CN109124686A - A kind of blood flow measurement device and method - Google Patents
A kind of blood flow measurement device and method Download PDFInfo
- Publication number
- CN109124686A CN109124686A CN201811055051.9A CN201811055051A CN109124686A CN 109124686 A CN109124686 A CN 109124686A CN 201811055051 A CN201811055051 A CN 201811055051A CN 109124686 A CN109124686 A CN 109124686A
- Authority
- CN
- China
- Prior art keywords
- light
- module
- detection light
- detection
- blood flow
- 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.)
- Pending
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/06—Measuring blood flow
-
- 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
- A61B3/12—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
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/10—Eye inspection
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/48—Diagnostic techniques
- A61B8/488—Diagnostic techniques involving Doppler signals
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- General Health & Medical Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- Biophysics (AREA)
- Veterinary Medicine (AREA)
- Public Health (AREA)
- Physics & Mathematics (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Medical Informatics (AREA)
- Molecular Biology (AREA)
- Surgery (AREA)
- Radiology & Medical Imaging (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Ophthalmology & Optometry (AREA)
- Pathology (AREA)
- Hematology (AREA)
- Vascular Medicine (AREA)
- Eye Examination Apparatus (AREA)
- Investigating Or Analysing Materials By Optical Means (AREA)
Abstract
The invention discloses a kind of blood flow measurement device and method, the equipment includes light source module, spectral module, reference arm module, sample arm module and detecting module, the first lens, rotatable Wollaston prism, the second lens and delay coding module be ensure that when optical path is arranged simultaneously around the light path light axis rotation of detection light, so that detection light is broken down into two beam standalone probe light k by Wollaston prism1And k2When reaching eyeground, regardless of scanning element is line scanning or circular scanning, light k is detected1And k2With changeless angle α.A branch of detection photodegradation is parallel to each other by the present invention using Wollaston prism and delay coding module at two beams and two beams with optical path difference detect light, and recorded the frequency shift signal on two detection directions simultaneously with a detector, to realize single light source, single detector while acquire both direction blood flow doppler signal.
Description
Technical field
The present invention relates to photoelectron technical field more particularly to a kind of blood flow measurement device and method.
Background technique
Studies have shown that eyeground perfusion abnormality and diabetic retinopathy, glaucoma, retinal vein occlusion and year
A series of fundus oculi diseases such as age is macular degeneration related are closely related.At present retinal vessel related disease detection goldstandard be
Fluorescein angiographic (FA) and indocyanine angiography (ICGA) based on Fluorescencecontro agent.But this fluoroscopic visualization
Technology can only observe distribution and the flowing information of blood vessel, and the flow information of blood can not be obtained by calculation.Therefore, develop one
Kind technology, which measures clinical diagnosis, treatment and research for retinal disease to retinal blood flow quantity, has important meaning
Justice.
Optical Coherence Tomography Imaging Technology (Optical Coherence Tomography, OCT) is a kind of Noninvasive
Detection Techniques.OCT technology has been widely used in the living body cross section structure imaging of biological tissue.Pass through measurement and depth phase
The scattering light of pass, OCT can provide high-resolution, highly sensitive institutional framework.Meanwhile OCT technology can also detect scattering
The doppler shifted signal of light to obtain the motion information of fluid or sample, thus is particularly suited for surveying relative to other technologies
Measure intraretinal blood flow.Part Research Team uses Doppler's OCT technology and only can be complete with a branch of OCT detection light
The measurement of pairs of blood flow, but the method for this single beam also needs further to measure between detection light incident direction and blood vessel
Doppler's angle, and can not directly be obtained from Doppler shift information perpendicular to the blood flow information of detection light direction.Therefore
The measurement method of this single beam receives significant limitation.
In order to overcome the above problem of single beam, people, which have gradually focused on, realizes dual-beam with Doppler OCT
Method measures in blood flow.Its essence is the angles it is to be understood that between two detection light beams, and the detectable signal on different light beam
It to acquire simultaneously as far as possible, otherwise can be influenced measuring accuracy by eye movement.Dave in 2000 et al. is based on Doppler OCT and transports for the first time
A branch of detection photodegradation is realized into external pair at the dual-beam measurement method of two beam orthogonal polarisation states with Wollaston prism
Light velocity measurement fluid flow.But this method receives the blood flow doppler signal of two detection directions with two detectors respectively,
Increase equipment cost and system complexity.The program is suitable only for in-vitro measurements and is not used to eyeground measurement simultaneously.2007
A piece of glass plate is inserted at the half position of a branch of detection light beam by Pedersen et al., i.e. a semi-permeable glass of light beam
Plate, in addition half is without glass plate, and blood flow measures while realizing dual-beam in the method for being expected that by this delay coding
Amount.Although this method is fairly simple, and can be presented on the detectable signal on different directions in same figure simultaneously, actually
The frequency shift signal on single direction that this method obtains only has the 1/4 of resultant signal, greatly reduces the sensitivity of system, increases
The phase noT of system.Meanwhile when detection light arrival eyeground, two parts are by the folder between the light beam of different degrees of delay coding
Angle can be smaller, influences the convenience and operability of measurement.Wang Yimin in 2008 et al. around optic disk by continuously sweeping
Two different concentric circles of radius are retouched, the timesharing measurement for realizing dual-beam for the first time obtains eyeground blood flow total amount.But the party
Method causes to calculate excessively complicated there is still a need for the flow direction for calculating blood flow.Again since two continuous concentric circles are not to survey simultaneously
Amount, so accuracy is influenced vulnerable to eye movement.Blatter in 2013 et al. has built the OCT system based on Dove prism come real
Blood flow measurement while existing dual-beam, but this method has equally used the labyrinth of double detector, is not easy to promote.
The prior art has been realized equally also to be realized using the reflective mirror or glass parallel flat of tilted-putted rotation
The measurement of the timesharing blood flow of dual-beam, but it is similar with the scheme that Wang Yimin et al. is proposed, and which is also that timesharing is adopted
The signal for collecting two detection directions increases the degree of difficulty of calculating, and influences vulnerable to eye movement.
To sum up, it was found by the inventors of the present invention that in the technology of existing dual-beam Doppler OCT measurement blood flow or being
Two detection light beams are timesharing measurements, are easy to be influenced accuracy by eye movement；It is two detection light beams while measurement but utilizes
Two detectors receive the signal of two detection directions respectively, increase the complexity and cost of system；It is two detection light
Beam measures simultaneously and is detected simultaneously with the same detector signal of both direction, but the signal of each detection direction detection
Only the 1/4 of resultant signal, reduces system sensitivity, increases phase noT.Therefore, there are no a perfect technical solutions
It realizes that two detection light beams measure simultaneously and with the same detector while detecting the signal of both direction, and also ensures
The signal strength of both direction will not be weak.
Summary of the invention
Technical problem to be solved by the present invention lies in provide a kind of blood flow measurement device and method, can utilize
One detection light beam is resolved into two and is separated from each other and parallel detection light beam by Wollaston prism, then with delay coding
Technology one detector of the frequency shift signal on two detection directions is recorded simultaneously, to realize single light source, single
Detector acquires both direction blood flow doppler signal simultaneously.
