CN106618639B - A kind of quantitative shearing wave elastograph imaging method - Google Patents
A kind of quantitative shearing wave elastograph imaging method Download PDFInfo
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Abstract
The present invention relates to Medical ultrasound image technology field, in particular to a kind of quantitative shearing wave elastograph imaging method.The strain of ultrasonic quantitative elastograph imaging method provided by the invention and system based on sliding window linear fit and the shear-wave velocity detection algorithm using two-dimensional linear fitting, noise resisting ability is stronger, as a result more reliable.Simultaneously in the case where not increasing ultrasonic front end storage additionally with transmission module load, realizes ultrasonic universe and quantify elastogram, significantly reduce the design difficulty and equipment cost of ultrasonic quantitative elastogram system.
Description
Technical field
The present invention relates to Medical ultrasound image technology field, in particular to a kind of quantitative shearing wave elastograph imaging method.
Background technique
In recent years, tumor disease has become the primary killers for endangering our people's health.The prevention and treatment of tumor disease
Key is early detection.Clinically, often tumor disease mostly important early stage is pre- for the mechanical characteristics variation of tissue
Alert signal, such as mammary gland, thyroid gland neoplastic lesion.With the growth of tumour, pathological tissues are compared with normal tissue, viscoelasticity hair
Raw large change, if breast cancer about differs 90 times with normal surrounding tissue, fibrosed tissue, non-invasive carcinoma becomes and wellability
Also there is larger difference in the shearing elasticity coefficient of cancerous issue, therefore, obtain tissue parameter information relevant to viscoplasticity
(such as deformational displacement, shear wave velocity etc.) in area of medical diagnostics especially to breast cancer, thyroid cancer and prostate cancer early stage
Detection is of great significance.
Medical ultrasonic elastogram be it is a kind of by histokinesis show the ultrasound of tissue elasticity modulus or soft or hard degree at
Image space formula, traditional squash type elastogram mode need doctor to make its movement under force using probe pinch detection position, thus
Obtain tissue elasticity information, the deficiency of this mode is: doctor needs with operation pinch detection position appropriate, subjectivity
By force；Due to needing doctor to squeeze, the result of different doctors operation or the operation of same doctor's different times is difficult directly to carry out pair
Than testing result is difficult to reappear, and can only often be used as qualitative testing result, quantitative detection information can not be obtained, to disease
The tracking and clinical follow of disease.
The Ultrasonic Elasticity Imaging that can be carried out quantitative analysis at present, is mainly based upon acoustic radiation force elastogram
(Acoustic Radiation Force Imaging, ARFI), ARFI utilize the focusing ultrasound in medical ultrasonic power bracket
Driving pulse generates acoustic radiation force in bioviscoelasticity tissue focal zone, and making tissue, deformation occurs, then utilizes detection pulse
Echo-signal detect the deformational displacement situation of tissue in different time points by the time-delay calculation method of correlation, be imaged
Qualitatively reflect the Viscoelastic Properties of tissue afterwards.ARFI elastogram overcomes conventional freehand elastogram can not be from vitro to depth
Portion's tissue effectively pressure and because operator use habit difference caused by the poor disadvantage of repeatability.But it is disadvantageous in that
The opposite deformational displacement difference of tissue is shown in image, and can not quantitatively estimate the elasticity modulus of tissue completely.It is based on
(SWI, shear wave imaging) is imaged in ultrasonic shear wave derived from ARFI technology, by adjusting pulse excitation mode, root
The shear-wave velocity laterally propagated is estimated according to the displacement-time curve of the multiple points of horizontal direction, is then propagated using shearing wave special
Property and biological tissue elasticity feature between inner link, finally quantitatively reconstruct tissue elasticity modulus to form two-dimensional figure
Picture.
But existing quantitative elastogram SWI is needed using the original radio frequency signal number before the Beam synthesis of ultrasonic front end
According to needing to emit based on plane wave and receive, plane wave technology is per second to need N*c/2z calculating, and wherein N is parallel reception sound
Beam number, c are the velocity of sound, and z is scan depths.And the calculation amount of traditional beam synthesizing method is then much smaller, only M/P/
One, wherein M be emitting times, P be and line number, such as M be equal to 100, P be equal to 2 when, the calculation amount of plane-wave method be tradition
At least 50 times (sometimes even up to hundreds times) of ARFI method；Other than the greatest differences of calculation amount, it is based on plane wave skill
The receiving end software Beam synthesis of art also needs to store a large amount of original echoed signals, and data are greatly improved and store and transmit firmly
Part cost is not easy to integrate and promote and apply with medical ultrasound system.
