CN104367346A - Echo displacement detecting method and imaging method based on sound radiation force - Google Patents
Echo displacement detecting method and imaging method based on sound radiation force Download PDFInfo
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Abstract
The invention discloses an echo displacement detecting method and imaging method based on sound radiation force. Linear interpolation is used for removing the invalid echo corresponding to an drive pulse signal; a time sampling window is adjusted in a self-adaptive mode according to the smoothness index of the echo; a two-dimensional self-correlation Loupas algorithm is used for calculating the average displacement speed of the echo in the time sampling window, and the specific displacement of the echo in the time direction is obtained; a movement filtering manner is used for eliminating the interference information, brought by the tissue movement, on the echo displacement, the reliability of displacement detection is higher, and the noise-resistance capability is higher. The imaging method includes the displacement detecting method, multi-mode sound radiation force imaging correlated to the organization visco-elasticity can be provided, meanwhile, frame correlation processing is adopted for removing the interference generated by electronic noise so that image displaying can be more stable, the display resolution of a stretched and strengthened image is compared, the pressure information in the current working state is provided for sound radiation force imaging, and a doctor can conveniently analyze the image and safely operate.
Description
Technical field
The present invention relates to medical ultrasound image field, particularly one is based on acoustic radiation force echo displacement detecting method and formation method.
Background technology
Medical ultrasonic vibratility elastogram is invented in 1998 by Fatemi and Greenleaf.This technology produces a low-frequency vibration with a ultrasound field and acts on by inspection tissue, and tissue is subject to excitation and produces different Oscillation Amplitudes according to the elastic modelling quantity size of self, and eventually through image appearance out.Adopt pulse imaging (the acoustic radiation force impulse imaging of acoustic radiation force excitation, ARFI) one of vibratility elastogram is belonged to, this technology utilizes journey focusing ping in short-term to act on and organizes ROI (region of interest, area-of-interest), make it produce instantaneous, micron order displacement and launch ping sequence detection displacement of tissue simultaneously.Displacement size depends on tissue elasticity.The Acuson S2000 of Germany Siemens develops sound palpation and organizes quantification technique.This system uses standard ultrasound probe, and use the sampling frame being about 1cm of a depth adjustable, frequency is that the probe of 3.5MHZ sends ping to tissue, and this ping is propagated at organization internal and produced a shearing wave.System sends direct impulse and shearing wave detected and then measure its velocity of wave.And shear-wave velocity size just in time reflects the hardness level of tissue, but, the fetch long price of this instrument.
Current acoustic radiation force imaging technique applies partial radiation pressure to tissue by the long pulsed ultrasonic wave of transmitting focusing, the promotion that tissue is subject to radiant force produces certain strain, then acoustic radiation force is stopped, the strained situation of different time points is detected in strain recovery process, thus the viscous-elastic behaviour of reflection tissue.This incentive program is relatively simple, can be integrated into existing medical ultrasound system easily, is convenient to clinical practice and promotes.But also there are some problems:
1, the vibration that causes of ultrasonic action is in micron number magnitude, and its echo is easy to the interference being subject to system noise and organism displacement (as heart beating, breathing).The sampling window (being called for short time sampling window) of traditional displacement detecting algorithm time orientation is often fixed as 2, and the displacement detected like this is very large by the interference of noise, and the displacement curve obtained is not level and smooth;
2, the imaging of existing medical ultrasonic acoustic radiation force generally only provides the displacement imaging of fixed time, fails to make full use of the diagnostic message that acoustic radiation force imaging produces.
3, in medical ultrasonic image, the scintillation effect that system electronic noise and speckle noise are introduced greatly can reduce image resolution ratio, makes clinical diagnosis become abnormal difficult, needs post-processing approach reasonable in design to improve elastic image resolution and contrast.
Summary of the invention
The object of the invention is to overcome the problem that echo is vulnerable to the interference of system noise and organism displacement (as heart beating, breathing), a kind of echo displacement detecting method based on acoustic radiation force be provided:
Step 1: by the acoustic radiation force echo that detects, linear interpolation is carried out to the echo-signal corresponding with excitation pulse signal; In ultrasonic radiation force testing process, include driving pulse (long pulse) in single pulse train, detect pulse (short pulse), wherein, driving pulse number+detection pulse number=sampling volume number (Ensemble size), described sampling volume number is 16,24,32 (can set as required) etc., echo-signal and above-mentioned pulse one_to_one corresponding, but the echo-signal corresponding with driving pulse (long pulse) is because being subject to launching the interference of long wave and not calculating value, therefore need to be removed, and adopt linear interpolation method to replace.
Step 2: comprise and adopt two-dimensional autocorrelation Loupas algorithm to calculate the average displacement speed of described echo in time sampling window N; Described two-dimensional autocorrelation Loupas algorithmic formula is:,
Wherein I, Q are the echo data after signal amplification, analog digital conversion, quadrature demodulation, and c is the velocity of sound, f
csignal center frequency, f
pRFpulse recurrence frequency, f
sbe sample frequency, M is depth direction sampling window size, and N is time sampling window size, and its span is: 2≤N≤sampling volume number (Ensemble size), and m is the degree of depth, and n is the time,
the average displacement speed of echo in time sampling window N.