To solve the above problems, one embodiment of the present of invention provides a kind of blood flow measurement equipment, comprising: light source die
Block, spectral module, reference arm module, sample arm module and detecting module；
The light source module is used for the spectral module emission detection light；
The spectral module, for the detection photodegradation to be detected light and the second detection light at the first of preset ratio,
And the first detection light and the second detection light are transmitted separately to the reference arm module and the sample arm module；
The reference arm module, for first detection road Guang Anyuan to be reflected back the spectral module, as reference
Light；
The sample arm module is used for first with rotatable Wollaston prism and postpones coding module for described second
Third detection light and the 4th detection light that photodegradation is parallel to each other at two beams and has optical path difference are detected, scanning element is then utilized
It controls the third detection light and the 4th detection light is scanned eyes, and will be detected respectively with the third after scanning
Light and the corresponding two beams signal light of the 4th detection light are by spectral module described in backtracking；
The spectral module is also used to respectively carry out two beam signal lights with the reference light interference and is formed by interference light
Control system is transferred to by the detecting module to be handled, and two position phase shifts letter corresponding with two beam signal lights is obtained
Number, and then the blood flow of eyes medium vessels is calculated.
Further, the sample arm module, including beam splitting module, scanning element, field mirror, dichroscope and eyeground
Mirror；
The beam splitting module, including optical axis and coaxial the first lens of the detection optical axis of light, rotatable Walla this
Pause prism and the second lens, further includes the delay coding module for being inserted into any beam in third detection light or the 4th detection light；
Scanning element, including the first scanning element and the second scanning element；Wherein, first scanning element is for receiving
The third detection light and the 4th detection light, and second scanning element is reflexed to, then by second scanning element
By the field mirror by reflected light back to the dichroscope, further by the dichroscope by reflected light back extremely
The ophthalmoscope, so that reflected light is converged to eyes by the ophthalmoscope.
Further, the sample arm module further includes driving the beam splitting module with the optical axis of the detection light for rotation
The driving device of shaft synchronous rotary, and the calculating equipment of the control system is loaded, the calculating equipment is also used to control
The rotation of the driving device and the scanning element in the sample arm module.
Further, the sample arm module, further includes previewing module, for visiting respectively with the third after obtaining scanning
It surveys light and the corresponding two beams signal light of the 4th detection light carries out preview；Specifically,
The previewing module includes imaging len and image pick-up device, and the ophthalmoscope, which converges to reflected light after eyes, to be occurred to dissipate
It penetrates, scattering light successively reaches the image pick-up device after the ophthalmoscope, the dichroscope and the imaging len, by described
Image pick-up device shoots fundus image.
Further, described to control the third detection light and the 4th detection light to eyes progress using scanning element
Scanning, specifically:
Third detection light and the 4th detection light are controlled using scanning element with identical scanning direction and identical
Scanning track, the blood vessels of eyes is carried out while being scanned；Alternatively,
Third detection light and the 4th detection light are controlled using scanning element with identical scanning direction and identical
Circular scanning track, to blood vessels all in optic disk carry out circular scanning.
Further, the calculation formula of the blood flow are as follows:
Wherein, F is the blood flow of blood vessel B, VBIt is respectively true velocity of the blood vessel B in X-Z plane and point speed with V
Degree, SBIt is respectively the cross-sectional area and area of section of blood vessel B with S, the section is intercepted for the sweep trace of detection light
Vascular cross-section, the sweep trace are the trajectory line that the detection light scans on eyeground；VBRelationship with V is
SBRelationship with S is SB=S × cos β, β are not equal to 90 ° of odd-multiple；
Component velocity of the blood vessel B in X-Z plane be
Wherein, λ0For the central wavelength for detecting light, n is the blood refractive index in blood vessel B, and τ is two adjacent light of OCT system
The time interval of line scanning, α are that the third detects light and the 4th detection light in the angle of inside of eye.
Further, the first collimation lens, the reference are provided between the spectral module and the reference arm module
A plane mirror is as reference mirror built in module；The second collimation is provided between the spectral module and the sample arm module
Lens.
One embodiment of the present of invention additionally provides a kind of blood flow measurement method, suitable in above-mentioned blood stream measurement
It is executed in amount equipment, includes at least following steps:
Light source module is controlled to spectral module emission detection light, so that the spectral module presses preset ratio for the detection
The the first detection light and the second detection light that photodegradation is formed are transmitted separately to the reference arm module and the sample arm module；Institute
It states reference arm module and first detection road Guang Anyuan is reflected back the spectral module, as reference light；
Drive the beam splitting module using the optical axis of the detection light as rotary shaft synchronous rotary in control sample arm module
The rotation of driving device and scanning element is parallel to each other using two beams that the second detection photodegradation is formed and has optical path difference
Third detection light and the 4th detection light eyes are scanned, and light and described the will be detected with the third respectively after scanning
The corresponding two beams signal light of four detection light is by spectral module described in backtracking, so that the spectral module divides two beam signal lights
Formed interference light is not interfered with the reference light；
The interference light is obtained by detecting module, and is obtained according to the interference light two corresponding with two beam signal lights
Position phase shift signal, and then the blood flow of eyes medium vessels is calculated.
Further, two beams formed using the second detection photodegradation are parallel to each other and the with optical path difference
Three detection light and the 4th detection light are scanned eyes, specifically:
Third detection light and the 4th detection light are controlled using scanning element with identical scanning direction and identical
Scanning track, the blood vessels of eyes is carried out while being scanned；Alternatively,
Third detection light and the 4th detection light are controlled using scanning element with identical scanning direction and identical
Circular scanning track, to blood vessels all in optic disk carry out circular scanning.
Further, the calculation formula of the blood flow are as follows:
Wherein, F is the blood flow of blood vessel B, VBIt is respectively true velocity of the blood vessel B in X-Z plane and point speed with V
Degree, SBIt is respectively the cross-sectional area and area of section of blood vessel B with S, the section is intercepted for the sweep trace of detection light
Vascular cross-section, the sweep trace are the trajectory line that the detection light scans on eyeground；VBRelationship with V is
SBRelationship with S is SB=S × cos β, β are not equal to 90 ° of odd-multiple；
Component velocity of the blood vessel B in X-Z plane be
Wherein, λ0For the central wavelength for detecting light, n is the blood refractive index in blood vessel B, and τ is two adjacent light of OCT system
The time interval of line scanning, α are that the third detects light and the 4th detection light in the angle of inside of eye.
The implementation of the embodiments of the present invention has the following beneficial effects:
A kind of blood flow measurement device and method provided in an embodiment of the present invention, the equipment include light source module, divide
Optical module, reference arm module, sample arm module and detecting module ensure that the first lens, rotatable Walla when optical path is arranged
This prism, the second lens and delay coding module are simultaneously around the light path light axis rotation of detection light, so that detection light is by Walla
This prism is broken down into two beam standalone probe light k1And k2When reaching eyeground, regardless of scanning element is that line scanning or annular are swept
It retouches, detects light k1And k2With changeless angle α.The present invention will be a branch of using Wollaston prism and delay coding module
It detects photodegradation to be parallel to each other at two beams and the two beams detection light with optical path difference, and with a detector by two detection directions
On frequency shift signal record simultaneously, to realize single light source, single detector while acquire both direction flow Doppler
Signal.
