CN106997045A - Ultrasonic imaging method with compressed sensing is measured based on ultrasonic system point spread function - Google Patents
Ultrasonic imaging method with compressed sensing is measured based on ultrasonic system point spread function Download PDFInfo
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Abstract
The present invention relates to ultrasonic imaging field, relate more specifically to measure the ultrasonic imaging method with compressed sensing based on ultrasonic system point spread function.The purpose of the present invention is：While high frame frequency and the ultrasonic imaging compared with high imaging quality is ensured, realize the hardware computing platform for only needing to reduced levels with regard to that can be imaged.Comprise the following steps for the ultrasonic imaging method that this present invention is provided：Obtain the point spread function of the ultrasonic image-forming system；According to the point spread function opening relationships matrix M；The equation group of relation between the sub- scatter intensity distribution I of scattering on the pixel of foundation reflection ultrasonic echo radiofrequency signal s and ultrasonoscopy：S=MI；Characterized in that, setting a threshold value, the element in the relational matrix M less than the threshold value is all set to 0.Present invention could apply to need high frame frequency and high-resolution imaging and the relatively low field of hardware computing platform level, such as medical imaging, with larger practical value.
Description
Technical field
The present invention relates to ultrasonic imaging field, relate more specifically to measure and press based on ultrasonic image-forming system point spread function
Contract the ultrasonic imaging method perceived.
Background technology
Traditional ultrasonic imaging operation principle, by taking linear array ultrasound transducer as an example, linear array transducer possess it is N number of can be only
The array element of vertical transmitting/reception, corresponding to N number of ultrasound emission passage and signal receiving channel, during ultrasound emission, utilizes multiple passages
Delay emission, make the ultrasonic signal of different passages while reaching focal position, formed transmitting focusing；When receiving echo, docking
The signal that receives carries out similar delay, by the different channel receptions returned from same reflection thing to signal be accumulated in together,
Form collectiong focusing.So once launch and once receive, a scan line can be formed.Usual ultrasonic imaging all uses electronics
The mode of scanning, carries out M focus emission/reception to obtain M bar scan lines, then by these scan conversions into a width completely two
Tie up image.Therefore, the frame frequency of conventional ultrasound imaging is very low, generally in more than ten frames between tens frames.For high rigidity tissue bullet
Property imaging, main artery high speed blood flow imaging, cardiac imaging and follow the trail of the imageable target such as acoustic contrast agent state change and quickly transport
Reason and the application field for needing high frame frequency, the frame frequency of conventional ultrasound imaging can not much meet needs.
Plane of ultrasound ripple imaging technique includes the transmitting of plane of ultrasound ripple and corresponding ultrasonic echo beam-forming technology, is state
Hot research direction on border in recent years on raising ultrasonic imaging frame frequency.The technology can be by traditional ultrasonic imaging frame frequency (one
As be more than ten frames to tens frames) improve hundred times, reach 10000-20000 frames.This method is general by all of linear array transducer
Array element is all used to launch, using the identical voltage pulse without relative time delay from each other, while encouraging linear array transducer each
Individual array element is to produce along the plane of ultrasound ripple propagated forward perpendicular to transducer face direction；When receiving echo-signal, using base
DAS (Delay and Sum, be delayed the addition method) beam-forming technology one width two dimensional image of formation in image slices vegetarian refreshments position.
So, it is only necessary to which once transmitting/reception can complete a two-dimensional imaging, drastically increase imaging frame frequency.But, due to
During using plane wave imaging technique, ultrasonic energy is evenly distributed in whole two-dimensional imaging plane, is reflected from different scattering
Echo understands aliasing together, by each channel reception, it is difficult to distinguish.Therefore, the image obtained by common Beamforming Method
Apparent artifact interference occurs.