Summary of the invention
It is an object of the invention to overcome existing quantitative elastography to need using original radio frequency signal (without wave
Shu Hecheng) bring is computationally intensive, required hardware design is difficult and problem with high costs, provide it is a kind of it is low for equipment requirements,
The small ultrasonic quantitative elastograph imaging method of calculation amount and system.
In order to achieve the above-mentioned object of the invention, the present invention provides following technical schemes:
A kind of quantitative shearing wave elastograph imaging method, comprises the following steps:
ARFI detection is carried out, each position strain stress in target area is obtained, wherein including specified reference position strain stressref；
Shearing wave detection is carried out, obtains and specifies reference position single-point shear-wave velocity c in target arearef；
Each position shear-wave velocity c is calculated according to the single-point shear-wave velocity；
Each position, which is obtained, according to each position strain gauge shear-wave velocity quantifies shearing wave elastic image E.
Further, each position strains in the target areaWherein, N is sliding for gradient
Dynamic calculation window size, ziIndicate the specific depth coordinate of each position,Indicate each position coordinates in gradient sliding calculation window
Mean value, yiIndicate current point displacement in gradient sliding calculation window,Indicate each position displacement in gradient sliding calculation window
Mean value.
Further, the single-point shear-wave velocity is according to the lateral distance of specified measurement point, axial distance and each finger
Determine measurement point and reach the time required for maximum transversal displacement to be calculated using two-dimensional linear fitting process.
Further, the single-point shear-wave velocity crefIt is obtained by formula X=A β, wherein In formula, xiIndicate the lateral distance of specified measurement point, tiIndicate that specified measurement point reaches most
The time required to big displacement, ziIndicate the axial distance of specified measurement point, β1As required specified measurement point single-point shear wave velocity
cref, β0And β2To calculate single-point shear wave velocity c using above formularefThe regression parameter that is calculated simultaneously in the process, in this method not
Use the two parameters.
Further, each position shear-wave velocityWherein, in focal zone, γ value 1；?
Axial region except focal zone,Wherein, z is axial distance, and n and σ are to indicate that the system of excitation sound field is normal
Number, value range is the value of two parameters of 0~10, n and σ can be identical or different.
Further, the focal zone DOF=8 (f#)2λ, wherein λ indicates wavelength, and f# is aperture control parameter,
For the real number between 0~5, it is seen that focal zone is usually determined that magnitude range is only related to device parameter by device parameter,
Unrelated with target area size, target area is likely larger than focal zone, it is also possible to be equal to focal zone, or be less than focal zone
Domain.
Further, the quantitative shearing wave elastic image E=3 ρ c2, wherein ρ is tested region Media density.
Above method may operate in following ultrasonic quantitative elastogram system, which includes,
Pulse generator is sheared, for emitting shearing wave driving pulse and detection pulse signal；
ARFI impulse generator, for emitting ARFI driving pulse and detection pulse signal；
Probe, for receiving shearing wave echo-signal or ARFI echo-signal；
Control device receives shearing wave echo for controlling the switch of shearing pulse generator, ARFI impulse generator
Signal and ARFI echo-signal, and, the strain stress of each position in target area is calculated according to ARFI echo-signal, wherein comprising referring to
Determine reference position strain stressref；Specified reference position single-point shear-wave velocity c is calculated according to shearing wave echo-signalref；According to list
Point shear-wave velocity calculates each position shear-wave velocity c；According to each position strain gauge shear-wave velocity c and strain stressrefIt obtains
Each position is taken to quantify shearing wave elastic image E；
Display device, for showing the quantitative shearing wave elastic image E.
The probe includes beam synthesizer, is used to close ARFI echo-signal or shearing wave echo-signal by wave beam
At synthesizing echo radiofrequency signal.
