CN117653204A - Ultrasonic measurement method and ultrasonic imaging equipment - Google Patents
Ultrasonic measurement method and ultrasonic imaging equipment Download PDFInfo
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Abstract
The application provides an ultrasonic measurement method and ultrasonic imaging equipment, wherein the ultrasonic measurement method comprises the following steps: controlling an ultrasonic probe to emit first ultrasonic waves to a target tissue, receiving ultrasonic echoes of the first ultrasonic waves to obtain first echo data, and generating an ultrasonic tissue image of the target tissue according to the first echo data; determining a region of interest of the target tissue based on the ultrasound tissue image; controlling the ultrasonic probe to emit second ultrasonic waves to the region of interest, and receiving ultrasonic echoes of the second ultrasonic waves returned from the region of interest to obtain second echo data; obtaining shear wave speed in the region of interest according to the second echo data, and obtaining longitudinal wave sound velocity in the region of interest according to the second echo data; and calculating at least one of poisson coefficient, lawster coefficient and bulk modulus according to the shear wave speed and the longitudinal wave sound velocity. The ultrasonic measurement method can more conveniently obtain the mechanical parameters of the target tissue.
Description
Technical Field
The invention relates to the technical field of ultrasound, in particular to an ultrasound measurement method and ultrasound imaging equipment.
Background
With the development of ultrasound imaging technology, various imaging modalities have emerged to assess the pathological state of tissue from different angles. For example, the ultrasonic viscoelastography technology, which performs imaging by extracting information about the elasticity and viscosity of tissues, is related to noninvasive auxiliary diagnosis of major diseases such as breast cancer, liver cirrhosis and the like, is a research hotspot in the field of ultrasonic imaging for the last twenty years, and is popular with doctors.
In most current elasticity-related studies, however, tissue is imaged as a assumption of a locally homogeneous pure elastomer. In particular to an ultrasonic quantitative elastography technology based on shear waves, which is based on the assumption that the poisson coefficient is a fixed constant, only the elastic modulus is calculated for display. However, more and more studies have shown that biological tissues are composite materials composed of both liquid and solid, and that the poisson's coefficient of tissues in different pathological conditions may be different. In addition, the measurement of the poisson coefficient can be used for researching tissue tumor, tissue permeability under edema and change of permeability, and the poisson coefficient has a very important role in the elasticity related research. Besides poisson's coefficient, the mechanical parameters such as the Lawsonia coefficient and the bulk modulus have respective effects, and in the field of ultrasonic imaging, how to better measure the poisson's coefficient of tissues, the mechanical parameters such as Lawsonia Mei Jishu and the bulk modulus are one of the problems to be solved or improved.
Disclosure of Invention
The application provides an ultrasonic measurement method and ultrasonic imaging equipment, and the ultrasonic measurement method and the ultrasonic imaging equipment applying the ultrasonic measurement method can acquire various mechanical parameters more conveniently.
To achieve the above object, an embodiment of the present application provides an ultrasonic measurement method, including:
controlling an ultrasonic probe to emit first ultrasonic waves to target tissues, receiving ultrasonic echoes of the first ultrasonic waves to obtain first echo data, and generating ultrasonic tissue images of the target tissues according to the first echo data;
determining a region of interest of the target tissue based on the ultrasound tissue image;
controlling an ultrasonic probe to emit a second ultrasonic wave to the region of interest to track a shear wave propagating in the region of interest, and receiving an ultrasonic echo of the second ultrasonic wave returned from the region of interest to obtain second echo data;
controlling an ultrasonic probe to emit third ultrasonic waves to the region of interest, and receiving ultrasonic echoes of the third ultrasonic waves returned from the region of interest to obtain third echo data;
obtaining shear wave velocity in the region of interest according to the second echo data, and obtaining longitudinal wave sound velocity in the region of interest according to the third echo data;
And calculating at least one of a poisson coefficient, a Lawster coefficient and a bulk modulus according to the shear wave speed and the longitudinal wave sound velocity.
To achieve the above object, another embodiment of the present application provides an ultrasonic measurement method, including:
controlling an ultrasonic probe to emit first ultrasonic waves to target tissues, receiving ultrasonic echoes of the first ultrasonic waves to obtain first echo data, and generating ultrasonic tissue images of the target tissues according to the first echo data;
determining a region of interest of the target tissue based on the ultrasound tissue image;
controlling an ultrasonic probe to emit a second ultrasonic wave to the region of interest to track a shear wave propagating in the region of interest, and receiving an ultrasonic echo of the second ultrasonic wave returned from the region of interest to obtain second echo data;
obtaining shear wave velocity in the region of interest according to the second echo data, and obtaining longitudinal wave sound velocity in the region of interest according to the second echo data;
and calculating at least one of a poisson coefficient, a Lawster coefficient and a bulk modulus according to the shear wave speed and the longitudinal wave sound velocity.
To achieve the above object, another embodiment of the present application provides an ultrasonic measurement method, including:
Controlling an ultrasonic probe to emit first ultrasonic waves to target tissues, receiving ultrasonic echoes of the first ultrasonic waves to obtain first echo data, and generating ultrasonic tissue images of the target tissues according to the first echo data;
determining a region of interest of the target tissue based on the ultrasound tissue image;
obtaining longitudinal wave sound velocity in the region of interest according to the first echo data;
controlling an ultrasonic probe to emit second ultrasonic waves to the region of interest, receiving ultrasonic echoes of the second ultrasonic waves returned from the region of interest to obtain second echo data, and obtaining shear wave speeds in the region of interest according to the second echo data;
and calculating at least one of a poisson coefficient, a Lawster coefficient and a bulk modulus according to the shear wave speed and the longitudinal wave sound velocity.
To achieve the above object, there is provided in still another embodiment of the present application an ultrasonic imaging apparatus including:
an ultrasonic probe for transmitting ultrasonic waves and receiving echo data of the ultrasonic waves;
a memory for storing a program;
and the processor is used for executing the program stored in the memory to realize the method.