To solve this problem, multi-angle coherent superposition imaging method is suggested.This method is from 2N+1 (N be a certain positive integer)
(one of angle is the usually used angle perpendicular to surface of ultrasonic transducer to individual angle, and other 2N angle surrounds this
Individual vertical angle is distributed in symmetrical shape, such as -2 °, -1 °, 0 °, 1 °, 2 °) launch plane of ultrasound ripple and equally using based on image
The DAS beam-forming technologies of pixel position obtain 2N+1 width two dimensional images, and these images are overlapped, equivalent to from multiple
Relevant enhancing is realized between the plane of ultrasound ripple of angular emission, is produced similar to the effect focused on, it is achieved thereby that image point
The enhancing of resolution and contrast.N values are bigger, and the raising effect to resolution ratio and contrast is more notable.Using this technology,
Through realizing high-spatial and temporal resolution, can to full cerebral microvascular respond brain activity produced by dynamic change carry out in real time into
The new technology of picture --- ultrasonic cerebral function imaging technology (functional ultrasound, fUS).The up to KHz order of magnitude
Frame frequency imaging effect, be the key of research trends blood flow situation of change.In addition, the technology is also apply to multiple biomedicines
In the forward position research direction of ultrasonics, such as real-time three-dimensional ultrasonography, high velocity Doppler blood flow flow field velocity are scattered in picture, two dimension
Real-time elastogram, heart, main artery strain imaging etc., with very wide application prospect.But, multi-angle coherent superposition
Imaging method is equivalent to frame frequency is again reduced, for example, using common plane of ultrasound wave imaging method, it is possible to achieve 10000 frames
Frame frequency per second, but in order to improve the resolution ratio and contrast of image, be changed to use multi-angle coherent superposition imaging method, by 51
The transmitting of angle/reception result synthesis piece image, frame frequency has dropped down to per second less than 200 frames.Therefore, multi-angle is relevant folded
Plus the application of imaging method is seriously restricted.
In summary, how while ensureing that frame frequency does not decline, the resolution ratio and contrast of image are improved as much as possible,
The major issue for needing to solve is imaged as plane of ultrasound ripple.
In recent years, some successively are sent out on the paper of the plane of ultrasound wave imaging method based on compressed sensing both at home and abroad
Table.These methods are all divided into following two steps：
(1) each pixel of image is considered as to a grid node in two dimensional surface, it is assumed that deposited at each grid node
Can cause the scattering of incident ultrasound in scattering, form echo, then it is believed that we will into ultrasonoscopy reality
Border reflection is the distribution that sub scattering strength is scattered on grid node in two dimensional surface.Firstly, it is necessary to set up reflection ultrasound
The mathematical modeling of relation between sub- scatter intensity distribution I is scattered on echo radiofrequency signal s and grid node, following form is formed
Equation group：
S=MI
Wherein matrix M is relational matrix.During due to actual imaging in ultrasonic echo radiofrequency signal noise presence, solve the equation
Group is an ill-posed problem under normal circumstances, it is impossible to try to achieve unique solution.
(2) as I sparse (sparse), i.e., when nonzero element quantity therein is much smaller than neutral element quantity, then pressure can be passed through
Contracting cognitive method is solved to above-mentioned equation group：
Wherein β, which reflects the how many noise contributions of permission, to be present.
For ultrasonic imaging, in (1) step, how the physical principle followed according to it, foundation can use up
The mathematical modeling of relation between s and I may truly be reflected, and set up the matrix M for being easy to complete subsequently to iterate to calculate accordingly, be to determine
Determine the key of ultrasonic imaging quality and imaging method practicality.And in (2) step, the circular of solving equations is
Through there is the iterative numerical approach of many maturations available, the emphasis that the present invention is illustrated is not belonging to.
For scattering sub- scatter intensity distribution in the reflection ultrasonic echo radiofrequency signal described in step (1) and grid node
Between relation mathematical modeling, that has delivered mainly has following three kinds：1. the compressibility distribution situation based on medium to be imaged
More complicated model (Bochum, Germany Rule university Martin F.Schiffner and Georg Schmitz etc.)；2. base
The fairly simple model being delayed in frequency-region signal (University Of Shantou Shen Min puts forth energy).
The final form of model 1. is：
Wherein G is a NelNk× N matrix, NelIt is the port number that ultrasound transducer array receives echo-signal, NkRefer to width
The ultrasound echo signal of band is divided into NkIndividual discrete wave number kl, 1≤l≤Nk, N=NxNzBe total pixel count of image (in other words
It is grid node number), Nx、NzIt is the line number and row of x directions (width) and z directions (depth direction) epigraph pixel respectively
Number.Each element definition in matrix G is：
Wherein m represents m-th of array element on transducer, 1≤m≤Nel, i represents the ith pixel on image, 1≤i≤N,Represent the acoustic pressure of incident ultrasound, rel,mRepresent the locus of m-th of array element on ultrasonic transducer, riRepresent on image
The position of ith pixel, gl(rel,m-ri) be open space Green's function, be defined as：
Wherein j represents imaginary part,It is the Equations of The Second Kind Hankel functions of zeroth order.pscRepresent ultrasonic echo radiofrequency signal, γκRepresent
The distribution situation for the compressibility of the medium to be imaged (compressibility of medium is the principal element for determining its sound scattering intensity).
