WO2019075697A1 - 一种超声弹性测量装置及弹性对比测量方法 - Google Patents

一种超声弹性测量装置及弹性对比测量方法 Download PDF

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WO2019075697A1
WO2019075697A1 PCT/CN2017/106897 CN2017106897W WO2019075697A1 WO 2019075697 A1 WO2019075697 A1 WO 2019075697A1 CN 2017106897 W CN2017106897 W CN 2017106897W WO 2019075697 A1 WO2019075697 A1 WO 2019075697A1
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elastic
interest
region
ultrasonic
result
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French (fr)
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李双双
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Shenzhen Mindray Bio Medical Electronics Co Ltd
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Shenzhen Mindray Bio Medical Electronics Co Ltd
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Priority to PCT/CN2017/106897 priority Critical patent/WO2019075697A1/zh
Priority to CN201780088411.2A priority patent/CN110418609B/zh
Priority to CN202110315553.6A priority patent/CN113180735B/zh
Publication of WO2019075697A1 publication Critical patent/WO2019075697A1/zh
Priority to US16/852,012 priority patent/US12089994B2/en
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/5215—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data
    • A61B8/5238—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data for combining image data of patient, e.g. merging several images from different acquisition modes into one image
    • A61B8/5246—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data for combining image data of patient, e.g. merging several images from different acquisition modes into one image combining images from the same or different imaging techniques, e.g. color Doppler and B-mode
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/46—Ultrasonic, sonic or infrasonic diagnostic devices with special arrangements for interfacing with the operator or the patient
    • A61B8/461—Displaying means of special interest
    • A61B8/463—Displaying means of special interest characterised by displaying multiple images or images and diagnostic data on one display
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/46—Ultrasonic, sonic or infrasonic diagnostic devices with special arrangements for interfacing with the operator or the patient
    • A61B8/467—Ultrasonic, sonic or infrasonic diagnostic devices with special arrangements for interfacing with the operator or the patient characterised by special input means
    • A61B8/469—Ultrasonic, sonic or infrasonic diagnostic devices with special arrangements for interfacing with the operator or the patient characterised by special input means for selection of a region of interest
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/48—Diagnostic techniques
    • A61B8/485—Diagnostic techniques involving measuring strain or elastic properties
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/5215—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data
    • A61B8/5223—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data for extracting a diagnostic or physiological parameter from medical diagnostic data
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/54—Control of the diagnostic device

Definitions

  • the invention relates to a medical device, in particular to an ultrasonic elastic measuring device and an elastic contrast measuring method.
  • Ultrasound elastography is one of the hotspots of clinical research in recent years. Because it mainly reflects the elasticity or softness of tissue, it is more and more applied in the auxiliary detection of cancerous lesions, benign and malignant discrimination, and evaluation of prognosis.
  • Ultrasound elastography mainly reflects the softness and hardness of tissue by imaging the elasticity-related parameters in the region of interest.
  • elastography In the past two decades, there have been many different methods of elastography, such as quasi-static elastography based on strain caused by probe pressing tissue, elastography or elastic measurement based on acoustic radiation to generate shear waves, and shear based on external vibration. Instantaneous elastography of waves, etc.
  • Either elastography method is calculated on the assumption that the target organization is an isotropic medium.
  • the characteristics or extent of this tissue anisotropy may provide new information to the physician.
  • the present application provides an ultrasonic elastic measuring device and an elastic contrast measuring method, which can measure anisotropy parameters of biological tissues by an ultrasonic elastic measuring device.
  • an ultrasonic elastic measuring device comprising:
  • An ultrasound probe comprising at least one transducer, the first portion of the transducer being for transmitting ultrasound to the biological tissue for the purpose of detecting an elastic result of the same region of interest to form at least two different regions in the region of interest a second portion of the transducer for receiving ultrasound echoes returned by biological tissue, the ultrasound echo comprising the region of interest Two ultrasonic echoes of different cross sections;
  • a transmit/receive sequence control module for generating a transmit sequence for controlling the corresponding transducer to transmit ultrasonic waves and a receive sequence for controlling the corresponding transducer to receive the ultrasonic echo;
  • An echo processing module for processing ultrasonic echoes
  • a transmitting and receiving module electrically connected to the ultrasound probe, the transmit/receive sequence control module and the echo processing module, respectively, for transmitting the transmit sequence generated by the transmit/receive sequence control module to the ultrasound probe, and the ultrasound received by the ultrasound probe
  • the echo is transmitted to the echo processing module
  • a data processing module which is coupled to the echo processing module, the data processing module includes an elastic calculation module, and the elastic calculation module is configured to calculate the elasticity of the region of interest in each section according to the ultrasonic echoes of at least two different sections respectively result.
  • an embodiment provides an elastic contrast measurement method, including:
  • the first elastic result and the second elastic result are output.
  • an embodiment provides an elastic contrast measurement method, including:
  • the calculation in response to the elastic result outputs at least one of the following results:
  • an ultrasonic elastic measuring device including:
  • An ultrasound probe comprising at least one transducer, a first portion of the transducer for transmitting ultrasound to the region of interest for the purpose of detecting an elastic result of the same region of interest to form at least two regions in the region of interest a different section, a second portion of the transducer for receiving ultrasonic echoes returned by biological tissue, the ultrasonic echo comprising ultrasonic echoes of at least two different cross sections of the region of interest;
  • a transmitting and receiving module electrically connected to the ultrasonic probe for controlling the ultrasonic probe to emit the first ultrasonic wave to the region of interest when the biological tissue is deformed, and receiving the echo of the first ultrasonic wave to obtain the first echo signal
  • the ultrasonic probe is controlled to emit a second ultrasonic wave to the region of interest, and the echo of the second ultrasonic wave is received to obtain a second echo signal
  • a data processing module configured to obtain, according to the first echo signal, a first elastic result corresponding to the first cross section in the region of interest; and obtain, according to the second echo signal, different from the region of interest
  • a second elastic result corresponding to the second section of the first section outputs the first elastic result and the second elastic result.
  • an ultrasonic elastic measuring device including:
  • An ultrasound probe comprising at least one transducer for transmitting ultrasound waves to a region of interest, forming a first section and a second section in the same region of interest;
  • a data processing module configured to calculate a first elastic result corresponding to the region of interest according to the first cross section, calculate a second elastic result corresponding to the region of interest according to the second cross section, and calculate a sense according to the first elastic result and the second elastic result
  • the anisotropic parameter of the region of interest in response to the calculation of the elastic result, outputs at least one of the following results:
  • the anisotropic parameter of the region of interest is calculated by using the detected elastic parameter, the anisotropy degree of the region of interest is measured by the anisotropic parameter, and the anisotropic parameter is output, and the doctor diagnoses the lesion or Provide more reference information to the doctor during the process of judging the clinical prognosis.
  • Figure 1 is a schematic structural view of an ultrasonic elastic measuring device
  • Figure 2 is a schematic cross-sectional view
  • Figure 3 is a flow chart for calculating anisotropic parameters in an embodiment
  • Figure 4 is a schematic diagram of displacement detection during strain elastic imaging
  • Figure 5 is a schematic view of different cross-sectional distributions
  • Figure 6 is another schematic diagram of different cross-sectional distributions
  • Figure 7 is a flow chart showing an anisotropic parameter calculation in another embodiment
  • Figure 8 is a schematic diagram of a shear wave generated by an ultrasonic probe
  • Figure 9 is a schematic diagram of shear wave detection.
  • the elastic parameters of different sections of the biological tissue region of interest are measured by the ultrasonic device, and the anisotropic parameters of the region of interest are calculated according to the elastic parameters of the different sections.
