CN113261991A - Elasticity imaging method, system and computer readable storage medium - Google Patents
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Abstract
The embodiment of the application discloses an elastic imaging method, an elastic imaging system and a computer readable storage medium. The elastography method comprises the following steps: acquiring a motion parameter image of a tested tissue; determining a main propagation path of a shear wave propagating in the tissue under test in the motion parameter image; and displaying a motion parameter image containing the main propagation path. According to the embodiment of the application, the motion parameter image comprising the main propagation path is displayed after the main propagation path of the shear wave in the motion parameter image is obtained, so that the defect that medical staff cannot accurately explain the displayed meaning of the motion parameter image due to the influence of interference information such as various residual waves, reflected waves and the like caused by the vibration of the probe in the motion parameter image can be reduced, and the understandability of the elasticity test result is improved.
Description
Technical Field
The present application relates to the field of medical technology, and in particular, to an elastography method, system, and computer-readable storage medium.
Background
Instantaneous elasticity imaging utilizes probe vibration to generate shear waves to be transmitted into a tested tissue, and ultrasonic waves are transmitted to detect internal displacement of the tissue, so that elasticity parameters of the tested tissue are calculated and displayed. In transient elasticity techniques, in addition to providing elasticity measurements, a motion parameter image of tissue displacement or strain is typically provided. However, the vibration of the probe may cause interference information such as various residual waves and reflected waves, so that clinical staff cannot accurately interpret the displayed meaning of the motion parameter image.
Disclosure of Invention
The embodiment of the application provides an elasticity imaging method, an elasticity imaging system and a computer readable storage medium, which can improve the understandability of elasticity test results.
In one embodiment, an elastography method is provided, which is applied to an elastography system, the elastography system includes a probe, a transmitting circuit connected to the probe, a receiving circuit connected to the probe, a beam combiner connected to the receiving circuit, a processor connected to the beam combiner, and a display screen for displaying image information transmitted by the processor, the elastography method includes:
controlling the probe to transmit a first ultrasonic wave to the tested tissue when receiving a first transmission time sequence of the transmission circuit so as to track a shear wave propagating in the tested tissue;
the probe is controlled to receive a first ultrasonic echo returned by the tested tissue, and the first ultrasonic echo is converted into an electric signal and then transmitted to the receiving circuit;
controlling the beam synthesizer to perform beam synthesis on the electric signal transmitted by the receiving circuit to obtain first ultrasonic echo data;
controlling the processor to obtain a motion parameter image of the tissue under test based on the first ultrasound echo data;
controlling the processor to determine a main propagation path of the shear wave in the motion parameter image, obtaining a main propagation path map, wherein the main propagation path map characterizes the main propagation path of the shear wave in the tissue under test;
controlling the processor to determine elasticity information of the tested tissue according to the first ultrasonic echo data or the motion parameter image or the main propagation path diagram;
controlling the processor to display the main propagation path map and the elastic information of the tested tissue in the display screen.
In one embodiment, there is provided an elastography method, the method comprising:
transmitting a first ultrasonic wave to a tissue under test to track a shear wave propagating within the tissue under test;
receiving a first ultrasonic echo returned by the tested tissue to obtain first ultrasonic echo data;
obtaining motion parameters of the tested tissue at different moments and different depths, which are caused by the propagation of the shear wave in the tested tissue, according to the first ultrasonic echo data;
determining a main propagation path of the shear wave according to the motion parameters, and obtaining a main propagation path diagram, wherein the main propagation path diagram characterizes the main propagation path of the shear wave in the tested tissue;
determining elasticity information of the tested tissue according to the first ultrasonic echo data or the motion parameters or the main propagation path;
displaying the main propagation path map and the elastic information of the tested tissue.
In one embodiment, there is provided an elastography method, the method comprising:
transmitting a first ultrasonic wave to a tissue under test to track a shear wave propagating within the tissue under test;
receiving a first ultrasonic echo returned by the tested tissue to obtain first ultrasonic echo data;
obtaining motion parameters of the tested tissue at different moments and different depths, which are caused by the propagation of the shear wave in the tested tissue, according to the first ultrasonic echo data;
determining a main propagation path of the shear wave according to the motion parameters, and obtaining a main propagation path diagram, wherein the main propagation path diagram characterizes the main propagation path of the shear wave in the tested tissue;
and displaying the main propagation path diagram.
In one embodiment, there is provided an elastography method, comprising:
acquiring a motion parameter image of a tested tissue;
determining a main propagation path of a shear wave propagating in the tissue under test from the motion parameter image;
and displaying the main propagation path.
In one embodiment, there is provided an elastography system, comprising:
the probe is used for transmitting a first ultrasonic wave to a tested tissue so as to track a shear wave propagating in the tested tissue, and is also used for receiving a first ultrasonic echo returned by the tested tissue to obtain first ultrasonic echo data;
a processor connected to the probe, the processor configured to obtain motion parameters of the tissue under test at different times and different depths caused by propagation of the shear wave in the tissue under test based on the first ultrasonic echo data, determine a main propagation path of the shear wave according to the motion parameters, obtain a main propagation path diagram, and determine elasticity information of the tissue under test according to the first ultrasonic echo data or the motion parameters or the main propagation path diagram, wherein the main propagation path diagram characterizes the main propagation path of the shear wave in the tissue under test;
a display screen coupled to the processor, the processor configured to display the primary propagation path map and the elastic information of the tissue under test within the display screen.
In one embodiment, a computer-readable storage medium for storing a computer program for electronic data exchange is provided, wherein the computer program causes a computer to perform some or all of the steps described in any of the methods of the preceding embodiments.
The elastography method, the elastography system and the computer-readable storage medium of the embodiment of the application acquire the main propagation path of the shear wave according to the motion parameter or the motion parameter image, and display the main propagation path, so that the defect that medical staff cannot accurately explain the displayed meaning of the motion parameter image due to the influence of interference information such as various residual waves, reflected waves and the like caused by the vibration of a probe in the motion parameter image can be reduced, and the improvement of the intelligibility of the elasticity test result is facilitated.
Drawings
In order to more clearly illustrate the embodiments of the present application or the technical solutions in the prior art, the drawings used in the description of the embodiments or the prior art will be briefly described below, it is obvious that the drawings in the following description are only some embodiments of the present application, and for those skilled in the art, other drawings can be obtained according to the drawings without creative efforts.
Fig. 1 is a schematic hardware configuration diagram of an elastography system in an embodiment of the present application.