In the above embodiment, the shear wave velocity in the target tissue is obtained by referring to the shear wave elastography technology, that is, the transverse wave velocity in the target tissue is obtained, and meanwhile, the longitudinal wave sound velocity in the target tissue is obtained by referring to the longitudinal wave sound velocity imaging technology, so that the poisson coefficient, the tensile Mei Jishu, the bulk modulus and other mechanical parameters can be calculated according to the obtained shear wave velocity and the longitudinal wave sound velocity.
Drawings
FIG. 1 is a block diagram of an ultrasound imaging device of an embodiment;
FIG. 2 is a flow chart of an ultrasonic measurement method of an embodiment;
FIG. 3 is a flow chart of acquiring longitudinal wave sound velocity for one embodiment;
FIG. 4 is a flow chart of acquiring longitudinal wave sound velocity according to another embodiment;
FIG. 5 is a schematic diagram of a region of interest and a reference region of an embodiment;
FIG. 6 is a schematic diagram of an ultrasound tissue image and Poisson's coefficients simultaneously displayed for one embodiment;
FIG. 7 is a flow chart of one embodiment for generating and displaying Poisson coefficient variation curves;
FIG. 8 is a graph showing Poisson's coefficient variation curves for two materials according to one embodiment;
Fig. 9 is a schematic diagram of two curves of poisson's coefficient change of interest and corresponding to one embodiment.
Detailed Description
The invention will be described in further detail below with reference to the drawings by means of specific embodiments. Wherein like elements in different embodiments are numbered alike in association. In the following embodiments, numerous specific details are set forth in order to provide a better understanding of the present application. However, one skilled in the art will readily recognize that some of the features may be omitted, or replaced by other elements, materials, or methods in different situations. In some instances, some operations associated with the present application have not been shown or described in the specification to avoid obscuring the core portions of the present application, and may not be necessary for a person skilled in the art to describe in detail the relevant operations based on the description herein and the general knowledge of one skilled in the art.
Furthermore, the described features, operations, or characteristics of the description may be combined in any suitable manner in various embodiments. Also, various steps or acts in the method descriptions may be interchanged or modified in a manner apparent to those of ordinary skill in the art. Thus, the various orders in the description and drawings are for clarity of description of only certain embodiments, and are not meant to be required orders unless otherwise indicated.
The numbering of the components itself, e.g. "first", "second", etc., is used herein merely to distinguish between the described objects and does not have any sequential or technical meaning. The terms "coupled" and "connected," as used herein, are intended to encompass both direct and indirect coupling (coupling), unless otherwise indicated.
The most important concept of the invention is that the transverse wave velocity is obtained by referring to an elastic measurement mode, the longitudinal wave sound velocity is obtained by referring to a sound velocity measurement mode, and the related mechanical parameters are obtained by calculating the obtained shear wave velocity and the longitudinal wave sound velocity.
The elastic measurement means referred to herein may be one or a combination of two or more of a vibrating elastic measurement means based on external force vibration, a shear wave measurement means based on acoustic radiation force, and a strain elastic measurement means.
Specifically, the vibration elasticity measurement mode based on external force vibration generates shear waves by external force vibration to be transmitted into tissues, and then reflects hardness differences among tissues by a method of generating propagation of the shear waves inside biological tissues and detecting propagation parameters (such as propagation speed) thereof. For isotropic elastic tissue, shear wave velocity C s The following relationship exists between the elastic modulus E of the tissue: young's modulus (where ρ is the tissue density). That is, there is a one-to-one correspondence between shear wave velocity and elastic modulus.
Shear wave measurement based on acoustic radiation force means generates propagation of shear wave inside biological tissue by ultrasonic acoustic radiation force, and then reflects hardness difference between biological tissues by a method of generating propagation of shear wave inside biological tissue and detecting propagation parameters (such as propagation velocity) thereof. For isotropic elastic tissue, shear wave velocity C s The following relationship exists between the elastic modulus E of the tissue: young's modulus(where ρ is the tissue density). That is, there is a one-to-one correspondence between shear wave velocity and elastic modulus.
The basic principle of the strain elastic measurement mode, or the conventional ultrasonic elastic measurement mode, is as follows: the ultrasonic probe slightly presses the target biological tissue or forms certain pressure on the tissue by means of the breathing, vascular pulsation and other processes of the human body, two frames of ultrasonic echo signals before and after compression are obtained, when the biological tissue is compressed, strain along the compression direction is generated in the biological tissue, if Young modulus distribution in the biological tissue is uneven, strain distribution in the biological tissue is also different, strain information of the biological tissue is detected through a plurality of methods, and parameters related to tissue elasticity such as strain quantity, strain rate and the like are calculated and output, so that the elasticity difference between different tissues in a pressure application area is indirectly reflected. Specifically, according to hooke's law, for isotropic elastomers, stress σ=strain ε×Young's modulus E, i.e., E=σ/ε. Where Young's modulus E is a parameter related to tissue stiffness, with higher Young's modulus indicating greater tissue stiffness. The ultrasonic probe generates deformation by pressing biological tissues so as to detect the elastic result of the region of interest, and the elastic result obtained by calculation is a quasi-static elastic parameter of the region of interest. The quasi-static elastic parameter is the strain amount or strain rate.
In the present embodiment, the elastic measurement method is not limited to the elastic measurement method listed above, and may be another elastic measurement method based on ultrasound elastography.
An embodiment of the present invention provides an ultrasonic imaging apparatus 10 so that mechanical parameters can be conveniently measured. A block diagram of an ultrasound imaging apparatus 10 is shown in fig. 1. The ultrasound imaging apparatus 10 includes, among other things, an ultrasound probe 110, a transmit/receive controller 120, a memory 130, a processor 140, and a display 150. The transmit/receive controller 120 may include a transmit controller for exciting the ultrasound probe 110 to transmit ultrasound waves to the target tissue and a receive controller for receiving ultrasound echoes returned from the target tissue by the ultrasound probe 110. The processor 140 may obtain echo data based on the ultrasound echoes, and process the echo data to obtain an ultrasound image of the target tissue. For example, echo data is subjected to beam synthesis processing by a beam synthesis circuit. The ultrasound images obtained by the processor 140 may be stored in the memory 130. Also, the ultrasound image may be displayed on the display 150.
