• 专利附录
  • 专利说明
  • 权利要求
  • 类似技术
  • 同族专利
  • 引用文献
  • 法律状态
  • 优先权
    • 专利摘要:
    ULTRASONIC DIAGNOSTIC IMAGING SYSTEM FOR SHEAR WAVE ANALYSIS AND METHOD FOR OPERATING AN ULTRASONIC DIAGNOSTIC IMAGING SYSTEM TO MEASURE SHEAR WAVES. An ultrasonic diagnostic imaging system produces an image of shear wave velocities by transmitting energy pulses to generate shear waves. A plurality of tracking lines are transmitted and echoes received by the focus of a beamformer adjacent to the location of the energy pulses. Trace lines are time-interleaved sampled. The echo data acquired along each tracking line is processed to determine the period of maximum tissue displacement caused by shear waves at points along the tracking line, and the peak periods in adjacent tracking lines compared to calculate a velocity of the local shear wave. The resulting map of shear wave velocity values is color coded and displayed over an anatomical image of the region of interest.
    公开号:BR112012012230B1
    申请号:R112012012230-4
    申请日:2010-11-15
    公开日:2021-04-20
    发明作者:Roy B. Peterson；Vijay Shamdasani；Robert Randall Entrekin；Yan Shi；Hua Xie；Jean-Luc Robert；Anna Teresa Fernandez
    申请人:Koninklijke Philips N.V.；
    IPC主号:
    专利说明:

    [001] This invention relates to medical diagnostic ultrasound systems and, in particular, to ultrasound systems that perform measurements of tissue stiffness or elasticity using shear waves.
    [002] One of the sought after goals of diagnostic imaging is an accurate tissue characterization. A physician would like to obtain a diagnostic region of an organ of the body and have an imaging system that identifies tissue characteristics in the image. Conveniently, the physician would like to have an imaging system to identify a lesion as malignant or benign.
    [003] While fully achieving this goal, the production of diagnostic imaging can, however, give the physician clues as to the composition of tissue. One technique in this area is elastography, which measures the elasticity or stiffness of tissues in the body. For example, breast tumors or masses with high rigidity can be malignant, while lighter and more complicated masses are just as benign. Since the rigidity of a mass is known to correlate with benignity or malignancy, elastography provides the physician with another piece of evidence to aid in diagnosing and determining a treatment regimen.
    [004] Elastography, as initially observed, evaluated the tissue in the body when subjected to compressive pressure. When an ultrasound probe is pressed firmly against the body, the underlying soft tissue will compress to a greater degree than the underlying hard tissue. But elastography can be very operator dependent, with results being influenced by where and how much pressure is being applied to the body. It would be desirable to be able to assess elasticity by a method that is not as operator dependent.
    [005] An alternative approach to elastically measuring is shear wave measurement. When a point in the body is compressed, then released, the underlying tissue is compressed downward, then resumes upward as the compressive force is released. But since tissue under the compressive force is continuously joined to the surrounding tissue, the lateral tissue decompressed from the force vector will respond to the up and down movement of the compressed tissue. A ripple effect in this lateral direction, referred to as a shear wave, is the response in the surrounding tissue to the downward compressive force. In addition, it has been determined that the force required to push tissue downward can be produced by the radiation pressure of an ultrasound pulse, and ultrasound reception can be used to sense and measure tissue motion induced by shear waves. The velocity of the shear wave is determined by the mechanical properties of the local tissue. The shear wave will travel at one speed through the soft tissue, and at another, higher speed through the hard tissue. In measuring the velocity of the shear wave at a point on the body, information is obtained for tissue characteristics such as its elastic shear modulus, Young's modulus and dynamic shear viscosity. The laterally propagating shear wave travels slowly, usually a few meters per second or less, making the shear wave susceptible to detection, although it attenuates quickly over a few centimeters or less. See, for example, U.S. Patent 5,606,971 (Sarvazyan) and U.S. Patent 5,810,731 (Sarvazyan et al.). Since the same “pulse of energy” can be repeated for each measurement, the shear wave technique lends itself to objective quantification of tissue characteristics with ultrasound. In addition, the shear wave velocity is independent of the energy pulse intensity, making the measurement less user dependent.
    [006] In conventional pulse-echo ultrasound, an ultrasound pulse is transmitted outside the probe and the echoes reflected back to tissue encountered by the pulse are received directly. However, since the shear wave travels laterally, it cannot be directly received absent a window laterally situated to a receiver. See, for example, Figure 2 of the Sarvazyan et al. patent, which suggests receiving the shear waves on a different side of the transmitter tissue when measuring the shear waves in the sinus. But such a technique requires separate transmitters and receivers, and differently situated acoustic windows are not always available. So researchers looked for indirect ways to measure the shear wave. A common way to do this is to acquire successive sets of tissue image data, then process the data to detect shear wave propagation through the tissue as manifested in the resulting tissue motion caused by the shear wave. See Sarvazyan and Sarvazyan et al. to discuss about this approach. The acquired echo data, when ultrasound is used as opposed to magnetic resonance imaging, can be processed by known ultrasound techniques to detect motion, including Doppler and sequential echo data correlation.
    [007] But it takes time to acquire a series of datasets and, as previously mentioned, shear waves attenuate quickly in tissue, which presents a problem to solve motion in insufficient detail to measure the velocity of shear wave propagation amplitude, which typically causes tissue displacement of less than 30 micrometers. A solution to this problem was put forward by Fink et al. in U.S. Patent 7,252,004, which proposes to observe the propagation of the shear wave by rapidly acquiring the images of unfocused plane waves, each insonification of a large tissue expansion and repeated at a rate of at least 500 repetitions per second, and preferably in the range of 1000 to 5000 repetitions per second. Rather than acquiring an image by transmitting and receiving individual lines of data through the image field, which implies a complete transmit-receive cycle for each line, Fink et al. it insonifies the entire Region of Interest (ROI) with a single unfocused wave, then acquires echoes resulting from wave transmission through tissue during a subsequent reception period. (Sarvazyan considers an analogous approach by associating all elements of his transducer in parallel during reception.) Since each ROI interrogation only requires a single waveform transmission, datasets can be successively acquired at the high rate that Fink et al. want. A similar solution to achieve the required ultra-fast frame rate is carried out by Tanter et al. (Ultrasound in Medicine and Biology, 34(9) 1373-1386, 2008) and Bercoff et al. (IEEE Transactions on Ultrasonics, Ferroelectrics and Frequency Control, 51 (4) 396-409, 2004) via emission mode reduction to a single flat wave insonification. While unfocused waveform lacks signal-to-noise performance and the focal resolution of individual image lines, Fink et al. intends to compensate for this deficiency with its high data acquisition rate. It would be desirable, however, to be able to observe and measure the propagation velocity of a shear wave with precision and good signal-to-noise performance and thus with conventional ultrasound systems.