FIG. 2 is a flow chart illustrating steps of an elastography method in an embodiment of the present application.
Fig. 3 is a schematic diagram of a motion parameter image according to an embodiment of the present application.
Fig. 4 is a block diagram of a hardware structure of a probe according to an embodiment of the present application.
Fig. 5 is a schematic diagram of a plurality of strip-shaped regions in a motion parameter image according to an embodiment of the present application.
Fig. 6 is a schematic diagram of binarization of a main propagation path diagram in an embodiment of the present application.
Fig. 7 is a non-binary diagram of a main propagation path diagram in an embodiment of the present application.
FIG. 8 is a schematic diagram of a main propagation path in an embodiment of the present application.
FIG. 9 is a flowchart illustrating steps of an elastography method in an embodiment of the present application.
FIG. 10 is a block diagram schematic of an elastography system in an embodiment of the present application.
Fig. 11 is a schematic diagram of a motion parameter image according to an embodiment of the present application.
Fig. 12 is a schematic diagram of a motion parameter image in a further embodiment of the present application.
Fig. 13 is a schematic diagram of a motion parameter image in a further embodiment of the present application.
Detailed Description
In order to make the technical solutions of the present application better understood, the technical solutions in the embodiments of the present application will be clearly and completely described below with reference to the drawings in the embodiments of the present application, and it is obvious that the described embodiments are only a part of the embodiments of the present application, and not all of the embodiments. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present application.
The terms "first," "second," and the like in the description and claims of the present application and in the above-described drawings are used for distinguishing between different objects and not for describing a particular order. Furthermore, the terms "include" and "have," as well as any variations thereof, are intended to cover non-exclusive inclusions. For example, a process, method, system, article, or apparatus that comprises a list of steps or elements is not limited to only those steps or elements listed, but may alternatively include other steps or elements not listed, or inherent to such process, method, article, or apparatus.
Reference herein to "an embodiment" means that a particular feature, structure, or characteristic described in connection with the embodiment can be included in at least one embodiment of the application. The appearances of the phrase in various places in the specification are not necessarily all referring to the same embodiment, nor are separate or alternative embodiments mutually exclusive of other embodiments. It is explicitly and implicitly understood by one skilled in the art that the embodiments described herein can be combined with other embodiments.
Referring to fig. 1, a hardware structure diagram of an elastography system in an embodiment of the present application is shown. The elastography system 10 may include a probe 100, a transmitting circuit 102 connected to the probe 100, a receiving circuit 104 connected to the probe 100, a beam combiner 106, a processor 110, and a display 112, wherein the receiving circuit 104, the beam combiner 106, the processor 110, and the display 112 may be electrically connected in sequence. In this embodiment, the elastography system 10 may acquire a motion parameter or a motion parameter image of the tissue under test, and obtain a main propagation path of the shear wave in the tissue under test according to the motion parameter or the motion parameter image, and may display the main propagation path in the display screen 112. Because the main propagation path can be a single path which can accurately represent the propagation positions of the shear waves at different depths, and various interference information such as residual waves, reflected waves and the like can be eliminated when the main propagation path is obtained, medical personnel can visually diagnose through the motion parameter image comprising the main propagation path or the main propagation path diagram, and the improvement of the understandability of the elastic test result is facilitated. In one embodiment, the beam combiner 106 and the processor 110 may be implemented by dedicated circuitry or commercially available chips.
Referring to fig. 2, a flowchart of steps of an elastography method according to an embodiment of the present application is shown. The elastic imaging method comprises the following steps:
step 200, acquiring a motion parameter image of the tested tissue.
In this embodiment, the transmitting circuit 102 transmits a first transmitting timing sequence to the probe 100 to control the probe 100 to transmit a first ultrasonic wave to the tissue under test, wherein the first ultrasonic wave is used for tracking a shear wave propagating in the tissue under test. After the probe 100 transmits the first ultrasonic wave to the tissue under test, the probe 100 may receive, with a delay, the first ultrasonic echo reflected from the tissue under test and carrying the information of the test object. The probe 100 may convert this ultrasonic echo into an electrical signal. The receiving circuit 104 receives the electrical signals generated by the conversion of the probe 100, obtains first ultrasonic echo data, and sends the first ultrasonic echo data to the beam synthesizer 106. The beam synthesizer 106 performs beam synthesis processing such as focusing delay, weighting and channel summation on the ultrasound echo data, and then sends the ultrasound echo data after beam processing to the processor 110, and the processor 110 acquires a motion parameter or a motion parameter image of the measured tissue according to the first ultrasound echo data for displaying on the display screen 112.
Fig. 3 is a schematic view of a motion parameter image according to an embodiment of the present application. The motion parameter image includes a lateral temporal attribute and a longitudinal depth attribute. In this embodiment, after the shear wave spreads into the tissue to be tested, along with the propagation of shear wave, the inside vibration that can take place of tissue to be tested, the vibration makes the corresponding position of tissue to be tested take place the displacement. By transmitting a first ultrasonic wave into the tissue under test for a certain period of time and receiving its echo.
The processor 110 obtains motion parameters of the tissue under test at different times and at different depths caused by the propagation of the shear wave in the tissue under test based on the first ultrasonic echo data, wherein the motion parameters may include displacement, velocity or strain. For example, the processor 110 performs a comparative analysis (e.g., a cross-correlation algorithm) on the first ultrasonic echo data obtained at different times, may calculate displacements of the measured tissue at different times, and perform displacement calculations on the first echo data from the measured tissue at different depths, respectively, so as to finally obtain a displacement matrix corresponding to different depths at different times. In the displacement matrix, each data represents displacement information of tested tissues at a certain depth at a certain moment. When the gradient of the displacement matrix along the depth direction is solved, the strain matrix can be correspondingly obtained. In the strain matrix, each data represents strain information of the tested tissue at a certain depth at a certain time. In the above calculation process, it is also possible to add some filtering operation in the time direction or the depth direction in order to improve the signal-to-noise ratio.
The processor 110 may determine a motion parameter image 150 of the tissue under test based on the motion parameters of the shear waves at different times and at different depths.