In embodiments of the present invention, the processor 140 may determine the longitudinal wave sound velocity and the shear wave velocity of the ultrasound wave propagating in the target tissue based on the echo data, as will be described in more detail in subsequent embodiments of the present specification.
Alternatively, the display 150 in the ultrasound imaging device 10 may be a touch display screen, a liquid crystal display screen, or the like; or the display 150 may be a stand-alone display device such as a liquid crystal display, television, or the like that is independent of the ultrasound imaging device 10; or the display 150 may be a display screen of an electronic device such as a smart phone, tablet, etc. Wherein the number of displays 150 may be one or more.
Alternatively, the memory 130 in the ultrasound imaging device 10 may be a flash memory card, a solid state memory, a hard disk, or the like. Which may be volatile memory and/or nonvolatile memory, removable memory and/or non-removable memory, and the like.
Alternatively, the processor 140 in the ultrasound imaging device 10 may be implemented by software, hardware, firmware, or any combination thereof, and may use circuitry, single or multiple application specific integrated circuits (Application Specific Integrated Circuit, ASIC), single or multiple general purpose integrated circuits, single or multiple microprocessors 140, single or multiple programmable logic devices, or any combination of the foregoing, or other suitable circuits or devices, such that the processor 140 may perform the corresponding steps of the methods in the various embodiments in this specification.
It should be understood that the components included in the ultrasound imaging device 10 shown in fig. 1 are illustrative only and may include more or fewer components. For example, the ultrasound imaging device 10 may also include input devices such as a keyboard, mouse, scroll wheel, trackball, etc., and/or output devices such as a printer in addition to the display 150. The corresponding external input/output port may be a wireless communication module, a wired communication module, or a combination of both. The external input/output ports may also be implemented based on USB, bus protocols such as CAN, and/or wired network protocols, among others. The invention is not limited in this regard.
Fig. 2 is a schematic flow chart of an ultrasonic measurement method according to an embodiment of the present invention. The method shown in fig. 2 comprises the following steps:
step A100, controlling the ultrasonic probe 110 to transmit a first ultrasonic wave to the target tissue, receiving an ultrasonic echo of the first ultrasonic wave to obtain first echo data, and generating an ultrasonic tissue image of the target tissue according to the first echo data.
The target tissue may be an organ, site, etc. of the object to be detected. The type of ultrasound tissue image is also different based on different ultrasound imaging modes, which may include B-image, C-image, D-image, etc., or other types of two-dimensional ultrasound tissue images or three-dimensional ultrasound tissue images. In this embodiment, after the ultrasound tissue image is acquired, the ultrasound tissue image is also displayed on the display 150.
In some embodiments, ultrasound tissue images may also be understood in a broad sense, and may include real-time ultrasound tissue images acquired with ultrasound imaging device 10, ultrasound tissue image video data over a period of time acquired with ultrasound imaging device 10, or a frame of ultrasound tissue images acquired with ultrasound imaging device 10, etc.
Step A200, determining a region of interest of the target tissue based on the ultrasonic tissue image.
The region of interest referred to herein may include: one of a pixel point in an ultrasound tissue image, a plurality of discrete distributed pixel points, a plurality of continuously distributed pixel points, an image region characterizing the entire ultrasound probe 110 scan region, and a plurality of discrete distributed image regions, etc.
The region of interest may be obtained based on system defaults, based on user input, and/or based on an image automatic segmentation process. For example, based on system defaults, an image region that characterizes the entire ultrasound probe 110 scan region or an image region that characterizes multiple consecutively distributed pixels of a portion of the ultrasound probe 110 scan region may be taken as the region of interest.
For another example, the region of interest is determined based on a selection instruction entered by a user in the acquired ultrasound tissue image using the operation control module. The operation control module may be a human-computer interaction device, such as a mouse, a keyboard, or a scroll wheel, or when the display 150 is a touch screen, the operation control module may be a gesture detection module, for detecting a selection instruction given by a user on the touch display screen.
Also for example, the identification of the region of interest may be based on an image automatic segmentation process that the system operates automatically. For example, after image automatic segmentation processing is performed in the obtained ultrasonic heart image, an image area or a partial image area of a tissue organ such as an arterial root vessel wall, a ventricular wall, or the like is identified.
Still further, the identification of the region of interest may also be a semi-automated process. For example, a target tissue region (such as a heart wall, a liver, a stomach wall, a blood vessel wall, and the like) is obtained based on an image automatic segmentation processing method of the system automatic operation, and then a selection instruction input by a user in the target tissue region by utilizing an operation control module is received so as to determine the region of interest. Also for example, based on the system default, an image area representing the entire scanning area of the ultrasonic probe 110 or an image area formed by a plurality of continuously distributed pixels representing a part of the scanning area of the ultrasonic probe 110 is taken as a target area, and then a selection instruction input by a user in the target area by using the operation control module is received to determine the aforementioned region of interest.
Step a300, controlling the ultrasound probe 110 to emit a second ultrasound wave to the region of interest to track a shear wave propagating within the region of interest, and receiving an ultrasound echo of the second ultrasound wave returned from the region of interest to obtain second echo data.
The shear wave is generated in the manner described in detail above. The location of the shear wave generation may be determined by default in the system or by the location of the region of interest.
In this step, shear waves may be generated inside the tissue by various methods, such as by external force vibration outside the tissue, or by transmitting acoustic radiation force pulses (ARFI, acoustic radiation force impulse) inside the tissue. Wherein the acoustic radiation force pulse may or may not be focused.
