CN105796053B - Utilize the method for OCT measurement dynamic contrast and the lateral flow of estimation - Google Patents

Abstract

The invention discloses the methods using OCT measurement dynamic contrast and the lateral flow of estimation.The determination method of sample motion-vector includes：The sample image for obtaining the T1 moment, selects predeterminable area therein as tracking image, obtains image recognition information and the position at T1 moment of tracking image；The sample image for obtaining the T2 moment is wherein finding position identical with the position at tracking image T1 moment as tracking frame；Using a point for tracking frame as reference point, reference point is determined along horizontal axis and the moveable maximum magnitude of vertical pivot, moveable maximum magnitude is divided into multiple shift positions；When calculating reference point is according to vector movement and traversal shift position, the image recognition information and reference point of T1 moment tracking image track the related coefficient of the image recognition information of image in frame when being moved to each shift position, the mobile vector of the corresponding reference point of the maximum value of related coefficient is the sample T2 moment vector mobile relative to the T1 moment.

Description

Utilize the method for OCT measurement dynamic contrast and the lateral flow of estimation

Technical field

It is the present invention relates to optical image technology field, in particular to a kind of horizontal using OCT measurement dynamic contrast and estimation To the method for flow.

Background technique

Optical coherence tomography (optical coherence tomography, OCT) is a kind of light of non-intrusion type Learn imaging technique.In recent years, in medical domain, especially in field of ophthalmology, optical coherence tomography system can survey shooting The tomography for trying object (retina on such as eyeground, arteria and vena centralis retinae etc.) carries out three-dimensional visualization imaging, such as to eyeground spy The tomography for determining position carries out three-dimensional visualization imaging.It is first when the tomography to eyeground privileged site carries out three-dimensional visualization imaging It first needs to carry out the position that two-dimensional imaging determines eyeground to eyeground, by finding the privileged site on eyeground in eyeground two-dimensional imaging, OCT scan is carried out to carry out three-dimensional visualization imaging to the privileged site on eyeground.But because the eye movement of watching attentively property can cause eye The movement at bottom, i.e. eyeground are moved.In the prior art, the camera lens for carrying out OCT scan is not adjusted with the movement on eyeground Whole, in this way, the concrete position on the eyeground for resulting in OCT scan to be scanned is changed, affect three-dimensional visible chemical conversion The accuracy of picture.

Summary of the invention

The present invention provides a kind of using OCT measurement dynamic contrast and estimates the method for lateral flow, sample movement To method for determination of amount and collecting method, carrying out three-dimensional to the privileged site of sample caused by solving because of sample movement can Technical problem depending on being melted into the accuracy difference of picture.

In order to achieve the above objectives, the present invention provides following technical scheme：

A kind of sample it is mobile to method for determination of amount, which is characterized in that include the following steps：

The sample image for obtaining the T1 moment selects the predeterminable area of the sample image at T1 moment as tracking image, obtains Tracking image image recognition information for identification and the position at tracking image T1 moment；

The sample image for obtaining the T2 moment, finds the position phase with the tracking image T1 moment in the sample image at T2 moment Same position is as tracking frame；

A point to track frame establishes plane right-angle coordinate as origin, to track a point of frame as reference point, really Determine reference point along horizontal axis and the moveable maximum magnitude of vertical pivot, it will movably most along horizontal axis and the moveable minimum spacing of vertical pivot It is divided into multiple shift positions on a large scale；

Calculating reference point is according to vector (m, n) movement and when traversing shift position, the image recognition of T1 moment tracking image Information and reference point track the related coefficient of the image recognition information of image in frame, the phase when being moved to each shift position Mobile vector (the m of the corresponding reference point of the maximum value of relationship number_max,n_max) be the sample T2 moment relative to the T1 moment it is mobile to Amount, T2 moment are later than the T1 moment.

Sample provided by the invention it is mobile to method for determination of amount, tracking image from the sample image at T1 moment, Two kinds of information are obtained, and one is image recognition letters tracking image and other parts image distinguished to identify Breath, another kind is tracking image in the position at T1 moment；Then, the sample image for obtaining the T2 moment, at this time due to the shifting of sample Dynamic, the position of tracking image has been moved, and in order to find the mobile vector of tracking image, is needed using tracking image at the T1 moment Position the frame of position identical with its position is found in the sample image at T2 moment as tracking frame；Later, frame is tracked It is moved in its moveable maximum magnitude, tracks frame when calculating the every bit that tracking frame is moved in moveable maximum magnitude The image recognition information of interior image and the related coefficient of the image recognition information at tracking image T1 moment, i.e., the image of two images The degree of correlation of identification information；The position that the corresponding tracking frame of the maximum value of the related coefficient is moved to is the figure of two images It is the position of tracking image being moved to as the immediate position of identification information.The movement of tracking image is the movement by sample Caused, therefore, the vector of the movement of tracking image is exactly the sample T2 moment vector mobile relative to the T1 moment.In this way, can Very easily to determine the vector of the movement of sample, improves and the accurate of three-dimensional visualization imaging is carried out to the privileged site of sample Property.

Detailed description of the invention

Fig. 1-01 is the mobile schematic diagram of the eye fundus image at T1 moment into method for determination of amount in eyeground of the invention；

Fig. 1-02 is the mobile schematic diagram of the eye fundus image at T2 moment into method for determination of amount in eyeground of the invention；

Mobile eyeground figure of the determining tracking image at the T2 moment into method for determination of amount in eyeground Fig. 1-03 of the invention The schematic diagram of the position of picture；

Eyeground movement Fig. 1-04 of the invention derives schematic diagram to the principle of method for determination of amount；

Shown in FIG. 1 is the frame diagram of SDOCT system.Low-coherence light source S (k) is divided into reference arm and sample by fibre optic interferometer Product arm.Reflected light is assembled and is tested in spectrometer, so that the depth of reflection profile is computed；

Shown in Fig. 2 is the phase of the simulation for the fluid mass motion that radian is π (a quarter of imaging source wavelength) Delta data；

Shown in Fig. 3 is the scatterer expected phase variance test result figure whithin a period of time of movement；

Fig. 4 A shows overview diagram relevant to the non-averagely OCT intensity image of sample in Fig. 4 B；In order to obtain this image, 2% agarose well is dissolved into the fat emulsion solution that density matching is 0.1%；Luminance contrast is confined to flowing in image The boundary at edge and air；

Fig. 5 A is period of time T=40us phase change figure；

Fig. 5 B is period of time T=80us phase change figure；

Fig. 6 A is period of time T=200us phase change figure；

Fig. 6 B is period of time T=400us phase change figure；

Fig. 7 A is period of time T=800us phase change figure；

Fig. 7 B is period of time T=1.6ms phase change figure；

Fig. 8 A is the phase change comparison diagram of maximum phase transformation period cycle T 2=40T1；

Fig. 8 B is the phase change comparison diagram of maximum phase transformation period cycle T 2=20T1；

Fig. 9 A is the phase change comparison diagram of maximum phase transformation period interval T2=10T1；

Fig. 9 B is the largest the phase change comparison diagram of phase change time interval T2=5T1；

Shown in Fig. 10 is the phase change data of single scatterer in water；Shown in sphere diameter be respectively 0.5um, 2um and 5um.Diameter is that the sphere of 2um demonstrates the influence of phase error, is primarily due to the phase change number of desired form It is weak according to middle OCT signal；

Figure 11 A shows the image of the lateral scanning pattern of MB- scanning；

The image of the lateral scanning pattern of the scanning of BM- shown in Figure 11 B；

It is the OCT gray level image of the zebra fish tail obtained using MB- scanning mode shown in Figure 12 A；Shown in Figure 12 B It is the phase change contrast image that zebra fish tail is obtained using MB- scanning mode；The size of image is 900um*325um. T2=1ms, T1=40us；

It is the OCT gray level image of the zebra fish tail obtained with BM- scanning mode shown in Figure 13 A；

It is the phase change contrast image of the zebra fish tail obtained using BM- scanning mode shown in Figure 13 B；Figure The size of 13A and Figure 13 B image is all 815um*325um；Phase error in Figure 13 B has been eliminated, the time of contrast image Cycle T 2 is estimated as 40ms；The areas imaging size that note that phase change contrast image is that MB- shown in Figure 12 B is swept 4 times of the contrast image retouched；

It is shown in figure 14 A be low speed transverse movement occur a time point average brightness image, the image sources in The data of the transverse movement for the retina that BM- is scanned；

It is the phase contrast image after noise elimination and median filtering shown in Figure 14 B, is laterally transported from retina Dynamic BM- scan data；Figure 14 B is that there are the phase contrast images at the time point of a small amount of fluid transverse movement；

Shown in figure 15 is the phase change contrast image of uncorrected a large amount of fluid transverse movements；

Figure 16 A and Figure 16 B are the comparison diagrams of one group of phase contrast image；It is uncorrected shown in Figure 16 A in the presence of big Measure the image of transverse movement；

In the case where being α=0 shown in Figure 16 B, the image of corrected a large amount of transverse movements；

Figure 17 A and 17B are that the contrast by the collected retina depth of 2.6S summarizes image；

Figure 17 A is the image before α=0 without overcompensation；

Figure 17 B is the image after α=0 through overcompensation；

It is that BM- scans average OCT grayscale image shown in Figure 18 A；

Figure 18 B, 18C, 18D are three phase change contrast figures of different time points；Each image be all 50ms it Inside collect.The region that arrow is directed toward is spine longitudinal direction angiosomes, two different segmental vessels (Se), spine aorta (DA), axial vein (AV)；