Referring to fig. 4, a block diagram of a hardware structure of a probe according to an embodiment of the present invention is shown. The probe 100 includes an array-type acoustic head 130, a vibrator 132, and a transducer 134 positioned between the array-type acoustic head 130 and the vibrator 132. Prior to transmission of the first transmit timing sequence by transmit circuit 102 to probe 100, transmit circuit 102 may transmit an excitation timing sequence to probe 100 to control vibrator 132 of probe 100 to vibrate and generate shear waves in the tissue under test. Thereafter, the array-type acoustic head 130 of the probe 100 tracks the shear wave propagating in the tissue under test according to the first transmission timing. The array-type acoustic head 130 includes a predetermined number of array elements, and the array elements of the array-type acoustic head 130 are arranged in a linear arrangement or a sector arrangement. The sensor 132 is used to sense the force with which the probe 100 is pressed against the tissue being tested. In one embodiment, the probe 100 may not include the sensor 134.
In one embodiment, the medical staff may need to perform detection on a target position range of the tissue to be detected, and therefore, the medical staff needs to select an area of interest corresponding to the target position range in a basic image, wherein the basic image includes one or more of a B image and a C image. In acquiring the base image of the tissue under test, the transmission circuit 102 transmits a second transmission timing to the probe 100 to control the probe 100 to transmit a second ultrasonic wave to the tissue under test. After the probe 100 transmits the second ultrasonic wave to the tissue under test, the probe 100 may receive, with a delay, the second ultrasonic echo reflected from the tissue under test and carrying the information of the object under test. The probe 100 may convert this ultrasonic echo into an electrical signal. The receiving circuit 104 receives the electrical signals generated by the conversion of the probe 100, obtains second ultrasonic echo data, and sends the second ultrasonic echo data to the beam synthesizer 106. The beam synthesizer 106 performs beam synthesis processing such as focusing delay, weighting and channel summation on the ultrasound echo data, then sends the ultrasound echo data after beam processing to the processor 110, the processor 110 performs different processing on signals according to different imaging modes required by a user to obtain tissue image data in different modes, and then performs processing such as log compression, dynamic range adjustment, digital scan conversion and the like to form ultrasound tissue images in different modes for displaying on the display 112, wherein the ultrasound tissue images in different modes may include an M image, a B image, a C image and the like, or other types of two-dimensional ultrasound tissue images or three-dimensional ultrasound tissue images. In an embodiment, the first ultrasonic wave and the second ultrasonic wave transmitted by the probe 100 may be the same, that is, the processor 110 may obtain the parameter information corresponding to the shear wave, generate the instantaneous elastogram, and generate the ultrasonic tissue images in different modes at the same time after processing the ultrasonic echo received by the probe 100; in an embodiment, the first ultrasonic wave and the second ultrasonic wave transmitted by the probe 100 may be different, that is, the probe 100 may transmit the first ultrasonic wave and the second ultrasonic wave in sequence, or transmit the second ultrasonic wave and the first ultrasonic wave in sequence, or transmit the first ultrasonic wave and the second ultrasonic wave in an interleaving manner (for example, transmit the second ultrasonic wave after transmitting the first ultrasonic wave, and then transmit the first ultrasonic wave, and thus the interleaving manner is repeated and circulated), so that the processor 110 may obtain the parameter information corresponding to the shear wave after receiving the first ultrasonic echo corresponding to the first ultrasonic wave for the probe 100, generate the instantaneous elasticity map, and may generate the ultrasonic tissue images in different modes after receiving the second ultrasonic echo corresponding to the second ultrasonic wave for the probe 100.
When the base image is displayed within the display screen 112, the healthcare worker may determine a region of interest in the base image; the processor 110 may acquire a target position range corresponding to the region of interest in the first ultrasound echo data and determine elasticity information of the tissue under test, such as shear wave propagation velocity, shear modulus, young's modulus, etc., within the target position range of the tissue under test based on the first ultrasound echo data within the target position range.
In this embodiment, the processor 110 determines a target area corresponding to the motion parameter located in the preset range at each depth in the motion parameter image 150, and determines a target time range of the target area on the time attribute, where the target time range includes a plurality of target times. The processor 110 determines a band-shaped region based on consecutive target regions in the motion parameter image 150. The processor 110 may obtain one or more strip regions when acquiring the strip regions based on the continuous target regions in the motion parameter image 150 due to the influence of interference information such as various residual waves, reflected waves, and the like caused by the vibration of the probe.
Fig. 5 is a schematic diagram of a plurality of strip-shaped regions in a motion parameter image according to an embodiment of the present application. The motion parameter image 150 may include a first strip-shaped region S1, a second strip-shaped region S2, and a third strip-shaped region S3. In this embodiment, the motion parameter image 150 includes a plurality of pixels. The pixel value of each pixel in the motion parameter image 150 corresponds to the motion parameter at the depth corresponding to the pixel. For example, when the motion parameter image 150 is a non-gray scale image (e.g., the motion parameter image 150 is a pseudo-color image), the processor 110 may perform a graying process on the motion parameter image 150. When the value corresponding to the motion parameter is larger, in the motion parameter image after graying, the pixel point under the corresponding depth is close to white (for example, the pixel value of the pixel point is close to 255); when the value corresponding to the motion parameter is smaller, in the motion parameter image after graying, the pixel point under the corresponding depth is close to black (for example, the pixel value of the pixel point is close to 0). In determining the target region, the processor 110 may determine the maximum extremum range or the minimum extremum range as the preset range, where the maximum extremum range may be a to 255, and the target region may be a bright-band region in the motion parameter image 150 (fig. 3); the minimum extremum may be 0 to b, and the target region may be a black band region in the motion parameter image 150 (fig. 3).
In other embodiments, the target area may also be an area between a bright band area and a black band area in the motion parameter image 150 (fig. 3). For example, for a set depth, when the pixel value of a pixel is in the minimum extremum range and the pixel values of other pixels spaced from the pixel by a predetermined number are in the maximum extremum range, the processor 110 may use the pixel and other pixels spaced from the pixel by the predetermined number as the corresponding target regions at the set depth; or, when the pixel value of a pixel is in the maximum extremum range and the pixel values of other pixels spaced from the pixel by the preset number are in the minimum extremum range, the processor 110 may use the pixel and other pixels spaced from the pixel by the preset number as the corresponding target regions at the set depth.