    [008] In accordance with the principles of the present invention, a diagnostic ultrasonic imaging system and method is described and allows a user to acquire sufficient highly resolved image data to measure the velocity of a shear wave that propagates through of the fabric. One or more energy pulses are transmitted into tissue with an ultrasound probe to ultrasonically compress the tissue in the vector direction of the energy pulses. Immediately thereafter, focused tracking pulses are transmitted and received by the probe in proximity to the vector of the energy pulse that generates the shear wave. Each tracking pulse vector is repeatedly time-interleaved sampled so that motion produced by a shear wave can be detected when it occurs at each location of the tracking pulse vector, preferably by correlating the echo data from successive interrogations of the vector. As the shear wave moves laterally away from the energy pulse vector, the positioning of the tracking pulses can also be moved laterally to follow the propagation of the shear wave. Repeatedly sampled tracking pulse vector data is processed to find the periods at which the shear wave causes a maximum displacement at each point of the tracking pulse vector, preferably by cross-correlation, curve fitting, or successive displacement measurements of interpolation. Analysis of the periods at which points on adjacent sample vectors undergo maximum displacement yields a measurement corresponding to the velocity of the shear wave at particular locations in the vector, with velocity variations indicating tissues of different stiffness or elasticity. Since shear waves attenuate very quickly, it is generally not possible to acquire shear wave data for an entire image field with a single vector of the energy pulse. Thus, the process is repeated at another location in the tissue to acquire speed from the shear wave measurements in another region of the tissue. The process is repeated until the shear wave data has been acquired over the desired image field. The velocity information is preferably presented as a two- or three-dimensional image of the tissue, color-coded by the velocity of the shear wave data at points in the image. In the drawings:
    [009] Figure 1 illustrates in block diagram of an ultrasonic diagnostic imaging system built in accordance with the principles of the present invention.
    [010] Figures 2a-2d illustrate the transmission of a sequence of energy pulses to different depths to produce the shear wavefront.
    [011] Figure 3 spatially illustrates the pulse sequence that pulses along an energy pulse vector, the resulting shear wave front, and a pulse vector series of traces.
    [012] Figure 4 illustrates the transmission and reception of the 4x multiline for the production of four adjacent multiline tracking pulse vectors.
    [013] Figure 5 illustrates four laterally adjacent groups of 4x multiline tracking pulse vectors.
    [014] Figure 6 illustrates the shear wave displacement curves at two locations as they pass through the tissue.
    [015] Figures 7a-7c illustrate a spatially time-interleaved sequence of energy pulse vectors distributed laterally over an image field.
    [016] With reference to the first in figure 1, an ultrasound system constructed according to the principles of the present invention for measuring shear waves is shown in block diagram form. An ultrasound probe 10 has a transducer array 12 of transducer elements for transmitting and receiving the ultrasound signals. The array can be an array of dimensional or two dimensional transducer elements. Any type of matrix can digitize a 2D plane and the two-dimensional matrix can be used to digitize a volumetric region in front of the matrix. The matrix elements are coupled to a transmit beamformer 18 and a multi-line receive beamformer 20 by a transmit/receive (T/R) switch 14. Coordination of transmission and reception by the beamformers is controlled by a controller of the beamformer 16. The multiline receive beamformer produces several, spatially distinct receive lines (A-lines) of echo signals during a single transmit-receive interval. The echo signals are processed by filtering, noise reduction and the like by a signal processor 22, then stored in an A-line memory 24. A-line samples temporarily distinct with respect to the same spatial vector location are associated with a with the other in a set of echoes referring to a common point in the image field. The echo signals by r.f. of the successive A-line sampling of the same spatial vector are correlated by a cross correlator by r.f. from A-line 26 to produce the sequence of tissue displacement samples for each sampling point in the vector. Alternatively, the A-lines of a spatial vector can be processed by Doppler to detect shear wave motion along the vector, or other phase-sensitive techniques can be employed. A wavefront peak detector 28 is amenable to detecting the displacement of the shear wave along the A-line vector to detect the peak of the shear wave displacement at each sampling point on the A-line. In a preferred embodiment this is done by curve fitting, although cross-correlation and other interpolation techniques can also be employed if desired. The period in which the peak shear wave displacement occurs is observed with respect to periods of the same event at other locations on the A-line, all in a common time reference, and this information is coupled to a front velocity detector. of a 30 wave that differentially calculates the shear wave velocity of the periods of maximum displacement in the adjacent A-lines. This velocity information is coupled into a velocity display map 32 which indicates the velocity of the shear wave at spatially different points in a 2D or 3D image field. The velocity display map is coupled to an image processor 34 which processes the velocity map, preferably overlaying the anatomical ultrasound image of the tissue, onto the screen in an image display 36.
    [017] Figures 2a-2d illustrate transmission of the energy pulse sequence with high focused magnetic image (eg magnetic image of 1.9 or less to be within FDA diagnostic limits) along a single direction to produce the shear wave front. The long duration, high magnetic image pulses are used so that enough energy is transmitted to move the tissue down along the transmission vector and cause the shear wave to develop. In Figure 2a, probe 10 on skin surface 11 transmits a first energy pulse 40 into tissue with a beam profile 41a, 41b at a given focal depth indicated by shaded area 40. This energy pulse will shift tissue at focus to low, resulting in a shear wavefront 42 emitting outward from the displaced tissue.
    [018] Figure 2b illustrates a second pulse of energy 50 transmitted by the probe 10 along the same vector and focused on the deeper depth of the shaded area 50. This second pulse of energy 50 displaces the tissue at the focal depth, causing the shear wave front 52 emits outwardly of the displaced tissue. Thus, the frontal shear waves 42 and 52 are propagating laterally through the tissue, with the initial wavefront 42 before the second.
    [019] Figures 2c and 2d illustrate the transmission by probe 10 of two more energy pulses 60 and 70, each at a successively greater depth and each emitting outwards the front of the shear wave 62 and 72. It is seen in Figure 2d that the wavefront of the composite of the four energy pulses, indicated by dotted lines 75a and 75b, extends to an appreciable depth in the tissue, from the shallow depth of the first energy pulse 40 to the deepest of the fourth energy pulse 70 This allows the measurement of the shear wave over an appreciable depth of tissue. In an implementation described below, this technique is used to detect shear wave propagation over a depth of 6 cm, a depth suitable for imaging and sinus diagnosis.
