CN110448267A - A kind of multimode eyeground dynamic imaging analysis system and its method - Google Patents
A kind of multimode eyeground dynamic imaging analysis system and its method Download PDFInfo
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Abstract
The invention proposes a kind of multimode eyeground dynamic imaging analysis system and its method, which includes first light source transmitter, the first lens, dichroscope, reflective mirror, hollow reflective mirror, eyepiece and eyeground；The light source of the first light source transmitter transmitting successively arrives at eyeground after the first lens, dichroscope, reflective mirror, hollow reflective mirror, eyepiece；The light of the light of incident reflective mirror and incident hollow reflective mirror is in α °.Multimode eyeground dynamic imaging analysis system proposed by the invention can overcome the shortcomings of the single wide spectrum observation of traditional fundus camera, it protrudes the different levels on eyeground under different narrow-band spectrums and reflects the different morphological feature of emphasis, and light stimulus innovatively is carried out to the interested position in eyeground using dynamic light stimulus screen, whole process recording, the dynamic response variation of the oxygen content and diameter that measure and analyze retinal microvascular in the form of video.
Description
Technical field
The present invention relates to a kind of multimode eyeground technical fields, more particularly to a kind of multimode eyeground dynamic imaging analysis system
And its method.
Background technique
For traditional fundus camera due to using white-light illuminating, spectrum is very wide, and camera receives to own in wide spectrum simultaneously
The information of the information of spectrum, the specific wavelength for causing some specific tissues or lesion locations to eyeground sensitive is submerged, nothing
Method embodies, and can not be studied personnel or doctor observes, this greatly limits divide eyeground structure and function exception
It distinguishes, and early detection and diagnosis to eyeground pathological changes.Using multispectral technology, can obtain in a series of different narrowband wavelengths
Light irradiates the spectrum picture on lower tester eyeground, morphological feature that accordingly see eyeground different levels, that reflection emphasis is different
Or pathological characters.Multispectral fundus imaging technology can help doctor earlier, preferably and more targetedly to identify, manage
Solve, make a definite diagnosis and manage relevant ophthalmic conditions and disease.
However, existing multispectral eyeground imaging system, only makes moderate progress in system imaging equipment composition, not sufficiently
Early screening and the diagnosis of disease are done using the change of the relevant physiological status of the disease provided in system.For example, patent Shen
Numbers 2017101099747 please propose a kind of multispectral eyeground camera system, have cost it is low, it is small in size, practical,
Feature easy to operate.Number of patent application 2016212023969 proposes a kind of multispectral eyeground layered device, can set at this
When the height of standby height and detected object mismatches, make the height-adjustable of the equipment by adjusting lifting device, with
The detected object of different heights is adapted to, to provide more easily service performance.Number of patent application 201810363180.8 mentions
A kind of multispectral eyeground imaging system of dynamic vision stimulation is gone out, the invention is by combining dynamic vision to stimulate, by static state
Multispectral eyeground quiescent imaging is extended to dynamic function imaging field, and image procossing and machine learning is combined to be dedicated to improving eye
The universality and accuracy of bottom methods for the diagnosis of diseases.It can be said that the eyeground physiology shape that the invention provides eyeground multispectral camera
The Testing index of state has had a degree of exploration.However, the system do not provide to eye movement, pupil, blood vessel diameter and
Blood flow changes the monitoring of (blood flow, blood flow velocity etc.), and these indexs are for the diagnosis of eye disease and its related disease
Important foundation, for example, Patients with Chronic Renal Disease retina Mean Arterial blood oxygen saturation is higher, vein caliber is wider, arteriovenous
Caliber ratio is smaller；Diabetes will lead to retina microangioma, and blood vessel hyperplasia damages retina blood capillary, makes its substrate
Film obviously thickens, and the oxygen for being diffused into retinal tissue from capillary significantly reduces, and retinal tissue is caused hypoxic conditions occur,
Arteria retina blood oxygen saturation increases simultaneously；For hypertensive patient, retinal vessel diameters can correspondingly attenuate.Therefore,
These indexs can provide more comprehensively parameter for the change of the relevant physiological status of disease, facilitate the early stage sieve to disease
It looks into and Accurate Diagnosis.
Summary of the invention
The present invention is directed at least solve the technical problems existing in the prior art, a kind of multimode eye is especially innovatively proposed
Bottom dynamic imaging analysis system and its method.
