CN104739448B - A kind of ultrasonic imaging method and device - Google Patents
A kind of ultrasonic imaging method and device Download PDFInfo
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- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
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- A61B8/065—Measuring blood flow to determine blood output from the heart
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- A61B8/5207—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of raw data to produce diagnostic data, e.g. for generating an image
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Abstract
The present invention relates to a kind of ultrasonic imaging method and device, wherein, the method includes：Obtain N × K very first time delayed data tn,k；Obtain D × K the second time delay data td,k；By the ultrasonic echo rf digital signal, accordingly matrixing is that length is the vectorial s of D × K；Using the corresponding second time delay data t of data point d of k-th passage in the vectorial sd,kAnd corresponding very first time delayed data t under same channelsn,kDetermine matrix M；Wherein, the matrix M is sparse matrix；Equation group is set up according to the vectorial s and the matrix M；Wherein, the equation group is：S=MI；I represents that the scatter intensity distribution of scattering, length are the vector of N；The equation group is solved by compressed sensing algorithm, vectorial I is obtained；According to the ultrasonoscopy that the vectorial I determines to want.
Description
Technical field
The present invention relates to medical imaging technology field, more particularly to a kind of ultrasonic imaging method and device.
Background technology
Medical ultrasound image technology by over half a century development, because its is real-time, it is high to soft tissue taste,
The advantages of easy to use and good economy performance, have become most widely used image technology and clinical various diseases in clinical medicine
The prefered method of diagnosis.
The frame frequency of conventional ultrasound imaging is very low, generally in more than ten frames between tens frames.For high rigidity tissue elasticity into
Picture, main artery high speed blood flow imaging, cardiac imaging and follow the trail of the imageable target such as acoustic contrast agent state change quickly move because
And the application field of high frame frequency is needed, the frame frequency of conventional ultrasound imaging cannot much meet needs.
Plane of ultrasound ripple imaging technique includes the transmitting of plane of ultrasound ripple and corresponding ultrasonic echo beam-forming technology, ultrasound
Traditional ultrasonic imaging frame frequency (generally more than ten frames to tens frames) can be improved hundred times by imaging technique, reach 10000~
20000 frames.The general all array elements by linear array transducer of the method are all used to launch, using no relative time delay from each other
Identical voltage impulses, while encouraging each array element of linear array transducer to produce what edge was propagated forward perpendicular to transducer face direction
Plane of ultrasound ripple；When receiving echo-signal, using DAS (Delay and Sum, time delay superposition based on image slices vegetarian refreshments position
Method) beam-forming technology one width two dimensional image of formation.So, it is only necessary to which once transmitting/reception can complete a two-dimensional imaging,
Drastically increase imaging frame frequency.But, because when using plane wave imaging technique, ultrasonic energy is evenly distributed in entirely
Two-dimensional imaging plane, understands aliasing together, by each channel reception, it is difficult to distinguish from the echo of different scattering reflection.Therefore,
The image obtained by common Beamforming Method occurs apparent artifact interference.
To solve this problem, multi-angle coherent superposition imaging method is suggested.The 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 is around this
Individual vertical angle in symmetrical shape be distributed, such as -2 °, -1 °, 0 °, 1 °, 2 °) transmitting plane of ultrasound ripple and equally using based on scheme
As the DAS beam-forming technologies of pixel position obtain 2N+1 width two dimensional images, these images are overlapped, equivalent to from many
Relevant enhancing is realized between the plane of ultrasound ripple of individual angular emission, is produced similar to the effect for focusing on, it is achieved thereby that image
The enhancing of resolution ratio and contrast.N values are bigger, and the raising effect to resolution ratio and contrast is more notable.Using this technology,
High-spatial and temporal resolution is had been realized in, the dynamic change produced by the response brain activity of full cerebral microvascular can be carried out in real time
The new technology of imaging --- ultrasonic cerebral function imaging technology (functional ultrasound, fUS).Up to KHz quantity
The frame frequency imaging effect of level, is the key of research trends blood flow situation of change.Additionally, the technology is also apply to multiple biological doctors
Learn 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
Real-time elastogram, heart, main artery strain imaging etc. are tieed up, with very wide application prospect.But, multi-angle is relevant folded
Plus 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
Frame frame frequency per second, but in order to improve the resolution ratio and contrast of image, be changed to using multi-angle coherent superposition imaging method, by 51
The transmitting of individual angle/reception result synthesis piece image, frame frequency has dropped down to per second less than 200 frames.Therefore, multi-angle is concerned with
The range of application of stacking image method is seriously restricted.
In sum, how while ensureing that frame frequency does not decline, the resolution ratio and contrast of image are improved as much as possible,
As the major issue that ultrasonic imaging needs to solve.
The content of the invention
To solve the problems, such as above-mentioned technology, the present invention proposes a kind of ultrasonic imaging method and device.
To achieve the above object, the invention provides a kind of ultrasonic imaging method, the method includes：
Obtain N × K very first time delayed data tn,k；Wherein, the very first time delayed data tn,kIt is ultrasonic signal
Since the ultrasound emission moment, by n-th scattering of scattering, k-th channel position of ultrasound transducer array is returned
Total time delay；N represents the pixel number of the ultrasonoscopy wanted, and K represents array element number in ultrasound transducer array；
N represents some scattering, scatters sub- n=1,2 ... ..., N；K represents some passage in ultrasound transducer array, k=1,
2 ... ..., K；
Obtain D × K the second time delay data td,k；Wherein, the second time delay data td,kFor known from super
Sound emission moment, the elapsed time postpones, and starts to sample ultrasonic echo radiofrequency signal, obtains ultrasonic echo radio frequency number
Word signal, the moment of k-th channel reception to d-th data point of the ultrasonic echo rf digital signal believes relative to ultrasound
The time delay of number delivery time；D represents the sampling number of each passage, and d represents a channel reception to ultrasonic echo radio frequency number
The a certain data point of word signal, d=1,2 ... ..., D；
By the ultrasonic echo rf digital signal, accordingly matrixing is that length is the vectorial s of D × K；
Using the corresponding second time delay data t of data point d of k-th passage in the vectorial sd,kAnd it is identical logical
Corresponding very first time delayed data t under roadn,kDetermine matrix M；Wherein, the matrix M is sparse matrix；
Equation group is set up according to the vectorial s and the matrix M；Wherein, the equation group is：S=MI；I dissipates for expression
The length for penetrating the scatter intensity distribution of son is the vector of N；
The equation group is solved by compressed sensing algorithm, vectorial I is obtained；
According to the ultrasonoscopy that the vectorial I determines to want.
Preferably, the step of determination matrix M includes：
Data point d to k-th passage sets up the vectorial m that length is N, obtains D × K vector m；In the vectorial m
Each element determines that method is：If the corresponding second time delay data t of the data point d of k-th passaged,kAnd it is identical logical
Corresponding very first time delayed data t under roadn,kMeetThen from n-th ultrasonic echo of scattering son scattering
Information is included in k-th data point d of passage, then nth elements are set to 1 in vector m, otherwise, are set to 0；
D × K vector m is configured to the matrix M of D × K row, N row.