It is the OCT visual image of 3 days zebra fish being quickly fertilized shown in Figure 19 A and 19B；Figure 19 A is the bright visual field MIcrosope image, Figure 19 B are the images of 3 days groupers being quickly fertilized, and all illustrate the anatomical features of desired grouper； The line drawn in Figure 19 A and 19B represents the scanning area of OCT image；Further analysis average flow rate and phase change can Promote the quality of these images；

The OCT gray level image of Figure 20 A illustrates the internal structure of grouper in Figure 19；

It is the blood flow of endocardial shown in Figure 20 B, this image phase noise and OCT image picture in decreased image Element；Phase contrast image after the elimination phase error influence of Figure 20 C description；Figure 20 B clearly describes the appearance of heart, figure The region expected in the flow direction and Figure 19 B of the yolk bag that arrow direction shown in 20C refers to matches；

It is the schematic diagram relative to the direction of the flow in imaging source direction shown in Figure 21；It is seen using Doppler OCT technology The axial flow component observed uses V_zCalibration；

The phase noise of SNR- limitation and the relational graph of average OCT strength signal is shown in Figure 22；

Pair of the grouper tail generated shown in Figure 23 A, 23B, 23C and 23D using the data that MB- scanning mode acquires Than degree image；Figure 23 A is the gray level image of structural information；Arrow in Figure 23 A points out the desired region detected, the region It is main two blood vessels of fish, spine artery and axial blood vessel；Figure 23 B is phase change contrast images, and the time cycle is T2= 1ms and T1=40us, radian change from 0 to 2, observed region be on Doppler OCT image it is sightless, Doppler OCT can only observe sufficiently stable static region.Arrow in Figure 23 B points out the desired motor area observed Domain.Figure 23 C is Doppler flow image, and the scope of application is+- 0.12 radian=+ -200um/s, and phase change average value is 5； It is Doppler flow image shown in Figure 23 D, the scope of application is+- 0.12 radian=+ -200um/s, and phase change average value is 100.More and more stable static characteristic improves visual quality, and the position for understanding each section in advance is conducive to visually Research；

It is the same area of zebra fish in Figure 23 A, 23B, 23C and 23D shown by Figure 24 A and 24B, however, use It is the BM- scanning mode that trace interval is T=10ms；In order to select best parameter, the image of 200 horizontal pixel is acquired Time used in data is 50ms；Due to reducing the dynamic range of Doppler OCT method acquisition data, acquired using this method Image will be no longer presented；The OCT average brightness figure of Figure 24 A is compared with the phase variance contrast image of Figure 24 B, and 5 times B- is swept It retouches.Each durection component carries out median filtering, radian variation range 0 to 3；The arrow of each image points out spine master pulse and axial direction The relevant region of blood vessel.Figure 24 B is phase change contrast image, and the same area of MB- scanning can be clearly observed, but It is since the variation of blood vessel refractive index has additional shade below blood vessel；

It is the phase contrast summary image of the slices across of grouper cardiac position in 2.6s shown in Figure 25.When each Between point collected in 50ms；Such method is equally used in Figure 17；Variation in blood vessel and heart can be visible in detail； It is the data image of the heart contrast changing value changed over time shown in Figure 26.The variation of contrast, with lithosporic in region The variation of fish normal cardiac rate and the changes in flow rate of viewing area are related；

It is the contrast for changing over time some lateral position of grouper shown in Figure 26；The contrast summarizes 3 horizontal pixel (7.2um) covers the entire depth of grouper；

It is the direct picture of grouper heart shown in Figure 27 A, 27B, 27C；Figure 27 A is that OCT intensity is total in logarithmic range And image；Figure 27 B is phase change summation image, improves visualization compared to Figure 27 C；Figure 27 B and quickly fertilization in 3 days The confocal images of grouper Green Fluorescent Protein have similar area；It is the grouper at the similar age shown in Figure 27 C The Confocal Images that injection fluorescent material generates in vivo, Figure 27 B movement contrast images show relevant blood-vessel image；

It is average OCT gray level image shown in Figure 28 A；

It is the doppler flow spirogram picture of MB- scanning mouse retina shown in Figure 28 B；The Doppler flow diagram of Figure 28 B Picture, does not use any threshold value, and variation range is+- 2.5mm/s.The main fast flow of the retinal vessel observed is axis To flow, but suprachoroid vascular flow is not observed using the image analysis technology；Figure 28 A shows a series of phases The phase change contrast image at position transformation period interval；Blood vessel (choroidal artery) can be improved by extending phase change time interval Visualization, but also increase the contrast shade below blood vessel simultaneously.The extension of time interval equally also increases transverse movement Sensitivity and vertical direction on contrast；

Figure 29 A is the phase change contrast figure of MB- scanning, time interval 40us, phase change 10；

Figure 29 B show MB- scanning phase change contrast figure, time interval 160us, phase change 40；

Figure 29 C show MB- scanning phase change contrast figure, time interval 240us, phase change 40；

Figure 29 D show MB- scanning phase change contrast figure, time interval 320s, phase change 40；Figure 29 A, It is the retinal images after flattening shown in 29B, 29C and 29D, is mainly used to elimination optical path change and causes mouse eyeball The influence of the variation of curvature.The flattening of retina and identification layer of retina separate confinement are two kinds of main extraction letters in image The method of breath, information extraction is in, with contrast-data, analysis acquisition data, formation is laterally in the depth areas of three dimensional grey scale image Or positive image；

It is the B- scan image before retina flattening does not rearrange shown in Figure 30 A；

It is the B- scan image after retina flattening rearranges shown in Figure 30 B；

Figure 31 A, 31B and 31C are the BM- scan image of mouse retina；

Figure 31 A is mean intensity scan image；Figure 31 B is phase change image, the image do not eliminate it is any mathematically Phase error, also do not filter；Figure 31 C is the phase change contrast image after noise is eliminated and after median filtering, is become Change range is 0 to 3 radians；

It is the direct picture of entire retina BM- scanning shown in Figure 32 A；

It is the positive phase contrast image of entire retina BM- scanning shown in Figure 32 B；

The direct picture of total intensity shown in Figure 33 A, Figure 33 B are the phase change contrasts of retina top half Image；The retinal vessel of the contrast image display surface of Figure 33 B, arrow meaning are the region of capillary；

The direct picture of total intensity of display depth shown in Figure 34 A, Figure 34 B are the phase changes of retina lower half portion Contrast image；The contrast image of Figure 34 B shows the shade contrast of choroidal blood vessel and main retinal vessel；Arrow Head meaning is the region of capillary；

It is that BM- scans positive summation gray level image shown in Figure 35 A, is the total phase in BM- scanning front shown in Figure 35 B Change contrast image.Figure 35 A is the image of entire retina, however the contrast image of Figure 35 B, only horizontal pixel are The image of 200 BM- scanning retina top half；The pixel of the single contrast image of Figure 35 B is 200*51, by entirely regarding The image of the independent scanning collection of the top area of nethike embrane.Arrow points out to be some lesser visible blood vessels；

Positive total phase contrast image shown in Figure 36 A, 36B, 36C and 36D, the BM- that horizontal pixel is 100 are swept The image of the top half for the retina that the mode of retouching acquires；BM- is used alone to system and sweeps some images of continuous scanning acquisition, this The pixel of a little images is 100*50, concludes therefrom that the contrast of part on retina is 100*100；Arrow marks some visible Capillary, but these blood vessels are because the intermittence of its contrast is not can all occur on other images；Image Transversal scanning region with Figure 34 A be with the region of 34B as；

Average contrast's image of two different acquisition method statistics for repeating BM- scanning shown in Figure 37 A and 37B, For the image of retina top half；Figure 37 A and 37B acquisition are the images for being orthogonal to main horizontal scanning direction.As Contrast images can be inferred that pixel size is 100 × 100.

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.

Embodiment one

The eyeground of one embodiment of the present of invention it is mobile to method for determination of amount, include the following steps：

As shown in Fig. 1-01, the eye fundus image 100 at T1 moment is obtained, the predeterminable area of the eye fundus image at T1 moment is selected to make For tracking image 110, tracking image image recognition information for identification and the position at tracking image T1 moment are obtained；

As shown in Fig. 1-02, the eye fundus image 200 at T2 moment is obtained, is found in the eye fundus image at T2 moment and tracking figure As the frame of the identical position in the position at T1 moment is as tracking frame 210；

A point to track frame establishes plane right-angle coordinate as origin, to track a point of frame 210 as reference point, Determine that reference point, will be moveable along horizontal axis and the moveable minimum spacing of vertical pivot along horizontal axis and the moveable maximum magnitude of vertical pivot Maximum magnitude is divided into multiple shift positions 220；

When calculating reference point traverses shift position according to vector (m, n) is mobile, the image recognition letter of T1 moment tracking image Breath and reference point track the related coefficient of the image recognition information of image in frame, the correlation when being moved to each shift position Mobile vector (the m of the corresponding reference point of the maximum value of coefficient_max,n_max) be the eyeground T2 moment relative to the T1 moment it is mobile to Amount, T2 moment are later than the T1 moment.