In order to realize above-mentioned purpose of the invention, the present invention provides a kind of multimode eyeground dynamic imaging analysis system, packets
Include first light source transmitter, the first lens, dichroscope, reflective mirror, hollow reflective mirror, eyepiece and eyeground；The first light source
The light source of transmitter transmitting successively arrives at eyeground after the first lens, dichroscope, reflective mirror, hollow reflective mirror, eyepiece；Enter
The light of reflective mirror and the light of incident hollow reflective mirror are penetrated in α °；
Further include relay lens, the second lens and image acquisition device, fundus reflex light successively through eyepiece, hollow reflective mirror,
Image acquisition device is arrived at after relay lens and the second lens；
And further include second light source transmitter and the third lens, the light source of second light source transmitter transmitting successively passes through the
Eyeground is arrived at after three lens, dichroscope, reflective mirror, hollow reflective mirror, eyepiece；The light of incident dichroscope and incidence are reflective
The light of mirror is in β °；
The control terminal of first light source transmitter is connected with the first light source control terminal of controller, controls first light source transmitter
Emit the light source of different wave length；The control terminal of second light source transmitter is connected with the second light source control terminal of controller, control the
The stimulating light source of two light source emitters transmitting different images；The image data output end of image acquisition device and the picture number of controller
It is connected according to input terminal, the image data of image acquisition device acquisition is transferred to controller record.
In the preferred embodiment of the present invention, first light source transmitter is laser light source transmitter；
And/or second light source transmitter is image generator；
And/or image acquisition device is one of camera, CCD camera, CMOS camera.
In the preferred embodiment of the present invention, first light source transmitter emits 840nm under the control of the controller
Infrared laser source；
And/or second light source transmitter emits stimulating image under the control of the controller.
The invention also discloses a kind of multimode eyeground dynamic imaging analysis methods, comprising the following steps:
S1 obtains image to be processed；
The image procossing to be processed obtained in step S1 is segmentation blood-vessel image by S2；
S3 divides the minimum pixel value that vascular cross-section is found on blood-vessel image, as incident intensity figure obtained in S2
As gray value；
S4 calculates the output intensity gray value of image on segmentation blood-vessel image obtained in step S2；
S5 calculates retinal blood oxygen saturation, and the figure being calculated according to the value that step S3 and step S4 are calculated
As being showed.
In the preferred embodiment of the present invention, step S2 are as follows: by the image to be processed obtained in step S1 through scheming
As obtaining correcting image after one of denoising and image adaptive histogram treatment or any combination, by the correction figure of acquisition
As processing is segmentation blood-vessel image.
In the preferred embodiment of the present invention, image to be processed or correcting image are handled to divide in step s 2
Cut the calculation method of blood-vessel image are as follows:
Matched filter:
|x|≤t1σ,
Wherein, σ is the scale of filter, and L is the neighborhood length along y-axis for carrying out noise smoothing；
After image to be processed or correcting image and matched filter are carried out image convolution operation, blood vessel segmentation figure is obtained
Picture.
In the preferred embodiment of the present invention, in step s3, the meter of the minimum pixel value of vascular cross-section is found
Calculation method are as follows:
Wherein,Indicate a bit in vessel centerline,WithRespectively indicate the point on the right and left vascular wall, t2
For the constant from 0 to 1,It indicatesThe grey scale pixel value at place.
In the preferred embodiment of the present invention, in step s 4, the calculation method of output intensity gray value of image
Are as follows:
Wherein,It is illustrated respectively inThe pixel grey scale at place
Value, D are the blood vessel width along centerline direction each point,For the unit vector vertical with blood vessel.
In the preferred embodiment of the present invention, the calculation method of retinal blood oxygen saturation are as follows:
Wherein, IoutFor output intensity gray value of image, IinFor incident intensity gray value of image.
In the preferred embodiment of the present invention, for each branch pointSuccessively search its branch
Starting pointFrom different branches, every P o'clock as one section of small blood
Pipeline section, the P are positive integer, calculate the direction of the thin vessels section blood vessel, are indicated with the angle theta with horizontal direction, and blood is distinguished
The inside and outside pixel of pipe, needs to judge vascular wall, for a point d (x_loc on vessel segmenti,y_loci) using such as
Under formula:
X=x_loci+ L ' × cos (θ-pi/2),
Y=y_loci+ L ' × sin (θ-pi/2), L ' are the length of thin vessels section blood vessel；
To the continuous iterative search of vascular wall formula, judge that whether in the blood vessels point (x, y), then can obtain this section of section
The position of the blood vessel pixel of vertical vessel directions, and taking intravascular minimum gray value is transmitted light intensity gray value；
Carrying out geometric distance operation to left and right vascular wall can be obtained blood vessel width D:
Wherein, (xl, yl), the coordinate when left side and the right that (xr, yr) is respectively vascular wall take gray value minimum.
In conclusion by adopting the above-described technical solution, multimode eyeground dynamic imaging proposed by the invention analyzes system
System can overcome the shortcomings of the single wide spectrum observation of traditional fundus camera, the different layers on the prominent eyeground under different narrow-band spectrums
Morphological feature secondary and that reflection emphasis is different, and light innovatively is carried out to the interested position in eyeground using dynamic light stimulus screen
Stimulation, whole process recording, the dynamic response variation of the oxygen content and diameter that measure and analyze retinal microvascular in the form of video.