Step 3: comprise and calculate the step of described echo in the concrete displacement of time orientation,
Wherein
for the local displacement organizing time orientation corresponding, d
ifor tested tissue is in local displacement corresponding to time orientation, the span of i is between 0 to sampling volume number, d
0for initial time because there is no the excitation of acoustic radiation force, d
0=0;
Further, in described two-dimensional autocorrelation algorithm, time sampling window N value is more than 2, below sampling volume number, due to N value hour, described phase of echo displacement meter evaluation time is short, but the error of calculation is larger, when N value is excessive, described phase of echo displacement meter evaluation time of calculating is long, but result of calculation can not increase with the value of N and linearly improve.Therefore, the present invention is by before complete detection, relatively act on smoothness index under the echo-signal different time sampling window organizing focal position (target location or selected reference position) to the size of control N, detailed process is: arrive large change time sampling window size from childhood, the tested multinomial S organizing echo displacement-time curve matching 6 rank of focal position under test different time sampling window size, by itself and the displacement-time curve that obtained by matching
between root-mean-square error as smoothness index, its computing formula is:
(wherein S
ifor its echo displacement-time curve,
for its echo displacement versus time matched curve, Ensemblesize is sampling volume number).Select the value of time sampling window corresponding to minimum smoothness index as N, thus the size of Dynamic controlling N.
Further, excitation pulse signal quantity in single pulse train is Dynamic controlling, and the excitation pulse signal quantity in described single pulse train is determined by the tested peak change rate between the displacement matched curve of focus position under different excitation pulse signal quantity and the Euclidean distance organized; Its concrete grammar is: before carrying out complete detection, selectes and organizes focal position (this position is target location or selected reference position), carry out acoustic radiation force detection, by the excitation pulse signal quantity NUM in single pulse train for this reference site
pincrease successively by 1, test NUM
pdifferent values under the peak change rate of displacement matched curve and Euclidean distance, the computing formula of Euclidean distance is:
it represents NUM
pthe similarity of different value bottom offset matched curve.Work as NUM
pwhen echo-peak rate of change under two adjacent values is minimum or Euclidean distance is minimum, the driving pulse number in the single pulse train when excitation pulse signal quantity determining in current pulse train is complete detection.
Further, after carrying out two-dimensional autocorrelation Loupas algorithm and calculating, also comprise and motion filtering is carried out to displacement curve, eliminate the step of the displacement information organizing displacement to bring, its concrete mode for: determine excitation pulse signal in single pulse train launch before detection pulse signal corresponding to echo displacement, and, in single pulse train excitation pulse signal no longer launch after the echo displacement corresponding to detection pulse signal be histokinesis with reference to displacement, move according to described reference bit and revise described echo displacement further, because the pulse of (end position in sampling volume window) all can be considered with reference to detecting pulse before in single pulse train, excitation pulse signal is launched and after in the single pulse time, excitation pulse signal is no longer launched, displacement now stems from the motion of tissue to be measured self (as breathed, heart beating), but not acoustic radiation force, therefore the displacement of these two time periods is defined as tissue with reference to displacement, and move the described echo displacement of correction further according to described reference bit.
The displacement imaging of fixed time is generally only provided in order to overcome the imaging of existing medical ultrasonic acoustic radiation force, fail to make full use of in the diagnostic message and ultrasonic image that acoustic radiation force imaging produces, the scintillation effect that system electronic noise and speckle noise are introduced greatly can reduce image resolution ratio, make clinical diagnosis become the problems such as exception is difficult, the present invention also provides a kind of image processing method detecting displacement of tissue based on acoustic radiation force:
Comprise the step detecting acoustic radiation force echo-signal;
Comprise the step of described echo-signal being carried out successively signal amplification, analog digital conversion, quadrature demodulation;
Comprise the step adopting displacement detecting method as above to detect described echo-signal displacement;
Comprise and described displacement data is carried out imaging, and to the step of the image after imaging by the smoothing process of medium filtering.
Further, described displacement data is being carried out in the step of imaging, the displacement of tissue imaging S that acoustic radiation force described in single pulse train disappears moment t1 is being provided
t1.
In certain embodiments, described displacement data is carried out in the step of imaging, the instant maximum displacement imaging max (S of time orientation is provided
t2), described t2 value is between 0 to sampling volume number, described S
t2represent the displacement in t2 moment.
In other embodiment, described displacement data is being carried out in the step of imaging, the imaging of the displacement rise time of different tissues position deformation in described acoustic radiation force load applying process is being provided; The formula of described time is: T
up=t (max (S
t3))-t4, T
upfor representing the time of organizing diverse location from equilibrium state to largest deformation, described t3 value is between 0 to sampling volume number, described S
t3represent the displacement organizing the t3 moment, described max (S
t3) represent the maximum displacement organized, t (max (S
t3)) representing the time of organizing when arriving maximum displacement, described t4 is that tissue leaves the initial equilibrium state time.
In certain embodiments, described displacement data is being carried out in the step of imaging, displacement T fall time of organized renewing equilbrium position after providing described acoustic radiation force load to disappear
down=t5-t (max (S
t3)) carry out imaging, T
downorganize diverse location to get back to the time of equilibrium state by largest deformation for representing, described t3 value is between 0 to sampling volume number, and described t5 is that tissue gets back to the equilibrium state time, described S
t3represent the displacement organizing the t3 moment, described max (S
t3) represent the maximum displacement organized, t (max (S
t3)) represent the time of organizing when arriving maximum displacement.
In other embodiment, carried out by described displacement data, in the step of imaging, also can providing displacement of tissue indicative curve, it better observes overall or local message for helping user.
In other embodiment, described displacement data is being carried out, in the step of imaging, also provide acoustic radiation force indicative curve, its safety carried out quantitative analysis for helping user and judge current operation.
Further, the described image processing method detecting displacement of tissue based on acoustic radiation force, also comprise the step of described image being carried out frame process, its computing formula of carrying out frame process is I '
k=α I '
k-1+ (1-α) I
k, wherein, α be by two frames between motion conditions determine be greater than 0 numerical value being less than 1, I is data before frame process, and I ' is data after frame process.