The determination method of the eyeground motion-vector of the present embodiment, firstly, from the tracking image in the eye fundus image at T1 moment, Two kinds of information are obtained, and one is image recognition letters tracking image and other parts image distinguished to identify Breath, another kind is tracking image in the position at T1 moment；

Then, the eye fundus image at T2 moment is obtained, at this time due to the movement on eyeground, the position of tracking image has been moved, In order to find the mobile vector of tracking image, need using tracking image in the position at T1 moment in the eye fundus image at T2 moment The frame of position identical with its position is found as tracking frame；

Later, tracking frame moves in its moveable maximum magnitude, calculates tracking frame and is moved to moveable maximum model The image recognition information of image is related to the image recognition information at tracking image T1 moment in tracking frame when enclosing interior every bit Coefficient, i.e., the degree of correlation of the image recognition information of two images；The corresponding tracking of the maximum value of the related coefficient is frameed shift dynamic To position be two images the immediate position of image recognition information, be tracking image the position being moved to；That is basis The image recognition information of tracking image finds the position of tracking image in the eye fundus image at T2 moment, as shown in Fig. 1-03.And it chases after The movement of track image be as caused by the movement on eyeground, therefore, the vector of the movement of tracking image be exactly the eyeground T2 moment it is opposite In the vector that the T1 moment is mobile.

In this way, the vector of the movement on eyeground can be determined very easily, improving can to the privileged site progress three-dimensional on eyeground Accuracy depending on being melted into picture.The every bit for realizing that tracking frame is moved in moveable maximum magnitude in actual operation is less It is real and unnecessary, while one region when tracking frame, it frames shift dynamic description to simplify tracking, introduces reference point, because This, will establish plane right-angle coordinate as origin using a point for tracking frame, to track a point of frame 210 as reference point, really Determine reference point along horizontal axis and the moveable maximum magnitude of vertical pivot, it will movably most along horizontal axis and the moveable minimum spacing of vertical pivot It is divided into multiple shift positions on a large scale.In this way, realizing tracking frame in the expression of the movement of its moveable maximum magnitude.

Selection for trace regions, can be there are many selection mode, as a preferred mode, the tracking image It is the region that center is in the eye fundus image at T1 moment.Tracking image positioned at center, convenient for tracking.

Specifically, the tracking image is the picture element matrix in center of the eye fundus image at T1 moment, with M × N It indicates, as in Fig. 1-01, using the pixel of the first row first row in picture element matrix as origin, the orientation of the first row pixel is cross Axis is positive, and the orientation of first row pixel is that vertical pivot forward direction establishes coordinate system, the horizontal axis coordinate i=0 of picture element matrix, and 1 ..., M-1；Vertical pivot the coordinate j=0,1 ..., N-1 of picture element matrix；In this way, pixel in picture element matrix M × N is with coordinate (0,1), (0, 2) ... (0, N-1) ... (M-1, N-1) is indicated.

Specifically, the pixel to track the first row first row in frame is established flat square as origin and is sat as in Fig. 1-02 Mark system, tracking the reference point of frame, according to vector (m, n), mobile and reference point traversal is each in the tracking moveable maximum magnitude of frame A pixel, i.e. each pixel are shift positions.

Specifically, the movement of tracking image is caused by being moved as eyeground, and eyeground movement is because of the eye movement of watching attentively property Cause.Reference point is determined along horizontal axis and the moveable maximum magnitude of vertical pivot by the eye movement of watching attentively property.Further, according to because The mobile moveable maximum magnitude m in eyeground caused by the eye movement of watching attentively property belongs to section (- 50,50), i.e. m ∈ (- 50, 50), n belongs to section (- 50,50), i.e. n ∈ (- 20,20), in this way, can calculate in the moveable maximum magnitude of tracking frame Shift position is 100 × 40=4000.At this point, 4000 cross-correlations can be obtained.Select cross-correlation maximum Corresponding vector (the m of value_max,n_max), precisely due to the vector of the movement on the eyeground that the eye movement of watching attentively property generates.

Specifically, preset cross-correlation formula is specially：

Wherein, x (i, j) is the image recognition information at tracking image T1 moment, and y (i-m, j-n) is reference point according to vector Image recognition information after (m, n) is mobile, mx are the mean values of x (i, j), and my is the mean value of y (i-m, j-n), and r (m, n) is tracking The intersection phase of image recognition information when the image recognition information and reference point at image T1 moment are moved to each shift position Relationship number, i=0,1 ..., M-1；J=0,1 ..., N-1.

Specifically, described image identification information is gray value.

It should be noted that the eyeground of the present embodiment be it is a kind of specifically can mobile sample, the movement on eyeground Determine in method, pertain only to that this characteristic may be moved, be not related to eyeground he manages it other, therefore, other can be mobile Sample can be applicable in above-mentioned determining method, i.e., the determination method of the movement on the eyeground of the present embodiment can extend be applicable in it is all Can mobile sample and the present invention extend to the mobile determination method of sample.

The principle that the determination method of eyeground motion-vector is described below derives：

In nature or human society, if two variables have certain connection on the size and Orientation of development and change System then claims related between variable.

Crosscorrelation is relevant one kind, it indicate two variables between while or non-concurrent correlation.For one-dimensional letter Number, cross correlation algorithm is the standard method for evaluating the correlation of two columns.Assuming that there are two columns x (i) and y (i), i =1,2...N-1, then two columns are shown in the following formula of correlation coefficient r (d) that delay is d：

Wherein, mx, my are respectively the mean value of two columns, and the value range of r (d) is [- 1,1], and r (d)=0 indicates two column Number is uncorrelated；R (d)=- 1 indicates two columns in maximum negatively correlated；R (d)=1 indicates that two columns are positively correlated in maximum.

The cross correlation algorithm of one-dimensional signal is expanded in two dimensional image, can be used for the knowledge of specific region feature in image Not and track.As shown in Fig. 1-04, a borderline region picture element matrix mark1 of the 1st width image is first taken, size is M × N.First According to the position of battery limit (BL) domain matrix mark1 inside the 1st width image in t (t>1) borderline region matrix is found in width image Mark2, then borderline region matrix mark1 moves frontier district domain matrix mark2 according to vector (m, n), such as Fig. 1-04 It is shown.

Then crosscorrelation is done to mark1 and mark2, shown in following formula：

Obtained r (m, n) is cross-correlation result.Find r maximum value r_maxCorresponding vector (m_max,n_max), then The vector that the region in t width image is moved for the 1st width image is (m_max,n_max), mobile horizontal distance is | m_max|, mobile vertical range is | n_max|。

Embodiment two

During carrying out three-dimensional imaging using means of optical coherence tomography, need to carry out OCT scan to sample Acquire data.

If sample be it is mobile, carry out the optical coherence tomography galvanometer system of OCT scan before and after sample is mobile Without correction, it will cause the camera lens of the optical coherence tomography galvanometer system of OCT scan to the position of Sample Scan It changes.Therefore, to can mobile sample, need to find the mobile vector of sample before scanning, accordingly adjust OCT scan Optical coherence tomography galvanometer system so that the camera lens of the optical coherence tomography galvanometer system of OCT scan is to sample Same position be scanned acquisition data, specific implementation is realized by the collecting method of embodiment two.

Implementation of the invention provides a kind of collecting method, includes the following steps：

Obtain sample sample image formed by the T1 moment, select the predeterminable area of sample image formed by the T1 moment as Trace regions establish plane right-angle coordinate as origin using a point of trace regions；According to sample sample formed by the T1 moment Product image determines the position of shooting test object, carries out first scan to shooting test object and acquires data；

Trace regions are determined in the moveable maximum magnitude of horizontal axis and vertical pivot of plane right-angle coordinate, along horizontal axis and vertical pivot Moveable maximum magnitude is divided into multiple shift positions by mobile minimum spacing；

It calculates trace regions and vector mobile according to vector (m, n) in its moveable maximum magnitude and traverses shift position When, the vector with the one-to-one trace regions in shift position；

According to cross-correlation formula, the position and trace regions where the calculating trace regions T1 moment are according to vector The cross-correlation of position after (m, n) is mobile, the vector of the corresponding trace regions of the maximum value of the cross-correlation (m_max,n_max) it is vector of the sample T2 moment relative to the movement of T1 moment；Wherein, the T2 moment is later than the T1 moment；

Optical coherence tomography galvanometer system is corrected according to the sample T2 moment relative to the motion-vector at T1 moment, Scanning collection data again are carried out to shooting test object.

In this way, reducing the mobile influence to optical coherence tomography galvanometer system scanning collection data of sample, improve The accuracy of optical coherence tomography galvanometer system scanning imagery.

Embodiment three

The embodiments of the present invention also provide a kind of using means of optical coherence tomography measurement dynamic contrast and estimates The method for counting lateral flow.

Utilize the method for means of optical coherence tomography measurement dynamic contrast and the lateral flow of estimation, the method packet Include following steps,

Data acquisition is carried out using the collecting method of embodiment two, wherein use optical coherence tomography system Multiple B- scanning collection data are carried out to sample, in the Multiple-Scan of transverse area, comprising each B- scanning, are carried out Data acquisition, data include at least phase information, strength information；

The determination of phase change data, wherein data of the determination of phase variance based on B- scanning collection, also, sample It moves contrast and depends on phase variance.

Specifically, wherein determining that phase change data include the following steps：Scanning primary to sample or even multiple utilizes The motion phase variance changed over time identifies and determines the movement of scatterer.

Specifically, determining the time fluctuation of the data of acquisition using optical coherence tomography system, and determine base In the movement contrast of time fluctuation.

Specifically, determining movement contrast in the variation of flow region estimation refractive index, while based on the above estimation.

Specifically, estimating that refractive index starts the time point changed and estimation in one or more phase contrast image The ingredient of refractive index in flow region.

Specifically, multiple B- scanning should include that MB- is scanned, BM- scanning, or both has.