Detailed description of the invention
Fig. 1 is a kind of structural schematic diagram for blood flow measurement equipment that first embodiment of the invention provides；
Fig. 2 is a kind of another structural schematic diagram for blood flow measurement equipment that first embodiment of the invention provides；
Fig. 3 is the structural schematic diagram of sample arm in first embodiment of the invention；
Fig. 4 is that the two beam standalone probe light that rotatable Wollaston prism generates in first embodiment of the invention are incident to
The angle α that eye retina is formed and the geometric space schematic diagram constituted with blood vessel B；
Fig. 5 is a kind of flow diagram for blood flow measurement method that second embodiment of the invention provides；
Fig. 6 is the flow diagram that the method for all blood vessel flows in optic disk is measured in second embodiment of the invention；
Fig. 7 is that the ring of total blood flow in measurement optic disk in second embodiment of the invention sweeps the scanning schematic diagram of mode.
Specific embodiment
Following will be combined with the drawings in the embodiments of the present invention, and technical solution in the embodiment of the present invention carries out clear, complete
Site preparation description, it is clear that described embodiments are only a part of the embodiments of the present invention, instead of all the embodiments.It is based on
Embodiment in the present invention, it is obtained by those of ordinary skill in the art without making creative efforts every other
Embodiment shall fall within the protection scope of the present invention.
It should be noted that the embodiment of the present invention provides a kind of blood flow measurement device and method, for measuring people's
The blood flow of histoorgan.Histoorgan herein includes the eyes of people or animal.Although selected in attached drawing of the present invention
Measurement object be that the blood vessels of eyes but itself with regard to the blood flow measurement device and method is equally applicable to survey
Measure other histoorgans of human or animal other than eyes.
It is understood that sample hereinafter includes but is not limited to the eyes of human or animal.
First embodiment of the invention:
Please refer to Fig. 1-4.
As shown in Figs. 1-2, a kind of blood flow measurement equipment provided in this embodiment, comprising: light source module 100, light splitting
Module 200, reference arm module 300, sample arm module 500 and detecting module 600.
The light source module 100 is used for the 200 emission detection light of spectral module.
The spectral module 200, for the detection photodegradation to be detected light and the second detection at the first of preset ratio
Light, and the first detection light and the second detection light are transmitted separately to the reference arm module 300 and the sample arm
Module 500.
Wherein, the first collimation lens, the ginseng are provided between the spectral module 200 and the reference arm module 300
A plane mirror built in module is examined as reference mirror 303；It is set between the spectral module 200 and the sample arm module 500
It is equipped with the second collimation lens 400.
The reference arm module 300 is made for first detection road Guang Anyuan to be reflected back the spectral module 200
For reference light.
The sample arm module 500, for first with rotatable Wollaston prism 502 and delay coding module 504
The second detection photodegradation is parallel to each other at two beams and the third detection light and the 4th with optical path difference detects light, it is then sharp
The third detection light is controlled with scanning element 510 and the 4th detection light is scanned eyes 800, and will be divided after scanning
Two beams signal light corresponding with third detection light and the 4th detection light is by spectral module 200 described in backtracking.
Wherein, as shown in figure 3, the sample arm module 500, including beam splitting module, scanning element 510, field mirror
516, dichroscope 511 and ophthalmoscope 512.
The beam splitting module, including optical axis first lens 501 coaxial with the detection optical axis of light, rotatable Walla
This prism 502 and the second lens 503 further include the delay coding mould for being inserted into any beam in third detection light or the 4th detection light
Block 504.
Scanning element 510, including the first scanning element and the second scanning element；Wherein, first scanning element is used for
The third detection light and the 4th detection light are received, and reflexes to second scanning element, then scanned by described second
Element passes through the field mirror 516 by reflected light back to the dichroscope 511, further by the dichroscope 511
By reflected light back to the ophthalmoscope 512, so that reflected light is converged to eyes 800 by the ophthalmoscope 512.
It is understood that the scanning element 510 cooperates the driving device 505 to rotate synchronously, scanning comes from Walla
Two beam standalone probe light of this prism 502, and detection light is projected in parallel to the field mirror 516, then by described two
Enter eyes 800 after reflexing to the ophthalmoscope 512 to Look mirror 511.
Preferably, the sample arm module 500 further includes driving the beam splitting module with the optical axis of the detection light for rotation
The driving device 505 of shaft synchronous rotary, and the calculating equipment of the control system 700 is loaded, the calculating equipment is also used
In the rotation for controlling the scanning element 510 in the driving device 505 and the sample arm module 500.
In the present embodiment, the second detection light is focused on rotatable Wollaston rib by first lens 501
After on interface inside mirror 502, the second detection light has been broken down into the mutually orthogonal standalone probe of two beam polarization states
Light beam uses k respectively1And k2It indicates.It is collimated into two beams again after two beams independent detection beam Propagation to second lens 503
Then the delay coding module 504 is inserted in any a branch of collimated light beam by the collimated light beam being parallel to each other, thus
It is parallel to each other to two beams and the third detection light and the 4th with optical path difference detects light.
In this, it is assumed that the delay coding module 504 is inserted into k1In, the insertion of the delay coding module 504 is right
k1And k2Realize delay coding, i.e. k1And k2Between according to it is described delay coding module 504 refractive index and thickness and introduce
Certain optical path difference.
It should be noted that the rotation of optical axis, rotatable Wollaston prism 502 due to first lens 501
The optical axis of axis and second lens 503 is coaxial with the optical axis of detection light, so the driving device 505 drives described point
When beam module is to detect the optical axis of light as rotary shaft synchronous rotary, two beam generated of Wollaston prism 502 can't be caused
The collimating status of independent detection light beam and the state being parallel to each other.
In the present embodiment, as shown in figure 4, Fig. 4 is rotatable Wollaston prism 502 in first embodiment of the invention
The two beam standalone probe light generated are incident to the angle α of 800 retina of eyes formation and show with the blood vessel B geometric space constituted
It is intended to.
When detection light is focused on the interface inside rotatable Wollaston prism 502 by first lens 501
Afterwards, the mutually orthogonal standalone probe light beam of two beam polarization states, k have been resolved into simultaneously1And k2.Wherein, k1It is compiled across the delay
The scanning element 510 is reached after code module 504, with direction k1It is incident on the retinal vessel B of eyes 800, then along Y
Direction vessel scanning B.The signal light scattered by eyeground, along the scanning element 510, the delay coding module 504, described
Second lens 503, rotatable Wollaston prism 502 and first lens 501 return to the spectral module 200, and
It is interfered in the spectral module 200 with the reference light that the reference arm module 300 is reflected back, interference light is by the detection
Module 600 detects and is transferred to control system 700, and after the processing of control system 700, the OCT for obtaining 800 eyeground of eyes is disconnected
Layer image and first phase shift signal psi1。
When detection light is focused on the interface inside rotatable Wollaston prism 502 by first lens 501
Afterwards, the mutually orthogonal standalone probe light beam of two beam polarization states, k have been resolved into simultaneously1And k2.Wherein, k2Without the delay
Coding module 504 and directly reach the scanning element 510, direction k2It is incident on the retinal vessel B of eyes 800, then
Vessel scanning B along the Y direction.The signal light scattered by eyeground, along the scanning element 510, the delay coding module
504, second lens 503, rotatable Wollaston prism 502 and first lens 501, return to the spectral module
200, and the reference light being reflected back with the reference arm module 300 interferes in the spectral module 200, interference light quilt
The detecting module 600 detects and is transferred to control system 700, after the processing of control system 700, obtains eyes 800
The OCT tomographic imaging figure at bottom and first phase shift signal psi2。
It should be noted that k1And k2Angle be α, and constitute X-Z plane, detect light beam sweep trace be Y-axis.