It will be appreciated that since the shear wave itself generated by the emitted acoustic radiation force pulses is of small amplitude, and since the shear wave will decay rapidly as it propagates, the intensity of the shear wave can be increased by emitting a series of acoustic radiation force pulses, or by widening the range of propagation of the shear wave, or by changing the waveform characteristics of the shear wave to increase the detection sensitivity, etc., thereby avoiding affecting imaging due to the decay of the shear wave.
Further, in one embodiment, multiple focusing pulses may be transmitted sequentially to the same measurement location to increase the intensity of the generated shear wave. The longitudinal (referring to the direction of the focused emission) and transverse (referring to the direction perpendicular to the focused emission) positions of the continuously emitted focused pulses can also be varied to widen the propagation range of the shear wave and cause the shear wave to propagate along a particular direction. Or, the pulse can be emitted at different transverse positions at the same time, so that two shear wave waveforms arriving at different times in sequence are overlapped, and the detection is convenient.
And step A400, obtaining the shear wave velocity in the region of interest according to the second echo data.
In some examples, step a400 may further comprise:
step A410, acquiring reference echo data. It will be appreciated that the reference echo data may be selected as desired. The reference pulse may be transmitted prior to propagation of the shear wave and echo data of the reference pulse may be used as reference echo data. The reference echo data is needed for cross-correlation comparison with the second echo data.
Step A420, cross-correlation comparison is performed between the second echo data of each position of the region of interest at different times and the reference echo data corresponding to the position, so as to obtain particle displacement data of different times at the position. Further, a displacement versus time curve at the location may be formed during which time the shear wave may go through the whole process of approaching, reaching and leaving the location, with a peak appearing in the corresponding curve. Because of pre-estimated chase detection, each transverse position can obtain a corresponding small displacement-time curve, but the corresponding moments of the curves are different, and the corresponding moments of adjacent positions may be partially overlapped. The position of the peak on the displacement-time curve corresponds to the moment when the shear wave reaches this position.
There are a number of calculation methods available for shear wave velocity, taking as an example the propagation of shear waves laterally inside tissue. For example, a cross-correlation comparison of displacement versus time curves corresponding to two different lateral positions at the same depth may result in a corresponding time difference between the two lateral positions that corresponds to the shear wave propagation time between the two lateral positions. The ratio of the distance between the lateral positions to the propagation time, i.e. the shear wave velocity between the two lateral positions.
For example, for a certain position, displacement data of each transverse position corresponding to two moments when the shear wave reaches the position are taken out, a displacement-transverse position curve of the two moments is formed, the two curves are subjected to cross correlation comparison, and the transverse position difference between the two moments can be obtained, wherein the position difference corresponds to the propagation distance of the shear wave between the two moments. The ratio of the propagation distance to the time difference between the two moments is the shear wave velocity near the position.
For example, the approximate calculation formula can be derived directly from the propagation equation of the wave as follows:
wherein C is s Indicating shear wave velocity, u z The longitudinal displacement data can be considered, the longitudinal speed data can also be used for calculation, x represents the transverse coordinate, and z represents the longitudinal coordinate. The above formula may also be transformed to the frequency domain for calculation.
It should be noted that other elastic measurement means may be used to obtain the shear wave velocity.
Step a500, controlling the ultrasound probe 110 to transmit a third ultrasound wave to the region of interest, and receiving an ultrasound echo of the third ultrasound wave returned from the region of interest to obtain third echo data.
And step A600, obtaining the longitudinal wave sound velocity in the region of interest according to the third echo data.
In some embodiments, the shear wave velocity and the longitudinal wave sound velocity may be perpendicular. Here, the vertical includes absolute vertical or near vertical. In practical applications, shear waves mostly propagate transversely in the tissue, while longitudinal wave ultrasonic waves corresponding to sound velocity mostly propagate from the surface of the tissue to the depth (also can be understood as propagating longitudinally in the tissue), so based on the perpendicular condition of the transverse propagation direction of the shear waves and the longitudinal propagation direction of the longitudinal wave ultrasonic waves in the tissue, the obtained shear wave velocity and the longitudinal wave sound velocity can be perpendicular correspondingly. Of course, reference to perpendicular in this application is merely illustrative as an example, and it is understood that the direction of propagation of shear wave and the direction of propagation of longitudinal wave ultrasound corresponding to the speed of sound may also be non-perpendicular within the tissue, e.g., the longitudinal wave ultrasound does not have to travel absolutely longitudinally within the tissue in the case of deflected emission, and therefore the shear wave speed and the speed of sound may also be non-perpendicular.
In some embodiments, as shown in fig. 3, step a600 may further include:
and step A6110, processing the third echo data by utilizing the first preset sound speeds to obtain multi-frame image matrix data corresponding to the first preset sound speeds one by one. The image matrix data may be image data or echo data after multi-frame beam forming, and the image matrix data is taken as image data for illustration.
Specifically, a plurality of first preset sound speeds may be preset, assuming that there are M first preset sound speeds. Processing the third echo data by utilizing each first preset sound velocity to obtain corresponding image data; that is, M-frame image data corresponding to M first preset sound speeds one-to-one can be obtained.
Step A6120, selecting first target data of preset conditions from multi-frame image matrix data.
When the image matrix data is image data, the considered preset condition may be one of the highest signal-to-noise ratio, the lowest bit error rate, the highest resolution, and the like. Alternatively, the preset condition may be that the value obtained by integrating various factors such as signal-to-noise ratio, bit error rate, resolution, etc. is the maximum. Alternatively, the preset condition may be set based on another parameter related to the image quality, which is not limited by the present invention. In other words, one frame of image data having the best quality can be selected from the plurality of frames of image data.
The preset condition is assumed to be the highest signal to noise ratio. As an example, selecting the first target data satisfying the preset condition may include: respectively carrying out spectrum analysis on the multi-frame image data to obtain a spectrum analysis result corresponding to the multi-frame image data; and determining one frame of image data with the highest signal-to-noise ratio from the spectrum analysis result corresponding to the multi-frame image data as the first target data. The spectrum analysis may refer to a specific process of spectrum analysis in the process of processing the signal, which is now known and possible in the future, and will not be described herein.
