[go: up one dir, main page]

WO2016188178A1 - 一种测量血管血液流量的设备及方法 - Google Patents

一种测量血管血液流量的设备及方法 Download PDF

Info

Publication number
WO2016188178A1
WO2016188178A1 PCT/CN2016/075790 CN2016075790W WO2016188178A1 WO 2016188178 A1 WO2016188178 A1 WO 2016188178A1 CN 2016075790 W CN2016075790 W CN 2016075790W WO 2016188178 A1 WO2016188178 A1 WO 2016188178A1
Authority
WO
WIPO (PCT)
Prior art keywords
optical path
light
blood vessel
translating device
module
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/CN2016/075790
Other languages
English (en)
French (fr)
Other versions
WO2016188178A8 (zh
Inventor
郭曙光
万明明
李鹏
代祥松
张德兴
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Shenzhen Certainn Technology Co Ltd
Original Assignee
Shenzhen Certainn Technology Co Ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Shenzhen Certainn Technology Co Ltd filed Critical Shenzhen Certainn Technology Co Ltd
Priority to EP16799067.0A priority Critical patent/EP3305187A4/en
Priority to US15/574,934 priority patent/US10456033B2/en
Publication of WO2016188178A1 publication Critical patent/WO2016188178A1/zh
Anticipated expiration legal-status Critical
Publication of WO2016188178A8 publication Critical patent/WO2016188178A8/zh
Ceased legal-status Critical Current

Links

Images

Classifications

    • 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
    • A61B3/12—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for looking at the eye fundus, e.g. ophthalmoscopes
    • A61B3/1225—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for looking at the eye fundus, e.g. ophthalmoscopes using coherent radiation
    • A61B3/1233—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for looking at the eye fundus, e.g. ophthalmoscopes using coherent radiation for measuring blood flow, e.g. at the retina
    • 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]
    • 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
    • A61B3/12—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for looking at the eye fundus, e.g. ophthalmoscopes
    • A61B3/1241—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for looking at the eye fundus, e.g. ophthalmoscopes specially adapted for observation of ocular blood flow, e.g. by fluorescein angiography
    • 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
    • A61B3/14—Arrangements specially adapted for eye photography
    • 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
    • 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
    • A61B5/02—Detecting, measuring or recording for evaluating the cardiovascular system, e.g. pulse, heart rate, blood pressure or blood flow
    • A61B5/026—Measuring blood flow
    • 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
    • A61B5/7203—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal
    • 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
    • A61B5/7203—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal
    • A61B5/7207—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal of noise induced by motion artifacts
    • 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
    • G01B9/0201—Interferometers characterised by controlling or generating intrinsic radiation properties using temporal phase variation
    • 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
    • G01B9/02015—Interferometers characterised by the beam path configuration
    • G01B9/02029—Combination with non-interferometric systems, i.e. for measuring the object
    • G01B9/0203—With imaging systems
    • 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
    • G01B9/02055—Reduction or prevention of errors; Testing; Calibration
    • G01B9/02075—Reduction or prevention of errors; Testing; Calibration of particular errors
    • G01B9/02076—Caused by motion
    • 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
    • G01N21/47—Scattering, i.e. diffuse reflection
    • G01N21/4795—Scattering, i.e. diffuse reflection spatially resolved investigating of object in scattering medium

