WO2017133083A1 - 基于全空间调制谱分割角度复合的微血管造影方法与系统 - Google Patents

基于全空间调制谱分割角度复合的微血管造影方法与系统 Download PDF

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WO2017133083A1
WO2017133083A1 PCT/CN2016/079693 CN2016079693W WO2017133083A1 WO 2017133083 A1 WO2017133083 A1 WO 2017133083A1 CN 2016079693 W CN2016079693 W CN 2016079693W WO 2017133083 A1 WO2017133083 A1 WO 2017133083A1
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modulation spectrum
arm
sample
lens
full
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李鹏
李培
程宇轩
周丽萍
丁志华
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Zhejiang University ZJU
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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
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0073—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence by tomography, i.e. reconstruction of 3D images from 2D projections
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording for evaluating the cardiovascular system, e.g. pulse, heart rate, blood pressure or blood flow
    • A61B5/026—Measuring blood flow
    • A61B5/0275—Measuring blood flow using tracers, e.g. dye dilution
    • A61B5/02755—Radioactive tracers
    • 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
    • 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
    • A61B5/0077—Devices for viewing the surface of the body, e.g. camera, magnifying lens
    • A61B5/0079—Devices for viewing the surface of the body, e.g. camera, magnifying lens using mirrors, i.e. for self-examination
    • 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
    • A61B5/0082—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording for evaluating the cardiovascular system, e.g. pulse, heart rate, blood pressure or blood flow
    • A61B5/026—Measuring blood flow
    • A61B5/0261—Measuring blood flow using optical means, e.g. infrared light
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7235—Details of waveform analysis
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7271—Specific aspects of physiological measurement analysis
    • A61B5/7275—Determining trends in physiological measurement data; Predicting development of a medical condition based on physiological measurements, e.g. determining a risk factor
    • 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
    • G01B9/02041—Interferometers characterised by particular imaging or detection techniques
    • G01B9/02044—Imaging in the frequency domain, e.g. by using a spectrometer
    • 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
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/102—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for optical coherence tomography [OCT]
    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T2207/00—Indexing scheme for image analysis or image enhancement
    • G06T2207/10—Image acquisition modality
    • G06T2207/10072—Tomographic images
    • G06T2207/10101—Optical tomography; Optical coherence tomography [OCT]