The control device includes shearing wave signal processing module, single-point shear wave velocity computing module；
The shearing wave signal processing module receives shearing wave echo radiofrequency signal from probe, and demodulated, displacement is estimated
Calculate the shearing wave displacement versus time data for obtaining tested tissue target area each position or only obtaining specified reference position；
The single-point shear wave velocity computing module calculates specified reference position shearing wave according to shearing wave displacement versus time data
Velocity of wave cref, obtained by formula X=A β, whereinIn formula, xiIt indicates
The lateral distance of specified measurement point (specified measurement point includes specified reference position), tiIndicate that specified measurement point reaches maximum displacement
Required time, ziIndicate the axial distance of specified measurement point, β1As required specified measurement point single-point shear wave velocity cref；
The control device further includes ARFI signal processing module, strain calculation module；
The ARFI signal processing module is used to receive ARFI echo radiofrequency signal from popping one's head in, and demodulated, displacement is estimated
Calculate the ARFI displacement versus time data for obtaining tested tissue target area each position；
The strain calculation module calculates the strain of target area each position according to the ARFI displacement versus time dataWherein, N is that gradient slides calculation window size, ziIndicate the specific depth coordinate of each position,
Indicate the mean value of each position coordinates in gradient sliding calculation window, yiIndicate current point displacement in gradient sliding calculation window,
Indicate the mean value of each position displacement in gradient sliding calculation window, the strain stress comprising specified reference position in εref。
The control device further includes elasticity modulus computing module；
The control device further includes velocity of wave computing module and elasticity modulus computing module；
The velocity of wave computing module is used to calculate each position shearing wave according to specified reference position single-point shear-wave velocity
Velocity of waveWherein, in focal zone, γ value 1；Axial region except focal zone,
Wherein, z is axial distance, and n and σ are the system constants for indicating excitation sound field, and value range is two parameters of 0~10, n and σ
Value can be identical or different；
The elastic image computing module is used for according to c and strain stressrefIt obtains each position and quantifies shearing wave elastic image E
=3 ρ c2, wherein ρ is tested region Media density.
The control device controls the shearing pulse generator, ARFI impulse generator alternate emission.
The shearing pulse generator and the ARFI impulse generator are the realization of same circuit, are filled by the control
It sets control and sends shearing wave impulse or ARFI pulse；,
The shearing pulse generator and the ARFI impulse generator are the realization of respective independent circuits, by the control
Device processed controls starting, shut-in time.
The shearing pulse generator and/or ARFI impulse generator share 24 tunnels or more.
The shearing pulse generator or ARFI impulse generator include the driving amplifier being sequentially connected in series, pulse generation
Device, overcurrent-overvoltage protecting circuit, Tx/Rx switch, and limiting amplifier, D/A converting circuit from Tx/Rx switch feedback.
Compared with prior art, beneficial effects of the present invention:
Strain and use two dimension of the ultrasonic quantitative elastograph imaging method provided by the invention based on sliding window linear fit
The shear-wave velocity detection algorithm of linear fit, result robustness is more preferable, noise resisting ability is stronger, as a result more reliable.Simultaneously
In the case where not increasing ultrasonic front end storage additionally with transmission module load, realizes ultrasonic universe and quantify elastogram, greatly
Reduce to width the design difficulty and equipment cost of ultrasonic quantitative elastogram system.
It is provided with efficient circuit switching and protective module in the system of the method for the present invention operation, system is allowed to meet ARFI and cut
While cutting wave difference transmitting timing requirements, effective protection human body and circuit system, and carry out acoustically-driven to greatest extent to reach
To more preferable detection effect.
Detailed description of the invention:
Fig. 1 is ultrasonic quantitative elastograph imaging method flow chart provided by the invention.
Fig. 2 is ultrasonic quantitative elastogram system block diagram provided by the invention.
Fig. 3 is that pulse generator and/or the exemplary structural frames of ARFI impulse generator composition are sheared in the present invention
Figure.
Fig. 4 is the transmitting pulse train schematic diagram that acoustically-driven uses in the present invention in the present invention.
Fig. 5 is that shear-wave velocity calculates the impulse ejection schematic diagram used.
Specific embodiment
With reference to the accompanying drawing and specific embodiment the present invention is described in further detail.But this should not be interpreted as to this
The range for inventing above-mentioned theme is only limitted to embodiment below, all to belong to the present invention based on the technology that the content of present invention is realized
Range.
Embodiment 1: it as shown in Figure 1, the present invention provides a kind of quantitative shearing wave elastograph imaging method, comprises the following steps:
S100: carrying out ARFI detection, obtains each position strain stress in target area, wherein answering comprising specified reference position
Become εref；
S200: carrying out shearing wave detection, obtains and specifies reference position single-point shear-wave velocity c in target arearef；
The execution sequence of step S100 and S200 have no particular/special requirement, can such as first carry out S100, then execute S200, can also
To first carry out S200, then execute S100.