    [020] It will be noted that a number of higher or lower energy pulses can be transmitted along the energy pulse vector, including a single energy pulse. Multiple pulses of energy can be transmitted in any order, with the order determining the shape and direction of the composite's shear wavefront. For example, if the energy pulses of Figures 2a-2d were transmitted in sequence from deepest (70) to shallowest (40), the composite shear wave front of Figure 2d would have the inverse slope shown in Figure 2d. In a preferred embodiment, each energy pulse is a long pulse of 50 to 200 microseconds in duration. A typical duration is 100 microseconds, for example. The ultrasound produced during the 100 microsecond duration of the pulse is compression waves and can have a frequency of 7 or 8 MHz, for example. The energy pulses are well focused, preferably at an f-number of 1 or 2. In an implementation of the sequence of four energy pulses shown in figure 2a-2d, one energy pulse is transmitted every 2.5 milliseconds, giving the energy pulses at a transmission frequency of 400 Hz. In another implementation, all four energy pulses are transmitted in a sequence to cast the entire shear wavefront before tracking of the A-lines begins.
    [021] Figure 3 is another illustration of the use of four energy pulses to create a composite shear wavefront. The four energy pulses are transmitted along vectors 44, 54, 64 and 74 which are seen to be aligned along a single vector direction in Figure 3. When the shallowest 44 vector energy pulse is transmitted first followed by successively deeper energy pulses, the front shear waves of the respective energy pulses will have propagated as indicated by waves 46, 56, 66 and 76 for a short time after the last energy pulse (vector 74) has been transmitted. As shear waves 46, 56, 66, and 76 travel outward from the energy pulse vector, they are interrogated by the tracking pulses 80 shown in spatial progression along the top of the drawing. Tracking pulses can occur between and after energy pulses.
    [022] According to the principles of the present invention, the velocity of the shear wave that travels laterally is detected by sensing the tissue displacement caused by the shear wave as it proceeds through the tissue. This is done with transmitted time-interleaved sampling pulses adjacent to the energy pulse vector as shown in Figure 5. In this example the energy pulse 40 is transmitted along the energy pulse vector 40 to cause a traveling shear wave. laterally. The A-line vectors adjacent to energy pulse vector 40 are sampled by sampling pulses T1, T2, T3, T4, and T5 transmitted along each vector in a time-interleaved sequence. For example, the location of the first vector A1 is sampled by a first pulse T1, then the location of the second vector A2 by the next pulse T2, then A3, A4, and A5. Thus, the A1 location of the vector is sampled again, and the sequence repeats. Since sampling is time-interleaved, each of the five vector locations is sampled once every five sampling pulses in this example. In this example, each vector location is pulsed fifty-five times for a total tracking period of 27.5 ms each pulse results in echoes returning along the vector that are sampled by a high-speed A/D converter. Thus, for each point sampled along each vector there is a set of 55 samples, with each sample taken at one fifth of the pulse rate of the pulse sequence of the T1-T5 sample. The sampling rate will be chosen in consideration of the frequency content of the displacement of the shear wave being detected to satisfy the Nyquist criterion for sampling. Since the purpose of sampling is to feel and track the displacement effect of the shear wave as it proceeds through tissue, the vector locations can be located together to slowly move the shear waves and further apart to more quickly move the shear waves. Other time-interleaved sequences of vector sampling can also be employed. For example, odd-numbered vectors could be sampled in sequence, followed by sampling the even-numbered vectors. As another example, vector locations A1-A3 could be sampled time-interleaved, so vector locations A2-A4, then vector locations A3-A5 track the displacement of the shear wave as it proceeds. Other sequences can also be used depending on the situation. The time-interleaved sample sets at each point along each sample vector are then processed to find the maximum tissue displacement period at each point of each vector as described in detail below.
    [023] According to another aspect of the present invention, multi-line transmission and reception is employed so that a single tracking pulse can simultaneously sample a plurality of closely spaced adjacent A-line locations. With reference to Figure 4, a preferred technique for multi-line transmission and reception is shown. In Figure 4 a single A-line tracking pulse with a beam profile 82a, 82b that insonifies various locations of the receive line is transmitted as indicated by the large arrow A#. Preferably the tracking pulse is called a "fat pulse" as described in U.S. Patent 4,644,795 (Augustine), for example. In this example, four receive line locations A1-1, A1-2, A1-3, and A1-4 are sleepless. The echoes from the four receive lines (4x multiline) are received in response to the single transmit pulse and are approximately delayed and summed to produce coherent echo signals along each of the receive lines. The beamformer capable of producing such simultaneous multilines is described, for example, in U.S. Patents 5,318,033 (Savord), 5,345,426 (Lipschutz), 5,469,851 (Lipschutz) and 6.695,783 (Henderson et al. ) These multi-line beamformers are typically used to reduce acquisition time and thus increase the frame rate of live ultrasound images, which is particularly useful when imaging the beating heart and blood flow in real-time echocardiography. They are also useful in 3D ultrasound imaging so that real-time screen frame rates can be obtained. See, in this regard, U.S. Patent 6,494,838 (Cooley et al.). In an implementation of the present invention, the benefit of multiline acquisition is twofold: it allows for a closely spaced sampling line density and the rapid acquisition of a short duration shear wave that only travels a short distance through the tissue before being dissipated by attenuation. While higher order multiline can be employed and sample over a larger number of A-lines at the same time and thus a higher sampling rate, this will require a wider transmit beam (A#) to simultaneously insonify the greatest number of receive lines. The wider transmit beam will consequently decrease the signal-to-noise performance of the higher order implementation.
    [024] Figure 5 illustrates the use of 4x multiline reception for transmission and reception along each sampling vector A1-A5. A first tracking pulse I'I is transmitted close to the energy pulse vector 44, insonifying four locations of the receive line A1-1 to A1-4 and four multiline A-lines are received in response from the adjacent side region A1. When the four multilines are centered with respect to the transmitted tracking pulse, echoes from the two A-lines are received on either side of the center of the center of the tracking pulse beam, shown by A1-1 and A1-2 to the left of center and A1 -3 and A1-4 right of center. In a preferred embodiment, the A-lines are spaced 0.5 mm apart from each other. Shear waves generally move at a speed of 1-10 meters per second, and consequently the tracking pulses are repetitively transmitted below the A1-A5 regions in time-interleaved form and the A-line samples received from the A-line locations. A during time intervals and between energy pulses (if any), and for 20 ms after the last energy pulse, after the shear wave has propagated out of a one-centimeter sampling window A1-A5. Since shear waves can have frequency components in the range of approximately 100 Hz to approximately 1000 Hz, sampling theory dictates that each A-line should have a sampling rate of 2 kHz. This results in a series (set) of fifty-five A-line samples from each sampling point in each multiline A-line.
