KR20140068346A - Optical coherence tomography for processing three-dimensional oct data using 64 bit based dynamic memory allocation method - Google Patents

Abstract

The objective of the present invention is to improve a data processing speed in an SS-optical coherence tomography (OCT) and an FD-OCT including the SS-OCT and to reconfigure a tomography image in real time and provide the reconfigured tomography image to a user by processing massive data acquired by a reception unit faster than a data acquisition speed. To achieve the objective of the present invention, an OCT according to an embodiment of the present invention comprises a light source unit which generates coherent light; an interferometer unit which generates an interference fringe from a sample which is measured by the incident light from the light source unit; a reception unit which receives the interference fringe irradiated from the interferometer unit to convert the interference fringe into an electrical signal; and a processing unit which images data acquired by the reception unit, wherein the processing unit groups the acquired data into multiple data sets to perform parallel processing of the data sets.

Description

TECHNICAL FIELD [0001] The present invention relates to an optical coherence tomography apparatus for processing three-dimensional OCT data. More particularly, the present invention relates to an optical coherence tomography apparatus for processing three-

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an optical coherent tomography (OCT) for processing a three-dimensional image at a high speed, and more particularly, to a three- To an optical coherence tomography apparatus.

As a conventional imaging device, 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 of specific fields depending on different physical properties, resolution, penetration depth, and the like. Recently, researches on the development of medical diagnostic devices using light have been actively conducted.

Among them, OCT is the most representative. Optical coherence tomography was based on Optical Coherence Domain Tomography (OCDR) technology, and Dawei and IMITIC first suggested the possibility of "seeing through skin" in the early 1970s. This technique uses cross-sectional imaging in a non-invasive, non-contact way by measuring the optical reflection of the internal structure of biological tissues using the low coherence characteristics of the laser. .

OCT has been developed to supplement the problems of human hazards, price problems, and measurement resolution of conventional measurement equipment such as X-ray computed tomography (CT), ultrasound imaging, and magnetic resonance imaging .

The image technique of the OCT is based on a Michelson interferometer and the output of a light source with low coherence is divided into two directions of the interferometer arm. The reflected light returned from the reference end and the backward scattered light from the sample end are again brought into interference and imaged through signal processing.

The interference properties of light reflected from the living tissue have time-of-flight information on the microstructure derived from the reflection boundary of the tissue and back-scattering. Such optical coherence tomography (OCT) is harmless even if it is used for diagnosis of human body because it uses light, and the most typical diagnosis field is diagnosis of eye retina.

OCT has a higher resolution (resolution) than conventional ultrasound images, and it has many advantages such as the ability to capture the inside of the object in a non-incision manner, real-time tomographic imaging, and the production of small and low- Have.

Conventional OCT technology, which shows 2D tomographic images, is being developed to show three-dimensional images at a time as wavelength tunable lasers and high-speed CCD cameras are developed. However, since the capacity of OCT data for implementing 3D image exceeds several gigabytes, the OCT processing method based on the existing 32-bit operating system can not perform memory address declaration and data processing at a time. Furthermore, in the conventional method of displaying three-dimensional images at a time after storing the data on a separate storage medium, if the OCT images continuously obtained are continuously processed, the amount of data is further increased and serious data bottleneck phenomenon . Therefore, real-time three-dimensional imaging is possible if a technology capable of imaging and processing three-dimensional data over several gigabytes without bottleneck is developed. Currently, we are using a method to acquire and process data as much as possible for processing, or to narrow down the region of interest (ROI) of the OCT.

The following description provides a simplified description of one or more embodiments in order to provide a basic understanding of embodiments of the invention. This section is not a comprehensive overview of all possible embodiments and is not intended to identify key elements or to cover the scope of all embodiments of all elements. Its sole purpose is to present the concept of one or more embodiments in a simplified form as a prelude to the more detailed description that is presented later.

An object of the present invention is to provide a user with a large amount of data of several gigabytes or more generated in real time when real-time three-dimensional images are formed using OCT.