Preferably, the ultrasonic signal is plane of ultrasound ripple signal.
Preferably, the very first time delayed data tn,kExpression formula be：
Wherein, k-th locus coordinate of passage is (xk,0)；N-th scattering on the ultrasonoscopy wanted
Locus coordinate be (xn,zn)；C represents sound wave spread speed in media as well；X directions are the widths of ultrasonoscopy,
Z directions are the depth directions of ultrasonoscopy.
Preferably, the ultrasonic signal is ultrasonic convex surface ripple signal, ultrasonic concave surface ripple signal.
Preferably, the second time delay data td,kExpression formula be：
td,k=t0+(d-1)/fs
Wherein, t0Represent since the ultrasound emission moment carries out sampling instant to ultrasonic echo radiofrequency signal when
Between length of delay, fsRepresent sample frequency.
Preferably, it is described to include the step of solved by compressed sensing algorithm to the equation group：
If vector I is sparse, equation group s=MI is solved by compressed sensing algorithm, that is, metThe I values of condition are the optimal solution of equation group；Wherein, β represents permission how many noise contribution
In the presence of；S.t. it is the formal notation for representing logical relation；
Otherwise, sparse transformation is carried out to vectorial I；Equation group s=MI is solved by compressed sensing algorithm, that is, is metThe I values of condition are the optimal solution of equation group；Wherein, Ψ represents sparse transformation matrix, β
Representing allows how many noise contributions to exist；S.t. it is the formal notation for representing logical relation.
Preferably, the compressed sensing algorithm be matching pursuit algorithm, Bregman algorithms, operator/variable splitting algorithm,
Fixing point continuation algorithm, L1 norm magics algorithm, Newton tangential method.
Preferably, the step of ultrasonoscopy that the determination is wanted, includes：
Vectorial I is transformed to image array Φ；Wherein, described image matrix Φ is a NxRow NzCapable matrix；NxRepresent
The number of x directions epigraph pixel, N in three-dimensional system of coordinatezRepresent the number of z directions epigraph pixel in three-dimensional system of coordinate, N=
Nx×Nz；
To the matrix Φ treatment, the ultrasonoscopy wanted is obtained；Wherein, the method for the treatment of includes：The number of winning the confidence
Envelope, log-compressed, adjustment and carry out digital scan conversion at image display dynamic range.
To achieve the above object, present invention also offers a kind of supersonic imaging device, the device includes：
Very first time delayed data determining unit, for obtaining N × K very first time delayed data tn,k；Wherein, it is described
Very first time delayed data tn,kIt is ultrasonic signal since the ultrasound emission moment, by n-th scattering of scattering, returns
Total time delay of k-th channel position of ultrasound transducer array；N represents the pixel number of the ultrasonoscopy wanted, K
Represent array element number in ultrasound transducer array；N represents some scattering, scatters sub- n=1,2 ... ..., N；K represents ultrasound
Some passage, k=1,2 ... ..., K in transducer array；
Second time delay data determination unit, for obtaining D × K the second time delay data td,k；Wherein, it is described
Second time delay data td,kFor known since the ultrasound emission moment, the elapsed time postpones, and starts to believe ultrasonic echo radio frequency
Number sampled, obtained ultrasonic echo rf digital signal, k-th channel reception to the ultrasonic echo rf digital signal
Time delay of d-th data point relative to ultrasonic signal delivery time；D represents the sampling number of each passage, and d represents that one leads to
Road receives a certain data point of ultrasonic echo rf digital signal, d=1,2 ... ..., D；
Converter unit, for by the ultrasonic echo rf digital signal accordingly matrixing be length for D × K to
Amount s；
Matrix determining unit, for corresponding second time delays of data point d using k-th passage in the vectorial s
Data td,kAnd corresponding very first time delayed data t under same channelsn,kDetermine matrix M；Wherein, the matrix M is sparse
Matrix；
Model sets up unit, for setting up equation group according to the vectorial s and the matrix M；Wherein, the equation group
For：S=MI；I represents that the scatter intensity distribution of scattering, length are the vector of N；
Unit is solved, for being solved by compressed sensing algorithm to the equation group, vectorial I is obtained；
Ultrasound imaging unit, for the ultrasonoscopy for determining to want according to the vectorial I.
Preferably, the matrix determining unit includes：
Vector sets up module, and the vectorial m that length is N is set up for the data point d to k-th passage, obtain D × K to
Amount m；Each element in the vectorial m determines that method is：If corresponding second time delays of the data point d of k-th passage
Data td,kAnd corresponding very first time delayed data t under same channelsn,kMeetThen from n-th scattering
The ultrasonic echo information of son scattering is included in k-th data point d of passage, then nth elements are set to 1 in vector m, otherwise,
It is set to 0；
Constructing module, the matrix M for D × K vector m to be configured to D × K row, N row.
Preferably, the ultrasonic signal of the supersonic imaging device treatment is plane of ultrasound ripple signal.
Preferably, the very first time delayed data t that the very first time delayed data determining unit is obtainedn,kExpression formula
For：
Wherein, k-th coordinate of passage is (xk,0)；The coordinate of n-th scattering of the ultrasonoscopy wanted is (xn,
zn)；C represents sound wave spread speed in media as well.
Preferably, the ultrasonic signal of the supersonic imaging device treatment is ultrasonic convex surface ripple signal, ultrasonic concave surface ripple signal.
Preferably, the second time delay data t that the second time delay data determination unit is obtainedd,kExpression formula
For：
td,k=t0+(d-1)/fs
Wherein, t0Represent time-delay value, fsRepresent sample frequency.
Preferably, the solution unit includes：
First solves module, for the vectorial I it is sparse when, equation group s=MI is asked by compressed sensing algorithm
Solution, that is, meetThe I values of condition are the optimal solution of equation group；Wherein, how much β represents permission
Noise contribution is present；S.t. it is the formal notation for representing logical relation；
Second solves module, for the vectorial I it is not sparse when, sparse transformation is carried out to vectorial I；Calculated by compressed sensing
Method is solved to equation group s=MI, that is, meetThe I values of condition be equation group most
Excellent solution；Wherein, Ψ represents sparse transformation matrix, and β represents that the how many noise contributions of permission are present；S.t. it is the public affairs for representing logical relation
Formula symbol.
Preferably, it is described solve the compressed sensing algorithm that uses of unit for matching pursuit algorithm, Bregman algorithms, operator/
Variable splitting algorithm, fixing point continuation algorithm, L1 norm magics algorithm, Newton tangential method.
Preferably, the ultrasound imaging unit includes：
Conversion module, for vectorial I to be transformed into image array Φ；Wherein, described image matrix Φ is a NxRow Nz
The matrix of row；NXThe number of x directions epigraph pixel in three-dimensional system of coordinate is represented, Nz represents the upper figure in z directions in three-dimensional system of coordinate
As the number of pixel, N=Nx×Nz；
Processing module, for the matrix Φ treatment, obtaining the ultrasonoscopy wanted；Wherein, the side for the treatment of
Method includes：Take signal envelope, log-compressed, adjustment image display dynamic range and carry out digital scan conversion.