In certain embodiments, the described image processing method detecting displacement of tissue based on acoustic radiation force, also comprise the step of described image being carried out to contrast stretching, the computing formula of described contrast stretching is I'=β (I-μ)+H, wherein μ is original displacement image, H is the display image pixel average of setting, and β is the customer parameter for regulating contrast.
In addition, in order to allow user's observed image more intuitively, the described image processing method detecting displacement of tissue based on acoustic radiation force, also comprises and image is carried out color map, obtain the step of coloured image.
The present invention provides a kind of echo displacement detection system based on acoustic radiation force simultaneously, comprises control module, linear interpolation module, echo rate of displacement computing module, echo displacement computing module; Described linear interpolation module, echo rate of displacement computing module, echo displacement computing module are connected with described control module respectively; Described linear interpolation module is used for the echo-signal corresponding with excitation pulse signal to carry out linear interpolation; Described echo rate of displacement computing module calculates the average displacement speed of described echo in time sampling window N for adopting two-dimensional autocorrelation Loupas algorithm; Described echo displacement computing module is for calculating the displacement of described echo on time orientation.
Further, described echo displacement detection system also comprises displacement calculation optimization module, and it is for time orientation sampling window described in the smoothness index Dynamic controlling by calculating echo.
Further, described echo displacement detection system also comprises acoustic radiation force incentive optimization module, and it is for the quantity by driving pulse in single pulse train when the peak change rate between the displacement matched curve of computation organization focal position under different driving pulse quantity and Euclidean distance Dynamic controlling complete detection.
Further, described echo displacement detection system also comprises displacement correction module, and it for determining that echo is with reference to displacement, and moves the described echo displacement data of correction further according to described reference bit.
The present invention also provides a kind of echo displacement imaging system of acoustic radiation force, comprises control module, echo detecting module, signal amplification module, analog-to-digital conversion module, quadrature demodulation unit, echo displacement detection system, image-forming module and image processing module as above; Described echo detecting module, signal amplification module, analog-to-digital conversion module, quadrature demodulation unit, described echo displacement detection system, image-forming module and image processing module are all connected with control module;
Described echo detecting module is for detecting acoustic radiation force echo-signal.
Described signal amplification module, analog-to-digital conversion module, quadrature demodulation unit are respectively used to described acoustic radiation force echo-signal to carry out signal amplification, analog digital conversion, quadrature demodulation.
Described image-forming module and image processing module are used for as required imaging being carried out in the echo displacement that described echo displacement detection system calculates, and to the smoothing process of image.
Further described image-forming module comprises acoustic radiation force disappearance moment displacement image-forming module, its displacement imaging S disappearing moment t1 for providing acoustic radiation force described in single pulse train
t1.
Described image-forming module comprises the instant maximum displacement image-forming module of time orientation in certain embodiments, and it is for providing the instant maximum displacement imaging max (S of time orientation
t2), described t2 value is between 0 to sampling volume number, described S
t2represent the displacement in t2 moment.
In other embodiment, described image-forming module comprises displacement of tissue rise time image-forming module, and it is for providing the imaging of the displacement rise time of different tissues position deformation in described acoustic radiation force load applying process; The formula of described time is: T
up=t (max (S
t3))-t4, T
upfor representing the time of organizing diverse location from equilibrium state to largest deformation, described t3 value is between 0 to sampling volume number, described S
t3represent the displacement organizing the t3 moment, described max (S
t3) represent the maximum displacement organized, t (max (S
t3)) representing the time of organizing when arriving maximum displacement, described t4 is that tissue leaves the initial equilibrium state time.
In some embodiments, described image-forming module comprises displacement of tissue image-forming module fall time, its displacement T fall time disappearing rear organized renewing equilbrium position for providing described acoustic radiation force load
down=t5-t (max (S
t3)) carry out imaging, T
downorganize diverse location to get back to the time of equilibrium state by largest deformation for representing, described t3 value is between 0 to sampling volume number, and described t5 is that tissue gets back to the equilibrium state time, described S
t3represent the displacement organizing the t3 moment, described max (S
t3) represent the maximum displacement organized, t (max (S
t3)) represent the time of organizing when arriving maximum displacement.
In some embodiments, described image-forming module comprises displacement of tissue indicative curve image-forming module, and it is for providing displacement of tissue indicative curve, and it better observes overall or local message for helping user.
In some embodiments, described image-forming module comprises acoustic radiation force indicative curve image-forming module, and it is for providing acoustic radiation force indicative curve, its safety carried out quantitative analysis for helping user and judge current operation.
Further, described displacement imaging system also comprises frame processing module, and it is for carrying out frame process by described image, and its computing formula of carrying out frame process is I '
k=α I '
k-1+ (1-α) I
k, wherein, α be by two frames between motion conditions determine be greater than 0 numerical value being less than 1, I is data before frame process, and I ' is data after frame process.
Further, described displacement imaging system also comprises picture contrast stretching module, it is for carrying out contrast stretching to described image, the computing formula of described contrast stretching is I'=β (I-μ)+H, wherein μ is original displacement image, H is the display image pixel average of setting, and β is the customer parameter for regulating contrast.
Further, described displacement imaging system also comprises image color mapping block, and it, for image is carried out color map according to gray scale, obtains coloured image.
Compared with prior art, beneficial effect of the present invention: (1) have employed the echo displacement detecting method based on acoustic radiation force provided by the invention, can time sampling window in adaptive adjustment movement detection process, make displacement detecting reliability higher, simultaneously, the present invention utilizes reference bit to remove except the noise owing to organizing displacement to produce, and improves data monitoring accuracy.
(2) method of optimization acoustic radiation force excitation wave number provided by the invention, can reduce acoustical power, ensure the safety of patient and probe better while the arousal effect obtained as far as possible.