Definitions

  • the present invention relates to the field of optoelectronic technology, and in particular, to an apparatus and method for measuring blood flow of a blood vessel.
  • retinal diseases are associated with abnormal blood flow to the eye, such as retinopathy caused by diabetes, retinal vein occlusion, and age-related macular degeneration.
  • retinal insufficiency is considered to be a possible cause of the development and progression of glaucoma. Therefore, measurement of retinal blood flow is of great significance for the clinical diagnosis, treatment and research of retinal diseases.
  • OCT Optical Coherence Tomography
  • OCT is a non-invasive detection technique that is widely used for imaging live structures in biological tissues.
  • OCT can provide a high-resolution, high-sensitivity tissue structure.
  • OCT technology can also detect the Doppler shift of scattered light to obtain motion information of fluids and samples, and is therefore suitable for measuring blood flow in the retina.
  • the frequency shift detected by the single-beam Doppler OCT is only related to the blood flow velocity in the direction of the probe beam, and the blood flow information perpendicular to the direction of the probe light cannot be directly obtained from the Doppler shift, and the intravascular can not be obtained. The actual flow rate.
  • (1) through three-dimensional scanning of the retina, obtain the direction of the blood vessels in the retina in space, thereby determining the Doppler angle of the probe light, and then using the Doppler angle to calculate the actual flow velocity, but due to the blood vessels of the retina It is close to the detector beam and this method is less accurate.
  • the space vector of the blood vessel to be tested is determined, and then the Doppler angle is calculated to obtain the actual flow velocity.
  • the measurement results of this method are affected by eye movements, and it can only measure blood vessels around the optic disc and cannot measure blood flow in other areas of the retina.
  • the OCT probe light is split into two beams by a glass plate.
  • the two beams are concentrated in the fluid to form a double beam.
  • the two-angle illumination method can obtain the real fluid in the blood vessel by analyzing the Doppler shift detected by the two beams. speed.
  • the drawback of this method is that it is not suitable for frequency domain OCT systems due to the time delay between the two paths of light.
  • dual light split by polarized light can be utilized The beam OCT system measures flow velocity and flow in the retinal vessels, or synchronizes with the OCT scanning mechanism using a DOVE prism to achieve a circular scan of the dual beam on the retina.
  • these two-beam systems are composed of two Michelson interferometers, which are complicated in structure and difficult to adjust, and based on the consideration of the safety of the probe light, the power of each probe light is much lower than that of the single-beam system, which reduces the double-beam OCT.
  • the sensitivity of the system increases the phase noise of the system.
  • FIG. 11 are schematic diagrams of circular scanning of all blood vessels in the optic disc.
  • a thick black line indicates the scanning direction of the probe light scanning fundus B, which corresponds to the Y direction in Fig. 9.
  • background Doppler which is not required, is a low-frequency background Doppler between light and dark and a high-frequency background Doppler with a sharp vertical line.
  • the original Doppler image (not shown) also appears as shown in FIG. Phase-to-phase low-frequency background Doppler and distinct vertical line-like high-frequency background Doppler.
  • background Doppler there are two reasons for generating background Doppler: First, the chief ray of the probe light is not incident on the rotating axis of the scanning unit. When the scanning unit is an XY galvanometer, the rotation axis of the Y galvanometer is considered to be the rotation axis of the scanning unit. Referring to FIG.
  • the incident direction e of the probe light and the scanning direction of the probe light on the imaging plane d of the lens 1 with the XY oscillating motion No longer vertical. If the incident light deviates from the galvanometer axis 1, the galvanometer scanning angular velocity is w, and the lens 1 focal length is f, the frequency shift is ( ⁇ 0 is the center wavelength of the probe light).
  • the high-frequency background Doppler needs to remove one line in the longitudinal direction when removing, and it is easy to find the corresponding background. The background error will directly affect the accuracy of the measurement.
  • the eyeball will rotate involuntarily, so the probe light cannot always illuminate the same position of the eyeball at the same angle, which brings The low-frequency background Doppler in the form of a region between the light and dark shown in FIG.
  • the present invention is directed to an apparatus and method for eliminating high frequency background Doppler and accurately measuring blood flow to blood vessels in the optic disc.
  • An apparatus for measuring blood flow of a blood vessel comprising: a light source, a beam splitting module, a reference arm module, a sample arm module, a detecting module and a control system; wherein the light source is split by the splitting module to form reference light and probe light, the reference Light is incident on the reference arm module, the probe light is incident on the sample arm module; the sample arm module includes a scanning unit and a rotatable optical path translating device, and a chief ray of the probe light is at a rotation axis of the scanning unit on;
  • the detecting light is reflected by the scanning unit and enters the optical path translating device.
  • the blood vessel is scanned in a first direction and carries information of the scanned blood vessel.
  • the sample arm module generating interference with the reference light returned from the reference arm at the beam splitting module to generate first interference light; the first interference light is detected by the detecting module, and processed by the control system Obtaining a first phase shift signal of the blood vessel;
  • the detecting light is reflected by the scanning unit and enters the optical path translating device.
  • the blood vessel is scanned in a second direction and carries the scanned blood vessel.
  • the principal ray of the probe light incident on the optical path translating device coincides with the rotation axis of the optical path translating device.
  • the angle is 180°.
  • the sample arm module further includes a collimating mirror, a relay lens, a dichroic mirror and an ophthalmoscope;
  • the collimating mirror is configured to collimate the probe light obtained by splitting the spectroscopic module;
  • the relay lens converges the probe light from the optical path translating device to the dichroic mirror;
  • the dichroic mirror reflects the probe light from the relay lens to the ophthalmoscope, and is concentrated by the ophthalmoscope After scanning the blood vessels.
  • a preview module which includes an illumination source, a first lens, and a camera; the light emitted by the illumination source illuminates the eye, and reflection occurs in the fundus, and the reflected light sequentially passes through the ophthalmoscope, the second After being transmitted to the color mirror and the first lens, it is received by the camera and displayed by a computer.
  • the scanning unit is an X-Y galvanometer
  • a rotation axis of the scanning unit is a rotation axis of the X-Y galvanometer.
  • the optical path translating device is at least one of flat glass in which both ends are chamfered, two mirrors or prisms arranged in parallel.
  • the invention also discloses a method for measuring blood flow of a single blood vessel, comprising the following steps:
  • the sample arm module comprises a scanning unit and a rotatable optical path translating device; and the main light of the detecting light obtained by the splitting of the light source On the axis of rotation of the scanning unit;
  • the detecting light is reflected by the scanning unit and enters the optical path translating device, after which the blood vessel is scanned in a first direction and a first phase shift signal is generated;
  • the detecting light is reflected by the scanning unit and enters the optical path translating device, and then scans the blood vessel in a second direction to generate a second phase shift signal;
  • the blood flow of the blood vessel is calculated based on the first phase shift signal and the second phase shift signal.
  • the method further includes: modifying the second phase shift signal, the specific steps are:
  • the second phase shift signal is corrected using an interpolation calculation.
  • the method further includes:
  • the detecting light scans the blood vessel in a first direction when the optical path translating device is in a first position; the detecting light scans the blood vessel in a second direction when the optical path translating device is in a second position; the first direction and The second direction constitutes an XZ plane.
  • the present invention also discloses a method of measuring total blood flow near the optic disc, comprising the steps of:
  • the sample arm module includes a scanning unit and a rotatable optical path translating device; and the light source is split by the spectroscopic module to obtain the detecting light
  • the chief ray of the probe light is on a rotation axis of the scanning unit;
  • the detecting light is reflected by the scanning unit to the optical path translating device, and after the control unit controls the scanning unit and the optical path translating device to rotate synchronously, the optical disc is scanned in a circular direction in a first direction. a number of first phase shift signals corresponding to all blood vessels in all nearby blood vessels;
  • the detecting light is reflected by the scanning unit to the optical path translating device, and after the control unit controls the scanning unit and the optical path translating device to rotate synchronously, the optical disc is scanned in a circular direction in the second direction. a plurality of corrected second phase shift signals corresponding to all blood vessels in all nearby blood vessels;
  • the blood flow rate of the plurality of single blood vessels is taken as an absolute value, and the blood flow of all blood vessels near the optic disc is calculated;
  • the scanning trajectory when the detecting light is scanned in the second direction is the same as the scanning trajectory when scanning in the first direction.
  • the chief ray of the probe light is on the rotation axis of the scanning unit, and the probe light is reflected by the scanning unit to the optical path translating device.
  • the optical path translating device is in the first position, after the detecting light passes through the optical path translating device, the blood vessel B is scanned along the Y direction in the first direction S1, and the system obtains the first phase shift signal of the blood vessel; when the optical path translating device is in the second position
  • the probe light scans the blood vessel B along the Y direction in the second direction S2
  • the system obtains the second phase shift signal of the blood vessel B, and the system moves the first phase shift signal and the second phase shift signal into
  • the blood flow rate in the blood vessel B is calculated, and the blood flow rate is further determined.
  • the probe light Since the chief ray of the probe light is on the rotation axis of the scanning unit, the probe light is reflected by the scanning unit and enters the optical path translating device, and then the fundus blood vessel is scanned, so that the light is not detected in the first position or in the second position.
  • the main ray is always locked on the rotating axis of the scanning unit when the scanning unit scans the blood vessel, effectively avoiding the high frequency background Doppler appearing in the original fundus Doppler image shown in FIG. 4, thereby eliminating the removal. Extra work and errors caused by high frequency background Doppler.
  • the principal ray of the probe light is also placed on the rotation axis of the scanning unit, and the probe light is also reflected by the scanning unit to the optical path translating device, and the scanning unit and the optical path are controlled by the control system.
  • the device rotates synchronously, and the probe light annularly scans all blood vessels in the vicinity of the optic disc in the first direction S1 and the second direction S2, respectively.
  • the chief ray of the probe light is always located on the rotation axis of the scanning unit, the high-frequency background as shown in FIG. 4 does not appear in the original fundus Doppler image obtained by all the blood vessels near the circular scanning optic disc. Doppler eliminates the extra work and errors associated with removing high frequency backgrounds.
  • FIG. 1 is a schematic view showing a principal ray of a probe light falling on a rotation axis of a scanning unit
  • FIG. 2 is a schematic view of the principal ray of the probe light deviating from the rotation axis of the scanning unit;
  • Figure 3 is a video screenshot of one of the blood vessels B of the fundus scanning fundus
  • Figure 4 is a raw Doppler image of the collected blood vessel B, which has low frequency background Doppler and high frequency background Doppler;
  • Figure 5 is an image of the high frequency background Doppler processed in Figure 4.
  • FIG. 6 is a schematic structural diagram of a blood flow measuring device according to an embodiment of the present invention.
  • FIG. 7 is a detailed optical path diagram of the first structure of the optical path translating device 502 of the sample arm module 500 of FIG. 6 in a first position;
  • Figure 8 is a detailed view of the optical path when the first structure of the optical path translation device 502 of the sample arm module 500 of Figure 6 is in the second position; compared with Figure 7, the optical path translation device 502 is rotated through an angle of 180 °;
  • FIG. 9 is a detailed optical path diagram of the second structure of the optical path translating device 502 of the sample arm module 500 of FIG. 6 in a first position;
  • Figure 10 is a second configuration of the optical path translation device 502 of the sample arm module 500 of Figure 6
  • the detailed optical path at the second position; the angle of the optical path translating device 502 is 180° compared to FIG.
  • Figure 11 is a detailed optical path diagram of the third structure of the optical path translating device 502 of the sample arm module 500 of Figure 6 in a first position;
  • Figure 12 is a detailed view of the optical path when the third structure of the optical path translating device 502 of the sample arm module 500 of Figure 6 is in the second position; compared to Figure 11, the optical path translating device 502 is rotated through an angle of 180°.