Compared with prior art, the present invention realizes a ultrasound emission/reception and just can complete a two-dimensional imaging,
Theoretic most fast frame frequency is reached, while considerably improving the resolution ratio and contrast of image.And, it can both be applied
In the imaging of plane of ultrasound ripple, it may have be applied to the potentiality of the ultrasonic imaging of other nonplanar wave radiation patterns, be medical ultrasonic
The development of imaging technique provides a new direction, and international monopoly monopolization is broken to China's medical ultrasonic image equipment, realizes
The advanced technology breakthrough for grasping independent intellectual property right is significant.
Brief description of the drawings
In order to illustrate more clearly about the embodiment of the present invention or technical scheme of the prior art, below will be to embodiment or existing
The accompanying drawing to be used needed for having technology description is briefly described, it should be apparent that, drawings in the following description are only this
Some embodiments of invention, for those of ordinary skill in the art, on the premise of not paying creative work, can be with
Other accompanying drawings are obtained according to these accompanying drawings.
Fig. 1 is traditionally ultrasonic imaging principle schematic；
Fig. 2 is a kind of ultrasonic imaging method flow chart proposed by the present invention；
Fig. 3 is the simulation experiment result figure being imaged to the sparse imitative body of point-like using the technical program；
Fig. 4 is the simulation experiment result figure being imaged to the sparse imitative body of point-like using traditional time delay addition method；
Fig. 5 is the simulation result figure being imaged to non-sparse imitative body using the technical program；
Fig. 6 is the simulation result figure being imaged to non-sparse imitative body using traditional time delay addition method；
Fig. 7 is renal tissue section original image；
Fig. 8 is the imaging results figure obtained using the technical program；
Fig. 9 is the imaging results figure obtained using traditional time delay addition method；
Figure 10 is a kind of supersonic imaging device block diagram proposed by the present invention.
Specific embodiment
Principle of the invention and spirit are described below with reference to some illustrative embodiments.It should be appreciated that providing this
A little implementation methods are used for the purpose of better understood when those skilled in the art and then realizing the present invention, and not with any
Mode limits the scope of the present invention.Conversely, these embodiments are provided so that the disclosure is more thorough and complete, and energy
It is enough that the scope of the present disclosure is intactly conveyed into those skilled in the art.
Art technology technical staff knows, embodiments of the present invention can be implemented as a kind of system, device, equipment,
Method or computer program product.Therefore, the disclosure can be implemented as following form, i.e.,：It is complete hardware, complete soft
Part (including firmware, resident software, microcode etc.), or the form that hardware and software is combined.
According to the embodiment of the present invention, it is proposed that a kind of ultrasonic imaging method and device.
Herein, it is to be understood that in involved term：
1st, ultrasonic imaging：By taking linear array ultrasound transducer as an example, as shown in figure 1, linear array transducer possess K can be independent
The array element of transmitting/reception, corresponding to K ultrasound emission passage and signal receiving channel.During ultrasound emission, using multiple passages
Delay emission, makes the ultrasonic signal of different passages while reaching focal position, forms transmitting focusing；When receiving echo, to receiving
To signal carry out similar time delay, by the different channel receptions returned from same reflection thing to signal be accumulated in together, shape
Into collectiong focusing.So once launch and once receive, a scan line can be formed.Usual ultrasonic imaging is all swept using electronics
The mode retouched, carries out P focus emission/reception to obtain P bar scan lines, then by these scan conversions into the complete two dimension of a width
Image.
2nd, compressed sensing (Compressive sensing), also referred to as compression sampling (Compressive
Sampling), sparse sampling (Sparse sampling), compression sensing., used as a new sampling theory, it is by opening for it
The sparse characteristic of signalling, under conditions of much smaller than Nyquist sample rates, the discrete sample of signal is obtained with stochastical sampling,
Then the perfect reconstruction signal of non-linear algorithm for reconstructing is passed through.
Additionally, any number of elements in accompanying drawing is used to example and unrestricted, and any name is only used for distinguishing,
Without any limitation.
Below with reference to some representative embodiments of the invention, principle of the invention and spirit are explained in detail.
Summary of the invention
In recent years, some papers on the plane of ultrasound wave imaging method based on compressed sensing successively send out both at home and abroad
Table.These methods are all divided into two steps：
(1) each pixel of image is considered as a grid node in two dimensional surface, it is assumed that at each grid node
The scattering of incident ultrasound can be all caused in the presence of scattering, echo is formed.Then it is believed that the ultrasound that we want is schemed
The actual reflection of picture is the distribution that sub scattering strength is scattered on grid node in two dimensional surface.
Firstly, it is necessary to set up on reflection ultrasonic echo radiofrequency signal s and grid node scatter between sub- scatter intensity distribution I
The Mathematical Modeling of relation, forms the equation group of following form：
S=MI
Wherein, matrix M is encoder matrix (encoding matrix).But it is under normal circumstances one to solve equation group
Ill-posed problem, i.e. equation quantity are less than unknown number quantity, 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 can lead to
Overcompression cognitive method is solved to above-mentioned equation group：
Wherein β reflects us allows how many noise contributions to exist.
For ultrasonic imaging, in (1st) 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 encoder matrix M for being easy to complete follow-up iterative calculation accordingly,
It is the key for determining ultrasonic imaging quality and imaging method practicality.And in (2nd) step, the specific calculating side of solving equations
Method has had the iterative numerical approach of many maturations available, is not belonging to the emphasis of the application elaboration.
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 two：
The first Mathematical Modeling：The more complicated model of the compressibility distribution situation based on medium to be imaged
The final form of the first Mathematical Modeling is：
Wherein, G is a NelNkThe encoder matrix of × N, NelIt is the port number of ultrasound transducer array reception echo-signal,
NkThe ultrasound echo signal in broadband is divided into N by fingerkIndividual discrete wave number kl, 1≤l≤Nk, N=Nx×NzIt is total pixel of image
Number (or perhaps grid node number), Nx, NzIt is respectively x directions (width) and z directions (depth direction) epigraph pixel
Line number and columns.Each element definition in matrix G is：
Wherein, m represents m-th array element on transducer, 1≤m≤Nel, i represents the ith pixel on image, Represent the acoustic pressure of incident ultrasound, rel,mRepresent m-th locus of array element, r on ultrasonic transduceri
Represent the position of ith pixel on image, 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, γκ
Represent the compressibility of the medium to be imaged distribution situation (compressibility of medium be determine its sound scattering intensity it is main because
Element).
Second Mathematical Modeling：Fairly simple model based on frequency-region signal time delay
The final form of second Mathematical Modeling is：X (ω)=A (ω) S (ω)
Processed by being then based on frequency-region signal, actually taken ω=2 π f0, wherein, f0It is the ultrasonic transduction for being used
The emission center frequency of device.X is that, by the ultrasonic echo radiofrequency signal after Short Time Fourier Transform, S is the scattering to be imaged
Sub- scattering strength corresponds to f on frequency domain0Mapping, A for K × L the encoder matrix being made up of time delay data, definition
For：
[A(ω)k]i=exp [j ω τk(ρi)]
Wherein, K be ultrasound transducer array receive echo-signal port number, L for image total pixel count (in other words
It is grid node number), 1≤k≤K, 1≤i≤L, ρiA pixel (or grid node) on image is represented,The echo-signal that expression sends from certain pixel reaches certain ultrasound transducer array and leads to
The time delay in road, rkThe locus of certain ultrasound transducer array passage is represented,Represent certain pixel ρiSpace
Position.It may be noted that X be intercepted out from whole ultrasonic echo radiofrequency signals it is a bit of carry out short time discrete Fourier transform after obtain
Frequency-region signal, if therefore whole ultrasonic echo radiofrequency signal is divided into Q section, to complete all to be imaged, it is necessary to will be follow-up
Solution procedure is repeated Q times.