    [025] In the example of Figure 5, five tracking pulses, T1-T5, are transmitted over the successive sampling windows A1-A5 adjacent to the energy pulse vector 44 to prove the effect of shear wave displacement per wave spreads. A typical sampling pulse is a short pulse, usually just one or two cycles, at a frequency suitable for penetrating the depth being studied, such as 7-8 MHz. Each tracking pulse is offset by 2 mm from its adjacent neighbors, resulting in twenty A-lines spaced 0.5 mm apart with 4x multiline over a total distance of one centimeter. There are several ways to interrogate the sampling windows. One is to just sample region Al until the shear wave is detected, then start sampling in region A2, then A3, and so on. Another is to time-interleave sampling in the regions as described above, sampling with T1-T5 tracking pulses in succession, then repeating the sequence. With the latter approach five sampling windows with twenty A-line tracking positions can track the shear wave effect simultaneously. After the shear wave has passed through the nearest sampling window Al, then the adjacent windows prove that the window can be terminated and that the sampling time can be devoted to the remaining sampling windows through which the shear wave is still is propagating. Sampling continues until the shear wave has propagated from a one cm sampling region, at which time the shear wave has generally attenuated below a detectable level. Shear waves on average have a relaxation time of 10 ms.
    [026] It is necessary that the sampling periods of the tracking A-line positions are related to a common time base when the tracking pulses are time-interleaved where the results can be used to make a continuous time measurement, and thus the velocity, through the sampling region of one cm. For example, since the sampling pulses for the A2 sampling window do not occur within 50 microseconds following the corresponding sampling pulses for the Al window, a time offset of 50 microseconds goes out between the sampling periods of the two adjacent windows. This time difference should be taken into account when comparing the maximum displacement periods in the respective windows, and should be considered cumulatively across a total sampling window of one centimeter. Referencing the sampling periods of each sampling vector in a common time reference can solve the problem of compensated sampling periods.
    [027] It will be observed that the shear wave emits out radially from the vector where the energy pulse displaced the tissue. This means that the shear wave can be traced on either side of the energy pulse vector in a 2D image plane through tissue. In the example in Figure 5 the shear wave is shown being tracked to the right of the energy pulse vector 44, although it could also be tracked as it propagates to the left of the vector. The shear wave could also be tracked on both sides of the energy pulse vector at the same time by time-interleaving the tracking pulses on both sides of the energy pulse vector, but without being able to prove a total region on both sides pulse energy without sacrificing sample line density, sample line frequency (PRF), shear wave tracking distance, or a combination of these.
    [028] Since the diagnostic region of interest (ROI) is generally greater than one centimeter in width, the procedure of figure 5 is repeated with energy pulses transmitted at different lateral locations by the image field. An image field is then interrogated into one cm wide regions, and the results of the regions are shifted adjacent to each other to present an image of the total ROI. In a preferred implementation, a Philips Healthcare L12-5 probe is used, which has an aperture of 5 cm. A four cm wide image field is interrogated into adjacent four cm or one cm overlapping regions, which are then displayed side-by-side or completely or partially superimposed on the screen.
    [029] Figure 6 illustrates the sequence of displacement values for two laterally adjacent points in two adjacent A-lines as A1-3 and A1-4 in figure 5. Curve 100 represents the displacement over time caused by the passage of the wave of shear through a point on A-line A1-3, and curve 120, the displacement at an adjacent point on A-line A1-4. The 102-118 tissue displacement point values are calculated from the local cross-correlation of the r.f. (eg 10-30 samples per r.f. in depth) acquired around a sampling point depth in A1-3 over time to reproduce the local displacement values over time at the depth point. The 102-118 points of displacement values detected in successive periods (y-axis), when plotted as a function of time, are joined to form the first displacement curve 100. At a point on the second line-A Al-4 spaced apart to the right of the point on the first A-line, the 122-136 succession of displacement values produced by the local cross-correlation can be joined to form a second displacement curve 120. Since the shear wave is traveling from left to right in this For example, the second curve 120 to the rightmost A-line is shifted to the right (in time) of the first offset curve 100. An accurate time reference of the wavefront passing from one point to the next is measured by the maximum point or detected inflection of each displacement curve, indicated at 200 and 220 in this example. Various techniques can be used to find the peak of the curve. In a preferred embodiment, the displacement values of each curve are processed by fitting the curves to the values to form the complete displacement curves 100, 120 and the peaks of the curve. Another technique is to interpolate additional points between detected points to find the peak. Yet another technique is to determine the slopes of the curve on either side of the peak and determine the peak of the intersection of the slope lines. Yet another approach is cross-correlation of curve data. When shear wave displacement peaks at successive positions of the A-line are found by the waveform peak detector 28, their occurrence periods with respect to the detection of points on the curves are observed. The differences in these periods, taking into account the sampling time compensation, and the spacing between the A-lines (eg 0.5 mm) can be used by the wavefront velocity detector 30 to determine the wave velocity of shear as it travels between the two locations of the A-line. After the entire ROI has been interrogated in this way and the complete displacement curves and periods of maximum occurrence determined for each sample point in each A-line vector, the velocity of the shear wave path can be calculated from point to point by the entire region of interest. These two-dimensional velocity matrix values are color-coded or otherwise encoded in a screen variation for the velocity display map. The velocity display map is shown on screen 36, preferably superimposed and in spatial alignment with a B-mode image of the region of interest.
    [030] In the example above, the shear waves were detected and measured as they travel horizontally through the region of interest. However, many lesions are rounded or otherwise appear as two-dimensional objects in a 2D image. To precisely locate the edge of a circular lesion, it would conveniently be desirable to direct the shear waves into the lesion from a full 360° radius of direction around the lesion.
    [031] Directing shear waves along a set of directional passages and compounding the results with measurements taken from shear waves crossing other directional passages through the ROI can produce more accurate and reliable images of lesions and their margins. One way to do this is to apply vibration to the energy pulse vectors and sequences across the imaging field as illustrated by figures 7a-7c. These figures show a series of energy pulses with respect to a fixed 5 cm wide region of interest. Energy pulses are differently sequenced, spatially interleaved, and spatially vibrated to interrogate the region of interest with differently directed shear waves. In addition, the temporal and spatial gap reduces energy creation at any particular point in the imaging field that would exceed the desired thermal limits on the body. Scanning begins in Figure 7a with a vector of the Pi energy pulse at the center of the image field (2.5 cm. dot) of four energy pulses, 1-4, which are sequenced from a shallow depth to a deeper one in the image field. As explained above, these four energy pulses will produce a composite shear wavefront that is slanted to propagate in a slightly downward direction as indicated by arrows 301 and 302. The next energy pulse vector, P2, is transmitted to left of imaging field (0.5 cm dot), well removed to the left of the previous energy pulse. Since the successive energy pulse vectors are not adjacent to each other but are largely spatially compensated, the thermal effects of the two energy pulse vectors are separate so they cannot accumulate at any point. Similarly, the third vector of the P3 energy pulse is located to the right away from the imaging field (4.5 cm dot), the next vector of the P4 energy pulse is located to the left of the center of the field (1st dot). .5 cm), and so on. Nine energy pulse vectors are transmitted in this spatially separated form in figure 7a.
    [032] It is also seen that the sequence of the vector pulses changes. Vectors P1-P5 use a sequence of energy pulses starting at the shallowest depth and ending at the deepest (1-4), while vectors Pδ~P9 use the sequence from bottom to shallow (4-1). This results in an alternation in the sequence of the energy pulse from vector to vector by the image field.