According to an embodiment of the present invention, an optical coherence tomography (OCT) may be disclosed. The optical coherent tomography apparatus includes a light source section for generating coherent light, an interferometer section for generating an interference fringe from a sample measured by receiving the emitted light from the light source section, Dimensional OCT data by using a 64-bit based dynamic memory allocation scheme, and the processing unit converts the 3-dimensional OCT data into a data address Can be defined.

Further, the obtained three-dimensional OCT data includes a total of l * m * n pieces of data including 1 pieces along the A-scan line, m pieces along the B-scan line, and n pieces along the C- And data addresses can be defined for each of l * m * n data.

The acquired three-dimensional OCT data is grouped into a plurality of data sets along one scan line direction of the A-scan line, the B-scan line, or the C-scan line, Can be processed in parallel.

In addition, the processing unit includes a multicore processor (CPU), and the plurality of data sets can be parallel-processed by being allocated by dividing the number of cores (threads) of the multicore processor.

The display unit may further include a display unit for displaying data imaged by the processing unit, wherein the receiving unit performs conversion of the interference fringe into the electrical signal in one of the cores of the multicore processor, Wherein the processor executes the display in one of the cores of the multicore processor that is not used by the receiver, and the processor is operable to perform the display from the cores of the cores of the multicore processor that are not used by the processor and the receiver And the number of cores used in the processing unit may be two or more.

The processor may further include a rendering unit for rendering the obtained three-dimensional OCT data, wherein the processing unit processes the plurality of data sets in cores that are not used in the processing unit and the receiving unit among the cores of the multicore processor, A plurality of data sets may be processed in parallel to form a two-dimensional cross-sectional image, and the rendering unit may render the two-dimensional cross-sectional image and image the three-dimensional image.

According to another embodiment of the present invention, a method for processing three-dimensional OCT data obtained in an optical coherence tomography (OCT) is disclosed. The method may include defining a data address using a 64-bit based dynamic memory allocation scheme for each of the obtained data.

Further, the obtained three-dimensional OCT data includes a total of l * m * n pieces of data including 1 pieces along the A-scan line, m pieces along the B-scan line, and n pieces along the C- And data addresses can be defined for each of l * m * n data.

The obtained three-dimensional OCT data is grouped into a plurality of data sets along one scan line direction of the A-scan line, B-scan line, or C-scan line, Can be processed in parallel by processing in a plurality of cores of the processor.

According to another embodiment of the present invention, there is provided a computer readable recording medium having program code for causing at least one computer to process three-dimensional OCT data obtained from an optical coherence tomography (OCT) Lt; / RTI > 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.

Further, the obtained three-dimensional OCT data includes a total of l * m * n pieces of data including 1 pieces along the A-scan line, m pieces along the B-scan line, and n pieces along the C- And data addresses can be defined for each of l * m * n data.

The obtained three-dimensional OCT data is grouped into a plurality of data sets along one scan line direction of the A-scan line, B-scan line, or C-scan line, Can be processed in parallel by processing in a plurality of cores of the processor.

According to the configuration of the present invention, when processing three-dimensional OCT data obtained from an OCT, it is possible to increase data processing speed by allocating and parallelizing an address by using a 64-bit based dynamic memory allocation method, Dimensional OCT images can be realized in real time.

To the accomplishment of the foregoing and related ends, the one or more embodiments comprise the features hereinafter described and particularly pointed out in the claims. The following description and the annexed drawings set forth in further detail certain illustrative aspects of these embodiments. Those skilled in the art will appreciate that these aspects are merely exemplary and that various modifications are possible. Furthermore, the presented embodiments are construed to include both these embodiments and equivalents of such embodiments.