  • Figure 13 is a schematic diagram showing the geometric angle formed by the angle ⁇ formed by the probe light incident on the retina of the eye and the blood vessel B when the optical path translation device 502 is in the first position and the second position;
  • Figure 14 is a scanning trajectory diagram of all blood vessels in the detection optical ring scan disk
  • Figure 15 is a schematic view of the probe light ring-scanning all blood vessels in the optic disc in the same direction in the first direction and the second direction;
  • Figure 16 is a graph showing changes in the first phase shift signal and the second phase shift signal over time
  • Figure 17 is a flow chart for eliminating high frequency background Doppler measurement of blood flow of a single blood vessel near the optic disc;
  • Figure 18 is a diagram of a method for eliminating blood flow in all blood vessels near the optic disc with high frequency background Doppler.
  • optical path translation device 502, optical path translation device
  • the present invention provides an apparatus for measuring blood flow to a blood vessel for measuring blood flow of a human tissue, including but not limited to human or animal eyes.
  • the selected measurement object is the blood vessel of the eye
  • the apparatus and method are equally applicable to measuring blood flow of human or animal tissues other than the eye, only However, it is necessary to replace the eyes mentioned in the technical examples with other tissues and organs, and to change the schematic diagram of the eye relating to the other tissues and organs in the drawings of the specification.
  • the blood flow measuring device capable of eliminating high frequency background Doppler includes a light source 100, a beam splitting module 200, a reference arm module 300, a sample arm module 500, a detecting module 600, and a control system 700.
  • the light emitted by the light source 100 is transmitted to the beam splitting module 200, and the light splitting module 200 divides the received light into reference light and probe light, wherein the reference light is transmitted to the reference arm module 300, and the probe light is transmitted to the sample arm module 500.
  • the reference arm module 300 reflects the received reference light and returns it to the beam splitting module 200.
  • the sample arm module 500 scans the eye 800 and is scattered by the tissue in the eye 800.
  • the signal light is again returned to the beam splitting module 200 via the collimating mirror 400, and the signal light and the reference light interfere with each other at the beam splitting module 200 to form interference light.
  • the detection module 600 receives the interference light
  • the signal of the interference light is transmitted to the control system 700, and the control system 700 processes the signal to obtain a phase shift signal of the tissue of the scanned eye.
  • the reference arm module 300 has a reference mirror 301 built therein, and the reference light obtained by the splitting module 200 is reflected by the reference mirror 301 and returned to the spectroscopic module 200 where it interferes with the signal light.
  • the reference mirror 301 is preferentially selected as a planar mirror.
  • the control system 700 referred to herein can be understood as a processing module of a computer.
  • the sample arm module 500 includes at least a scanning unit 501 and an optical path translating device 502, and the chief ray of the probe light split from the spectroscopic module 200 is directly incident on the rotational axis of the scanning unit 501.
  • the scanning unit is preferably an X-Y galvanometer
  • the rotational axis of the scanning unit is the rotational axis 501B of the X-Y galvanometer 501A in FIG.
  • the scanning unit 501 of Figs. 7 to 12 during the entire scanning process, the principal ray of the probe light is always located on the rotation axis 501B of the scanning unit 501 (see Fig. 1, at this time, the scanning unit 501 is preferably the X-Y galvanometer 501A).
  • FIGS. 7 through 12 specifically describe the specific optical path configuration of the sample arm module 500 for the three embodiments included in the optical path translating device 502, respectively. It should be noted that these three embodiments are merely exemplary, and the purpose thereof is to cause the principal ray 50 of the probe light to shift when it enters the light path translating device 502 and exits the optical path translating device 502. Therefore, any optical path structure that can achieve the above object falls within the protection scope of the present invention.
  • the optical path translating device 502 is a glass plate whose both ends are beveled.
  • the detecting light main ray 50 is incident on the rotating shaft of the scanning unit 501, and is reflected by the scanning unit 501 to the optical path translating device 502.
  • the detecting light is again refracted by the exit surface 502B of the optical path translating device 502, and the refractiond detecting light scans one of the eyes 800 in the first direction S1 and in the Y direction.
  • Blood vessel B (see Figure 13). After the scan is completed, the probe light carries the signal of the blood vessel B, and is scattered through the fundus, and the original path returns to the split mode in FIG.
  • the first interference light is detected by the detecting module 600, and the system obtains a first phase shift signal of the scanned blood vessel B. ⁇ a. It should be noted that, in FIG. 7, the chief ray 50 of the probe light reflected from the scanning unit 501 to the incident surface 502A of the optical path translating device 502 coincides with the rotational axis 502C of the optical path translating device 502.
  • the detecting light chief ray 50 is incident on the rotating shaft of the scanning unit 501, and is reflected to the optical path by the scanning unit 501.
  • the translating device 502 generates refraction at the incident surface 502A of the optical path translating device 502, and the refracted probe light is again refracted by the exit surface 502B of the optical path translating device 502.
  • the detecting light is scanned in the second direction S2 and in the Y direction.
  • the blood vessel B, the second signal carrying the blood vessel B after being scattered through the fundus, returns to the light splitting module 200 in FIG.
  • the second interference light is detected by the detecting module 600 to obtain a second phase shift signal ⁇ b of the scanned blood vessel.
  • the chief ray 50 of the probe light reflected from the scanning unit 501 to the exit surface 502B of the optical path translating device 502 coincides with the rotation axis 502C of the optical path translating device 502.
  • the optical path translating device 502 is two mirrors distributed in parallel.
  • the optical path translating means 502 is composed of two parallel first mirrors 502D and second mirrors 502E.
  • the detecting light chief ray 50 is incident on the rotating shaft of the scanning unit 501, is reflected by the scanning unit to the optical path translating device 502, and is reflected by the first reflecting mirror 502D.
  • the second mirror 502E is further emitted by the second mirror 502E, and the probe light scans one of the blood vessels B of the eye 800 in the first direction S1 and in the Y direction (see FIG. 13).
  • the signal of the probe light carrying the blood vessel B is reflected by the fundus, returns to the beam splitting module 200 in FIG. 6 in the original way, and interferes with the reference light returned from the reference arm module 300 at the beam splitting module 200 to form a first
  • the interference light is detected by the detection module 600, and the system obtains the first phase shift signal ⁇ of the scanned blood vessel B.
  • the chief ray 50 of the probe light reflected by the scanning unit 501 to the first mirror 502D and the rotation axis 502C of the optical path translating device 502 coincide.
  • the optical path translating device 502 when the optical path translating device 502 is in the second position, at this time, the first mirror 502D and the second mirror 502E are rotated as a whole along the rotating shaft 502C by 180°. Detecting light master The light 50 is incident on the rotating shaft of the scanning unit 501, is reflected by the scanning unit 501 to the optical path translating device 502, is reflected by the second reflecting mirror 502E to the first reflecting mirror 502D, and is then emitted by the first reflecting mirror 502D.
  • the second direction S2 scans one of the blood vessels B of the eye 800 in the Y direction. After the scanning is completed, the signal of the probe light carrying the blood vessel B is reflected by the fundus, returns to the beam splitting module 200 in FIG.
  • the system obtains the second phase shift signal ⁇ b of the scanned blood vessel B. It should be noted that, in FIG. 10, the chief ray 50 of the probe light reflected by the scanning unit 501 to the first mirror 502D and the rotation axis 502C of the optical path translating device 502 coincide.
  • the optical path translating device 502 is a prism.
  • the optical path translating device 502 when the optical path translating device 502 is in the first position, the probe main ray 50 is incident on the rotational axis of the scanning unit 501, and is reflected by the scanning unit 501 to the optical path translating device 502.
  • the optical path translating device 502 is a prism.
  • the probe light is reflected by the first reflecting surface 502F of the prism to the second reflecting surface 502G, and then emitted by the second reflecting surface 502G, and the detecting light scans one of the blood vessels B of the eye 800 in the first direction S1 and in the Y direction.
  • the signal of the probe light carrying the blood vessel B is reflected by the fundus, and returns to the beam splitting module 200 in FIG.
  • the reference light returned from the reference arm module 300 interferes at the beam splitting module 200 to form a first interference.
  • the first interference light is detected by the detection module 600 to obtain a first phase shift signal ⁇ a of the scanned blood vessel B. It should be noted that, in FIG. 11, the chief ray 50 of the probe light reflected by the scanning unit 501 to the first reflecting surface 502F and the rotating shaft 502C overlap.
  • the detecting main ray 50 is incident on the rotating shaft of the scanning unit 501, and is reflected by the scanning unit 501 to the optical path.
  • Device 502. The probe light is reflected by the second reflecting surface 502G of the prism to the first reflecting surface 502F, and then emitted by the first reflecting surface 502F, and the detecting light scans one of the blood vessels B of the eye 800 in the second direction S2 and in the Y direction. After the scanning is completed, the signal of the probe light carrying the blood vessel B is reflected by the fundus, returns to the beam splitting module 200 in FIG.
  • the interference light is detected by the detection module 600 to obtain a second phase shift signal ⁇ b of the scanned blood vessel B. It should be noted that, in FIG. 12, the chief ray 50 of the probe light reflected by the scanning unit 501 to the first reflecting surface 502F and The rotating shaft 502C coincides.
  • the angle formed by the first direction S1 and the second S2 direction is defined as ⁇ , and the plane formed is the X-Z plane.
  • the blood flow velocity V of the blood vessel B to be tested is calculated.
  • ⁇ 0 is the center wavelength of the probe light
  • n is the rate of blood in the blood vessel B in Fig. 13
  • ⁇ is the time interval of scanning of two adjacent rays of the OCT system
  • ⁇ is the blood flow direction of the blood vessel B.
  • the angle between VB and plane XZ which can be obtained from the three-dimensional projection of the retina.
  • the probe light is three-dimensionally scanned in the X-axis direction when it is incident on the blood vessel B in the first direction S1, and the angle between the blood vessel B and the X direction is the ⁇ angle in the combined fundus plan view.
  • the blood flow velocity V of the blood vessel B to be tested in the retina of the eye 800 can be determined according to the formula (1). Therefore, the blood flow rate of any single blood vessel in the retina of the eye 800 at any time can be calculated according to the formula (1).
  • the scanning light of the scanning unit 501 is used to realize various scanning modes such as X-direction scanning, Y-direction scanning or oblique line scanning. Therefore, the probe light is adjusted in accordance with the actual direction of the blood vessel B to be tested.
  • the sample arm module 500 further includes a collimating mirror 400, a dichroic mirror 503, and an ophthalmoscope 504 and a relay lens 506.
  • the collimating mirror 400 is disposed between the beam splitting module 200 and the scanning unit 501, and is responsible for collimating the reference light incident to the scanning unit 501.
  • the relay lens 506 converges the probe light from the optical path translating device 502 onto the dichroic mirror 503, which reflects the probe light from the relay lens 506 to the ophthalmoscope 504, and then transmits through the ophthalmoscope 504. After that, it is incident on the eye 800. After the probe light is reflected by the fundus, the information of the scanned blood vessel is carried, and the original path returns to the beam splitting module 200 in FIG.
  • the device of the present invention further includes a preview module 505.
  • the preview module 505 includes an illumination source (not shown), a first lens 505A, and a camera 505B.
  • the light emitted by the illumination source illuminates the eye 800 and scatters in the eye 800.
  • the scattered reflected light passes through the ophthalmoscope 504 and reaches the dichroic mirror 503, which is transmitted through the dichroic mirror 503 and then passed.
  • the first lens 505A is transmitted and reaches the camera 505B, and information of the reflected light is captured by the camera 505B.
  • the image taken by the camera 505B is displayed on the display screen of the control system 700 for the operator to know the relevant information of the eye 800 for further operation.
  • the probe light is reflected by the scanning unit 501 to the radiation path generating means 502. That is, when the optical path translating device 502 is in the first position and the second position, respectively, the chief ray of the detecting light is always on the rotating axis of the scanning unit 501, that is, the chief ray of the detecting light does not rotate due to the optical path translating device 502. And deviating from the rotation axis 501B of the scanning unit 501, thus avoiding the unnecessary high-frequency background Doppler appearing in the original Doppler image of the blood vessel B to be measured shown in FIG.