Definitions

  • the invention relates to optical coherence tomography (OCT) and based on the labelless three-dimensional optical micro-angiography (OCT Angiography, Angio-OCT), in particular to segmentation angle composite based on full spatial modulation spectrum Microangiography methods and systems.
  • OCT technology is a new imaging technology that has been developed in the biomedical field since the 1990s. With its advantages of no label, non-invasive, non-contact, high imaging resolution and high detection sensitivity, it attracts more and more researchers at home and abroad to study it more deeply. It has been widely used.
  • the OCT technique mainly obtains the reflectance information of the sample backscattered light due to the detected optical non-uniformity of the biological sample, and obtains the reflectance information inside the sample, thereby reconstructing the tomographic image of the sample.
  • Functional OCT technology has been developed and widely used in order to obtain more physiological information than the tissue morphology of biological samples.
  • Angio-OCT technology is a promising tool for the diagnosis of vascular diseases. It can distinguish between static tissue and dynamic blood flow signals, and realizes the function of OCT in acquiring intravascular blood flow information. Sexual expansion. Compared with the traditional contrast technique, the advantage is that it can realize high-contrast imaging of microvascular three-dimensional depth resolution without the need to inject developer and utilize X-ray, combined with the characteristics of the OCT technology described above.
  • the model of blood flow contrast is mathematically analyzed to analyze the temporal statistical properties of the light-scattering signal and to segment the dynamic blood flow signal and the static tissue background signal with a threshold.
  • the dynamic and static signal segmentation errors are caused, and the blood flow contrast is affected.
  • an effective method to improve the blood flow contrast of the contrast image helps to more clearly explain the characteristics of the image.
  • independent contrast subgraphs can be obtained by methods such as wavelength diversity, angular diversity, and polarization diversity.
  • Jia et al. proposed a spectral segmentation Angio-OCT method similar to wavelength diversity. The method divides the full-wavelength spectrum of the OCT interference signal into different sub-spectra, and each sub-spectrum can generate an independent contrast subgraph, which is combined to form a new angiogram. However, compared to the original full spectrum, each sub-spectral bandwidth is narrowed, resulting in a decrease in the axial resolution of the image.
  • the invention aims at the deficiencies of the prior art, and proposes a micro-angiography method and system based on full-space modulation spectrum segmentation angle composite.
  • the microvascular angiography method based on the full-space modulation spectrum segmentation angle composite includes the following steps:
  • the angiograms obtained in 3) or 4) are averaged to obtain a plurality of spatial angle composite angiograms.
  • Micro-angiography method based on full-space modulation spectrum segmentation angle composite Micro-angiography method based on full-space modulation spectrum segmentation angle composite:
  • the interference spectrum real signal corresponding to one horizontal scan can be expressed as S(k, x), where k represents the wave number and x represents the lateral fast sweep direction. Since the spectral real signal is directly Fourier transformed in the lateral x direction, the resulting spatial frequency distribution will produce aliasing of positive and negative frequencies, so it is necessary to reconstruct the complex value OCT interference spectrum.
  • the real spectrum S(k, x) is Fourier transformed along the k direction to obtain the spatial structure information of the depth domain (z).
  • half of the z-space corresponds to an imaging range of about 3 mm, which can satisfy most application requirements, so that the sample to be tested is completely placed on one side of the zero optical path difference to distinguish the complex conjugate image.
  • the inverse Fourier transform is performed along the k direction, and finally a complex-valued spectral signal is obtained.
  • the complex spectrum is subjected to Fourier transform in the x direction, and a full-space lateral scan modulation spectrum is obtained in the spatial frequency domain.
  • the beam diameter required to be irradiated onto the objective lens is as large as possible. Therefore, when a collimated beam of a certain width is irradiated to the center of the rotating shaft of the scanning arm of the sample arm, the beam has a certain offset ⁇ from the center of the rotating shaft.
  • the offset ⁇ introduces the modulation of the optical path of the sample arm, resulting in lateral scanning modulation in the spatial frequency domain, and its modulation frequency f m is linearly related to the offset ⁇ :
  • the traditional Doppler shift velocity method can only measure the velocity component parallel to the direction of the probe beam.
  • To measure the absolute velocity of the blood flow it is also necessary to measure the angle between the direction of the probe beam and the direction of blood flow (ie, the Doppler angle).
  • the angle-resolved modulation sub-spectrum obtained by the segmentation can be calculated by using the Doppler blood flow velocity calculation method.
  • the flow velocity components of the different incident angle detection directions are obtained, and the absolute blood flow velocity values can be determined according to the geometric relationship.
  • a micro-angiography system based on a full-space modulation spectrum segmentation angle composite comprising a low-coherence broadband source, an optical circulator, a fiber coupler, a reference arm, a sample arm, a spectrometer, and a signal processing module;
  • the reference arm includes a reference arm polarization control device, and a reference Arm collimating lens, reference arm focusing lens and plane mirror;
  • sample arm includes sample arm polarization controller, sample arm collimating lens, orthogonal scanning galvanometer and sample arm focusing objective lens;
  • spectrometer includes spectrometer collimating lens, blazed grating, Fourier lens and line array CMOS camera;
  • the low-coherence broadband light source is connected to the input end of the fiber coupler via the optical circulator; one of the output ports on the other side of the fiber coupler is connected to the reference arm collimating lens via the reference arm polarization control device; the reference arm focusing lens
  • the optical axis coincides with the optical axis of the reference arm collimating lens, the planar mirror is placed at the focal plane of the reference arm focusing lens; the other output port on the other side of the fiber coupler passes through the sample arm polarization controller and the sample arm Straight lens is connected;
  • the center of the first scanning mirror of the orthogonal scanning galvanometer is located on the optical axis of the collimating lens of the sample arm, and the center of the rotating shaft of the second scanning mirror is located on the optical axis of the focusing objective of the sample arm, and the sample to be tested is placed on the sample
  • the arm focuses on the focal plane of the objective lens; the other output port of the optical circulator is connected to the spectroscope collimating lens
  • the light from the low-coherence broadband light source passes through the optical circulator and is incident on the fiber coupler.
  • the emitted light is divided into two parts, one part enters the reference arm, is collimated and then irradiated to the plane mirror; the other part enters the sample arm and is collimated.
  • the orthogonal scanning galvanometer of the sample arm realizes the three-dimensional scanning of the sample arm beam to be tested; the light reflected back by the reference arm mirror and the backscattered light of the sample to be tested are at the fiber coupler Interference occurs, and the emitted interference light passes through the spectrometer and is collected and processed by the signal processing module.