  • the anisotropy parameter is used to reflect the degree of tissue anisotropy in a certain part. Anisotropy means that the characteristics of a tissue change with the direction, and exhibit different characteristics in different directions. Therefore, each The anisotropic parameter is used to characterize the biological tissue (eg, the biological tissue can be the anatomical structure of the heart, muscle, blood vessels, etc. of a human or animal) that exhibits differential properties in different directions as all changes with direction.
  • the anisotropic parameter includes a ratio of characteristics corresponding to at least two directions, a difference between characteristics corresponding to at least two directions, a square of a ratio of ratios of characteristics corresponding to at least two directions, and the like, or The anisotropic parameter may also be a secondary statistical analysis amount of the characteristic obtained correspondingly in at least two directions.
  • the elastic measurement combined with the ultrasonic device will be specifically described below as a manner of obtaining the aforementioned characteristics.
  • the anisotropic parameter may include a comparative analysis result of a plurality of elastic parameters obtained along different cross sections, for example, a ratio between a plurality of elastic parameters, a difference between a plurality of elastic parameters, and a plurality of elastic parameters The ratio between the analysis and the like is the second statistical analysis.
  • the ultrasonic device is referred to as an ultrasound elastic measuring device, but those skilled in the art will appreciate that the ultrasonic device may also add other functions, such as performing a general ultrasonic diagnosis, generating a B-mode ultrasound image, a C-mode ultrasound image, or Doppler ultrasound images and more.
  • the elastic measurement method mentioned herein may be one or a combination of one or more of a vibration elastic measurement method based on external force vibration, a shear wave measurement method based on sound amplitude radiation, and a strain elastic measurement method.
  • the vibration elastic measurement method based on the external force vibration generates a shear wave into the tissue by the external force vibration, and then reflects the inter-tissue by generating a shear wave propagation inside the biological tissue and detecting its propagation parameters (such as the propagation speed).
  • the difference in hardness For an isotropic elastic structure, the following relationship exists between the shear wave propagation velocity C s and the tissue elastic modulus E: Young's modulus (where ⁇ is the tissue density). That is to say, there is a one-to-one correspondence between the shear wave velocity and the elastic modulus.
  • the acoustic wave-based shear wave measurement method generates shear wave propagation inside the biological tissue by ultrasonic sound radiation force, and then generates shear wave propagation inside the biological tissue and detects its propagation parameters (such as propagation speed). Methods to reflect differences in hardness between biological tissues.
  • the shear wave propagation velocity C s and the tissue elastic modulus E Young's modulus (where ⁇ is the tissue density). That is to say, there is a one-to-one correspondence between the shear wave velocity and the elastic modulus.
  • the strain elastic measurement method has the following basic principles:
  • the probe is slightly pressed against the target biological tissue or a certain pressure is applied to the tissue by the body's own breathing, vascular pulsation, etc., and ultrasonic echo signals are obtained before and after compression, and when the biological tissue is compressed, an edge will be generated in the biological tissue.
  • the strain in the compression direction if the Young's modulus distribution in the biological tissue is not uniform, the strain distribution in the biological tissue will also be different, and then the strain information of the biological tissue will be detected by some methods, and then the strain, the strain rate, etc.
  • the parameters related to tissue elasticity are calculated and output, which indirectly reflects the difference in elasticity between different tissues in the pressure-applying area.
  • Young's modulus E is a parameter related to tissue hardness, and the higher the Young's modulus, the greater the tissue hardness.
  • the ultrasonic probe generates deformation by pressing the biological tissue to detect the elastic result of the region of interest, and the calculated elastic result is a quasi-static elastic parameter of the region of interest.
  • the quasi-static elastic parameter is the strain or strain rate.
  • the elastic measurement method is not limited to the above-mentioned elastic measurement method, and may be other elastic measurement methods based on ultrasonic elastography.
  • the ultrasonic elastic measuring apparatus 100 includes an ultrasonic probe 101 , a transmitting/receiving sequence control module 102 , a transmitting and receiving module 103 , an echo processing module 104 , a data processing module 105 , and a display module 106 .
  • the transmit/receive sequence control module 102 is coupled to the ultrasound probe 101 via the transmit and receive module 103.
  • the ultrasound probe 101 is coupled to the echo processing module 104 via the transmit and receive module 103.
  • the output of the echo processing module 104 and the data processing module 105 is connected, and the output of the data processing module 105 is connected to the display module 106.
  • the ultrasound probe 101 includes at least one transducer for transmitting ultrasound waves based on electrical signals or converting received ultrasound waves into electrical signals.
  • the plurality of transducers are arranged in a row, such as a line array probe; or, the plurality of transducers are arranged in a two-dimensional matrix, such as a two-dimensional ultrasound probe or a surface array probe.
  • a portion of the transducer of the ultrasound probe 101 is used to transmit ultrasound waves to the biological tissue 108, and another portion of the transducer is used to receive ultrasound echoes returned by the biological tissue.
  • the transmit/receive sequence control module 102 is configured to generate a transmit sequence and a receive sequence for providing a number of transducers for transmitting in the ultrasound probe 101 and parameters for transmitting ultrasound to the biological tissue (eg, amplitude, according to instructions of the control module 107)
  • the frequency, the number of waves, the wave angle, the wave pattern, etc., the received sequence is used to provide the number of transducers received in the ultrasound probe 101 and the parameters (eg, received angle, depth, etc.) of the echoes it receives.
  • the transmission sequence and the reception sequence are also different for different purposes, or for generating images.
  • the corresponding transducer in the ultrasonic probe 101 emits ultrasonic waves of a certain amplitude, frequency and angle into the biological tissue 108 according to the emission sequence, and the ultrasonic wave forms a cross section in the biological tissue 108. 109. Simultaneously receiving the ultrasonic echo of the section.
  • different cross sections can be formed by the user manually changing the placement direction or position of the ultrasonic probe 101, and different cross sections can be formed by automatically changing the transducers, which will be described later in detail.
  • the transmitting and receiving module 103 is connected between the ultrasound probe and the transmit/receive sequence control module 102 and the echo processing module 104 for transmitting the transmit sequence of the transmit/receive sequence control module 102 to the ultrasound probe 101 according to the control of the control module 107. And transmitting the ultrasonic echo received by the ultrasonic probe 101 to the echo processing module 104.
  • the echo processing module 104 is configured to process ultrasonic echoes, such as filtering, amplifying, beamforming, etc., the ultrasonic echoes.
  • the data processing module 105 receives the echo signals processed by the output of the echo processing module 104, and uses the correlation algorithm to obtain the required parameters or images.
  • the data processing module 105 includes an elastic calculation module 1051, and further includes an anisotropic calculation module 1052.
  • the elastic calculation module 1051 is configured to calculate elastic results corresponding to the respective sections according to the ultrasonic echoes of the at least two different sections, and further generate various elastic distribution image data or various charts and figures according to the elastic results.
  • the anisotropy calculation module 1052 is configured to calculate an anisotropic parameter of a region of interest in the biological tissue or biological tissue based on the at least two elastic results.
  • the inductive regions referred to herein may be part or all of the biological tissue.
  • the determination of the region of interest may be automatically generated based on the system or may be based on the user making a selection on the ultrasound image.
  • the data processing module further generates ultrasound image data from the ultrasound echoes and outputs to the display module display, the region of interest being selected by the user on the ultrasound image.
  • the display module 106 serves as an output module, and the display module 106 receives various visualization data output by the data processing module 105, and displays various images, graphics, charts, characters or data on the display interface, including anisotropic parameters and/or various Elastic image.
