专利摘要:
An ultrasonic imaging method in which a transducer (32) is transmitted with multiple push pulses, the push pulses producing (48) a wave in the tissue of a patient; physiological motion is taken into account (36) using the displacements in response to the multiple pushing pulses; a viscoelastic parameter is calculated (42) as a function of the displacements and the estimated movement; and producing (48) an image according to the viscoelastic parameter.
公开号:FR3039981A1
申请号:FR1670434
申请日:2016-08-03
公开日:2017-02-17
发明作者:Yassin Labyed；Liexiang Fan
申请人:Siemens Medical Solutions USA Inc；
IPC主号:

专利说明:

ADAPTIVE ESTIMATION OF MOVEMENTS IN IMAGING BY THE STRENGTH OF ACOUSTIC RADIATION
BACKGROUND
The present embodiments relate to imaging by the force of acoustic radiation. In particular, the present embodiments relate to motion correction in acoustic radiation force imaging.
[0002] Imaging by force of acoustic radiation indicates the viscoelastic property of the tissue. Tissue displacement is caused by a wave produced by a stress, such as an acoustic force radiation (ARFI) pulse. The reaction of the tissue to the wave is monitored as a function of time. Tissue deformation parameters, such as shear wave propagation parameters, are second-order estimates from the phase or displacement of the followed reaction.
[0003] Imaging by force of acoustic radiation is sensitive to movement artifacts. The patient can move, the transducer probe can move and / or the anatomy can move. These movements contribute to the displacement and / or the parameters obtained. The result is a force image of acoustic radiation of poor quality or biased and poorly reproducible. Physiological and transducer movement is unavoidable during in vivo scans and can cause large errors in estimates of mechanical tissue parameters.
As tracking is used, motion correction can be applied to echo data frames before determining the displacement. Motion correction can eliminate some undesirable distortions, but does not deal with off-plane movement. Stress-free wave-induced tissue movement can be used to estimate a motion that is not desired to subsequently eliminate wave-induced displacements. Where the undesired motion is different during the propagation of the wave or at the measurement location, this removal may not be accurate and may introduce an error.
SUMMARY SUCCINCT
By way of introduction, the preferred embodiments described below include methods, instructions and ultrasound imaging systems by the force of acoustic radiation. Multiple travel profiles are acquired for a given location. An axial and / or lateral, physiological and / or transducer movement is taken into account by using the displacements from the pulses by the force of the acoustic radiation. For axial movement, a difference between the displacements of the different profiles provides information on the movement during the displacement at the induced location just by the undesirable movement. A more accurate estimation of the undesirable movement for removal of the displacement profile is obtained. For lateral movement, displacement profiles are obtained using waves arriving from various directions relative to the given location. An average of the speeds estimated from the different profiles eliminates the lateral movement that is not desired.
According to a first facet, there is provided a method of ultrasound imaging by the force of acoustic radiation. A transducer transmits multiple push pulses in sequence. The push pulses produce waves in the tissue of a patient. The movements of the tissue are monitored in response to the pushing pulses. Physiological, transducer or physiological movement and the transducer are taken into account using displacements in response to multiple pushing pulses. A viscoelastic parameter is estimated as a function of movement and estimated motion. An image is produced according to the viscoelastic parameter.
According to a second facet, there is provided a method of ultrasound imaging by the force of acoustic radiation. An ultrasound system acquires first tissue displacements at a location and in response to a first wave produced from an acoustic force radiation pulse laterally away from a first side of the location. A first velocity of the first wave at the location is estimated from the first movements of the tissue. Ultrasound system acquires second tissue displacements at and in response to a second wave produced from a second distance acoustic force radiation shock laterally along a second side of the tissue. location, the second side being different from the first side. A second velocity of the second wave at the location is estimated from the second displacements of the tissue. We calculate the average of the first and second speeds and we take out the average speed.
According to a third facet, there is provided a method of ultrasonic imaging by the force of acoustic radiation, which comprises: acquiring by an ultrasound system, first tissue displacements as a function of time at a location and in response to a first wave produced from a first shock of the radiation of the acoustic force and acquire by the ultrasound system second displacements of the tissue as a function of time at the location and in response to a second wave produced from a second shock of the radiation of the acoustic force. Produce combined displacements as a function of time from the first and second displacements of the tissue. Adjust a curve to combined movements; subtract the curve from the first movements of the tissue and estimate a viscoelastic value from the results of the subtraction; and take out the viscoelastic value.
Other facets and advantages of the invention are discussed below, in connection with the preferred embodiments and may be worth, independently or in combination.
BRIEF DESCRIPTION OF THE DRAWINGS
The elements and figures are not necessarily to scale, the emphasis being, on the contrary, on the illustration of the principles of the invention. In addition, in the figures of the same references designate parts that correspond in the various views.
FIG. 1 is a flowchart of an embodiment of an ultrasound imaging method by the force of acoustic radiation with correction of the axial and / or lateral movement; FIG. 2 is a graph showing by way of example displacement profiles and physiological movement as a function of time; Figure 3 is a graph showing by way of examples, the displacement profiles of Figure 2 after correction of the axial movement; Figures 4 and 5 are displacements, for example, as a function of time in various remote locations laterally caused by pushing pulses on different sides of a region to which one is interested (ROI ).
Figures 6 and 7 are displacements, for example, Figures 4 and 5 after taking into account the physiological axial movement and / or the transducer; Figures 8 represent two displacement profiles, for example, from different thrust pulses and undesired axial movement; FIG. 9 represents the displacement profiles by way of example after elimination of the axial movement which is not desired; and [0018] Fig. 10 is a block diagram of an embodiment of an ultrasound imaging system by the force of acoustic radiation.