    [033] The pulse sequence of figure 7b follows from figure 7a and starts with the vector of the energy pulse Pi to the left of the image field (0.5 cm. dot). This energy pulse vector is well offset from the preceding vector, which was P9, to the right of the center of the imaging field in Figure 7a. The vector Pi in Figure 7b is also seen to have the reserve pulse sequence of its spatially corresponding vector P2 in Figure 7a. The sequence for vector P2 in Figure 7b is from shallower depth, while the sequence for vector P2 in Figure 7a was from shallow to deep. This causes the shear waves of vector Pi in figure 7b to travel slightly upwards (see arrows 304 and 306), while the shear waves of vector P2 in figure 7a travel slightly downwards (see arrows 301 and 302) . In addition, vector Pi in figure 7b is shifted slightly to the left of the 0.5 cm point of the image field, while vector P2 in figure 7a (and all other vectors in figure 7a) is aligned with the 0 point .5 cm from the field. This change is made through the image field, which can be seen by comparing the alignment of the five vectors of the 310 band, which are aligned with the centimeter markers, with the five vectors of the 312 band, which are all seen to be alternated on the left of centimeter markers. The combination of these differences further reduces the energy creation at a particular point in the image, and is also seen to drive the shear waves along the different propagation paths from figure 7a to figure 7b. As mentioned before, the successively transmitted energy pulse vectors are widely separated, and the sequence of the energy pulses alternates from vector to vector across the image field. If desired, the focal points of the energy pulses can also be varied between vectors.
    [034] This sequence of transmission variation is seen to continue in Figure 7c. In this sequence of nine energy pulse vectors is seen such that the energy pulse vectors are shifted to the right of the centimeter markers, which can be seen by comparing the vectors in the 314 range with these 310 and 312 ranges. In such combinations of pulse sequence and spatial change and separation, heat effects can be reduced and measurements of the velocity of differently directed shear waves can be composited by averaging or similar to produce the most reliable elasticity quantification.
    权利要求:
    Claims (15)
    [0001]
    1. ULTRASOUND DIAGNOSTIC IMAGING SYSTEM FOR SHEAR WAVE ANALYSIS, characterized by comprising: an ultrasonic array probe (10) that transmits an energy pulse along a predetermined vector to generate a shear wave, transmits pulses of tracking along the tracking lines adjacent to the energy pulse vector, and receiving echo signals from the points along the tracking lines; a line A memory (24) for storing the tracking line echo data; a tracking line data receptive motion detector for detecting motion due to a shear wave passing through the tracking line locations; a velocity detector (30) that measures the velocity of the shear waves passing through the tracking line locations; and a screen (36) for displaying the results of the shear wave measurement. a multi-line beamformer (20, 18) coupled to the array probe that controls the array probe to transmit and focused tracking pulses (80) that insonify a plurality of adjacent tracking lines and simultaneously receive coherent echoes along the lines of tracking adjacent in a time-interleaved sequence;
    [0002]
    2. ULTRASONIC DIAGNOSTIC IMAGE FORMATION SYSTEM, according to claim 1, characterized in that the motion detector detects tissue displacement caused by shear waves.
    [0003]
    3. ULTRASONIC DIAGNOSTIC IMAGE SYSTEM according to claim 2, characterized in that the motion detector additionally comprises a tracking line echo cross data correlator (26) and a displacement peak detector (28).
    [0004]
    4. ULTRASONIC DIAGNOSTIC IMAGING SYSTEM, according to claim 3, characterized in that the velocity detector is adapted to determine the velocity by comparing the periods of occurrence of the two displacement peaks.
    [0005]
    5. ULTRASONIC DIAGNOSTIC IMAGE FORMATION SYSTEM, according to claim 1, characterized in that the screen displays a two-dimensional image of the values of the shear wave velocity.
    [0006]
    6. ULTRASONIC DIAGNOSTIC IMAGING SYSTEM, according to claim 5, characterized in that shear wave velocity values are color-coded in an anatomical image.
    [0007]
    7. ULTRASONIC DIAGNOSTIC IMAGING SYSTEM according to claim 1, characterized in that the multiline beamformer is adapted to detect echo signals along a plurality of tracking line locations in response to a single transmission event. tracking pulse.
    [0008]
    8. ULTRASONIC DIAGNOSTIC IMAGING SYSTEM according to claim 1, characterized in that the motion detector is adapted to detect a period of maximum tissue displacement at a plurality of sample points along each of the locations of the line of tracking.
    [0009]
    9. ULTRASONIC DIAGNOSTIC IMAGING SYSTEM according to claim 8, characterized in that the motion detector is further adapted to detect displacement values by local cross-correlation of echo data acquired from a tracking line location.
    [0010]
    10. ULTRASONIC DIAGNOSTIC IMAGING SYSTEM, according to claim 9, characterized in that the motion detector is further adapted to detect a period of maximum tissue displacement by fitting the curve into a plurality of displacement values.
    [0011]
    11. ULTRASONIC DIAGNOSTIC IMAGING SYSTEM, according to claim 9, characterized in that the motion detector is further adapted to detect a maximum tissue displacement period by interpolating a plurality of displacement values.
    [0012]
    12. METHOD FOR OPERATING AN ULTRASOUND DIAGNOSTIC IMAGING SYSTEM FOR MEASURING SHEAR WAVES, comprising: transmitting an energy pulse along an energy pulse vector; transmitting a plurality of tracking pulses; receiving echo signals in response to transmitting tracking signals; processing the echo signals to determine shear wave velocity values at a plurality of two- or three-dimensional points in a region of interest; and displaying a two- or three-dimensional image of shear wave velocity values; characterized in that tracking pulses are focused and transmitted along a plurality of tracking lines adjacent to the energy pulse vector, where the tracking pulses are transmitted along each tracking line at various periods in a time-interleaved fashion ; and that receiving the echo signals are focused from a plurality of tracking lines and being simultaneously receiving in response to the transmission of a tracking pulse.
    [0013]
    13. The method of claim 12, characterized in that receiving the focused echo signals further comprises receiving focused echo signals along a plurality of tracking lines in response to a single tracking pulse transmission event.
    [0014]
    14. The method according to claim 12, characterized in that the processing further comprises processing the echo signals to determine tissue motion resulting from the shear waves.
    [0015]
    15. METHOD according to claim 14, characterized in that the processing further comprises processing the echo signals to determine the tissue displacement at the points in the region of interest.