Specifically, wherein optical coherence tomography system should include Fourier optical coherence tomography analysis system.

Specifically, wherein Fourier optical coherence tomography analysis system should include domain optical coherence tomoscan skill Art scans source optical coherence tomography scanning technique and optimal frequency domain analysis imaging.

A kind of method of the kinetic characteristic in different motion region in determining sample, including the following contents, make in multiple regions It determines the movement contrast of multiple regions in aforementioned manners, and identifies the kinetic characteristic in one or more region of sample.

Specifically, wherein one or more the moving region is defined as three-dimensional.

Specifically, wherein the movement 3D regions of one or more definition include the blood vessel of three-dimensional, target blood, Or both have concurrently.

A kind of computer executable command being used to determine sample motion contrast in optical coherence tomography analysis system Readable medium, which is characterized in that including the following contents：Multiple B- is carried out to sample using optical coherence tomography analysis system to sweep Acquisition data are retouched, wherein the scanning includes the data acquisition of the Multiple-Scan within the scope of transverse area；Determine phase variance Data, wherein the phase variance is to be determined based on B- scanning collection data, and determine sample based on phase variance Movement comparison；

A kind of optical coherence tomography analysis system, the analysis system include：

Computer-readable media with computer executable command is used to determine the movement comparison of sample；

Multiple B- scanning collection data are carried out to sample using optical coherence tomography analysis system, wherein the scanning Data acquisition including the Multiple-Scan within the scope of transverse area.

Determine phase variance data, wherein the phase variance be determined based on B- scanning collection data, and The movement contrast of sample is determined based on phase variance.

In the method that one of optical coherence tomography analysis system determines sample motion contrast, which is characterized in that institute The method of stating includes：Acquisition data are taken multiple scan to sample using optical coherence tomography analysis system；Determine statistical data Phase variance；Wherein the phase variance and intensity data are not related, and the movement pair of sample is determined based on phase variance Degree of ratio.

Specifically, one or many scannings include multiple B- scanning.

Firstly, introduce the embodiment of the present invention using means of optical coherence tomography measurement dynamic contrast and Estimate the background technique of the method for lateral flow：

OCT is a kind of optical image technology of non-intrusion type, can generate high-resolution by weak coherent light interferometer system The depth reflected image of the sample of rate.In various biosystems, OCT image can observe the three-dimensional structure of sample interior, It is that other imaging techniques cannot compare, not just for observing the retina of eyes.

The visualization of blood vessel and the quantitative information of blood flow are very important the diagnosing and treating of many diseases.? In OCT image system, Doppler OCT (Doppler OCT) technology for analyzing phse sensitivity is visualization of blood vessels and diagnosis Important form.Phase is a kind of method of high-resolution position that fathoms, and direction is the optics road along imaging system The direction of diameter reflection, is the cycle frequency of the light beam of optical source wavelength half.Wavelength is changing for the depth location of optical source wavelength half Change can generate same phase measurement.Phase change is proportional to axial flow.The flow component parallel with imaging direction is v (cos θ), v are the speed of flow, and θ refers to the angle of flow direction and light beam of light source direction.In system, it is based on local SNR Phase noise determine the smallest axial flow, prevent from limiting the visualization of flow when v cos θ is very small.Such as In retina, the direction of some flow directions and light source is almost vertical, then θ is equivalent to 90 degree, cos θ is equivalent to 0.At this In a little situations, the speed of flow very high could in this way must could be visualized flow.

The developing direction of OCT mainly towards fast imaging techniques develop, at the same time to more large area carry out at Picture.In order to obtain quick image taking speed, some continuous depth method for reflection are used only in Doppler OCT image technology, referred to as For A-scans (typical number is about 5), be averaged phase change wherein.Between A-scans and phase measurement, have The statistical data of limit and the smallest axial flow being able to observe that almost is limited in the short time, can only to most fast flow into Row visualization.

In response to this, the phase variance being computed on image does not increase additional movement contrast.Lack volume Outer contrast is because of phase transformation error, and local signal-to-noise ratio has dominated the calculating of the phase variance of all areas, in addition in phase Traffic visualization region with speed uses Doppler OCT technology.

Speckle analysis is conceived to the change of image intensity, is proved to limit normal work in the field OCT.In OCT, greatly Part is all towards this direction about the work of speckle, reduces the artifact of the multipath reflection generation of sample interior to promote image Quality.From the point of view of the image of a single static, identification flow region is gone in the change that space density is utilized in speckle analysis technology. These technologies are merely able to analyze the region higher than image spatial resolution, and in the case where no OCT image distinguishes depth Typically apply.In consideration of it, it is necessary to propose a kind of accurate effective mode in the field OCT to determine the stream of biofluid It measures to carry out the diagnosing and treating of disease.Particularly, in OCT system, need to develop a kind of method to estimate lateral flow speed Contrast is moved with determining.

In order to deepen the understanding of the present invention and recognize, the present invention is made into one with reference to the accompanying drawings and detailed description Step description and introduction.

The further application of this method is OCT image momentary fluctuation intensity.OCT image momentary fluctuation intensity can by with The flow and absorption variations within the scope of sample depth are observed as the contrast of other forms.

These methods and techniques show movement contrast in OCT image.Move contrast, especially phase change pair Nanoscale Blang diffusion motion and the movement of other nonfluids can be observed than degree.Phase change contrast can be used to distinguish not With the moving region of movement contrast, while the property of scattering movement can also be determined by phase information.For flow region, Described analysis method can identify different zones, can also characterize kinetic characteristic.Quantitative flow estimation can determine stream Amount, the independent, direction relative to imaging direction.The shade and cymomotive force of phase change contrast, which calculate, to be used to determine flow area The variation of the refractive index and absorptivity in domain.

Described herein is a kind of inefficient, advanced IT application diagnostic method, and is that efficient three-dimensional is swept Retouch acquisition method.Efficient method can make moving region three-dimensional visualization, such as the blood vessel of sample.The spirit of these inventive methods Activity is to identify intermittent flow region, such as identifies the movement of erythrocyte in fine vascular.This identification interval Property blood flow region ability assisted diagnosis and patient in need can be treated.

Invention also contemplates that the equipment that a kind of computer is executable, for determining the movement contrast of sample.The computer Executable equipment carries out primary or even multiple scanning, acquisition phase delta data to sample using OCT equipment, and determination is based on The movement contrast of phase change.The further application that equipment can be performed in the computer is that acquisition cymomotive force or speckle information come Determine the movement contrast of sample.The phase variance changed over time can identify and determine the movement in OCT sample image and dissipate Beam.The executable equipment of computer shows motor area and quantitative Diagnosis scatterer with screen.

A kind of OCT equipment including the equipment of computer executable command determine sample movement contrast be also considered including. Primary or even multiple scanning is carried out to sample including the OCT equipment that equipment can be performed in computer, acquisition phase delta data determines Movement contrast based on phase change.Further applying comprising the OCT equipment that equipment can be performed in computer is acquisition cymomotive force Or speckle information determines the movement contrast of sample.The phase variance changed over time can identify and determine OCT sample Mobile scatterer in image.Motor area and quantitative Diagnosis scattering are shown including the OCT equipment screen that equipment can be performed in computer Body.

The detailed description of invention：

The OCT system herein proposed is a kind of spectral domain optical coherence tomography (SDOCT), and step is as shown in Figure 1, optical fiber Light beam is divided into reference arm and sample arm by interferometer.Acquisition described herein and analytical technology are independent of the OCT used System, only related with the speed of the depth of each sample reflection, intensity and phase, referred to as A-scan.

Phase change ΔΦ (z_i, T) and it is depth z_iWith the function of time interval T, in conjunction with influence factor once：

ΔΦ(z_i, T) and=ΔΦ_{motion,scanerer}(z_i,T)+ΔΦ_motion,bulk(T)+ΔΦ_error,SNR(z_i)+Δ Φ_error,other(z_i)

Phase change ΔΦ (z_i, T) not only only include depth z_iΔ is used in the individual scatterer movement at place Φ_{motion,scatterer}(z_i, T) define, but it is same include whole fluids between sample and system axially phase To movement ΔΦ_motion,bulk(T)。ΔΦ_error,SNR(z_i) it is depth z_iLocate the phase error of the SNR data calculated.It has delivered Experimental result is verified to go out to test accuracy of the noise than determining measurement phase change of local signal：

ΔΦ_error,other(z_i) it include other phase transformation errors, these errors are probably derived from the measurement of OCT phase, but It is not limited to transversal cross-section scanning error, the transverse movement of sample, or is limited to the sample axial movement production of sampling depth Raw artifact.In order to identify the movement ΔΦ of scatterer_{motion,scatterer}(z_i, T), need to eliminate or reduce other shapes The influence of the phase noise of formula.The depth of sample reflects the fluid motion between the other parts of imaging system, and it is every to calculate it One phase.Independent measurement phase change is the mass motion that impossible distinguish sample and system axial and individual independently movings Moving region.The influence of mass motion is not eliminated, the smallest movement that can be measured of sample will be by the fluid of system Mass motion and sample motion are limited.

One of them may be used to determine the method for the relative motion of sample fluid, exactly be set using additional motion measurement It is standby, such as interferometer, for determining allocinesis most strong in sample.Fourier optical coherence tomography system, packet Tomoscan containing domain optical coherence and swept-source optical coherence tomography scanning (reference optical frequency image), sample it is all Depth information is measured in the same time.All depth reflective informations can pass through phase change information acquisition, it is more likely that Eliminate the relative motion of fluid.