The final form of model 2. is：
X (ω)=A (ω) S (ω)
Handled by being then based on frequency-region signal, actually take the π f of ω=20, wherein f0For used ultrasonic transducer
Emission center frequency.X is the ultrasonic echo radiofrequency signal after Short Time Fourier Transform, and S dissipates for the scattering to be imaged
Penetrate intensity and correspond to f on frequency domain0Mapping, A be K × L the relational matrix being made up of time delay data, be defined as：
[A(ω)k]i=exp [j ω τk(ρi)]
Wherein K is the port number that ultrasound transducer array receives echo-signal, L for image total pixel count (or perhaps net
Lattice nodes), 1≤k≤K, 1≤i≤L, ρiA pixel (or grid node) on image is represented,Represent that the echo-signal sent from some pixel reaches some ultrasound transducer array passage
Time delay,The locus of some ultrasound transducer array passage is represented,Represent some pixel ρiLocus.
It may be noted that X is that the frequency obtained after a bit of progress short time discrete Fourier transform is intercepted out from whole ultrasonic echo radiofrequency signals
Domain signal, if therefore whole ultrasonic echo radiofrequency signal is divided into Q section, to complete all to be imaged, it is necessary to by follow-up solution
Process is repeated Q times.
Set up after above-mentioned two model, solving equations are carried out by compression sensing method, it is possible to solve γκ(model
1.) or S (model is 2.), then by it from the matrix that vector transformation is correspondence image pixel quantity, it is possible to be shown as us
The image of desired acquisition.
Above-mentioned two, which reflects, scatters relation between sub- scatter intensity distribution on ultrasonic echo radiofrequency signal and grid node
Mathematical modeling, respectively there is its limitation.
The foundation of model 1., is from the mathematical modeling for being proved to more accurately acoustic propagation and scattering, advantage
Be can the more real various physical phenomenons of reflection sound in media as well, but shortcoming is also clearly, is exactly that model is excessively multiple
It is miscellaneous.Relational matrixSize it is excessively huge, it is necessary to a large amount of internal memories be taken, while also resulting in the meter of follow-up solution procedure
Calculation amount is very huge.With the imaging experiment data instance carried out in its paper, work as Nx=400, Nz=600, Nel=128, Nk=
When 1000, the internal memory that matrix G takes is up to 458GB.Therefore, to realize the algorithm, all have to again it be counted during G using calling every time
Calculate the method for its each element numerical value to carry out, significantly increase amount of calculation.Moreover, actually above-mentioned parameter value can not at all
The need for meeting normal medical ultrasound image, if imaging depth is more than 5cm, NzValue generally all more than 3000, therefore
EMS memory occupation amount will be also further added by 5 times, be not the task that common computer can undertake completely.
Model is 2. due to only considering the time delay of ultrasonic echo radiofrequency signal, while only considering the emission center frequency of ultrasound
Rate f0Without considering other frequency contents of signal, therefore the scale of its used relational matrix A (ω) is greatly reduced.But,
The model still has following problem.First, all elements of matrix A (ω) are all non-zeros, and X is returned from all ultrasounds
The frequency-region signal obtained after a bit of progress short time discrete Fourier transform is intercepted out in ripple radiofrequency signal, if whole ultrasonic echo radio frequencies
Signal is divided into Q sections, then to complete all imagings, it is necessary to which follow-up solution procedure is repeated Q times, therefore carry out follow-up matrix
Amount of calculation is still very big during multiplying.Secondly, for convenience to signal carry out time delay calculating, all fortune of the model
Calculate and all carried out in frequency domain.This is accomplished by, first by the ultrasonic echo radiofrequency signal of time domain, being transformed into by Short Time Fourier Transform
Frequency domain.This process not only increases amount of calculation, can also introduce due to the calculation error of the limited generation of signal length, and then influences
To final image quality.