In this embodiment, when determining the first strip-shaped area S1, the second strip-shaped area S2, and the third strip-shaped area S3 in the motion parameter image 150, if the preset range is the minimum extremum range, the processor 110 determines a target area corresponding to the depth V1, which includes a target area AB and a target area EF, where the target area AB is a set of pixels (e.g., a segment AB) in the motion parameter image 150, where the motion parameter is located in the minimum extremum range at the depth V1, and a target time range corresponding to the target area AB is a target time from t1 to t 2; the target area EF is a set of pixels (e.g., a segment EF) in the motion parameter image 150, where the motion parameter is located in the minimum extremum range at a depth of V1, and the target time range corresponding to the target area EF is the target time from t5 to t 6; the areas other than the target area AB and the target area EF at the depth V1 in the motion parameter image 150 do not satisfy the minimum extremum range. The processor 110 may further determine a target area corresponding to the depth V2, including a target area CD, where the target area CD is a set of pixels (e.g., a segment CD) in the motion parameter image 150 where the motion parameter is located within the minimum extremum range at the depth V2, a target time range corresponding to the target area CD is t3 to t4 target times, and other areas outside the target area CD in the motion parameter image 150 at the depth V2 do not satisfy the minimum extremum range.
The processor 110 determines one or more banded regions based on consecutive target regions in the motion parameter image 150. Since the shear wave is continuous in the tissue under test, the target areas at different depths are continuous. In this way, if the processor 110 determines the first strip-shaped region S1, the second strip-shaped region S2 and the third strip-shaped region S3 in the motion parameter image 150, the processor 110 determines the strip-shaped regions formed by the consecutive target regions in the motion parameter image 150.
Since the shear wave propagates in the tissue under test, the corresponding propagation path is single. If the processor 110 determines that a plurality of strip-shaped regions exist in the motion parameter image 150, it indicates that the interference information exists in the motion parameter image 150, and therefore, the processor 110 may determine that a target strip-shaped region satisfying a preset condition among the plurality of strip-shaped regions is a main propagation path of the shear wave.
In one embodiment, since the shear wave is generated after the vibration of the probe 100 is finished, the processor 110 may obtain a reference time corresponding to the vibration of the probe 100 is finished, and determine a main propagation path of a strip region composed of target regions with target times later than the reference time in the one or more strip regions. For example, if the reference time corresponding to the end of the vibration of the probe 100 is t0, the processor 110 determines the target region of the first and second band regions S1 and S2 whose target time is later than the reference time t0 because the target time corresponding to the third band region S3 is earlier than the reference time t 0. Since the motion parameter image 150 further includes the first strip-shaped region S1 and the second strip-shaped region S2, the main propagation path of the motion parameter image 150 is a strip-shaped region. At this time, the processor 110 may determine that the strip region having the largest length or the largest area of the first strip region S1 and the second strip region S2 is the main propagation path of the shear wave, wherein each strip region includes a first oblique side and a second oblique side, and the length of the strip region may be expressed as the length of the first oblique side or the second oblique side, or the longer one of the first oblique side and the second oblique side; the area of the strip-shaped area can be expressed as the area of a quadrangle enclosed by a first oblique side, a second oblique side, the difference between the projection of the first end of the first oblique side and the projection of the first end of the second oblique side on the time axis, and the difference between the projection of the second end of the first oblique side and the projection of the second end of the second oblique side on the time axis. Since the length of the hypotenuse at which the AC is located in the first strip region S1 is greater than the length of the hypotenuse at which the E is located in the second strip region S2, the processor 110 may determine that the first strip region is the primary propagation path of the shear wave.
In one embodiment, the processor 110 may directly determine that one or more of the banded regions having the maximum length or the maximum area is the primary propagation path of the shear wave. For example, in the first strip-shaped region S1, the second strip-shaped region S2, and the third strip-shaped region S3, the first strip-shaped region S1 has the largest length and the largest area, and thus, the processor 110 may determine that the first strip-shaped region is the main propagation path of the shear wave.
In one embodiment, when the processor 110 determines that the number of the strip regions composed of the target regions with the target time later than the reference time is one, the processor 110 may not need to determine the attribute information of the length or the area of the strip region.
In one embodiment, in determining the region of interest of the tissue under test, the region of interest may be at a predetermined depth, and at this time, the processor 110 may determine the target strip region at the predetermined depth as the main propagation path. For example, when the preset depth is the depth V1, the processor 110 may determine that the target area below the line segment AB in the first strip-shaped area S1 satisfies the condition, the second strip-shaped area S2 satisfies the condition, and the target area below the line segment EF in the third strip-shaped area S3 satisfies the condition, so that the processor 110 may also obtain three strip-shaped areas. Since the motion parameter image 150 further includes the first strip-shaped region S1 and the second strip-shaped region S2, the main propagation path of the motion parameter image 150 is a strip-shaped region. At this time, the processor 110 may determine, as the main propagation path of the shear wave, a band region having the maximum length or the maximum area among target regions below the line segment AB in the first band region S1, the second band region S2, and the third band region S3, among target regions below the line segment EF, if the processor 110 may determine, as the main propagation path of the shear wave, a target region below the line segment AB in the first band region S1.
In one embodiment, when determining that there are multiple target strip regions located at the predetermined depth, the processor 110 also determines the target strip region according to the reference time corresponding to the end of the vibration of the probe 100. For example, since the target times corresponding to the second strip-shaped region S2 are both earlier than the reference time t0, the processor 110 may determine that the target regions below the line segment AB in the first strip-shaped region S1 and below the line segment EF in the third strip-shaped region S3 satisfy the condition, and then the processor 110 may determine that the strip-shaped region having the maximum length or the maximum area among the target regions below the line segment AB in the first strip-shaped region S1 and below the line segment EF in the third strip-shaped region S3 is the main propagation path of the shear wave, that is, the processor 110 may determine that the target region below the line segment AB in the first strip-shaped region S1 is the main propagation path of the shear wave.
In this context, the main propagation path diagram is a diagram representing the actual main propagation path of the shear wave in the tissue under test, which is obtained based on the motion parameters or motion parameter diagrams of the tissue under test at different times and at different depths, which are caused by the propagation of the shear wave in the tissue under test.
Figures 11, 12 and 13 are graphs of the motion parameters or motion parameters of tissue under test at different times and depths, respectively, resulting from the propagation of shear waves through the tissue under test in some embodiments of the present invention. In fig. 11, the right-side band-shaped region extending to the upper right is a reflected wave of the shear wave, the right-side band-shaped region of the dotted line in fig. 12 is a residual wave of the shear wave, and the right-side band-shaped and oblong-shaped regions of the dotted line in fig. 13 are a reflected wave and a residual wave of the shear wave. It can be seen that the obtained motion parameter or motion parameter map includes various residual waves of the shear wave and interference information such as reflected waves, which may affect the examination of the doctor and the detection of the elastic parameter.