  • the data processing module 105 may directly output the calculated elastic result to the display module for display, and the user may compare the elastic result according to different sections. The degree of anisotropy of the region of interest.
  • the output module may also be an audio play module, and the audio signal output by the data processing module 105 is played out by sound.
  • the display module can be a touch display screen, Or multiple displays and so on.
  • the output module outputs at least one of the following results in response to the calculated elastic result:
  • the different cross sections described above are mutually parallel sections or intersecting sections in the region of interest.
  • the elastic result used to calculate the tissue anisotropy parameter may be an elastic parameter obtained in the process of detecting the strain of the biological tissue, or may be an elastic parameter obtained in the process of detecting the shear wave. The details are described below through different embodiments.
  • the ultrasonic elastic measuring device 100 detects the strains of two different sections of the biological tissue region of interest, and calculates the anisotropic parameters of the region of interest according to the strain.
  • the processing flow is as shown in FIG. 3, including The following steps:
  • step 10 the biological tissue is deformed in the first position.
  • the first position of the biological tissue is pressed in the axial direction of the probe by manually pressing the probe or the vibrator to drive the probe to deform the biological tissue.
  • Step 11 Generate a first transmit and receive sequence, control the ultrasound probe to emit a first ultrasonic wave to the biological tissue, receive an echo of the first ultrasonic wave, and obtain a first echo signal.
  • the method of deforming the biological tissue to perform the elastic measurement may adopt the strain elastic measurement method mentioned above and/or the vibration elastic measurement method based on the external force vibration.
  • the transmitting/receiving sequence control module controls the ultrasonic probe to emit a first ultrasonic wave to the region of interest of the biological tissue, the first ultrasonic wave propagates in the first direction in the biological tissue, and forms a first cross section in the region of interest, and simultaneously receives The ultrasonic echo of the first section obtains the first echo signal.
  • Information of a plurality of biological tissue position points on the first section can be obtained based on the first echo signal.
  • the region of interest may be selected by the user, for example, when an ultrasound image is displayed on the display screen, the user may select a region of interest on the ultrasound image, and the ultrasound elasticity measuring device may calculate the transmission and reception sequences based on the selected region of interest.
  • the ultrasound elastic measuring device defaults to a sub-skinned setting range of the tissue contacted by the probe as the region of interest.
  • Step 12 Calculate a first elastic result corresponding to the first cross section in the region of interest according to the first ultrasonic echo signal of the cross section, and the first elastic result may be the dependent variable M1 of the region of interest in the first cross section.
  • the data processing module can determine the position of the region of interest after the tissue is deformed according to the two frames of ultrasonic echo data before and after the deformation of the tissue.
  • a common algorithm such as block-matching, is shown in Figure 4. That is, for two frames of echo data before and after the change, data A and B of a certain region of interest are selected in one frame of data, and in another frame of data. Searching at different locations and finding the location A', B' of the data that best matches it, the above-mentioned region of interest is considered to have moved to the location, and the difference in position between the two frames is the displacement of the region of interest.
  • the strain M of the region of interest can be calculated according to the definition of the strain, namely:
  • L is the length of the region of interest before tissue deformation
  • ⁇ L is the amount of change in length of the region of interest after tissue deformation
  • the first elastic distribution image can be obtained from the dependent variable M1.
  • Step 13 When the biological tissue is deformed, generating a second transmitting and receiving sequence, controlling the ultrasonic probe to transmit the second ultrasonic wave to the region of interest, and receiving the echo of the second ultrasonic wave to obtain the second echo signal.
  • the biological tissue in this step is deformed by deforming the biological tissue at the aforementioned first position, or deforming the biological tissue at a second position different from the first position.
  • the second position of the biological tissue is pressed along the axial direction of the probe by manually pressing the probe or the vibrator to drive the probe to vibrate. deformation.
  • the transmit/receive sequence control module controls the ultrasonic probe to emit a second ultrasonic wave to the region of interest of the biological tissue, the second ultrasonic wave propagates in a second direction within the biological tissue, and forms a second cross section in the region of interest, and simultaneously receives the first
  • the ultrasonic echo of the two cross sections obtains the second echo signal.
  • Information of a plurality of biological tissue position points on the second section can be obtained from the second echo signal.
  • Step 14 Calculate, according to the second echo signal, a second elastic result corresponding to the second cross section in the region of interest, wherein the first cross section is different from the second cross section.
  • the second elastic result may be the amount of strain M2 of the region of interest within the second section.
  • the closed region represents biological tissue 108
  • the solid line segment represents a first section 1091
  • the dashed line segment represents a second section 1092.
  • the first section 1091 and the second section 1092 are intersecting sections.
  • the first section 1091 and the second section 1092 are also parallel sections.
  • one section may be a section along the direction of the muscle fibers, and the other section may be a section perpendicular to the direction of the muscle fibers.
  • the position and orientation of the ultrasound probe determines the section.
  • the position of the ultrasonic probe is the position of the ultrasonic probe relative to the surface of the living body
  • the direction of the ultrasonic probe is the spatial orientation of the ultrasonic probe relative to the surface of the living body, whether the position is changed or the spatial orientation is changed, and the ultrasonic probe is transformed.
  • Ultrasonic waves for the purpose of detecting the elastic results of the region of interest by the position and/or direction, so that at least two different cross sections can be formed, and at least two sections of elasticity can be obtained for the same region of interest. result.
  • the user needs to manually adjust the position and/or direction of the ultrasonic probe (hereinafter referred to as manual adjustment).
  • manual adjustment When the user adjusts the ultrasonic probe to the first position placed on the biological tissue, the biological tissue is pressed along the axial direction of the probe by manually pressing the probe or the vibrator to vibrate the probe to deform the biological tissue while transmitting/receiving.
  • the sequence control module controls the ultrasound probe to emit ultrasonic waves on the first section to the region of interest of the biological tissue, forming a first section in the region of interest, and the ultrasound probe receives the ultrasound echo of the first section correspondingly to obtain the first ultrasound echo signal;
  • the user can independently select or adjust the position and/or direction of the ultrasonic probe by the system, so that when the ultrasonic probe is located on the biological tissue different from the second position of the first position, the probe is vibrated by manually pressing the probe or the vibrator.
  • the transmitting/receiving sequence control module controls the ultrasonic probe to emit ultrasonic waves on the second section to the region of interest of the biological tissue, forming a second cross section in the region of interest , the ultrasonic probe receives the second section of the ultrasonic echo corresponding to obtain the first Ultrasound echo signals.
  • the section can be changed by the user manually adjusting the position and/or direction of the ultrasound probe, as described above.
  • the emission direction of the ultrasonic wave or the direction of the emission plane can also be adjusted by delay control to obtain at least two sections in the same region of interest, for example, the emission direction or the emission plane can be adjusted by the transmission and reception sequence.
  • changing the cross section hereinafter referred to as automatic adjustment.
  • the emission transducer and/or the emission direction different from the first cross section are defined by the emission sequence, resulting in a second cross section different from the first cross section.
  • the first section and the second section may be simultaneously formed for the same pressing of the probe, and the first section and the second section may be respectively formed for the two pressing of the probe.
  • the cross section can also be changed by the user manually adjusting the position or direction of the ultrasonic probe, so that the first cross section and the second cross section are successively formed, and the ultrasonic waves of the first cross section and the second cross section are successively received. wave.
  • the ultrasonic probe is emitted to the same region of interest by different emission directions or emission planes by the control of the emission sequence.
  • the elastic result of the region of interest is measured for the purpose of the ultrasonic waves, thereby forming at least two different cross sections.