Meanwhile the system combination laser light source, be based on laser speckle contrast imaging technology, can also directly, quantitatively measure retina
The blood flow velocity of microcirculation changes it is possible to further study functionality, the metabolic of retina whole blood perfusion amount under light stimulus
Become.The system is ophthalmology disease, systemic disease and neururgic research provide very important tool, there is great face
Bed and scientific research value.
Additional aspect and advantage of the invention will be set forth in part in the description, and will partially become from the following description
Obviously, or practice through the invention is recognized.
Detailed description of the invention
Above-mentioned and/or additional aspect of the invention and advantage will become from the description of the embodiment in conjunction with the following figures
Obviously and it is readily appreciated that, in which:
Fig. 1 is the laser speckle imaging systems in the present invention.
Fig. 2 is the schematic diagram for carrying out eye-tracking in the present invention using pupil-cornea tracing.
Fig. 3 is the non-pupil template of pupil-in the present invention.
Fig. 4 is the signal for the pupil acquisition process being made of in the present invention two steps of full frame operation and pupil candidate operation
Figure.
Fig. 5 is to carry out the image after blood vessel segmentation in the present invention by matching matrix.
Fig. 6 is the blood vessel width calculated result in the present invention.
Specific embodiment
The embodiment of the present invention is described below in detail, examples of the embodiments are shown in the accompanying drawings, wherein from beginning to end
Same or similar label indicates same or similar element or element with the same or similar functions.Below with reference to attached
The embodiment of figure description is exemplary, and for explaining only the invention, and is not considered as limiting the invention.
The present invention provides a kind of multimode eyeground dynamic imaging analysis systems, including first light source transmitter 1, the first lens
2, dichroscope 3, reflective mirror 6, hollow reflective mirror 7, eyepiece 8 and eyeground 9；The light source that the first light source transmitter 1 emits according to
It is secondary that eyeground 9 is arrived at after the first lens 2, dichroscope 3, reflective mirror 6, hollow reflective mirror 7, eyepiece 8；Incident reflective mirror 6
The light of light and same incident hollow reflective mirror 7 is in α °；The light of the light of incident hollow reflective mirror 7 and same incident eyepiece 8
Line is in γ °.
It further include relay lens 10, the second lens 11 and image acquisition device 12, fundus reflex light is successively through eyepiece 8, hollow
Image acquisition device 12 is arrived at after reflecting mirror 7, relay lens 10 and the second lens 11；
And further include second light source transmitter 4 and the third lens 5, the light source that second light source transmitter 4 emits successively passes through
Eyeground 9 is arrived at after crossing the third lens 5, dichroscope 3, reflective mirror 6, hollow reflective mirror 7, eyepiece 8；The light of incident dichroscope 3
The light of line and same incident reflective mirror 6 is in β °；In the present embodiment, α °, β °, γ ° takes pi/2.
The control terminal of first light source transmitter 1 is connected with the first light source control terminal of controller 13, control first light source hair
The light source of the transmitting different wave length of emitter 1；The second light source control terminal phase of the control terminal of second light source transmitter 4 and controller 13
Even, control second light source transmitter 4 emits the stimulating light source of different images；The image data output end of image acquisition device 12 and control
The image data input of device 13 processed is connected, and the image data that image acquisition device 12 acquires is transferred to controller record.
In the preferred embodiment of the present invention, first light source transmitter 1 is laser light source transmitter；
And/or second light source transmitter 4 is image generator；
And/or image acquisition device 12 is one of camera, CCD camera, CMOS camera.
In the preferred embodiment of the present invention, first light source transmitter 1 emits under the control of controller 13
840nm infrared laser source；
And/or second light source transmitter 4 emits stimulating image under the control of controller 13.
The invention also discloses a kind of multimode eyeground dynamic imaging analysis methods, comprising the following steps:
S1 obtains image to be processed；
The image procossing to be processed obtained in step S1 is segmentation blood-vessel image by S2；
S3 divides the minimum pixel value that vascular cross-section is found on blood-vessel image, as incident intensity figure obtained in S2
As gray value；
S4 calculates the output intensity gray value of image on segmentation blood-vessel image obtained in step S2；
S5 calculates retinal blood oxygen saturation, and the figure being calculated according to the value that step S3 and step S4 are calculated
As being showed.
In the preferred embodiment of the present invention, step S2 are as follows: by the image to be processed obtained in step S1 through scheming
As obtaining correcting image after one of denoising and image adaptive histogram treatment or any combination, by the correction figure of acquisition
As processing is segmentation blood-vessel image.