DETAILED DESCRIPTION OF THE DRAWINGS AND PREFERRED EMBODIMENTS CURRENTLY
[0019] An adaptive estimate of the physiological movement and the transducer is provided in acoustic imaging force pulsing applications (ARFI). Axial and lateral components of the physiological motion and / or the transducer are adaptively estimated and corrected. Multiple ARFI excitations are used to isolate physiological and / or transducer shifts of ARFI-induced tissue displacement. In one embodiment, a signal pattern is generated multiple times to detect background (physiological) motion. ARFI excitations are used to produce tissue deformation as the signal configuration. The physiological movement is separated by filtering into a shear wave velocity or other ARFI imagery.
Figure 1 illustrates an ultrasonic imaging method by the force of acoustic radiation. In general, multiple push pulses are transmitted and multiple corresponding displacement profiles are measured at a location. We can estimate the axial component of a physiological movement by a difference between the displacement profiles and eliminate it from displacements. The lateral component of a physiological movement can be eliminated by averaging values (for example velocities) estimated from the displacement profiles induced by the multiple pushing pulses.
The operations are performed by an ultrasound imaging system as described in Figure 10. A transducer and / or beamformers are used to acquire data and a processor estimates displacements from the data. A processor takes into account the motion that is not desired and estimates a value of the viscoelastic parameter from the information obtained. The ultrasound imaging system outputs the value of the viscoelastic parameter. Other devices, such as a computer or a detector, may be used to perform any of the operations.
It may provide additional operations different or in smaller numbers in the process of Figure 1.1 / operation 48 may for example not be provided. As another example, only lateral movement correction (for example operations 42 and 26) is performed among the operations (36 to 46) to be taken into account. In another example, only axial motion correction (for example, operations 38 to 44) is performed among the operations (36 to 46) to be taken into account.
Operations are performed in the order described or shown. We can foresee different orders.
In step 30, an ultrasound system acquires tissue displacements as a function of time (i.e., motion profiles). As a wave caused by the ARFI (eg a push pulse or a shock excitation of acoustic radiation) passes into a location of the patient, the tissue moves. By scanning the tissue with ultrasound, the data are acquired to calculate the displacements as a function of time. By using a correlation or other similar measures, the displacements represented by the sweeps acquired at different times are determined. Displacements are also determined before the wave reaches the location and / or after the tissue relaxes.
Displacement profiles are obtained in response to multiple pushing pulses. Waves are propagated in the location in response to the pushing pulses. The displacements caused by the waves produced by each thrust pulse are measured, which results in multiple displacement profiles.
Operations 32 and 34 provide an example of tissue displacement acquisition. It is possible to provide different or fewer additional operations to acquire movements of the fabric at a location by pushing pulses.
In step 32, a beam former produces electrical signals for focused ultrasound transmission, and a transducer transforms electrical signals into acoustic signals to transmit the push pulse from the transducer. The force of the acoustic radiation is used. An acoustic excitation is transmitted to the patient. Acoustic excitation acts as a pulse excitation to cause displacement. For example, a 400-cycle transmission waveform with peak power or peak amplitude levels similar to or less than B-mode transmissions for imaging tissue is transmitted in the form of an acoustic beam. In one embodiment, the transmission is a sequence producing a shear wave applied to the field of view. Any ARFI imaging sequence or shear wave can be used.
The transmission is configured by the amplitude power, rate, or other characteristics to cause strain on the tissue sufficient to move the tissue to a location or multiple locations. A focus of transmission of the beam is relative for example to a field of view or ROI to cause a displacement in the field of view or region of interest.
The shock excitation produces a longitudinal or shear wave at a location in space. Where the excitation is sufficiently intense, a wave is produced. The shear wave propagates in the tissue more slowly than does the longitudinal wave in the direction of emission of the acoustic wave so that the wave type can be distinguished by the rate and / or by the management. The difference in rate is used to isolate the shear wave of a longitudinal wave or vice versa. The wave propagates in various directions, such as a direction perpendicular to the direction of the applied stress. The displacement of the wave is greater at locations closer to the focal location where the wave is produced. As the wave propagates, its amplitude decreases.
Multiple thrust pulses are transmitted in sequences. Operation 34 is tracked in response to each of the push pulses prior to transmission of the next push pulse. Any number of push pulses can be transmitted in sequence. As a result, multiple travel profiles are acquired at the same location, but for different periods. Each displacement profile is in response to a different boost pulse, but has the same temporal sampling or similar sampling.
In one embodiment, thrust pulses are focused on different locations laterally distance. The focal positions are for example on the opposite sides of a region of interest or a location where the movement of the tissue is followed. The ARFI is transmitted to remote locations laterally at the same distance, but on opposite sides of the location for tracking tissue. For a two-dimensional scan, laterally spaced locations are in the azimuthal-axial scan plane (eg the left and right sides of the slot).
For a three-dimensional scan, the laterally spaced locations are on opposite sides in any azimuthal-elevation direction. When more than two push pulses are used, the laterally spaced focal locations are evenly distributed around the location or locations for measuring the movement of the tissue. In alternative embodiments, non-opposed focal locations and / or at a distance not equal to the location or locations of movement of the tissue are used.
In other embodiments, thrust pulses are transmitted along the same scanning line and / or they have the same focal position. Multiple ARFI excitation pulses can be generated on the same side with or without the same focal position of an ROI or displacement measurement location.
In operation 34, movements of the fabric are followed. The ultrasound system, such as a system processor, tracks the movements in response to the push pulses. We follow the displacement caused by the propagating wave. Tracking is axial (that is, one-dimensional movements along a scan line are followed), but this can be two-dimensional or three-dimensional tracking.
The tracking is performed as a function of time. Displacements of the tissue at the location are obtained for any number of temporal samplings over a period during which the wave is expected to propagate to the location. By following, for each thrust pulse, one obtains patterns of displacement of the fabric as a function of time.