  • the area array probe can be used to automatically adjust, for example, to form at least two sets of transducers using transducer combinations of different spatial arrangements in the selected area array probe, using at least two sets of transducer groups
  • the regions of interest in the biological tissue respectively emit at least two emission directions or emission planes, thereby forming at least two different cross sections.
  • the linear array probe can be realized by adjusting the placement position of the ultrasonic probe on the biological tissue in the manner as described above. Taking the area array probe as an example, in addition to the placement position, it can also be implemented in the following manner.
  • the ultrasonic probe Transmitting, by the ultrasonic probe, a first ultrasonic wave in a first emission direction to the region of interest, and transmitting, by the ultrasonic probe, a second ultrasonic wave in a second emission direction to the region of interest; wherein the first emission direction intersects the second emission direction .
  • the emission of the first ultrasonic wave and the second ultrasonic wave may be separately transmitted through different sets of transducer groups, and the spatial arrangement of the different transducer groups is different, and there may be an intersection between the transducer groups.
  • the manner in which the biological tissue is deformed includes a combination of one or more of an external force vibration, an ultrasonic sound radiation force, and an ultrasonic probe press.
  • the direction of the emission can be measured by the angle between the scanning plane formed by the ultrasonic wave emitted from the ultrasonic probe and the surface of the ultrasonic probe, and the spatial arrangement of the different transducer groups is different, corresponding to different emission directions, thereby forming different ultrasonic waves.
  • Launch plane the spatial arrangement of the different transducer groups is different, corresponding to different emission directions, thereby forming different ultrasonic waves.
  • the ultrasonic probe generates shear waves propagating in at least two different directions in the same region of interest of the biological tissue, and emits ultrasonic waves for the purpose of detecting the shear waves, thereby forming at least two different cross sections, wherein the ultrasound
  • the probe realizes at least two ultrasonic waves for detecting different elastic directions or emission planes of the same region of interest by detecting the spatial position of the transducer group for transmitting the ultrasonic waves, so as to detect the elastic result of the region of interest.
  • Different cross sections are used to obtain at least two elastic results corresponding to different cross sections.
  • the elastic calculation result is displayed by the display module, for example, in some embodiments, the data processing module outputs at least one of the following results in response to the calculation of the foregoing elastic result:
  • the elastic distribution map may also be output according to the elastic result.
  • the elastic result corresponding to each position point in the biological tissue may be obtained according to the ultrasonic echo signal, and the elastic result corresponding to each position point may be mapped to the spatial distribution of each position point or the unified coordinate.
  • the system is formed to form an elastic distribution map.
  • the ultrasound probe generates a deformation by pressing the biological tissue to detect the elastic result of the region of interest, which is a quasi-static elastic parameter of the region of interest.
  • the quasi-static elastic parameter is the strain or strain rate.
  • the data processing module also generates elastography data based on quasi-static elastic parameters.
  • the anisotropic parameters may be further calculated in step 15.
  • the anisotropic parameter includes a secondary statistical analysis quantity based on the first elastic result and the second elastic result, for example, the anisotropy parameter includes at least: a ratio of the first elastic result to the second elastic result, the first elastic result, and the second One of a difference in the elastic result, a function of the ratio or difference of the first elastic result to the second elastic result, or the like.
  • the function of the ratio or difference of the first elastic result to the second elastic result may be the ratio or the square of the difference, the third power, and the like.
  • the data processing module calculates an anisotropic parameter according to the strain M1 of the region of interest in the first section and the strain M2 of the region of interest in the second section, and the anisotropic parameter may be the difference between M1 and M2, or Is the ratio of M1 to M2, and can be other functions of difference or ratio.
  • Step 16 Output a first elastic result and a second elastic result calculated according to the first echo signal and the second echo signal, respectively, for example, display the processing result.
  • the data processing module processes the elastic result into visual data and sends it to the display module for display.
  • the display mode can be digital or text, or can be a chart such as a column chart, a pie chart, or a line chart.
  • the data processing module may further generate strain-type elastic image data according to the dependent variable of the region of interest in the section, and display the elastic image on the display interface, and also display an anisotropic parameter of the region of interest.
  • the data processing module can further calculate the strain rate of the region of interest in different sections, and can further further determine the strain rate of the region of interest in different sections.
  • the anisotropy parameter of the region of interest is calculated.
  • the ultrasonic elastic measuring device may further include a pressure sensor mounted on the ultrasonic probe.
  • the upper part is used for sensing the pressure and feeding the sensed pressure to the data processing module.
  • the elastic imaging performed according to the strain of the biological tissue is called quasi-static elastic imaging.
  • the elastic parameter detected in the quasi-static elastography process is called a quasi-static elastic parameter
  • the strain is a quasi-static elastic parameter.
  • One kind, one skilled in the art should understand that when calculating the anisotropic parameters of the tissue, it is also possible to obtain the tissue according to other quasi-static elastic parameters, for example, according to the length change amount ⁇ L of the region of interest after deformation of the tissue. Anisotropic parameters.
  • the ultrasound probe simultaneously or sequentially generates shear waves propagating in at least two different directions in the same region of interest of the biological tissue, and emits ultrasonic waves for the purpose of detecting the shear waves, thereby forming at least two A different cross section
  • the ultrasonic elastic measuring device 100 detects the shear wave elastic parameters of different sections, and calculates the anisotropic parameters of the region of interest according to the shear wave elastic parameters.
  • Shear waves can be generated in a variety of ways, such as by transmitting an acoustic wave (eg, an ultrasonic pulse wave) to a tissue through an ultrasound probe to produce a transversely propagating shear wave within the tissue, or by impacting the tissue through an ultrasound probe to produce longitudinal propagation within the tissue. Shear wave.
  • the processing flow of this embodiment is as shown in FIG. 7, and includes the following steps:
  • step 20 an acoustic radiation force is emitted to the biological tissue for deforming the biological tissue.
  • the ultrasonic probe is further configured to emit a pulse wave, and when the user places the ultrasonic probe on the biological tissue, the ultrasonic probe transmits a pulse wave to the biological tissue.
  • the ultrasonic probe 101 is in close contact with the surface 110 of the tissue 160.
  • the pulse wave 120 generated by the ultrasonic probe 101 strikes the tissue 160, a focus point 130 is formed in the tissue 160 due to the beam characteristics of the pulse wave. Displacement in the direction of the beam is produced, and lateral shear waves 140 and 150 are formed near the focus point 130 due to adhesion between the tissues.
  • the shear wave can also be generated by vibrating the probe to vibrate the tissue. This shear wave elastography is called transient elastography.
  • Step 21 generating a transmission and reception sequence of shear wave elastography, and controlling the ultrasound probe to the living
  • the object tissue emits a first ultrasonic wave to form a first cross section in the biological tissue, and receives an echo of the first ultrasonic wave to obtain a first echo signal for detecting the ultrasonic echo of the first cross section.
  • the shear wave elastic parameter is used to calculate the anisotropic parameter, so the transmit and receive sequence is the same as the transmit and receive sequence for performing shear wave elastography, for example, the transmit sequence includes transducer parameters for determining the transmit.
  • the receiving sequence includes transducer parameters for determining reception, angles of reception, depth, and the like.
  • the simultaneous transmit/receive sequence control module controls the ultrasonic probe to emit ultrasonic waves to the region of interest of the tissue and to continue the ultrasonic wave for a period of time, the ultrasonic wave scans the region of interest and forms a first cross section, and the ultrasonic probe simultaneously receives the first The ultrasonic echo of the cross section obtains the first echo signal.
  • Step 22 Calculate a shear wave elastic parameter of the region of interest in the first section according to the first echo signal corresponding to the first section as a first elastic result.