In the embodiments of the present disclosure, as described above and below, a main propagation path diagram representing an actual main propagation path of the shear wave in the tissue under test is obtained based on the motion parameter or the motion parameter diagram, and interference information such as a residual wave, a reflected wave, and the like in the motion parameter or the motion parameter diagram may be excluded from the main propagation path diagram, so that the actual main propagation path of the shear wave in the tissue under test can be more accurately reflected, and is convenient for a doctor to view.
And step 204, displaying the motion parameter image containing the main propagation path.
When the processor 110 acquires the main propagation path of the shear wave in the motion parameter image 150, the processor 110 displays a main propagation path map 160 (shown in fig. 6) through the display screen 112, wherein the main propagation path map is also the motion parameter image including the main propagation path. Because the main propagation path diagram includes the display area corresponding to the main propagation path and other areas except the main propagation path, the main propagation path diagram eliminates the influence of interference information, improves the understandability of the elasticity test result, and enables medical staff to diagnose intuitively according to the main propagation path diagram.
In one embodiment, the processor 110 may also determine the elastic information of the tissue under test based on the aforementioned first ultrasound echo data or the aforementioned motion parameter image or the aforementioned main propagation path map. Here, the elastic information of the tissue under test may be parameters such as a shear wave propagation speed, young's modulus of the tissue under test, shear modulus of the tissue under test, and the like.
Please refer to fig. 6, which shows a schematic diagram of binarization of a main propagation path diagram in an embodiment of the present application. After obtaining the main propagation path in the motion parameter image 150, the processor 110 may perform binarization processing on the motion parameter image 150, so that the main propagation path in the motion parameter image 150 is displayed in a first color, and an area outside the main propagation path is displayed in a second color, which is better for medical care personnel to identify. For example, the processor 110 may set a target strip-shaped region corresponding to the main propagation path in the motion parameter image 150 to be a first color (e.g., white), and set a region outside the target strip-shaped region corresponding to the main propagation path to be a second color (e.g., black).
In an embodiment, the influence of the interference information is weak, and after the processor 110 performs binarization processing on the motion parameter image 150, the display area of the main propagation path and other areas outside the main propagation path can be distinguished from the obtained main propagation path map. For example, when the preset range is the minimum extremum range, the processor 110 sets the pixel point of the motion parameter image 150 whose pixel value is greater than the preset threshold value as the first color, that is, sets the color of the other region outside the main propagation path as black; the processor 110 further sets a pixel point in the motion parameter image whose pixel value is not greater than the preset threshold value as a second color, that is, sets the color of the display area of the main propagation path as white. In this way, the main propagation path map 160 can be directly obtained after the processor 110 performs binarization processing on the motion parameter image 150.
Fig. 7 is a non-binary diagram of a main propagation path diagram according to an embodiment of the present application. In one embodiment, since the motion parameters (such as strain information or displacement information) or energy of the tissue under test gradually decrease as the shear wave propagates through the tissue under test, and the propagation depth and propagation time increase, the processor 110 may display the main propagation path map 160 in a non-binary manner to more clearly show the change. The processor 110 may set the pixel value of the pixel point at each depth in the target strip region corresponding to the main propagation path to have a third color corresponding to the motion parameter, where the third colors corresponding to different motion parameters are different; and the region outside the target banded region corresponding to the main propagation path may be set to the fourth color.
Referring to fig. 8, a schematic diagram of a main propagation path in another embodiment of the present application is shown. When the processor 110 determines that the first strip-shaped region S1 is the main propagation path, the processor 110 may also simply display some points at a specific depth on the main propagation path. For example, the processor 110 may display only the circle in fig. 8 (excluding the two oblique sides of the first strip-shaped area S1) in the display screen 112 for easy display.
In one embodiment, in determining the dominant propagation path in the motion parameter image 150, the processor 110 may calculate elastic parameters of the tissue under test, including but not limited to shear wave velocity, Young's modulus, shear modulus, and the like. As shown in fig. 5, the processor 110 may fit a straight line shown by a dashed line based on the main propagation path, wherein the slope of the straight line shown by the dashed line may be used to represent the shear wave velocity; the processor 110 may be used to calculate the Young's modulus of the tissue under test, etc., based on the shear wave velocity. In one embodiment, the processor 110 also includes statistics of multiple measurements of the above parameters, such as median, quartile, ratio of quartile to median, etc. of Young's modulus obtained from 10 measurements.
In one embodiment, processor 110 may control display 112 to display the base image and the region of interest within the base image, the Young's modulus of the tissue under test, and/or the main propagation path map for the medical practitioner to diagnose.
According to the elastic imaging method, the motion parameter image comprising the main propagation path is displayed after the main propagation path of the shear wave in the motion parameter image is obtained, so that the defect that medical staff cannot accurately explain the displayed meaning of the motion parameter image due to the influence of interference information such as various residual waves, reflected waves and the like caused by the vibration of the probe in the motion parameter image can be reduced, and the understandability of the elastic test result is improved.
In one embodiment, a method of elasticity imaging may comprise the steps of:
transmitting a first ultrasonic wave to the tissue under test to track a shear wave propagating within the tissue under test;
receiving an ultrasonic echo (referred to as a first ultrasonic echo) of the first ultrasonic wave returned by the tested tissue to obtain first ultrasonic echo data;
obtaining motion parameters of the tested tissue at different moments and different depths caused by the propagation of the shear wave in the tested tissue according to the first ultrasonic echo data, wherein the motion parameters can comprise the displacement, the speed or the strain of the tested tissue;
determining a main propagation path of the shear wave according to the motion parameters, and generating a main propagation path diagram based on the main propagation path;
and displaying the obtained main propagation path diagram.
In this embodiment, the elasticity information of the tissue under test can be determined according to the first ultrasonic echo data, the motion parameter or the main propagation path diagram, and the elasticity information of the tissue under test is also displayed to the user. The elastic information may be displayed simultaneously with the main propagation path diagram or may be displayed non-simultaneously with the main propagation path diagram.
In this embodiment, a motion parameter (referred to as a "target motion parameter" herein) satisfying a preset condition may be determined from the motion parameters, and a main propagation path of the shear wave may be obtained according to a depth and a time corresponding to the target motion parameter. Here, the preset condition may be various suitable conditions, and may be set according to actual needs, for example, the preset condition may be greater than a preset threshold, within a preset range, and the like.