The tracking period may include times before transmission of the push pulse and / or before the wave reaches the location. Similarly, the follow-up period may include times after the tissue relaxes or the entire wave has spread beyond the location. For example, if K is the reference tracking number (i.e., the number of times the tissue is scanned to detect a displacement (before transmitting an excitation pulse or before the arrival of the wave) where L is the number of traces after the arrival excitation pulse of the wave and M = K + L being the total number of traces M is sufficiently large so that the The last N tracks have only axial displacement from the physiological movement and no displacement from a shear wave.
A transducer and a beamformer acquire echo data at different times to determine the displacement of the tissue. Displacement is detected by ultrasonic scanning. Ultrasound data is obtained. At least some of the ultrasound data responds to a displacement caused by the wave or pressure. A region, such as a region, a full field of view, or a subregion of interest, is scanned by ultrasound. For shear and longitudinal waves, the region is monitored to detect the wave. The echo data represents the fabric when it is subjected to different pressures at different times. The region can be any size, such as 5x5 mm lateral and 10 mm axial. For example, B-mode scans can be used to detect tissue displacement. To detect displacement, Doppler, color flow, or other ultrasound modes can be used.
For a given time, ultrasound is transmitted to the tissue or the region to which one is interested. Any known displacement imaging now or that will be developed later can be used. For example, pulses having a duration of 1 to 5 cycles with an intensity of less than 720 mW / cm 2 are used. It is possible to use pulses having other intensities. The scan is performed for any number of scan lines. For example, 8 or 16 reception beams are formed in two dimensions in response to each transmission. After or while applying a stress, Mode B transmissions are repeatedly performed along a single transmission scan line and receive along adjacent receive scan lines. In other embodiments, only a single receive beam or other numbers of receive beams are formed in response to each transmission. Additional transmission scan lines and a corresponding line or receive lines may be used. Any number of repetitions can be used, such as about 120 times or 15 ms.
The intensity in mode B may vary due to the displacement of the fabric as a function of time. For the scanned scan lines, there is provided a data sequence representing a profile as a function of time of the movement of the tissue from the stress. By transmitting and receiving multiple times, data is received representing the region at different times. Transmission and reception are performed multiple times to determine a change due to the displacement caused by the change in stress. By repeatedly scanning with ultrasound, the position of the tissue is determined at different times.
In one embodiment, the displacement is detected for each of the multiple locations in the space or for a single location. For example, the speed, variance, intensity pattern offset (for example, spot tracking), or other information from the received data is detected as the displacement between two times. A permanence or sequence of movement can be detected for the location or locations.
In one embodiment using mode B data, the data from different scans is correlated axially with time. For each depth or location in space, a correlation is performed on the plurality of depths or locations in space (for example, 64-depth core, the center of the nucleus being the point at which the profile). For example, a present set of data is correlated several times with a reference data set. The location of a subset of data, centered at a given location in the reference game, is identified in the present game. Different relative translations are performed between the two sets of data.
The reference is a first or another data set or data from another scan. The reference game comes from before the constraint, but can come from the constraint. The same reference is used for all motion detection or the reference data changes in a permanent or moving window.
The level of similarity or correlation of the data is calculated at each of the different offset positions. The translation with a very large correlation represents the motion vector or the offset for the instant associated with the present datum relative to the reference.
Any correlation known now or that will be developed later, such as a cross-correlation, a configuration adjustment or a minimum sum of absolute differences, can be used. The structure of the fabric and / or the spots are correlated. Using a Doppler detection, a parasite filter can pass information associated with moving tissue. The velocity of the tissue is deduced from multiple echoes. Speed is used to determine the movement toward or away from the transducer. Alternatively, the relative difference between speeds of different locations may indicate deformation or displacement.
FIG. 2 represents, by way of example, two displacement profiles as a function of time for a location. The amplitude, or distance of the motion vector as a function of time from the reference data, is represented. The analysis period is approximately 25 ms, but may be longer or shorter (eg 12 ms at a sampling rate of 4.8 kHz). Other displacement profiles are possible. Any number of locations can be measured for displacement, such as measuring every millimeter in the 10x5 mm region of interest or measuring at one location only. Displacement is measured for each location and for each sampling time. As shown in FIG. 2, multiple push pulses and corresponding traces are used to acquire multiple motion profiles for each location. Similar profiles are calculated for any other location.
Displacements are used as a function of time and / or space for the calculation. In one embodiment, the displacements for different depths are combined by leaving azimuth and / or elevation distance displacements. For example, the average is based on the depth for displacements for a given scan line, or for a lateral location. As an alternative to averaging, a maximum or other selection criterion is used to determine the displacement for a given lateral location. One can use displacements for only one depth. One can independently use displacements for different depths.
Referring again to FIG. 1, the ultrasound system or processor takes into account the physiological, transducer or physiological movement and the transducer, using displacements in response to multiple pushing pulses. This movement, which is not desired, has axial and lateral components. We take into account one of these components or these two components. Displacements from the different thrust pulses are used to account for lateral movement and / or axial movement caused by forces other than waves produced by the thrust pulses.
Operations 38 to 46 illustrate taking into account the movement that is not desired. One or more of these operations may serve an additional purpose. Thus, for example, the operation 42 is performed whether the movement is correlated or not. Additional or different additional operations may be provided to account for motion that is not desired or not due to the wave.
The taking into account of the axial movement is independent of the taking into account of the lateral movement; The axial movement of the displacements of the displacement profiles can be eliminated (for example, operations 38, 40 and 44). Lateral movement can be eliminated by averaging the viscoelastic parameters calculated from different displacement profiles (eg operation 46). The consideration can be made only for axial movement or only for lateral movement in other embodiments. In the embodiment of FIG. 1, both the axial and lateral movements which are not desired are eliminated.
In operation 38, the displacements as a function of time are combined in response to different thrust pulses. The profiles are temporally aligned, such as shifting one profile relative to the other in time to obtain the best fit. In other solutions, the peaks are identified and positioned at the same time.