  • the shear wave elastic parameters are shear wave propagation velocity, Young's modulus value or shear modulus value.
  • the data processing module can calculate the displacement amount of the portion of the set depth of the tissue during a period of time during the shear wave propagation according to the received echo signal.
  • the first section 1091 sweeps the shear wave.
  • the path of the C point can be used to detect whether the shear wave has reached point C. When the displacement of the C point is the largest, it is considered that the shear wave 140 reaches the C point, or the moving speed of the C point is the fastest, and the shear wave 140 is considered to reach the C point, or the phase of the C point motion reaches a certain value. It is the shear wave that has reached this position.
  • Various methods can be used to calculate the propagation velocity of the shear wave.
  • the time at which the shear wave 140 reaches the C point can locate the propagation path or propagation trajectory of the shear wave, and the shear wave trajectory map can be drawn, according to the shear
  • the trajectory of the wave can obtain the slope of each point on the shear wave propagation path, and the slope is the propagation speed of the shear wave.
  • the shear wave propagation velocity has the following approximate relationship between Young's modulus and shear modulus:
  • ⁇ is the tissue density
  • E is the Young's modulus value of the tissue
  • G is the shear modulus of the tissue.
  • ⁇ is the density value of water. Therefore, when the shear wave propagation velocity is obtained, other elastic correlation parameters such as Young's modulus and shear modulus can be further calculated.
  • step 23 the ultrasonic echo of the second section is detected.
  • Adopting the steps in step 13 of the first embodiment The same method transforms the cross section to obtain an ultrasonic echo of the second cross section.
  • the ultrasonic probe is controlled to emit a second ultrasonic wave to the region of interest for forming a second cross section in the biological tissue, and receiving an echo of the second ultrasonic wave to obtain a second echo signal corresponding to the second cross section.
  • the shear wave propagating inside the tissue is generated by transmitting a pulse wave to the tissue or impacting the tissue through the probe, and simultaneously transmitting/receiving the sequence control module.
  • the ultrasound probe is controlled to emit ultrasound waves to the region of interest of the tissue for a period of time that scans the region of interest and forms a second section, the ultrasound probe simultaneously receiving ultrasound echoes of the second section.
  • the first section and the second section may be simultaneously formed for the same shear wave generated, or the first section and the second section may be respectively formed by two different shear waves, two different shears. Waves can be generated simultaneously or at different times.
  • a first ultrasonic beam is emitted to the biological tissue to deform the biological tissue, and the ultrasonic probe is controlled to emit the first ultrasonic wave to the region of interest to obtain a first echo signal; to the biological tissue
  • the second ultrasonic beam is emitted to deform the biological tissue, and the ultrasonic probe is controlled to emit the second ultrasonic wave to the region of interest to obtain a second echo signal.
  • the first ultrasonic beam is different from the second ultrasonic beam in the biological tissue, or the shear wave generated in the biological tissue is different.
  • the first ultrasonic beam is emitted to the biological tissue to generate a first shear wave in the biological tissue, and the ultrasonic probe is controlled to emit the first ultrasonic wave to the region of interest through which the first shear wave passes, thereby obtaining the first echo signal.
  • the second ultrasonic beam is emitted to the biological tissue to generate a second shear wave in the biological tissue, and the ultrasonic probe is controlled to emit the second ultrasonic wave to the region of interest through which the second shear wave passes, thereby obtaining a second echo signal.
  • the propagation directions of the first shear wave and the second shear wave may be the same or different.
  • the region of interest through which the first shear wave travels is the same region of interest as the region of interest through which the second shear wave travels.
  • the ultrasound probe generates shear waves propagating in at least two different directions in the same region of interest of the biological tissue and emits ultrasonic waves for the purpose of detecting the shear waves, thereby forming at least two different section. See the previous description for how the first ultrasonic wave and the second ultrasonic wave form different two cross sections.
  • the first shear wave and the second shear wave mentioned above may be generated simultaneously or sequentially.
  • Step 24 Calculate a shear wave elastic parameter of the region of interest in the second section according to the second ultrasonic echo signal corresponding to the second section, as a second elastic result.
  • the first elastic result and the second elastic result may be directly output to the display module for display, for example, on the same display interface. Show, to facilitate the doctor to compare the elastic results of the two sections.
  • step 25 can also be performed.
  • an anisotropic parameter is calculated.
  • the data processing module calculates an anisotropic parameter according to the shear wave elastic parameter N1 of the region of interest in the first section and the shear wave elastic parameter N2 of the region of interest in the second section, and the anisotropic parameter may be the difference between N1 and N2.
  • the value can also be the ratio of N1 and N2, and can be other functions of the difference or ratio.
  • Step 26 Output a first elastic result and a second elastic result calculated according to the first echo signal and the second echo signal, respectively, for example, display the processing result.
  • the elastic calculation result is output, for example, by the display module.
  • the data processing module outputs at least one of the following results in response to the calculation of the aforementioned elastic result:
  • Step 26 can be specifically referred to step 15 as described above.
  • the ultrasonic probe generates a shear wave in the biological tissue to detect the elastic result of the region of interest, and then calculates the obtained elastic result as the shear wave elastic parameter of the region of interest.
  • Shear wave elastic parameters are shear wave propagation velocity, Young's modulus value or shear modulus value
  • the data processing module may also output the shear wave elastic parameter of the region of interest in a certain section to the display module for display, and display the anisotropic parameter of the region of interest.
  • Display methods include text, numbers, and/or graphics.
  • the user may also select a plurality of regions of interest, and the ultrasonic elastic measuring device calculates anisotropy parameters of the plurality of regions of interest in the manner described above, performs contrast display, or displays multiple regions of interest.
  • Anisotropic parameter distribution map may be selected from a plurality of regions of interest, and the ultrasonic elastic measuring device calculates anisotropy parameters of the plurality of regions of interest in the manner described above, performs contrast display, or displays multiple regions of interest.
  • Anisotropic parameter distribution map is also select a plurality of regions of interest.
  • a deformation is required for the tissue.
  • the tissue can be deformed once for each elastic parameter of the cross-section, but can also be transmitted and received by the transmit/receive sequence control module after the tissue is deformed once.
  • Different cross-sections are formed to simultaneously receive ultrasonic echoes of different cross-sections, so that multiple deformations of the tissue are not required.
  • anisotropic parameters of the region of interest may also be calculated using ultrasound echoes of more different cross sections of the same region of interest.
  • an elastic contrast measurement method which includes the following steps:
  • Step A1 forming a first cross section in the region of interest, and calculating a first elastic result corresponding to the region of interest according to the first cross section;
  • Step A2 forming a second cross section in the region of interest, and calculating a second elastic result corresponding to the region of interest according to the second cross section;
  • Step A3 calculating an anisotropic parameter of the region of interest according to the first elastic result and the second elastic result;
  • Step A4 in response to the calculation of the elastic result, outputting at least one of the following results:
  • the anisotropic parameter includes a secondary statistical analysis quantity based on the first elastic result and the second elastic result.
  • the anisotropy parameter includes at least: a ratio of the first elastic result to the second elastic result, and the first elasticity.
  • the result is one of a difference between the result and the second elastic result, and a function of the ratio or difference of the first elastic result to the second elastic result.
  • the function of the ratio or difference of the first elastic result to the second elastic result may be the ratio or the square of the difference, the third power, and the like.
  • the elastic distribution map in this embodiment is an elastic distribution map formed by mapping the spatial position distribution of the region of interest according to the elasticity result corresponding to each position point in the region of interest.
  • the above step A1 can also refer to the related description of the related steps 10 to 12 or the related description of the steps 20 to 22.