Due to the optical axis of first lens 501, the rotary shaft of rotatable Wollaston prism 502 and second lens 503
Optical axis is coaxial, k with the optical axis of detection light1And k2Angle be that α will not be rotated with it and be changed, and k1And k2It is regarded on eyeground
Scanning track on nethike embrane is completely coincident.
The spectral module 200, be also used to respectively carry out two beam signal lights with the reference light interference be formed by it is dry
It relates to light control system 700 is transferred to by the detecting module 600 and handled, obtain two positions corresponding with two beam signal lights
Phase shift signal, and then the blood flow of 800 medium vessels of eyes is calculated.
Wherein, the calculation formula of the blood flow are as follows:
Wherein, F is the blood flow of blood vessel B, VBIt is respectively true velocity of the blood vessel B in X-Z plane and point speed with V
Degree, SBIt is respectively the cross-sectional area and area of section of blood vessel B with S, the section is intercepted for the sweep trace of detection light
Vascular cross-section, the sweep trace are the trajectory line that the detection light scans on eyeground；VBRelationship with V is
SBRelationship with S is SB=S × cos β, β are not equal to 90 ° of odd-multiple；
Component velocity of the blood vessel B in X-Z plane be
Wherein, λ0For the central wavelength for detecting light, n is the blood refractive index in blood vessel B, and τ is two adjacent light of OCT system
The time interval of line scanning, α are that the third detects the angle of light and the 4th detection light inside eyes 800.
In the present embodiment, final instantaneous blood flow F can not have to know that β can be calculated.Due to blood
The flowing of liquid be in periodically having certain pulsation, therefore may finally be continuously quickly within one or more pulsation periods
Repeatedly measurement instantaneous blood flow F, and its average value is worked as into the actual flow of blood magnitude for the blood vessel.
It should be noted that in the present embodiment, according to the trend and distribution situation of blood vessel B, passing through the scanning element
510 and the driving device 505 cooperation, can make detect light beam realize any direction scanning, thus make detect light beam root
Practical according to blood vessel B moves towards adjustment scanning direction.
Preferably, described to control the third detection light and the 4th detection light to eyes 800 using scanning element 510
It is scanned, specifically:
The third detection light and the 4th detection light are controlled using scanning element 510 with identical scanning direction and phase
Same scanning track carries out while scanning to the blood vessel of eyes 800；Alternatively,
The third detection light and the 4th detection light are controlled using scanning element 510 with identical scanning direction and phase
Same circular scanning track carries out circular scanning to blood vessels all in optic disk.
It should be noted that blood flow direction VBThe angle β between plane X-Z constituted with two detection light beam k1 and k2 cannot
Equal to 90 ° (or 90 ° odd-multiple), in order to avoid blood vessel B is made to lead to no measurement result without component velocity in X-Z plane, therefore it is
The accuracy for guaranteeing measurement, should be avoided β close to 90 °.
In this embodiment, it is preferred that the sample arm module 500, further includes previewing module, for dividing after obtaining scanning
Two beams signal light corresponding with third detection light and the 4th detection light carries out preview；Specifically,
The previewing module includes imaging len 513 and image pick-up device 514, and reflected light is converged to eye by the ophthalmoscope 512
It is scattered after eyeball 800, scattering light successively passes through the ophthalmoscope 512, the dichroscope 511 and the imaging len 513
After reach the image pick-up device 514, fundus image is shot by the image pick-up device 514.
It is understood that the optical scanning that light source module 100 issues is to eyes 800, and scatters in eyes 800,
Reflected light reaches the dichroscope 511 after the ophthalmoscope 512 transmission.The dichroscope 511 is to the light source die
The light that block 100 issues has high-transmission rate, and reflected light arrives after successively transmiting the dichroscope 511 and the imaging len 513
Fundus image is taken up to the image pick-up device 514, and by the image pick-up device 514.The fundus image that the image pick-up device 514 is shot is shown to
On the display screen of control system 700, so that operator understands the relevant information of the eyes 800, convenient for further operation.
A kind of blood flow measurement device provided in this embodiment, due to ensure that when optical path is arranged the first lens 501,
The light path light axis of rotatable Wollaston prism 502, the second lens 503 and delay coding module 504 simultaneously around detection light rotates,
When so that detection light being broken down into the arrival eyeground two beam standalone probe light k1 and k2 by Wollaston prism 502, regardless of scanning
Unit 510 is line scanning or circular scanning, and detection light k1 and k2 have changeless angle α.Again due to the first lens 501
Detection light is focused on 502 inside interface of Wollaston prism, this enables the detection of two beams light k1 and k2 to gather simultaneously
Coke arrives the same point on eyeground.First phase signals and second phase signals can one-shot measurement it is Polaroid in simultaneously
It arrives, these all make the blood flow finally calculated more accurate.
It should be noted that the driving device 505 of the present embodiment is preferentially selected as motor, naturally it is also possible to be that motor drives
Other power devices of driving.Delay coding module 504 is preferentially selected as parallel plate, and scanning element 510 is preferentially selected as
Galvanometer.
A kind of blood flow measurement equipment provided in this embodiment, by driving device 505 control rotatable Walla this
The rotation of prism 502, two beam independent light beams of generation can detect the first phase shift signal and second of blood vessel simultaneously
Phase shift signal can guarantee that the instantaneous flow being calculated is more accurate.Due to delay coding techniques, first phase shift
Dynamic signal and second phase shift signal can show simultaneously in a width figure, this for blood vessel registration and go background to make an uproar
Sound is more easily also more acurrate, and two position phase shift signal strengths respectively account for the 1/2 of resultant signal, take full advantage of signal energy.
I.e. a branch of detection photodegradation is parallel to each other by the present embodiment using Wollaston prism 502 and delay coding module 504 at two beams
And two beams with optical path difference detect light, and are recorded the frequency shift signal on two detection directions simultaneously with a detector
Come, to realize single light source, single detector while acquire both direction blood flow doppler signal.
Second embodiment of the invention:
Please refer to Fig. 5-7.
As shown in figure 5, the present embodiment additionally provides a kind of blood flow measurement method, suitable in above-mentioned blood stream measurement
It is executed in amount equipment, includes at least following steps:
S101, control light source module 100 are to 200 emission detection light of spectral module, so that the spectral module 200 is by default
The first detection light that the detection photodegradation is formed and the second detection light are transmitted separately to 300 He of reference arm module by ratio
The sample arm module 500；First detection road Guang Anyuan is reflected back the spectral module by the reference arm module 300
200, as reference light.