In the preferred embodiment of the present invention, image to be processed or correcting image are handled to divide in step s 2
Cut the calculation method of blood-vessel image are as follows:
Matched filter:
Wherein, σ is the scale of filter, t1For constant, L is the neighborhood length along y-axis for carrying out noise smoothing；
After image to be processed or correcting image and matched filter are carried out image convolution operation, blood vessel segmentation figure is obtained
Picture.
In the preferred embodiment of the present invention, in step s3, the meter of the minimum pixel value of vascular cross-section is found
Calculation method are as follows:
Wherein,Indicate a bit in vessel centerline,WithRespectively indicate the point on the right and left vascular wall, t2
For the constant from 0 to 1,It indicatesThe grey scale pixel value at place.
In the preferred embodiment of the present invention, in step s 4, the calculation method of output intensity gray value of image
Are as follows:
Wherein,It is illustrated respectively inThe pixel grey scale at place
Value, D are the blood vessel width along centerline direction each point,For the unit vector vertical with blood vessel.
In the preferred embodiment of the present invention, the calculation method of retinal blood oxygen saturation are as follows:
Wherein, IoutFor output intensity gray value of image, IinFor incident intensity gray value of image.
In the preferred embodiment of the present invention, for each branch pointSuccessively search its branch
Starting pointFrom different branches, every P o'clock as one section of small blood
Pipeline section, the P calculate the direction of the thin vessels section blood vessel preferably every 4 o'clock as one section of thin vessels section for positive integer,
It is indicated with the angle theta with horizontal direction, distinguishes the pixel of extra vascular, need to judge vascular wall, for blood vessel
A point d (x_loc in sectioni,y_loci) use following formula:
X=x_loci+ L ' × cos (θ-pi/2),
Y=y_loci+ L ' × sin (θ-pi/2), L ' are the length of thin vessels section blood vessel；
To the continuous iterative search of vascular wall formula, judge that whether in the blood vessels point (x, y), then can obtain this section of section
The position of the blood vessel pixel of vertical vessel directions, and taking intravascular minimum gray value is transmitted light intensity gray value；
Carrying out geometric distance operation to left and right vascular wall can be obtained blood vessel width D:
Wherein, (xl, yl), the coordinate when left side and the right that (xr, yr) is respectively vascular wall take gray value minimum.
Subfunction 1: it realizes 840nm infrared laser preview video recording, stimulator is combined with laser speckle imaging systems, In
Speckle is recorded and calculated simultaneously in stimulating course.
As shown in Figure 1, first light source transmitter 1 emits laser speckle light source, preferred emission swashs laser speckle imaging systems
Radiant, wavelength can be selected according to the design needs, and this programme selects 840nm infrared laser source, successively thoroughly by first
Mirror 2, dichroscope 3, reflective mirror 6, hollow reflective mirror 7 and connect mesh object lens 8 enter eyeground 9.The reflected light of retina is by connecing mesh
Object lens 8, hollow reflective mirror 7, relay lens 10, the second lens 11 are acquired by image acquisition device 12.Image acquisition device can be phase
Machine, CCD camera, CMOS camera etc..Acquired image is sent in controller 13 (computer) and carries out by image acquisition device 12
Algorithm process realizes real-time record and the calculating of speckle.In the same time, second light source transmitter 4 (stimulator) to eyeground into
Row stimulation in real time.Second light source transmitter 4 generate stimulating image, successively by the third lens 5, dichroscope 3, reflective mirror 6,
Hollow reflective mirror 7 enters eyeground 9 with mesh object lens 8 are connect, and stimulates eyeground.The combination of stimulator and laser speckle imaging systems
The variation that can effectively observe eyeground under stimulation state can obtain more effectively letters by subsequent algorithm process
Breath.
Subfunction 2: using the near infrared imaging of 840nm, eye movement is tracked.
Optokinetics is widely used in following research field: human factor, behavioral study, pattern-recognition, market
Research, medical research, highway engineering research, driver training and evaluation, meter panel design evaluatio and Reading studies etc..
Eyes are there are three types of basic exercise form: watching attentively, beat and smooth pursuit movement.When we usually see thing,
Actually eyes are all carrying out various forms of movements.Firstly, two eyes must keep certain orientation, it can just make object
Picture fall in the central fovea of two retinas, to obtain most clear sight, the activity of this eye alignment object is called
Watch attentively.Object is watched attentively in order to realize and maintain, eyes must carry out other two kinds of movements: the bounce of eyeball and chasing after for eyeball
With movement.The final purpose of the activity form of these types of eyeball is provided to guarantee the clear consciousness to object.