  • the blood vessel B is one of the optic discs of the eye 800, which is merely exemplary, and can also eliminate the original Doppler image of the blood vessel B when the blood vessel of other tissues in the sample is scanned by the device. Appeared in the background Doppler.
  • the present invention also discloses a method of blood flow measurement of a blood vessel comprising the following steps:
  • the sample arm module includes: the sample arm module includes a scanning unit and a rotatable optical path translating device; Obtaining the probe light and the reference light through the spectroscopic module; the chief ray of the probe light is on a rotation axis of the scanning unit;
  • S104 Calculate a blood flow rate of the blood vessel according to the first phase shift signal and the second phase shift signal.
  • the illuminating light source 100 and the spectroscopic module need to be sequentially arranged according to FIG. 200.
  • the light emitted by the illuminating light source 100 passes through the beam splitting module 200 and is split into two beams: reference light and probe light. Wherein the reference light is transmitted to the reference arm module 300, and the probe light is transmitted to the sample arm module 500.
  • the reference arm module 300 reflects the received reference light back to the beam splitting module 200; after the probe light passes through the sample arm module 500, the eye 800 scans the blood vessel, and then carries the information of the blood vessel, and returns to the fundus in the eye 800 to return to the eyeball.
  • the splitting module 200 detects that the returned probe light carrying the blood vessel information interferes with the reference light at the beam splitting module 200 to generate interference light; the detecting module 600 receives the interference light, and then transmits the interference light to the control system 700, and the control system A 700 phase treatment obtains a phase shift signal of the scanned blood vessel.
  • the sample arm module 500 module includes at least a scanning unit 501 and an optical path translating device 502.
  • the optical path translating device 502 can rotate.
  • the optical path translating device 502 can be driven to rotate by a motor or can be driven to rotate by other mechanical structures.
  • the chief ray of the probe light is on the rotation axis of the scanning unit 501, the principal ray 50 of the probe light is always locked at the scanning unit 501 regardless of whether the optical path translating device 502 is in the first position or is rotated by 180° in the second position. Rotating on the shaft, so that the single blood vessel is scanned by the device, and the high-frequency background Doppler in Fig. 4 will not appear in the original Doppler image obtained by scanning, which reduces the processing of high-frequency background Doppler. Extra work and errors.
  • the optical path translating device 502 is first placed in the first position.
  • the light emitted by the light source 100 is split by the spectroscopic module 200 to obtain the probe light and the reference light.
  • the probe light is collimated by the collimating mirror 400, its chief ray is on the rotating axis of the scanning unit 501.
  • the probe light is reflected by the scanning unit 501 to the optical path translating device 502.
  • the detected light is transmitted through the relay lens 506, then reflected by the dichroic mirror 503 to the ophthalmoscope 504, and finally transmitted through the ophthalmoscope 504.
  • the blood vessel B After entering the eye 800, the blood vessel B is scanned in the first direction S1 (see FIG. 13) and in the Y direction, and the information carrying the blood vessel B is returned to the beam splitting module 200 via the original path.
  • the probe light carrying the blood vessel B information and the reference light returned from the reference arm module 300 interfere in the beam splitting module 200 to obtain the first interference light, and after being processed by the control system 700, the blood vessel B is obtained.
  • One phase shift signal ⁇ a may be omitted.
  • step S103 referring to FIG. 8, FIG. 10 and FIG. 12, after the optical path translating device 502 is rotated by 180°, it is in the second position.
  • the light emitted by the light source 100 is split by the spectroscopic module 200 to obtain the probe light and the reference light. Test light.
  • the chief ray 50 is on the rotating axis of the scanning unit 501, and the detecting light is reflected by the scanning unit 501 to the optical path translating device 502. After being emitted, the detecting light is transmitted through the relay lens 506.
  • the ophthalmoscope 504 And then reflected by the dichroic mirror 503 to the ophthalmoscope 504, finally transmitted through the ophthalmoscope 504 and then enters the eye 800, in the second direction S2 (see FIG. 13) and scans the blood vessel B in the Y direction, carrying the information of the blood vessel B,
  • the original path returns to the spectroscopic module 200.
  • the probe light carrying the blood vessel B information and the reference light returned from the reference arm module 300 interfere in the beam splitting module 200 to obtain the second interference light, and after being processed by the control system 700, the blood vessel B is obtained.
  • the two phase shift signal ⁇ b Similarly, in order to optimize the device, as previously described, the collimating mirror 400, the relay lens 506, the dichroic mirror 503, and the ophthalmoscope 504 can all be omitted.
  • S104 Calculate a blood flow rate of the blood vessel to be tested according to the first phase shift signal and the second phase shift signal;
  • the first phase shift signal ⁇ a measured by the probe light at the first position of the optical path translating device 502 and the second phase shift signal ⁇ b measured by the optical path translating device 502 at the second position are Using the formula (1), the flow rate of the blood vessel B can be obtained.
  • the flow rate at any time in the blood vessel B is defined as V(y, z, t):
  • V(y,z,t) v A (y,z)P(t) (2)
  • the control system obtains the average flow of blood in blood vessel B by integrating space and time. for:
  • T is the pulsation cycle of blood flow and P(t) is the blood flow pulsation function in the blood vessel.
  • the blood flow rate of the blood vessel B to be measured in the retina of the eye can be calculated. It should be emphasized that the formula (1) to formula (3) find the blood flow of any single blood vessel in the retina of the eye.
  • step S103 and before S104 it is also necessary to perform correction on the second phase shift signal ⁇ b, which is specifically described below.
  • the first phase shift signal ⁇ a and the second phase shift signal ⁇ b are not coincident at the acquisition time point. Since the blood flow in the blood vessel B is pulsating, the blood flow rate at different times is not As such, it is therefore necessary to utilize control system 700 to modify the second phase shift signal ⁇ b.
  • the correction process includes the following steps:
  • the probe light alternately scans the blood vessel B in the first direction S1 direction and the second direction S2 direction for a predetermined time, such as 2 seconds, when the optical path translating device 502 is in the first position and the second position, respectively.
  • a time-dependent phase shift signal profile as shown in FIG. 16 is obtained.
  • the control system 700 collects a series of first phase shift signals ⁇ a at different time points in the first S1 direction; the white frame is the optical path translating device 502. In the two positions, the control system 700 measures a series of second phase shift signals ⁇ b at different time points in the second direction S2 direction.
  • the second phase shift signal ⁇ b is corrected by interpolation calculation.
  • ⁇ a1 is the first phase shift signal obtained by scanning at time ta
  • ⁇ b2 is the second phase shift signal obtained by scanning at time tb.
  • the method further includes the step of measuring an angle between an axial direction of the blood vessel and an X direction.
  • the probe light illuminates the blood vessel B of the eye 800 along the first direction S1 and scans in the Y direction; when the optical path translating device 502 is rotated 180° in the second position The probe light illuminates the blood vessel B of the eye 800 along the second direction S2 and scans in the Y direction; the first direction S1 and the second direction S2 form an XZ plane, and the X direction is parallel to the X axis of the XZ plane. Therefore, as long as the spatial distribution of the blood vessel B is known, the angle ⁇ can be obtained.
  • the present invention also discloses a method of measuring blood flow in all blood vessels near the optic disc, comprising the steps of:
  • S201 setting a light source, a detecting module, a beam splitting module, a reference arm module, a sample arm module, and a control system according to the optical path;
  • the sample arm module includes a scanning unit and a rotatable optical path translating device;
  • the light source is split by the spectroscopic module to obtain the probe light and the reference light, and the chief ray of the probe light is on the rotation axis of the scanning unit;
  • the scanning trajectory of the detecting light when scanning in the second direction is the same as the scanning trajectory when scanning in the first direction; when the optical path translating device is turned from the first position to the second position, the angle of rotation is 180°.
  • step S201 refer to the description of step S101, and no further description is provided here.
  • step S202 when the optical path translating device 502 is in the first position as shown in FIGS. 7, 9, and 11, the control system 700 controls the detection light to perform a circular scan on the circumference C (see FIG. 14) around the optic disc region.
  • Fig. 15 describes how such a circular scan is realized: the scanning unit 501 controls the point S at which the detection light falls on the circumference (corresponding to the circumference C in Fig. 14), and if the scanning unit 501 remains stationary, the optical path shifting means 502 When the 360° rotation is performed, the probe light will move in a circular motion around the tapered surface Co.
  • the control system 700 controls the optical path translating device 502 to rotate in synchronization with the scanning unit 501.
  • the detecting light will circularly scan all the blood vessels near the optic disc in the direction of the space vector shown in the first direction S1 (see FIG. 13) where the solid arrow is incident (see FIG. 14).
  • a series of first phase shift signals of blood flow in all blood vessels near the optic disc can be obtained: ⁇ a1, ⁇ a2, ⁇ a3, ... ⁇ aN.
  • step S203 when the detection light circular scan returns to S point one week (see FIG. 15), the optical path translation device 502 quickly switches one phase ⁇ (ie, turns 180°), and at this time, the optical path translation device 502 is in the first Two positions, at which time the probe light will switch to the second direction S2 (see FIG. 13) incident along the dotted arrow, and similarly, as in step S202, the control system 700 controls the scanning unit 501 and the optical path translating device 502 to rotate synchronously, detecting light.
  • the control system 700 controls the scanning unit 501 and the optical path translating device 502 to rotate synchronously, detecting light.
  • a plurality of first phase shift signals ⁇ a1, ⁇ a2, ⁇ a3, ... ⁇ aN and a plurality of second phase shift signals ⁇ b1, ⁇ b2, ⁇ b3, ... ⁇ bN are paired.
  • the pairing referred to here means that ⁇ a1 and ⁇ b1 are paired, ⁇ a2 and ⁇ b2 are paired, and ⁇ a3 and ⁇ b3 are paired.
  • ⁇ aN and ⁇ bN are paired.
  • the two ring scan intervals need to be set to a certain interval period (for example, 2 seconds).
  • the reference fundus map can determine the angle ⁇ between the axial VB and the X direction of all blood vessels in the optic disc.
  • An angle ⁇ between the axial VB of the scanned blood vessel B and the X direction is exemplarily illustrated in FIG.
  • the above fundus map can be obtained in various ways, such as by three-dimensional OCT, fundus black and white or color photography, line scan imaging, and the like. In this way, the angle ⁇ between the axial direction of all the blood vessels in the vicinity of the optic disc and the X direction can be determined.
  • the blood flow velocity values V1, V2, V3 are obtained, and since the blood flow velocity has directionality, it is necessary to take absolute values of these blood flow velocity values.
  • the blood flow rate values V1, V2, V3, ..., VN after taking the absolute value are substituted into the formula (2) and the formula (3), and the total blood flow rate of the blood vessels near the optic disc of the eye 800 can be obtained.
  • the detecting light makes two circular scans on a circumference C around the optic disc region
  • the scanning trajectory of the detecting light is the same circumference
  • the detecting light circularly scans each blood vessel in the vicinity of the optical disc in the first direction S1; when the optical path translating device 502 is in the second position, the detecting light is in the second direction S2
  • the ring scans each blood vessel near the optic disc.
  • the direction in which the first direction S1 and the second direction S2 are maintained while detecting the circular scanning of the blood vessel remains unchanged, that is, the angle ⁇ formed by the first direction S1 and the second direction S2 during the entire circular scanning process remains unchanged.
  • the apparatus and method for measuring blood flow since the principal ray 50 of the probe light is always on the rotation axis 501B of the scanning unit 501 shown in FIG. 1 when the optical path is set, It is avoided that the high-frequency background Doppler of the original Doppler image shown in FIG. 4 is processed, and the Doppler image not including the high-frequency background Doppler shown in FIG. 5 can be directly obtained, thereby reducing the processing. Additional work and errors caused by Doppler on high frequency background.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Engineering & Computer Science (AREA)
  • General Health & Medical Sciences (AREA)
  • Medical Informatics (AREA)
  • Biophysics (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Pathology (AREA)
  • General Physics & Mathematics (AREA)
  • Ophthalmology & Optometry (AREA)
  • Hematology (AREA)
  • Physiology (AREA)
  • Signal Processing (AREA)
  • Vascular Medicine (AREA)
  • Psychiatry (AREA)
  • Computer Vision & Pattern Recognition (AREA)
  • Cardiology (AREA)
  • Artificial Intelligence (AREA)
  • Optics & Photonics (AREA)
  • Chemical & Material Sciences (AREA)
  • Analytical Chemistry (AREA)
  • Biochemistry (AREA)
  • Immunology (AREA)
  • Eye Examination Apparatus (AREA)
  • Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)