Wherein, the first collimation lens, the ginseng are provided between the spectral module 200 and the reference arm module 300
A plane mirror built in module is examined as reference mirror 303；It is set between the spectral module 200 and the sample arm module 500
It is equipped with the second collimation lens 400.
Drive the beam splitting module same as rotary shaft using the optical axis of the detection light in S102, control sample arm module 500
The rotation for walking the driving device 505 and scanning element 510 of rotation, two beams formed using the second detection photodegradation are mutually flat
Row and with optical path difference third detection light and the 4th detection light eyes 800 are scanned, and will scanning after respectively with it is described
Third detects light and the corresponding two beams signal light of the 4th detection light by spectral module 200 described in backtracking, so that described
Two beam signal lights are interfered formed interference light with the reference light respectively by spectral module 200.
Wherein, as shown in figure 3, the sample arm module 500, including beam splitting module, scanning element 510, field mirror
516, dichroscope 511 and ophthalmoscope 512.
The beam splitting module, including optical axis first lens 501 coaxial with the detection optical axis of light, rotatable Walla
This prism 502 and the second lens 503 further include the delay coding mould for being inserted into any beam in third detection light or the 4th detection light
Block 504.
Scanning element 510, including the first scanning element and the second scanning element；Wherein, first scanning element is used for
The third detection light and the 4th detection light are received, and reflexes to second scanning element, then scanned by described second
Element passes through the field mirror 516 by reflected light back to the dichroscope 511, further by the dichroscope 511
By reflected light back to the ophthalmoscope 512, so that reflected light is converged to eyes 800 by the ophthalmoscope 512.
It is understood that the scanning element 510 cooperates the driving device 505 to rotate synchronously, scanning comes from Walla
Two beam standalone probe light of this prism 502, and detection light is projected in parallel to the field mirror 516, then by described two
Enter eyes 800 after reflexing to the ophthalmoscope 512 to Look mirror 511.
Preferably, the sample arm module 500 further includes driving the beam splitting module with the optical axis of the detection light for rotation
The driving device 505 of shaft synchronous rotary, and the calculating equipment of the control system 700 is loaded, the calculating equipment is also used
In the rotation for controlling the scanning element 510 in the driving device 505 and the sample arm module 500.
In the present embodiment, the second detection light is focused on rotatable Wollaston rib by first lens 501
After on interface inside mirror 502, the second detection light has been broken down into the mutually orthogonal standalone probe of two beam polarization states
Light beam uses k respectively1And k2It indicates.It is collimated into two beams again after two beams independent detection beam Propagation to second lens 503
Then the delay coding module 504 is inserted in any a branch of collimated light beam by the collimated light beam being parallel to each other, thus
It is parallel to each other to two beams and the third detection light and the 4th with optical path difference detects light.
In this, it is assumed that the delay coding module 504 is inserted into k1In, the insertion of the delay coding module 504 is right
k1And k2Realize delay coding, i.e. k1And k2Between according to it is described delay coding module 504 refractive index and thickness and introduce
Certain optical path difference.
It should be noted that the rotation of optical axis, rotatable Wollaston prism 502 due to first lens 501
The optical axis of axis and second lens 503 is coaxial with the optical axis of detection light, so the driving device 505 drives described point
When beam module is to detect the optical axis of light as rotary shaft synchronous rotary, two beam generated of Wollaston prism 502 can't be caused
The collimating status of independent detection light beam and the state being parallel to each other.
In the present embodiment, as shown in figure 4, Fig. 4 is rotatable Wollaston prism 502 in first embodiment of the invention
The two beam standalone probe light generated are incident to the angle α of 800 retina of eyes formation and show with the blood vessel B geometric space constituted
It is intended to.
When detection light is focused on the interface inside rotatable Wollaston prism 502 by first lens 501
Afterwards, the mutually orthogonal standalone probe light beam of two beam polarization states, k have been resolved into simultaneously1And k2.Wherein, k1It is compiled across the delay
The scanning element 510 is reached after code module 504, with direction k1It is incident on the retinal vessel B of eyes 800, then along Y
Direction vessel scanning B.The signal light scattered by eyeground, along the scanning element 510, the delay coding module 504, described
Second lens 503, rotatable Wollaston prism 502 and first lens 501 return to the spectral module 200, and
It is interfered in the spectral module 200 with the reference light that the reference arm module 300 is reflected back, interference light is by the detection
Module 600 detects and is transferred to control system 700, and after the processing of control system 700, the OCT for obtaining 800 eyeground of eyes is disconnected
Layer image and first phase shift signal psi1。
When detection light is focused on the interface inside rotatable Wollaston prism 502 by first lens 501
Afterwards, the mutually orthogonal standalone probe light beam of two beam polarization states, k have been resolved into simultaneously1And k2.Wherein, k2Without the delay
Coding module 504 and directly reach the scanning element 510, direction k2It is incident on the retinal vessel B of eyes 800, then
Vessel scanning B along the Y direction.The signal light scattered by eyeground, along the scanning element 510, the delay coding module
504, second lens 503, rotatable Wollaston prism 502 and first lens 501, return to the spectral module
200, and the reference light being reflected back with the reference arm module 300 interferes in the spectral module 200, interference light quilt
The detecting module 600 detects and is transferred to control system 700, after the processing of control system 700, obtains eyes 800
The OCT tomographic imaging figure at bottom and first phase shift signal psi2。
It should be noted that k1And k2Angle be α, and constitute X-Z plane, detect light beam sweep trace be Y-axis.
Due to the optical axis of first lens 501, the rotary shaft of rotatable Wollaston prism 502 and second lens 503
Optical axis is coaxial, k with the optical axis of detection light1And k2Angle be that α will not be rotated with it and be changed, and k1And k2It is regarded on eyeground
Scanning track on nethike embrane is completely coincident.
S103, the interference light is obtained by detecting module 600, and obtained and two beam signal lights pair according to the interference light
The two position phase shift signals answered, and then the blood flow of 800 medium vessels of eyes is calculated.
Wherein, the calculation formula of the blood flow are as follows:
Wherein, F is the blood flow of blood vessel B, VBIt is respectively true velocity of the blood vessel B in X-Z plane and point speed with V
Degree, SBIt is respectively the cross-sectional area and area of section of blood vessel B with S, the section is intercepted for the sweep trace of detection light
Vascular cross-section, the sweep trace are the trajectory line that the detection light scans on eyeground；VBRelationship with V is
SBRelationship with S is SB=S × cos β, β are not equal to 90 ° of odd-multiple；
Component velocity of the blood vessel B in X-Z plane be
Wherein, λ0For the central wavelength for detecting light, n is the blood refractive index in blood vessel B, and τ is two adjacent light of OCT system
The time interval of line scanning, α are that the third detects the angle of light and the 4th detection light inside eyes 800.
In the present embodiment, final instantaneous blood flow F can not have to know that β can be calculated.Due to blood
The flowing of liquid be in periodically having certain pulsation, therefore may finally be continuously quickly within one or more pulsation periods
Repeatedly measurement instantaneous blood flow F, and its average value is worked as into the actual flow of blood magnitude for the blood vessel.