FIG. 1 shows a schematic diagram of an optical coherence tomography (OCT) according to an embodiment of the present invention.
FIG. 2 is a schematic view of a case where an OCT is an SS-OCT using a two-dimensional camera according to an embodiment of the present invention.
FIG. 3 illustrates a data set in which one three-dimensional volume image of a human eye is scanned according to an embodiment of the present invention.
FIG. 4 illustrates a method of parallel processing of a plurality of data sets according to an embodiment of the present invention.
5 shows a schematic diagram of an arithmetic procedure for acquiring, processing and outputting an interference signal in an OCT according to an embodiment of the present invention.
FIG. 6 shows a schematic diagram of an arithmetic process for acquiring, processing, rendering, and outputting an interference signal in an OCT according to an embodiment of the present invention.
7 is a flow chart of a method for processing three-dimensional OCT data obtained in an optical coherence tomography apparatus according to an embodiment of the present invention.

Various embodiments are now described with reference to the drawings, wherein like reference numerals are used throughout the drawings to refer to like elements. For purposes of explanation, various descriptions are set forth herein to provide an understanding of the present invention. It is evident, however, that such embodiments may be practiced without these specific details. In other instances, well-known structures and devices are shown in block diagram form in order to facilitate describing the embodiments.

1 is a schematic diagram of an optical coherence tomography (OCT) device according to an embodiment of the present invention.

Referring to FIG. 1, the OCT includes a light source 10 for generating coherent light, an interferometer for generating interference fringes from a sample measured by receiving the emitted light from the light source 10, A reception unit 50 for receiving an interference fringe to be examined and converting the interference fringe to an electrical signal, and a processing unit 60 for imaging the data acquired by the reception unit.

The light source unit 10 may generate incoherent light.

When the OCT is SD-OCT, the light source unit 10 includes a superluminescent LED (SLD) for emitting light and an optical band splitting means (for example, a prism or the like) for radiating light from the SLD into a broadband light ).

When the OCT is SS-OCT, the light source unit 10 may include a tunable laser and an SOA.

When the OCT is a full-field OCT (FF-OCT), a suitable wide-band light source can be used accordingly.

The light emitted from the light source 10 of the OCT should be broadband and have a harmless intensity when irradiated to the human body.

The interferometer unit includes a beam splitter 20 for splitting the coherent light generated from the light source unit 10 into a first light incident on the reference end 30 and a second light incident on the sample end, A reference stage 30 including a mirror or the like for reflecting one light beam back to the beam splitter 20 and a sample stage 30 for scanning the sample using the incident second light beam and reflecting it back to the beam splitter 20 (40).

Beam splitter 20 divides the light from light source 10 into a first light at reference end 30 and a second light into sample end 40 and transmits the light from reference end 30 and sample end 40 And combines and interferes with the incoming light again. The beam splitter 20 must be capable of accurately dividing the broadband light from the light source 10 into a first light and a second light at a predetermined ratio without loss. The beam splitter 20 mainly divides the first light and the second light in a ratio of 50:50, and may include, for example, an optical coupler.

The reference stage 30 can reflect light incident from the beam splitter 20, for example, by including a mirror or the like. The reference stage 30 is for generating a reference light for generating an interference signal with light incident from the sample stage 40 to the beam splitter 20, The length of the optical path of the light source 30 should be appropriately adjusted.

The sample stage 40 is, for example, a part for scanning a sample (for example, the eye of a human body) using light incident from the beam splitter 20 by including a galvanometer or the like. The light reflected from the sample may again be incident on the beam splitter 20 and combine with light from the reference end 30 to generate an interference signal.

The OCT may include a receiver 50 for receiving the interference signal generated by coupling the light reflected from the reference stage 30 and the sample stage 40 in the beam splitter 20 and converting the received interference signal into an electrical signal.

In case of the SS-OCT, the receiver 50 may include a digitizer (1 GS sample / second or more) capable of acquiring a high-speed signal. In case of the SD-OCT, the receiver 50 may use a high-speed frame grabber.

When the OCT is a full-field OCT (FF-OCT), in the case of a Doppler OCT, an appropriate optical signal detecting device can be used accordingly.

The receiving unit 50 can acquire the interference signal data at a rate that can realize the image of the sample in real time.