In this embodiment, the confidence of the elastic information of the tested tissue may also be determined according to the obtained main propagation path. For example, one or more confidence parameters corresponding to the main propagation path may be determined according to the main propagation path, and the confidence of the elastic information of the tested tissue may be determined according to the one or more confidence parameters. Here, the confidence parameter may include one or more of a linearity parameter of the main propagation path, an error parameter when the main propagation path straight line fitting calculates the shear wave propagation velocity, a length parameter of the main propagation path, an area parameter of the main propagation path, and the like.
In this embodiment, a base image of the tissue under test may also be acquired and displayed simultaneously with the main propagation path map and the elastic information of the tissue under test. Here, the base image may be one or more of a B image, a C image, or an image of another pattern of the tissue under test. The basic image can be obtained by an ultrasonic imaging system in real time, namely, ultrasonic waves are transmitted to the tested tissue through an ultrasonic probe and ultrasonic echoes are received, an ultrasonic echo signal is obtained, and the basic image of the tested tissue is obtained according to the ultrasonic echo signal; the base image of the tissue under test may also be obtained and stored from a pre-acquisition read by another device.
In this embodiment, the confidence level of the elastic information of the tested tissue may also be displayed.
Referring to FIG. 9, a flowchart illustrating steps of an elastography method in accordance with yet another embodiment of the present application is shown. The elastic imaging method comprises the following steps:
Step 300 in this embodiment is similar to step 200 in the previous embodiment, and refer specifically to step 200.
Step 302 in this embodiment is similar to step 202 in the previous embodiment, with specific reference to step 202.
And 304, displaying the motion parameter image containing the main propagation path.
Step 304 in this embodiment is similar to step 204 in the previous embodiment, with specific reference to step 204.
When acquiring the main propagation path of the shear wave in the motion parameter image 150, the processor 110 may calculate the elastic information of the tissue under test according to the main propagation path, and further, the reliability of the main propagation path affects the elastic information of the tissue under test. Accordingly, the processor 150 may determine the confidence of the elastic information of the measured tissue based on one or more confidence parameters corresponding to the main propagation path, wherein the confidence parameters include one or more of a linearity parameter of the main propagation path, an error parameter when the main propagation path is straight-line fit to calculate the propagation velocity of the shear wave, a length parameter of the main propagation path, and an area parameter of the main propagation path.
For example, the length of the main propagation path, the strength of energy, and the linearity of the main propagation path can be easily determined from the main propagation path diagram. In clinical hepatic fibrosis detection, the Young modulus value of the liver tissue is calculated mainly by judging the average propagation speed of the shear wave in the liver tissue, so that the degree of hepatic fibrosis is reflected. Generally, a larger Young's modulus indicates a harder liver tissue and a higher degree of liver fibrosis. Since hepatic fibrosis is mainly diffuse lesion, the speed is uniform when the shear wave propagates, the main propagation path is represented as a straight line path, and the slopes of the straight line path correspond to the speed of the shear wave one by one. In some inspections, if the main propagation path is too short (e.g., only 50mm deep), this may indicate a weak or large attenuation of the shear wave energy, resulting in insufficient penetration; if the primary propagation path exhibits a curve or a less straight line, indicating that the shear wave propagation is not uniform, the calculated slope or velocity of shear wave propagation or young's modulus of the tissue results may be inaccurate; if the main propagation path is not calculated at all, the data quality of the examination is too poor, and a valid result is difficult to obtain.
The confidence may be a linearity parameter of the main propagation path (e.g., determining the degree of linearity of the main propagation path), and when the linearity of the main propagation path is better, it indicates that the processor 110 determines that the reliability of the elastic information of the tested tissue is higher; alternatively, the confidence may be an error corresponding to the process of the processor 110 performing a straight line fitting (e.g., fitting by a least square method) on the main propagation path and calculating the slope of the straight line after fitting, and when the error is smaller, it indicates that the reliability of the processor 110 determining the elastic information of the measured tissue is higher; alternatively, the confidence level may be that the processor 110 may determine the length parameter of the main propagation path, and when the length parameter of the main propagation path is longer, the processor 110 may determine that the reliability of the elastic information of the tested tissue is higher; alternatively, the confidence level may be an area parameter that the processor 110 may determine the primary propagation path, with a larger area indicating a higher reliability of the processor 110 in determining the elasticity information of the tissue under test.
In one embodiment, the confidence level may be a composite score parameter that the processor 110 may obtain based on a weighted balance of the confidence level parameters, wherein a higher composite score parameter indicates a higher reliability of the processor 110 in determining the elasticity information of the tissue under test.
And 308, controlling to output prompt information corresponding to the confidence coefficient of the elastic information of the tested tissue.
The processor 110 may display on the display 112 a confidence level for determining the elasticity information of the tested tissue based on the above-mentioned one or more confidence level parameters, and the corresponding numerical value of each confidence level parameter has a corresponding confidence level, such as a confidence level of 90%, so that the medical staff can determine the reliability of calculating the elasticity information of the tested tissue according to the displayed confidence level.
In one embodiment, after the processor 110 obtains the base image of the tissue under test, the processor 110 may display the base image, confidence level, and main propagation path map of the tissue under test on the display 112.
In one embodiment, the processor 110 may also display the region of interest determined by the healthcare worker on the base image, and may display the Young's modulus of the tissue under test calculated from the calculated shear wave velocity.
According to the elastic imaging method, the confidence coefficient of the elastic information of the tested tissue is determined through the main propagation path diagram, and medical personnel can conveniently determine the reliability and the understandability of the elastic information of the tested tissue according to the displayed confidence coefficient.
Referring to FIG. 10, a block diagram of an elastography system 80 in another embodiment of the present application is shown. As shown in FIG. 10, the elastography system 80 may employ the various embodiments described above. The elastography system 80 provided in the present application is described below, the elastography system 80 may include a processor 800, a storage device 802, a probe 100, a control circuit 804, a display screen 112, and a computer program (instructions) stored in the storage device 802 and executable on the processor 800, and the elastography system 80 may further include other hardware components, such as a communication device, keys, a keyboard, and the like, which are not described herein again. The processor 800 may exchange data with the probe 100, the control circuitry 904, the memory device 802, and the display screen 112 via signal lines 808.