Several main eye movement recording methods have: 1, electromagnetic induction method；2, mechanical recorder technique；3, electric current writing-method；4, light
Learn writing-method.These types of recording method is specifically addressed below:
Electromagnetic induction method: the eyes of subject are anaesthetized, and a contact lens equipped with exploring coil is adsorbed on eyes.
There are induced voltages in coil can accurately measure eye both horizontally and vertically by the phase-sensitive detection to induced voltage
It is dynamic.This precision of method is high, but the discomfort of subject can be caused by contacting eyeball.
Mechanical recorder technique: by a small mirror be attached to subject eyes on, light directive mirror, reflected light line with
The movement of eyeball and change, to obtain eye movement signal.Its technical characterstic is precision highest, high bandwidth, interferes greatly people, is made one
There is uncomfortable feeling.
Electric current writing-method: eye movement can produce bio-electric phenomenon.The metabolism of cornea and retina is different
, the metabolic rate at cornea position is smaller, and the metabolic rate at nethike embrane position is larger, so it is formed 0.4 between cornea and nethike embrane~
The potential difference of 1.0mV, cornea is positively charged, and nethike embrane is negatively charged.When eye movement does not occur in front of eye gaze, stabilization can recorde
Reference potential, when eyes move in the horizontal direction, the potential difference between oculus sinister and the skin on right side can become
Change, and when eyes move in vertical direction, the potential difference of eyes the upper side and lower side can change.By two pairs of chlorination parchment coverings
Skin surface electrode is respectively placed in eyes or so, upper and lower two sides, can cause the ultra-weak electronic signal in eyeball change direction, through amplifying
After obtain oculomotor location information.The characteristics of this method, is high broadband, low precision, interferes greatly people.
Optical recording:
Corneal reflection tracing: because cornea is protruded from the surface of augen, during eye movement,
Cornea is also variation to the reflection angle of the light from fixed light source, therefore a near-infrared can be placed in front of human eye
The light of LED light source and a camera being fixed on immediately ahead of subject's head, corneal reflection passes through the light beam point before eyes
From equipment and some reflecting mirrors, lens transmission to camera.Same device is set to another drawing axis.Corneal reflection light
Position is determined by the image that is fixed in the camera screen in front of head and corresponding some algorithms.The maximum mistake of the system
The sliding and the error due to caused by the distance between eyes and camera gun that difference is mainly head optical system.
Pupil-cornea tracing: as shown in Fig. 2, system infrared light 3 irradiates eyes, system optics are solid in space
Fixed, the eyes 1 of opposite subject have relatively fixed distance, and the image of reflection is recorded by the video camera 4 of optical element 2
Get off, the data that video camera 4 is obtained distinguish pupil and CR (cornea), then angle by computer or microprocessor processes
Film reflects basic point of the point data as the relative position of eye camera and eyeball, is calculated and is being shielded according to pupil center location coordinate
Fixation point in curtain space.This method is accurate, error is small and noiseless to people.
Subfunction 3: pupil observation is carried out in stimulating course: the detection of pupil size is realized using contraposition iris camera,
And it is recorded in the variation tendency of stimulating course.
The detection technique of pupil of human size has important research and application value in medical domain.Pupil not only due to
The power of light and change, certain physiology courses and noematic occur also will affect the variation of pupil size.By to people
The information such as its available physiology of the detection of body pupil size, pathology and nerve consciousness.
Currently, the detection method of pupil size has a figure method, corneal reflection method, infrared TV method, infrared broadcasting and TV bounce technique, pupil
Hole-cornea tracing, mathematical morphology method and image treating, wherein image treating is high with accuracy, error is small, right
The features such as human eye is noiseless becomes the pupil size detection method being widely used at present.
Carry out pupil size detection with image treating, be generally divided into following steps: image preprocessing obtains candidate
Pupillogram, binaryzation, edge detection, storage pupil boundary and pupil, which are fitted, determines pupil position and size.
To the pupil changed under the stimulation of fixed wave length and light intensity, associated picture is captured by contraposition iris camera, it is right
The image is handled, to detect position and the size of pupil, and is recorded in the variation tendency of stimulating course, specific implementation
It is as follows:
Pupil acquisition process is made of two steps of full frame operation and pupil candidate operation.