After alignment, the displacement amplitudes are combined for each instant. Any combination can be used such as summation, averaging or ratio. In one embodiment, distances are differentiated as a function of time for one profile or subtracted from displacements as a function of time for another profile. The combination eliminates or reduces the contribution to the displacement of ARFI-induced waves.
We can model the axial component of the displacement from a physiological movement or a transducer in the form of a polynomial of order N. We model for example the displacements from the movement which is not desired in the form of a third-order polynomial. The axial displacement followed at a given position is given by
yi (t) and yr (t) being the axial displacements measured at time t after left (1) and right (r) excitation (that is, push pulses on opposite sides of the ROI). ) respectively. The indices 1 and r designate left and right respectively. The axial displacement induced by an excitation pulse ARFI is x (t) which is, in general, the same for both left and right excitation. We model the physiological axial displacements and a transducer by polynomials whose coefficients are given by ai, bi, ci, di and ar, br, cr, dr.
The equation 1 has two parts, one for the instants i = K + 1: MN during which the displacements include a reaction to the wave generated by ARFI (that is to say a part with x (t)) and one for the instants i = N + 1: M during which the displacements do not include the wave produced by ARFI (that is, a part without x (t)). Equation 2 has the same partition. The temporal separation or values of K and N can be predetermined.
Using a ratio, a difference or some other combination of the displacement profiles, eliminates x (t) even for times during which the motions include a reaction to the wave produced by ARFI. For example, subtracting equation 2 from equation 1 gives a difference value as a function of time, Ydiff (t) in the form of:
which is also a polynomial of the third order. This difference value represents a movement occurring during ARFI induced wave propagation, but does not include displacements from ARFI induced waves. It follows that the difference gives information of the physiological movement and / or transducer during the propagation time of the wave and other times.
In the operation 40, a curve is adjusted to the combined displacements (for example, ydiff (t) for 1: M). The coefficients of the polynomial of the model are determined, such as by determining ai, bi, Ci, di and ar, br, cr, dr.
The curve can be additionally adjusted to other displacements, such as displacements coming from different profiles for instants that are not subjected to a movement originating from the ARFI-induced wave (for example, part 2 of each one). equations 1 and 2-x 1: K and MN: N). The coefficients ai, bi, Ci, di and ar, br, cr, dr are determined from the differences in tissue displacements between the push pulses for instants responding to push pulses and from the differences and displacements of the fabric profiles for instants not responding to thrust impulses.
Any curve adjustment can be used. In one embodiment, the coefficients of the polynomial are estimated by resolution using least squares. The polynomial model is a least squares fit to the combined motions of the tissue for ARFI-mediated wave-reactive instants and tissue displacements from the profiles for nonreactive ARFI-induced instants. Thus, for example, the following least squares fit is used to find the coefficients for the curve representing displacement due to axial movement of a physiological transducer or transducer and physiological.
In this matrix, the upper rows rest on the combination displacements and the lower rows rely on the displacements of the distinct profiles and only for moments during which a movement is not subject to, or caused by, the waves induced by ARFI. Using the combined displacements (eg Ydiff (t)) the number of measurements for the adjustment is actually increased to M samples. The estimates of the polynomial coefficients can be more accurate, which results in an estimate of the axial displacement caused by a physiological movement of a transducer, better than if one estimates only with the displacements limited in time of the profiles of displacements individual (ie using only the yi and yr values mentioned in the matrices above).
The curve defined by the estimated coefficients represents the displacements due to the physiological movement and / or a transducer, without the ARFI induced movement. As a result, the axial motion is not desired as a function of time.
For lateral movement, taking into account is part of the calculation of the viscoelastic parameter. The calculation of the operation 42 includes the correction of the estimated axial movement and the elimination of the effects of the lateral movement.
In operation 42, the processor calculates a value or values of a viscoelastic parameter. For example, any viscoelastic parameter such as deformation, rate of deformation, Young's modulus, elasticity or other property can be calculated. In one embodiment, the shear rate is calculated as a viscoelastic parameter.
The value is calculated for each of one or more locations in the region of interest. For example, the value for a single point selected by the user is calculated. As another example, values are calculated for various locations laterally apart in the region of interest.
The value is estimated from the displacement profile. Although two or more displacement profiles are available for each location, only one can be used to estimate the value of the viscoelastic parameter. The others are used for motion correction. Alternatively, separate estimates of the distinct displacement profiles are estimated and used to determine the value for the location.
To estimate the value in one embodiment, the maximum peak or amplitude of the profile is determined. Based on a distance from the location at the source of the constraint (e.g., ARFI focal position), a time difference between the application of the stress and the peak amplitude indicates a velocity. In an alternative solution, the displacement profiles of different locations are correlated to find a delay between locations. This phase shift can be used to calculate the speed between the locations associated with the correlated profiles. In other embodiments, an analytical datum is calculated from the displacement profile and a phase shift is used to determine the elasticity. A phase difference as a function of the time of the displacements of the different voxels or a zero crossing of the phase for a given voxel indicates a speed. The velocity can be used to determine other parameters, such as using shear rate and a known or measured value of stress to determine a Young's modulus.
The calculation of the value of the viscoelastic parameter is a function of the motion correction. Operations 44 and 46 provide correction of the axial and lateral movement respectively.
In operation 44, the axial movement is corrected by modifying the profile or the displacement profiles, which are then used to calculate the value of the viscoelastic parameter. Axial motion that is not desired is eliminated from the displacement profile or displacement profiles. The curve representing the physiological modeled movement and / or transducer for a given profile is subtracted from the measured displacement profile. Where modeling estimates coefficients for each displacement profile, the corresponding curve is subtracted from the respective displacement profile.