The Processor 800 may be a Central Processing Unit (CPU), other general purpose Processor, a Digital Signal Processor (DSP), an Application Specific Integrated Circuit (ASIC), a Field-Programmable Gate Array (FPGA) or other Programmable logic device, discrete Gate or transistor logic device, discrete hardware component, etc. The general purpose processor may be a microprocessor or the processor may be any conventional processor or the like that is the control center for the elastography system 80, with various interfaces and lines connecting the various parts of the overall elastography system 80. In this embodiment, the processor 800 may be used to implement all functions of the image processing module 110, or may be integrated with functions of the elements such as the beam combiner 106, and the functions of the specific elements may refer to the foregoing embodiments. For example, the processor 800 may generate a first transmission timing to control the probe 100 to generate a first ultrasonic wave; the processor 800 may generate a second transmission timing to control the probe 100 to generate a second ultrasonic wave; the processor 800 may generate excitation timing and control the generation of shear waves in the tissue under test after the probe 100 is vibrated.
The control circuit 804 may include the functions of the components of the transmitting circuit 102, the receiving circuit 104, and/or the beam combiner 106 in the above embodiments, and the functions of the specific components may refer to the foregoing embodiments. For example, the control circuit 804 may generate a first transmission timing to control the probe 100 to generate a first ultrasonic wave; the control circuit 804 may generate a second transmission timing to control the probe 100 to generate a second ultrasonic wave; control circuitry 804 may generate excitation timing and control the generation of shear waves in the tissue under test as probe 100 vibrates.
The storage device 802 may be used to store the computer programs and/or modules, and the processor 800 implements the various functions of the above-described elastography method by running or executing the computer programs and/or modules stored in the storage device 802 and calling the data stored in the storage device 802. The storage device 802 may store the ultrasound echo data and may be used by the processor 800 to determine the main propagation path of the shear wave according to the ultrasound echo data, and the storage device 802 may mainly include a storage program area and a storage data area, wherein the storage program area may store an operating system, an application program required for at least one function, and the like. In addition, the storage device 802 may include a high-speed random access memory device, and may also include a non-volatile storage device such as a hard disk, a memory, a plug-in hard disk, a Smart Media Card (SMC), a Secure Digital (SD) Card, a Flash memory Card (Flash Card), at least one piece of magnetic disk storage, a Flash memory device, or other volatile solid state storage.
The display 112 may display a User Interface (UI), a Graphical User Interface (GUI), and the display 112 may include at least one of a Liquid Crystal Display (LCD), a thin film transistor LCD (TFT-LCD), an Organic Light Emitting Diode (OLED) touch display, a flexible touch display, a three-dimensional (3D) touch display, and the like.
The processor 800 runs a program corresponding to the executable program code by reading the executable program code stored in the storage device 802 for performing the elastography method in any of the previous embodiments.
In the foregoing embodiments, the descriptions of the respective embodiments have respective emphasis, and for parts that are not described in detail in a certain embodiment, reference may be made to related descriptions of other embodiments. The foregoing detailed description of the embodiments of the present application has been presented to illustrate the principles and implementations of the present application, and the above description of the embodiments is only provided to help understand the method and the core concept of the present application; meanwhile, for a person skilled in the art, according to the idea of the present application, there may be variations in the specific embodiments and the application scope, and in summary, the content of the present specification should not be construed as a limitation to the present application.
Claims (15)
1. An elastography method, characterized in that it comprises:
acquiring a motion parameter image of a tested tissue;
determining a target area corresponding to a motion parameter within a preset range at each depth in the motion parameter image, and determining one or more strip-shaped areas based on continuous target areas in the motion parameter image;
determining a target strip-shaped area meeting a preset condition in the one or more strip-shaped areas as a main propagation path of the shear wave, and obtaining a main propagation path diagram, wherein the main propagation path diagram characterizes an actual main propagation path of the shear wave in the tested tissue;
displaying the main propagation path diagram;
wherein the determining that a target strip region of the one or more strip regions that meets a preset condition is a main propagation path of the shear wave includes any one of:
determining a target area of the one or more strip-shaped areas, wherein the target time is later than a reference time, determining a strip-shaped area formed by the target areas of the one or more strip-shaped areas, wherein the target time is later than the reference time, as the main propagation path, wherein each target area corresponds to a target time range, each target time range comprises a plurality of target times, and the reference time is a time corresponding to the end of the probe vibration;
determining a target banded region positioned at a preset depth as the main propagation path;
determining a target strip region of the one or more strip regions having a maximum length or a maximum area as the primary propagation path.
2. An elastography method, characterized in that it comprises:
acquiring a motion parameter image of a tested tissue;
automatically determining a main propagation path of a shear wave propagating in the tissue under test in the motion parameter image, and obtaining a main propagation path diagram, wherein the main propagation path is a strip-shaped region, and the main propagation path diagram characterizes an actual main propagation path of the shear wave in the tissue under test;
displaying the main propagation path diagram, wherein a banded region corresponding to the main propagation path in the main propagation path diagram is displayed as one color, and other regions except the main propagation path in the main propagation path diagram are all displayed as another different color.
3. An elastography method, characterized in that it comprises:
acquiring a motion parameter image of a tested tissue;
automatically determining a main propagation path of a shear wave propagating in the tested tissue in the motion parameter image to obtain a main propagation path diagram, wherein the main propagation path is a strip-shaped region, the main propagation path diagram characterizes an actual main propagation path of the shear wave in the tested tissue, and only one main propagation path is included in the main propagation path diagram;
and displaying the main propagation path diagram.
4. The elastography method of any of claims 1-3, wherein said acquiring motion parameter images of the tissue under test comprises:
transmitting a first ultrasonic wave to the tissue under test when the probe receives a first transmission timing sequence to track a shear wave propagating in the tissue under test;
the probe receives a first ultrasonic echo returned by the tested tissue and converts the first ultrasonic echo into an electric signal;
performing beam synthesis on the electric signal to obtain first ultrasonic echo data;
obtaining a motion parameter image of the tissue under test based on the first ultrasound echo data.
5. The elastography method of claim 4, wherein said obtaining a motion parameter image of the tissue under test based on the first ultrasound echo data comprises:
obtaining motion parameters of the tested tissue at different moments and different depths caused by the propagation of the shear wave in the tested tissue based on the first ultrasonic echo data, wherein the motion parameters comprise displacement, speed or strain;
and determining a motion parameter image of the tested tissue based on the motion parameters of the shear waves at different moments and different depths.
6. The elastography method of claim 2 or 3, wherein said automatically determining a principal propagation path of shear waves propagating within the tissue under test in the motion parameter image comprises:
determining an area corresponding to a pixel point with a pixel value larger than a preset threshold value in the motion parameter image as the main propagation path by using a binarization processing mode, wherein the motion parameter image comprises a plurality of pixel points, and the pixel value of each pixel point corresponds to the size of the motion parameter under the depth corresponding to the pixel point; or,
and determining the area of the motion parameter image with the motion parameter larger than a preset threshold value as the main propagation path by using a binarization processing mode.