S300: each position shear-wave velocity c is calculated according to the single-point shear-wave velocity；
S400: each position is obtained according to each position strain gauge shear-wave velocity and quantifies shearing wave elastic image E.
Specifically, each position strains in the target areaWherein, N is gradient sliding
Calculation window size, ziIndicate the specific depth coordinate of each position,Each position coordinates is equal in expression gradient sliding calculation window
Value, yiIndicate current point displacement in gradient sliding calculation window,Each position displacement is equal in expression gradient sliding calculation window
Value.
The single-point shear-wave velocity is according to the lateral distance of specified measurement point, axial distance and each specified measurement point
Reaching the time required for maximum transversal displacement is calculated using two-dimensional linear fitting process.
The single-point shear-wave velocity crefIt is obtained by formula X=A β, wherein In formula, usually we preset I depth in axial depth, preset J designated position (point) in each depth,
Altogether, m designated position (point), m=I*J；Each position (point) is reached the time of maximum displacement by we under shearing wave effect
Regard that shearing wave travels to the time of the position (point) as, is transmitted by the available shearing wave of shearing wave displacement versus time data
To the time of the position (point), i.e. ti；Meanwhile ziIndicating specified measurement position (point), (characterization is deep in the axial distance of axial depth
Spend position), xiIndicate the lateral distance (characterization lateral position) of specified measurement position (point), that is, when each designated position (point)
When selected, each element value and z in XiValue just it has been determined that we only need to be found out from shearing wave displacement versus time data it is each
Designated position (point) reaches t the time required to maximum displacementiCalculating can be completed；In formula, β1As required specified measurement point list
Point shear wave velocity cref；Simultaneously, it is noted that β0And β2To calculate single-point shear wave velocity c using above formularefIt counts simultaneously in the process
The regression parameter obtained in this method and does not use the two parameters, and effect and meaning do not have essential meaning to the present invention.
Each position shear-wave velocityWherein, in focal zone γ value 1；Focal zone it
Outer axial region (when target area is greater than focal zone, need to use herein),Wherein, z is axial distance,
N and σ is the system constants for indicating excitation sound field, and value range is the value of two parameters of 0~10, n and σ can be identical or not
Together.
The quantitative shearing wave elastic image E=3 ρ c2, wherein ρ is tested region Media density.
Method provided in this embodiment may operate in ultrasonic quantitative elastogram system as shown in Figure 2 and Figure 3, should
System includes,
Pulse generator is sheared, for emitting shearing wave driving pulse and detection pulse signal；
ARFI impulse generator, for emitting ARFI driving pulse and detection pulse signal；
Probe, for receiving shearing wave echo-signal or ARFI echo-signal；
Control device 1 receives shearing wave and returns for controlling the switch of shearing pulse generator, ARFI impulse generator
Wave signal and ARFI echo-signal, and, the strain stress of each position in target area is calculated according to ARFI echo-signal, wherein including
Specified reference position strain stressref；Specified reference position single-point shear-wave velocity c is calculated according to shearing wave echo-signalref；According to
Single-point shear-wave velocity calculates each position shear-wave velocity c；According to each position strain gauge shear-wave velocity c and strain stressref
It obtains each position and quantifies shearing wave elastic image E.
Display device, for showing the quantitative shearing wave elastic image E.Specifically, further including pair before display
The elastic image E data that control device is calculated are scanned conversion, and a series for the treatment of process such as smoothing processing finally will
The image is presented to user by display.
The probe includes beam synthesizer 2, is used for ARFI echo-signal or shearing wave echo-signal by wave beam
Synthesis, synthesizes echo radiofrequency signal.