In full frame operation, following image processing process is executed:
Iris image is subjected to 1/4*1/4 down-sampling, to reduce calculation amount；
For the subgraph that down-sampling obtains, it is filtered enhancing, filtering core is the non-pupil template of pupil-, such as Fig. 3 institute
Show, horizontal line label indicates the pixel of pupil region in template, and slash mark indicates the pixel of non-pupil region in template, cross spider
Label indicates template center pixel, and the enhancing image is stored in pupil candidate list；
In pupil candidate operation, following image processing process is executed:
To every piece image in pupil candidate list, the same position of its corresponding high-definition picture in its center is adjusted
It sets and matches, obtain initially constraining square, the ROI of Lai Dingyi high-definition picture；
Binaryzation is carried out to ROI, method is image pixel intensities method and pseudo- gradient method, and carries out edge detection to binary map,
The edge detection of middle puppet gradient method is based on the edge graph that image pixel intensities method obtains, as shown in figure 4, the example of upper access
Figure is that image pixel intensities method obtains as a result, the exemplary diagram of underpass is the result that pseudo- gradient method obtains；
Two binary edge figures derived above are combined, obtain pupil edge pixel map, and be stored in corresponding pupil
In bore edges pixel list；
Pupil position and size are determined in conjunction with least square method using best-fit-circle.
Subfunction 4: pass through the image or speckle result progress vessel extraction in the infrared preview of 840nm, analysis stimulation
The calculating of front and back blood oxygen and the variation of stimulating course medium vessels diameter.
The image under 840nm is acquired, blood vessel segmentation I is obtained by multiscale matched filtering methodvStructure.By different
Stimulation can carry out the calculating of front and back blood oxygen, observe the variation of stimulating course medium vessels diameter.Because of the retinal blood under 840nm
Pipe structure carries out blood vessel segmentation using the method for matched filter without largely mark segmentation sample, this patent.Matched filtering
Device method can preferably distinguish be the pixel of blood vessel and be not blood vessel pixel, blood vessel has different trends in space, leads to
It crosses and designs the image that blood vessel detection can be obtained by filtration in various filters and each pixel convolution of original image.Specific implementation is such as
Under:
Single order Gauss matched filtering device:
Wherein, σ is the scale of filter, and common filter factor is2,4, this method can be in σ=2
Obtain best effects.T is constant, is usually arranged as 3 because be more than under Gaussian curve 99% region all in [- 3 σ, 3 σ] range
It is interior.L is the neighborhood length along y-axis for carrying out noise smoothing.Blood vessel be it is linear, in certain length range, their side
To being identical, therefore we can be rightFritter carry out and meanwhile filter, efficiency can be improved in this way.
Correcting image I is obtained after 840nm image is carried out image denoising processing and image adaptive histogram treatmentGC, with
After matched filter group W carries out image convolution operation, blood vessel segmentation image I is obtainedv, as shown in Figure 5.
Iv=IGC* W,
Wherein, W is integrated with the height of various scales (the different values of σ, it is understood that for the filter on 12 directions)
This matched filter.
After obtaining blood vessel segmentation image, for a bit in vessel centerlineIt enablesWithRespectively represent the right and left
Point on vascular wall, finds the minimum pixel value of this section of vascular cross-section, compares the pixel on the section line perpendicular to vessel directions
The gray value size of point, is indicated with following formula:
Wherein, min { } is the minimum value in set, and arg min { f (x) } indicates the value of x when f (x) is minimized.It indicatesThe grey scale pixel value at place, t are the constant from 0 to 1.
The blood vessel external reflectance light intensity (being also output intensity) of same point is by wide apart from about blood vessel of the right and left vascular wall
The gray value of the pixel of degree represents, and can indicate are as follows:
Wherein,It is illustrated respectively inThe pixel grey scale at place
Value, D are the blood vessel width along centerline direction each point,For the unit vector vertical with this section of blood vessel.
The branch point recorded from previous step, for each branch pointA=1,2 ..., k, k are blood
Pipe branch total number, successively searches the starting point of its branchFrom different
Branch sets out, and every four o'clock as one section of thin vessels section, calculates the direction of this section of blood vessel, to come with the angle theta of horizontal direction
It indicates.The pixel for distinguishing extra vascular, needs to judge vascular wall, for a point d (x_loc on vessel segmenti,
y_loci) use following formula:
X=x_loci+ L ' × cos (θ-pi/2),
Y=y_loci+ L ' × sin (θ-pi/2),
To the continuous iterative search of vascular wall formula, judge that whether in the blood vessels point (x, y), then can obtain this section of section
The position of the blood vessel pixel of vertical vessel directions, and taking intravascular minimum gray value is incident intensity gray value.
Carrying out geometric distance operation to left and right vascular wall can be obtained blood vessel width D:
Wherein, (xl, yl), the coordinate when left side and the right that (xr, yr) is respectively vascular wall take gray value minimum, blood vessel
Width result is as shown in Figure 6.