And step A6130, determining a first preset sound velocity corresponding to the first target data as a longitudinal wave sound velocity in the region of interest.
The above-described manner of obtaining the longitudinal wave sound velocity is simple and straightforward, but has a disadvantage in that accuracy is not high enough.
In other embodiments, as shown in fig. 4, step a600 may further include:
and step A6210, processing the third echo data by using a plurality of second preset sound speeds to obtain multi-frame image matrix data corresponding to the second preset sound speeds one by one.
This step is similar to step a6110 described above, and the first preset sound speed and the second preset sound speed may be the same or different.
And step A6220, selecting second target data meeting preset conditions from the multi-frame image matrix data.
This step is similar to the above-described step a6120, and when the image matrix data is image data, that is, one frame of image data having the best quality is selected from the plurality of frames of image data as the second target data.
Step a6230, determining a second preset sound speed corresponding to the selected second target data as a longitudinal wave sound speed of a reference region, the reference region being a region through which ultrasonic waves emitted to the target tissue propagate to the region of interest.
In some embodiments, the reference region is the area of the surface of the ultrasound probe 110 to the top of the region of interest. For example, as shown in fig. 5, where the outlined area represents the region of interest, and in addition, the probe surface and the top of the region of interest are shown in fig. 5, then the area from the probe surface to the top of the region of interest is the reference area.
For convenience of description, it may be assumed that the depth of the reference region is 0 to h1, and the depth of the region of interest is h1 to h2, wherein h2 is greater than h1.
And A6240, obtaining the longitudinal wave sound velocity in the region of interest based on the longitudinal wave sound velocity of the reference region.
In some embodiments, the longitudinal wave sound velocity of the reference area may be utilized to remove the portion of the third echo data corresponding to the reference area, then the remaining third echo data is processed by using a plurality of first preset sound velocities to obtain multi-frame image matrix data corresponding to the plurality of first preset sound velocities one to one, and then step a6120 and step a6130 are performed similarly, that is, the first target data meeting the condition is determined from the multi-frame image matrix data, and the longitudinal wave sound velocity of the region of interest is obtained according to the first preset sound velocity corresponding to the first target data.
Specifically, assuming that the longitudinal wave sound velocity of the reference region is V2, the portion of the third echo data reflected by the reference region is received in time 0 to 2×h1/V2. Subsequently, the portion of the third echo data received after the time 2×h1/V2 may be processed with a plurality of first preset sound speeds.
Wherein it can be appreciated that the data amount of the processed third echo data is also different using the different first preset sound speeds. For example, if the first preset sound speed is V11, the third echo data received in the time of 2×h1/V2 to 2×h2/V11 needs to be processed; if the first preset sound speed is used as V12, the third echo data received in the time of 2×h1/V2 to 2×h2/V12 needs to be processed.
The mode of processing the longitudinal wave sound velocity in the divided regions can obtain more accurate longitudinal wave sound velocity even if the target tissue is uneven.
In this application, other means for measuring the velocity of longitudinal wave may be used to obtain the velocity of longitudinal wave. For example, the average longitudinal wave sound velocity may also be corrected by analysis of spatial frequency components of a single two-dimensional image to determine the longitudinal wave sound velocity value that yields the best quality of lateral focus, best image lateral resolution. The longitudinal wave sound velocity value obtained by estimation based on the whole two-dimensional image is global average longitudinal wave sound velocity in the whole area from the surface of the probe to the maximum depth of the image.
In some embodiments, at least one of the shear wave velocity and the longitudinal wave sound velocity may also be displayed, thereby allowing the user to know the shear wave velocity and/or the longitudinal wave sound velocity in the region of interest.
And step A700, calculating at least one of a Poisson coefficient, a Latin coefficient and a bulk modulus according to the shear wave speed and the longitudinal wave sound velocity.
In some embodiments, poisson's coefficient may be calculated using the following formula:
wherein v is poisson coefficient, C s For shear wave velocity, C P Is the longitudinal wave sound velocity.
In some embodiments, the prune coefficient includes a first parameter and a second parameter, which may be calculated using the following formulas:
wherein lambda is a first parameter in the Lame coefficient, mu is a second parameter in the Lame coefficient, rho is the density of the target tissue, C s For shear wave velocity, C P Is the longitudinal wave sound velocity.
In some embodiments, the bulk modulus can be calculated using the following formula:
where ρ is the density, k, of the target tissue v For bulk modulus, C s For shear wave velocity, C P Is the longitudinal wave sound velocity.
In the above steps a100 to a600, the shear wave velocity and the longitudinal wave velocity are obtained separately, and intuitively, in some embodiments, the user performs the B-mode imaging detection first, then the user may observe the position, the morphology, etc. of the target tissue in real time according to the B-mode image, adjust the ultrasound probe 110 to a suitable angle until a suitable tangential plane is obtained, confirm the detected region of interest, transmit the ultrasound elastic scan sequence again, calculate the shear wave velocity according to the echo data, transmit the ultrasound longitudinal wave velocity measurement scan sequence again, receive the echo data and calculate the longitudinal wave velocity, and finally calculate the approximate poisson coefficient or the praise coefficient or the bulk modulus according to the shear wave velocity and the longitudinal wave velocity.
In other embodiments, the shear wave velocity and the longitudinal wave sound velocity may also be obtained by echo data of the same ultrasound scanning sequence, that is, the shear wave velocity may be obtained by second echo data, or multiple frames of image matrix data may be generated by the second echo data, and then the longitudinal wave sound velocity of the region of interest may be obtained according to the multiple frames of image matrix data.