After setting up above-mentioned two model, solving equations are carried out by compression sensing method, it is possible to solve γκ(first
Plant Mathematical Modeling) or S (second Mathematical Modeling), then by it from the matrix that vector transformation is correspondence image pixel quantity,
Our the desired images for obtaining can be just shown as.
Above-mentioned two reflects relation between sub- scatter intensity distribution is scattered on ultrasonic echo radiofrequency signal and grid node
Mathematical Modeling, respectively there is its limitation.
The foundation of the first Mathematical Modeling, is gone out from the Mathematical Modeling for being proved to more accurately acoustic propagation and scattering
Hair, advantage be can more real reflection sound various physical phenomenons in media as well, but shortcoming is also clearly, is exactly model
It is excessively complicated.The size of encoder matrix G is excessively huge, it is necessary to take a large amount of internal memories, while also resulting in follow-up solution procedure
Amount of calculation 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 be counted using when calling G every time
Calculate the method for its each element numerical value to carry out, significantly increase amount of calculation.And, actually above-mentioned parameter value at all cannot
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 completely the task that common computer can undertake.
The first Mathematical Modeling due to only considering the time delay of ultrasonic echo radiofrequency signal, while in only considering ultrasound
Heart tranmitting frequency f0Greatly contracted without other frequency contents of consideration signal, therefore the scale of its encoder matrix A (ω) for being used
It is small.But, the model still has following problem.First, all elements of matrix A (ω) are all non-zeros, and X is from complete
The a bit of frequency-region signal for carrying out and being obtained after short time discrete Fourier transform is intercepted out in portion's ultrasonic echo radiofrequency signal, if all ultrasounds
Echo radiofrequency signal is divided into Q sections, then to complete all imagings, it is necessary to follow-up solution procedure is repeated Q times, therefore after carrying out
Amount of calculation is still very big during continuous matrix multiplication operation.Secondly, for convenience time delay calculating is carried out to signal, the model
All computings all carried out in frequency domain.This is accomplished by, first by the ultrasonic echo radiofrequency signal of time domain, becoming by Fourier in short-term
Change and be transformed into frequency domain.This process not only increases amount of calculation, can also introduce due to the leakage errors of the limited generation of signal length
And leakage error, and then have influence on final image quality.
The purpose of the technical program is relative to the first Mathematical Modeling, encoder matrix to be simplified as far as possible, when reducing computing
Memory storage space and amount of calculation；Relative to the second Mathematical Modeling, it is to avoid use Fourier transform and frequency-domain calculations；Ensureing
Frame frequency high and while compared with high imaging quality, the hardware computing platform that realization only needs to reduced levels can just be carried out using this method
Imaging, is easy to implement the industry conversion of the technical program.
The technical program by ultrasonic echo radiofrequency signal relative to ultrasonic wave x time time delay information with dissipate
The relation penetrated between the spatial positional information of sub- distribution, sets up the encoder matrix M in time domain expression, forms following reflection ultrasound
The equation group s=MI of relation between sub- scatter intensity distribution I is scattered on echo rf digital signal s and grid node；Due to this
When encoder matrix M be a sparse matrix, therefore internal memory of its occupancy can be greatly lowered by way of sparse expression deposit
Storage space, while amount of calculation when using its computing is also very low.Finally, by ripe compressed sensing algorithm to above-mentioned side
Journey group is solved, and obtains vectorial I, as desired to obtain by it from the matrix that vector transformation is correspondence image pixel quantity
The ultrasonoscopy for obtaining.
After general principle of the invention is described, lower mask body introduces various non-limiting embodiment party of the invention
Formula.
Application scenarios overview
Ultrasonic imaging is using ultrasonic acoustic beam scanning human body, by the reception to reflected signal, treatment, to obtain internal device
The image of official.Conventional ultrasonic instrument has various：A types (amplitude mode) are to represent the strong of reflected signal with the height of wave amplitude
It is weak, it is shown that a kind of " echogram ".M types (spot scan type) are represented from shallow to deep locus, water with vertical direction
Square to the time is represented, movement profiles of the luminous point in different time are shown as.Above amphitypy is one-dimensional display, range of application
It is limited.Type B (brightness mode) is tomosonography instrument, referred to as " B ultrasonic ".It is that reception signal is represented with the different luminous point of brightness
Power, when probe is moved along horizontal level, luminous point on display screen also synchronizing moving in the horizontal direction connects luminescent spot track
It is two-dimensional imaging into the sectional drawing that ultrasonic acoustic beam is scanned.Because Type B ultrasonic image is clear, directly perceived, stereovision is strong, therefore is facing
Bed is widely used.It is that .C types are made then with the scan mode of approximate TV according to principle of Doppler as D types, shows vertical
Directly in the cross section acoustic image of acoustic beam.In recent years, ultrasonic imaging technique is continued to develop, and such as GTG show and colored display, real-time
Imaging, ultrasound holography, penetration ultrasonic imaging, ultrasonoscope and machine tomography rubbish shadow, three-dimensional imaging, ultrasonic imaging in body cavity
Deng.
Ultrasonic imaging method is commonly used to judge the position of internal organs, size, form, determines the scope and physical property of focus,
The internal anatomy of some gland tissues is provided, differentiate fetus it is normal with it is abnormal, in ophthalmology, gynemetrics and cardiovascular system, digestion
System, urinary system application it is quite varied.
The technical program enters row energization to ultrasound transducer array by computer controls ultrasound emission circuit first, and transmitting is super
Acoustical signal.When each passage (each passage corresponds to an array element) of ultrasound transducer array is excited simultaneously, launch
Ultrasonic signal, ultrasonic signal is propagated in media as well, is scattered, and forms ultrasound echo signal.Ultrasound echo signal is changed by ultrasound
Energy device array received, forms ultrasonic echo radiofrequency signal, then by ultrasonic reception circuit sampling, forms ultrasonic echo RF digital letter
Number.Ultrasonic echo rf digital signal is sent back in computer, and realizes ultrasonic imaging in a computer.
Illustrative methods
Next, being introduced to exemplary embodiment of the invention with reference to Fig. 2.