In view of this, it is necessary to develop a kind of new method to overcome drawbacks described above.
The content of the invention
For above-mentioned the deficiencies in the prior art, the purpose of the present invention is, to simplify relation square as far as possible relative to model 1.
Battle array, memory storage space and amount of calculation during reduction computing；, it is to avoid use Fourier transform and frequency domain meter relative to model 2.
Calculate.
In order to achieve the above object, the present invention proposes a kind of measured based on ultrasonic image-forming system point spread function and compression
The ultrasonic imaging method of perception, so that while high frame frequency is ensured and compared with high imaging quality, realization only needs to the hard of reduced levels
Part calculating platform can be just imaged using this method, be easy to implement the industry conversion of the present invention.
The invention provides a kind of ultrasonic imaging side measured based on ultrasonic image-forming system point spread function with compressed sensing
Method, it may comprise steps of：Obtain the point spread function of the ultrasonic image-forming system；Set up according to the point spread function
Relational matrix M；And the scattering sub- scattering strength point set up on the pixel of reflection ultrasonic echo radiofrequency signal s and ultrasonoscopy
The equation group of relation between cloth I：S=MI；Characterized in that, setting a threshold value, the threshold will be less than in the relational matrix M
The element of value is all set to 0.
In some embodiments, the ultrasonic image-forming system is obtained in certain ultrasound emission by way of testing measurement
The point spread function under pattern at locus corresponding with all pixels point on ultrasonoscopy.
In some embodiments, the mode of the experiment measurement may comprise steps of：(i) with ultrasonoscopy
Sufficiently small scattering of size is placed on the corresponding locus of some pixel, while there is no any scattering in other positions
The interference of son；(ii) ultrasonic image-forming system launches the ultrasonic signal of certain pattern, after the scattering reflection, forms super
Sound echo-signal, the ultrasound echo signal is received by the ultrasonic image-forming system, wherein the ultrasonic echo letter received
Number i.e. the system under certain described ultrasound transmission modes the locus point spread function；(iii) to described super
All pixels point on acoustic image performs step (i) and (ii), obtains the ultrasonic image-forming system in certain ultrasound transmission modes
Under the point spread function at locus corresponding with all pixels point on the ultrasonoscopy.
In some embodiments, it is described that the ultrasonic image-forming system is obtained by way of testing measurement in certain ultrasound
The point spread function under emission mode at locus corresponding with all pixels point on ultrasonoscopy can include but
It is not limited to the mode measured in the sink using nylon wire.
In some embodiments, methods described can also comprise the following steps：Pass through ripe compressed sensing algorithm pair
The equation group s=MI is solved, and obtains vectorial I, by it from the matrix that vector transformation is correspondence image pixel quantity, then
The steps such as dynamic range and digital scan conversion are adjusted, the ultrasonoscopy intentionally got is obtained.
In some embodiments, the ripe compressed sensing algorithm includes but is not limited to matching pursuit algorithm
(matching pursuit method), Bregman algorithms, operator/variable splitting, FPC (Fixed-
point continuation：Fixed point is continuous) algorithm, L1-magic algorithms, Newton tangential method etc..
In some embodiments, when I is not sparse, sparse transformation Ψ can be carried out to I, makes θ=Ψ I, wherein θ
Coefficients of the I in sparse transform-domain, θ be it is sparse, can be according to the solution formula of compressed sensingTo solve I, wherein β represents to allow the presence of how many noise contribution.
In some embodiments, the sparse transformation Ψ can include but is not limited to discrete cosine transform (DCT), it is various
Wavelet transformation etc..
In some embodiments, the ultrasonic image-forming system can use plane of ultrasound ripple emission mode.
In some embodiments, the ultrasonic image-forming system can be using ultrasonic convex surface ripple emission mode.
In some embodiments, the ultrasonic image-forming system can be using ultrasonic concave surface ripple emission mode.
In some embodiments, the transmitting that the ultrasonic image-forming system can be encouraged using any irregular waveform signal
Pattern.
The present invention is while high frame frequency and the ultrasonic imaging compared with high imaging quality is ensured, realization only needs to reduced levels
Hardware computing platform has larger practical value with regard to that can be imaged.
Those skilled in the art read entire disclosure and will be understood that during claims the present invention these advantages and
Further advantage.