(3) present invention also offers and the multi-mode acoustic radiation force displacement imaging organizing viscoelasticity relevant, provide the clinical assistant diagnosis information of more horn of plenty.
(4) invention also provides the real-time indicative curve of displacement of tissue and acoustic radiation force size indicative curve, be not only convenient to the convenient comprehensive viscoelasticity information understanding tissue of doctor, and it can be helped according to safe and reliable complete operation.
(5) image processing method detecting displacement of tissue based on acoustic radiation force provided by the invention, it is more steady that the interference utilizing frame relevant treatment to eliminate electronic noise generation makes image show, contrast stretches and enhances the display resolution of image, and color map coding then can make the movable information of the easier tissue visualization of doctor.
Accompanying drawing illustrates:
Fig. 1 is the flow chart of echo displacement detecting method provided by the invention.
Fig. 2 is the flow chart detecting the image processing method of displacement of tissue based on acoustic radiation force provided by the invention.
Fig. 3 is the launch pulse sequence schematic diagram that in the present invention, acoustically-driven uses.
The displacement of tissue indicative curve provided in Fig. 4 the present invention and acoustic radiation force indicative curve schematic diagram.
Fig. 5 is echo displacement detection system theory diagram provided by the invention.
Fig. 6 is echo displacement imaging system theory diagram provided by the invention.
Detailed description of the invention
Below in conjunction with Fig. 1 to Fig. 4 and detailed description of the invention, the present invention is described in further detail.But this should be interpreted as that the scope of the above-mentioned theme of the present invention is only limitted to following embodiment, all technology realized based on content of the present invention all belong to scope of the present invention.
Embodiment 1: as shown in Figure 1, the object of the present embodiment is to overcome the problem that echo easily receives the interference of system noise and organism displacement (as heart beating, breathing), provides a kind of echo displacement detecting method based on acoustic radiation force:
Comprising the step S011 echo-signal corresponding with excitation pulse signal being carried out to linear interpolation, in ultrasonic radiation force testing process, including with reference to detecting pulse in single pulse train, driving pulse (long pulse), detect pulse (short pulse), have in echo-signal and above-mentioned pulse echo-signal one to one, but the echo-signal corresponding with driving pulse (long pulse) is because being subject to launching the interference of long wave and not calculating value, therefore need to be removed, and adopt linear interpolation method to replace, when pulse number of repetition (sampling volume number) as time orientation is 24, single pulse train comprises 4 groups of driving pulses (long pulse) and 20 detections pulse (short pulse), and the echo-signal coding of its correspondence is respectively T1, T2, T3, T4, P1, T5, T6, P2, T7, T8, T9, T10, T11, P3, T12, T13, T14, T15, P4, T16, T17, T18, T19, T20 (be only citing, do not represent the actual proportions or the shooting sequence that limit driving pulse and detect pulse), wherein P1, P2, P3, P4 signal is the echo-signal of 4 groups of driving pulses (long pulse) correspondences, and it does not calculate value by the interference of launching long wave, need to remove, and the echo T signal adopting adjacent detection pulse corresponding respectively carries out linear interpolation replacement.
Comprise the step S021 adopting two-dimensional autocorrelation Loupas algorithm to calculate the average displacement speed of described echo in time sampling window N, described auto-correlation Loupas algorithmic formula is:
, wherein I, Q are the echo data after signal amplification, analog digital conversion, quadrature demodulation, and c is the velocity of sound, f
csignal center frequency, f
pRFpulse recurrence frequency, f
sbe sample frequency, M is depth direction sampling window size, and N is time sampling window, and m is the degree of depth, and n is the time,
the average speed of echo in time sampling window N.
Comprise and calculate the step S031 of described echo in the concrete displacement of time orientation, its computing formula is:
Wherein
for the local displacement organizing time orientation corresponding, d
ifor tested tissue is in local displacement corresponding to time orientation, the span of i is between 0 to sampling volume number, d
0for initial time because there is no the excitation of acoustic radiation force, d
0=0.
Further, in described auto-correlation algorithm, (value is more than 2 for time sampling window N, below sampling volume number), in the present embodiment, sampling volume number was 24 (namely comprising 24 group pulses in single pulse train), therefore the span of N is 2≤N≤24, due to N value hour, described phase of echo displacement meter evaluation time is short, but the error of calculation is larger, when N value is excessive, described phase of echo displacement meter evaluation time of calculating is long, but result of calculation can not increase with the value of N and linearly improve.Therefore, the present invention is by before starting in complete detection, relatively act on the size of the smoothness index control N under the echo-signal different time sampling window organizing focal position (this position is target location or selected reference position), detailed process is: arrive large change time sampling window size from childhood, the tested multinomial S organizing echo displacement-time curve matching 6 rank of focal position under test different time sampling window size, by itself and the displacement-time curve that obtained by matching
between root-mean-square error as smoothness index, its computing formula is:
(wherein S
ifor its echo displacement-time curve,
for its echo displacement versus time matched curve, Ensemble size is sampling volume number).Select the value of time sampling window corresponding to minimum smoothness index as N, thus the size of Dynamic controlling N.
Further, the excitation pulse signal quantity NUM in single pulse train
pfor Dynamic controlling, described NUM
psize by tested position at NUM
pdifferent values under displacement matched curve between peak change rate and Euclidean distance determine; Its concrete grammar is: before carrying out complete detection, selectes and organizes focal position (this position is target location or selected reference position), carry out acoustic radiation force detection, by the excitation pulse signal quantity NUM in single pulse train for this reference site
pincrease successively by 1, test NUM
pdifferent values under the peak change rate of displacement matched curve and Euclidean distance, the computing formula of Euclidean distance is:
it represents NUM
pthe similarity of different value bottom offset matched curve.As its NUM
pwhen echo-peak rate of change under different value is minimum or Euclidean distance is minimum, the driving pulse number in the single pulse train when excitation pulse signal quantity determining in current pulse train is complete detection.