The control device 1 includes shearing wave signal processing module 13, single-point shear wave velocity computing module 14；
The shearing wave signal processing module 13 receives shearing wave echo radiofrequency signal from probe, and demodulated as IQ
Data further carry out the shearing wave displacement versus time that offset estimation obtains tested tissue target area each position to the I/Q data
Data；
The single-point shear wave velocity computing module 14 calculates specified reference position shearing according to shearing wave displacement versus time data
Wave velocity of wave cref, obtained by formula X=A β, whereinIn formula, xiTable
Show the lateral distance of specified measurement point, tiThe time required to indicating that specified measurement point reaches maximum displacement, ziIndicate specified measurement point
Axial distance, β1As required specified measurement point single-point shear wave velocity cref；
The control device 1 further includes ARFI signal processing module 11, strain calculation module 12；
The ARFI signal processing module 11 is used to receive ARFI echo radiofrequency signal from popping one's head in, and demodulated formation IQ
Data, and further by I/Q data carry out offset estimation obtain tested tissue target area each position ARFI displacement-when
Between data；
The strain calculation module 12 calculates the strain of target area each position according to the ARFI displacement versus time dataWherein, N is that gradient slides calculation window size, ziIndicating each position, (each position herein is logical
Often it is also to be chosen from target area) specific depth coordinate,Each position coordinates is equal in expression gradient sliding calculation window
Value, yiIndicate current point displacement in gradient sliding calculation window,Each position displacement is equal in expression gradient sliding calculation window
Value.
The control device 1 further includes velocity of wave computing module 15 and elasticity modulus computing module 16；
The velocity of wave computing module 15 is used to calculate each position shearing according to specified reference position single-point shear-wave velocity
Wave velocity of waveWherein, in focal zone, γ value 1；Axial region except focal zone,Wherein, z is axial distance, and n and σ are the system constants for indicating excitation sound field, value range be 0~10, n and
The value of two parameters of σ can be identical or different；
The elastic image computing module 16 is used for according to c and strain stressrefIt obtains each position and quantifies shearing wave elastic graph
As E=3 ρ c2, wherein ρ is tested region Media density.
The control device 1 controls the shearing pulse generator, ARFI impulse generator alternate emission.
Specifically, as described in Figure 3, in some embodiments, 1 hardware components of control device can by PC, control circuit board and
Fpga chip group forms, and in other embodiment, control device is also possible to completely integrated integrated circuit and constitutes,
Above-mentioned shearing wave signal processing module, single-point shear wave velocity computing module, ARFI signal processing module, strain calculation module,
Elasticity modulus computing module is distributed in above-mentioned hardware device by function.
The shearing pulse generator and the ARFI impulse generator are the realization of same circuit, are filled by the control
It sets control and sends shearing wave impulse or ARFI pulse；Or,
The shearing pulse generator and the ARFI impulse generator are the realization of respective independent circuits, by the control
Device processed controls starting, shut-in time.
Specifically, being the implementation that same circuit is realized in the shearing pulse generator and the ARFI impulse generator
In example, as shown in figure 3, generator includes driving amplifier 100, impulse generator 101, the over-current over-voltage protection electricity being sequentially connected in series
Road 102, Tx/Rx switch 103, and limiting amplifier 104, D/A converting circuit 105 from Tx/Rx switch feedback.It crosses and flows through
Voltage protection circuit 102 can allow system meet ARFI and shearing wave difference transmitting timing requirements while, effective protection human body and
Circuit system, and carry out acoustically-driven to greatest extent to reach more preferable detection effect.
The shearing pulse generator and/or ARFI impulse generator share 24 tunnels or more, such as 48 tunnels, 64 tunnels, 128
Road, 256 tunnels etc..
It is sent out in use, control device controls pulse according to parameter informations such as voltage set by user, pulse length and phases
Raw device (shearing pulse generator and/or the ARFI impulse generator) generates excitation and detection pulse signal, switchs in T/R
Control under the ultrasonic wave that generates of transmit circuit enter biological tissue, receive circuit receives echo-signal.System is emitting or is connecing
When the collection of letters, by the way that aperture control parameter f# and depth of focus z is arranged, and formula is utilizedTo control activity array element (arteries and veins
Rush generator) number, in formula, D is probe pore size, i.e. user passes through setting aperture control parameter f# and the depth of focus
Z realizes the control to movable element number of array to control the size in movable probe aperture, and user can be according to circumstances in maximum activity
Selection activity array element quantity actually required in array number (such as 64 tunnels), if for example, system includes No. 64 impulse generators,
The maximum probe pore size that system may be implemented is the area that 64 array element is distributed, and aperture control parameter f# is usually big
It is less than or equal to 5 real number in 0.Because motivating tissue to generate the power of deformation is to be emitted by popping one's head according to option set by user
Short duration pulse wave is formed in focal zone, unrelated with the operation technique of operator, it can be considered that in effective imaging area
The size of domain internal force be it is uniform, it is consistent.The depth (Depth of Focus) of focal zone can be described as: DOF=8
(f#)2λ, λ indicate wavelength；For example, the sound for the driving pulse of 5MHz, if aperture control parameter f#=2, in biological tissue
Speed is approximately equal to 1540m/s, then the value of DOF is close to 1cm.ARFI elastogram is scanned using by-line mode, each
Horizontal position all can emit driving pulse according to identical system parameter and tissue is made to generate miniature deformation, it can be considered that
Acoustic radiation force within the scope of near focal point 1cm can be regarded as uniformly, consistent, we are known as focal zone in this region,
As described above, in focal zone, shear-wave velocity calculation formulaIn γ value be 1.