As shown in Fig. 2 being a kind of ultrasonic imaging method flow chart proposed by the present invention.The method includes：
Step 201)：Obtain N × K very first time delayed data tn,k；Wherein, the very first time delayed data tn,kFor
Ultrasonic signal, by n-th scattering of scattering, returns k-th of ultrasound transducer array since the ultrasound emission moment
Total time delay of channel position；N represents the pixel number of the ultrasonoscopy wanted, and K is represented in ultrasound transducer array
Array element number；N represents some scattering, scatters sub- n=1,2 ... ..., N；Some leads to during k represents ultrasound transducer array
Road, k=1,2 ... ..., K；
Step 202)：Obtain D × K the second time delay data td,k；Wherein, the second time delay data td,kFor
Known the elapsed time postpones, and starts to sample ultrasonic echo radiofrequency signal since the ultrasound emission moment, obtains ultrasound and returns
Ripple rf digital signal, the moment of k-th channel reception to d-th data point of the ultrasonic echo rf digital signal is relative
In the time delay of ultrasonic signal delivery time；D represents the sampling number of each passage, and d represents that a channel reception is returned to ultrasound
The a certain data point of ripple rf digital signal, d=1,2 ... ..., D；
Step 203)：By the ultrasonic echo rf digital signal, accordingly matrixing is that length is the vectorial s of D × K；
Step 204)：Using the corresponding second time delay data t of data point d of k-th passage in the vectorial sd,kWith
And corresponding very first time delayed data t under same channelsn,kDetermine matrix M；Wherein, the matrix M is sparse matrix；
Step 205)：Equation group is set up according to the vectorial s and the matrix M；Wherein, the equation group is：S=MI；I
For the length for representing the scatter intensity distribution of scattering is the vector of N；
Step 206)：The equation group is solved by compressed sensing algorithm, vectorial I is obtained；
Step 207)：According to the ultrasonoscopy that the vectorial I determines to want.
This method is not limited to just in the imaging of plane of ultrasound ripple.If for example, ultrasound transducer array send be
Convex surface ripple or concave surface ripple, as long as the case may be, changing above-mentioned calculating ultrasonic signal since the ultrasound emission moment, pass through
The scattering of certain scattering is crossed, the very first time delayed data t of certain element position of ultrasound transducer array is returnedn,k's
Computing formula.Other all sames.
So that ultrasonic signal is plane of ultrasound ripple signal as an example, it is known that ultrasound transducer array includes K array element, wherein kth
The coordinate of individual array element is (xk,0).The pixel number (the grid node number for being divided to imaging plane) of the ultrasonoscopy wanted
It is N=Nx×Nz, wherein, Nx、NzBe respectively x directions (width) and z directions (depth direction) epigraph pixel line number and
Columns.The coordinate of the sub- n of scattering at some grid node is (xn,zn).Then have, ultrasonic signal since the ultrasound emission moment,
By the scattering of this scattering, k-th element position of ultrasound transducer array is returned, total very first time delay is：
Wherein, c is sound wave spread speed in media as well.It is corresponding, N × K very first time delayed data can be obtained
tn,k。
It is known since the ultrasound emission moment, by t0Time delay, start to adopt ultrasonic echo radiofrequency signal
Sample, sample frequency is fs, the sampling number of each passage is D, then d of k-th channel reception to ultrasonic echo radiofrequency signal
At the time point of individual data, the time delay relative to the ultrasound emission moment is：
td,k=t0+(d-1)/fs
It is corresponding, D × K the second time delay data t can be obtainedd,k。
Include for the present embodiment, the step of determine matrix M：
Data point d to k-th passage sets up the vectorial m that length is N, obtains D × K vector m；In the vectorial m
Each element determines that method is：If the corresponding second time delay data t of the data point d of k-th passaged,kAnd it is identical logical
Corresponding very first time delayed data t under roadn,kMeetThen from n-th ultrasonic echo of scattering son scattering
Information is included in k-th data point d of passage, then nth elements are set to 1 in vector m, otherwise, are set to 0；
D × K vector m is configured to the matrix M of D × K row, N row.
It is described to include the step of solved by compressed sensing algorithm to the equation group for the present embodiment：
If vector I is sparse, equation group s=MI is solved by compressed sensing algorithm, that is, metThe I values of condition are the optimal solution of equation group；Wherein, β represents permission how many noise contribution
In the presence of；S.t. it is the formal notation for representing logical relation；
Otherwise, sparse transformation is carried out to vectorial I；Equation group s=MI is solved by compressed sensing algorithm, that is, is metThe I values of condition are the optimal solution of equation group；Wherein, Ψ represents sparse transformation matrix, β
Representing allows how many noise contributions to exist；S.t. it is the formal notation for representing logical relation.
For the technical program, ripe compressed sensing algorithm includes but is not limited to matching pursuit algorithm (matching
Pursuitmethod), Bregman algorithms, operator/variable splitting algorithm (operator/variable splitting),
Fixing point continuation algorithm (Fixed-point continuation), L1 norm magics algorithm (L1-magic), Newton tangential method
Deng.
For the present embodiment, it is determined that want ultrasonoscopy the step of include：
Vectorial I is transformed to image array Φ；Wherein, described image matrix Φ is a NXThe matrix of row Nz row；NXRepresent
The number of x directions epigraph pixel in three-dimensional system of coordinate, Nz represents the number of z directions epigraph pixel in three-dimensional system of coordinate, N=
Nx×Nz；
To the matrix Φ treatment, the ultrasonoscopy wanted is obtained；Wherein, the method for the treatment of includes：The number of winning the confidence
Envelope, log-compressed, adjustment and carry out digital scan conversion at image display dynamic range.
In the present embodiment, the technical program is verified using Field II ultrasonic imagings simulation software.Such as Fig. 3
It is shown, it is the simulation experiment result figure being imaged to the sparse imitative body of point-like using the technical program.As shown in figure 4, to adopt
The simulation experiment result figure being imaged to the sparse imitative body of point-like with traditional time delay addition method (DAS).Can be with by contrast
It was found that, the technical program can remove the horizontal artifact occurred in conventional method.
As shown in figure 5, being the simulation result figure being imaged to non-sparse imitative body using the technical program.As shown in fig. 6,
It is the simulation result figure being imaged to non-sparse imitative body using traditional time delay addition method (DAS).By contrast it can be found that
The technical program can obtain more preferable contrast, and can remove the artifact occurred in conventional method near field.
As shown in fig. 7, being renal tissue section original image.As shown in figure 8, being the imaging obtained using the technical program
Result figure.As shown in figure 9, being the imaging results figure obtained using traditional time delay addition method (DAS).Found by contrast, this
Image formed by technical scheme, shows that the profile of kidney, structure are apparent, and soft tissue level becomes apparent from, and contrast in tissue increases,
And the artifact occurred in conventional method near field can be removed.
The technical program considers that ultrasonic echo radiofrequency signal, relative to the time delay of ultrasonic wave x time, does not differentiate between it
In different frequency composition, it is all greatly simplified relative to the first Mathematical Modeling, the second Mathematical Modeling.The technical program returns ultrasound
Ripple radiofrequency signal has been contacted relative to the time delay information of ultrasonic wave x time with the spatial positional information of scattering son distribution
Come, by setting up more massive encoder matrix M, solve the time domain expression problem to signal time Delay computing, no longer need
Carry out Fourier transform and calculated in frequency domain, it is to avoid because carry out Fourier transform and caused by calculation error.