  • the present invention has the following beneficial effects:
  • the full-space lateral modulation spectrum segmentation technique referred to in the present invention can provide a horizontal modulation spectrum of the spatial frequency domain to the maximum, and eliminate the lateral resolution degradation caused by modulation spectrum segmentation.
  • the measurement of the absolute flow velocity of the blood flow can be achieved with a single beam single measurement.
  • Figure 1 is a schematic view of a scanning beam of a sample arm
  • Figure 3 is an aliasing diagram of the positive and negative frequency of the transverse scan modulation spectrum
  • Figure 4 is a flow chart showing the implementation of the method of the present invention.
  • Figure 5 is a schematic illustration of an imaging system of the present invention.
  • Figure 1 1, the probe beam; 2, the scanning galvanometer; 3, the center of the galvanometer shaft; 4, the focusing objective.
  • A represents the OCT interference spectrum real signal
  • B represents the spatial structure information of the depth (z) domain
  • C represents the spatial structure information after the conjugate term is removed
  • D represents the complex-valued interference spectrum
  • E represents the spatial frequency domain.
  • F1 to Fn respectively represent the modulated sub-spectrum spectra
  • G1 to Gn respectively represent z-domain spatial structure signals
  • H1 to Hn respectively represent optical contrast sub-graphs
  • I represents optical contrast images
  • Figure 5 1, low coherent broadband source; 2, optical circulator; 3, fiber coupler; 4, reference arm polarization control device; 5, reference arm collimating lens; 6, reference arm focusing lens; 7, plane reflection Mirror; 8, sample arm polarization control device; 9, sample arm collimating lens; 10, orthogonal scanning galvanometer; 11, sample arm focusing objective; 12, sample to be tested; 13, collimating lens; 14, blazed grating; 15, Fourier lens; 16, linear array CMOS camera; 17, signal processing module.
  • FIGS. 1, 2 and 3 show a schematic diagram of the lateral modulation principle of the present invention.
  • the schematic diagrams in Figs. 1, 2 and 3 will be described in detail below.
  • the beam diameter required to be irradiated onto the objective lens is as large as possible. Therefore, in Fig. 1, when a collimated beam of a certain width is irradiated to the center of the rotating shaft of the scanning arm of the sample arm, the beam has a certain offset ⁇ from the center of the rotating shaft.
  • the offset ⁇ introduces the modulation of the optical path of the sample arm, resulting in lateral scanning modulation in the spatial frequency domain (Fig. 2).
  • the modulation frequency f m is linearly related to the offset ⁇ :
  • the interference spectrum obtained corresponding to one horizontal scan is a real value signal. Since the spectral real signal is directly subjected to Fourier transform along the lateral fast sweep direction, the resulting spatial frequency distribution will produce aliasing of positive and negative frequencies (Fig. 3), so it is necessary to reconstruct the complex value OCT interference spectrum.
  • FIG. 4 is a flow chart showing a specific implementation of the method of the present invention. The process in Figure 4 is described in detail below:
  • the interference spectrum real signal i.e., box A
  • the real-number spectrum is Fourier transformed along the wavenumber k direction to obtain spatial structure information of the depth z-domain (ie, block B).
  • the spectral domain OCT half of the z-space corresponds to an imaging range of about 3 mm, which can satisfy most application requirements, so that the sample to be tested is completely placed on one side of the zero optical path difference to distinguish the complex conjugate image.
  • New z-domain spatial structure information ie, box C
  • the obtained lateral modulation spectrum is segmented, and the incident angle-resolved mutually independent OCT interference sub-spectra (ie, blocks F1 to Fn) can be obtained.
  • the number of sub-spectrums obtained by segmentation and the overlap between sub-spectra are determined by the final image effect: the more the number of segments, the more the lateral resolution is reduced, and the complexity of the processing algorithm is increased; The larger the overlap between the spectra, the lower the independence of the sub-spectra, affecting the detection of different incident angles.
  • the traditional Doppler shift velocity method can only measure the velocity component parallel to the direction of the probe beam.
  • To measure the absolute velocity of the blood flow it is also necessary to measure the angle between the direction of the probe beam and the direction of blood flow (ie, the Doppler angle).
  • the Doppler angle Based on full spatial modulation spectral segmentation, it is possible to resolve probe beams at different angles of incidence.
  • the Doppler blood flow velocity calculation method can be used to obtain flow velocity components of different incident angle detection directions, and the absolute blood flow velocity values can be determined according to the geometric relationship.
  • FIG. 5 is a schematic illustration of the imaging system of the present invention. FIG. 5 will be described in detail below.
  • a micro-angiography system based on full spatial modulation spectrum segmentation angle composite comprising a low coherence broadband light source 1, an optical circulator 2, a fiber coupler 3, a reference arm, a sample arm, a spectrometer, and a signal processing module 17;
  • the reference arm includes a reference arm polarization Control device 4, reference arm collimating lens 5, reference arm focusing lens 6 and plane mirror 7;
  • sample arm including sample arm polarization controller 8, sample arm collimating lens 9, quadrature scanning galvanometer 10 and sample arm focusing objective lens 11;
  • the spectrometer comprises a spectrometer collimating lens 13, a blazed grating 14, a Fourier lens 15 and a line CMOS camera;
  • the low-coherent broadband light source 1 is connected to the input end of the fiber coupler 3 via the optical circulator 2; one of the output ports of the other side of the fiber coupler 3 passes the reference arm polarization control device 4 and the reference arm
  • the straight lens 5 is connected; the optical axis of the reference arm focusing lens 6 coincides with the optical axis of the reference arm collimating lens 5, the plane mirror 7 is placed at the focal plane of the reference arm focusing lens 6, and the other side of the optical fiber coupler 3
  • Another output port is connected to the sample arm collimating lens 9 via the sample arm polarization controller 8; the first scanning mirror axis of the orthogonal scanning galvanometer 10 is located on the optical axis of the sample arm collimating lens 9, the second scan
  • the center of the mirror shaft is located on the optical axis of the sample arm focusing objective lens 11, and the sample 12 to be tested is placed at the focal plane of the sample arm focusing objective lens 11; the other output port of the optical circulator 2 is connected to the spectr
  • the light emitted by the low-coherence broadband light source 1 passes through the optical circulator 2 and is incident on the fiber coupler 3, and the emitted light is divided into two parts, a part of which enters the reference arm, is collimated and then irradiated to the plane mirror 7; the other part enters the sample arm, After collimating the focus, it is irradiated onto the sample 12 to be tested; the orthogonal scanning galvanometer 10 of the sample arm realizes the three-dimensional scanning of the sample arm beam 12 to be tested; The light reflected back by the mirror 7 interferes with the backscattered light of the sample 12 to be tested at the fiber coupler 3, and the emitted interference light is collected by the signal processing module 17 after passing through the spectrometer.