Emit pulse train signal as shown in figure 4, according to ROI window depth location, signal center frequency size, PRF
The state modulators such as (pulse repeat frequency, pulse recurrence frequency), driving voltage and pulse length emit pulse
Sequence.The head of sequence be one or more detection pulses (Detect beam, high voltage (such as 80V, generally with B-mode phase
Together), short pulse (such as 2 periods)) reference signal as displacement of tissue information；Followed by multiple groups driving pulse/detection
Pulse pair, driving pulse (Push beam, lower voltage (such as 20~40V), long pulse (100~250 periods)) are used for
The regional area excitation of near focal point generates micro-displacement in organizing.
Detection pulse (short pulse of high voltage) is for tracking the deformation that acoustic radiation force load is organized during the loading process
Situation；It is the deformation situation organized after a series of detection pulse tracking acoustic radiation force load disappears later.The work of driving pulse
With being that vibrate the local organization at focal position can under safety condition, long echo signal is due to its spatial resolution
Difference cannot be used for offset estimation, so probe array element shutdown signal apodization when emitting driving pulse, the hair of all activity array elements
Penetrate that signal amplitude is identical, the energy that enhancing signal carries under safety condition to generate bigger acoustic radiation force.For motivating
Long pulse wave frequency rate and short pulse wave centre frequency for detection may be selected it is identical or different, it is preferable that centre frequency
Difference, in this way can interference in order to avoid driving pulse to detection pulse echo signal, while being easy to area in signal processing
The echo-signal that shunt excitation is encouraged and detected.
In addition emit pulse train in long pulse wave number mesh be it is variable, the wave number mesh of entire sequence be also it is variable,
Here the wave number mesh for once motivating entire sequence is defined as sampling volume number (ensemble size) by we, such as 16,
24,32.Long pulse wave number mesh (field wave)+short pulse wave number mesh (reference and detection wave)=sampling volume number, gradient sliding
Arbitrary value of the size of calculation window N between 0~sampling volume number, specific its are to be automatically selected using adaptive algorithm, this
Place repeats no more.
One group of shearing wave transmitting pulse includes several different spatials transmitting pulse train as shown in Figure 4, wherein
Driving pulse spatial position is fixed, and the detection pulse interval position of different transmitting sequences is different；As shown in figure 5, D is detection
Wave, P are field wave, if there is one group of shearing wave transmitting pulse using the transmitting pulse train for being divided into 1mm between 5, this 5 sequences
Field wave P1, P2, P3, P4, P5 in the same space position, and detection wave D1, D2, D3 in 5 transmitting pulse trains,
D4, D5 in identical or different spatial position, meanwhile, at least one detection pulse spatial position it is identical with pulse location,
D1 in such as figure.
The transmitting pulse train that ARFI impulse generator uses is identical as shearing pulse generator, but a frame ARFI is imaged
Field wave keeps with detection wave being the same space position in scanning process.
Claims (5)
1. a kind of quantitative shearing wave elastograph imaging method, which is characterized in that comprise the following steps:
ARFI detection is carried out, each position strain stress in target area is obtained, wherein including specified reference position strain stressref；
Shearing wave detection is carried out, obtains and specifies reference position single-point shear-wave velocity c in target arearef；
Each position shear-wave velocity c is calculated according to the single-point shear-wave velocity；
Each position, which is obtained, according to each position strain gauge shear-wave velocity quantifies shearing wave elastic image E；
Wherein, each position strains in the target areaWherein, N is that gradient slides calculation window
Size, ziIndicate the specific depth coordinate of each position,Indicate the mean value of each position coordinates in gradient sliding calculation window, yi
Indicate current point displacement in gradient sliding calculation window,Indicate the mean value of each position displacement in gradient sliding calculation window；
The single-point shear-wave velocity reaches maximum according to the lateral distance of specified measurement point, axial distance and each specified measurement point
Time required for lateral displacement is calculated using two-dimensional linear fitting process.