  • the above step A2 can also refer to the related description of the related steps 13 to 14 or the related description of the steps 23 to 24.
  • the ultrasonic echo signals of two different sections continuously collected by the system for the user are performed. Processing, or processing the ultrasonic echo signals of two different sections selected by the user through a button or a touch screen, thereby obtaining the elastic results of the two sections, or first obtaining the elastic results of more sections, and then more One Two of the elastic results are selected. The system then correlates the elastic results of the two sections to compare the elastic results of the two sections.
  • a multi-section test mode for example, a tissue anisotropy measurement mode or an elastic contrast mode
  • the correlation processing may be, for example, performing the same screen display on the elastic results of the two sections, so that the user can understand the elastic results of two different sections by the same screen observation, wherein the elastic result may be an image, or may be a numerical value, a text or a chart.
  • the association process can also be to compute the elastic results of the two sections and then output the anisotropic parameters.
  • an anisotropic parameter corresponding to each region of interest can be obtained for the first elastic result and the second elastic result corresponding to each region of interest, when there are multiple regions of interest. Then, a plurality of anisotropic parameters corresponding to the plurality of inductive regions may be correspondingly obtained. Therefore, in one embodiment, a plurality of anisotropic parameters may also be output, each anisotropic parameter corresponding to one region of interest.
  • the system can calculate the anisotropy parameters of different target regions (the target region can include multiple regions of interest), and then perform contrast display between different regions of interest in the target region, or generate more Distribution map of anisotropic parameters in the region of interest.
  • the anisotropic parameters corresponding to the plurality of regions of interest are mapped to the same coordinate system according to the spatial position distribution of the plurality of regions of interest, and the directions corresponding to the plurality of inductive regions are obtained. The distribution of the parameters of the opposite sex is then displayed.
  • the aforementioned transmitting and receiving module may be configured to control the ultrasonic probe to emit a first ultrasonic wave to the region of interest when the biological tissue is deformed, and receive an echo of the first ultrasonic wave to obtain a first echo signal;
  • the ultrasonic probe is controlled to emit a second ultrasonic wave to the region of interest, and an echo of the second ultrasonic wave is received to obtain a second echo signal.
  • the data processing module is used to calculate the first elastic result and the second elastic result, and can also be used to calculate the elastic distribution map and the anisotropic parameter.
  • the transmit/receive sequence control module (102), the echo processing module (104), and the transmit and receive module (103) and the data processing module (105) may be integrated on the same board or multiple boards, or Part or all of the calculation process in the transmit/receive sequence control module (102), the echo processing module (104), and the transmit and receive module (103) and the data processing module (105) may be integrated in one or more processes Implemented in the device.
  • the functions involved in the present application can be implemented by means of the program described in the above embodiments, or by hardware, for example, by using a gate circuit to build an application specific integrated circuit.