    类似技术:
    公开号 | 公开日 | 专利标题
    BR112012012230B1|2021-04-20|ultrasonic diagnostic imaging system for shear wave analysis and method for operating an ultrasonic diagnostic imaging system for measuring shear waves
    US20200060655A1|2020-02-27|Adjusting measurements of the effects of acoustic radiation force for background motion effects
    EP2816958B1|2020-03-25|Determining material stiffness using multiple aperture ultrasound
    Kanai et al.1997|Noninvasive evaluation of local myocardial thickening and its color-coded imaging
    US9237878B2|2016-01-19|Generation and assessment of shear waves in elasticity imaging
    EP2453800B1|2018-11-21|Spatially-fine shear wave dispersion ultrasound vibrometry sampling
    EP2654552B1|2021-06-23|Shear wave velocity estimation using center of mass
    US10448924B2|2019-10-22|Ultrasonic acoustic radiation force excitation for ultrasonic material property measurement and imaging
    CN106419961B|2020-09-15|Adaptive motion estimation in acoustic radiation force imaging
    US20210007714A1|2021-01-14|Ultrasound system for shear wave imaging in three dimensions
    KR102210372B1|2021-02-01|Tissue viscoelastic estimation from shear velocity in ultrasound medical imaging
    US20190231320A1|2019-08-01|Ultrasonic shear wave imaging with background motion compensation
    KR102206496B1|2021-01-22|Shear wave imaging based on ultrasound with increased pulse repetition interval
    WO2019192970A1|2019-10-10|Ultrasonic shear wave imaging with improved accuracy and reliability
    Trahey et al.2007|Radiation force imaging: challenges and opportunities
    同族专利:
    公开号 | 公开日
    US20190314002A1|2019-10-17|
    JP6148010B2|2017-06-14|
    US10368843B2|2019-08-06|
    JP6235625B2|2017-11-22|
    CN102667522B|2014-10-08|
    EP2504716B1|2014-07-30|
    WO2011064688A1|2011-06-03|
    RU2012126172A|2013-12-27|
    BR112012012230A2|2017-12-19|
    EP2504716A1|2012-10-03|
    US20130131511A1|2013-05-23|
    JP2016116875A|2016-06-30|
    CN102667522A|2012-09-12|
    RU2552894C2|2015-06-10|
    JP2013512026A|2013-04-11|
    引用文献:
    公开号 | 申请日 | 公开日 | 申请人 | 专利标题
    SU1378812A1|1984-07-12|1988-03-07|Московский медицинский стоматологический институт им.Н.А.Семашко|Method of diagnosis of ovulation|
    US4644795A|1985-07-29|1987-02-24|Advanced Technology Laboratories, Inc.|High resolution multiline ultrasonic beamformer|
    US5318033A|1992-04-17|1994-06-07|Hewlett-Packard Company|Method and apparatus for increasing the frame rate and resolution of a phased array imaging system|
    US5345426A|1993-05-12|1994-09-06|Hewlett-Packard Company|Delay interpolator for digital phased array ultrasound beamformers|
    US5469851A|1994-08-09|1995-11-28|Hewlett-Packard Company|Time multiplexed digital ultrasound beamformer|
    JPH08191834A|1995-01-17|1996-07-30|Hitachi Medical Corp|Ultrasonic measuring device|
    US5606971A|1995-11-13|1997-03-04|Artann Corporation, A Nj Corp.|Method and device for shear wave elasticity imaging|
    US5810731A|1995-11-13|1998-09-22|Artann Laboratories|Method and apparatus for elasticity imaging using remotely induced shear wave|
    AU1983397A|1996-02-29|1997-09-16|Acuson Corporation|Multiple ultrasound image registration system, method and transducer|
    US7374538B2|2000-04-05|2008-05-20|Duke University|Methods, systems, and computer program products for ultrasound measurements using receive mode parallel processing|
    EP1278459A1|2000-04-26|2003-01-29|Koninklijke Philips Electronics N.V.|Ultrasonic method and system for shear wave parameter estimation|
    US6468216B1|2000-08-24|2002-10-22|Kininklijke Philips Electronics N.V.|Ultrasonic diagnostic imaging of the coronary arteries|
    US6558324B1|2000-11-22|2003-05-06|Siemens Medical Solutions, Inc., Usa|System and method for strain image display|
    US6695783B2|2000-12-22|2004-02-24|Koninklijke Philips Electronics N.V.|Multiline ultrasound beamformers|
    FR2844058B1|2002-09-02|2004-11-12|Centre Nat Rech Scient|IMAGING METHOD AND DEVICE USING SHEAR WAVES|
    JP4130604B2|2003-04-16|2008-08-06|アロカ株式会社|Ultrasonic diagnostic equipment|
    FR2905180B1|2006-08-22|2008-12-05|Super Sonic Imagine|ULTRASONIC IMAGING PROBE FOR IMAGING TRANSIENT MODIFICATION OF A MEDIUM|
    US8118744B2|2007-02-09|2012-02-21|Duke University|Methods, systems and computer program products for ultrasound shear wave velocity estimation and shear modulus reconstruction|
    FR2913875B1|2007-03-21|2009-08-07|Echosens Sa|DEVICE FOR MEASURING VISCOELASTIC PROPERTIES OF BIOLOGICAL TISSUES AND METHOD USING THE DEVICE|
    US8545407B2|2007-05-16|2013-10-01|Super Sonic Imagine|Method and device for measuring a mean value of visco-elasticity of a region of interest|
    FR2917831B1|2007-06-25|2009-10-30|Super Sonic Imagine Sa|METHOD OF RHEOLOGICAL CHARACTERIZATION OF A VISCOELASTIC MEDIUM|
    US8197408B2|2008-02-27|2012-06-12|Siemens Medical Solutions Usa, Inc.|Sparse tissue property measurements in medical ultrasound imaging|
    US9043156B2|2008-10-28|2015-05-26|The University Of North Carolina At Chapel Hill|Methods, systems, and computer readable media for monitored application of mechanical force to samples using acoustic energy and mechanical parameter value extraction using mechanical response models|WO2010120907A2|2009-04-14|2010-10-21|Maui Imaging, Inc.|Multiple aperture ultrasound array alignment fixture|
    US9282945B2|2009-04-14|2016-03-15|Maui Imaging, Inc.|Calibration of ultrasound probes|
    KR102322776B1|2010-02-18|2021-11-04|마우이 이미징, 인코포레이티드|Method of constructing an ultrasound image and multi-aperture ultrasound imaging system therefor|
    EP2589341A1|2010-06-30|2013-05-08|FUJIFILM Corporation|Ultrasound diagnostic device and ultrasound diagnostic method|