FIG. 2 is a schematic view of a case where an OCT is an SS-OCT using a two-dimensional camera according to an embodiment of the present invention. 2, when the OCT is SS-OCT using a 2D charge coupled device (CCD) camera, the light source unit 10 may include a tunable laser 101 and an optical signal amplification SOA 102 .

The interferometer includes a beam splitter 20 for splitting the coherent light generated from the tunable laser light source 10 into a first light incident on the reference end 30 and a second light incident on the sample end, A reference stage 30 including a mirror or the like for reflecting the incident first light back to the beam splitter 20, and a second optical system for scanning the sample using the incident second light and reflecting it back to the beam splitter 20 (Not shown).

Beam splitter 20 divides the light from light source 10 into a first light at reference end 30 and a second light into sample end 40 and transmits the light from reference end 30 and sample end 40 And combines and interferes with the incoming light again. 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 can reflect light incident from the beam splitter 20, for example, by including a mirror or the like. The sample stage 40 is, for example, a part for scanning a sample using light incident from the beam splitter 20, including a galvanometer or a moving stage. The light scattered from the sample is not scattered at a point, but is scattered in a sample of a certain area. The scattered light in the sample may again be incident on the beam splitter 20 and combine with the light from the reference end 30 to generate an optical interference signal corresponding to each region of the sample.

The OCT is a receiver for receiving an interference signal generated by coupling the light reflected from the reference stage 30 and the sample stage 40 in the beam splitter 20 by using the two-dimensional CCD camera 501 and converting it into an electrical signal (50). The two-dimensional CCD camera 501 can detect an optical interference signal scattered in a certain area at one time, unlike a photodetector that obtains an optical interference signal scattered at one point.

The receiving unit 50 may acquire the interference signal data at a rate capable of realizing a three-dimensional image of a certain region of the sample in real time. The receiving unit 50 may include a frame grabber 502 for digitizing an electrical signal received from the two-dimensional CCD camera. The OCT may include a processing unit 60 for processing the three-dimensional OCT data acquired by the receiving unit 50 to implement a sample image.

The processing unit 60 processes the obtained 3-dimensional OCT data based on a 64-bit based dynamic memory allocation method.

When the data is processed in the 32-bit manner as in the conventional method, the maximum data capacity to be declared is limited to about 3 gigabytes. Since at least 8 gigabytes of data are required to process three-dimensional OCT data at the same time, conventional 32-bit data processing methods can not process more than 8 gigabytes of data at a time. Therefore, in the case of a 32-bit base, the size of the original image must be reduced or a large amount of data must be separately stored and processed separately.

Once all three-dimensional OCT data corresponding to one 3D volume image is acquired by a high-speed digitizer or frame grabber, it is necessary to define and copy it to the memory of the host computer.

FIG. 3 illustrates a data set in which one three-dimensional volume image of a human eye is scanned according to an embodiment of the present invention.

Referring to FIG. 3, three-dimensional OCT data is defined using a 64-bit based dynamic memory allocation scheme. (Xxxx + (l-1), and the last data is expressed as (xxxx + (1-xxxx + 1)) by declaring the first data among the three- dimensional OCT data as a specific address (xxxx) 1) * (m-1) * (n-1).

Because this dynamic memory allocation scheme uses 64-bit data format, it can also declare addresses over 3 gigabytes. Specifically, processing in a 64-bit data format can theoretically process data at a size of 2 ^ 64, and in a 64-bit operating system, addresses can be declared up to 8 terabytes. Therefore, it is possible to define three-dimensional OCT data over several gigabytes at a time, and to perform a signal processing process.

In addition, data declaration using existing array uses static memory allocation method, and physical copying of data occurs in memory area when data copying and arithmetic operation occurs. Therefore, the time required for data copying . On the other hand, the dynamic memory allocation method does not copy the whole data but processes the data using only the start address and the end address of the memory area in which the data exists, so that it takes little time to copy the data.

 FIG. 4 illustrates a method of parallel processing of a plurality of data sets according to an embodiment of the present invention.