In other embodiments, the longitudinal wave sound velocity and the ultrasonic tissue image may also be obtained by echo data of the same ultrasonic scanning sequence, after the first ultrasonic wave is emitted to the target tissue, an ultrasonic tissue image is generated according to the first echo data of the first ultrasonic wave, the region of interest is determined according to the ultrasonic tissue image, and the longitudinal wave sound velocity in the region of interest may also be obtained according to the first echo data. And transmitting a second ultrasonic wave to the region of interest to track the shear wave in the region of interest, and obtaining the shear wave speed of the region of interest according to the second echo data of the second ultrasonic wave.
After obtaining the mechanical parameters such as poisson's coefficient, the prune coefficient, and the bulk modulus, the obtained mechanical parameters may be displayed by the display 150. In some embodiments, the ultrasound tissue image and the mechanical parameters may also be displayed simultaneously, such as in FIG. 6, the ultrasound tissue image and the Poisson's coefficients.
In some embodiments, in the process of acquiring poisson's coefficient, as shown in fig. 7, the steps may also be performed:
and step B100, deforming the region of interest.
In this embodiment, the region of interest may be deformed by pressing it with the ultrasound probe 110. In embodiments, the deformation of the region of interest may also be performed in other ways that exist.
And step B200, obtaining the strain of the region of interest in the deformation process according to the second echo data in the deformation process of the region of interest.
The strain of the region of interest may be obtained by referring to the strain elastic measurement method described above, and the second echo data of the region of interest before and after compression may be obtained, so as to calculate the strain of the region of interest.
In some embodiments, after determining the region of interest, the ultrasound probe 110 may transmit only the second ultrasound wave to the region of interest, and the second echo data is the echo data of the region of interest, from which the strain of the region of interest may be calculated.
In other embodiments, the user may control the ultrasound probe 110 to emit the second ultrasound wave to the target region including the region of interest, and the second echo data is echo data of the target region, and the strain of the target region may be calculated according to the second echo data, and then the region of interest is identified from the target region, and the strain of the region of interest is extracted from the strain of the target region according to the identified region of interest.
And step B300, acquiring poisson coefficients of the region of interest in the deformation process.
The poisson coefficient may be obtained in this step by referring to the descriptions in steps a100 to a700, that is, the poisson coefficient of the region of interest is obtained at the same time when the strain of the region of interest is obtained.
And step B400, generating a Poisson coefficient change curve of Poisson coefficient changing along with the strain according to the strain and Poisson coefficient of the region of interest in the deformation process.
And step B500, displaying a Poisson coefficient variation curve to represent the permeability of the region of interest.
When pressure is applied to the target tissue, the target tissue is a composite material consisting of liquid and solid, so that the distribution of liquid phases and solid phases in the target tissue can be influenced in the pressing process, and the poisson coefficient of the target tissue is changed. When the permeability of the target tissue is large, the Poisson coefficient is changed greatly in the process of applying pressure, and conversely, the Poisson coefficient is changed slightly, so that the Poisson coefficient can reflect the permeability of the target tissue along with the change of strain or the slope of a time-varying curve. As shown in fig. 8, poisson coefficients of 2 different materials change along with the strain in the pressing process, the poisson coefficients of the materials with high permeability change along with the strain greatly (as shown by a curve S1 in the drawing), the poisson coefficients of the materials with low permeability change along with the strain slightly (as shown by a curve S2 in the drawing), and therefore, the poisson coefficient measurement can directly reflect the permeability of tissues and has very important significance for poisson coefficient measurement. By displaying the poisson coefficient change curve, the permeability of the target tissue can be acquired in an auxiliary manner, so that whether edema exists in the target tissue is judged.
In some embodiments, the region of interest may include more than one region of interest, and each region of interest may have a poisson coefficient corresponding to the poisson coefficient, and referring to fig. 9, fig. 9 includes two regions of interest (left square and circular frames) and two poisson coefficient curves, where the two poisson coefficient curves are superimposed on the same coordinate system, so that a user may compare the permeability of the two regions of interest, and in addition, the two poisson coefficient curves are different in color. In addition, in fig. 9, the region of interest is marked in the ultrasound tissue map, and the marking manner of the region of interest is associated with the display manner of the poisson coefficient change curve corresponding to the region of interest, so that a user can intuitively distinguish which region of interest corresponds to which poisson coefficient change curve, for example, in fig. 9, the border color of the region of interest is the same as the color of the poisson coefficient change curve corresponding to the region of interest, and in other embodiments, the border of the region of interest and the poisson coefficient change curve corresponding to the region of interest can be displayed through the same line type. Alternatively, in fig. 9, the shape of the border of the region of interest is the same as the shape of the marker points of the poisson's coefficient change curve.
The poisson's coefficient variation curve is understood in a broad sense, and in fig. 9, the poisson's coefficient variation curve is a scatter diagram, and in other embodiments, a smooth curve or various charts with broken lines may be used.
In the above embodiment, the shear wave velocity and the longitudinal wave sound velocity in the target tissue are obtained by referring to the ultrasonic imaging technology, so that the poisson coefficient, the Law Mei Jishu, the bulk modulus and other mechanical parameters can be conveniently calculated, and the permeability of the target tissue is intuitively reflected by the poisson coefficient change curve
Reference is made to various exemplary embodiments herein. However, those skilled in the art will recognize that changes and modifications may be made to the exemplary embodiments without departing from the scope herein. For example, the various operational steps and components used to perform the operational steps may be implemented in different ways (e.g., one or more steps may be deleted, modified, or combined into other steps) depending on the particular application or taking into account any number of cost functions associated with the operation of the system.