  • a person skilled in the art may understand that various programs in the foregoing embodiments may be stored in a computer readable storage medium, and the storage medium may include: a read only memory, a random access memory, and a magnetic The disk or optical disk, etc., the data processing module can implement the above functions by executing a program.

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Abstract

一种超声弹性测量装置(100)包括超声探头(101)、发射/接收序列控制模块(102)、发射和接收模块(103)、回波处理模块(104)和数据处理模块(105)，超声探头(101)向生物组织(108)发射以检测同一感兴趣区域的弹性结果为目的的超声波，以在该感兴趣区域形成至少两个不同的截面(1091，1092)，并接收至少两个不同截面(1091，1092)的超声回波，数据处理模块(105)根据至少两个不同截面(1091，1092)的超声回波计算与各截面(1091，1092)对应的弹性结果，还可进一步根据至少两个弹性结果计算感兴趣区域的各向异性参数，从而可反映感兴趣区域的各向异性程度，在医生对病灶进行诊断或者对临床预后效果进行判断的过程中给医生提供更多的参考信息。

Description

一种超声弹性测量装置及弹性对比测量方法 技术领域
本发明涉及医疗设备，具体涉及一种超声弹性测量装置及弹性对比测量方法。
背景技术
超声弹性成像是近年来临床研究的热点之一，由于其主要反映组织的弹性或软硬程度，因此在组织癌症病变的辅助检测、良恶性判别、预后恢复评价等方面得到越来越多应用。
超声弹性成像主要通过对感兴趣区域内的弹性相关参数进行成像，从而反映组织的软硬程度。近二十年来，已经出现了许多种不同的弹性成像方法，比如基于探头按压组织造成应变的准静态弹性成像，基于声辐射力产生剪切波的弹性成像或弹性测量，基于外部振动产生剪切波的瞬时弹性成像等。
不论哪种弹性成像方法，都是在假设目标组织为各向同性的介质的前提下进行计算的。人体组织种类多，结构也复杂多样，大部分人体组织都可近似为各向同性的弹性介质，即不同方向的弹性特征是相同的。但某些人体组织，比如肌肉，其各向异性的特征非常强，不同方向或者不同截面内弹性差异极大。因此，从不同的角度或截面进行弹性成像或测量时，所获得的值或图像可能是不同的。这种组织各向异性的特点或程度，可能可以提供新的信息给医生。
发明内容
本申请提供一种超声弹性测量装置及弹性对比测量方法，可通过超声弹性测量装置测量生物组织的各向异性参数。
根据第一方面，一种实施例中提供一种超声弹性测量装置，包括：
超声探头，其包括至少一个换能器，所述换能器中第一部分用于向生物组织发射以检测同一感兴趣区域的弹性结果为目的的超声波，以在该感兴趣区域形成至少两个不同的截面，所述换能器中的第二部分用于接收由生物组织返回的超声回波，所述超声回波包括该感兴趣区域的至 少两个不同截面的超声回波；
发射/接收序列控制模块，用于产生控制相应换能器发射超声波的发射序列和控制相应换能器接收超声回波的接收序列；
回波处理模块，用于对超声回波进行处理；
发射和接收模块，其分别与超声探头、发射/接收序列控制模块和回波处理模块电连接，用于将发射/接收序列控制模块产生的发射序列传输给超声探头，并将超声探头接收的超声回波传输给回波处理模块；
数据处理模块，其与回波处理模块连接，所述数据处理模块包括弹性计算模块，所述弹性计算模块用于分别根据至少两个不同截面的超声回波计算与各截面内感兴趣区域的弹性结果。
根据第二方面，一种实施例中提供一种弹性对比测量方法，包括：
在生物组织产生形变时，控制超声探头向感兴趣区域发射第一超声波；
接收所述第一超声波的回波，获得第一回波信号；
在生物组织产生形变时，控制超声探头向所述感兴趣区域发射第二超声波；
接收所述第二超声波的回波，获得第二回波信号；
根据所述第一回波信号，获得所述感兴趣区域中第一截面对应的第一弹性结果；
根据所述第二回波信号，获得所述感兴趣区域中第二截面对应的第二弹性结果，其中第一截面不同于第二截面；
输出所述第一弹性结果和第二弹性结果。
根据第三方面，一种实施例中提供一种弹性对比测量方法，包括：
在感兴趣区域内形成第一截面，根据第一截面计算感兴趣区域对应的第一弹性结果；
在感兴趣区域内形成第二截面，根据第二截面计算感兴趣区域对应的第二弹性结果；
根据所述第一弹性结果和第二弹性结果计算感兴趣区域的各向异性参数；
响应于弹性结果的计算输出至少以下结果之一：
(1)根据所述第一弹性结果输出第一弹性分布图，和根据所述第二弹性结果输出第二弹性分布图；和，
(2)根据所述第一弹性结果与第二弹性结果显示各向异性参数。
根据第四方面，一种实施例中提供一种超声弹性测量装置，包括：
超声探头，其包括至少一个换能器，所述换能器中第一部分用于向感兴趣区域发射以检测同一感兴趣区域的弹性结果为目的的超声波，以在该感兴趣区域形成至少两个不同的截面，所述换能器中的第二部分用于接收由生物组织返回的超声回波，所述超声回波包括该感兴趣区域的至少两个不同截面的超声回波；
发射和接收模块，其与超声探头电连接，用于在生物组织产生形变时，控制超声探头向感兴趣区域发射第一超声波，并接收所述第一超声波的回波，获得第一回波信号；在生物组织产生形变时，控制超声探头向所述感兴趣区域发射第二超声波，接收所述第二超声波的回波，获得第二回波信号；
数据处理模块，用于根据所述第一回波信号，获得所述感兴趣区域中第一截面对应的第一弹性结果；根据所述第二回波信号，获得所述感兴趣区域中不同于第一截面的第二截面对应的第二弹性结果，输出所述第一弹性结果和第二弹性结果。
根据第五方面，一种实施例中提供一种超声弹性测量装置，包括：
超声探头，其包括至少一个换能器，所述换能器用于向感兴趣区域发射超声波，在同一感兴趣区域内形成第一截面和第二截面；
数据处理模块，用于根据第一截面计算感兴趣区域对应的第一弹性结果，根据第二截面计算感兴趣区域对应的第二弹性结果，根据所述第一弹性结果和第二弹性结果计算感兴趣区域的各向异性参数，响应于弹性结果的计算输出至少以下结果之一：
(1)根据所述第一弹性结果输出第一弹性分布图，和根据所述第二弹性结果输出第二弹性分布图；和，
(2)根据所述第一弹性结果与第二弹性结果显示各向异性参数。
本发明实施例中，采用检测的弹性参数计算感兴趣区域的各向异性参数，通过各向异性参数衡量感兴趣区域的各向异性程度，并输出各向异性参数，在医生对病灶进行诊断或者对临床预后效果进行判断的过程中给医生提供更多的参考信息。
附图说明
图1是超声弹性测量装置的结构示意图；
图2是截面示意图；
图3是一种实施例中各向异性参数计算流程图；
图4是应变性弹性成像过程中位移检测示意图；
图5是不同截面分布的一种示意图；
图6是不同截面分布的另一种示意图；
图7是另一种实施例中各向异性参数计算流程图；
图8是超声探头产生剪切波示意图；
图9是剪切波检测示意图。
具体实施方式
下面通过具体实施方式结合附图对本发明作进一步详细说明。其中不同实施方式中类似元件采用了相关联的类似的元件标号。在以下的实施方式中，很多细节描述是为了使得本申请能被更好的理解。然而，本领域技术人员可以毫不费力的认识到，其中部分特征在不同情况下是可以省略的，或者可以由其他元件、材料、方法所替代。在某些情况下，本申请相关的一些操作并没有在说明书中显示或者描述，这是为了避免本申请的核心部分被过多的描述所淹没，而对于本领域技术人员而言，详细描述这些相关操作并不是必要的，他们根据说明书中的描述以及本领域的一般技术知识即可完整了解相关操作。
另外，说明书中所描述的特点、操作或者特征可以以任意适当的方式结合形成各种实施方式。同时，方法描述中的各步骤或者动作也可以按照本领域技术人员所能显而易见的方式进行顺序调换或调整。因此，说明书和附图中的各种顺序只是为了清楚描述某一个实施例，并不意味着是必须的顺序，除非另有说明其中某个顺序是必须遵循的。
本文中为部件所编序号本身，例如“第一”、“第二”等，仅用于区分所描述的对象，不具有任何顺序或技术含义。而本申请所说“连接”、“联接”，如无特别说明，均包括直接和间接连接(联接)。
在本发明实施例中，通过超声设备测量生物组织感兴趣区域不同截面的弹性参数，根据不同截面的弹性参数计算感兴趣区域的各向异性参 数，各向异性参数用于反映某部位组织各向异性的程度，各向异性是指组织的特性随着方向的改变而有所变化，在不同的方向上呈现出差异的性质，因此，各向异性参数表征生物组织(例如，生物组织可以是人或动物的心脏、肌肉、血管等等解剖结构)在随方向的改变而所有变化时在不同方向上呈现出的差异性质。在本文中，各向异性参数包括至少两个方向上对应的特性之比、至少两个方向上对应的特性之差、或者至少两个方向上对应的特性之比的比值的平方等等，或者，各向异性参数还可以是至少两个方向上对应获得的特性的二次统计分析量。以下将结合在超声设备中的弹性测量作为前述特性的获取方式来具体说明。
本实施例中，各向异性参数可以包括沿不同截面获得的多个弹性参数的对比分析结果，例如，多个弹性参数之间的比值、多个弹性参数之间的差值、多个弹性参数之间的占比分析等等二次统计分析量。本文中，该超声设备称为超声弹性测量装置，但本领域技术人员应当理解，该超声设备也可以附加其它功能，例如进行通常的超声诊断，生成B模式的超声图像、C模式的超声图像或多普勒超声图像等等。