Brief description of the drawings
Fig. 1 is shown imitates cavity contrast the emulation that body is imaged using method according to the embodiment of the present invention
Experimental result.
Fig. 2 is shown imitates cavity contrast the emulation experiment that body is imaged using traditional delay addition method (DAS)
As a result.
Embodiment
The specific embodiment of the present invention is illustrated below in conjunction with the accompanying drawings.Specific reality of the invention described below
Apply in example, some very specific technical characteristics are described for better understanding of the present invention, but it will be apparent that for
For those skilled in the art, these not all technical characteristics are all the essential features for realizing the present invention.Under
Some specific embodiments of the invention described by text be the present invention some exemplary specific embodiments, its should not by regarding
For limitation of the present invention.In addition, in order to avoid making the present invention become indigestion, not carried out for some known technologies
Description.
Method of the present invention is realized using ultrasonic image-forming system.In one embodiment, first by ultrasound into
As the computer control ultrasound emission circuit of system enters row energization to ultrasound transducer array, to launch ultrasonic signal.Work as ultrasound
When each passage (each passage corresponds to an array element) of transducer array is excited simultaneously, the ultrasonic signal launched is one
Group plane wave signal, you can to think its wave surface perpendicular to ultrasound emission direction, wave surface arrives at a certain depth in imaging plane
The time of degree is consistent.The ultrasonic signal is propagated in media as well, is scattered, and forms ultrasound echo signal.Ultrasonic echo is believed
Number received by ultrasound transducer array, then by ultrasonic reception circuit sampling, form ultrasonic echo radiofrequency signal.Ultrasonic echo radio frequency
Signal is sent back in the computer, and realizes that the ultrasound of the present invention based on compressed sensing is put down in the computer
Face ripple imaging.
In this embodiment, it is known that ultrasound transducer array includes K array element, wherein the coordinate of k-th of array element is
(xk,0).Will into ultrasonoscopy pixel number (i.e. to imaging plane divide grid node number) be N=Nx×Nz, its
Middle Nx、NzIt is the line number and columns of x directions (width) and z directions (depth direction) epigraph pixel respectively.Some grid
The coordinate of the sub- n of scattering at node is (xn,zn).The sample frequency of ultrasonic echo radiofrequency signal is fs, the sampled point of each passage
Number is D, then the ultrasonic radio frequency echo data sum that a plane of ultrasound ripple transmitting/reception is gathered is D × K.
First, by way of testing measurement, used ultrasonic image-forming system is obtained under certain ultrasound transmission modes
Point spread function.Experiment is typically carried out in the sink.In one embodiment, on image corresponding to some pixel
Sufficiently small scattering of size is placed on locus (for example, vertical on direction perpendicular to the imaging plane tense one very
Thin nylon wire), while not having the interference of any scattering in other positions, system launches the ultrasonic signal of certain pattern,
After scattering son reflection, the ultrasound echo signal being received by the system again, i.e., the system is under certain ultrasound transmission modes
Point spread function in the locus, can be regarded as a size and is D × K matrix, and can further be transformed to one
Length is D × K vectorial m.
Therefore, to the sub- n of scattering at each grid node, a vector m can be generatedn.Obtained by testing measurement
Point spread function of the system on the locus under certain ultrasound transmission modes on image corresponding to all pixels point, i.e.,
One shared N number of scattering, combines, and is constructed for as D × K row, the relational matrix M of N row.If I is all grid sections
The scattering strength of scattering on point, i.e. I is the vector that a length is N.Then have：
S=MI
In addition, in relational matrix M now, the values of most elements is close to 0.Therefore a threshold value can be set, by M
In be all set to 0 less than the element of the threshold value, then M can be stored and used by way of sparse expression, and it is greatly reduced and accounts for
Memory storage space and amount of calculation.
So far, the side of relation between sub- scatter intensity distribution I is scattered on reflection ultrasonic echo radiofrequency signal s and grid node
Journey group is set up and finished.Finally, above-mentioned equation group is solved by ripe compressed sensing algorithm, obtains vectorial I, by its from
Vector transformation is the matrix of correspondence image pixel quantity, then is adjusted the steps such as dynamic range and digital scan conversion, i.e.,
The ultrasonoscopy for wishing to obtain can be obtained.The ripe compressed sensing algorithm includes but is not limited to matching pursuit algorithm
(matching pursuit method), Bregman algorithms, operator/variable splitting, FPC (Fixed-
point continuation：Fixed point is continuous) algorithm, L1-magic algorithms, Newton tangential method etc..