Referring to FIG. 4, there are shown data sets (l samples x m B-scan lines x n C-scan lines) corresponding to the volume shown in FIG.

)로 분리되어 있다. 4, a data set includes l * m * n data along each A-scan line, m * n vectorized data sets (

).

That is, in the present embodiment, sets of m * n data in the A-scan line direction are vectorized with reference to the A-scan line. The vectorization of the data can be implemented using, for example, Intel Corporation's IPP data processing language.

This is only an example and the data can be vectorized by classifying the data acquired by the receiving unit 50 according to various conditions. For example, data can be vectorized based on a B-scan line or a C-scan line rather than an A-scan line.

Referring to FIG. 4, the processing unit 60 may include a multicore processor 310.

)로 구분한 후에, k개의 묶음이 되도록 나누어 k개의 코어들(310₂,310₃,...,310_k+1)각각에 배분한다. 예를 들어, 도 4에 도시된 바와 같이 m*n개의 벡터화된 복수의 데이터 세트들(

)을 k로 나누고 균등하게 k개의 코어들(310₁,310₂,...,310_k)에 배분할 수 있다. 멀티 코어 프로세서(310)는 각각의 코어에 배분된 데이터 세트를 OCT 데이터 처리 명령에 맞추어 동시에 처리하고, 모든 코어에서 데이터 처리가 완료되면 하나의 데이터로 모아서 하나의 화면에 해당하는 영상으로 컴퓨터 모니터에 보이게 할 수 있다. 2개의 잔여 코어(310₁및 310_k+2)는 추후에 도 6와 관련하여 설명하는 바와 같이 각각 데이터 획득 및 영상 디스플레이에 이용될 수 있다. The multicore processor 310 may include, for example, k + 2 cores (or threads). In the present invention, the obtained large-capacity OCT data is read one by one and is not sent to the processing apparatus. Instead, one data is divided into m * n vectorized data sets (

, And then divided into k bundles to be distributed to k cores 310 ₂ , 310 ₃ , ..., and 310 _{k + 1} , respectively. For example, as shown in FIG. 4, m * n vectorized plurality of data sets (

) Can be divided by k and evenly distributed to k cores 310 ₁ , 310 ₂ , ..., 310 _k . The multicore processor 310 simultaneously processes the data sets allocated to the respective cores in accordance with the OCT data processing command. When the data processing is completed in all the cores, the multicore processor 310 collects the data sets as one data, It can be seen. The two remaining cores 310 ₁ and 310 _{k + 2} may be used for data acquisition and image display, respectively, as will be described later with reference to FIG.

The number of the plurality of data sets and the number of cores is only an example, and the number of the plurality of data sets may be appropriately distributed according to the number of the plurality of data sets and the number of the cores, and the processing may be performed in the plurality of cores.

In this manner, when a plurality of vectorized data sets are processed using a multicore, the number of times of copying and operation of necessary data can be reduced as compared with the case where data is read one by one and processed by a processing apparatus. Therefore, Time can be reduced. The processing of data for each core can be implemented using a data code set, for example, OpenMP.

5 shows a schematic diagram of a parallel computation process for acquiring, processing, and outputting an interfering signal in an OCT according to an embodiment of the present invention.

As shown in FIG. 4, when the data sets are grouped into a plurality of data sets by vectorization and parallel processing is performed using multicore, the OCT data processing time is sufficiently shortened and the time required to acquire the data Or the OCT data acquisition time of the frame grabber) or the time required for display on the computer monitor. In this case, it is possible to escape from the serial structure in time to acquire, process, display and reacquire, process and display the data.

A data processing step (signal domain conversion, noise filtering, inverse Fourier transform, and the like) for processing the acquired data through a series of processes, and a computer monitor And a display step of transmitting data to the graphic card so as to output an image to the graphic card.