In certain embodiments, after carrying out two-dimensional autocorrelation Loupas algorithm and calculating, also comprise and motion filtering is carried out to displacement curve, eliminate the step of the displacement information organizing displacement to bring, its concrete mode for: determine excitation pulse signal in single pulse train launch before detection pulse signal corresponding to echo displacement, and, in single pulse train excitation pulse signal no longer launch after the echo displacement corresponding to detection pulse signal be histokinesis with reference to displacement, move according to described reference bit and revise described echo displacement further, as shown in Figure 3, as in the present embodiment single pulse train, echo sequence corresponding to each pulse is T1, T2, T3, T4, P1, T5, T6, P2, T7, T8, T9, T10, T11, P3, T12, T13, T14, T15, P4, T16, T17, T18, T19, T20 (be only citing, do not represent the actual proportions or the shooting sequence that limit driving pulse and detect pulse), then, and 4 echo T1 wherein before echo P1, T2, T3, 5 echo T16 after T4 and P4, T17, T18, T19, the displacement of T20 is that (actual Control echo may be more or less with reference to displacement, by in single pulse train, excitation pulse signal and last excitation pulse signal are arranged in the position decision of sequence for the first time for they), move according to described reference bit and further revise described echo displacement because before in single pulse time series, excitation pulse signal is launched and in the single pulse time excitation pulse signal no longer launch after echo displacement stem from the motion of tissue to be measured self (as breathed, heart beating), but not acoustic radiation force, therefore the displacement of these two time periods is defined as with reference to displacement, and moves the described echo displacement of correction further according to described reference bit, to get rid of the displacement interference that human body displacement causes.
Embodiment 2: as shown in Figure 2, the displacement imaging of fixed time is generally only provided in order to overcome the imaging of existing medical ultrasonic acoustic radiation force, fail to make full use of in the diagnostic message and ultrasonic image that acoustic radiation force imaging produces, the scintillation effect that system electronic noise and speckle noise are introduced greatly can reduce image resolution ratio, make clinical diagnosis become the problems such as exception is difficult, the present embodiment provides a kind of image processing method detecting displacement of tissue based on acoustic radiation force:
Comprise the step S100 detecting acoustic radiation force echo-signal;
Comprise the step S200 described echo-signal being carried out successively signal amplification, analog digital conversion, quadrature demodulation;
Comprise the step S300 adopting displacement detecting method as described in Example 1 to detect described echo-signal displacement;
Comprise and described displacement data is carried out imaging, and to the step S400 of the image after imaging by median filter smoothness of image process, echo-signal phase-shifted data according to obtaining in step S300 draw tested tissue misalignment, and the misalignment imaging of described tested tissue are shown as required.
Further, S400 in the step of described displacement data being carried out imaging, provides the tested tissue displacement imaging S that acoustic radiation force described in single pulse train disappears moment t1
t1, namely when sampling volume number is 24 (namely comprising 24 group pulses in single pulse train), pulse (short pulse) is detected comprising 4 groups of driving pulses (long pulse) and 20, the echo-signal coding of its correspondence is respectively T1, T2, T3, T4, P1, T5, T6, P2, T7, T8, T9, T10, T11, P3, T12, T13, T14, T15, P4, T16, T17, T18, T19, T20 (is only citing, do not represent the actual proportions or the shooting sequence that limit driving pulse and detect pulse), wherein P1, P2, P3, P4 signal is the echo-signal of 4 groups of excitations (long pulse) correspondences, namely the described t1 moment refers to this moment that the driving pulse (long pulse) that P4 is corresponding disappears, each position displacement situation of tested tissue.
In certain embodiments, S400 in the step of described displacement data being carried out imaging, provides the instant maximum displacement imaging max (S between time orientation 0 to sampling volume number
t2) (described t2 value is between 0 to sampling volume number), described S
t2represent the displacement in t2 moment, namely in the single pulse train time, the maximum displacement imaging contexts of tested tissue in each pulse.
Further, S400 in the step of described displacement data being carried out imaging, provides the imaging of the displacement rise time of different tissues position deformation in described acoustic radiation force load applying process; The formula of described time is: T
up=t (max (S
t3))-t4, T
upfor representing the time of organizing diverse location from equilibrium state to largest deformation, described t3 value is between 0 to sampling volume number, described S
t3represent the displacement organizing the t3 moment, described max (S
t3) represent the maximum displacement organized, t (max (S
t3)) representing the time of organizing when arriving maximum displacement, described t4 is that tissue leaves the initial equilibrium state time.
In certain embodiments, S400 in the step of described displacement data being carried out imaging, displacement T fall time of organized renewing equilbrium position after providing described acoustic radiation force load to disappear
down=t5-t (max (S
t3)) carry out imaging, T
downorganize diverse location to get back to the time of equilibrium state by largest deformation for representing, described t3 value is between 0 to sampling volume number, and described t5 is that tissue gets back to the equilibrium state time, described S
t3represent the displacement organizing the t3 moment, described max (S
t3) represent the maximum displacement organized, t (max (S
t3)) represent the time of organizing when arriving maximum displacement.
As shown in Fig. 4 lower-left, carried out by described displacement data in the step S400 of imaging, the present invention also provides Real time Organization displacement indicative curve, and it better observes overall or local message for helping user; Its horizontal axis plots time, the longitudinal axis represents displacement, can see the displacement-time curve in certain territory, local cell of organization internal intuitively.