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Abstract

一种基于全空间调制谱分割角度复合的微血管造影方法与系统，其中结合了光学相干层析技术的三维空间分辨能力和动态散射技术的运动识别能力，用于实现无标记的三维光学微血管造影。利用空间频率域的横向扫描调制谱编码不同入射角度的探测光，通过分割调制谱获得入射角度分辨的相互独立的血管造影子图，实现多个空间角度复合的微血管造影图。通过在深度(z)域去除共轭镜像，重构复数值的OCT干涉光谱，在空间频率域得到全空间的调制谱，避免调制谱共轭镜像的干扰。该微血管造影方法中的角度复合技术可以增强血管造影的对比度，空间频率域的全空间技术提供最大化的调制谱带宽和对比度增强效果，多个角度分辨的探测技术可以实现血流绝对流速的测量。

Description

基于全空间调制谱分割角度复合的微血管造影方法与系统 技术领域
本发明涉及光学相干层析成像技术(Optical Coherence Tomography，OCT)以及在此基础之上的无标记三维光学微血管造影技术(OCT Angiography,Angio-OCT)，尤其涉及基于全空间调制谱分割角度复合的微血管造影方法与系统。
技术背景
OCT技术是自从上世纪90年代以后逐步发展起来的在生物医学领域具有重大应用价值的一种新型成像技术。凭借着无标记物、非侵入性、非接触性、高成像分辨率和高探测灵敏度等优点，它吸引着越来越多的国内外科研工作者更加深入地对其进行研究，目前在医学临床中得到了广泛应用。OCT技术主要依据所探测到的由于生物样品的光学不均匀性所导致的样品背向散射光光强变化，获取样品内部的反射率信息，进而重构出样品的断层结构图像。然而通常在疾病的早期阶段，由于正常的和病变的生物组织间光散射特性的差异性较小，运用传统的结构型OCT较难加以检测并区分，故而在临床应用上其存在诸多的局限性。为了能够获得除生物样品组织形态结构之外更多的生理信息，功能型OCT技术得到了开发并广泛应用。
诸多的疾病(如青光眼、老年黄斑病变等眼底疾病，脑中风等脑疾病)与血流灌注的病态变化存在密切的相关性。如若能够实时监测病人血管的变化，并提供血管的三维影像，对该类疾病的早期诊断和控制具有重要的意义。Angio-OCT技术是一项具有巨大前景的可有助于血管疾病诊断的工具，其能够较好的区分静态的组织和动态的血流信号，实现了OCT在获取血管内血流信息方面的功能性拓展。相较于传统的造影技术，其优势体现在无需注入显影剂和利用X射线，并结合前面所述OCT技术的特点，能够实现微血管三维深度分辨的高对比度的成像。通常，血流对比度的模型建立是运用数学的手段分析光散射信号的时间统计特性，并用阈值分割动态的血流信号和静态的组织背景信号来实现的。然而由于动态和静态信号统计曲线之间存在重叠，导致动态和静态信号分割错误，血流对比度受 到抑制。因此，采取有效的方法提高造影图的血流对比，有助于更加清晰地解释说明图像的特征。
基于Angio-OCT信号的时间统计特性研究得出：多个独立的血管造影子图的平均可以提高造影的对比度。参照一些消除散斑的方法，可以通过波长多样性、角度多样性和偏振多样性等方法来获取独立的造影子图。Jia等人提出了一种类似于波长多样性的光谱分割Angio-OCT方法。该方法将OCT干涉信号的全波长光谱分割成不同的子光谱，每个子光谱可产生独立的造影子图，通过复合形成新的血管造影图。然而相对于原来的全光谱，每个子光谱带宽变窄，导致图像的轴向分辨率下降。
发明内容
本发明针对现有技术的不足，提出了基于全空间调制谱分割角度复合的微血管造影方法与系统。
基于全空间调制谱分割角度复合的微血管造影方法，具体包括以下步骤：
1)通过在OCT深度(z)域去除共轭镜像，重构复数值的干涉光谱，在空间频率域得到全空间的横向扫描调制谱；
2)利用空间频率域的横向扫描调制谱编码不同入射角度的探测光，通过分割调制谱获得入射角度分辨的相互独立的OCT干涉子光谱；
3)结合2)中的调制谱分割技术与光学微血管造影技术，得到基于横向扫描调制谱分割的多个角度分辨的独立的血管造影子图；
4)结合1)中的全空间调制谱和2)中的调制谱分割技术和与光学微血管造影技术，获得基于全空间横向扫描调制谱分割的多个角度分辨的独立的血管造影子图；
5)对3)或4)中得到的血管造影子图进行平均，得到多个空间角度复合的血管造影图。
根据2)中的调制谱分割技术，实现基于横向扫描调制谱分割的多个角度分辨的血流绝对流速测量；
根据1)中的全空间调制谱和2)中的调制谱分割技术，实现基于全空间横向扫描调制谱分割的多个角度分辨的血流绝对流速测量。
本发明的目的是通过如下技术方案实现的：
基于全空间调制谱分割角度复合的微血管造影方法：
1)在OCT成像中，对应于一次横向扫描得到的干涉光谱实数信号，可表示为S(k,x)，其中k代表波数，x代表横向的快扫方向。由于直接对光谱实数信号沿横向x方向作傅里叶变换，所得到的空间频率分布会产生正负频率的混叠，因此需要重构出复数值的OCT干涉光谱。为了重构出复数谱，对实数谱S(k,x)沿着k方向进行傅里叶变换，得到深度域(z)的空间结构信息。通常在谱域OCT中，一半的z空间对应约3mm的成像范围，能够满足绝大多数的应用要求，于是将待测样品完全置于零光程差的一边，以分辨复共轭镜像。通过去除z域中的共轭项，沿k方向进行傅里叶逆变换，最终得到复数值的光谱信号