Of these, the data acquisition step is already determined by the limiting factors of the external device (light source, digitizer, frame grabber, etc.) such as the repetition rate of the OCT laser light source and the data acquisition rate of the digitizer, The core is distributed one by one because it takes the least time in general because it is only required to output to the monitor, and the plurality of cores are distributed in the processing stage where the processing load is relatively large. Here, as the number of cores increases, the data processing speed increases proportionally.

As a result, by using a plurality of cores in the processing step, it is possible to minimize the actual repetition time of the entire OCT image by reducing the time required for the data processing step to be shorter than the time required for the acquisition step.

5, 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 (Cores 1 to 5) that have the longest data acquisition time, pass the data to the cores used for data processing (cores 2 to 5), and immediately wait for data processing and display Acquisition.

Similarly, cores (cores 2 to 5) used for data processing receive and process the OCT interference signal data obtained from the core (core 1) used for data acquisition, and use the processed data for display To the core (core 6). After waiting for the data to be transferred from the core (core 1) used for data acquisition again, the process is repeated.

When cores (cores 6 to 5) used for data processing pass cores of processed OCT image data to cores (cores 6) used for display, cores (cores 2 to 5) The core 2 to 5) waits for the processed video data to be passed, and then repeats a series of processes.

Since the above-described processes are performed in parallel in time as shown in FIG. 5, the overall imaging time can be minimized as compared with the serial type method, and the ultimate real-time imaging is possible. The temporal parallel structuring method can be implemented using, for example, an MFC-based multi-threading technique.

FIG. 6 shows a schematic diagram of an arithmetic process for acquiring, processing, rendering, and outputting an interference signal in an OCT according to an embodiment of the present invention.

As shown in FIG. 4, when data sets are grouped into a plurality of data sets and parallel processing is performed using multicore, data for forming a two-dimensional OCT image can be created.

When data for forming a two-dimensional OCT image is created, it can be sent to a rendering unit including a graphics card processing unit (GPU) to form a three-dimensional image.

GPU operations can be performed very quickly, but the built-in memory is limited and is basically unsuitable for large-volume data processing based on 32-bit operations. However, it is possible to collect the two-dimensional image data already processed by the processing unit and to make the three-dimensional image, that is, 3D rendering. As shown in FIG. 6, the processing unit copies the processed data to the graphic card and renders it as a three-dimensional image in the rendering unit, and displays it on the monitor.

Accordingly, the OCT data processing time can be shortened to be equal to or less than the time required to acquire the data (OCT data acquisition time of the high-speed digitizer or frame grabber) or the display time required for the computer monitor. In this case, it is possible to escape from the serial structure in time to acquire, process, display and reacquire, process and display the data.

6, cores (cores 1) used for data acquisition, cores (cores 2 to 5) used for data processing, GPUs used for 3D image rendering, (Core 1), which is used for data acquisition, transfers the data to the cores (cores 2 to 5) used for data processing when the data acquisition that takes the longest time is completed, and all data processing and display We do not wait for it to finish, but do data acquisition right away.

Similarly, cores (cores 2 to 5) used for data processing receive and process the OCT interference signal data obtained from the core (core 1) used for data acquisition, and process the processed 2-dimensional OCT image And passes the data for formation to the GPU. After waiting for the data to be transferred from the core (core 1) used for data acquisition again, the process is repeated.

The GPU used for 3D image rendering renders the 2-D OCT image data that has been processed by cores (core 2 ~ 5) used for data processing to render it as a 3-dimensional image, And passes the 3D OCT image data to the core (core 6) used for display. After waiting for the processed video data in the cores (cores 2 to 5) used for data processing to pass, the process is repeated.

The core (core 6) used in the display also displays 3D OCT image data that has been rendered by the GPU, and displays the 3D OCT image data that has been processed in the GPU used for 3D image rendering. Repeat the sequence of steps after waiting until you are over.

Since the above-described processes are performed in parallel in time as shown in FIG. 6, the overall imaging time can be minimized compared with the serial type method, and ultimate real-time imaging is possible. The temporal parallel structuring method can be implemented using, for example, an MFC-based multi-threading technique.