FIG. 2 represents two physiological movements estimated for the two respective displacement profiles. For each moment, the curve gives a value of an axial movement due to the physiological movement. The measured displacement profile includes physiological axial movement and ARFI induced wave motion. By subtracting the physiological axial movement, the resulting displacement profile is the ARFI induced wave motion without the undesired motion. Using equations 1 and 2, the axial displacement x (t), caused by the excitation pulse ARFI, is estimated by subtracting the polynomial from the measured displacement y (t). For each moment, the axial displacement resulting from the physiological movement and / or a transducer, is subtracted from the measured displacement. FIG. 3 represents the displacement profiles obtained for the ARFI-induced wave motion after motion correction (ie after filtration (subtraction for each moment) to eliminate the axial motion that is not desired) .
After eliminating the axial movement which is not desired, the value of the viscoelastic parameter is calculated. For a shear rate, the peak or phase shift is used to determine the value. The value is estimated from the results of the subtraction or from the displacement profile as corrected to eliminate axial displacement due to physiological movement and / or transducer.
Where the value is calculated from each of the different profiles for the location, the values obtained can be averaged. Alternatively, a selection (e.g., maximum, minimum, or median) is used. In still other embodiments, the axial movement correction is carried out for one of the profiles and a single value is calculated from the displacement profile obtained.
In operation 46 of FIG. 1, the influence of the lateral movement which is not desired in the calculation of the value is reduced. The reduction of the lateral component of the physiological movement and / or of a transducer also makes use of multiple pulses of ARFI excitations on each side of the region of interest. Displacements measured in response to ARFI excitations on opposite sides of the location are used. ARFI excitations are used equally or otherwise around the region of interest or the single location.
The pulse repetition frequency (PRF) and the pulse repetition interval (PRI) of the tracking pulses being respectively given, the velocity of a physiological movement and a transducer in the lateral direction, on the Time interval T is eliminated from the calculation. The time interval T is given by: T = 2 (PRI M + t excitation) (5) in which texCitation is the excitation time ARFI and M is the total number of follow-ups or follow-up scans before and after each ARFI excitation. The factor of 2 comes from the use of two ARFI excitations, which gives two displacement profiles. It is assumed that the lateral velocity of the physiological movement is constant over the interval T (i.e., the lateral displacement due to the physiological movement is linear over the interval T).
The lateral movement takes place in one of the two directions (for example, either left or right) with respect to the location. Since displacement profiles are provided for calculating the value of the viscoelastic parameter from the traveling wave in each of these directions, the obtained values are influenced in opposite manner by the undesired lateral movement. The processor calculates different values of the viscoelastic parameter from the movements of the tissue due to the different thrust pulses. For example, a shear rate from one shear profile and another shear rate for the same location from another shear profile is estimated. If Vs is the speed of the shear wave, Vm is the combined velocity of the physiological movement and a transducer in the lateral direction, Vsi the shear wave measured from the left-hand excitation, Vsr the wave of shear measured from the right excitation, and x 1 distance from the excitation location to the tracking location, x will be treated as equal for the left and right velocities, but may not be equal in d other embodiments. The arrivals of the wave at the lateral x distance of the left and right excitation positions are given by:
(6) (7)
Equations 6 and 7 show that the shear wave arrives earlier if the motion is in the direction of propagation of the shear wave, and later, if the movement is in the opposite direction to the propagation of the shear wave. shear wave.
The Vsi and Vsr excitation speeds left and right are calculated from the respective displacement profiles. The speed of the excitation induced shear wave ARFI is Vs, and the lateral velocity of the physiological movement and a transducer is Vm as represented by:
(8) (9) Equation 8 is an average. The shear rate for the location is the average of the shear rates for that location, as calculated from the displacement profiles for wave propagation induced in opposite directions. By using the opposite directions, the average suppresses or reduces the influence of lateral movement that is not desired. The result of averaging the different values is the final value of the viscoelastic parameter, such as an average speed used as the shear rate for the location.
Equation 9 represents the lateral movement that is not desired. This lateral movement that is not desired is calculated or not. The undesired lateral velocity caused by transducer and / or physiological movement is eliminated by averaging velocities for shear waves propagating in opposite directions. Alternatively, the undesired rate is calculated and eliminated (i.e., subtracted) from an estimate or several velocity estimates.
In operation 48, the viscoelastic value is output. In one embodiment, an image is output. After taking into account the lateral and / or axial movement that is not desired, values are estimated for different locations. The values for locations in the region of interest are determined by forming parallel receive beams and / or repeating the entire process (eg, ARFI transmission and tracking) for different locations. These values as a function of space or location are mapped to image values to display elasticity and / or shear image. Any imagery of elasticity, currently known or to be developed later, can be used. For example, a shear wave, a longitudinal wave, a deformation or another image is produced. A single image or a sequence of images is produced.
The elasticity or the shear image is displayed alone. Alternatively, a mode B or another image representing the same region or a different field of view is displayed in the vicinity of the elasticity image. In another variant, the elasticity or the shear image is combined with or superimposed on a B-mode image.
In another embodiment, the value is output for a location in the form of a text, a number or a code in a graph. The user selects, for example, a location on a B-mode image. In response, the ultrasound system calculates the value of the viscoelastic parameter of interest for that selected location. A numerical, textual and / or graphical representation of the calculated value is superimposed on the B-mode image, displayed independently or otherwise communicated to the user. In still other embodiments, the output is performed by transfer over a network and / or by being sent to a memory for storage.
Figures 2 to 9 show exemplary results of eliminating axial motion that is not desired. Axial displacement of the physiological movement or transducer is eliminated using in vivo liver data obtained in a Virtual Touch Quantization (VTQ) mode, (i.e., estimating shear rate for a point selected by the user). Figure 2 shows an example of a displacement profile measured at a given lateral location during an in vivo scan. FIG. 2 also shows the polynomial curves adjusted after having performed the least squares algorithm according to equation 4. FIG. 3 represents the displacement profiles from left and right excitation pulses after filtering the axial displacement physiological movement. In other embodiments, the displacement profiles from push pulses are focused to the same position, but at different times.