Figure PCTCN2016079693-appb-000001
对该复数谱沿x方向进行傅立叶变换，在空间频率域获得全空间的横向扫描调制谱。
2)通常在OCT系统的样品臂中，为获得较高的横向成像分辨率，要求照射到物镜上的光束直径尺寸尽量大。因此，当一定宽度的准直光束照射到样品臂扫描振镜的转轴中心时，光束距离转轴中心存在一定的偏移量δ。而偏移量δ会引入样品臂光程的调制，导致在空间频率域的横向扫描调制，其调制频率fm与偏移量δ成线性函数关系：
Figure PCTCN2016079693-appb-000002
其中，k表示光源的中心波数，ω表示扫描振镜的角速度。因此，在全空间的横向扫描调制谱中，不同的调制频率对应着不同入射角度的探测光。对该调制谱进行分割，可获得入射角度分辨的相互独立的OCT干涉子光谱。分割得到的子光谱个数及子光谱间的重叠视最终的图像效果而定：分割的个数越多会导致横向分辨率减小得越多，此外还增加了处理算法的复杂度；子光谱间相互重叠的部分越大，会导致子光谱相互之间的独立性下降，影响编码不同入射角度的探测光。
3)对获得的入射角度分辨的相互独立的子光谱，利用目前的微血管造影技术，如幅值差分法、复数差分法、去互相关法和散斑方差法等，分别产生相对应的独立的造影子图。对这些空间角度分辨的造影子图进行复合平均，得到新的微血管造影图。
传统的多普勒频移测流速法只能测量与探测光束方向平行的速度分量。要测量血流的绝对速度，还需测得探测光束方向与血流方向的夹角(即多普勒角)。基于全空间调制谱分割，能够分辨不同入射角度的探测光束。对分割得到的角度分辨的调制子光谱，利用多普勒血流速度计算方法，可 以获得不同入射角度探测方向的流速分量，进而根据几何关系可确定绝对的血流速度值。
基于全空间调制谱分割角度复合的微血管造影系统，包括低相干宽带光源、光环行器、光纤耦合器、参考臂、样品臂、光谱仪和信号处理模块；其中参考臂包括参考臂偏振控制器件、参考臂准直透镜、参考臂聚焦透镜和平面反射镜；样品臂包括样品臂偏振控制器、样品臂准直透镜、正交扫描振镜和样品臂聚焦物镜；光谱仪包括光谱仪准直透镜、闪耀光栅、傅里叶透镜和线阵CMOS相机；
低相干宽带光源经过光环行器与光纤耦合器一侧的输入端相连接；光纤耦合器另一侧的其中一个输出端口经过参考臂偏振控制器件与参考臂准直透镜相连接；参考臂聚焦透镜的光轴与参考臂准直透镜的光轴重合，平面反射镜置于参考臂聚焦透镜的焦平面处；光纤耦合器另一侧的另外一个输出端口，经过样品臂偏振控制器与样品臂准直透镜相连接；正交扫描振镜的第一扫描镜转轴中心位于样品臂准直透镜的光轴上，第二扫描镜转轴中心位于样品臂聚焦物镜的光轴上，待测样品置于样品臂聚焦物镜的焦平面处；光环行器的另一个输出端口与光谱仪准直透镜相连接，闪耀光栅根据分光原理放置在光谱仪准直透镜的出射光路上，傅里叶透镜置于闪耀光栅的出射光路上，线阵CMOS相机的采光面与傅里叶透镜的后焦平面重合；线阵CMOS相机后面接信号处理模块；
低相干宽带光源发出的光经过光环行器后入射到光纤耦合器，出射光分成两部分，一部分进入参考臂，经准直聚焦后照射到平面反射镜；另一部分进入样品臂，经过准直聚焦后照射到待测样品上；样品臂的正交扫描振镜实现样品臂光束对待测样品的三维扫描；参考臂反射镜反射回的光与待测样品背向散射回的光在光纤耦合器处发生干涉，出射的干涉光经过光谱仪后由信号处理模块采集处理。
与背景技术相比，本发明具有的有益效果是：
1)利用本发明获得的多个空间角度复合的微血管造影图，具有增强的对比度和血管连通性
2)相比于背景技术中谈及的类似于波长多样性的光谱分割Angio-OCT方法，其对光谱分割会导致轴向分辨率的下降。本发明对轴向分辨率不产生影响。
3)本发明谈及的全空间的横向调制谱分割技术，可以提供最大化的空间频率域的横向调制谱，消除由于调制谱分割导致的横向分辨率下降。
4)利用本发明谈及的基于全空间调制谱分割的多个角度分辨的探测技术，可以在单光束单次测量的情况下实现血流绝对流速的测量。
附图说明
图1为样品臂扫描光束示意图；
图2为偏移量δ引入的调制频率fm图；
图3为横向扫描调制谱正负频率混叠图；
图4是本发明的方法实现流程图；
图5是本发明的成像系统示意图。
图1中：①、探测光束；②、扫描振镜；③、振镜转轴中心；④、聚焦物镜。
图2中：偏移量δ引入的调制频率fm。
图3中：正负频率混叠的横向扫描调制谱。
图4中：A表示OCT干涉光谱实数信号；B表示深度(z)域的空间结构信息；C表示去除共轭项后的空间结构信息；D表示复数值的干涉光谱；E表示空间频率域的全空间横向扫描调制谱；F1至Fn分别表示分割得到的调制子光谱；G1至Gn分别表示z域空间结构信号；H1至Hn分别表示光学造影子图；I表示光学造影图；
图5中：1、低相干宽带光源；2、光环行器；3、光纤耦合器；4、参考臂偏振控制器件；5、参考臂准直透镜；6、参考臂聚焦透镜；7、平面反射镜；8、样品臂偏振控制器件；9、样品臂准直透镜；10、正交扫描振镜；11、样品臂聚焦物镜；12、待测样品；13、准直透镜；14、闪耀光栅；15、傅里叶透镜；16、线阵CMOS相机；17、信号处理模块。