As shown in Fig. 4 bottom right, described displacement data is being carried out in the step S400 of imaging, real-time acoustic radiation force indicative curve is also being provided, its safety carried out quantitative analysis for helping user and judge current operation; The size of the power that scale representative applies, arrow position is the size position of current acoustic radiation force.
Further, the described image processing method detecting displacement of tissue based on acoustic radiation force, also comprise the step S500 described image being carried out frame process, its computing formula of carrying out frame process is I '
k=α I '
k-1+ (1-α) I
k, wherein, α be by two frames between motion conditions determine be greater than 0 numerical value being less than 1, I is data before frame process, and I ' is data after frame process.
In certain embodiments, the described image processing method detecting displacement of tissue based on acoustic radiation force, also comprise the step S600 described image being carried out to contrast stretching, the computing formula of described contrast stretching is I'=β (I-μ)+H, wherein μ is original displacement image, H is the display image pixel average of setting, and β is the customer parameter for regulating contrast.
In addition, in order to allow user's observed image more intuitively, the described image processing method detecting displacement of tissue based on acoustic radiation force, also comprises and image is carried out color map, obtain the step of coloured image.
Embodiment 3: as shown in Figure 5, the present embodiment provides a kind of echo displacement detection system based on acoustic radiation force, comprises control module 1, linear interpolation module 2, echo rate of displacement computing module 3, echo displacement computing module 4, described linear interpolation module 1, echo rate of displacement computing module 2, echo displacement computing module 3 are connected with described control module 1 respectively, described linear interpolation module 2, for the echo-signal corresponding with excitation pulse signal is carried out linear interpolation, in ultrasonic radiation force testing process, includes with reference to detecting pulse in single pulse train, driving pulse (long pulse), detect pulse (short pulse), have in echo-signal and above-mentioned pulse echo-signal one to one, but the echo-signal corresponding with driving pulse (long pulse) is because being subject to launching the interference of long wave and not calculating value, therefore need to be removed, and adopt linear interpolation method to replace, when pulse number of repetition (sampling volume number) as time orientation is 24, detect pulse (short pulse) comprising 4 groups of driving pulses (long pulse) and 20, the echo-signal coding of its correspondence is respectively T1, T2, T3, T4, P1, T5, T6, P2, T7, T8, T9, T10, T11, P3, T12, T13, T14, T15, P4, T16, T17, T18, T19, T20 (be only citing, do not represent the actual proportions or the shooting sequence that limit driving pulse and detect pulse), wherein P1, P2, P3, P4 signal is the echo-signal of 4 groups of driving pulses (long pulse) correspondences, it does not calculate value by the interference of launching long wave, need to remove, and the echo T signal adopting adjacent detection pulse corresponding respectively carries out linear interpolation replacement, as P1 adopts the value of T4 and T5 to carry out linear interpolation, P4 adopts T15, the value of T16 carries out linear interpolation.
Described echo rate of displacement computing module 3 calculates the average displacement speed of described echo in time sampling window N for adopting two-dimensional autocorrelation Loupas algorithm; Described echo displacement computing module is for calculating the displacement of described echo on time orientation, and described two-dimensional autocorrelation Loupas algorithmic formula is:
Described displacement computing module 4 is for calculating described echo in the concrete displacement of time orientation, and its computing formula is:
Wherein
for the local displacement organizing time orientation corresponding, d
ifor tested tissue is in local displacement corresponding to time orientation, the span of i is between 0 to sampling volume number, d
0for initial time because there is no the excitation of acoustic radiation force, d
0=0.
Further, described echo displacement detection system also comprises displacement calculation optimization module 5, it is for time sampling window N described in the smoothness index Dynamic controlling by calculating echo, in described two-dimensional autocorrelation algorithm, (value is more than 2 for time sampling window N, below sampling volume number), in the present embodiment, sampling volume number was 24 (namely comprising 24 group pulses in single pulse train), therefore the span of N is 2≤N≤24, due to N value hour, described phase of echo displacement meter evaluation time is short, but the error of calculation is larger, when N value is excessive, described phase of echo displacement meter evaluation time of calculating is long, but result of calculation can not increase with the value of N and linearly improve.Therefore, therefore, the present invention is by before starting in complete detection, relatively act on the size of the smoothness index control N under the echo-signal different time sampling window organizing focal position (this position is target location or selected reference position), detailed process is: arrive large change time sampling window size from childhood, the tested multinomial S organizing echo displacement-time curve matching 6 rank of focal position under testing different sampling window size, by itself and the displacement-time curve that obtained by matching
between root-mean-square error as smoothness index, its computing formula is:
(wherein S
ifor its echo displacement-time curve,
for its echo displacement versus time matched curve, Ensemble size is sampling volume number).Select the value of time sampling window corresponding to minimum smoothness index as N, thus the size of Dynamic controlling N.
Further, described echo displacement detection system also comprises acoustic radiation force incentive optimization module 6, driving pulse quantity NUM in single pulse train when it is tested for Dynamic controlling
p.Described NUM
pvalue size by tested position at NUM
pdifferent values under displacement matched curve between peak change rate and Euclidean distance determine; Its concrete grammar is: before carrying out complete detection, selectes and organizes focal position (this position is target location or selected reference position), carry out acoustic radiation force detection, by the excitation pulse signal quantity NUM in single pulse train for this reference site
pincrease successively by 1, test NUM
pdifferent values under the peak change rate of displacement matched curve and Euclidean distance, the computing formula of Euclidean distance is:
it represents NUM
pthe similarity of different value bottom offset matched curve.Work as NUM
pwhen echo-peak rate of change under different value is minimum or Euclidean distance is minimum, the driving pulse number in the single pulse train when excitation pulse signal quantity determining in current pulse train is complete detection.