Additionally, as will be appreciated by one of skill in the art, the principles herein may be reflected in a computer program product on a computer readable storage medium preloaded with computer readable program code. Any tangible, non-transitory computer readable storage medium may be used, including magnetic storage devices (hard disks, floppy disks, etc.), optical storage devices (CD-ROMs, DVDs, blu-Ray disks, etc.), flash memory, and/or the like. These computer program instructions may be loaded onto a general purpose computer, special purpose computer, or other programmable data processing apparatus to produce a machine, such that the instructions which execute on the computer or other programmable data processing apparatus create means for implementing the functions specified. These computer program instructions may also be stored in a computer-readable memory that can direct a computer or other programmable data processing apparatus to function in a particular manner, such that the instructions stored in the computer-readable memory produce an article of manufacture including means which implement the function specified. The computer program instructions may also be loaded onto a computer or other programmable data processing apparatus to cause a series of operational steps to be performed on the computer or other programmable apparatus to produce a computer implemented process such that the instructions which execute on the computer or other programmable apparatus provide steps for implementing the functions specified.
While the principles herein have been shown in various embodiments, many modifications of structure, arrangement, proportions, elements, materials, and components, which are particularly adapted to specific environments and operative requirements, may be used without departing from the principles and scope of the present disclosure. The above modifications and other changes or modifications are intended to be included within the scope of this document.
The foregoing detailed description has been described with reference to various embodiments. However, those skilled in the art will recognize that various modifications and changes may be made without departing from the scope of the present disclosure. Accordingly, the present disclosure is to be considered as illustrative and not restrictive in character, and all such modifications are intended to be included within the scope thereof. Also, advantages, other advantages, and solutions to problems have been described above with regard to various embodiments. The benefits, advantages, solutions to problems, and any element(s) that may cause any benefit, advantage, or solution to occur or become more pronounced are not to be construed as a critical, required, or essential feature. The terms "comprises," "comprising," or any other variation thereof, are intended to cover a non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements does not include only those elements but may include other elements not expressly listed or inherent to such process, method, system, article, or apparatus. Furthermore, the term "couple" and any other variants thereof are used herein to refer to physical connections, electrical connections, magnetic connections, optical connections, communication connections, functional connections, and/or any other connection.
Those skilled in the art will recognize that many changes may be made to the details of the above-described embodiments without departing from the underlying principles of the invention. Accordingly, the scope of the invention should be determined from the following claims.
Claims (20)
1. An ultrasonic measurement method, comprising:
controlling an ultrasonic probe to emit first ultrasonic waves to target tissues, receiving ultrasonic echoes of the first ultrasonic waves to obtain first echo data, and generating ultrasonic tissue images of the target tissues according to the first echo data;
determining a region of interest of the target tissue based on the ultrasound tissue image;
controlling an ultrasonic probe to emit a second ultrasonic wave to the region of interest to track a shear wave propagating in the region of interest, and receiving an ultrasonic echo of the second ultrasonic wave returned from the region of interest to obtain second echo data;
controlling an ultrasonic probe to emit third ultrasonic waves to the region of interest, and receiving ultrasonic echoes of the third ultrasonic waves returned from the region of interest to obtain third echo data;
obtaining shear wave velocity in the region of interest according to the second echo data, and obtaining longitudinal wave sound velocity in the region of interest according to the third echo data;
And calculating at least one of a poisson coefficient, a Lawster coefficient and a bulk modulus according to the shear wave speed and the longitudinal wave sound velocity.
2. The method of claim 1, wherein said deriving a longitudinal wave speed of sound within the region of interest from the third echo data comprises:
processing the third echo data by using a plurality of first preset sound speeds to obtain multi-frame image matrix data corresponding to the first preset sound speeds one by one;
selecting first target data meeting preset conditions from the multi-frame image matrix data;
and determining a first preset sound speed corresponding to the first target data as a longitudinal wave sound speed in the region of interest.
3. The method of claim 1, wherein said deriving a longitudinal wave speed of sound within the region of interest from the third echo data comprises:
processing the third echo data by using a plurality of second preset sound speeds to obtain multi-frame image matrix data corresponding to the second preset sound speeds one by one;
selecting second target data meeting preset conditions from the multi-frame image matrix data;
determining a preset sound speed corresponding to the second target data as a longitudinal wave sound speed of a reference area, wherein the reference area is an area through which ultrasonic waves emitted to the target tissue propagate to the region of interest;
And obtaining the longitudinal wave sound velocity in the region of interest based on the longitudinal wave sound velocity of the reference region.
4. An ultrasonic measurement method, comprising:
controlling an ultrasonic probe to emit first ultrasonic waves to target tissues, receiving ultrasonic echoes of the first ultrasonic waves to obtain first echo data, and generating ultrasonic tissue images of the target tissues according to the first echo data;
determining a region of interest of the target tissue based on the ultrasound tissue image;
controlling an ultrasonic probe to emit a second ultrasonic wave to the region of interest to track a shear wave propagating in the region of interest, and receiving an ultrasonic echo of the second ultrasonic wave returned from the region of interest to obtain second echo data;
obtaining shear wave velocity in the region of interest according to the second echo data, and obtaining longitudinal wave sound velocity in the region of interest according to the second echo data;
and calculating at least one of a poisson coefficient, a Lawster coefficient and a bulk modulus according to the shear wave speed and the longitudinal wave sound velocity.
5. The method of claim 4, wherein said deriving a longitudinal wave speed of sound within said region of interest from said second echo data comprises:
Processing the second echo data by using a plurality of first preset sound speeds to obtain multi-frame image matrix data corresponding to the first preset sound speeds one by one;
selecting first target data meeting preset conditions from the multi-frame image matrix data;
and determining a first preset sound speed corresponding to the first target data as a longitudinal wave sound speed in the region of interest.
6. The method of claim 4, wherein said deriving a longitudinal wave speed of sound within said region of interest from said second echo data comprises:
processing the second echo data by using a plurality of second preset sound speeds to obtain multi-frame image matrix data corresponding to the second preset sound speeds one by one;
selecting second target data meeting preset conditions from the multi-frame image matrix data;
determining a preset sound speed corresponding to the second target data as a longitudinal wave sound speed of a reference area, wherein the reference area is an area through which ultrasonic waves emitted to the target tissue propagate to the region of interest;
and obtaining the longitudinal wave sound velocity in the region of interest based on the longitudinal wave sound velocity of the reference region.