具体实施方式
下面结合附图和实施例子对本发明作进一步的说明。
图1、图2和图3所示为本发明的横向调制原理示意图。下面对图1、图2和图3中的示意图作详细说明。
1)通常在OCT系统的样品臂中，为获得较高的横向成像分辨率，要求照射到物镜上的光束直径尺寸尽量大。因此，在图1中，当一定宽度的准直光束照射到样品臂扫描振镜的转轴中心时，光束距离转轴中心存在一 定的偏移量δ。而偏移量δ会引入样品臂光程的调制，导致在空间频率域的横向扫描调制(如图2)，其调制频率fm与偏移量δ成线性函数关系：
Figure PCTCN2016079693-appb-000003
其中，k表示光源的中心波数，ω表示扫描振镜的角速度。因此，在全空间的横向扫描调制谱中，不同的调制频率对应着不同入射角度的探测光。
2)在OCT成像中，对应于一次横向扫描得到的干涉光谱为实数值信号。由于直接对光谱实数信号沿横向快扫方向作傅里叶变换，所得到的空间频率分布会产生正负频率的混叠(如图3)，因此需要重构出复数值的OCT干涉光谱。
图4所示为本发明的方法的具体实现流程图。下面对图4中的过程进行详细说明：
1)在OCT成像中，对应于一次横向扫描得到的是干涉光谱实数信号(即方框A)。为了重构出复数值的光谱信号，对实数谱沿着波数k方向进行傅里叶变换，得到深度z域的空间结构信息(即方框B)。通常在谱域OCT中，一半的z空间对应约3mm的成像范围，能够满足绝大多数的应用要求，于是将待测样品完全置于零光程差的一边，以分辨复共轭镜像。通过去除z域中的共轭项，得到新的z域空间结构信息(即方框C)。而后沿着k方向进行傅里叶逆变换，最终得到复数值的光谱信号
Figure PCTCN2016079693-appb-000004
(即方框D)。对该复数谱沿x方向进行傅立叶变换，在空间频率域获得全空间的横向扫描调制谱(即方框E)。
2)对得到的横向调制谱进行分割，可获得入射角度分辨的相互独立的OCT干涉子光谱(即方框F1至Fn)。分割得到的子光谱个数n及子光谱间的重叠视最终的图像效果而定：分割的个数越多会导致横向分辨率减小得越多，此外还增加了处理算法的复杂度；子光谱间相互重叠的部分越大，会导致子光谱相互之间的独立性下降，影响编码不同入射角度的探测光。
3)对获得的入射角度分辨的相互独立的子光谱(即方框F1至Fn)，分别沿着x方向进行傅里叶逆变换，再沿着k方向进行傅里叶变换，得到z域的空间结构信息(即方框G1至Gn)。利用目前的光学微血管造影技术，如幅值差分法、互相关法等，分别产生相对应的独立的造影子图(即 方框H1和Hn)。对这些空间角度分辨的造影子图进行复合平均，得到新的微血管造影图(即方框I)，其血流对比度得到了提高。
传统的多普勒频移测流速法只能测量与探测光束方向平行的速度分量。要测量血流的绝对速度，还需测得探测光束方向与血流方向的夹角(即多普勒角)。基于全空间调制谱分割，能够分辨不同入射角度的探测光束。对分割得到的调制子光谱(即方框F1至Fn)，利用多普勒血流速度计算方法，可以获得不同入射角度探测方向的流速分量，根据几何关系可确定绝对的血流速度值。
图5所示为本发明的成像系统示意图。下面对图5进行详细说明。
基于全空间调制谱分割角度复合的微血管造影系统，包括低相干宽带光源1、光环行器2、光纤耦合器3、参考臂、样品臂、光谱仪和信号处理模块17；其中参考臂包括参考臂偏振控制器件4、参考臂准直透镜5、参考臂聚焦透镜6和平面反射镜7；样品臂包括样品臂偏振控制器8、样品臂准直透镜9、正交扫描振镜10和样品臂聚焦物镜11；光谱仪包括光谱仪准直透镜13、闪耀光栅14、傅里叶透镜15和线阵CMOS相机；
其特征在于：低相干宽带光源1经过光环行器2与光纤耦合器3一侧的输入端相连接；光纤耦合器3另一侧的其中一个输出端口经过参考臂偏振控制器件4与参考臂准直透镜5相连接；参考臂聚焦透镜6的光轴与参考臂准直透镜5的光轴重合，平面反射镜7置于参考臂聚焦透镜6的焦平面处；光纤耦合器3另一侧的另外一个输出端口，经过样品臂偏振控制器8与样品臂准直透镜9相连接；正交扫描振镜10的第一扫描镜转轴中心位于样品臂准直透镜9的光轴上，第二扫描镜转轴中心位于样品臂聚焦物镜11的光轴上，待测样品12置于样品臂聚焦物镜11的焦平面处；光环行器2的另一个输出端口与光谱仪准直透镜13相连接，闪耀光栅14根据分光原理放置在光谱仪准直透镜13的出射光路上，傅里叶透镜15置于闪耀光栅14的出射光路上，线阵CMOS相机16的采光面与傅里叶透镜15的后焦平面重合；线阵CMOS相机16后面接信号处理模块17；
低相干宽带光源1发出的光经过光环行器2后入射到光纤耦合器3，出射光分成两部分，一部分进入参考臂，经准直聚焦后照射到平面反射镜7；另一部分进入样品臂，经过准直聚焦后照射到待测样品12上；样品臂的正交扫描振镜10实现样品臂光束对待测样品12的三维扫描；参考臂反 射镜7反射回的光与待测样品12背向散射回的光在光纤耦合器3处发生干涉，出射的干涉光经过光谱仪后由信号处理模块17采集处理。