Figures 4 and 5 show displacement projections for thrust pulses on opposite sides of a region of interest respectively. The horizontal axis is the time and the vertical axis is the lateral spacing. For each transmission beam for tracking, four receive beams are sampled at a given depth. As a result, measurements occur at the same time for every four locations laterally apart. The transmission of the push pulse and the corresponding tracking are repeated for each group of four locations, which results in the horizontal band aspect of Figures 4 and 5. Due to the axial displacement from the physiological movement, the moment of appearance of the peaks for the various locations is partially hidden and is not consistent, as would be desired between locations.
Figures 6 and 7 show the displacement projections of Figures 4 and 5 respectively (i.e. for excitations on opposite sides) after elimination of the axial displacement caused by the physiological movement. The axial component of the physiological motion and a transducer is reduced or eliminated resulting in a clearer indication of the peak as a function of time for each location and more consistency between locations. The shear rate or other value of the viscoelastic parameter is more likely to be accurate or calculated with greater confidence when the undesired axial movement is eliminated from the displacements.
FIG. 8 represents an example of two displacement profiles measured at a given lateral location by transmitting two ARFI excitation pulses (at different times) at the same focal position on the left of the region to which it is located. interested (that is, the left of the measurement location). The two profiles are different because the physiological movement varies with time and the ARFI excitation pulses, and the associated tracking, are performed sequentially. Figure 9 shows displacement profiles after filtering out the axial displacement of the physiological movement. The displacement curve that is not desired is adjusted to the differentiated displacement for all instants, and the individual displacements for moments before the ARFI excitation and after tissue relaxation. The adjustment curve is subtracted from the measured displacement. Figure 9 shows that the algorithm accurately eliminates the axial component of physiological movement and a transducer.
In order to test the lateral displacement resulting from the physiological movement and / or a transducer, a linear stage moves in translation a transducer array, at a constant speed laterally on the surface of a ghost imitating a tissue. This arrangement mimics a lateral movement of a transducer. Lateral displacement that is not desired may be due to movement of the transducer (for example, a sonograph rotating the transducer and / or translating it) to patient movement (causing the transducer to move relative to the transducer). to the patient) or to a physiological movement. During lateral movement of the transducer array in the test arrangement, displacements are measured at a location selected by a user, using push pulses on opposite sides of the location. The shear rate measured from the displacements measured on one side is greater than the shear rate measured from displacements measured from the opposite side. By reversing the direction of movement of the transducer, the side with the largest shear rate changes. Lateral movement that is not desired increases one of the speeds and decreases the other in the direction of movement, the average reducing the influence of the lateral movement that is not desired.
FIG. 10 shows an embodiment of a system 10 for ultrasonic imaging by the force of the acoustic radiation. The system 10 implements the method of Figure 1 or other methods. The system 10 comprises a transmission beamformer 12, a transducer 14, a reception beamformer 16, an image processor 18, a display 20 and a memory 22. Additional or different elements may be provided. User input is provided for example for user interaction with the system, such as to select a location where a measurement is to take place.
The system 10 is an ultrasound imaging system for medical diagnosis. The system 10 is configured to acquire echo data for shear or other elasticity imaging using multiple push pulses. In variants, the system 10 is a personal computer, a workstation, a PACS station or other arrangement in one location or distributed over a network for real-time or post-acquisition imaging. System 10 acquires data from a memory or other ultrasound imaging system.
The transmission beam former 12 is an ultrasonic transmitter, a memory, a pulse generator, an analog circuit, a digital circuit or one of their combinations. The transmission beamformer 12 may operate to produce waveforms for a plurality of channels with different or relative amplitudes, delays, and / or phase shifts. After transmission of acoustic waves by the transducer 14 in response to the created electric waveforms, a beam or multiple beams are formed. A transmission beam sequence is produced to scan a region. Sector, Vector®, Linear or other scan formats can be used. We can scan the same area several times. For circulation or doppler imaging and for shear imaging, a scanning sequence is used along the same line or lines. In Doppler imaging, the sequence may comprise multiple beams along a same scan line before scanning a neighboring scan line. For shear or longitudinal wave imaging, one can scan or nest frames (for example, scan the entire region before rebalancing). One can use a nesting of lines or groups of lines. In variants, the transmission beamformer 12 produces a plane wave or a diverging wave for faster scanning.
The same transmission beam former 12 can produce shock excitations or electric waveforms to produce acoustic energy to cause displacement. Electric waveforms are produced for acoustic radiation force shocks. In variants, a different transmission beamformer is provided to produce the shock excitation. The transmission beam former 12 causes the transducer 14 to produce thrust pulses or acoustic radiation force shocks. By using the delay profile between the channels, the transmission beamformer 12 directs the push pulses to the desired focal position or focal positions.
Transducer 14 is a network for producing acoustic energy from electric waveforms. For a network, relative delays focus the acoustic energy. A given transmission event corresponds to the transmission of acoustic energy by different elements at a time substantially the same given by the delays. The transmission event can provide an ultrasonic energy pulse for moving the tissue. The pulse is a shock excitation or a tracking pulse. Shock excitation includes waveforms having many cycles (e.g., 500 cycles), but occurs in a relatively short time to cause movement of the tissue over a longer time. A tracking pulse can be a B mode transmission, such as using 1 to 5 cycles. Follow-up pulses are used to scan a region of a patient undergoing a stress change.
The transducer 14 is a network of dimension 1, 1.25, 1.5, 1.75, or 2 of piezoelectric or capacitive membrane elements. A modulator matrix can be used. Transducer 14 comprises a plurality of elements for transduction between acoustic and electrical energies. Receiving signals are generated in response to ultrasonic energy (echoes) arriving at the transducer elements 14. The elements are connected to channels of the transmit and receive beam formers 12, 16.