The calculating of retinal blood oxygen saturation depends on the calculating of optical density ratio ODR, i.e. light is close under two different wave lengths
The ratio of degree.And the calculating of optical density needs to obtain the numerical value of incident intensity and transmitted light intensity, respectively by the pixel of extravascular
The image pixel intensities of intensity and internal blood vessel indicate.For every a bit of blood vessel, the pixel of this section of vessel cross-sections can be used
Minimum gradation value indicate output intensity, and the gray value of the pixel of this section of blood vessel the right and left certain position can then be used
To indicate incident intensity.Therefore, the key for carrying out blood oxygen calculating is to obtain the picture in the region that eye fundus image represents corresponding light intensity
Element value.Then the background pixel point at both ends is chosen are as follows:
The gray value of intravascular and background pixel is calculated.The then optical density function OD at this are as follows:
Wherein, IoutFor output intensity gray value of image, IinFor incident intensity gray value of image, ODλIt is full for retina blood oxygen
And degree.
Subfunction 5: the calculating of blood flow variation (blood flow, blood flow velocity etc.) is carried out in stimulating course by speckle.
When scattering particles movement, interference pattern can be changed over time, and by coherent light source illumination to biological tissue and use phase
The speckle image of machine record reflection, the movement of scattering particles will lead to obscuring for speckle image in a finite integration time, this
Kind fog-level can be indicated with speckle contrast.The calculation method of laser speckle have it is a variety of, can substantially be divided into 3 classes: when
Between contrast calculating method, calculating method is contrasted in space, and time-space contrasts calculating method.
Time contrasts calculating method: using the original speckle image of CCD or CMOS camera continuous acquisition multiframe (usually 25 frames or
49 frames), the standard deviation and mean value of any pixel point speckle Strength Changes in time series in image are then calculated, by all pictures
The value of contrasting of vegetarian refreshments combines and then obtains whole picture and contrast figure.The method spatial resolution with higher still has lower
Temporal resolution, while it is more demanding to the frame per second of camera.
Contrast calculating method in space: with the spatial window (usually 5*5 or 7*7 pixel) of a fixed size, calculating this
The standard deviation and mean value of all pixels in a window, so that obtain window center position pixel contrasts value.By this window with
Pixel is unit, is horizontally and vertically moved along original speckle image, traverses entire image, obtains each pixel
Contrast value, finally obtains whole picture and contrast figure.This method temporal resolution with higher still has lower spatial resolution.
Time-space contrasts calculating method: this method contrasts calculating method by binding time and the excellent of calculating method is contrasted in space
Gesture can retain higher temporal resolution and higher spatial resolution simultaneously.Its concrete operations process is first to each frame
Image carry out space contrast value calculate then on this basis according to time series carry out time contrasts value calculating, finally
Obtain that treated contrasts image.
It is worth noting that, value is contrasted in the space of speckle only when assuming that speckle intensity meets negative exponent probability distribution
It could accurately be estimated, that is, need to scatter speckle completely.Specific estimation measure are as follows: minimum speckle size is greater than CCD
The 2 times or more of Pixel Dimensions.There is following relationship between minimum speckle size and the pore size of camera lens:
ρs=2.44* λ * f/#* (1+M)
Wherein, λ is optical maser wavelength；F/# is the f number of imaging lens；M is the amplification factor of imaging system
The variation of velocity of blood flow can effectively be reflected by contrasting image by laser speckle, by with optical stimulation device
In conjunction with, can more comprehensively recognize the variation of eyeground velocity of blood flow in entire stimulating course, be fundus oculi disease diagnosis band
Carry out more information.
Although an embodiment of the present invention has been shown and described, it will be understood by those skilled in the art that: not
A variety of change, modification, replacement and modification can be carried out to these embodiments in the case where being detached from the principle of the present invention and objective, this
The range of invention is defined by the claims and their equivalents.
Claims (10)
1. a kind of multimode eyeground dynamic imaging analysis system, which is characterized in that including first light source transmitter (1), the first lens
(2), dichroscope (3), reflective mirror (6), hollow reflective mirror (7), eyepiece (8) and eyeground (9)；The first light source transmitter
(1) light source emitted successively passes through the first lens (2), dichroscope (3), reflective mirror (6), hollow reflective mirror (7), eyepiece (8)
Arrive at eyeground (9) afterwards；The light of incident reflective mirror (6) and the light of incident hollow reflective mirror (7) are in α °；
Further include relay lens (10), the second lens (11) and image acquisition device (12), fundus reflex light successively through eyepiece (8),
Hollow reflective mirror (7), relay lens (10) and the second lens (11) arrive at image acquisition device (12) afterwards；
And further include second light source transmitter (4) and the third lens (5), the light source of second light source transmitter (4) transmitting is successively
Eyeground (9) are arrived at after the third lens (5), dichroscope (3), reflective mirror (6), hollow reflective mirror (7), eyepiece (8)；It is incident
The light of dichroscope (3) and the light of incident reflective mirror (6) are in β °；
The control terminal of first light source transmitter (1) is connected with the first light source control terminal of controller (13), control first light source hair
The light source of emitter (1) transmitting different wave length；The control terminal of second light source transmitter (4) and the second light source of controller (13) control
End is connected, the stimulating light source of control second light source transmitter (4) transmitting different images；The image data of image acquisition device (12) is defeated
Outlet is connected with the image data input of controller (13), and the image data of image acquisition device (12) acquisition is transferred to controller
Record.