Claims (4)

  1. 基于全空间调制谱分割角度复合的微血管造影方法，其特征在于，该方法具体包括以下步骤：
    1)通过在OCT深度(z)域去除共轭镜像，重构复数值的干涉光谱，在空间频率域得到全空间的横向扫描调制谱；
    2)利用空间频率域的横向扫描调制谱编码不同入射角度的探测光，通过分割调制谱获得入射角度分辨的相互独立的OCT干涉子光谱；
    3)结合2)中的调制谱分割技术与光学微血管造影技术，得到基于横向扫描调制谱分割的多个角度分辨的独立的血管造影子图；
    4)结合1)中的全空间调制谱和2)中的调制谱分割技术和与光学微血管造影技术，获得基于全空间横向扫描调制谱分割的多个角度分辨的独立的血管造影子图；
    5)对3)或4)中得到的血管造影子图进行平均，得到多个空间角度复合的血管造影图。
  2. 根据权利要求1所述的基于全空间调制谱分割角度复合的微血管造影方法，其特征在于：根据2)中的调制谱分割技术，实现基于横向扫描调制谱分割的多个角度分辨的血流绝对流速测量。
  3. 根据权利要求1所述的基于全空间调制谱分割角度复合的微血管造影方法，其特征在于：根据1)中的全空间调制谱和2)中的调制谱分割技术，实现基于全空间横向扫描调制谱分割的多个角度分辨的血流绝对流速测量。
  4. 基于全空间调制谱分割角度复合的微血管造影系统，包括低相干宽带光源、光环行器、光纤耦合器、参考臂、样品臂、光谱仪和信号处理模块；其中参考臂包括参考臂偏振控制器件、参考臂准直透镜、参考臂聚焦透镜和平面反射镜；样品臂包括样品臂偏振控制器、样品臂准直透镜、正交扫描振镜和样品臂聚焦物镜；光谱仪包括光谱仪准直透镜、闪耀光栅、傅里叶透镜和线阵CMOS相机；
    其特征在于：低相干宽带光源经过光环行器与光纤耦合器一侧的输入端相连接；光纤耦合器另一侧的其中一个输出端口经过参考臂偏振控制器件与参考臂准直透镜相连接；参考臂聚焦透镜的光轴与参考臂准直透镜的光轴重合，平面反射镜置于参考臂聚焦透镜的焦平面处；光纤耦合器另一 侧的另外一个输出端口，经过样品臂偏振控制器与样品臂准直透镜相连接；正交扫描振镜的第一扫描镜转轴中心位于样品臂准直透镜的光轴上，第二扫描镜转轴中心位于样品臂聚焦物镜的光轴上，待测样品置于样品臂聚焦物镜的焦平面处；光环行器的另一个输出端口与光谱仪准直透镜相连接，闪耀光栅根据分光原理放置在光谱仪准直透镜的出射光路上，傅里叶透镜置于闪耀光栅的出射光路上，线阵CMOS相机的采光面与傅里叶透镜的后焦平面重合；线阵CMOS相机后面接信号处理模块；
    低相干宽带光源发出的光经过光环行器后入射到光纤耦合器，出射光分成两部分，一部分进入参考臂，经准直聚焦后照射到平面反射镜；另一部分进入样品臂，经过准直聚焦后照射到待测样品上；样品臂的正交扫描振镜实现样品臂光束对待测样品的三维扫描；参考臂反射镜反射回的光与待测样品背向散射回的光在光纤耦合器处发生干涉，出射的干涉光经过光谱仪后由信号处理模块采集处理。
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Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN115639198A (zh) * 2022-11-15 2023-01-24 南京理工大学 一种全场光学时空相干编码动态体成像装置及方法