In some cases, in order to eliminate relative motion, a branch of strong reflected light of sample is used as fixed ginseng The reflected light examined.Many examples do not use the fixed reflector of high reflectance, therefore the depth of entire sample must be used to Calculate fluid motion.There are several methods that can calculate sample fluid movement from all depth analysis phase change information.With The relevant big phase noise of depth does not reflect or signal is near the grade of noise, due to these low signal conditionings, The average value of all phase changes can be distorted.The Threshold Analysis of phase data can reduce the influence of these modes.Phase becomes The calculating mode of change also can be used for determining that fluid motion, and the parameter by calculating mode can accurately calculate fluid Movement.

Weighted average calculation allows the fluid motion to some sample examples to estimate.Fluid motion in this method Calculating be summarized as ΔΦ_motion,bulk(T)=∑ [w (z_i)ΔΦ(z_i,T)]/∑[w(z_i)], weighted factor w (z_i) depend on In imaging contexts.Weighted factor is by linear OCT intensity I²(z_i) determine, the intensity is most strong dependent on stationary sample interior Reflection.Use OCT amplitude I (z_i) weighted factor, in testing can be sensitiveer to the phase noise of low frequency signal.By threshold Value brings weighted factor into, and the influence of the phase transformation noise of low frequency signal will gradually reduce in many cases.Weighting pattern includes Spatial coherence handles special sample and kinetic property.For example, the sample fixed area under high speed flow velocity measures phase Variation will appear unstable condition, this weighting for just needing to occur different in sample, or is higher than flow region or is lower than flow region Domain.Weighted factor also may include the weighting of the shape of local strength's variation of depth reflection.The secondary lobe of reflectance spectrum and inclined Phase motion, which can generate artifact, leads to undesirable difference, which can result in the distortion of the estimation of the relative motion of fluid.

Because of the periodicity of phase measurement, phase change section is that-π arrives+π.It moves section and (is equal to light than this range The a quarter of source bandwidth) greatly, jump, which occurs, for phase interval causes to calculate wrong (phase change+π+δ is mistakened as work-π+δ).? In phase test example, the fluid motion phase of sample is similar to +/- π, and phase error will will lead to calculated phase change It is distributed similar with the data presented in Fig. 2.The phase change distribution for not having additional correction to cross, the phase interval calculated It may be incorrect.Before the movement of fluid as stated above occurs, the distribution of phase should be zeroed again, so that Average value more accurately embodies motion state.

From calculated phase change ΔΦ (z_i,T)-ΔΦ_motion,bulk(T) fluid motion of estimation is eliminated in, always Quantity the summation of variance that changes close to single factor of variance：

σ_ΔΦ ²(z_i, T) and=σ_{ΔΦ,motion_scatterer} ²(z_i,T)+σ_{ΔΦ,SNR_error} ²(z_i)+σ_{error_other} ²(z_i)

The source spent as a comparison, phase change analysis target is scatterer motion phase version σ_{ΔΦ,motion_scatterer} ²(z_i,T).Limit the phase transformation variances sigma of SNR_{SNR_error} ²(z_i) it is to be determined by the noise ratio of local signal , which is independently of the time interval T's of phase test.The factor σ of last phase change_{error_other} ²(z_i) and other Phase error factor it is all not related, mostly come from fluid motion calculation method error and other various Δs Φ_error,other(z_i) influence.The phase error for being limited to SNR generally will limit the visualization of scatterer movement.

The phase measurement moved by scatterer, the part component of many forms of motion can be observed, still It is not limited to following component：

The variation of axial flow component；

The influence of the lateral flow of incoherent scatterer；

The axial component of Production of Brown Type of Ammonia random motion；

The entirety of incoherent scatterer is static to influence that (multiple scattering body can be positioned in the high-resolution image of system And can identify the position of single scatterer).

The variation of the movement of each above-mentioned form, phase increase with the variation of time interval.In big portion In the case of point, the limiting factor for influencing to observe most weak scatterer movement is that the phase that each SNR relevant to reflection is limited is missed Difference.Because this phase variance independently of the time, waits the longer time in test, the phase change for allowing scatterer to move is more than The limits value of phase error.Further extending time interval will continue to improve measurement phase variance ability.This process will be after It is continuous to be similar to the degree of the phase signal of completely random until phase change process reaches.The further enhancing of scatterer movement will The phase variance of test will not be made more than the phase signal of completely random.

The wherein influence of one side is that lateral flow has longer time interval, causes to will appear fortune below flow region Dynamic shade.Caused by this is the refraction effect as lateral flow region.In OCT the test of phase it is remarkable be based on to The change of fixed reflector locations, it is the change of optical path.Therefore, in entire period of time T, pass through reflected light measurement Also the variance of all refractive index is measured while all depth of sample.

The reflector fixed for one, in average refractive index variableUnder, extend depth z_n, calculating Phase change is：

For example, going a kind of method for creating complete random phase test, 15 microns of blood vessels below are measured with this method Blood flow, by the wavelength of light source close to for 800nm, the minimum average B configuration refractive index variance needed is：

By understanding time point and flow region folding generating shade by variations in refractive index in phase contrast image The knowledge of rate is penetrated, lateral flow and traffic intensity variance are to can determine.Correspondingly, flow region refractive index variance is estimated to be Help determine movement contrast in OCT system.

In order to prove that movement variance increases with the increase of time interval, proved as an example with Brownian movement.2% Agarose well be added in Intralipid fat emulsions injection, be diluted strong for the movement that matches agarose scatterer Degree.Agarose is gelatin, is stable for the Fat Emulsion scatterer of movement.

The different image-region of different time intervals, phase change calculate phase variance.Fig. 5 A, Fig. 5 B, Fig. 6 A, figure Since 6B, Fig. 7 A, Fig. 7 B are shown testing imaging system shortest time point, and time interval continuously increases.The shortest time The imaging of spaced phases variance is controlled by the phase noise of signal-to-noise ratio.It as time increases, include that mobile English is de- in region The phase variance calculated value of the special fat emulsion injection of benefit also increases.

In order to which scatterer movement contrast is preferably imaged, need to eliminate the phase noise of signal-to-noise ratio.Wherein one Kind method is the phase variance using different clock interval T1 and T2.If we can assume that other phase errors are can With what is ignored, the phase variance of different time intervals calculates as follows：

σ² _Δφ(z_i,T₁)≌σ² _{Δφ,scatterer}(z_i,T₁)+σ² _Δφ,SNR(z_i)

σ² _Δφ(z_i,T₂)≌σ² _{Δφ,scatterer}(z_i,T₂)+σ² _Δφ,SNR(z_i)

T is set₂=β T₁, β is much larger than 1, it is assumed that the variances sigma of the scattering movement in system² _{Δφ,scatterer}(z_i,T₂) be much larger than σ² _{Δφ,scatterer}(z_i,T₁).Under these conditions, the basic phase contrast standard for the imaging of phase variance contrast It is σ² _{Δφ,scatterer}(z_i,T₂)-σ² _{Δφ,scatterer}(z_i,T₁) as follows：

σ² _{Δφ,scatterer}(z_i,T₂)-σ² _{Δφ,scatterer}(z_i,T₁)≌σ² _{Δφ,scatterer}(z_i,T₂)

Know the phase noise of the signal-to-noise ratio of form known, the mathematic expectaion inside Numerical value can be used for eliminating in image Phase noise.Noise of the Numerical value of phase noise based on the intensity for reflecting signal in OCT and the imaging system described before Feature.Based on the accuracy of the estimation to noise, this situation creates the images of similar contrast.

With the variation of time, phase variance can describe the kinetic characteristic of scattering movement.It is that observation is different that Figure 10, which is shown, The data of the time point various sizes of particle phase variance of Brownian movement in water, the diameter of an independent scatterer becomes in water Changing range is from 0.5 μm to 5 μm.Due to heat fluctuation, phase variance data can be used to analyze, and visualize to random motion.In advance Phase, these scatterers needed to calculate variance as time change variance is equal to zero movement to be imaged.0.5 μm of diameter is to 5 μ The particle of m moves the very bright sense of OCT signal strength relative to scatterer, these phase errors can be ignored.For diameter 2 μm of particle, in the case that OCT signal is very weak, phase error cannot ignore.It is expected that forms of motion need with Other forms of motion compare, and Figure 10 shows the phase error in conjunction with forms of motion.Phase changes with the variation of time, The data of enough phase variances are acquired, exercise data can be therefrom extracted.

For Brownian movement, the phase variance data (few many relative to random phase variance data) of measurement are tested The relationship such as following formula of the forms of motion of amount and the Brownian movement for changing over time little phase error：

σ_Δφ ²(z_i, T) and=A²+DT^γ

In order to make the phase variance of measurement reach desired value with the variation of time, (diffusion is normal for the kinematic parameter of scatterer Number) D can determine its size.

Collecting method：

It goes to identify or mark sign moving region to acquire more data, time interval must long enough.One most simple Single method is waited in each lateral position, with time change, is obtained phase information, is waited long enough for adopt The transformation information of statistical data and the variation with the time needed for collection.For the scanning technical term of OCT, A- scanning is needle The method that reflection measurement depth is utilized to single position.As the variation of time is in the multiple A- scanning of the same cross-section location Referred to as M- scanning.Multiple A- scanning is referred to as B- scanning in entire cross-sectional extent.In the mistake that each cross-section location waits Journey generates M- scanning, and the duplicate M- scanning in cross-sectional extent is referred to as MB- scanning.