Abstract

本发明公布了一种测量血管血液流量的设备和方法，包括：在光路上设置光源、分光模块、参考臂模块、样品臂模块、探测模块和控制系统；样品臂模块主要包括扫描单元和可旋转的光路平移装置；光源经分光模块后得到探测光，其主光线一直处于扫描单元的转动轴上；探测光经扫描单元扫描反射至光路平移装置，在光路平移装置分别处于第一位置及第二位置时，分别扫描眼底血管，得到被测血管的第一位相信号和第二位相信号，最后根据公式求得视盘附近单根血管的血液流速和流量，以及所有血管的血液流量。本设备和方法，避免了采集到的血管的原始多普勒图像出现的高频背景多普勒，省去了去除高频背景多普勒带来的额外工作和误差。

Description

一种测量血管血液流量的设备及方法 技术领域
本发明涉及光电子技术领域，尤其涉及一种测量血管血液流量的设备及方法。
背景技术
许多视网膜疾病与非正常的眼部血液流量有关，例如糖尿病引起的视网膜病变、视网膜静脉阻塞以及与年纪有关的黄斑退化。在青光眼病研究中，视网膜供血不足被认为是青光眼病发生和发展的一个可能原因。因此，对视网膜血液流量进行测量对于视网膜疾病的临床诊断、治疗和研究具有重要意义。
光学相干层析成像技术(Optical Coherence Tomography，OCT)是一种非侵入的探测技术，它被广泛应用于生物组织的活体截面结构成像。通过测量与深度有关的散射光，OCT可以提供高分辨，高灵敏度的组织结构。同时，OCT技术也可以探测散射光的多普勒频移，以获得流体和样品的运动信息，因而适合用于测量视网膜内的血液流量。遗憾的是，单光束多普勒OCT探测到的频移只与探测光束方向的血液流速有关，而垂直于探测光方向的血流信息不能直接从多普勒频移中得到，无法得到血管内的实际流速。
为了解决上述问题，人们发展了一系列技术来获得血管中的实际流速：
(1)、通过对视网膜进行三维扫描，获得视网膜中血管在空间中的走向，从而确定出探测光的多普勒角度，再利用多普勒角度，计算出实际的流速，但由于视网膜的血管和探测光束接近垂直，这种方法准确度较低。另外，通过连续扫描两个平面或圆环，定出待测血管的空间矢量，进而计算出多普勒角度，得到实际流速。这种方法的测量结果会受到眼动的影响，而且它只能对视盘周围的血管进行测量，无法测量视网膜其他区域的血流情况。
(2)、利用多束、多角度探测光扫描样品中的同一点，以便获得血管中真实的流体速度。OCT探测光被一块玻璃平板分成两束，这两束光会聚在流体中，形成双光束，双角度照明方式，通过分析两束光探测到的多普勒频移，可以得到血管中的真实流体速度。这种方法的缺陷在于：由于两路光之间有时间上的延迟，对于频域OCT系统并不适用。另外，可利用由偏振光分束的双光 束OCT系统，测量视网膜血管中的流速和流量，或利用一个DOVE棱镜与OCT扫描机构同步，实现了双光束在视网膜上的环形扫描。但是这些双光束系统由两个迈克耳逊干涉仪构成，结构复杂、调整困难，而且基于探测光安全方面的考虑，每一路探测光的功率要大大低于单光束系统，这降低了双光束OCT系统的灵敏度，从而加大了系统的位相噪声。
为测量视盘内单根血管和视盘内所有血管的流速和流量，则必须要利用眼科检测设备对眼底血管进行扫描，具体请参考图3中对视盘内其中一根血管的线扫描视频截图和图10及图11中对视盘内所有血管的环形扫描示意图。在图3中，黑色的粗线表示探测光扫描眼底血管B的扫描方向，该扫描方向相当于图9中的Y方向.。经过探测光扫描后，得到原始眼底多普勒图像，如图4所示。在图4中，出现了并不需要的背景多普勒，即明暗相间的低频背景多普勒和明显的竖线状的高频背景多普勒。同样的，在进行如图10、图11所示的对视盘内所有血管进行环形扫描的过程中，得到的原始多普勒图像(未图示)中也会出现如图4中所出现的明暗相间的低频背景多普勒和明显的竖线状的高频背景多普勒。经过分析，产生背景多普勒的原因有两点：第一、探测光的主光线没有入射到扫描单元的转动轴上。当扫描单元为X-Y振镜时，即认为Y振镜的转动轴为扫描单元的转动轴。参考图1，当扫描单元为X-Y振镜时，若探测光的主光线落入X-Y振镜501A的转动轴501B上，即认为探测光的主光线处于扫描单元的转动轴上。随着X-Y振镜501A的摆动，探测光的入射方向e与探测光在透镜1成像面d上的扫描方向相互垂直，在此情况下不会引入额外的背景多普勒。参考图2，若探测光的主光线不是落入X-Y振镜501A的转动轴501B上，随着X-Y振镜的摆动，探测光的入射方向e与探测光在透镜1成像面d上的扫描方向不再垂直。假若入射光偏离振镜轴1，振镜扫描角速度为w，透镜1焦距为f，则由此带来频移为
Figure PCTCN2016075790-appb-000001
(λ0为探测光的中心波长)。该高频背景多普勒在去除时需要在纵向一条线一条线的去除，且极易找错相应的背景。而背景找错将直接影响测量的准确性；第二，眼睛在检测过程中，眼球会不自主的微微转动，因此探测光不可能一直以同一角度照射眼球的同一位置，这就带来了如图4所示的明暗相间的呈区域状的低频背景多普 勒。
对于低频背景多普勒来说，可以用众所周知的去多普勒背景的方法轻易去除。而对于高频背景多普勒来说，由于其相邻的每条线之间的背景都不同，且是毫无规律的，所以需要每条线逐一寻找其背景多普勒。这不仅使去背景的过程更繁琐，还难以保证去背景的准确率。而背景找错将直接影响血管血液流速测量的准确性。因此，需要通过光路的调整将高频背景多普勒去除。
发明内容
针对上述现有技术的不足，本发明旨在提供一种既能消除高频背景多普勒、又能精确测量视盘内血管血液流量的设备和方法。
本发明公布的测量血管血液流量的设备的技术方案如下：
一种测量血管血液流量的设备，包括：光源、分光模块、参考臂模块、样品臂模块、探测模块和控制系统；所述光源经所述分光模块分光后形成参考光和探测光，所述参考光入射至所述参考臂模块，所述探测光入射至所述样品臂模块；所述样品臂模块包括扫描单元和可转动的光路平移装置，所述探测光的主光线处于扫描单元的转动轴上；
当所述光路平移装置处于第一位置时，探测光经所述扫描单元反射后进入所述光路平移装置，经所述光路平移装置后，以第一方向扫描血管并携带被扫描血管的信息，经所述样品臂模块返回，与从参考臂返回的参考光在所述分光模块处发生干涉生成第一干涉光；所述第一干涉光被所述探测模块探测到，经所述控制系统处理后得到所述血管的第一位相移动信号；
当所述光路平移装置处于第二位置时，探测光经所述扫描单元反射后进入所述光路平移装置，经所述光路平移装置后，以第二方向扫描所述血管并携带被扫描血管的信息，经所述样品臂模块返回，与从参考臂返回的参考光在所述分光模块处发生干涉生成第二干涉光；所述第二干涉光被所述探测模块探测到，经所述控制系统处理后得到所述血管的第二位相移动信号；
其中，入射至所述光路平移装置的探测光的主光线和所述光路平移装置的旋转轴重合。
进一步地，所述光路平移装置由所述第一位置转到所述第二位置时，转过 的角度为180°。
进一步地，所述样品臂模块还包括准直镜、中继透镜、二向色镜和眼底镜；所述准直镜用于准直来自所述分光模块分光后得到的所述探测光；所述中继透镜将来自所述光路平移装置的探测光汇聚于所述二向色镜；所述二向色镜将来自所述中继透镜的探测光反射至所述眼底镜，经眼底镜汇聚后扫描血管。
进一步地，还包括预览模块，其包括照明光源、第一透镜和摄像器；所述照明光源发出的光照射眼睛，在眼底内发生反射，所述反射光依次经所述眼底镜、所述二向色镜和所述第一透镜透射后，由所述摄像器接收并由计算机显示。
进一步地，所述扫描单元为X-Y振镜，所述扫描单元的转动轴为所述X-Y振镜的转动轴。
进一步地，所述光路平移装置至少为其中两端被斜切的平板玻璃、两平行布置的反射镜或棱镜中的一种。
本发明还公布了一种测量单根血管血液流量的方法，包括如下步骤：
依照光路设置光源、探测模块、分光模块、参考臂模块、样品臂模块和控制系统；所述样品臂模块包括扫描单元和可转动的光路平移装置；所述光源经分光得到的探测光的主光线处于扫描单元的转动轴上；
当所述光路平移装置处于第一位置时，探测光经扫描单元反射后进入所述光路平移装置，经其后以第一方向扫描血管并生成第一位相移动信号；
当所述光路平移装置处于第二位置时，探测光经扫描单元反射后进入所述光路平移装置，经其后以第二方向扫描血管并生成第二位相移动信号；
根据所述第一位相移动信号及第二位相移动信号计算血管的血液流量。
进一步地，在所述探测光以第二方向扫描血管并生成第二位相移动信号后，还包括对所述第二位相移动信号进行修正，具体步骤为：
获得所述第一位相移动信号和所述第二位相移动信号分别随时间变化的关系；
利用插值计算对所述第二位相移动信号进行修正。
进一步地，在根据所述第一位相移动信号及所述第二位相移动信号计算所测血管的血液流量之前，还包括：
测量所述血管的轴向与X方向的夹角；
其中，所述光路平移装置处于第一位置时探测光以第一方向扫描所述血管；所述光路平移装置处于第二位置时探测光以第二方向扫描所述血管；所述第一方向和所述第二方向构成X-Z平面。
本发明还公布了一种测量视盘附近总的血液流量的方法，包括如下步骤：
依照光路设置光源、探测模块、分光模块、参考臂模块、样品臂模块和控制系统；所述样品臂模块包括扫描单元和可转动的光路平移装置；所述光源经所述分光模块分光得到探测光，所述探测光的主光线处于所述扫描单元的转动轴上；
当所述光路平移装置处于第一位置时，探测光由扫描单元反射至所述光路平移装置，经控制系统控制所述扫描单元和所述光路平移装置同步转动后，以第一方向环形扫描视盘附近所有血管，得到与所有血管一一对应的若干第一位相移动信号；
在所述光路平移装置处于第二位置时，探测光由扫描单元反射至所述光路平移装置，经控制系统控制所述扫描单元和所述光路平移装置同步转动后，以第二方向环形扫描视盘附近所有血管，得到与所有血管一一对应的若干经修正后的第二位相移动信号；
将所述若干第一位相移动信号和所述若干第二位相移动信号一一配对计算，得到所述若干单根血管的血液流速；
将所述若干单根血管的血液流速取绝对值，经计算得到视盘附近所有血管的血流流量；
其中，探测光以第二方向扫描时的扫描轨迹和以第一方向扫描时的扫描轨迹相同。
本发明所公布的设备和方法的有益技术效果：
第一、测量视盘附近任一单根血管血液流速和流量时，探测光的主光线处在扫描单元的转动轴上，探测光经过扫描单元反射至光路平移装置。当光路平移装置处于第一位置时，探测光经过光路平移装置发生后，以第一方向S1沿着Y方向扫描血管B，系统获得血管的第一位相移动信号；当光路平移装置处于第二位置时，探测光以第二方向S2沿着Y方向扫描血管B，系统获得血管B的第二位相移动信号，系统对第一位相移动信号和第二位相移动信号进 行处理，经计算得到血管B内的血液流速，并进而求得血液流量。由于探测光的主光线处于扫描单元的转动轴上，探测光经扫描单元反射后进入光路平移装置，然后才扫描眼底血管，因此，不管光路平移装置在第一位置或者在第二位置，探测光的主光线在扫描单元扫描血管时一直锁定在扫描单元的转动轴上，有效的避免了图4中所示的原始眼底多普勒图中出现的高频背景多普勒，从而省去了去除高频背景多普勒带来的额外工作和误差。
第二，在测量视盘附近所有血管血液流量时，同样让探测光的主光线处在扫描单元的转动轴上，探测光也是经过扫描单元反射至光路平移装置，经控制系统控制扫描单元和光路平移装置同步转动，探测光分别以第一方向S1和第二方向S2环形扫描视盘附近所有血管。同样的，由于探测光的主光线也一直位于扫描单元的转动轴上，因此，在环形扫描视盘附近所有血管得到的原始眼底多普勒图像中也不会出现如图4所示的高频背景多普勒，从而省去了去除高频背景所带来的额外工作和误差。
附图说明
图1为探测光的主光线落在扫描单元的转动轴的示意图；
图2为探测光的主光线偏离扫描单元的转动轴的示意图；
图3为探测光扫描眼底的其中一条血管B的视频截图；
图4为采集到的血管B的原始多普勒图像，该图中有低频背景多普勒和高频背景多普勒；
图5为图4中高频背景多普勒经过处理后的图像；
图6为本发明的实施例提供的血液流量测量设备的结构示意图；
图7为图6中的样品臂模块500的光路平移装置502的第一种结构处于第一位置时的光路详图；
图8为图6中的样品臂模块500的光路平移装置502的第一种结构处于第二位置时的光路详图；和图7相比，光路平移装置502转过的角度为180°；
图9为图6中的样品臂模块500的光路平移装置502的第二种结构处于第一位置时的光路详图；
图10为图6中的样品臂模块500的光路平移装置502的第二种结构处于 第二位置时的光路详图；和图9相比，光路平移装置502转过的角度为180°。