    JP5808325B2|2010-06-30|2015-11-10|富士フイルム株式会社|Ultrasonic diagnostic apparatus and method of operating ultrasonic diagnostic apparatus|
    US9788813B2|2010-10-13|2017-10-17|Maui Imaging, Inc.|Multiple aperture probe internal apparatus and cable assemblies|
    KR101906838B1|2010-10-13|2018-10-11|마우이 이미징, 인코포레이티드|Concave ultrasound transducers and 3d arrays|
    JP5886318B2|2010-12-22|2016-03-16|コーニンクレッカ フィリップス エヌ ヴェＫｏｎｉｎｋｌｉｊｋｅ Ｐｈｉｌｉｐｓ Ｎ．Ｖ．|Estimation of shear wave velocity using center of mass|
    WO2013015001A1|2011-07-28|2013-01-31|株式会社 日立メディコ|Ultrasound diagnostic device and shear elasticity measurement method|
    US10338203B2|2011-09-09|2019-07-02|Siemens Medical Solutions Usa, Inc.|Classification preprocessing in medical ultrasound shear wave imaging|
    CN103917167B|2011-11-17|2016-01-06|日立阿洛卡医疗株式会社|Diagnostic ultrasound equipment and method of generating ultrasonic image|
    TW201336478A|2011-12-01|2013-09-16|Maui Imaging Inc|Motion detection using ping-based and multiple aperture doppler ultrasound|
    EP2797515A4|2011-12-29|2015-07-22|Maui Imaging Inc|M-mode ultrasound imaging of arbitrary paths|
    CN104135937B|2012-02-21|2017-03-29|毛伊图像公司|Material stiffness is determined using porous ultrasound|
    CN103300890B|2012-03-16|2016-06-08|通用电气公司|For measuring the system and method for tissue mechanical properties|
    KR102103137B1|2012-03-26|2020-04-22|마우이 이미징, 인코포레이티드|Systems and methods for improving ultrasound image quality by applying weighting factors|
    US9211111B2|2012-04-05|2015-12-15|Hitachi Aloka Medical, Ltd.|Determination of shear wave characteristics|
    CN104470443B|2012-07-18|2017-10-31|皇家飞利浦有限公司|Method and system for handling ultrasound imaging data|
    RU2636262C2|2012-07-18|2017-11-21|Конинклейке Филипс Н.В.|Method and system for processing ultrasound imaging data|
    JP6270843B2|2012-08-10|2018-01-31|マウイ イマギング，インコーポレーテッド|Calibration of multiple aperture ultrasonic probes|
    EP3893022A1|2012-08-21|2021-10-13|Maui Imaging, Inc.|Ultrasound imaging system memory architecture|
    JP5733835B2|2012-08-27|2015-06-10|ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー|Measuring device and ultrasonic diagnostic device|
    US10624609B2|2012-10-07|2020-04-21|Mayo Foundation For Medical Education And Research|System and method for shear wave elastography by transmitting ultrasound with subgroups of ultrasound transducer elements|
    JP6257892B2|2012-12-10|2018-01-10|東芝メディカルシステムズ株式会社|Ultrasonic diagnostic apparatus and control program|
    RU2659627C2|2013-02-19|2018-07-03|Экоусенс|Multipulse elastography method|
    CN104302233B|2013-03-05|2016-10-12|株式会社日立制作所|Diagnostic ultrasound equipment and receiving/transmission method|
    US9510806B2|2013-03-13|2016-12-06|Maui Imaging, Inc.|Alignment of ultrasound transducer arrays and multiple aperture probe assembly|
    JP6161028B2|2013-05-09|2017-07-12|国立大学法人群馬大学|Image apparatus and image forming method|
    WO2014201020A1|2013-06-10|2014-12-18|Mayo Foundation For Medical Education And Research|System and method for acoustic radiation force creep-recovery and shear wave propagation for elasticity imaging|
    JP6305699B2|2013-07-01|2018-04-04|キヤノンメディカルシステムズ株式会社|Ultrasonic diagnostic apparatus and ultrasonic imaging program|
    JP6288996B2|2013-09-11|2018-03-07|キヤノンメディカルシステムズ株式会社|Ultrasonic diagnostic apparatus and ultrasonic imaging program|
    US9883848B2|2013-09-13|2018-02-06|Maui Imaging, Inc.|Ultrasound imaging using apparent point-source transmit transducer|
    WO2015040710A1|2013-09-18|2015-03-26|株式会社 東芝|Diagnostic ultrasound apparatus, medical image-processing device and medical image-processing method|
    CN103462643B|2013-09-29|2015-02-11|深圳市开立科技有限公司|Shear wave speed measurement method, device and system|
    US10278671B2|2013-09-30|2019-05-07|Siemens Medical Solutions Usa, Inc.|Shear wave detection in medical ultrasound imaging|
    JP5869548B2|2013-10-29|2016-02-24|ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー|Ultrasonic diagnostic apparatus and control program therefor|
    KR101649272B1|2014-01-06|2016-08-18|삼성전자주식회사|Ultrasonic diagnosis apparatus, method for photographing ultrasonic image, probe, and computer-readable recording medium|
    WO2015102474A1|2014-01-06|2015-07-09|Samsung Electronics Co., Ltd.|Ultrasound diagnostic apparatus, ultrasound image capturing method, and computer-readable recording medium|
    JP6172752B2|2014-01-21|2017-08-02|ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー|Ultrasonic diagnostic apparatus and program|
    FR3017041B1|2014-01-31|2016-03-04|Centre Nat Rech Scient|ULTRASONIC PROCESS AND DEVICE FOR CHARACTERIZING ANISOTROPIC SOFT MEDIA, AND ULTRASONIC PROBE ASSEMBLY FOR SUCH CHARACTERIZATION DEVICE|
    JP6243249B2|2014-02-19|2017-12-06|ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー|Ultrasonic diagnostic apparatus and program|
    JP6333608B2|2014-04-16|2018-05-30|キヤノンメディカルシステムズ株式会社|Ultrasonic diagnostic apparatus and control program|
    RU2689174C2|2014-05-16|2019-05-24|Конинклейке Филипс Н.В.|Autocorrelation-induced cross correlation in shear wave ultrasonic elastography|
    EP3150127B1|2014-05-28|2021-10-06|Shenzhen Mindray Bio-Medical Electronics Co., Ltd.|Ultrasonic imaging method and system|
    JP6722656B2|2014-08-18|2020-07-15|マウイ イマギング，インコーポレーテッド|Network-based ultrasound imaging system|
    CN106572837B|2014-08-28|2019-10-08|深圳迈瑞生物医疗电子股份有限公司|Shearing wave imaging method and system|
    JP6352734B2|2014-08-29|2018-07-04|国立大学法人京都大学|Ultrasonic diagnostic equipment|
    CN110368031A|2014-09-03|2019-10-25|深圳迈瑞生物医疗电子股份有限公司|Elasticity measurement detection method and system|
    JP6006769B2|2014-10-16|2016-10-12|株式会社日立製作所|Ultrasonic diagnostic equipment|