Further, described echo displacement detection system also comprises displacement correction module 7, it is for determining that echo is with reference to displacement, and move the described echo displacement data of correction further according to described reference bit, after carrying out two-dimensional autocorrelation Loupas algorithm and calculating, also comprise and motion filtering is carried out to displacement curve, eliminate the step of the displacement information organizing displacement to bring, its concrete mode for: determine excitation pulse signal in single pulse train launch before detection pulse signal corresponding to echo displacement, and, in single pulse train excitation pulse signal no longer launch after the echo displacement corresponding to detection pulse signal be histokinesis with reference to displacement, move according to described reference bit and revise described echo displacement further, as shown in Figure 3, as in the present embodiment single pulse train, echo sequence corresponding to each pulse is T1, T2, T3, T4, P1, T5, T6, P2, T7, T8, T9, T10, T11, P3, T12, T13, T14, T15, P4, T16, T17, T18, T19, T20 (be only citing, do not represent the actual proportions or the shooting sequence that limit driving pulse and detect pulse), then, and 4 echo T1 wherein before echo P1, T2, T3, 5 echo T16 after T4 and P4, T17, T18, T19, the displacement of T20 is that (actual Control echo may be more or less with reference to displacement, by in single pulse train, excitation pulse signal and last excitation pulse signal are arranged in the position decision of sequence for the first time for they), move according to described reference bit and further revise described echo displacement because before in single pulse time series, excitation pulse signal is launched and in the single pulse time excitation pulse signal no longer launch after echo displacement stem from the motion of tissue to be measured self (as breathed, heart beating), but not acoustic radiation force, therefore the displacement of these two time periods is defined as with reference to displacement, and moves the described echo displacement of correction further according to described reference bit, to get rid of the displacement interference that human body displacement causes.
Embodiment 4: the echo displacement imaging system providing a kind of acoustic radiation force, comprises echo detecting module 100, signal amplification module 200, analog-to-digital conversion module 300, quadrature demodulation unit 400, echo displacement detection system 500, image-forming module 600 and image processing module 700 as above; Described echo detecting module 100, signal amplification module 200, analog-to-digital conversion module 300, quadrature demodulation unit 400, described echo displacement detection system 500, image-forming module 600 and image processing module 700 connect successively;
Described echo detecting module 100 is for detecting acoustic radiation force echo-signal.
Described signal amplification module 200, analog-to-digital conversion module 300, quadrature demodulation unit 400 are respectively used to described acoustic radiation force echo-signal to carry out signal amplification, analog digital conversion, quadrature demodulation.
Described image-forming module 600 and image processing module 700 for as required imaging being carried out in the echo displacement that described echo displacement detection system calculates, and to the smoothing process of image.
Further described image-forming module 600 comprises acoustic radiation force disappearance moment displacement image-forming module, its displacement imaging S disappearing moment t1 for providing acoustic radiation force described in single pulse train
t1, namely when sampling volume number is 24 (namely comprising 24 group pulses in single pulse train), pulse (short pulse) is detected comprising 4 groups of driving pulses (long pulse) and 20, the echo-signal coding of its correspondence is respectively T1, T2, T3, T4, P1, T5, T6, P2, T7, T8, T9, T10, T11, P3, T12, T13, T14, T15, P4, T16, T17, T18, T19, T20 (is only citing, do not represent the actual proportions or the shooting sequence that limit driving pulse and detect pulse), wherein P1, P2, P3, P4 signal is the echo-signal of 4 groups of excitations (long pulse) correspondences, namely the described t1 moment refers to this moment that the driving pulse (long pulse) that P4 is corresponding disappears, each position displacement situation of tested tissue.
Described image-forming module 600 comprises the instant maximum displacement image-forming module of time orientation in certain embodiments, and it is for providing the instant maximum displacement imaging max (S of time orientation
t2), described t2 value is between 0 to sampling volume number, described S
t2represent the displacement in t2 moment.
In other embodiment, described image-forming module 600 comprises displacement of tissue rise time image-forming module, and it is for providing the imaging of the displacement rise time of different tissues position deformation in described acoustic radiation force load applying process; The formula of described time is: T
up=t (max (S
t3))-t4, T
upfor representing the time of organizing diverse location from equilibrium state to largest deformation, described t3 value is between 0 to sampling volume number, described S
t3represent the displacement organizing the t3 moment, described max (S
t3) represent the maximum displacement organized, t (max (S
t3)) representing the time of organizing when arriving maximum displacement, described t4 is that tissue leaves the initial equilibrium state time.
In some embodiments, described image-forming module 600 comprises displacement of tissue image-forming module fall time, its displacement T fall time disappearing rear organized renewing equilbrium position for providing described acoustic radiation force load
down=t5-t (max (S
t3)) carry out imaging, T
downorganize diverse location to get back to the time of equilibrium state by largest deformation for representing, described t3 value is between 0 to sampling volume number, and described t5 is that tissue gets back to the equilibrium state time, described S
t3represent the displacement organizing the t3 moment, described max (S
t3) represent the maximum displacement organized, t (max (S
t3)) represent the time of organizing when arriving maximum displacement.
In some embodiments, described image-forming module 600 comprises displacement of tissue indicative curve image-forming module, it is for providing displacement of tissue indicative curve, it better observes overall or local message for helping user, as shown in Fig. 4 lower-left, its horizontal axis plots time, the longitudinal axis represents displacement, can see the displacement-time curve in certain territory, local cell of organization internal intuitively.
In some embodiments, described image-forming module 600 comprises acoustic radiation force indicative curve image-forming module, it is for providing acoustic radiation force indicative curve, its safety carried out quantitative analysis for helping user and judge current operation, as shown in Fig. 4 bottom right, the size of the power that scale representative applies, arrow position is the size position of current acoustic radiation force.