7. The elastography method of claim 6, wherein said displaying the primary propagation path comprises:
setting the main propagation path in the main propagation path map to a first color;
setting an area other than the main propagation path in the main propagation path map as a second color.
8. The elastography method of claim 2 or 3, wherein said displaying the primary propagation path map comprises:
setting the pixel value of the pixel point at each depth in the strip-shaped area corresponding to the main propagation path to have a third color corresponding to the motion parameter, wherein the third colors corresponding to different motion parameters are different;
and setting the area outside the strip-shaped area corresponding to the main propagation path as a fourth color.
9. The elastography method of any of claims 1-3, further comprising:
determining one or more confidence coefficient parameters corresponding to the main propagation path;
determining a confidence level of elasticity information for the tissue under test based on the one or more confidence level parameters.
10. The elastography method of claim 9, wherein the confidence parameters comprise one or more of a linearity parameter of the principal propagation path, an error parameter when the principal propagation path line-fits the shear wave propagation velocity, a length parameter of the principal propagation path, an area parameter of the principal propagation path.
11. The elastography method of claim 4, further comprising:
acquiring a base image of the tested tissue and/or elasticity information of the tested tissue;
displaying a base image of the tested tissue and/or elasticity information of the tested tissue, wherein the base image, the elasticity information and the motion parameter image are scanned by using the same ultrasonic probe or different ultrasonic probes.
12. An elastography method, characterized in that it comprises:
acquiring a motion parameter image of a tested tissue;
determining a main propagation path of a shear wave propagating in the tissue under test from the motion parameter image;
determining one or more confidence coefficient parameters corresponding to the main propagation path;
determining a confidence level of elasticity information for the tissue under test based on the one or more confidence level parameters.
13. The elastography method of claim 12, wherein the confidence parameters comprise one or more of a linearity parameter of the principal propagation path, an error parameter when the principal propagation path line-fits the shear wave propagation velocity, a length parameter of the principal propagation path, an area parameter of the principal propagation path.
14. An elastography system, characterized in that the elastography system comprises:
the probe is used for transmitting a first ultrasonic wave to a tested tissue so as to track a shear wave propagating in the tested tissue, and is also used for receiving a first ultrasonic echo returned by the tested tissue to obtain first ultrasonic echo data;
a processor connected to the probe, the processor being configured to obtain motion parameters of the tissue under test at different times and different depths, which are caused by propagation of the shear wave in the tissue under test, based on the first ultrasonic echo data, determine a main propagation path of the shear wave according to the motion parameters, and obtain a main propagation path diagram, wherein the main propagation path diagram characterizes an actual main propagation path of the shear wave in the tissue under test;
and the display screen is connected with the processor, and the processor is used for displaying the main propagation path diagram in the display screen.
15. A computer readable storage medium storing computer instructions which, when executed by a processor, implement the elastography method of any of claims 1-13.
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| US10743837B2 (en) * | 2014-08-04 | 2020-08-18 | Delphinus Medical Technologies, Inc. | Ultrasound waveform tomography method and system |
| CN110507361B (en) * | 2014-08-28 | 2022-11-29 | 深圳迈瑞生物医疗电子股份有限公司 | Shear wave imaging method and system |
| CN107405133B (en) * | 2014-12-24 | 2021-06-08 | 声科影像有限公司 | Shear wave elastic imaging method and device suitable for anisotropic medium imaging |
| CN104605891B (en) * | 2014-12-31 | 2017-05-31 | 中国科学院苏州生物医学工程技术研究所 | Detect the shearing wave method of spread speed, the method for detection biological tissue elasticity and biological tissue elasticity imaging method in biological tissues |
| EP3359047B1 (en) * | 2015-10-08 | 2021-07-14 | Mayo Foundation for Medical Education and Research | Methods for ultrasound elastography with continuous transducer vibration |
| WO2017223312A1 (en) * | 2016-06-22 | 2017-12-28 | Duke University | Ultrasound transducers for constructive shear wave interference and related methods and systems |
| US11441987B2 (en) * | 2016-09-26 | 2022-09-13 | Duke University | Systems and methods for analysis of liquids by covered fluidic channels integrated onto sensor platforms |
| CN106618638B (en) * | 2016-11-04 | 2019-02-26 | 声泰特（成都）科技有限公司 | A kind of quantitative shearing wave elastogram system |
| KR20180054360A (en) * | 2016-11-15 | 2018-05-24 | 삼성메디슨 주식회사 | Ultrasonic diagnostic apparatus and method for controlling the same |
| CN114360727A (en) * | 2017-04-21 | 2022-04-15 | 深圳迈瑞生物医疗电子股份有限公司 | Ultrasonic elastography device and elastography result evaluation method |
| CN108720869B (en) * | 2017-04-25 | 2022-05-27 | 深圳迈瑞生物医疗电子股份有限公司 | Ultrasonic elasticity measurement method and device |
| CN107510474B (en) * | 2017-09-21 | 2020-07-10 | 深圳开立生物医疗科技股份有限公司 | Shear wave elastic imaging method and system |
| CN110292399B (en) * | 2018-05-04 | 2022-03-08 | 深圳迈瑞生物医疗电子股份有限公司 | Method and system for measuring shear wave elasticity |
| CN109919918A (en) * | 2019-02-21 | 2019-06-21 | 清华大学 | Control method and device, computer equipment and the readable storage medium storing program for executing of elastogram |
| CN109893172B (en) * | 2019-02-22 | 2020-06-19 | 清华大学 | Method and device for determining mechanical parameters based on elastography and computer equipment |
| CN118750029A (en) * | 2019-06-12 | 2024-10-11 | 深圳迈瑞生物医疗电子股份有限公司 | Ultrasonic elastography method and system |
| CN114287968A (en) * | 2019-09-27 | 2022-04-08 | 深圳迈瑞生物医疗电子股份有限公司 | Elasticity imaging method, system and computer readable storage medium |
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| CN114287968A (en) | 2022-04-08 |
| WO2021056645A1 (en) | 2021-04-01 |
| CN110710989B (en) | 2021-12-24 |
| CN110710989A (en) | 2020-01-21 |
| CN114072066A (en) | 2022-02-18 |
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