7. An ultrasonic measurement method, comprising:
Controlling an ultrasonic probe to emit first ultrasonic waves to target tissues, receiving ultrasonic echoes of the first ultrasonic waves to obtain first echo data, and generating ultrasonic tissue images of the target tissues according to the first echo data;
determining a region of interest of the target tissue based on the ultrasound tissue image;
obtaining longitudinal wave sound velocity in the region of interest according to the first echo data;
controlling an ultrasonic probe to emit second ultrasonic waves to the region of interest, receiving ultrasonic echoes of the second ultrasonic waves returned from the region of interest to obtain second echo data, and obtaining shear wave speeds in the region of interest according to the second echo data;
and calculating at least one of a poisson coefficient, a Lawster coefficient and a bulk modulus according to the shear wave speed and the longitudinal wave sound velocity.
8. The method of claim 7, wherein the deriving a longitudinal wave speed of sound within the region of interest from the first echo data comprises:
processing the first echo data by using a plurality of first preset sound speeds to obtain multi-frame image matrix data corresponding to the first preset sound speeds one by one;
Selecting first target data meeting preset conditions from the multi-frame image matrix data;
and determining a first preset sound speed corresponding to the first target data as a longitudinal wave sound speed in the region of interest.
9. The method of claim 7, wherein the deriving a longitudinal wave speed of sound within the region of interest from the first echo data comprises:
processing the first echo data by using a plurality of second preset sound speeds to obtain multi-frame image matrix data corresponding to the second preset sound speeds one by one;
selecting second target data meeting preset conditions from the multi-frame image matrix data;
determining a preset sound speed corresponding to the second target data as a longitudinal wave sound speed of a reference area, wherein the reference area is an area through which ultrasonic waves emitted to the target tissue propagate to the region of interest;
and obtaining the longitudinal wave sound velocity in the region of interest based on the longitudinal wave sound velocity of the reference region.
10. The method of any one of claims 1, 4, and 7, wherein calculating poisson's coefficient from the shear wave velocity and the longitudinal wave sound velocity comprises: poisson coefficients were calculated using the following formula:
Wherein v is poisson coefficient, C s For shear wave velocity, C P Is the velocity of sound of longitudinal waves; and/or
The plum blossom coefficient comprises a first parameter and a second parameter, and is obtained by calculation according to the shear wave speed and the longitudinal wave sound velocity, and the plum blossom coefficient comprises: the first and second parameters are calculated using the following formulas:
wherein lambda is a first parameter in the Lame coefficient, mu is a second parameter in the Lame coefficient, rho is the density of the target tissue, C s For shear wave velocity, C P Is the velocity of sound of longitudinal waves; and/or
Calculating to obtain bulk modulus according to the shear wave speed and the longitudinal wave sound velocity, wherein the method comprises the following steps: the bulk modulus was calculated using the following formula:
where ρ is the density, k, of the target tissue v For bulk modulus, C s For shear wave velocity, C P Is the longitudinal wave sound velocity.
11. The method of any one of claims 1, 4, and 7, wherein the method further comprises: displaying at least one of the poisson's coefficient, the praise coefficient and the bulk modulus.
12. The method of any one of claims 1, 4, and 7, wherein the method further comprises: displaying the shear wave velocity and/or the longitudinal wave sound velocity.
13. The method of any one of claims 1, 4, and 7, wherein the method further comprises:
Deforming the region of interest;
in the deformation process of the region of interest, obtaining the strain of the region of interest in the deformation process according to the second echo data;
acquiring a poisson coefficient of the region of interest in the deformation process;
generating a Poisson coefficient change curve of the Poisson coefficient changing along with the strain according to the strain and Poisson coefficient of the region of interest in the deformation process;
displaying the Poisson coefficient variation curve to represent the permeability of the region of interest.
14. The method of claim 13, wherein when the regions of interest include at least two, each of the regions of interest has a corresponding poisson's coefficient change curve, the method further comprising:
superposing different poisson coefficient change curves on the same coordinate system;
displaying different poisson curves in the same coordinate system.
15. The method of claim 14, wherein the color and/or curve type of the poisson's coefficient change curves are different for different ones of the poisson's coefficient change curves in the same coordinate system.
16. The method of any one of claims 13 to 15, wherein the method further comprises: and determining the region of interest based on a selection instruction of the region of interest input by a user for the ultrasonic tissue image, marking the region of interest in the ultrasonic tissue image, and associating the marking mode of the region of interest with the display mode of the poisson change curve corresponding to the region of interest.
17. The method of claim 16, wherein the marking of the region of interest is associated with a display of the poisson change curve corresponding to the region of interest, comprising:
the color of the region of interest is marked to be the same as the color of the poisson variation curve corresponding to the region of interest.
18. The method of claim 13, wherein the controlling the ultrasound probe to transmit a second ultrasound wave to the region of interest to track shear waves propagating within the region of interest, receiving an ultrasound echo of the second ultrasound wave returned from the region of interest to obtain second echo data, comprises:
controlling an ultrasonic probe to emit a second ultrasonic wave to a target region containing the region of interest to track a shear wave propagating in the target region, and receiving an ultrasonic echo of the second ultrasonic wave returned from the target region to obtain second echo data;
the step of deforming the region of interest, in the process of deforming the region of interest, obtaining the strain of the region of interest in the process of deforming according to the second echo data, includes:
And deforming the target region, obtaining the strain of the target region in the deformation process according to the second echo data in the deformation process of the target region, and extracting the strain of the region of interest from the strain of the target region in the deformation process.
19. The method of any one of claims 1, 4, and 7, wherein the shear wave velocity and the longitudinal wave sound velocity are perpendicular.
20. An ultrasonic imaging apparatus, comprising:
an ultrasonic probe for transmitting ultrasonic waves and receiving echo data of the ultrasonic waves;
a memory for storing a program;
a processor for implementing the method of any one of claims 1 to 19 by executing a program stored in the memory.
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