    JP6224572B2|2014-11-26|2017-11-01|ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー|Ultrasonic diagnostic apparatus and program|
    EP3231369A1|2014-12-08|2017-10-18|Hitachi, Ltd.|Ultrasound diagnostic device and elasticity evaluation method|
    CA2971676A1|2014-12-24|2016-06-30|Super Sonic Imagine|Shear wave elastography method and apparatus for imaging an anisotropic medium|
    CN107427278A|2015-01-02|2017-12-01|百胜集团|Pass through the elastic method of ultrasound quantification material|
    JP6361528B2|2015-03-03|2018-07-25|コニカミノルタ株式会社|Ultrasonic treatment equipment|
    JP5936734B1|2015-03-11|2016-06-22|日立アロカメディカル株式会社|Ultrasonic diagnostic equipment|
    JP6390516B2|2015-05-27|2018-09-19|コニカミノルタ株式会社|Ultrasonic diagnostic apparatus and control method of ultrasonic diagnostic apparatus|
    CN107690313B|2015-06-11|2021-06-15|皇家飞利浦有限公司|Ultrasound transducer array probe for shear wave imaging|
    JP6932084B2|2015-06-29|2021-09-08|コーニンクレッカ フィリップス エヌ ヴェＫｏｎｉｎｋｌｉｊｋｅ Ｐｈｉｌｉｐｓ Ｎ．Ｖ．|Ultrasonic system using asymmetric transmission signal|
    RU2641067C1|2015-08-03|2018-01-15|Конинклейке Филипс Н.В.|Ultrasonic system and method for measurement using shear wave|
    US11147531B2|2015-08-12|2021-10-19|Sonetics Ultrasound, Inc.|Method and system for measuring blood pressure using ultrasound by emitting push pulse to a blood vessel|
    CN105092595B|2015-08-31|2018-03-02|哈尔滨工业大学（威海）|Photoacoustic elastic imaging method and device applied to rail examination|
    JP6224674B2|2015-10-27|2017-11-01|ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー|Ultrasonic diagnostic apparatus and control program therefor|
    JP6208781B2|2016-01-08|2017-10-04|ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー|Ultrasonic diagnostic equipment|
    CN108778530B|2016-01-27|2021-07-27|毛伊图像公司|Ultrasound imaging with sparse array probe|
    US11006928B2|2016-02-10|2021-05-18|Siemens Medical Solutions Usa, Inc.|Sound speed imaging using shear waves|
    RU2740257C2|2016-03-24|2021-01-12|Конинклейке Филипс Н.В.|Ultrasound system and method of detecting lung slip|
    CN109069131A|2016-04-18|2018-12-21|皇家飞利浦有限公司|Ultrasonic system and method for breast tissue imaging|
    WO2017211757A1|2016-06-10|2017-12-14|Koninklijke Philips N.V.|Using reflected shear waves for monitoring lesion growth in thermal ablations|
    JP6601320B2|2016-06-16|2019-11-06|コニカミノルタ株式会社|Ultrasonic diagnostic apparatus and control method of ultrasonic diagnostic apparatus|
    CN109475343A|2016-08-01|2019-03-15|深圳迈瑞生物医疗电子股份有限公司|Ultrasonic elasticity measures display methods and system|
    WO2018051265A1|2016-09-15|2018-03-22|Koninklijke Philips N.V.|Ultrasonic elastographic pre-load measurement and display|
    WO2018060820A1|2016-09-29|2018-04-05|Koninklijke Philips N.V.|Ultrasonic shear wave imaging with background motion compensation|
    US10646202B2|2017-01-23|2020-05-12|Siemens Medical Solutions Usa, Inc.|Sheer speed imaging using coherence|
    CN107550458B|2017-07-27|2020-05-12|天津大学|Biological tissue multi-characteristic imaging method based on acoustoelectric effect and acoustic radiation force|
    UA120644C2|2017-10-27|2020-01-10|Євген Олександрович Баранник|METHOD AND DEVICE FOR ULTRASOUND MEASUREMENT AND VISUALIZATION OF EFFICIENCY OF BIOLOGICAL TISSUES IN REAL TIME|
    CN108186045B|2017-12-28|2021-01-19|深圳开立生物医疗科技股份有限公司|Method and device for exciting shear wave|
    US20210361262A1|2018-02-09|2021-11-25|Koninklijke Philips N.V.|Multi-parametric tissue stiffness quanatification|
    WO2019192970A1|2018-04-02|2019-10-10|Koninklijke Philips N.V.|Ultrasonic shear wave imaging with improved accuracy and reliability|
    CN110494082A|2018-04-11|2019-11-22|深圳迈瑞生物医疗电子股份有限公司|Ultrasonic elastograph imaging method and system|
    JP2019187777A|2018-04-25|2019-10-31|コニカミノルタ株式会社|Ultrasound diagnostic apparatus and ultrasound signal processing method|
    WO2019210479A1|2018-05-03|2019-11-07|深圳迈瑞生物医疗电子股份有限公司|Shear wave elasticity imaging method and ultrasonic imaging device|
    EP3823537A1|2018-07-18|2021-05-26|Koninklijke Philips N.V.|Intelligent guided wave elastography|
    CN110573084A|2018-08-29|2019-12-13|深圳迈瑞生物医疗电子股份有限公司|ultrasonic elasticity detection equipment and shear wave elasticity imaging method and device|
    CN109394268B|2018-12-07|2021-05-11|刘志红|Polyp harm degree mapping platform|
    法律状态:
    2018-02-06| B25D| Requested change of name of applicant approved|Owner name: KONINKLIJKE PHILIPS N.V. (NL) |
    2018-02-20| B25G| Requested change of headquarter approved|Owner name: KONINKLIJKE PHILIPS N.V. (NL) |
    2019-01-08| B06F| Objections, documents and/or translations needed after an examination request according [chapter 6.6 patent gazette]|
    2019-12-17| B15K| Others concerning applications: alteration of classification|Free format text: AS CLASSIFICACOES ANTERIORES ERAM: G01S 7/52 , A61B 8/08 , G01N 29/34 , G01N 29/07 Ipc: G01S 7/52 (1968.09), A61B 8/08 (1985.01), G01S 15/ |
    2019-12-17| B06U| Preliminary requirement: requests with searches performed by other patent offices: procedure suspended [chapter 6.21 patent gazette]|
    2021-02-17| B09A| Decision: intention to grant [chapter 9.1 patent gazette]|
    2021-04-20| B16A| Patent or certificate of addition of invention granted|Free format text: PRAZO DE VALIDADE: 20 (VINTE) ANOS CONTADOS A PARTIR DE 15/11/2010, OBSERVADAS AS CONDICOES LEGAIS. PATENTE CONCEDIDA CONFORME MEDIDA CAUTELAR DE 07/04/2021 - ADI 5.529/DF |
    优先权:
    申请号 | 申请日 | 专利标题
    US26427709P| true| 2009-11-25|2009-11-25|
    US61/264,277|2009-11-25|
    PCT/IB2010/055179|WO2011064688A1|2009-11-25|2010-11-15|Ultrasonic shear wave imaging with focused scanline beamforming|
    [返回顶部]