MB- scanning is earliest statistical data and phase change in order to characterize the kinetic characteristic of scatterer to acquire required The method of information.The description of this feature includes that the flow of the flow region along imaging direction and cross-sectional direction is quantitative.Other Characterization information includes some factors, including diffusion constant, scatter density and traffic flow information.Unique limit of this method System is to acquire the low efficiency of data.The time needed with the method to the visualization of moving region 3 D stereo is too long.For some Phase variance contrast visual one quick acquisition method is to need to scan bigger three-dimensional space.It is in the same localities The passage of waiting time until three-dimensional space it is sufficiently large come generate movement variance contrast, not as good as return to original position it Before, additional phase information is obtained by scanning multiple positions.Over time, multiple B- is carried out in same cross section The method of scanning is referred to as BM- scanning.

In a long time interval, BM- scanning is a kind of efficient without sacrificing any image acquisition time Phase information acquisition method.This scan method is restricted in time, but for the data of continuous A- scanning collection The sightless slow movement of analysis, this scan method are visible.Compared with MB- scan method, this scanning side Method is limited the quantitative analysis of flow.Some examples of these acquisition methods are shown in Figure 11 A, Figure 11 B.

The figure that the tail of zebra fish is scanned by MB- scanning and BM- is shown in Figure 12 A, Figure 12 B and Figure 13 A, Figure 13 B Picture.However in both figures, the same region of phase variance contrast image identification, the contrast that BM- scanning generates is MB- 4 times of scanning.It is as expected that sweep time used in BM- scanning is 40 times of MB- scanning sweep time used.From comparison The phase variance contrast image that degree figure can be seen that BM- scanning has shade, this is because time interval is too long to lead to flow region Domain exponentially changes.

The same area for the identical sample that Figure 12 A, Figure 12 B and Figure 13 A, Figure 13 B are shown.In entire imaging time, BM- scanning includes about 2.5 times of horizontal pixel, and being compared to MB- scanning reduces 3 times.BM- sweep time can be further It reduces, by the adjustment of the quantity of lateral position, the adjustment of the statistical data for calculating phase change information variance can subtract The time of few A- scan collecting system and the ability for improving system transversal scanning.

Transverse flow appraisal procedure：

The research achievement that Park et al. is delivered shows between continuous phase measurement, when the incoherent of transversal scanning The a part of the reflection light of sample as light beam of light source, desired phase error will appear.According to the definition of Park, phase difference Standard deviation be equal to phase difference square root.

In order to create phase contrast within shortest sweep time, the analysis of Park is the result is that scan it in continuous A- Between determine the restrictive condition of phase contrast, transversal scanning creates B- scanning simultaneously.It is reflected in sample irradiation and sample Between, a possibility that using quantitative predication of this desired phase error as transverse movement flow for opposite transverse movement is that do not have Have and is mentioned to.

If multiple A sweeps are separately carried out in same lateral position, due to sample irradiation and sample in period of time T Relative lateral motion between reflection will will appear phase noise.In continuous measurement process, in same cross-section location, similarly Light-source brightness, noise mostly come from lateral flow, particularly from incoherent reflection, such as find in blood similar Noise.Consider a Gaussian beam in focal point 1/e²Width of light beam=d, the at the same time identical lateral position of cycle T Use Method for Phase Difference Measurement.At the same time in cycle T, phase change variance is determined by the transverse movement of scatterer Δ x , by lateral movement velocity V_xIt generates.The bandwidth for defining light beam is Δ X/d, the side of the phase error as caused by transverse movement Difference calculates such as following formula：

Due to errors other during phase measurement, the accuracy of this technology depends on the standard of the calibration standard of system The elimination of true property and other forms phase error.In terms of the data that Park result of study is shown, the quantitative predication of lateral flow Dynamic range is about 20%≤Δ x/d≤80%.The smallest lateral velocity of phase noise limitation of signal-to-noise ratio limitation can be used should Method measurement.The random phase noise signal of the upper limit close to saturation limit value is only limitted between-π and π.This equation only allows For quantifying for flow, such as V_x>~0.8 T/d.The dynamic range of lateral flow measurement can be improved in the extension time.

By taking retina image-forming as an example, time interval is 40 milliseconds, 20 μm of the diameter of focus on light beam, and quantitative transverse direction flow moves State range is about 0.1mm/s to 0.4mm/s.

The dynamic range for changing flow can be realized by changing the lateral resolution of imaging system, or be surveyed by changing Measure period of time T.For example, beam diameter is 30 μm, lateral flow if the time cycle of retina image-forming is 10 milliseconds If dynamic range be about 0.6mm/s to 2.4mm/s. in this case, the statistical data of phase measurement be it is enough, sampling Period is that 10 milliseconds of phase data can also be used to calculate phase variance (the measurement phase bits per second that the sampling period is 20 milliseconds It sets).The dynamic range of quantitative flow measurement will increase by 2 times, and dynamic range in this case is about 0.3mm/s to 2.4mm/ s。

The method for determining lateral flow second is, due to the variation of the refractive index in lateral flow region, flow in image Low place can generate artifact.If occur time point it was determined that the depth bounds of flow region it was determined that in region Refractive index mean change can also determine.By the knowledge of the refractive index of scatterer in flow region it is found that lateral flow rate is It is confirmable.This method is likely to be useful in the case where in flow region including a plurality of types of ingredients, such as blood plasma With the blood flow of blood vessel in haemocyte.

The method of the lateral flow of another quantitative measurment sample is combined with BM scanning and MB scanning.BM scans phase Variance contrast is a kind of method of efficient mobility for identifying the 3D region in sample.It is scanned, can be identified using BM- Three-dimensional blood vessel, the flow direction relative to imaging direction can be scanned with this.MB scans the blood vessel and selectivity that can identify target The flow of ground analysis specific region.Average axial flow depending on average phase variation can be with the flow in determining area.It is logical The method for crossing screening determines position, and MB scans increased statistical data, and small-sized axial direction flow component can calculate.Known blood The blood flow direction of pipe, endovascular blood flow can be calculated with geometry.The phase variance changed over time can lead to The estimation for crossing lateral flow component provides the calculating of additional correlative flow.

Transverse movement noise is eliminated：

One proposition relevant to acquisition method is the additional noise along with the growth of time.It is more when giving scatterer Time it is mobile, that is, sample obtains more times to move.The axial movement of sample is by previously described fluid The removing method of movement is eliminated.The transverse movement of fluid is not the supplement of previous methods.Illustrated in document, sample and at As the relative lateral motion between light beam generates what a phase error was determined by the size of the waist order of magnitude of imaging beam【1】. The derivation of phase noise is based on scatterer irrelevant in sample it is assumed that due to the reflection inside the layer of sample, is not institute Some phase noises can derive in this way, such as retina.

Figure 14 A, Figure 14 B show the OCT image of Mouse Retina slice, compared with phase variance contrast image Average OCT signal strength image.This contrast image has used Numerical value to eliminate in signal-to-noise ratio phase noise and application Value filtering is further reduced artifact.In the image of contrast, moving region is it can clearly be observed that include the retina of top Blood vessel, the additional shade of artifact and bottom below blood vessel generated below without the choroidal artery of any OCT signal. There is a small amount of fluid that transverse movement occurs in the image of this contrast, in sample.Figure 15 is not the phase side of that example Poor contrast image is the image that big transverse movement later acquires when occurring in retina at same cross-section location.? In this image, zone flow visualization is still possible, but a certain number of additional noises hinder visualization.

This method assumes that whole image contains the lateral position of all BM scannings for treatment fluid transverse movement The additional phase noise of phase same level.Since BM- scanning is all to scan all lateral positions in a short period of time to acquire number According to all these points should undergo identical movement, generate identical phase noise.After the phase noise of signal-to-noise ratio is eliminated, All contrast-data points are not zero, the influence that the statistical data of picture contrast can be used to attempt to eliminate transverse movement. For the average value mu and standard deviation sigma of the non-zero contrast-data of image, picture contrast C (x, z) can pass through many method tune Whole includes null method and method for normalizing：

In this case, maximum phase of 3.3 radians as phase variance contrast value, as the measurement of a random phase Prestige value.Parameter alpha is adjustable, for improving the visualization of some regions, these regions be possible to because phase noise and It disappears.Image after above-mentioned additive phase is removed in the case where Figure 16 A, Figure 16 B display α=0.

The removal process of noise in retina contrast image is shown in Figure 17 A, Figure 17 B.Each two-dimensional contrast Image summarises entire sample depth and is described as an one-dimensional straight line.The image superposition of multiple acquisitions forms the sample The two-dimentional contrastographic picture of product.The vertical line that left image is shown shows that scanning contrast image in that time point BM volume occurs Outer movement contrast noise.Contrast image in the case that α=0 is shown in right image, after transverse movement elimination.Figure As the variation of position in medium vessels is due to caused by occurring transverse movement in imaging process.

The estimation method for eliminating phase noise for number in phase contrast image is based on the anti-of measurement phase noise Penetrate signal S².OCT strength signal I²It is reflection signal S²With noise signal N²Combination.The form of average OCT strength signal is such as Under：

Figure 21 describes the relationship of measured phase noise and desired form.Work as S>>N, phase noise are shown Expected form as previously described.

The method that others are used to eliminate transverse movement noise includes going to eliminate contrast figure using additional statistical data Any transverse movement noise for including as in.Use an external motion tracker or OCT intensity and contrast image Software is analyzed, BM- scanning can identify and eliminate apparent transverse movement.When less transverse movement occurs, same Region repeats BM- scanning collection and is able to satisfy the requirement for eliminating phase analysis processing.