Further, since the encoder matrix M that the technical program is set up is a sparse matrix, can be by sparse expression
Mode is greatly lowered the memory storage space of its occupancy, while amount of calculation when using its computing is also very low.With us
As a example by the simulation imaging experiment for carrying out, the data of ultrasonic echo radiofrequency signal points are 128 × 4364, and institute is into image pixel
It is 256 × 3000 to count, then the size of matrix M is 558592 × 768000, it is assumed that all elements in matrix M are all 64bit
Double-precision number, then it is 3423GB to need memory storage space.In fact, due to matrix M be it is sparse, nonzero element therein
Quantity is 98 × 106, therefore when using sparse expression, the memory storage space of the actual occupancy of M is 1.57GB.Compared to first
For Mathematical Modeling, if Nk1000 are taken, then its encoder matrix G needs 786GB memory storage spaces.It can be seen that the technical program institute
The memory storage space of occupancy greatly reduces.
Compared to the second Mathematical Modeling, although its encoder matrix A only needs to the memory space of 786MB, but due to need by
Whole ultrasonic echo radiofrequency signals are divided into Q sections, and the every one piece of data to intercepting out carries out short time discrete Fourier transform to obtain frequency domain
Signal, and repeat follow-up solution calculating.Therefore, the second Mathematical Modeling in total amount of calculation still above the technical program
(need certain overlap to improve the resolution ratio of depth direction, therefore number more than 4000 between former and later two segmentations of data
The length at strong point at least needs to be divided into 100 sections).Additionally, the second Mathematical Modeling for convenience time delay is carried out to signal
Calculate, all computings are all carried out in frequency domain.And Short Time Fourier Transform is calculated and not only increases amount of calculation, can also introduce due to letter
Leakage errors and leakage error that number limited length is produced, and then have influence on final image quality.
It should be noted that although the operation of the inventive method is described with particular order in the accompanying drawings, this is not required that
Or imply that these must be performed according to the particular order operates, or the operation having to carry out shown in whole could realize the phase
The result of prestige.Additionally or alternatively, it is convenient to omit some steps, multiple steps are merged into a step to perform, and/or will
One step is decomposed into execution of multiple steps.
Example devices
The device of exemplary embodiment of the invention is introduced below with reference to Figure 10.
As shown in Figure 10, a kind of supersonic imaging device block diagram proposed by the present invention.The device includes：
Very first time delayed data determining unit 101, for obtaining N × K very first time delayed data tn,k；Wherein, institute
State very first time delayed data tn,kIt is ultrasonic signal since the ultrasound emission moment, by n-th scattering of scattering, then returns
To total time delay of k-th channel position of ultrasound transducer array；N represents the pixel of the ultrasonoscopy wanted
Number, K represents array element number in ultrasound transducer array；N represents some scattering, scatters sub- n=1,2 ... ..., N；K is represented
Some passage, k=1,2 ... ..., K in ultrasound transducer array；
Second time delay data determination unit 102, for obtaining D × K the second time delay data td,k；Wherein, institute
State the second time delay data td,kFor known since the ultrasound emission moment, the elapsed time postpones, and starts to ultrasonic echo radio frequency
Signal is sampled, and obtains ultrasonic echo rf digital signal, the ultrasonic echo radiofrequency signal after k-th channel reception to sampling
Time delay of d-th data point relative to ultrasonic signal delivery time；D represents the sampling number of each passage, and d represents one
Channel reception to ultrasonic echo rf digital signal a certain data point, d=1,2 ... ..., D；
Converter unit 103, for accordingly matrixing to be that length is D × K by the ultrasonic echo rf digital signal
Vectorial s；
Matrix determining unit 104, prolongs for data point d corresponding second times using k-th passage in the vectorial s
Slow data td,kAnd corresponding very first time delayed data t under same channelsn,kDetermine matrix M；Wherein, the matrix M is dilute
Dredge matrix；
Model sets up unit 105, for setting up equation group according to the vectorial s and the matrix M；Wherein, the equation
Group is：S=MI；I represents that the scatter intensity distribution of scattering, length are the vector of N；
Unit 106 is solved, for being solved by compressed sensing algorithm to the equation group, vectorial I is obtained；
Ultrasound imaging unit 107, for the ultrasonoscopy for determining to want according to the vectorial I.
For the present embodiment, the matrix determining unit 104 includes：
Vector sets up module, and the vectorial m that length is N is set up for the data point d to k-th passage, obtain D × K to
Amount m；Each element in the vectorial m determines that method is：If corresponding second time delays of the data point d of k-th passage
Data td,kAnd corresponding very first time delayed data t under same channelsn,kMeetThen from n-th scattering
The ultrasonic echo information of son scattering is included in k-th data point d of passage, then nth elements are set to 1 in vector m, otherwise,
It is set to 0；
Constructing module, the matrix M for D × K vector m to be configured to D × K row, N row.
For the present embodiment, the ultrasonic signal of the supersonic imaging device treatment is plane of ultrasound ripple signal.It is this
In the case of, the very first time delayed data t that the very first time delayed data determining unit is obtainedn,kExpression formula be：
Wherein, k-th coordinate of passage is (xk,0)；The coordinate of n-th scattering of the ultrasonoscopy wanted is (xn,
zn)；C represents sound wave spread speed in media as well.
This method is not limited to just in the imaging of plane of ultrasound ripple.If for example, ultrasound transducer array send be
Convex surface ripple or concave surface ripple, as long as the case may be, changing above-mentioned calculating ultrasonic signal since the ultrasound emission moment, pass through
The scattering of certain scattering is crossed, the very first time delayed data t of certain element position of ultrasound transducer array is returnedn,k's
Computing formula.Other all sames.
The second time delay data t that the second time delay data determination unit is obtainedd,kExpression formula be：
td,k=t0+(d-1)/fs
Wherein, t0Represent time-delay value, fsRepresent sample frequency.
For the present embodiment, the solution unit 106 includes：
First solves module, for the vectorial I it is sparse when, equation group s=MI is asked by compressed sensing algorithm
Solution, that is, meetThe I values of condition are the optimal solution of equation group；Wherein, β represents that permission is more
Few noise contribution is present；S.t. it is the formal notation for representing logical relation；
Second solves module, for the vectorial I it is not sparse when, sparse transformation is carried out to vectorial I；Calculated by compressed sensing
Method is solved to equation group s=MI, that is, meetThe I values of condition be equation group most
Excellent solution；Wherein, Ψ represents sparse transformation matrix, and β represents that the how many noise contributions of permission are present；S.t. it is the public affairs for representing logical relation
Formula symbol.
For the present embodiment, ripe compressed sensing algorithm includes but is not limited to matching pursuit algorithm (matching
Pursuitmethod), Bregman algorithms, operator/variable splitting algorithm (operator/variable splitting),
Fixing point continuation algorithm (Fixed-point continuation), L1 norm magics algorithm (L1-magic), Newton tangential method
Deng.