It should be noted that in the present embodiment, according to the trend and distribution situation of blood vessel B, passing through the scanning element
510 and the driving device 505 cooperation, can make detect light beam realize any direction scanning, thus make detect light beam root
Practical according to blood vessel B moves towards adjustment scanning direction.
It should be noted that blood flow direction VBWith two detection light beam k1And k2Angle β between the plane X-Z of composition cannot
Equal to 90 ° (or 90 ° odd-multiple), in order to avoid blood vessel B is made to lead to no measurement result without component velocity in X-Z plane, therefore it is
The accuracy for guaranteeing measurement, should be avoided β close to 90 °.
Preferably, described to control the third detection light and the 4th detection light to eyes 800 using scanning element 510
It is scanned, specifically:
The third detection light and the 4th detection light are controlled using scanning element 510 with identical scanning direction and phase
Same scanning track carries out while scanning to the blood vessel of eyes 800；Alternatively,
The third detection light and the 4th detection light are controlled using scanning element 510 with identical scanning direction and phase
Same circular scanning track carries out circular scanning to blood vessels all in optic disk.
In the present embodiment, as shown in fig. 6-7, wherein Fig. 6 is that all blood in optic disk are measured in second embodiment of the invention
The flow diagram of the method for pipe blood flow, Fig. 7 are that the ring of total blood flow in measurement optic disk in second embodiment of the invention sweeps mould
The scanning schematic diagram of formula.On the basis of the blood flow measurement method, all blood vessel flows in the measurement optic disk
Method, suitable for executing in above-mentioned blood flow measurement equipment, steps are as follows:
S201, control light source module 100 are to 200 emission detection light of spectral module, so that the spectral module 200 is by default
The first detection light that the detection photodegradation is formed and the second detection light are transmitted separately to 300 He of reference arm module by ratio
The sample arm module 500；First detection road Guang Anyuan is reflected back the spectral module by the reference arm module 300
200, as reference light.
Drive the beam splitting module same as rotary shaft using the optical axis of the detection light in S202, control sample arm module 500
The rotation of the driving device 505 and scanning element 510 of rotation is walked, so that third detection light and the 4th detection light are with phase
Same scanning direction and identical circular scanning track carries out circular scanning to blood vessels all in optic disk, and generates all blood vessels
Corresponding two beams signal light is by spectral module 200 described in backtracking, so that the spectral module 200 distinguishes two beam signal lights
Interfered formed interference light with the reference light.
S203, the interference light is obtained by detecting module 600, and obtained and two beam signal lights pair according to the interference light
The two position phase shift signals answered, and then cut according to two position phase shift signals of all blood vessels, and the blood vessel that measurement obtains
Face area is calculated one by one, obtains the blood flow of all blood vessels in optic disk.
It is rotated synchronously specifically, control system 700 controls the driving device 505 with the scanning element 510, two beams are visited
Survey light k1And k2Make circular scanning on a circumference C around optic disk region.During doing circular scanning, the driving dress
Setting 505 rotation can guarantee to detect light k1And k2Composed plane and the tangential direction of circular scanning are vertical always.In this way,
Two position phase shift signals of all vascular flows in optic disk, first phase shift can be obtained simultaneously by scanning a circular scanning
Signal and second phase shift signal, and then calculate the instantaneous blood flow amount of this moment blood flow.In order to make system to blood flow
Measured value it is more credible, need continuously to measure the flow information of one or more pulsation heart beat cycle, and its average value is made
For the final intraretinal total blood flow of blood flow numerical quantity and eyes 800.
Wherein, the blood flow that blood vessel is calculated according to first phase shift signal and second phase shift signal it
Before, further includes:
Measure the area of section of the blood vessel；The section of the blood vessel refers to the blood that the sweep trace of detection light is intercepted
Tube section.The sweep trace of the detection light refers to the trajectory line that the detection light scans on eyeground.The detection light is swept
It retouches after trajectory line reaches eyeground with the rotatable Wollaston prism 502 two beams standalone probe light beam produced and is formed by
Plane is vertical.
A kind of blood flow measurement method provided in this embodiment, due to ensure that when optical path is arranged the first lens 501,
The light path light axis of rotatable Wollaston prism 502, the second lens 503 and delay coding module 504 simultaneously around detection light rotates,
So that detection light is broken down into two beam standalone probe light k by Wollaston prism 5021And k2When reaching eyeground, regardless of scanning is single
Member 510 is line scanning or circular scanning, detects light k1And k2With changeless angle α.Again since the first lens 501 will
Detection light has focused on 502 inside interface of Wollaston prism, this makes two beams detect light k1And k2It can focus on simultaneously
The same point on eyeground.First phase signals and second phase signals can one-shot measurement it is Polaroid in obtain simultaneously, this
All make the blood flow finally calculated more accurate a bit.
It should be noted that the driving device 505 of the present embodiment is preferentially selected as motor, naturally it is also possible to be that motor drives
Other power devices of driving.Delay coding module 504 is preferentially selected as parallel plate, and scanning element 510 is preferentially selected as
Galvanometer.
In this embodiment, it is preferred that the sample arm module 500, further includes previewing module, for dividing after obtaining scanning
Two beams signal light corresponding with third detection light and the 4th detection light carries out preview；Specifically,
The previewing module includes imaging len 513 and image pick-up device 514, and reflected light is converged to eye by the ophthalmoscope 512
It is scattered after eyeball 800, scattering light successively passes through the ophthalmoscope 512, the dichroscope 511 and the imaging len 513
After reach the image pick-up device 514, fundus image is shot by the image pick-up device 514.
It is understood that the optical scanning that light source module 100 issues is to eyes 800, and scatters in eyes 800,
Reflected light reaches the dichroscope 511 after the ophthalmoscope 512 transmission.The dichroscope 511 is to the light source die
The light that block 100 issues has high-transmission rate, and reflected light arrives after successively transmiting the dichroscope 511 and the imaging len 513
Fundus image is taken up to the image pick-up device 514, and by the image pick-up device 514.The fundus image that the image pick-up device 514 is shot is shown to
On the display screen of control system 700, so that operator understands the relevant information of the eyes 800, convenient for further operation.
A kind of blood flow measurement method provided in this embodiment, by driving device 505 control rotatable Walla this
The rotation of prism 502, two beam independent light beams of generation can detect the first phase shift signal and second of blood vessel simultaneously
Phase shift signal can guarantee that the instantaneous flow being calculated is more accurate.Due to delay coding techniques, first phase shift
Dynamic signal and second phase shift signal can show simultaneously in a width figure, this for blood vessel registration and go background to make an uproar
Sound is more easily also more acurrate, and two position phase shift signal strengths respectively account for the 1/2 of resultant signal, take full advantage of signal energy.
I.e. a branch of detection photodegradation is parallel to each other by the present embodiment using Wollaston prism 502 and delay coding module 504 at two beams
And two beams with optical path difference detect light, and are recorded the frequency shift signal on two detection directions simultaneously with a detector
Come, to realize single light source, single detector while acquire both direction blood flow doppler signal.
The above is a preferred embodiment of the present invention, it is noted that for those skilled in the art
For, without departing from the principle of the present invention, several improvement and deformations can also be made, these improvement and deformations are also considered as
Protection scope of the present invention.