The receive beamformer 16 comprises a plurality of channels having amplifiers, delays and / or phase rotations and one or more summers. Each channel is connected to one or more transducer elements. The receive beam former 16 is configured in hardware or software to apply relative delays, phases, and / or apodization to form one or more receive beams in response to each imaging or tracking transmission. A receiving operation may not occur for echoes from the shock excitation used to move the tissue. The receive beamformer 16 outputs data representing locations in the space using the reception signals. Relative delays and / or phase shift and summation of signals from different elements results in beam formation. In alternative embodiments, the beamformer 16 is a processor for producing samples, using a Fourier transform or the like.
The receive beamformer 16 may comprise a filter, such as a filter for isolating information at a second harmonic or other frequency band with respect to the transmitted frequency band. Such information may more likely include the desired tissue, contrast agent and / or motion information. In another embodiment, the receive beamformer 16 includes a memory or buffer and a filter or summator. Two or more receive beams are combined to isolate information at a desired frequency band, such as a second harmonic, a cubic fundamental, or another band.
In coordination with the transmission beam former 12, the reception beamformer 16 produces data representing a region of interest at different times. After the acoustic shock excitation, the receive beamformer 16 produces beams representing locations along a line or a plurality of lines at different times. By scanning the region of interest by ultrasound, data is produced (eg, beamformed samples). By repeating the scan, ultrasound data is acquired representing the region at different times after the shock excitation.
The receive beamformer 16 outputs beam summation data representing one or more locations in the space. A dynamic focus can be provided. The data may be for different purposes. For example, scans for mode B data or tissue data other than for ARFI ultrasound imaging are performed. Alternatively, the B mode data is also used to determine a value of the viscoelastic parameter. As another example, data is acquired for shear imaging by a series of shared scans and B or Doppler scanning is done separately or using some of the same data. The ultrasound or echo data comes from any processing stage such as beamformed data before detection or after data detection.
The processor 18 is a mode B detector, a Doppler detector, a pulsed wave Doppler detector, a correlation processor, a Fourier transform processor, an application specific integrated circuit, a general processor, a processor controller, an image processor, a user programmable gate array, a graphics processing unit, a digital signal processor, an analog circuit, a digital circuit, their combinations or other devices known hitherto or which will be developed later to detect and process information for display from beam-formed ultrasound samples.
In one embodiment, the processor 18 comprises a detector or several detectors and a separate processor. The separate processor is a control processor, a general processor, a digital signal processor, an application specific integrated circuit, a user programmable broadcast circuit, a network, a server, a processor group, a processor unit, graphical processing, a data path, their combinations or other devices known hitherto or which will be developed later for the correction of a movement and / or the calculation of a value of a viscoelastic parameter. An attenuation, a shear modulus, a shear viscosity, a shear rate or one or more other shear wave propagation properties can be estimated. The separate processor may be configured, for example, in hardware and / or software to perform any combination of one or more of the operations 36 to 48 shown in FIG.
The processor 18 is configured to estimate a tissue displacement induced by the acoustic shock excitation. By using correlation, tracking, motion detection or other displacement measurement, the amount of positional shift of the tissue is estimated. The estimation is carried out several times over a period of time, such as before the tissue moves due to stress, during stress and after the tissue has returned, for the most part, completely to a relaxed state ( for example, having recovered from the stress caused by shock excitation). Fabric offset differences between locations indicate relative stiffness or elasticity.
The processor 18 is configured to combine displacements of different profiles such as by subtracting a displacement profile from another. Using the combined displacements, the processor 18 is configured to adjust a curve to model axial displacements due to sources other than the ARFI induced wave. The curve is subtracted from a displacement profile measured by the processor 18 to isolate displacements due to the ARFI-induced wave.
The processor 18 is configured to estimate values of the viscoelastic parameter. Phase shift detection, correlation, displacement determination, peak identification, velocity calculation, stress measurements, strain relief and / or other processes can be used to estimate the elasticity, velocity, module or other parameters. The processor 18 is configured to take into account, in the estimation, the lateral and / or axial movement that is not desired. By subtracting the undesired axial motion from the displacement profile, the estimated value may be more representative of the ARFI induced motion. By averaging the value estimates from the displacement profiles produced by push pulses on opposite sides, the value obtained may have less undesired lateral movement.
The processor 18 is configured to produce an image or several images. A shear wave velocity image is produced, for example. Other elastography images may be produced, such as shear modulus, strain, or deformation rate image. The image is superimposed as a region of interest within a B-mode image. Elasticity values modulate colors at locations in the region of interest. . Where the value of the elasticity is less than a threshold, information in mode B can be displayed without modulation by the value of the elasticity. Alternatively or additionally, the values for a location or for a few locations are displayed as text, numerically and / or in the form of a graph.
The processor 18 operates according to instructions stored in the memory 22 or in another ultrasonic imaging memory of the force of the acoustic radiation. The memory 22 is a non-transitory memory medium that can be decrypted by a computer. Instructions for carrying out the operations, methods and / or techniques mentioned herein are provided on the storage medium that can be deciphered by a computer or on memories, such as a cache, a buffer, a RAM, removable media, a hard disk or other storage media that can be read by a computer. Computer-readable storage media include various types of volatile and non-volatile memory media. Functions, operations or tasks illustrated in the figures or described herein are performed in response to a set or sets of instructions stored in or on computer-readable storage media. Functions, operations, or tasks are independent of the particular type of instruction set, storage media, processor, or processing strategy, and can be performed in software, hardware, printed circuit boards, firmware, a microcode and the like, operating alone or in combination. Similarly, the processing strategies may include multiprocessing, multitasking, parallel processing, and the like. In one embodiment, the instructions are stored on a removable media device for playback by local or remote systems. In other embodiments, the instructions are stored in a remote location for transfer by a computer network or telephone lines. In still other embodiments, the instructions are stored in a given computer, CPU, GPU or system.