7 is a flow chart of a method for processing three-dimensional OCT data obtained in an optical coherence tomography apparatus according to an embodiment of the present invention.

Referring to FIG. 7, a method for processing three-dimensional OCT data obtained in an optical coherence tomography apparatus includes defining a data address using a 64-bit based dynamic memory allocation scheme for each of the obtained three-dimensional OCT data 601).

The obtained three-dimensional OCT data includes a total of l * m * n data including 1 data along the A-scan line, m data along the B-scan line, and n data along the C-scan line , and l * m * n data, respectively.

부터

까지 총 m*n개의 벡터화된 데이터 세트들이 정의될 수 있다. The method may then further comprise grouping (602) the plurality of data sets along the scan line direction of one of the A-scan line, the B-scan line, or the C-scan line. For example, when grouped along the A-scan line direction

from

A total of m * n vectorized data sets can be defined.

The method may then comprise a step 603 in which a plurality of data sets are processed in parallel by being processed in a plurality of cores of a multicore processor.

For example, when grouped along the A-scan line direction, the m * n vectorized data sets can be divided into k cores out of k + 2 cores of the multicore processor and processed in equal numbers.

The present invention can be applied to acquire and process three-dimensional OCT data in various types of OCT.

As the speed of the high-speed tunable laser increases, 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 (FDT-OCT) Dimensional OCT image can be realized by using the detected data. In this case, one embodiment of the present invention can be utilized to realize the detected data as a real-time three-dimensional image.

In the case of the spectral domain OCT (Spectral Domain OCT) based on the broadband semiconductor light source, as the CCD camera speed of the spectroscope becomes faster, the optical interference signal generated after the broadband semiconductor light source passes through the OCT interferometer is transmitted to the high- Dimensional OCT image can be realized with the data detected through the grabber. In this case, one embodiment of the present invention can be utilized to realize the detected data as a real-time three-dimensional image.

In addition, as the speed of the high-resolution two-dimensional CCD camera is increased in the case of the free-space FD OCT based on the tunable laser, the optical interference signal generated after the wavelength tunable laser light source passes through the OCT interferometer using the free- And 4-dimensional OCT images can be realized using the data detected through the frame grabber. In this case, one embodiment of the present invention can be utilized to realize the detected data as a real-time three-dimensional image.

In the case of full-field OCT (global OCT) based on a broadband light source, the data detected in the FF-OCT structure, in which the broadband light source passes through the free space interferometer and acquires depth image information in different plane retardation, OCT images can be implemented. In this case, one embodiment of the present invention can be utilized to realize the detected data as a real-time three-dimensional image.

In one or more exemplary implementations, the functions presented herein may be implemented in hardware, software, firmware, or a combination thereof. When implemented in software, the functions may be stored on or transmitted via 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 transfer of a computer program from one place to another. The storage medium may be a general purpose computer or any available medium that can be accessed by a special computer. By way of example, and not limitation, such computer-readable media can comprise any form of computer readable medium, such as RAM, ROM, EEPROM, CD-ROM or other optical disk storage media, magnetic disk storage media or other magnetic storage devices, And may include, but is not limited to, a general purpose computer, a special purpose computer, a general purpose processor, or any other medium that can be accessed by a particular processor. In addition, any connection means may be considered as a computer-readable medium. For example, if the software is transmitted from a web site, server, or other remote source over wireless technologies such as coaxial cable, fiber optic cable, twisted pair, digital subscriber line (DSL), or infrared radio, and microwave, Wireless technologies such as cable, fiber optic cable, twisted pair, DSL, or infrared radio, and microwave may be included within the definition of such medium. The discs and discs used here include compact discs (CDs), laser discs, optical discs, DVDs, floppy discs, and Blu-ray discs where disc plays the data magnetically, As shown in FIG. The combinations may also be included within the scope of computer readable media.

The description of the disclosed embodiments is provided to enable any person skilled in the art to make or use the present invention. Various modifications to these embodiments will be readily apparent to those skilled in the art, and the generic principles defined herein may be applied to other embodiments without departing from the scope of the invention. Thus, the present invention is not intended to be limited to the embodiments shown herein but is to be accorded the widest scope consistent with the principles and novel features presented herein.