Preferably, the ultrasound imaging unit 107 includes：
Conversion module, for vectorial I to be transformed into image array Φ；Wherein, described image matrix Φ is a NXRow Nz
The matrix of row；NXThe number of x directions epigraph pixel in three-dimensional system of coordinate is represented, Nz represents the upper figure in z directions in three-dimensional system of coordinate
As the number of pixel, N=Nx×Nz；
Processing module, for the matrix Φ treatment, obtaining the ultrasonoscopy wanted；Wherein, the side for the treatment of
Method includes：Take signal envelope, log-compressed, adjustment image display dynamic range and carry out digital scan conversion.
Have above-mentioned example method describe understand, the technical program on the one hand can realize superelevation frame frequency it is quick ultrasound into
Picture, on the other hand ensure that image quality higher, while the hardware computation platform for only needing to reduced levels can be achieved with, be easy to
Realize that industry is converted.
Although it should be noted that being referred to supersonic imaging device in above-detailed for a kind of appliance computer software generation
The device that code is realized, some units or module that the device includes, but this division is only not enforceable.It is actual
On, according to the embodiment of the present invention, the feature and function of above-described two or more devices can be in a system
Embody.Conversely, the feature and function of an above-described system can be further divided into being embodied by multiple devices.
Above-described specific embodiment, has been carried out further to the purpose of the present invention, technical scheme and beneficial effect
Describe in detail, should be understood that and the foregoing is only specific embodiment of the invention, be not intended to limit the present invention
Protection domain, all any modification, equivalent substitution and improvements within the spirit and principles in the present invention, done etc. all should include
Within protection scope of the present invention.
Claims (18)
1. a kind of ultrasonic imaging method, it is characterised in that the method includes：
Obtain N × K very first time delayed data tn,k；Wherein, the very first time delayed data tn,kIt is ultrasonic signal from super
The sound emission moment, by n-th scattering son scattering, return ultrasound transducer array k-th channel position it is total
Time delay；N represents the pixel number of the ultrasonoscopy wanted, and K represents array element number in ultrasound transducer array；N tables
Show some scattering, scatter sub- n=1,2 ... ..., N；K represents some passage in ultrasound transducer array, k=1,
2 ... ..., K；
Obtain D × K the second time delay data td,k；Wherein, the second time delay data td,kSent out from ultrasound for known
Penetrate and start constantly, the elapsed time postpones, and starts to sample ultrasonic echo radiofrequency signal, obtain ultrasonic echo RF digital letter
Number, the moment of k-th channel reception to d-th data point of the ultrasonic echo rf digital signal is sent out relative to ultrasonic signal
Send the time delay at moment；D represents the sampling number of each passage, and d represents that a channel reception is believed to ultrasonic echo RF digital
Number a certain data point, d=1,2 ... ..., D；
By the ultrasonic echo rf digital signal, accordingly matrixing is that length is the vectorial s of D × K；
Using the corresponding second time delay data t of data point d of k-th passage in the vectorial sd,kAnd under same channels
Corresponding very first time delayed data tn,kDetermine matrix M；Wherein, the matrix M is sparse matrix；
Equation group is set up according to the vectorial s and the matrix M；Wherein, the equation group is：S=MI；I is sub to represent scattering
Scatter intensity distribution length for N vector；
The equation group is solved by compressed sensing algorithm, vectorial I is obtained；
According to the ultrasonoscopy that the vectorial I determines to want.
2. the method for claim 1, it is characterised in that include the step of the determination matrix M：
Data point d to k-th passage sets up the vectorial m that length is N, obtains D × K vector m；Each in the vectorial m
Element determines that method is：If the corresponding second time delay data t of the data point d of k-th passaged,kAnd under same channels
Corresponding very first time delayed data tn,kMeetThen from n-th ultrasonic echo information of scattering son scattering
It is included in k-th data point d of passage, then nth elements are set to 1 in vector m, otherwise, are set to 0；
D × K vector m is configured to the matrix M of D × K row, N row.
3. method as claimed in claim 1 or 2, it is characterised in that the ultrasonic signal is plane of ultrasound ripple signal.
4. method as claimed in claim 3, it is characterised in that the very first time delayed data tn,kExpression formula be：
Wherein, k-th locus coordinate of passage is (xk,0)；N-th space of scattering on the ultrasonoscopy wanted
Position coordinates is (xn,zn)；C represents sound wave spread speed in media as well；X directions are the width of ultrasonoscopy, z directions
It is the depth direction of ultrasonoscopy.
5. method as claimed in claim 1 or 2, it is characterised in that the ultrasonic signal is recessed ultrasonic convex surface ripple signal, ultrasound
Face ripple signal.
6. method as claimed in claim 1 or 2, it is characterised in that the second time delay data td,kExpression formula be：
td,k=t0+(d-1)/fs
Wherein, t0Represent and prolong since the time the ultrasound emission moment carries out sampling instant to ultrasonic echo radiofrequency signal
It is worth late, fsRepresent sample frequency.
7. method as claimed in claim 1 or 2, it is characterised in that described to be entered by compressed sensing algorithm to the equation group
The step of row is solved includes：
If vector I is sparse, equation group s=MI is solved by compressed sensing algorithm, that is, met The I values of condition are the optimal solution of equation group；Wherein, β represents permission how many noise contribution
In the presence of；S.t. it is the formal notation for representing logical relation；
Otherwise, sparse transformation is carried out to vectorial I；Equation group s=MI is solved by compressed sensing algorithm, that is, is met The I values of condition are the optimal solution of equation group；Wherein, Ψ represents sparse transformation matrix, β
Representing allows how many noise contributions to exist；S.t. it is the formal notation for representing logical relation.
8. method as claimed in claim 7, it is characterised in that the compressed sensing algorithm is that matching pursuit algorithm, Bregman are calculated
Method, operator/variable splitting algorithm, fixing point continuation algorithm, L1 norm magics algorithm, Newton tangential method.
9. method as claimed in claim 1 or 2, it is characterised in that include the step of the ultrasonoscopy that the determination is wanted：
Vectorial I is transformed to image array Φ；Wherein, described image matrix Φ is a NxRow NzCapable matrix；NxRepresent three-dimensional
The number of x directions epigraph pixel, N in coordinate systemzRepresent the number of z directions epigraph pixel in three-dimensional system of coordinate, N=Nx×
Nz；
To the matrix Φ treatment, the ultrasonoscopy wanted is obtained；Wherein, the method for the treatment of includes：Take signal envelope,
Log-compressed, adjustment and carry out digital scan conversion at image display dynamic range.