In this embodiment, the ultrasonic image-forming system uses plane of ultrasound ripple emission mode.But actually originally
Method is not limited to just in plane of ultrasound ripple emission mode.If for example, ultrasonic system uses convex surface ripple or recessed
Face ripple emission mode, the emission mode even encouraged using any irregular waveform signal may be by this method realization
Imaging.
It should be noted that compressive sensing theory requires that unknown signaling I is sparse.And actually carrying out ultrasonic imaging
When, the scatter intensity distribution of scattering on grid node and may be unsatisfactory for this condition in itself.In this case, to I
Sparse transformation Ψ is carried out, it is coefficients of the I in sparse transform-domain to make θ=Ψ I, wherein θ.Now, θ is sparse, utilizes compression
The solution formula of perception is changed into：
The compressed sensing algorithm that maturation can thus be first passed through obtains I to the progress solution of above-mentioned equation group.Wherein, sparse transformation
Ψ includes but is not limited to discrete cosine transform (DCT), various wavelet transformations etc..
It is also to be noted that obtaining used ultrasonic image-forming system in certain ultrasound transmission modes by testing measurement
Under point spread function method include but is not limited to it is above-mentioned in the sink using nylon wire measure mode, it would however also be possible to employ its
He measures suitable experimental facilities and material.
Used model, 1. 2. all greatly simplified relative to model in the present invention.Solve and signal time is postponed
The time domain expression problem of calculating, it is no longer necessary to carry out Fourier transform and calculated in frequency domain, it is to avoid because carrying out Fourier
The calculation error for converting and causing.Further, since the relational matrix M that model of the present invention is set up finally is simplified in order to which one can
To carry out the matrix of sparse expression, significantly reduce the memory storage space and amount of calculation of its occupancy compared to model 1..Compare
In model 2., due to need by whole ultrasonic echo radiofrequency signals be divided into Q sections (data former and later two segmentation between need one
The fixed overlapping resolution ratio to improve depth direction, therefore the length of more than 4000 data point at least needs to be divided into 100 sections,
It is 100 sections in first embodiment, is in a second embodiment 200 sections, is in the third embodiment 400 sections), it is every to what is intercepted out
One piece of data carries out short time discrete Fourier transform and calculated with obtaining frequency-region signal, and repeating follow-up solution.Therefore model is 2. total
Amount of calculation on be much larger than model used in the present invention.In addition, model 2. for convenience to signal carry out time delay meter
Calculate, all computings are all carried out in frequency domain.And Short Time Fourier Transform calculates and not only increases amount of calculation, it can also introduce due to signal
The calculation error that limited length is produced, and then have influence on final image quality.
With reference now to Fig. 1 and 2, it illustrates ultrasonic imaging is emulated using ultrasonic imaging simulation software Field II
Result.Fig. 1 is shown using method (wherein, K=128, D=4364, N according to the embodiment of the present inventionx=256, Nz
=the simulation experiment result that body be imaged 3000) is imitated cavity contrast.Fig. 2 is shown using traditional delay addition method
(DAS) the simulation experiment result that body be imaged is imitated cavity contrast.From Fig. 1 and Fig. 2, the inventive method institute is into image
Contrast be substantially better than conventional method.
Therefore, new ultrasonic imaging method proposed by the invention, on the one hand can realize the quick ultrasound of superelevation frame frequency
Imaging, on the other hand ensure that higher image quality, while the hardware computation platform for only needing to reduced levels can be achieved with, just
Converted in industry of realizing.
Although according to preferred embodiment, the present invention is described, exist fall into the scope of the invention it
Interior change, displacement and various replacement equivalents.It should also be noted that there are a variety of methods for realizing the present invention and be
The optional mode of system.It is therefore intended that appended claims are construed to include within the spirit and scope of the invention
All these changes, displacement and various replacement equivalents.
Claims (9)
1. a kind of ultrasonic imaging method measured based on ultrasonic image-forming system point spread function with compressed sensing, it includes following step
Suddenly：
Obtain the point spread function of the ultrasonic image-forming system；
According to the point spread function opening relationships matrix M；And
Set up pass between the sub- scatter intensity distribution I of scattering on the pixel of reflection ultrasonic echo radiofrequency signal s and ultrasonoscopy
The equation group of system：S=MI；
Characterized in that,
One threshold value is set, the element in the relational matrix M less than the threshold value is all set to 0.