The display 20 is a CRT, LCD, projector, plasma or other display for displaying a value, two-dimensional images or three-dimensional representations. Two-dimensional images represent a spatial distribution in an area, such as a plane. Three-dimensional representations are rendered from data representing a spatial distribution in a volume. The display 20 is configured by a processor 18 or other device to input the displayed signals as an image. The display 20 displays an image representing the calculated value for a region of interest.
Although the invention has been described above with reference to various embodiments, it is obvious that one can make several changes and modifications without departing from the scope of the invention. It is therefore understood that the above detailed description is considered illustrative rather than limiting and it goes without saying that everything that falls within the spirit and scope of the invention, including equivalents, is protected. In Figure 1
Step 30: Acquire tissue displacements for two or more push pulses
Step 32: Transmit thrust impulses
Step 34: Follow a Movement
Step 36: Take into account physiological movement and / or transducer
Step 38: Produce Combined Movements
Step 40: Adjust a curve from combined moves
Step 42: Calculate a viscoelastic parameter Step 44: Subtract axial movement / curve Step 46: Average different directions Step 48: Remove the viscoelastic value In Figure 2 - Measured displacement displacement on the left - Physiological movement estimated during a push to the left - * - Measured displacement to the right - · - · * Physiological movement estimated during a push to the right In figure 3 - Displacement after filtering of physiological movement during a push to the left --- Movement after filtering of physiological movement FIG. 10: Transmission beamformer 14: Transducer (XDRC) 16: Reception beamformer 18: Processor 20: Display 22: Memory

权利要求:
Claims (12)
[1" id="c-fr-0001]
A method of acoustic ultrasound imaging by the force of acoustic radiation, characterized in that a transducer is transmitted (32) of multiple thrust pulses in sequence, the thrust pulses producing (48) a wave in the tissue of the 'a patient; following (34) movements of the tissue in response to the pushing pulses; considering (36) a physiological movement of the transducer or physiologic and the transducer using displacements in response to multiple pushing pulses; a viscoelastic parameter is calculated (42) as a function of the displacements and the estimated movement; and producing (48) an image according to the viscoelastic parameter.
[2" id="c-fr-0002]
2. Method according to claim 1, characterized in that the transmitter (32) comprises transmitting (32) at least a first of the thrust pulses of a first side of a region of interest, and transmitting (32) at least one second of the thrust pulses of a second side opposite to the first side of the region of interest.
[3" id="c-fr-0003]
3. Method according to claim 1 or 2 characterized in that taking into account (36) comprises estimating an axial movement and wherein calculating (42) comprises subtracting (44) the axial movement as a function of time of the displacements followed as a function of time and calculating (42) the viscoelastic parameter from the results of the subtraction (44).
[4" id="c-fr-0004]
A method according to claim 3, characterized in that estimating the axial movement comprises adjusting (40) a polynomial to differences in tissue displacements between the push pulses for periods of time in response to the pulsing and traveling pulses of the tissue during times when there is no reaction to the push pulses.
[5" id="c-fr-0005]
5. A method according to any one of claims 1 to 4, characterized in that taking into account (36) comprises taking into account (36) a lateral movement and wherein calculating (42) comprises reducing the influence of the lateral movement in the calculation (42).
[6" id="c-fr-0006]
Method according to Claim 5, characterized in that taking into account (36) and calculating comprises calculating (42) different values of the viscoelastic parameter from the tissue displacements of the different thrust pulses and calculating the average (46) of the values, the result of averaging (4 6) being the calculated viscoelastic parameter.
[7" id="c-fr-0007]
7. A method for ultrasound imaging by force of acoustic radiation, the method being characterized in that: (30) an ultrasound system acquires first tissue displacements at a location and in response to a first wave produced at from an acoustic force radiation pulse laterally away from a first side of the location; it is estimated (42) that a first velocity of the first wave at the location from the first movements of the tissue is acquired (30) by the ultrasound system, second displacements of the tissue at the location and in response to a second wave produced from a second radiation shock of the remote acoustic force laterally along a second side of the location, the second side being different from the first side; estimating (42) a second velocity of the second wave at the location from the second displacements of the tissue; the average (46) of the first and second speeds is calculated; and leaving (48) the average speed.
[8" id="c-fr-0008]
The method of claim 7, characterized in that calculating the average (46) comprises eliminating lateral movement due to movement of the physiological or transducer and physiological transducer.
[9" id="c-fr-0009]
9. A method for ultrasound imaging by the force of acoustic radiation, characterized in that it comprises: acquiring (30) by an ultrasound system, first tissue displacements as a function of time at a location and in response to a first wave produced from a first shock of the radiation of the acoustic force; acquiring (30) by the ultrasound system second tissue displacements as a function of time at and in response to a second wave produced from a second shock of the radiation of the acoustic force; producing (38) combined displacements as a function of time from the first and second displacements of the tissue; adjusting (40) a curve to the combined displacements; subtract (44) the curve of the first movements of the fabric; estimating (42) a viscoelastic value from the results of the subtraction (44); and outputting (48) the viscoelastic value.
[10" id="c-fr-0010]
The method according to claim 9, characterized in that acquiring (30) the first and second movements of the tissue comprises acquiring (30) first and second displacement profiles respectively for the location at different periods.
[11" id="c-fr-0011]
The method of claim 9, characterized in that producing (38) combined displacements comprises differentiating the first tissue displacements from the second tissue displacements.
[12" id="c-fr-0012]
A method according to claim 9, characterized in that adjusting (40) the curve to the combined movements of the tissue comprises at least making a least squares adjustment (40) of a polynomial to the combined movements of the fabric during reaction times. at the first and second waves and at the first and second movements of the tissue during non-reaction times at the first and second waves.

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