2. multimode eyeground dynamic imaging analysis system according to claim 1, which is characterized in that first light source transmitter
It (1) is laser light source transmitter；
And/or second light source transmitter (4) is image generator；
And/or image acquisition device (12) is one of camera, CCD camera, CMOS camera.
3. multimode eyeground dynamic imaging analysis system according to claim 2, which is characterized in that first light source transmitter
(1) emit 840nm infrared laser source under the control of controller (13)；
And/or second light source transmitter (4) emits stimulating image under the control of controller (13).
4. a kind of multimode eyeground dynamic imaging analysis method, which comprises the following steps:
S1 obtains image to be processed；
The image procossing to be processed obtained in step S1 is segmentation blood-vessel image by S2；
S3 divides the minimum pixel value that vascular cross-section is found on blood-vessel image obtained in S2, as incident intensity image ash
Angle value；
S4 calculates the output intensity gray value of image on segmentation blood-vessel image obtained in step S2；
S5 calculates retinal blood oxygen saturation according to the value that step S3 and step S4 are calculated, and the image being calculated into
Row shows.
5. multimode eyeground dynamic imaging analysis method according to claim 4, which is characterized in that step S2 are as follows: by step
The image to be processed obtained in S1 obtains after one of image denoising processing and image adaptive histogram treatment or any combination
It is segmentation blood-vessel image by the correcting image processing of acquisition to correcting image.
6. multimode eyeground dynamic imaging analysis method according to claim 4 or 5, which is characterized in that in step s 2 will
Image or correcting image processing to be processed is the calculation method of segmentation blood-vessel image are as follows:
Matched filter:
Wherein, σ is the scale of filter, and L is the neighborhood length along y-axis for carrying out noise smoothing；
After image to be processed or correcting image and matched filter are carried out image convolution operation, blood vessel segmentation image is obtained.
7. multimode eyeground dynamic imaging analysis method according to claim 4, which is characterized in that in step s3, find
The calculation method of the minimum pixel value of vascular cross-section are as follows:
Wherein,Indicate a bit in vessel centerline,WithRespectively indicate the point on the right and left vascular wall, t2For from 0
To 1 constant,It indicatesThe grey scale pixel value at place.
8. multimode eyeground dynamic imaging analysis method according to claim 4, which is characterized in that in step s 4, outgoing
The calculation method of intensity image gray value are as follows:
Wherein,It is illustrated respectively inThe grey scale pixel value at place, D
For along the blood vessel width of centerline direction each point,For the unit vector vertical with blood vessel.
9. multimode eyeground dynamic imaging analysis method according to claim 4, which is characterized in that retinal blood oxygen saturation
Calculation method are as follows:
Wherein, IoutFor output intensity gray value of image, IinFor incident intensity gray value of image.
10. the multimode eyeground dynamic imaging analysis method according to one of claim 7~9, which is characterized in that for each
A branch pointSuccessively search the starting point of its branchFrom difference
Branch set out, every P o'clock as one section of thin vessels section, the P is positive integer, calculate the direction of the thin vessels section blood vessel,
It is indicated with the angle theta with horizontal direction, distinguishes the pixel of extra vascular, need to judge vascular wall, for blood vessel
A point d (x_loc in sectioni,y_loci) use following formula:
X=x_loci+ L ' × cos (θ-pi/2),
Y=y_loci+ L ' × sin (θ-pi/2), L ' are the length of thin vessels section blood vessel；
To the continuous iterative search of vascular wall formula, whether in the blood vessels point (x, y) is judged, then it is vertical can to obtain this section of section
The position of the blood vessel pixel of vessel directions, and taking intravascular minimum gray value is transmitted light intensity gray value；
Carrying out geometric distance operation to left and right vascular wall can be obtained blood vessel width D:
Wherein, (xl, yl), the coordinate when left side and the right that (xr, yr) is respectively vascular wall take gray value minimum.
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| EP3954272A1 (en) * | 2020-08-10 | 2022-02-16 | Welch Allyn, INC. | Fundus imaging for microvascular assessment |
| CN116327111B (en) * | 2023-02-28 | 2024-01-16 | 中山大学中山眼科中心 | Fundus blood vessel blood oxygen function coefficient measurement system and method based on fundus photo |
| CN116327111A (en) * | 2023-02-28 | 2023-06-27 | 中山大学中山眼科中心 | Fundus blood vessel blood oxygen function coefficient measurement system and method based on fundus photo |
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