2. according to the method described in claim 1, it is characterised in that obtain the ultrasonic imaging system by way of testing measurement
The point spread function united under certain ultrasound transmission modes at locus corresponding with all pixels point on ultrasonoscopy
Number.
3. method according to claim 1 or 2, it is characterised in that the mode of the experiment measurement comprises the following steps：
(i) sufficiently small scattering of size is placed on locus corresponding with some pixel on ultrasonoscopy, while
There is no the interference of any scattering in other positions；
(ii) ultrasonic image-forming system launches the ultrasonic signal of certain pattern, after the scattering reflection, forms ultrasound and returns
Ripple signal, the ultrasound echo signal is received by the ultrasonic image-forming system, wherein the ultrasound echo signal received is i.e.
The system under certain described ultrasound transmission modes the locus point spread function；
(iii) step (i) and (ii) are performed to all pixels point on the ultrasonoscopy, obtains the ultrasonic image-forming system and exist
The point spread function under certain ultrasound transmission modes at locus corresponding with all pixels point on the ultrasonoscopy
Number.
4. method according to claim 2, it is characterised in that it is described obtained by way of testing measurement the ultrasound into
As the point of the system under certain ultrasound transmission modes at locus corresponding with all pixels point on ultrasonoscopy expands
Scattered function includes but is not limited to：The mode measured in the sink using nylon wire.
5. according to the method described in claim 1, it is characterised in that methods described is further comprising the steps of：Pass through ripe compression
Perception algorithm is solved to the equation group s=MI, obtains vectorial I, by its from vector transformation be correspondence image pixel number
The matrix of amount, then dynamic range and digital scan conversion step are adjusted, obtain the ultrasonoscopy intentionally got.
6. method according to claim 5, it is characterised in that the ripe compressed sensing algorithm includes：Match tracing
Method, Bregman algorithms, operator/variable splitting, FPC algorithm, L1-magic algorithms, Newton tangential method.
7. the method according to claim 5 or 6, it is characterised in that when I is not sparse, sparse transformation is carried out to I
Ψ, it is coefficients of the I in sparse transform-domain to make θ=Ψ I, wherein θ, and θ is sparse, according to the solution formula of compressed sensingTo solve I, wherein β represents to allow the presence of how many noise contribution.
8. method according to claim 7, it is characterised in that the sparse transformation Ψ includes：Discrete cosine transform
(DCT), various wavelet transformations.
9. method according to claim 1 or 2, it is characterised in that the ultrasonic image-forming system is sent out using plane of ultrasound ripple
Emission mode, ultrasonic convex surface ripple emission mode, ultrasonic concave surface ripple emission mode or the transmitting mould of any irregular waveform signal excitation
Formula.
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|---|---|---|---|---|
| CN104331913A (en) * | 2014-11-19 | 2015-02-04 | 西安电子科技大学 | Polarized SAR polarization method based on sparse K-SVD (Singular Value Decomposition) |
| CN104739448A (en) * | 2015-04-03 | 2015-07-01 | 深圳先进技术研究院 | Ultrasonic imaging method and device |
-
2017
- 2017-03-06 CN CN201710128830.6A patent/CN106997045B/en active Active
Patent Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN104331913A (en) * | 2014-11-19 | 2015-02-04 | 西安电子科技大学 | Polarized SAR polarization method based on sparse K-SVD (Singular Value Decomposition) |
| CN104739448A (en) * | 2015-04-03 | 2015-07-01 | 深圳先进技术研究院 | Ultrasonic imaging method and device |
Non-Patent Citations (2)
| Title |
|---|
| CONGZHI WANG 等: "Plane-wave Ultrasound Imaging Based on Compressive Sensing with Low Memory Occupation", 《2015 IEEE INTERNATIONAL ULTRASONICS SYMPOSIUM PROCEEDINGS》 * |
| 向馗: "《数据驱动的复杂动态系统建模》", 31 August 2013, 国防工业出版社 * |
Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN108957375B (en) * | 2018-07-23 | 2020-12-22 | 深圳先进技术研究院 | Magnetic resonance imaging method, device, equipment and storage medium |
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