Claims (13)

In optical coherence tomography (OCT)
A light source section for generating coherent light;
An interferometer unit for receiving the emitted light from the light source unit and generating an interference fringe from the measured sample,
A receiver for receiving an interference fringe emitted from the interferometer and converting the received interference fringe to an electrical signal;
A processor for imaging the three-dimensional OCT data acquired by the receiver,
Lt; / RTI >
Wherein the processor defines a data address using a 64-bit based dynamic memory allocation scheme for each of the obtained three-dimensional OCT data.
The method according to claim 1,
Wherein the light source unit includes a tunable laser for generating light and a semiconductor optical amplifier (SOA) for amplifying the light,
The receiving unit includes a two-dimensional CCD (charge coupled device) camera. The receiving unit receives the interference fringes by using the two-dimensional CCD camera, converts the interference fringes into electric signals,
Wherein the processor defines a data address using a 64-bit based dynamic memory allocation scheme for each of the obtained three-dimensional OCT data.
3. The method according to claim 1 or 2,
The obtained three-dimensional OCT data includes a total of l * m * n data including 1 data along the A-scan line, m data along the B-scan line, and n data along the C-scan line , and data addresses are defined for each of the l * m * n data.
The method of claim 3,
Dimensional OCT data is grouped into a plurality of data sets along one scan line direction of the A-scan line, the B-scan line, or the C-scan line,
And the plurality of data sets are processed in parallel by the processing unit.
5. The method of claim 4,
Wherein the processing unit includes a multi-core processor, and the plurality of data sets are processed in parallel by being divided by the number of cores of the multicore processor.
5. The method of claim 4,
A display unit for displaying data imaged by the processing unit,
Further comprising:
Wherein the receiving unit performs conversion of the interferogram into the electrical signal in one of the cores of the multicore processor,
Wherein the display unit executes the display in one core not used by the receiving unit among the cores of the multicore processor,
The processing unit processes the plurality of data sets in parallel by processing the cores in the cores of the multicore processor that are not used in the processing unit and the receiving unit,
Wherein the number of cores used in the processing section is two or more.
The method according to claim 6,
Dimensional OCT data, and a rendering unit
Further comprising:
The processing unit processes the plurality of data sets in parallel by processing cores in the cores of the multicore processor that are not used in the processing unit and the receiving unit to form a two-dimensional sectional image,
Wherein the rendering unit renders the two-dimensional cross-sectional image and images the three-dimensional image.
A method for processing three-dimensional OCT data obtained from an optical coherence tomography (OCT)
A step of defining a data address by using a 64-bit based dynamic memory allocation scheme on each of the obtained three-dimensional OCT data
Dimensional OCT data obtained in the optical coherence tomography apparatus.
9. The method of claim 8,
The obtained three-dimensional OCT data includes a total of l * m * n data including 1 data along the A-scan line, m data along the B-scan line, and n data along the C-scan line , l * m * n data, wherein data addresses are defined for each of the data.
10. The method of claim 9,
Dimensional OCT data is grouped into a plurality of data sets along one scan line direction of the A-scan line, the B-scan line, or the C-scan line,
Wherein the plurality of data sets are processed in parallel by processing in a plurality of cores of a multicore processor.
A computer-readable medium having program code for causing at least one computer to process three-dimensional OCT data obtained from an optical coherence tomography (OCT)
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
Readable recording medium.
12. The method of claim 11,
The obtained three-dimensional OCT data includes a total of l * m * n data including 1 data along the A-scan line, m data along the B-scan line, and n data along the C-scan line , and l * m * n data, respectively.
13. The method of claim 12,
Dimensional OCT data is grouped into a plurality of data sets along one scan line direction of the A-scan line, the B-scan line, or the C-scan line,
Wherein the plurality of data sets are processed in parallel by processing in a plurality of cores of a multicore processor.

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