图11为图6中的样品臂模块500的光路平移装置502的第三种结构处于第一位置时的光路详图；
图12为图6中的样品臂模块500的光路平移装置502的第三种结构处于第二位置时的光路详图；和图11相比，光路平移装置502转过的角度为180°。
图13为探测光在光路平移装置502处于第一位置和第二位置时探测光射入眼睛视网膜上的形成的夹角α及与血管B构成的几何空间示意图；
图14为探测光环形扫描视盘内所有血管的扫描轨迹图；
图15为探测光分别以第一方向和第二方向以同样的轨迹环形扫描视盘内所有血管的示意图；
图16为第一位相移动信号及第二位相移动信号随时间的变化关系图；
图17为消除高频背景多普勒的测量视盘附近单根血管血液流量的流程图；
图18为消除高频背景多普勒的测量视盘附近所有血管血液流量的方法。
图中，各序号及对应的名称分别为：
1、透镜；
100、光源；
200、分光模块；
300、参考臂模块；
401、参考镜；
400、准直镜；
50、探测光主光线；
500、样品臂模块；
501、扫描单元；
501A、X-Y振镜；
501B、转动轴；
502、光路平移装置；
502C、光路平移装置502的旋转轴；
502A、光路平移装置502的第一种结构的入射面；
502B、光路平移装置502的第一种结构的出射面；
502D、光路平移装置502的第二种结构的第一反射镜；
502E、光路平移装置502的第二种结构的第二反射镜；
502F、光路平移装置502的第三种结构的第一反射面；
502G、光路平移装置502的第三种结构的第二反射面；
503、二向色镜；
504、眼底镜；
505、预览模块；
505A、第一透镜；
505B、摄像器；
600、探测模块；
506、中继透镜；
700、控制系统；
800、眼睛；
具体实施方式
为了使本发明所要解决的技术问题、技术方案及有益效果更加清楚明白，以下结合附图及实施例，对本发明进行进一步详细说明。应当理解，此处所描述的具体实施例仅用以解释本发明，并不用于限定本发明。
本发明提供一种测量血管血液流量的设备，用于测量人的组织器官的血液流量，这里的组织器官包括但不限于人或者动物的眼睛。虽然在本专利申请文件的附图中，所选择的测量对象为眼睛的血管，但是，就该设备及方法而言，同样适用于测量人或者动物除了眼睛以外的其他组织器官的血液流量，只不过需要技术实施例的提到的眼睛换成其它组织器官，以及需要将说明书附图中涉及到眼睛示意图换成其他组织器官的示意图。同样地，对于在下文中提到的样品，包括但不限于人或者动物的眼睛，也可以将其替换成人或动物的其他组织器官。
参考图6，所述能消除高频背景多普勒的测量血液流量设备包括光源100、分光模块200、参考臂模块300、样品臂模块500、探测模块600及控制系统 700。光源100发出的光传递至分光模块200，分光模块200将接收到的光分成参考光和探测光，其中参考光传递给参考臂模块300，探测光传递给样品臂模块500。参考臂模块300将接收到的参考光经反射后传回到分光模块200；探测光经过准直镜400准直后，经样品臂模块500后扫描眼睛800，经眼睛800内的组织散射后形成信号光并再次经准直镜400返回分光模块200，信号光与参考光在分光模块200处干涉后形成干涉光。探测模块600接收干涉光后，将干涉光的信号传输至控制系统700，控制系统700处理该信号，得到被扫描的眼睛的组织的位相移动信号。其中，参考臂模块300内置有参考镜301，分光模块200分光得到的参考光经参考镜301反射后返回到分光模块200内，在此和信号光发生干涉。具体地，参考镜301优先选择为平面反射镜。另外，此处所说的控制系统700，可以理解为计算机的处理模块。
参考图7-图12。在图7-图12中，样品臂模块500至少包括了扫描单元501和光路平移装置502，从分光模块200分光得到的探测光的主光线直接入射至扫描单元501的转动轴。当扫描单元优选为X-Y振镜时，扫描单元的转动轴即为图1中的X-Y振镜501A的转动轴501B。图7到图12中的扫描单元501在整个扫描过程中，探测光的主光线一直位于扫描单元501的转动轴501B(见图1，此时，扫描单元501优选为X-Y振镜501A)上。
继续参考图7至图12，图7至图12具体描述了光路平移装置502分别包括的三种实施例时样品臂模块500的具体的光路结构。需要说明的是，这三种实施例仅仅是示例性的，其目的在于使探测光的主光线50在射入光路平移装置502时和从光路平移装置502出射时发生平移。因此，凡是能实现上述目的的光路结构，均属于本发明的保护范围。
第1实施例：光路平移装置502为两端被斜切的玻璃平板。
请参考图7，在测量血管B的血液流速时，当光路平移装置502处于第一位置时，探测光主光线50入射至扫描单元501的转动轴上，经过扫描单元501反射至光路平移装置502，在光路平移装置502的入射面502A发生折射后，探测光经光路平移装置502的出射面502B再次折射，再次折射后的探测光以第一方向S1并沿Y方向扫描眼睛800的其中一根血管B(见图13)。完成扫描后，探测光携带血管B的信号，经眼底散射，原路返回至图6中的分光模 块200，并和从参考臂模块300返回的参考光在分光模块200处发生干涉形成第一干涉光，第一干涉光被探测模块600探测到，系统得到被扫描血管B的第一位相移动信号фa。需要说明的是，在图7中，从扫描单元501反射至光路平移装置502的入射面502A的探测光的主光线50和光路平移装置502的旋转轴502C重合。
请参考图8，当光路平移装置502转过180°，处于图8中的所示的第二位置时，探测光主光线50入射至扫描单元501的转动轴上，经过扫描单元501反射至光路平移装置502，在光路平移装置502的入射面502A产生折射，折射后的探测光经光路平移装置502的出射面502B再次产生折射，参考图9，探测光以第二方向S2并沿Y方向扫描血管B，携带血管B的第二信号，经眼底散射后，原路返回图6中的分光模块200，并和从参考臂模块300返回的参考光在分光模块200处发生干涉形成第二干涉光，第二干涉光被探测模块600探测到，得到被扫描血管的第二位相移动信号фb。需要说明的是，在图8中，从扫描单元501反射至光路平移装置502的出射面502B的探测光的主光线50和光路平移装置502的旋转轴502C重合。
第2实施例：光路平移装置502为平行分布的两反射镜。
参考图9和图10，和第一实施例不同的是，光路平移装置502为由两块平行布置的第一反射镜502D和第二反射镜502E组成。请参考图9，当光路平移装置502处于第一位置时，探测光主光线50入射至扫描单元501的转动轴上，经过扫描单元反射至光路平移装置502，经第一反射镜502D反射至第二反射镜502E，再由第二反射镜502E出射，探测光以第一方向S1并沿Y方向扫描眼睛800的其中一根血管B(见图13)。完成扫描后，探测光携带血管B的信号，经眼底反射，按原路返回至图6中的分光模块200，并和从参考臂模块300返回的参考光在分光模块200处发生干涉形成第一干涉光，第一干涉光被探测模块600探测到，系统得到被扫描血管B的第一位相移动信号фa。需要说明的是，在图9中，由扫描单元501反射至第一反射镜502D的探测光的主光线50和光路平移装置502的旋转轴502C重合。
请参考图10，当光路平移装置502处于第二位置时，此时，第一反射镜502D和第二反射镜502E作为一个整体沿着旋转轴502C转动180°。探测光主 光线50入射至扫描单元501的转动轴上，经过扫描单元501反射至光路平移装置502，经第二反射镜502E反射至第一反射镜502D，再由第一反射镜502D出射，探测光以第二方向S2并沿Y方向扫描眼睛800的其中一根血管B。完成扫描后，探测光携带血管B的信号，经眼底反射，按原路返回至图6中的分光模块200，并和从参考臂模块300返回的参考光在分光模块200处发生干涉形成第二干涉光，第二干涉光被探测模块600探测到，系统得到被扫描血管B的第二位相移动信号фb。需要说明的是，在图10中，由扫描单元501反射至第一反射镜502D的探测光的主光线50和光路平移装置502的旋转轴502C重合。
第3实施例：光路平移装置502为棱镜。
参考图11，当光路平移装置502处于第一位置时，探测光主光线50入射至扫描单元501的转动轴上，经过扫描单元501反射至光路平移装置502。此时，光路平移装置502为棱镜。探测光经棱镜的第一反射面502F反射至第二反射面502G，再由第二反射面502G出射，探测光以第一方向S1并沿Y方向扫描眼睛800的其中一根血管B。完成扫描后，探测光携带血管B的信号，经眼底反射，按原路返回至图6中的分光模块200，和从参考臂模块300返回的参考光在分光模块200处发生干涉形成第一干涉光，第一干涉光被探测模块600探测到，得到被扫描血管B的第一位相移动信号фa。需要说明的是，在图11中，由扫描单元501反射至第一反射面502F的探测光的主光线50和旋转轴502C重合。
参考图12，当光路平移装置502处于第二位置时，即棱镜沿着旋转轴502C转动180°后，探测光主光线50入射至扫描单元501的转动轴上，经过扫描单元501反射至光路平移装置502。探测光经棱镜的第二反射面502G反射至第一反射面502F，再由第一反射面502F出射，探测光以第二方向S2并沿Y方向扫描眼睛800的其中一根血管B。完成扫描后，探测光携带血管B的信号，经眼底反射，按原路返回至图6中的分光模块200，并和从参考臂模块300返回的参考光在分光模块200处发生干涉形成第二干涉光，第二干涉光被探测模块600探测到，得到被扫描血管B的第二位相移动信号фb。需要说明的是，在图12中，由扫描单元501反射至第一反射面502F的探测光的主光线50和 旋转轴502C重合。
请继续参考图13，定义第一方向S1和第二S2方向构成的夹角为α，构成的平面为X-Z平面。当第一位相移动信号фa和第二位相移动信号фb确定后，根据公式：
Figure PCTCN2016075790-appb-000002
计算得到待测血管B的血液流速V。
在公式(1)中，λ0为探测光的中心波长，n为图13中血管B内的血液的率，τ为OCT系统两相邻光线扫描的时间间隔，β为血管B的血流方向VB与平面X-Z的夹角，它可以从视网膜的三维投影图上获得。例如，利用探测光在以第一方向S1射入血管B时沿X轴方向做三维扫描，在合成的眼底平面图中，血管B和X方向的夹角就是β角。当上述参数都确定后，根据公式(1)就能确定眼睛800的视网膜内的待测血管B的血液流速V。因此，根据公式(1)可以计算出眼睛800的视网膜内的任一单根血管在任一时刻的血液流速。
需要说明的是，在本发明的实施例中，根据血管B的走向及分布情况，通过扫描单元501的扫描配合，使探测光实现X方向扫描、Y方向扫描或斜线扫描等各种扫描方式，从而使探测光根据待测血管B的实际走向调整扫描方向。
进一步地，参考图7到图12，作为进一步改进，所述样品臂模块500还包括准直镜400、二向色镜503和眼底镜504和中继透镜506。准直镜400设置在分光模块200和扫描单元501之间，它负责对入射至扫描单元501的参考光进行准直。中继透镜506将来自光路平移装置502的探测光汇聚在二向色镜503上，二向色镜503则将来自中继透镜506的探测光反射至眼底镜504，然后再经眼底镜504透射后，入射至眼睛800。探测光经眼底反射后，携带有被扫描血管的信息，原路返回至图6中的分光模块200。
进一步地，参考图7到图12，本发明所述的设备还包括预览模块505。具体地，预览模块505包括照明光源(未图示)、第一透镜505A和摄像器505B。照明光源发出的光照射到眼睛800，并在眼睛800内发生散射，散射后的反射光经过眼底镜504透射后到达二向色镜503，经二向色镜503透射后，再通过 第一透镜505A透射后到达摄像器505B，反射光的信息由摄像器505B拍摄得到。摄像器505B拍摄的图像显示到控制系统700的显示屏上，以供操作人员了解所述眼睛800的相关信息，便于进一步的操作。
由于在本装置中，探测光的主光线一直处于扫描单元的转动轴上，探测光经过扫描单元501反射至射路发生装置502。即：光路平移装置502分别处于第一位置和第二位置时，探测光的主光线始终处于扫描单元501的转动轴上，也就是说，探测光的主光线不会因为光路平移装置502发生转动而偏离扫描单元501的转动轴501B，因此避免了图4中所出现的被测血管B中原始多普勒图像中出现的不必要的高频背景多普勒，直接得到了我们所需要的如图5所示的血管B的原始多普勒图像，以方便根据公式(1)求得被测血管B的血液流速。因此，该装置避免了由于无法正确去除高频背景多普勒带来的额外工作和误差。