Intermittent flow identification：

The challenge of one movement contrast screening is to identify the region for all not including scatterer in all time intervals. OCT needs measure phase according to the reflection in sample, but in some cases, it is not that the phase of any time all allows to be tested Amount.Requirement for sample reflectivity, zebra fish and segmental vessels are good examples.The segment of embryo after fertilization 3 days Blood vessel diameter is 7-12 microns, one of them big vessel branch is referred to as aorta dorsalis.The confocal imaging of embryo shows that blood is thin Born of the same parents whithin a period of time can be in specific position.If the cross-section location that OCT image just scans does not have haemocyte, blood There will be no enough reflection signals in pipe to generate phase contrast signal.

Figure 18 shows several OCT images, is same cross-section location in different time points, from the tail of zebra fish to its ovum The OCT scan image of yellow capsule scanning.All arrows specify desired position in flow region in image：Aorta dorsalis (DA), axial vein (AV), segmental vessels (SE) and back side stringer blood vessel (DLV).The position of these flow regions is in OCT intensity It is unobvious in image, it is that the intensity contrast and these thin vessels due to lacking these regions lack enough absorptivities.Back Aorta and axial vein all occur in all images, but segmental vessels and back side stringer blood vessel are not whenever all to go out It is existing, result as expected.

It also include very small blood vessel in retinal microvasculature, and not in institute's having time similar to such case Point is all comprising movement contrast.For any chance phenomenon, the increase of multiple visualization chance and statistical data can be helped whole A incident visualization.BM scanning collecting method is high-efficient, and the region of sweep time intermittent flow to be had is repeated with the method, such as micro- blood Pipe, in order to move the visualization of contrast.

Intensity, speckle contrast：

Up to the present all comparative analysis methods all refer to the phase variance of scatterer changed over time.With identical Acquisition method, while also having available OCT intensity information data as time goes by.The property of many samples can cause The fluctuation of image：Such as the variation of optical coupling, power-supply fluctuation, and changes over time polarization variations opposite in interferometer and be ok Cause to fluctuate.The example fluctuated caused by the movement of sample includes, but are not limited to：

The reflection interference of multiple obstacles in the resolution ratio of system, as what intravascular independent small scatterer reflected does It disturbs.

Variance variation based on the reflective portion changed over time in flow region.

Over time blood flow region absorptivity variation.

Over time, the fluctuation of intensity and/or speckle analysis can analyze phase from identical acquisition data simultaneously Position variance.Assuming that there are the transverse movement of the fluid of high speed in sample, intensive analysis is more useful for identification flow locations. The analytical technology of one available strength information at that time is OCT intensity variance.In order to which variance contrast is reasonably imaged, As a result, strength information must standardize (for example, average value, median, maximum or the smallest intensity value).That has announced is strong Degree fluctuation and/or spot-analysis technology using normalization space wave in single image, limit contrast figure as a comparison The spatial resolution of picture.In one period of time T, Strength Changes variance will identify the contrast in moving region and absorptivity Change (above-mentioned).The strength fluctuation (for example, couple variations) of above-mentioned system can also cause pair of static region in image It is observed than degree.One method for attempting to reduce this unnecessary fluctuation is using based on OCT intensity and sample structure It is expected that the Numerical value of fluctuating range.The form of fluctuating range of one of which estimation is：

The time-domain information analytical technology of another fluctuating range is to determine that the time domain of fluctuation is distributed using Fourier transformation.Fu In shape, bandwidth and the amplitude information of frequency spectrum of leaf transformation to can be used to identify multiple mobility parameters include but is not limited to scatterer Average diameter and diffusion constant.

Shown in FIG. 1 is the frame diagram of SDOCT system.Low-coherence light source S (k) is divided into reference arm and sample by fibre optic interferometer Product arm.Reflected light is assembled and is tested in spectrometer, so that the depth of reflection profile is computed；Shown in Fig. 2 is radian For the phase change data of the simulation of the fluid mass motion of π (a quarter of imaging source wavelength)；Shown in Fig. 3 is movement Scatterer expected phase variance test result figure whithin a period of time；Fig. 4 A shows non-average with sample in Fig. 4 B The relevant overview diagram of OCT intensity image；In order to obtain this image, 2% agarose well is dissolved into the rouge that density matching is 0.1% In fat milk solution；Luminance contrast is confined to the edge of flowing and the boundary of air in image；Fig. 5 A be period of time T= The phase change figure of 40us；Fig. 5 B is period of time T=80us phase change figure；Fig. 6 A is period of time T=200us phase Position variation diagram；Fig. 6 B is period of time T=400us phase change figure；Fig. 7 A is period of time T=800us phase change Figure；Fig. 7 B is period of time T=1.6ms phase change figure；