Further, described image processing module 700 comprises frame processing module, and it is for carrying out frame process by described image, and its computing formula of carrying out frame process is I '
k=α I '
k-1+ (1-α) I
k, wherein, α be by two frames between motion conditions determine be greater than 0 numerical value being less than 1, I is data before frame process, and I ' is data after frame process.
Further, described image processing module 700 also comprises picture contrast stretching module, it is for carrying out contrast stretching to described image, the computing formula of described contrast stretching is I'=β (I-μ)+H, wherein μ is original displacement image, H is the display image pixel average of setting, and β is the customer parameter for regulating contrast.
Further, described image processing module 700 also comprises image color mapping block, and it, for image is carried out color map according to gray scale, obtains coloured image.
Claims (10)
1. based on an echo displacement detecting method for acoustic radiation force, it is characterized in that, adopt following steps: step 1: echo-signal corresponding with excitation pulse signal in the acoustic radiation force echo detected is carried out linear interpolation;
Step 2: adopt two-dimensional autocorrelation Loupas algorithm to calculate the average displacement speed of described echo in time sampling window N, the dynamic change between 2 and sampling volume number of described time sampling window N value;
Step 3: calculate the displacement of described echo on time orientation.
2. the echo displacement detecting method based on acoustic radiation force according to claim 1, is characterized in that, in described step 2, time sampling window N is according to its value of smoothness index adaptive optimization of tested tissue focal position echo.
3. the echo displacement detecting method based on acoustic radiation force pulse according to claim 2, it is characterized in that, described smoothness index is by formula
obtain, wherein S
ifor echo displacement-time curve,
for the matched curve of echo displacement versus time, Ensemblesize is sampling volume number.
4. the echo displacement detecting method based on acoustic radiation force according to claim 1, it is characterized in that, the driving pulse quantity in described single pulse train organizes peak change rate between the echo displacement matched curve of focal position under different driving pulse quantity and Euclidean distance Dynamic controlling by tested.
5. the echo displacement detecting method based on acoustic radiation force according to any one of Claims 1-4, it is characterized in that, also comprise and motion filtering is carried out to displacement curve, eliminate the step of the displacement information organizing displacement to bring, its concrete mode for: determine excitation pulse signal in single pulse sequence launch before detection pulse signal corresponding to echo displacement, and, in single pulse sequence excitation pulse signal no longer launch after the echo displacement corresponding to detection pulse signal be histokinesis with reference to displacement, move according to described reference bit and revise described echo displacement further.
6. based on an echo displacement formation method for acoustic radiation force, it is characterized in that, comprise the step detecting acoustic radiation force echo-signal;
Comprise the step of described echo-signal being carried out successively signal amplification, analog digital conversion, quadrature demodulation;
Comprise the step of echo-signal displacement as described in the displacement detecting method detection of employing as described in any one of claim 1 to 5;
Comprise and described displacement data is carried out imaging, and the step to the picture smooth treatment after imaging.
7. the echo displacement formation method based on acoustic radiation force according to claim 6, is characterized in that, undertaken in the step of imaging by described echo displacement data, comprise following several imaging pattern:
1) the displacement imaging S that acoustic radiation force described in single pulse sequence disappears moment t1 is provided
t1;
2) the instant maximum displacement imaging max (S of time orientation is provided
t2), described t2 value is between 0 to sampling volume number, described S
t2represent the displacement in t2 moment;
3) imaging of the displacement rise time of different tissues position in described acoustic radiation force load applying process is provided; The formula of described time is: T
up=t (max (S
t3))-t4, T
upfor representing the time of organizing diverse location from equilibrium state to largest deformation, described t3 value is between 0 to sampling volume number, described S
t3represent the displacement organizing the t3 moment, described max (S
t3) represent the maximum displacement organized, t (max (S
t3)) representing the time of organizing when arriving maximum displacement, described t4 is that tissue leaves the initial equilibrium state time;
4) displacement T fall time of organized renewing equilbrium position after providing described acoustic radiation force load to disappear
down=t5-t (max (S
t3)) carry out imaging, T
downorganize diverse location to get back to the time of equilibrium state by largest deformation for representing, described t3 value is between 0 to sampling volume number, and described t5 is that tissue gets back to the equilibrium state time, described S
t3represent the displacement organizing the t3 moment, described max (S
t3) represent the maximum displacement organized, t (max (S
t3)) represent the time of organizing when arriving maximum displacement.
8. the echo displacement formation method based on acoustic radiation force according to claim 6, is characterized in that, is being carried out by described displacement data in the step of imaging:
1) provide displacement of tissue indicative curve, it better observes overall or local message for helping user;
2) acoustic radiation force indicative curve is provided, its safety carried out quantitative analysis for helping user and judge current operation.
9. the echo displacement formation method based on acoustic radiation force according to claim 6, is characterized in that, described echo displacement formation method also comprises the step of described image being carried out frame process, and its computing formula of carrying out frame process is I '
k=α I '
k-1+ (1-α) I
k, wherein, α be by two frames between motion conditions determine be greater than 0 numerical value being less than 1, I is data before frame process, and I ' is data after frame process; Also comprise the step of described image being carried out to contrast stretching, the computing formula of described contrast stretching is I'=β (I-μ)+H, wherein μ is original displacement image, and H is the display image pixel average of setting, and β is the customer parameter for regulating contrast.
10. the echo displacement formation method based on acoustic radiation force according to claim 6, is characterized in that, described echo displacement formation method also comprises the step that image color maps, and it, for image is carried out color map according to gray scale, obtains coloured image.
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