Those of ordinary skill in the art will appreciate that realizing all or part of the process in above-described embodiment method, being can be with
Relevant hardware is instructed to complete by computer program, the program can be stored in a computer-readable storage medium
In, the program is when being executed, it may include such as the process of the embodiment of above-mentioned each method.Wherein, the storage medium can be magnetic
Dish, CD, read-only memory (Read-Only Memory, ROM) or random access memory (Random Access
Memory, RAM) etc..
Claims (10)
1. a kind of blood flow measurement equipment characterized by comprising light source module, spectral module, reference arm module, sample
Arm module and detecting module；
The light source module is used for the spectral module emission detection light；
The spectral module, for the detection photodegradation to be detected light and the second detection light at the first of preset ratio, and will
The first detection light and the second detection light are transmitted separately to the reference arm module and the sample arm module；
The reference arm module, for first detection road Guang Anyuan to be reflected back the spectral module, as reference light；
The sample arm module, for being detected first with rotatable Wollaston prism and delay coding module by described second
Photodegradation is parallel to each other at two beams and the third detection light and the 4th with optical path difference detects light, is then controlled using scanning element
Third detection light and the 4th detection light are scanned eyes, and will be detected respectively with the third after scanning light and
Described 4th detects the corresponding two beams signal light of light by spectral module described in backtracking；
The spectral module is also used to respectively carry out two beam signal lights with the reference light interference and is formed by interference light and passes through
The detecting module is transferred to control system and is handled, and obtains two position phase shift signals corresponding with two beam signal lights, into
And the blood flow of eyes medium vessels is calculated.
2. blood flow measurement equipment according to claim 1, which is characterized in that the sample arm module, including beam splitting
Module, scanning element, field mirror, dichroscope and ophthalmoscope；
The beam splitting module, including optical axis first lens coaxial with the detection optical axis of light, rotatable Wollaston rib
Mirror and the second lens further include the delay coding module for being inserted into any beam in third detection light or the 4th detection light；
Scanning element, including the first scanning element and the second scanning element；Wherein, first scanning element is described for receiving
Third detects light and the 4th detection light, and reflexes to second scanning element, then passed through by second scanning element
The field mirror by reflected light back to the dichroscope, further by the dichroscope by reflected light back to described
Ophthalmoscope, so that reflected light is converged to eyes by the ophthalmoscope.
3. blood flow measurement equipment according to claim 1, which is characterized in that the sample arm module, further includes band
The beam splitting module is moved using the optical axis of the detection light as the driving device of rotary shaft synchronous rotary, and loads the control system
The calculating equipment of system, the equipment that calculates are also used to control the driving device and the scanning element in the sample arm module
Rotation.
4. blood flow measurement equipment according to claim 1, which is characterized in that the sample arm module, further includes pre-
It lookes at module, detects light after scanning with the third respectively and the corresponding two beams signal light of the 4th detection light carries out for obtaining
Preview；Specifically,
The previewing module includes imaging len and image pick-up device, and the ophthalmoscope scatters after reflected light is converged to eyes,
Scattering light successively reaches the image pick-up device after the ophthalmoscope, the dichroscope and the imaging len, is taken the photograph by described
As device shoots fundus image.
5. blood flow measurement equipment according to claim 1, which is characterized in that described using described in scanning element control
Third detection light and the 4th detection light are scanned eyes, specifically:
Third detection light and the 4th detection light are controlled with identical scanning direction using scanning element and identical are swept
Track is retouched, the blood vessel of eyes is carried out while being scanned；Alternatively,
The third detection light and the 4th detection light are controlled using scanning element with identical scanning direction and identical ring
Shape scans track, carries out circular scanning to blood vessels all in optic disk.
6. blood flow measurement equipment according to claim 1, which is characterized in that the calculation formula of the blood flow
Are as follows:
Wherein, F is the blood flow of blood vessel B, VBIt is respectively true velocity and component velocity of the blood vessel B in X-Z plane, S with VB
It is respectively the cross-sectional area and area of section of blood vessel B with S, the section is cut to detect the blood vessel that the sweep trace of light is intercepted
Face, the sweep trace are the trajectory line that the detection light scans on eyeground；VBRelationship with V isSBWith S's
Relationship is SB=S × cos β, β are not equal to 90 ° of odd-multiple；
Component velocity of the blood vessel B in X-Z plane be
Wherein, λ0For the central wavelength for detecting light, n is the blood refractive index in blood vessel B, and τ is that two adjacent rays of OCT system are swept
The time interval retouched, α are that the third detects light and the 4th detection light in the angle of inside of eye.
7. blood flow measurement equipment according to claim 1, which is characterized in that the spectral module and the reference arm
The first collimation lens is provided between module, a plane mirror is as reference mirror built in the reference module；The light splitting mould
The second collimation lens is provided between block and the sample arm module.
8. a kind of blood flow measurement method, suitable for being held in the described in any item blood flow measurement equipment of claim 1 to 7
Row, which is characterized in that include at least following steps:
Light source module is controlled to spectral module emission detection light, so that the spectral module is divided the detection light by preset ratio
The the first detection light and the second detection light that solution is formed are transmitted separately to the reference arm module and the sample arm module；The ginseng
It examines arm module and first detection road Guang Anyuan is reflected back the spectral module, as reference light；
Drive the beam splitting module using the optical axis of the detection light as the driving of rotary shaft synchronous rotary in control sample arm module
The rotation of device and scanning element, is parallel to each other and the with optical path difference using two beams that the second detection photodegradation is formed
Three detection light and the 4th detection light are scanned eyes, and will visit respectively with third detection light and the described 4th after scanning
The corresponding two beams signal light of light is surveyed by spectral module described in backtracking so that the spectral module by two beam signal lights respectively with
The reference light is interfered formed interference light；
The interference light is obtained by detecting module, and two position phases corresponding with two beam signal lights are obtained according to the interference light
Movable signal, and then the blood flow of eyes medium vessels is calculated.
9. blood flow measurement method according to claim 8, which is characterized in that described to utilize the second detection light point
Two beams that solution is formed are parallel to each other and the third detection light with optical path difference and the 4th detection light are scanned eyes, specifically
Are as follows:
Third detection light and the 4th detection light are controlled with identical scanning direction using scanning element and identical are swept
Track is retouched, the blood vessel of eyes is carried out while being scanned；Alternatively,
The third detection light and the 4th detection light are controlled using scanning element with identical scanning direction and identical ring
Shape scans track, carries out circular scanning to blood vessels all in optic disk.