2. imaging method as described in claim 1, which is characterized in that the single-point shear-wave velocity crefPass through formula X=A β
It obtains, whereinIn formula, xiIndicate the lateral distance of specified measurement point, ti
The time required to indicating that specified measurement point reaches maximum displacement, ziIndicate the axial distance of specified measurement point, β1As required is specified
Measurement point single-point shear wave velocity cref。
3. imaging method as described in claim 1, which is characterized in that each position shear-wave velocity
In focal zone γ value 1；Axial region except focal zone,Wherein, z is axial distance, and n and σ are
Indicate the system constants of excitation sound field, value range is the value of two parameters of 0~10, n and σ can be identical or different.
4. imaging method as claimed in claim 3, which is characterized in that the focal zone DOF=8 (f#)2λ, wherein λ is indicated
Wavelength, f# are aperture control parameter, for the real number between 0~5.
5. imaging method as described in claim 1, which is characterized in that the quantitative shearing wave elastic image E=3 ρ c2, wherein
ρ is tested region Media density.
Priority Applications (3)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201610973110.5A CN106618639B (en) | 2016-11-04 | 2016-11-04 | A kind of quantitative shearing wave elastograph imaging method |
| PCT/CN2017/107120 WO2018082458A1 (en) | 2016-11-04 | 2017-10-20 | Quantitative shear wave elasticity imaging method and system |
| US16/346,079 US11357480B2 (en) | 2016-11-04 | 2017-10-20 | Quantitative shear wave elasticity imaging method and system |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
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| CN201610973110.5A CN106618639B (en) | 2016-11-04 | 2016-11-04 | A kind of quantitative shearing wave elastograph imaging method |
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| TWI652048B (en) * | 2018-02-26 | 2019-03-01 | 長庚大學 | Ultrasound image uniformity detection method and system |
| CN109875607A (en) * | 2019-01-29 | 2019-06-14 | 中国科学院苏州生物医学工程技术研究所 | Infiltrate tissue testing method, apparatus and system |
| CN110927729B (en) * | 2019-11-09 | 2022-04-01 | 天津大学 | Acoustic radiation force pulse elastography method based on displacement attenuation characteristics |
| CN113545806A (en) * | 2020-04-26 | 2021-10-26 | 深圳迈瑞生物医疗电子股份有限公司 | Prostate elastography method and ultrasound elastography system |
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103720489A (en) * | 2013-12-30 | 2014-04-16 | 中国科学院深圳先进技术研究院 | Lesion tissue growth monitoring method and system |
| CN104055541A (en) * | 2014-06-26 | 2014-09-24 | 中国科学院苏州生物医学工程技术研究所 | Method for intravascular ultrasound multi-slice shear wave elastography |
| CN104306026A (en) * | 2014-11-18 | 2015-01-28 | 声泰特（成都）科技有限公司 | Echo displacement detection system and imaging system based on acoustic radiation force |
| CN104546014A (en) * | 2014-12-25 | 2015-04-29 | 中国科学院深圳先进技术研究院 | Shear wave velocity estimation method for biological tissue elasticity measurement |
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| US10136876B2 (en) * | 2012-09-27 | 2018-11-27 | Mayo Foundation For Medical Education And Research | System and method for local estimation of nonlinear tissue elasticity with acoustic radiation force |
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103720489A (en) * | 2013-12-30 | 2014-04-16 | 中国科学院深圳先进技术研究院 | Lesion tissue growth monitoring method and system |
| CN104055541A (en) * | 2014-06-26 | 2014-09-24 | 中国科学院苏州生物医学工程技术研究所 | Method for intravascular ultrasound multi-slice shear wave elastography |
| CN104306026A (en) * | 2014-11-18 | 2015-01-28 | 声泰特（成都）科技有限公司 | Echo displacement detection system and imaging system based on acoustic radiation force |
| CN104546014A (en) * | 2014-12-25 | 2015-04-29 | 中国科学院深圳先进技术研究院 | Shear wave velocity estimation method for biological tissue elasticity measurement |
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