需要说明的是，血管B为眼睛800的视盘中的其中一条，它仅仅是示例性的，当利用本设备扫描样品中的其他组织的血管时，也能消除血管B的原始多普勒图像中出现的背景多普勒。
参考图17，本发明还公布了一种血管血液流量测量的方法，包括如下步骤：
S101：依照光路设置光源、探测模块、分光模块、参考臂模块、样品臂模块和控制系统；所述样品臂模块包括：所述样品臂模块包括扫描单元和可转动的光路平移装置；所述光源经所述分光模块得到探测光和参考光；所述探测光的主光线处在扫描单元的转动轴上；
S102：当所述光路平移装置处于第一位置时，探测光经扫描单元反射后进入所述光路平移装置，以第一方向扫描血管并生成第一位相移动信号；
S103：当所述光路平移装置处于第二位置时，探测光经扫描单元反射后进入所述光路平移装置，以第二方向扫描血管并生成第二位相移动信号；
S104：根据所述第一位相移动信号及第二位相移动信号计算所述血管的血液流量。
下面对这步骤S101-S104展开具体描述。
对于步骤S101，首先需要按照图6依次设置好发光光源100，分光模块 200、参考臂模块300、样品臂模块500、探测模块600和控制系统700。发光光源100发出的光经过分光模块200后分为两束：参考光和探测光。其中参考光传递给参考臂模块300，探测光传递给样品臂模块500。参考臂模块300将接收到的参考光经反射后传回至分光模块200；探测光经样品臂模块500后入射眼睛800扫描血管，然后携带血管的信息，经眼睛800内的眼底散射后返回到分光模块200，返回的携带有血管信息的探测光与参考光在分光模块200处发生干涉，产生干涉光；探测模块600接收干涉光，后将干涉光传输至所述控制系统700，经控制系统700处理后得到被扫描的血管的位相移动信号。
请参考图7到图12，由于前面说过，样品臂模块500模块至少包括了扫描单元501和光路平移装置502。其中，光路平移装置502可以转动。具体地，光路平移装置502可以由电机驱动转动，也可以通过其他机械结构驱动其转动。当探测光的主光线处于扫描单元501的转动轴上时，不管光路平移装置502处于第一位置，或者经过转动180°处于第二位置，探测光的主光线50一直被锁定在扫描单元501的转动轴上，这样，利用本装置扫描单根血管，扫描得到的原始多普勒图像中将不会出现图4中的高频背景多普勒，减少了处理高频背景多普勒所带来的额外工作和误差。
对于步骤S102，具体请参考图7、图9和图11。首先使光路平移装置502处于第一位置。光源100发出光经过分光模块200分光得到探测光和参考光。探测光经过准直镜400准直后，其主光线处于扫描单元501的转动轴上。探测光经扫描单元501反射至光路平移装置502，经光路平移装置502出射后，探测光经中继透镜506透射后，再由二向色镜503反射至眼底镜504，最后经过眼底镜504透射后进入眼睛800，以第一方向S1(见图13)并沿Y方向扫描血管B，携带血管B的信息，经原路返回至分光模块200。参考图6，此时，携带血管B信息的探测光和从参考臂模块300返回的参考光在分光模块200中发生干涉，得到第一干涉光，经过控制系统700处理后，得到血管B的第一位相移动信号фa。当然，为了优化本装置，正如前面所说，准直镜400、中继透镜506、二向色镜503以及眼底镜504均可以省略。
对于步骤S103，请参考图8，图10和图12，光路平移装置502旋转180°后，处于第二位置。光源100发出的光经过分光模块200分光得到探测光和参 考光。探测光经过准直镜400准直后，主光线50处于扫描单元501的转动轴上，探测光经扫描单元501反射至光路平移装置502，经其出射后，探测光经中继透镜506透射后，再由二向色镜503反射至眼底镜504，最后经过眼底镜504透射后进入眼睛800，以第二方向S2(见图13)并沿Y方向扫描血管B，携带血管B的信息，经原路返回至分光模块200。参考图6，此时，携带血管B信息的探测光和从参考臂模块300返回的参考光在分光模块200中发生干涉，得到第二干涉光，经过控制系统700处理后，得到血管B的第二位相移动信号фb。同样地，为了优化本装置，正如前面所说，准直镜400、中继透镜506、二向色镜503以及眼底镜504均可以省略。
S104：根据所述第一位相移动信号及第二位相移动信号计算待测血管的血液流量；
具体地，在本发明实施例中，根据探测光在光路平移装置502处于第一位置测得的第一位相移动信号Фa及光路平移装置502处于第二位置测得的第二位相移动信号Фb，利用公式(1)，即可以得到所述血管B的流速。
考虑到血流的脉动，定义所述血管B中血液任一时刻流速为V(y，z，t)：
V(y，z，t)＝vA(y，z)P(t)         (2)
控制系统通过对空间及时间进行积分，获得血管B中血液的平均流量
Figure PCTCN2016075790-appb-000003
为：
Figure PCTCN2016075790-appb-000004
其中，T为血流的脉动周期，P(t)为血管中的血流脉动函数。
通过公式(1)到公式(3)，就能计算出眼睛视网膜内待测血管B的血液流量。需要强调的是，公式(1)到公式(3)求得的是眼睛视网膜内的任一单根血管的血液流量。
需要说明的是，在步骤S103后和S104之前，还需要执行对第二位相移动信号Фb进行修正，具体阐述如下。
在本发明的实施例中，第一位相移动信号Фa与第二位相移动信号Фb的采集时间点并不一致，由于血管B中的血流有脉动，不同时刻的血液流速不 一样，因而需要利用控制系统700对第二位相移动信号Фb进行修正。该修正过程包括如下步骤：
首先，获得第一位相移动信号Фa及第二位相移动信号Фb随时间的变化关系。
请参阅图13和图16。图13中，探测光在光路平移装置502分别处于第一位置和第二位置时，分别对血管B以第一方向S1方向和第二方向S2方向交替扫描，并持续预定时间，如2秒钟，从而得到如图16所示的一个和时间有关的位相移动信号分布图。其中，黑色圆点为光路平移装置502处于第一位置时，控制系统700在第一S1方向的不同时间点采集到一系列第一位相移动信号Фa；白色的方框为光路平移装置502处于第二位置时，控制系统700在第二方向S2方向上不同时间点测量到的一系列第二位相移动信号Фb。
然后，利用插值计算对所述第二位相移动信号Фb进行修正。
具体地，参考图16，Фa1为ta时刻扫描获得的第一位相移动信号，Фb2为tb时刻扫描获得的第二位相移动信号。控制系统对第一位相移动信号进行插值计算，得到在tb时刻的第一位相移动信号值Фa2，然后把tb时刻的第一位相移动信号值Фa2与ta时刻的第一位相移动信号Фa1进行比较，得到k＝Фa1/Фa2。用k去乘以tb时刻的第二位相移动信号Фb2，如此即可得到ta时刻的第二位相移动信号Фb1，Фb1＝kФb2。
需要说明的是，在执行步骤S104之前，还包括执行如下步骤：测量所述血管的轴向与X方向的夹角。具体地，参考图13，光路平移装置502处于第一位置时，探测光沿着第一方向S1照射眼睛800的血管B并沿Y方向扫描；光路平移装置502经过旋转180°处于第二位置时，探测光沿着第二方向S2照射眼睛800的血管B并沿Y方向扫描；第一方向S1和第二方向S2构成X-Z平面，X方向平行于X-Z平面的X轴。因此，只要知道血管B的空间分布，就能求出夹角β。
参考图18，本发明还公布了一种测量视盘附近所有血管血液流量的方法，包括如下步骤：
S201：依照光路设置光源、探测模块、分光模块、参考臂模块、样品臂模块和控制系统；所述样品臂模块包括扫描单元和可转动的光路平移装置；所述 光源经所述分光模块分光得到探测光和参考光，所述探测光的主光线处于所述扫描单元的转动轴上；
S202：当所述光路平移装置处于第一位置时，探测光经扫描单元反射至所述光路平移装置，经计算机控制所述扫描单元和所述光路平移装置同步转动后以第一方向环形扫描视盘附近所有血管，得到与所有血管一一对应的若干第一位相移动信号；
S203：在所述光路平移装置处于第二位置时，探测光经扫描单元反射至所述光路平移装置，经计算机控制所述扫描单元和所述光路平移装置同步转动后以第二方向环形扫描视盘附近所有血管，得到与所有血管一一对应的若干经修正后的第二位相移动信号；
S204：将所述若干第一位相移动信号和若干第二位相移动信号一一配对计算，得到所述若干单根血管的血液流速；
S205：将所述若干单根血管的血液流速取绝对值，经计算得到视盘附近所有血管的血流流量。
其中，探测光在第二方向扫描时的扫描轨迹和在第一方向扫描时的扫描轨迹相同；所述光路平移装置由第一位置转到第二位置时，转过的角度为180°。
下面对这5个步骤展开具体描述。
对于步骤S201，请参考步骤S101的说明，在此不再累述。
对于步骤S202，当光路平移装置502处于如图7、图9和图11所示的第一位置时，控制系统700控制探测光绕着视盘区域在一个圆周C(见图14)上作环形扫描。图15描述了如何实现这种环形扫描：由扫描单元501控制探测光落在圆周(相当于图14中的圆周C)上的S点，此时如果扫描单元501保持不动，光路平移装置502做360°转动，则探测光将绕着锥面Co作圆周运动。控制系统700控制光路平移装置502与扫描单元501同步转动，探测光将沿着实线箭头入射的第一方向S1(见图13)所示的空间矢量方向环形扫描视盘附近所有血管(见图14)，如此即可获得视盘附近所有血管内的血流的一系列第一位相移动信号：φa1、φa2、φa3...φaN。
对于步骤S203：当探测光环形扫描一周回到S点后(见图15)，光路平移装置502快速切换一个位相∏(即转过180°)，此时光路平移装置502处于第 二位置，这时探测光将切换到沿虚线箭头入射的第二方向S2(见图13)，同样的，和步骤S202一样，控制系统700控制扫描单元501和光路平移装置502同步转动，探测光沿着和光路平移装置502处于第一位置时扫描的相同圆周的轨迹，环形扫描视盘附近所有血管(见图14)，如此即可获得视盘附近所有血管内的血流的一系列第二位相移动信号φb1、φb2、φb3...φbN。需要说明的是，所述一系列第二位相移动信号φb1、φb2、φb3...φbN也要修正，其修正的方法和前面测视盘附近单根血管的方法相同。
对于步骤S204-S205：将若干第一位相移动信号：φa1、φa2、φa3...φaN和若干第二位相移动信号φb1、φb2、φb3...φbN配对。这里所说的配对，是指φa1和φb1配对，φa2和φb2配对，φa3和φb3配对.......φaN和φbN配对。为在短时间内测量视盘附近所有血管的血液流量，这两次环形扫描间隔需要设置一定的间隔周期(如2秒钟)。在探测光完成上述两次扫描后，参考眼底图可以确定视盘内所有血管的轴向VB与X方向的夹角β。图13中示例性的例举了其中的一条被扫描血管B的轴向VB与X方向的夹角β。具体地，上述眼底图可以以各种方式得到，如通过三维OCT、眼底黑白或彩色照相、线扫描成像等技术得到。通过这种方式，则视盘附近所有血管的轴向与X方向的夹角β可由此定出来。此时，利用公式(1)，求得若干单根血管的血液流速值V1，V2，V3.....VN，由于血液流速具有方向性，因此需要对这些血液流速值进行取绝对值，再将取绝对值后的各血液流速值V1，V2，V3.....VN代入公式(2)和公式(3)，即可获得眼睛800视盘附近血管的总血液流量。
需要再次说明的是，探测光绕着视盘区域在一个圆周C上作两次环形扫描时，光路平移装置502在处于第一位置和第二位置时，探测光的扫描轨迹为同一个圆周；所不同的是，光路平移装置502在处于第一位置时，探测光以第一方向S1环形扫描视盘附近的每一根血管；光路平移装置502在处于第二位置时，探测光以第二方向S2环形扫描视盘附近的每一根血管。第一方向S1和第二方向S2在探测光环形扫描血管时所保持的方向一直保持不变，即第一方向S1和第二方向S2在整个环形扫描过程中成构成的夹角α一直保持不变，这样利用公式(1)和(2)计算视盘附近若干单根血管血液流速更加准确，最后计算出的视盘附近所有血管的血液总的流量因此也更加准确。
综上所述，本发明所述的一种测量血液流量的设备和方法，由于在设置光路时，探测光的主光线50一直处在图1中所示的扫描单元501的转动轴501B上，避免了对得到图4所示的原始多普勒图像高频背景多普勒进行处理，可以直接得到图5中所示的不包含高频背景多普勒的多普勒图像，从而减少了处理高频背景多普勒所带来的额外工作和误差。
以上所述仅为本发明的较佳实施例而已，并不用以限制本发明，凡在本发明的精神和原则之内所作的任何修改、等同替换和改进等，均应包含在本发明的保护范围之内。