10. blood flow measurement method according to claim 8, which is characterized in that the calculation formula of the blood flow
Are as follows:
Wherein, F is the blood flow of blood vessel B, VBIt is respectively true velocity and component velocity of the blood vessel B in X-Z plane, S with VB
It is respectively the cross-sectional area and area of section of blood vessel B with S, the section is cut to detect the blood vessel that the sweep trace of light is intercepted
Face, the sweep trace are the trajectory line that the detection light scans on eyeground；VBRelationship with V isSBWith S's
Relationship is SB=S × cos β, β are not equal to 90 ° of odd-multiple；
Component velocity of the blood vessel B in X-Z plane be
Wherein, λ0For the central wavelength for detecting light, n is the blood refractive index in blood vessel B, and τ is that two adjacent rays of OCT system are swept
The time interval retouched, α are that the third detects light and the 4th detection light in the angle of inside of eye.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201811055051.9A CN109124686A (en) | 2018-09-11 | 2018-09-11 | A kind of blood flow measurement device and method |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201811055051.9A CN109124686A (en) | 2018-09-11 | 2018-09-11 | A kind of blood flow measurement device and method |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN109124686A true CN109124686A (en) | 2019-01-04 |
Family
ID=64824605
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201811055051.9A Pending CN109124686A (en) | 2018-09-11 | 2018-09-11 | A kind of blood flow measurement device and method |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN109124686A (en) |
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN111265183A (en) * | 2020-02-19 | 2020-06-12 | 淮阴工学院 | Retina blood flow measuring device based on light beam parallel scanning mode |
| CN112022085A (en) * | 2020-09-16 | 2020-12-04 | 中山大学 | Method for calculating blood vessel flow in retina |
| US11877831B2 (en) | 2022-03-14 | 2024-01-23 | O/D Vision Inc. | Systems and methods for artificial intelligence based blood pressure computation based on images of the outer eye |
Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN85103558A (en) * | 1985-05-07 | 1986-11-05 | 复旦大学 | A kind of method and instrument that utilizes ultrasonic Doppler effect to measure blood flow |
| US20120120408A1 (en) * | 2009-06-11 | 2012-05-17 | University Of Tsukuba | Two-beam optical coherence tomography apparatus |
| CN102525408A (en) * | 2010-12-02 | 2012-07-04 | 佳能株式会社 | Ophthalmologic apparatus and blood flow velocity calculation method |
| CN104159505A (en) * | 2014-05-14 | 2014-11-19 | 深圳市斯尔顿科技有限公司 | Blood pressure measurement device and method |
| EP2829219A1 (en) * | 2012-03-12 | 2015-01-28 | Kabushiki Kaisha Topcon | Optical image measurement device, image display device, and image display method |
| CN104825148A (en) * | 2015-05-27 | 2015-08-12 | 深圳市斯尔顿科技有限公司 | Device and method for measuring blood flow of blood vessels |
| CN105167766A (en) * | 2015-11-03 | 2015-12-23 | 深圳市斯尔顿科技有限公司 | Blood flow measuring device and blood flow measuring method |
| CN105769117A (en) * | 2016-01-11 | 2016-07-20 | 佛山科学技术学院 | Fundus optical full-field microangiography imaging device and method |
-
2018
- 2018-09-11 CN CN201811055051.9A patent/CN109124686A/en active Pending
Patent Citations (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN85103558A (en) * | 1985-05-07 | 1986-11-05 | 复旦大学 | A kind of method and instrument that utilizes ultrasonic Doppler effect to measure blood flow |
| US20120120408A1 (en) * | 2009-06-11 | 2012-05-17 | University Of Tsukuba | Two-beam optical coherence tomography apparatus |
| CN102525408A (en) * | 2010-12-02 | 2012-07-04 | 佳能株式会社 | Ophthalmologic apparatus and blood flow velocity calculation method |
| EP2829219A1 (en) * | 2012-03-12 | 2015-01-28 | Kabushiki Kaisha Topcon | Optical image measurement device, image display device, and image display method |
| CN104159505A (en) * | 2014-05-14 | 2014-11-19 | 深圳市斯尔顿科技有限公司 | Blood pressure measurement device and method |
| CN104825148A (en) * | 2015-05-27 | 2015-08-12 | 深圳市斯尔顿科技有限公司 | Device and method for measuring blood flow of blood vessels |
| CN105167766A (en) * | 2015-11-03 | 2015-12-23 | 深圳市斯尔顿科技有限公司 | Blood flow measuring device and blood flow measuring method |
| CN105769117A (en) * | 2016-01-11 | 2016-07-20 | 佛山科学技术学院 | Fundus optical full-field microangiography imaging device and method |
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN111265183A (en) * | 2020-02-19 | 2020-06-12 | 淮阴工学院 | Retina blood flow measuring device based on light beam parallel scanning mode |
| CN111265183B (en) * | 2020-02-19 | 2022-05-27 | 淮阴工学院 | Retina blood flow measuring device based on light beam parallel scanning mode |
| CN112022085A (en) * | 2020-09-16 | 2020-12-04 | 中山大学 | Method for calculating blood vessel flow in retina |
| US11877831B2 (en) | 2022-03-14 | 2024-01-23 | O/D Vision Inc. | Systems and methods for artificial intelligence based blood pressure computation based on images of the outer eye |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN110934563B (en) | Ophthalmologic information processing apparatus, ophthalmologic apparatus, and ophthalmologic information processing method | |
| EP1858402B1 (en) | Methods and apparatus for optical coherence tomography scanning | |
| US9848772B2 (en) | Image displaying method | |
| US9364144B2 (en) | Method and device for recording and displaying an OCT whole-eye scan | |
| Wang et al. | Pilot study of optical coherence tomography measurement of retinal blood flow in retinal and optic nerve diseases | |
| Werkmeister et al. | Measurement of absolute blood flow velocity and blood flow in the human retina by dual-beam bidirectional Doppler fourier-domain optical coherence tomography | |
| EP2301423B1 (en) | Optical image measuring device | |
| US6547731B1 (en) | Method for assessing blood flow and apparatus thereof | |
| CN101641045B (en) | Method for determining microvascular lesions | |
| CN109124686A (en) | A kind of blood flow measurement device and method | |
| CN111265183B (en) | Retina blood flow measuring device based on light beam parallel scanning mode | |
| CN104825148B (en) | A kind of device and method for measuring blood vessel flow | |
| KR101746763B1 (en) | Diagnostic technique and imaging method of retinal and choroidal optical coherence tomography angiography | |
| WO2015172322A1 (en) | Blood flow measuring device and method | |
| CN109363627A (en) | A kind of measuring device and method of velocity of blood flow | |
| JP3576212B2 (en) | In particular, a method and apparatus for measuring blood flow velocity | |
| US20200397282A1 (en) | Ophthalmologic apparatus and method of controlling the same | |
| CN113180631A (en) | Blood flow velocity and fractional flow reserve analysis method based on intravascular imaging | |
| Wan et al. | Dual-beam delay-encoded all fiber Doppler optical coherence tomography for in vivo measurement of retinal blood flow | |
| Sakai et al. | Retinal arteriole pulse waveform analysis using a fully-automated Doppler optical coherence tomography flowmeter: a pilot study | |
| RU2692220C1 (en) | Method of colour doppler mapping in endoscopic optical coherence tomography | |
| CN110811536A (en) | Ophthalmologic apparatus and control method therefor | |
| JP7106320B2 (en) | Ophthalmic device and control method for ophthalmic device | |
| CN107348940B (en) | Retinal blood flow speed detector based on the interference of Linnik type near-infrared simultaneous phase-shifting | |
| CN109691973A (en) | A kind of optical coherence tomography system pulsed for measuring eyeball |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| RJ01 | Rejection of invention patent application after publication |
Application publication date: 20190104 |
|
| RJ01 | Rejection of invention patent application after publication |