10. a kind of supersonic imaging device, it is characterised in that the device includes：
Very first time delayed data determining unit, for obtaining N × K very first time delayed data tn,k；Wherein, described first
Time delay data tn,kIt is ultrasonic signal since the ultrasound emission moment, by n-th scattering of scattering, returns ultrasound
Total time delay of k-th channel position of transducer array；N represents the pixel number of the ultrasonoscopy wanted, and K is represented
Array element number in ultrasound transducer array；N represents some scattering, scatters sub- n=1,2 ... ..., N；K represents ultrasonic transduction
Some passage, k=1,2 ... ..., K in device array；
Second time delay data determination unit, for obtaining D × K the second time delay data td,k；Wherein, described second
Time delay data td,kFor known since the ultrasound emission moment, the elapsed time postpones, and starts to enter ultrasonic echo radiofrequency signal
Row sampling, obtains ultrasonic echo rf digital signal, d of k-th channel reception to the ultrasonic echo rf digital signal
Time delay of the individual data point relative to ultrasonic signal delivery time；D represents the sampling number of each passage, and d represents a passage
Receive a certain data point of ultrasonic echo rf digital signal, d=1,2 ... ..., D；
Converter unit, for accordingly matrixing to be that length is the vectorial s of D × K by the ultrasonic echo rf digital signal；
Matrix determining unit, for the corresponding second time delay data of data point d using k-th passage in the vectorial s
td,kAnd corresponding very first time delayed data t under same channelsn,kDetermine matrix M；Wherein, the matrix M is sparse matrix；
Model sets up unit, for setting up equation group according to the vectorial s and the matrix M；Wherein, the equation group is：S=
MI；I represents that the scatter intensity distribution of scattering, length are the vector of N；
Unit is solved, for being solved by compressed sensing algorithm to the equation group, vectorial I is obtained；
Ultrasound imaging unit, for the ultrasonoscopy for determining to want according to the vectorial I.
11. devices as claimed in claim 10, it is characterised in that the matrix determining unit includes：
Vector sets up module, and the vectorial m that length is N is set up for the data point d to k-th passage, obtains D × K vector m；
Each element in the vectorial m determines that method is：If the corresponding second time delay data of the data point d of k-th passage
td,kAnd corresponding very first time delayed data t under same channelsn,kMeetThen dissipated from n-th scattering
The ultrasonic echo information penetrated is included in k-th data point d of passage, then nth elements are set to 1 in vector m, otherwise, are set to
0；
Constructing module, the matrix M for D × K vector m to be configured to D × K row, N row.
12. device as described in claim 10 or 11, it is characterised in that the ultrasonic signal of supersonic imaging device treatment is
Plane of ultrasound ripple signal.
13. devices as claimed in claim 12, it is characterised in that the very first time delayed data determining unit obtain the
One time delayed data tn,kExpression formula be：
Wherein, k-th coordinate of passage is (xk,0)；The coordinate of n-th scattering of the ultrasonoscopy wanted is (xn,zn)；
C represents sound wave spread speed in media as well.
14. device as described in claim 10 or 11, it is characterised in that the ultrasonic signal of supersonic imaging device treatment is
Ultrasonic convex surface ripple signal, ultrasonic concave surface ripple signal.
15. device as described in claim 10 or 11, it is characterised in that the second time delay data determination unit is obtained
The second time delay data td,kExpression formula be：
td,k=t0+(d-1)/fs
Wherein, t0Represent time-delay value, fsRepresent sample frequency.
16. device as described in claim 10 or 11, it is characterised in that the solution unit includes：
First solves module, for the vectorial I it is sparse when, equation group s=MI is solved by compressed sensing algorithm, i.e.,
Meet The I values of condition are the optimal solution of equation group；Wherein, β represents permission how many noise
Composition is present；S.t. it is the formal notation for representing logical relation；
Second solves module, for the vectorial I it is not sparse when, sparse transformation is carried out to vectorial I；By compressed sensing algorithm pair
Equation group s=MI is solved, that is, meet The I values of condition are optimal for equation group
Solution；Wherein, Ψ represents sparse transformation matrix, and β represents that the how many noise contributions of permission are present；S.t. it is the formula for representing logical relation
Symbol.
17. devices as claimed in claim 16, it is characterised in that the compressed sensing algorithm that the solution unit is used is matching
Back tracking method, Bregman algorithms, operator/variable splitting algorithm, fixing point continuation algorithm, L1 norm magics algorithm, newton decline
Method.
18. device as described in claim 10 or 11, it is characterised in that the ultrasound imaging unit includes：
Conversion module, for vectorial I to be transformed into image array Φ；Wherein, described image matrix Φ is a NxThe square of row Nz row
Battle array；NXThe number of x directions epigraph pixel in three-dimensional system of coordinate is represented, Nz represents z directions epigraph pixel in three-dimensional system of coordinate
Number, N=Nx×Nz；
Processing module, for the matrix Φ treatment, obtaining the ultrasonoscopy wanted；Wherein, the method bag for the treatment of
Include：Take signal envelope, log-compressed, adjustment image display dynamic range and carry out digital scan conversion.
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| CN106691499B (en) * | 2015-07-17 | 2020-09-18 | 安克生医股份有限公司 | Method for analyzing an ultrasonic echo signal using scatterer distribution statistics |
| WO2017035838A1 (en) * | 2015-09-06 | 2017-03-09 | 深圳迈瑞生物医疗电子股份有限公司 | Ultrasound gray-scale imaging system and method |
| CN105748103B (en) * | 2016-04-22 | 2019-08-23 | 深圳先进技术研究院 | Delayed excitation ultrasonic imaging method and device |
| CN106680825B (en) * | 2016-12-05 | 2019-06-04 | 中国科学院声学研究所 | A kind of acoustic array imaging system and method |
| CN106780329B (en) * | 2016-12-07 | 2019-08-30 | 华中科技大学 | A kind of plane of ultrasound wave imaging method based on the transformation of anti-perspective plane |
| CN106997045B (en) * | 2017-03-06 | 2020-08-28 | 中国科学院深圳先进技术研究院 | Ultrasonic imaging method based on ultrasonic system point spread function measurement and compressed sensing |
| CN106940883B (en) * | 2017-03-06 | 2020-10-16 | 中国科学院深圳先进技术研究院 | Ultrasonic imaging method based on point spread function simulation and compressed sensing of ultrasonic system |
| WO2019095376A1 (en) * | 2017-11-20 | 2019-05-23 | 深圳迈瑞生物医疗电子股份有限公司 | Ultrasound contrast imaging method and ultrasound imaging system |
| CN108445083A (en) * | 2018-02-11 | 2018-08-24 | 天津大学 | A kind of phased array supersonic image reconstruction optimization method based on frequency domain compressed sensing |
| CN109758091B (en) * | 2018-12-03 | 2020-12-01 | 深圳先进技术研究院 | Ultrasonic imaging method and device |
| CN110244305A (en) * | 2019-07-10 | 2019-09-17 | 南京信息工程大学 | A kind of emulation mode of Underwater Target Signal scattering |
| CN111580112B (en) * | 2020-06-11 | 2023-02-14 | 南京信息工程大学 | Underwater sonar sensor array imaging method based on plane waves |
Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN102920478A (en) * | 2012-11-22 | 2013-02-13 | 山东大学 | Synthetic-focusing imaging method of portable type-B ultrasonic equipment |
| EP2660618A1 (en) * | 2012-05-04 | 2013-11-06 | Esaote S.p.A. | Biomedical image reconstruction method |
Family Cites Families (2)
| Publication number | Priority date | Publication date | Assignee | Title |
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| US7584062B1 (en) * | 2008-06-20 | 2009-09-01 | The Boeing Company | Sub-wavelength ultrasound characterization of composite material |
| CN102058416B (en) * | 2010-12-14 | 2012-09-19 | 哈尔滨工业大学 | Microwave thermoacoustic imaging device and method based on compressive sensing |
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Patent Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
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