Claims (10)

  1. 一种测量血管血液流量的设备，其特征在于，包括：光源、分光模块、参考臂模块、样品臂模块、探测模块和控制系统；所述光源经所述分光模块分光后形成参考光和探测光，所述参考光入射至所述参考臂模块，所述探测光入射至所述样品臂模块；所述样品臂模块包括扫描单元和可转动的光路平移装置，所述探测光的主光线处于扫描单元的转动轴上；
    当所述光路平移装置处于第一位置时，探测光经所述扫描单元反射后进入所述光路平移装置，经所述光路平移装置后，以第一方向扫描血管并携带被扫描血管的信息，经所述样品臂模块返回，与从参考臂返回的参考光在所述分光模块处发生干涉生成第一干涉光；所述第一干涉光被所述探测模块探测到，经所述控制系统处理后得到所述血管的第一位相移动信号；
    当所述光路平移装置处于第二位置时，探测光经所述扫描单元反射后进入所述光路平移装置，经所述光路平移装置后，以第二方向扫描所述血管并携带被扫描血管的信息，经所述样品臂模块返回，与从参考臂返回的参考光在所述分光模块处发生干涉生成第二干涉光；所述第二干涉光被所述探测模块探测到，经所述控制系统处理后得到所述血管的第二位相移动信号；
    其中，入射至所述光路平移装置的探测光的主光线和所述光路平移装置的旋转轴重合。
  2. 如权利要求1所述的测量血管血液流量的设备，其特征在于，所述光路平移装置由所述第一位置转到所述第二位置时，转过的角度为180°。
  3. 如权利要求1或2所述的测量血管血液流量的设备，其特征在于：所述样品臂模块还包括准直镜、中继透镜、二向色镜和眼底镜；所述准直镜用于准直来自所述分光模块分光后得到的所述探测光；所述中继透镜将来自所述光路平移装置的探测光汇聚于所述二向色镜；所述二向色镜将来自所述中继透镜的探测光反射至所述眼底镜，经眼底镜汇聚后扫描血管。
  4. 如权利要求3所述的测量血管血液流量的设备，其特征在于：还包括预览模块，其包括照明光源、第一透镜和摄像器；所述照明光源发出的光照射眼睛，在眼底内发生反射，所述反射光依次经所述眼底镜、所述二向色镜和所述第一透镜透射后，由所述摄像器接收并由计算机显示。
  5. 如权利要求1或2所述的测量血管血液流量的设备，其特征在于：所述扫描单元为X-Y振镜，所述扫描单元的转动轴为所述X-Y振镜的转动轴。
  6. 如权利要求1或2中所述的测量血管血液流量的设备，其特征在于：所述光路平移装置至少为其中两端被斜切的平板玻璃、两平行布置的反射镜或棱镜中的一种。
  7. 一种测量单根血管血液流量的方法，其特征在于，包括如下步骤：
    依照光路设置光源、探测模块、分光模块、参考臂模块、样品臂模块和控制系统；所述样品臂模块包括扫描单元和可转动的光路平移装置；所述光源经分光得到的探测光的主光线处于扫描单元的转动轴上；
    当所述光路平移装置处于第一位置时，探测光经扫描单元反射后进入所述光路平移装置，经其后以第一方向扫描血管并生成第一位相移动信号；
    当所述光路平移装置处于第二位置时，探测光经扫描单元反射后进入所述光路平移装置，经其后以第二方向扫描血管并生成第二位相移动信号；
    根据所述第一位相移动信号及第二位相移动信号计算血管的血液流量。
  8. 如权利要求7所述的测量单根血管血液流量的方法，其特征在于：在所述探测光以第二方向扫描血管并生成第二位相移动信号后，还包括对所述第二位相移动信号进行修正，具体步骤为：
    获得所述第一位相移动信号和所述第二位相移动信号分别随时间变化的关系；
    利用插值计算对所述第二位相移动信号进行修正。
  9. 如权利要求7所述的测量单根血管血液流量的方法，其特征在于：在根据所述第一位相移动信号及所述第二位相移动信号计算所测血管的血液流量之前，还包括：
    测量所述血管的轴向与X方向的夹角；
    其中，所述光路平移装置处于第一位置时探测光以第一方向扫描所述血管；所述光路平移装置处于第二位置时探测光以第二方向扫描所述血管；所述第一方向和所述第二方向构成X-Z平面。
  10. 一种测量视盘附近总的血液流量的方法，其特征在于，包括如下步骤：
    依照光路设置光源、探测模块、分光模块、参考臂模块、样品臂模块和控制系统；所述样品臂模块包括扫描单元和可转动的光路平移装置；所述光源经所述分光模块分光得到探测光，所述探测光的主光线处于所述扫描单元的转动 轴上；
    当所述光路平移装置处于第一位置时，探测光由扫描单元反射至所述光路平移装置，经控制系统控制所述扫描单元和所述光路平移装置同步转动后，以第一方向环形扫描视盘附近所有血管，得到与所有血管一一对应的若干第一位相移动信号；
    在所述光路平移装置处于第二位置时，探测光由扫描单元反射至所述光路平移装置，经控制系统控制所述扫描单元和所述光路平移装置同步转动后，以第二方向环形扫描视盘附近所有血管，得到与所有血管一一对应的若干经修正后的第二位相移动信号；
    将所述若干第一位相移动信号和所述若干第二位相移动信号一一配对计算，得到所述若干单根血管的血液流速；
    将所述若干单根血管的血液流速取绝对值，经计算得到视盘附近所有血管的血流流量；
    其中，探测光以第二方向扫描时的扫描轨迹和以第一方向扫描时的扫描轨迹相同。
PCT/CN2016/075790 2015-05-27 2016-03-07 一种测量血管血液流量的设备及方法 Ceased WO2016188178A1 (zh)

Priority Applications (2)

Application Number Priority Date Filing Date Title
EP16799067.0A EP3305187A4 (en) 2015-05-27 2016-03-07 APPARATUS AND METHOD FOR MEASURING BLOOD FLOW IN A BLOOD VESSEL
US15/574,934 US10456033B2 (en) 2015-05-27 2016-03-07 Apparatus and method for measuring blood flow of vessels

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
CN2015102765642 2015-05-27
CN201510276564.2A CN104825148B (zh) 2015-05-27 2015-05-27 一种测量血管血液流量的设备及方法
CN201510276564.2 2015-05-27

Publications (2)

Publication Number Publication Date
WO2016188178A1 true WO2016188178A1 (zh) 2016-12-01
WO2016188178A8 WO2016188178A8 (zh) 2023-03-30

Family

ID=53803641

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/CN2016/075790 Ceased WO2016188178A1 (zh) 2015-05-27 2016-03-07 一种测量血管血液流量的设备及方法

Country Status (4)

Country Link
US (1) US10456033B2 (zh)
EP (1) EP3305187A4 (zh)
CN (1) CN104825148B (zh)
WO (1) WO2016188178A1 (zh)

Families Citing this family (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN104825148B (zh) * 2015-05-27 2017-11-14 深圳市斯尔顿科技有限公司 一种测量血管血液流量的设备及方法
CN105286779B (zh) * 2015-10-30 2017-06-30 温州医科大学 一种在体视网膜血流动力学的成像与绝对流速测量方法
CN105167766B (zh) * 2015-11-03 2018-06-08 深圳市斯尔顿科技有限公司 血液流量测量设备及血液流量测量方法
CN109124686A (zh) * 2018-09-11 2019-01-04 中山大学 一种血液流量测量设备及方法
CN109363627A (zh) * 2018-11-29 2019-02-22 中山大学 一种血液流速的测量装置及方法
JP7260426B2 (ja) * 2019-07-11 2023-04-18 株式会社トプコン 光コヒーレンストモグラフィ装置、その制御方法、光計測方法、プログラム、及び記憶媒体
CN111265183B (zh) * 2020-02-19 2022-05-27 淮阴工学院 基于光束平行扫描模式的视网膜血流测量装置
CN112022085B (zh) * 2020-09-16 2022-04-15 中山大学 一种视网膜内的血管流量的计算方法
CN112842286B (zh) * 2020-12-31 2022-08-05 温州医科大学 一种基于功能oct的无创血流粘滞度测量方法

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20080097185A1 (en) * 2006-10-18 2008-04-24 Cardiospectra, Inc. Hemoglobin contrast in ultrasound and optical coherence tomography for diagnosing diseased tissue, cancers, and the like
US20090270738A1 (en) * 2008-04-24 2009-10-29 Duke University Methods for single-pass volumetric bidirectional blood flow imaging Spectral Domain Optical Coherence Tomography using a modified hilbert transform
CN103002794A (zh) * 2010-02-08 2013-03-27 奥勒冈保健科学大学 用于超高灵敏光学微血管显影术之设备及方法
CN104159505A (zh) * 2014-05-14 2014-11-19 深圳市斯尔顿科技有限公司 血液流量测量装置及方法
CN104825148A (zh) * 2015-05-27 2015-08-12 深圳市斯尔顿科技有限公司 一种测量血管血液流量的设备及方法
CN204708834U (zh) * 2015-05-27 2015-10-21 深圳市斯尔顿科技有限公司 一种测量血管血液流量的设备

Family Cites Families (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20070291277A1 (en) 2006-06-20 2007-12-20 Everett Matthew J Spectral domain optical coherence tomography system
JP5721412B2 (ja) * 2010-12-02 2015-05-20 キヤノン株式会社 眼科装置、血流速算出方法およびプログラム
WO2012145882A1 (zh) * 2011-04-23 2012-11-01 深圳市斯尔顿科技有限公司 一种眼科oct系统和眼科oct成像方法
WO2014183123A1 (en) * 2013-05-10 2014-11-13 Oregon Health & Science University Oct vitrectomy probe
US9046339B2 (en) * 2013-09-30 2015-06-02 Carl Zeiss Meditec, Inc. Systems and methods for bidirectional functional optical coherence tomography
CN104168823B (zh) * 2014-02-28 2017-01-18 深圳市斯尔顿科技有限公司 一种血液流速的测量装置及方法
CN203885484U (zh) * 2014-06-03 2014-10-22 深圳市斯尔顿科技有限公司 用于旋转多普勒oct中提高血管采样频率的光学装置

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20080097185A1 (en) * 2006-10-18 2008-04-24 Cardiospectra, Inc. Hemoglobin contrast in ultrasound and optical coherence tomography for diagnosing diseased tissue, cancers, and the like
US20090270738A1 (en) * 2008-04-24 2009-10-29 Duke University Methods for single-pass volumetric bidirectional blood flow imaging Spectral Domain Optical Coherence Tomography using a modified hilbert transform
CN103002794A (zh) * 2010-02-08 2013-03-27 奥勒冈保健科学大学 用于超高灵敏光学微血管显影术之设备及方法
CN104159505A (zh) * 2014-05-14 2014-11-19 深圳市斯尔顿科技有限公司 血液流量测量装置及方法
CN104825148A (zh) * 2015-05-27 2015-08-12 深圳市斯尔顿科技有限公司 一种测量血管血液流量的设备及方法
CN204708834U (zh) * 2015-05-27 2015-10-21 深圳市斯尔顿科技有限公司 一种测量血管血液流量的设备

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See also references of EP3305187A4 *

Also Published As

Publication number Publication date
CN104825148A (zh) 2015-08-12
US20180160901A1 (en) 2018-06-14
US10456033B2 (en) 2019-10-29
CN104825148B (zh) 2017-11-14
EP3305187A1 (en) 2018-04-11
WO2016188178A8 (zh) 2023-03-30
EP3305187A4 (en) 2019-02-13

Similar Documents

Publication Publication Date Title
WO2016188178A1 (zh) 一种测量血管血液流量的设备及方法
CN106880335B (zh) 用于测量眼睛的生物识别变量以计算人工晶状体的装置
EP1894518B1 (en) Eye movement measuring apparatus
US9241627B2 (en) Method and analysis system for eye examinations
CN111671391B (zh) 一种光学相干断层扫描成像装置和成像方法
CN104159505B (zh) 血液流量测量装置及方法
CN101234015A (zh) 光图像计测装置
CN101268927A (zh) 光图像计测装置以及图像处理装置
CN105147241A (zh) 基于双空间载频技术拓展oct成像深度的方法与系统
CN109124686A (zh) 一种血液流量测量设备及方法
EP3539461B1 (en) Ophtalmologic apparatus
WO2015127661A1 (zh) 一种血液流速的测量装置及方法
CN111134614A (zh) 基于oct测量眼球血管中血流的绝对速度的方法及系统
CN110325101B (zh) 用于眼角膜的高分辨率地形图的方法和装置
JP6471593B2 (ja) Ｏｃｔ信号処理装置、およびｏｃｔ信号処理プログラム
JP6198448B2 (ja) 光断層画像撮影装置
JP6166645B2 (ja) 光断層画像撮影装置
JP6098079B2 (ja) 眼底断層像撮影装置
CN204708834U (zh) 一种测量血管血液流量的设备
CN213309629U (zh) 一种眼球成像装置以及眼球血液流速测量装置
CN109363627A (zh) 一种血液流速的测量装置及方法
JP6544071B2 (ja) 光コヒーレンストモグラフィ装置、および光コヒーレンストモグラフィ制御プログラム
US12376743B2 (en) Ophthalmic device
US10799116B2 (en) Device and method of measuring blood flow
EP3673788B1 (en) Ophthalmologic apparatus and method for controlling the same

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 16799067

Country of ref document: EP

Kind code of ref document: A1

WWE Wipo information: entry into national phase

Ref document number: 15574934

Country of ref document: US

NENP Non-entry into the national phase

Ref country code: DE