Families Citing this family (27)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN105852816A (zh) * 2016-05-16 2016-08-17 浙江大学 一种全通道调制编码的角度复合散斑降噪方法与系统
CN106236205A (zh) * 2016-07-27 2016-12-21 深圳市中科微光医疗器械技术有限公司 一种基于近红外相干断层成像技术的血管导航系统及方法
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CN107822600A (zh) * 2017-12-14 2018-03-23 天津海仁医疗技术有限公司 应用于血管性皮肤病检测、定位的装置和系统及工作方法
CN108852285B (zh) * 2018-04-16 2020-10-23 清华大学深圳研究生院 一种基于频域oct的微血管造影方法
CN108956533A (zh) * 2018-07-13 2018-12-07 福州大学 一种可消除多色误差的oct共轭镜像去除装置及方法
CN109008982B (zh) * 2018-08-09 2021-01-29 中南大学 一种多普勒光学相干层析的绝对流速测量装置与方法
CN110873956B (zh) * 2018-08-29 2021-07-23 暨南大学 一种超高速正交偏振成像装置及方法
CN109297599B (zh) * 2018-11-09 2023-08-18 福州大学 可消除oct共轭镜像的定相差线阵谱域oct装置及方法
CN109691971A (zh) * 2018-12-29 2019-04-30 佛山科学技术学院 眼前节组织动态参数快速成像的光学相干层析成像系统
CN109620134B (zh) * 2019-01-21 2020-05-22 浙江大学 基于光纤阵列多通道并行探测的微血管造影方法和系统
CN109965839A (zh) * 2019-04-08 2019-07-05 广东唯仁医疗科技有限公司 眼前节oct成像装置
CN110013212B (zh) * 2019-04-23 2024-04-16 广东唯仁医疗科技有限公司 基于光学相干断层扫描的多参数、多功能眼睛测量仪
CN110151133B (zh) * 2019-05-24 2021-10-01 哈尔滨工业大学 基于图像分割与时频信息融合的乳腺光学成像装置及方法
CN111134614A (zh) * 2019-12-20 2020-05-12 苏州大学 基于oct测量眼球血管中血流的绝对速度的方法及系统
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CN112075925A (zh) * 2020-09-21 2020-12-15 北京脑科学与类脑研究中心 基于散斑原理的荧光成像照明装置、成像系统及成像方法
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CN113267142B (zh) * 2021-05-17 2022-08-19 东北大学秦皇岛分校 一种表面轮廓成像装置及成像方法
CN113665150B (zh) * 2021-08-31 2022-07-12 广州永士达医疗科技有限责任公司 一种软管制作方法及探头软管
US20250252622A1 (en) * 2022-04-25 2025-08-07 Nanyang Technological University Phase-restoring translational shifting of multidimensional images
CN115089118A (zh) * 2022-06-20 2022-09-23 暨南大学附属第一医院（广州华侨医院） 一种双模态融合的血管成像系统
CN117297555B (zh) * 2023-11-29 2024-02-09 北京理工大学 一种基于并行光计算的光谱处理系统及在oct中的应用
CN120577263B (zh) * 2025-07-21 2025-10-03 长春理工大学 针对透明与非透明复合材料加工oct在线监测装置

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20120099076A1 (en) * 2010-10-21 2012-04-26 Canon Kabushiki Kaisha Imaging apparatus and ophthalmic apparatus
WO2013081902A1 (en) * 2011-11-30 2013-06-06 University Of Miami System and method for improving image quality in vivo oct imaging
US20130301001A1 (en) * 2012-05-10 2013-11-14 Matthew Carnevale Multimodality correlation of optical coherence tomography using secondary reference images
CN103565405A (zh) * 2013-11-15 2014-02-12 浙江大学 基于分段光谱光程编码的谱域oct探测系统及方法
CN104523239A (zh) * 2015-01-12 2015-04-22 南京理工大学 全深度谱域光学相干层析成像装置及方法
CN205458608U (zh) * 2016-02-05 2016-08-17 浙江大学 基于全空间调制谱分割角度复合的微血管造影系统

Family Cites Families (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2008154349A2 (en) * 2007-06-06 2008-12-18 Oregon Health & Science University Method and apparatus for localized polarization sensitive imaging
CN101803908A (zh) * 2010-03-01 2010-08-18 浙江大学 基于色散调制的无镜像光学频域成像系统及方法
EP2809225B1 (en) * 2012-02-03 2017-04-05 Oregon Health & Science University In vivo optical flow imaging
US8896841B2 (en) * 2012-03-13 2014-11-25 Kabushiki Kaisha Topcon Optical imaging method and optical imaging apparatus using optical coherence tomography
CN103267732B (zh) * 2013-05-21 2016-12-28 浙江大学 基于移动光栅空间载频谱域oct全量程成像方法

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20120099076A1 (en) * 2010-10-21 2012-04-26 Canon Kabushiki Kaisha Imaging apparatus and ophthalmic apparatus
WO2013081902A1 (en) * 2011-11-30 2013-06-06 University Of Miami System and method for improving image quality in vivo oct imaging
US20130301001A1 (en) * 2012-05-10 2013-11-14 Matthew Carnevale Multimodality correlation of optical coherence tomography using secondary reference images
CN103565405A (zh) * 2013-11-15 2014-02-12 浙江大学 基于分段光谱光程编码的谱域oct探测系统及方法
CN104523239A (zh) * 2015-01-12 2015-04-22 南京理工大学 全深度谱域光学相干层析成像装置及方法
CN205458608U (zh) * 2016-02-05 2016-08-17 浙江大学 基于全空间调制谱分割角度复合的微血管造影系统

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN115639198A (zh) * 2022-11-15 2023-01-24 南京理工大学 一种全场光学时空相干编码动态体成像装置及方法
CN115639198B (zh) * 2022-11-15 2024-05-07 南京理工大学 一种全场光学时空相干编码动态体成像装置及方法

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