Fig. 8 A is the phase change comparison diagram of maximum phase transformation period cycle T 2=40T1；Fig. 8 B is maximum phase variation The phase change comparison diagram of period of time T 2=20T1；Fig. 9 A is the phase change of maximum phase transformation period interval T2=10T1 Comparison diagram；Fig. 9 B is the largest the phase change comparison diagram of phase change time interval T2=5T1；Shown in Fig. 10 is single in water The phase change data of a scatterer；Shown in sphere diameter be respectively 0.5um, 2um and 5um.Diameter is that the sphere of 2um proves The influence of phase error, is primarily due to OCT signal in the phase change data of desired form weak；Figure 11 A shows The image of the lateral scanning pattern of MB- scanning；The image of the lateral scanning pattern of the scanning of BM- shown in Figure 11 B；Shown in Figure 12 A Be the zebra fish tail obtained using MB- scanning mode OCT gray level image；It is using MB- scanning mode shown in Figure 12 B Obtain the phase change contrast image of zebra fish tail；The size of image is 900um*325um.T2=1ms, T1=40us； It is the OCT gray level image of the zebra fish tail obtained with BM- scanning mode shown in Figure 13 A；It is using BM- shown in Figure 13 B The phase change contrast image for the zebra fish tail that scanning mode obtains；The size of Figure 13 A and Figure 13 B image is all 815um* 325um；Phase error in Figure 13 B has been eliminated, and the period of time T 2 of contrast image is estimated as 40ms；It note that phase becomes The areas imaging size for changing contrast image is 4 times of the contrast image that MB- shown in Figure 12 B is scanned；It is shown in figure 14 A It is the average brightness image at the time point that low speed transverse movement occurs, the image sources are in the BM- retina scanned The data of transverse movement；It is the phase contrast image after noise elimination and median filtering shown in Figure 14 B, derives from retina The BM- scan data of transverse movement；Figure 14 B is that there are the phase contrast images at the time point of a small amount of fluid transverse movement；Figure It is the phase change contrast image of uncorrected a large amount of fluid transverse movements shown in 15；Figure 16 A and Figure 16 B are one group of phases The comparison diagram of contrast image；It is that uncorrected there are the images of a large amount of transverse movements shown in Figure 16 A；It is α shown in Figure 16 B In the case where=0, the image of corrected a large amount of transverse movements；Figure 17 A and 17B are by the collected retina depth of 2.6S Contrast summarize image；Figure 17 A is the image before α=0 without overcompensation；Figure 17 B is after α=0 through overcompensation Image；It is that BM- scans average OCT grayscale image shown in Figure 18 A；Figure 18 B, 18C, 18D are three phases of different time points Change contrast figure；Each image is collected within 50ms.The region that arrow is directed toward is spine longitudinal direction angiosomes, two The different segmental vessels (Se) of kind, spine aorta (DA), axial vein (AV)；Be shown in Figure 19 A and 19B 3 days quickly by The OCT visual image of the zebra fish of essence；Figure 19 A is the MIcrosope image in the bright visual field, and Figure 19 B is 3 days lithosporics being quickly fertilized The image of fish all illustrates the anatomical features of desired grouper；The line drawn in Figure 19 A and 19B represents sweeping for OCT image Retouch region；Further analysis average flow rate and phase change are able to ascend the quality of these images；The OCT grayscale image of Figure 20 A As illustrating the internal structure of grouper in Figure 19；It is the blood flow of endocardial shown in Figure 20 B, this image decreased figure Phase noise and OCT image pixel as in；Phase contrast image after the elimination phase error influence of Figure 20 C description；Figure 20 B The appearance of heart, the region expected in the flow direction and Figure 19 B of the yolk bag that arrow direction shown in Figure 20 C refers to clearly are described Match；It is the schematic diagram relative to the direction of the flow in imaging source direction shown in Figure 21；It is observed using Doppler OCT technology The axial flow component arrived uses V_zCalibration；The phase noise and average OCT strength signal of SNR- limitation is shown in Figure 22 Relational graph；Pair of the grouper tail generated shown in Figure 23 A, 23B, 23C and 23D using the data that MB- scanning mode acquires Than degree image；Figure 23 A is the gray level image of structural information；Arrow in Figure 23 A points out the desired region detected, the region It is main two blood vessels of fish, spine artery and axial blood vessel；Figure 23 B is phase change contrast images, and the time cycle is T2= 1ms and T1=40us, radian change from 0 to 2, observed region be on Doppler OCT image it is sightless, Doppler OCT can only observe sufficiently stable static region.Arrow in Figure 23 B points out the desired motor area observed Domain.Figure 23 C is Doppler flow image, and the scope of application is+- 0.12 radian=+ -200um/s, and phase change average value is 5； It is Doppler flow image shown in Figure 23 D, the scope of application is+- 0.12 radian=+ -200um/s, and phase change average value is 100.More and more stable static characteristic improves visual quality, and the position for understanding each section in advance is conducive to visually Research；It is the same area of zebra fish in Figure 23 A, 23B, 23C and 23D shown by Figure 24 A and 24B, is swept however, using Retouch the BM- scanning mode that time interval is T=10ms；In order to select best parameter, the image data of 200 horizontal pixel is acquired Time used is 50ms；Due to reducing the dynamic range of Doppler OCT method acquisition data, the image acquired using this method It will be no longer presented；The OCT average brightness figure of Figure 24 A is compared with the phase variance contrast image of Figure 24 B, 5 B- scanning.Often A durection component carries out median filtering, radian variation range 0 to 3；The arrow of each image points out spine master pulse and axial blood vessel Relevant region.Figure 24 B is phase change contrast image, can be clearly observed MB- scanning same area, but by There is additional shade below blood vessel in the variation of blood vessel refractive index；It is the cross of grouper cardiac position in 2.6s shown in Figure 25 The phase contrast of tangential section summarizes image.Each time point collects in 50ms；Such method is equally used in Figure 17；Blood Variation in pipe and heart can be visible in detail；It is the number of the heart contrast changing value changed over time shown in Figure 26 According to image.The variation of contrast, it is related with the variation of grouper normal cardiac rate in region and the changes in flow rate of viewing area；Figure 26 Shown is the contrast for changing over time some lateral position of grouper；The contrast summarizes 3 horizontal pixel (7.2um), covering The entire depth of grouper；It is the direct picture of grouper heart shown in Figure 27 A, 27B, 27C；Figure 27 A is in logarithmic range OCT intensity summation image；Figure 27 B is phase change summation image, improves visualization compared to Figure 27 C；Figure 27 B and 3 The confocal images of its grouper Green Fluorescent Protein being quickly fertilized have similar area；It is in analog year shown in Figure 27 C The Confocal Images that injection fluorescent material generates in the grouper body in age, Figure 27 B movement contrast images show relevant blood vessel Image；It is average OCT gray level image shown in Figure 28 A；It is Doppler's flow of MB- scanning mouse retina shown in Figure 28 B Image；The Doppler flow image of Figure 28 B, does not use any threshold value, and variation range is+- 2.5mm/s.The view observed The main fast flow of film blood vessel is axial flow, but does not observe suprachoroid blood using the image analysis technology Pipe flow；Figure 28 A shows a series of phase change contrast image of phase change time intervals；Extend between the phase change time Every blood vessel (choroidal artery) visualization can be improved, but also increase the contrast shade below blood vessel simultaneously.Time interval Extend equally also increase transverse movement sensitivity and vertical direction on contrast；Figure 29 A is the phase change of MB- scanning Contrast figure, time interval 40us, phase change 10；Figure 29 B show MB- scanning phase change contrast figure, time Between be divided into 160us, phase change 40；Figure 29 C show MB- scanning phase change contrast figure, time interval 240us, Phase change is 40；Figure 29 D show MB- scanning phase change contrast figure, time interval 320s, phase change 40； It is the retinal images after flattening shown in Figure 29 A, 29B, 29C and 29D, is mainly used to elimination optical path change and causes always The influence of the variation of rathole ball curvature.The flattening of retina and identification layer of retina separate confinement are two kinds main in image The method for extracting information, information extraction is in the depth areas of three dimensional grey scale image and contrast-data, analysis acquisition data, shape At lateral or positive image；It is the B- scan image before retina flattening does not rearrange shown in Figure 30 A；Figure It is the B- scan image after retina flattening rearranges shown in 30B；Figure 31 A, 31B and 31C are mouse retina BM- scan image；Figure 31 A is mean intensity scan image；Figure 31 B is phase change image, which does not eliminate any number Phase error on, does not also filter；Figure 31 C is the phase change contrast figure after noise is eliminated and after median filtering Picture, variation range are 0 to 3 radians；It is the direct picture of entire retina BM- scanning shown in Figure 32 A；It is shown in Figure 32 B The positive phase contrast image of entire retina BM- scanning；The direct picture of total intensity shown in Figure 33 A, Figure 33 B are views The phase change contrast image of nethike embrane top half；The retinal vessel of the contrast image display surface of Figure 33 B, arrow Meaning is the region of capillary；The direct picture of total intensity of display depth shown in Figure 34 A, Figure 34 B are under retina The phase change contrast image of half part；The contrast image of Figure 34 B shows choroidal blood vessel and main retinal blood The shade contrast of pipe；Arrow meaning is the region of capillary；It is that BM- scans positive summation grayscale image shown in Figure 35 A Picture is the total phase change contrast image in BM- scanning front shown in Figure 35 B.Figure 35 A is the image of entire retina, so And the image for the BM- scanning retina top half that the contrast image of Figure 35 B, only horizontal pixel are 200；Figure 35 B is mono- The pixel of a contrast image is 200*51, passes through the image of the independent scanning collection of the top area of entire retina.Arrow refers to It is out some lesser visible blood vessels；Positive total phase contrast image shown in Figure 36 A, 36B, 36C and 36D, The image of the top half for the retina that the BM- scanning mode that horizontal pixel is 100 acquires；BM- is used alone to system and sweeps company The pixel of the continuous some images of scanning collection, these images is 100*50, concludes therefrom that the contrast of part is on retina 100*100；Arrow marks some visible capillaries, but these blood vessels are because the intermittence of its contrast is not at it Can all occur on his image；As the transversal scanning region of image with Figure 34 A is with the region of 34B；Figure 37 A and 37B institute The average contrast's image for the two different acquisition method statistics for repeating BM- scanning shown, is the figure of retina top half Picture；Figure 37 A and 37B acquisition are the images for being orthogonal to main horizontal scanning direction.Image can be inferred that picture as a comparison Plain size is 100 × 100.

Obviously, those skilled in the art can carry out various modification and variations without departing from this hair to the embodiment of the present invention Bright spirit and scope.In this way, if these modifications and changes of the present invention belongs to the claims in the present invention and its equivalent technologies Within the scope of, then the present invention is also intended to include these modifications and variations.

Claims (7)

1. utilizing the method for OCT measurement dynamic contrast and the lateral flow of estimation, which is characterized in that the method includes following steps Suddenly：

Data acquisition is carried out using collecting method, wherein carry out using optical coherence tomography system to sample multiple B- scanning collection data, comprising each B- scanning, carry out data acquisition, data in the Multiple-Scan of transverse area Including at least phase information, strength information；

The determination of phase change data, wherein data of the determination of phase variance based on B- scanning collection, also, the movement of sample Contrast depends on phase variance；

Wherein, the collecting method includes the following steps：The sample image at T1 moment is obtained, the sample drawing at T1 moment is selected The predeterminable area of picture obtains tracking image image recognition information for identification and tracking image T1 moment as tracking image Position；According to the sample image at T1 moment, the position of shooting test object is determined, first scan is carried out to shooting test object and is adopted Collect data；The sample image for obtaining the T2 moment, finds the position phase with the tracking image T1 moment in the sample image at T2 moment Same position is as tracking frame；A point to track frame establishes plane right-angle coordinate as origin, to track a point of frame For reference point, reference point is determined along horizontal axis and the moveable maximum magnitude of vertical pivot, along horizontal axis and the moveable minimum spacing of vertical pivot Moveable maximum magnitude is divided into multiple shift positions；Calculating reference point is mobile according to vector (m, n) and traverses mobile position When setting, image in tracking frame when the image recognition information and reference point of T1 moment tracking image are moved to each shift position The related coefficient of image recognition information, the mobile vector (m of the corresponding reference point of the maximum value of the related coefficient_max,n_max) be Vector of the sample T2 moment relative to the movement of T1 moment, T2 moment are later than the T1 moment；Optical coherence tomography galvanometer system root It is corrected according to the sample T2 moment relative to the vector of the movement at T1 moment, scanning collection number again is carried out to shooting test object According to；

Wherein it is determined that phase change data include the following steps：Scanning primary to sample or even multiple, using changing over time Motion phase variance identify and determine the movement of scatterer；

Wherein, in the variation of flow region estimation refractive index, while it includes based on the determining movement contrast of the above estimation：Estimation Refractive index starts the refractive index in the time point and estimation flow region of variation in one or more phase contrast image Ingredient.

2. the method according to claim 1 using OCT measurement dynamic contrast and the lateral flow of estimation, feature exist In multiple B- scanning includes that MB- is scanned, and BM- scanning, or both has.

3. the method according to claim 1 using OCT measurement dynamic contrast and the lateral flow of estimation, feature exist In wherein optical coherence tomography system includes Fourier optical coherence tomography analysis system.

4. the method according to claim 3 using OCT measurement dynamic contrast and the lateral flow of estimation, feature exist In wherein Fourier optical coherence tomography analysis system includes domain optical coherence layer scanning technology, scans source optics phase Dry layer scanning technology and optimal frequency domain analysis imaging.

5. a kind of method of the kinetic characteristic in different motion region in determining sample, which is characterized in that including：Make in multiple regions The movement contrast of multiple regions is determined with the method in claim 1, and identifies one or more region of sample Kinetic characteristic.

6. the method for the kinetic characteristic in different motion region in determining sample according to claim 5, which is characterized in that its Described in one or more moving region be defined as it is three-dimensional.

7. the method for the kinetic characteristic in different motion region in determining sample according to claim 6, which is characterized in that its Described in one or more definition movement 3D regions include three-dimensional blood vessel, target blood, or both has concurrently.