réception à une vitesse plus rapide que la vitesse d'obtention de données, reconfigurer une image de tomographie en temps réel et fournir l'image reconfigurée à un utilisateur. Afin d'atteindre le but, selon un mode de réalisation de la présente invention, la présente invention porte sur une OCT. Le dispositif OCT comprend : une unité de source lumineuse émettant une lumière cohérente ; une unité d'interféromètre générant un motif d'interférence à partir d'un échantillon mesuré par réception d'une lumière incidente émise par l'unité de source lumineuse ; l'unité de réception recevant le motif d'interférence émis par l'unité d'interféromètre et convertissant le motif d'interférence en un signal électrique ; et une unité de traitement créant une image à partir de données obtenues par l'unité de réception, l'unité de traitement pouvant regrouper les données obtenues en une pluralité d'ensembles de données et traiter la pluralité d'ensembles de données en parallèle.
PCT/KR2013/010701 2012-11-28 2013-11-22 Dispositif de tomographie à cohérence optique (oct) pour traitement de données oct tridimensionnelles Ceased WO2014084556A1 (fr)

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KR101746353B1 (ko) 2016-11-09 2017-06-12 한국기초과학지원연구원 공통 광경로식 광섬유기반 핸드 헬드 병렬 광간섭 단층 촬영 장치
KR102045880B1 (ko) * 2017-12-06 2019-11-18 한국광기술원 광간섭단층영상 시스템 및 그 처리방법
KR102062372B1 (ko) * 2017-12-13 2020-01-03 한국생산기술연구원 영역 분할 기법에 기반한 화질 개선 광간섭 단층 촬영 장치 및 그 영상 처리 방법
KR101990251B1 (ko) 2018-10-15 2019-06-17 경북대학교 산학협력단 광 간섭성 단층 촬영 장치 및 이를 이용한 영상 생성 방법
KR102679828B1 (ko) 2021-10-29 2024-07-01 주식회사 휴비츠 Oct 영상에서 망막 단층의 측정 방법
KR102636222B1 (ko) 2021-10-29 2024-02-14 주식회사 휴비츠 Oct 영상에서 망막 단층의 분할 방법
CN114331805B (zh) * 2021-12-27 2023-04-14 中国科学院苏州生物医学工程技术研究所 一种基于gpu的oct成像方法及系统
KR102881516B1 (ko) 2025-01-20 2025-11-05 한국전광(주) 대면적 시료용 고속 스웹 소스 광간섭 단층촬영장치

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KR100993578B1 (ko) * 2008-10-23 2010-11-10 부산대학교 산학협력단 라만 증폭기를 이용한 ｓｓ-ｏｃｔ 시스템
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KR20100044973A (ko) * 2008-10-23 2010-05-03 부산대학교 산학협력단 빗살무늬 스펙트럼의 광원을 이용한 광 간섭성 단층촬영 시스템
KR100993578B1 (ko) * 2008-10-23 2010-11-10 부산대학교 산학협력단 라만 증폭기를 이용한 ｓｓ-ｏｃｔ 시스템
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