本文中提到的弹性测量方式可以为基于外力振动的振动弹性测量方式、基于声幅射力的剪切波测量方式、和应变弹性测量方式中的其中之一或两种以上的结合。
具体的，基于外力振动的振动弹性测量方式通过外力振动产生剪切波传入组织，然后通过在生物组织内部产生剪切波的传播并检测其传播参数(比如传播速度)的方法来反映组织间的硬度差异。对于各向同性的弹性组织，剪切波的传播速度Cs与组织弹性模量E之间存在下列关系：杨氏模量
Figure PCTCN2017106897-appb-000001
(其中，ρ为组织密度)。也就是说，剪切波速度与弹性模量存在一一对应的关系。
基于声幅射力的剪切波测量方式通过超声声辐射力在生物组织内部产生剪切波的传播，然后通过在生物组织内部产生剪切波的传播并检测其传播参数(比如传播速度)的方法来反映生物组织间的硬度差异。对于各向同性的弹性组织，剪切波的传播速度Cs与组织弹性模量E之间存在下列关系：杨氏模量
Figure PCTCN2017106897-appb-000002
(其中，ρ为组织密度)。也就是说，剪切波速度与弹性模量存在一一对应的关系。
应变弹性测量方式，或称常规超声弹性测量方式，其基本原理是： 将探头轻微压迫目标生物组织或者借助人体自身的呼吸、血管搏动等过程对组织形成一定的压力，获取压缩前、后两帧超声回波信号，生物组织被压缩时，生物组织内将产生一个沿压缩方向的应变，如果生物组织内部杨氏模量分布不均匀，生物组织内的应变分布也将有所差异，然后通过一些方法检测出生物组织的应变信息，再将应变量、应变率等与组织弹性相关的参数计算出来并输出，从而间接反映施压区域内不同组织之间的弹性差异。具体的，根据胡克定律，对于各向同性的弹性体，应力σ＝应变ε×杨氏模量E，即E＝σ/ε。其中，杨氏模量E是与组织硬度相关的参数，杨氏模量越高，表明组织硬度越大。超声探头通过按压生物组织产生形变以进行感兴趣区域弹性结果的检测，则计算得到的弹性结果为感兴趣区域的准静态弹性参数。准静态弹性参数为应变量或应变率。
需要说明的是，在本实施例中，弹性测量方式并不限于上述列举的弹性测量方式，还可以是其他基于超声弹性成像的弹性测量方式。
请参考图1，超声弹性测量装置100包括超声探头101、发射/接收序列控制模块102、发射和接收模块103、回波处理模块104、数据处理模块105和显示模块106。发射/接收序列控制模块102通过发射和接收模块103与超声探头101信号连接，超声探头101通过发射和接收模块103与回波处理模块104信号连接，回波处理模块104的输出端与数据处理模块105连接，数据处理模块105的输出端与显示模块106连接。
超声探头101包括至少一个换能器，换能器用于根据电信号发射超声波，或将接收的超声波变换为电信号。多个换能器排列成一排，例如线阵探头；或者，多个换能器排布成二维矩阵，例如，二维超声探头或面阵探头。超声探头101的一部分换能器用于向生物组织108发射超声波，另一部分换能器用于接收由生物组织返回的超声回波。
发射/接收序列控制模块102用于根据控制模块107的指令产生发射序列和接收序列，发射序列用于提供超声探头101中发射用的换能器数和向生物组织发射超声波的参数(例如幅度、频率、发波次数、发波角度、波型等)，接收序列用于提供超声探头101中接收用的换能器数以及其接收回波的参数(例如接收的角度、深度等)。不同用途，或生成的图像不同，发射序列和接收序列也有所不同。如图2所示，当超声 探头101固定在生物组织108上的某个位置后，超声探头101中相应的换能器按照发射序列，向生物组织108内发射一定幅度、频率和角度的超声波，超声波在生物组织108内形成截面109，同时接收该截面的超声回波。本发明实施例中，可通过用户手动变换超声探头101的放置方向或位置形成不同的截面，也可通过自动变换换能器的方式形成不同的截面，这点后面将详细阐述。
发射和接收模块103连接在超声探头和发射/接收序列控制模块102、回波处理模块104之间，用于根据控制模块107的控制将发射/接收序列控制模块102的发射序列传输给超声探头101，并将超声探头101接收的超声回波传输给回波处理模块104。
回波处理模块104用于对超声回波进行处理，例如对超声回波进行滤波、放大、波束合成等处理。
数据处理模块105接收回波处理模块104输出端处理后的回波信号，并采用相关算法得到所需要的参数或图像。
本实施例中，数据处理模块105包括弹性计算模块1051，更进一步地包括，各向异性计算模块1052。弹性计算模块1051用于分别根据至少两个不同截面的超声回波，计算与各个截面对应的弹性结果，还可根据弹性结果进一步生成各种弹性分布图像数据或各种图表、图形。各向异性计算模块1052用于根据至少两个弹性结果计算生物组织或生物组织中某个感兴趣区域的各向异性参数。本文提到的感性区域可以是生物组织中的一部分或全部。感兴趣区域的确定可以基于系统自动生成，也可以基于用户在超声图像上进行选择而获得。在其中一个实施例中，数据处理模块还根据超声回波生成超声图像数据并输出至显示模块显示，感兴趣区域由用户在超声图像上选定。
显示模块106作为输出模块，显示模块106接收数据处理模块105输出的各种可视化数据，在显示界面上显示各种图像、图形、图表、文字或数据，其中包括各向异性参数和/或各种弹性图像。在有的实施例中，数据处理模块105在计算出与各截面对应的弹性结果后，可以直接将计算出的弹性结果输出至显示模块进行显示，用户可根据不同截面的弹性结果，自行比较该感兴趣区域的各向异性程度。在其它的实施例中，输出模块也可以是音频播放模块，将数据处理模块105输出的音频信号通过声音的方式播放出来。在一些实施例中，显示模块可以是触摸显示屏， 或多个显示器等等。在一些实施例中，输出模块响应于计算获得的弹性结果输出至少以下结果之一：
(1)根据与各个截面对应的弹性结果输出至少两个弹性分布图；和，(2)根据与各个截面对应的弹性结果输出感兴趣区域的各向异性参数。
上述不同截面为感兴趣区域内相互平行的截面或相交的截面。
用于计算组织各向异性参数的弹性结果可以是在检测生物组织应变过程中得到的弹性参数，也可以是在检测剪切波过程中得到的弹性参数。以下通过不同实施例进行详细说明。
在其中一个实施例中，超声弹性测量装置100检测生物组织感兴趣区域的两个不同截面的应变量，根据应变量计算感兴趣区域的各向异性参数，其处理流程如图3所示，包括以下步骤：
步骤10，在第一位置使生物组织产生形变。当用户将超声探头放置在生物组织上时，通过手动按压探头或振动器带动探头振动的方式沿探头的轴向按压生物组织的第一位置，以使生物组织产生形变。
步骤11，生成第一发射接收序列，控制超声探头向生物组织发射第一超声波，接收所述第一超声波的回波，获得第一回波信号。
本实施例中，使生物组织发生形变来进行弹性测量的方式可以采用前文提到的应变弹性测量方式和/或基于外力振动的振动弹性测量方式。
发射/接收序列控制模块控制超声探头向生物组织的感兴趣区域发射第一超声波，第一超声波在生物组织内的按照第一方向进行传播，并在感兴趣区域内形成第一截面，并同时接收第一截面的超声回波，获得第一回波信号。根据第一回波信号可以得到在第一截面上多个生物组织位置点的信息。
感兴趣区域可由用户选定，例如当显示屏上显示超声图像时，用户可在超声图像上选定感兴趣区域，超声弹性测量装置可根据选定的感兴趣区域计算发射和接收序列。在有的实施例中，超声弹性测量装置默认探头所接触的组织表皮下设定范围为感兴趣区域。
步骤12，根据截面第一超声回波信号计算获得感兴趣区域中第一截面对应的第一弹性结果，第一弹性结果可以是第一截面内感兴趣区域的应变量M1。
数据处理模块根据组织发生形变前后的两帧超声回波数据，可确定出感兴趣区域在组织发生形变后的位置。位移计算方法可以有很多种， 常见的算法比如block-matching的思路，如图4所示，即对于变化前后两帧回波数据，在其中一帧数据中选取某感兴趣区域的数据A、B，并在另一帧数据中不同位置进行搜索，找到与之最匹配的数据的位置A’、B’，则认为上述感兴趣区域移到了该位置，而两帧间的位置差即为上述感兴趣区域的位移量。
得到位移数据后，则可根据应变的定义，计算出感兴趣区域的应变M，即：
M＝ΔL/L
其中，L为感兴趣区域在组织形变前的长度，ΔL为感兴趣区域在组织发生形变后的长度变化量。
在有的具体实施例中，可根据应变量M1得到第一弹性分布图像。
步骤13，在生物组织发生形变时，生成第二发射接收序列，控制超声探头向感兴趣区域发射第二超声波，接收第二超声波的回波，获得第二回波信号。本步骤中的生物组织发生形变，可以是在前述第一位置处使生物组织产生形变，也可以是在不同于第一位置处的第二位置处使生物组织产生形变。在其中一个实施例中，当用户将超声探头放置在生物组织上时，通过手动按压探头或振动器带动探头振动的方式沿偏离探头的轴向按压生物组织的第二位置，以使生物组织产生形变。发射/接收序列控制模块控制超声探头向生物组织的感兴趣区域发射第二超声波，第二超声波在生物组织内的第二方向进行传播，并在感兴趣区域内形成第二截面，并同时接收第二截面的超声回波，获得第二回波信号。根据第二回波信号可以得到在第二截面上多个生物组织位置点的信息。
步骤14，根据第二回波信号，计算获得感兴趣区域中第二截面对应的第二弹性结果，其中第一截面不同于第二截面。在其中一个实施例中，第二弹性结果可以是第二截面内感兴趣区域的应变量M2。
如图5所示，图中以闭合区域代表生物组织108，实线段代表第一截面1091，虚线段代表第二截面1092。图5所示的实施例中，第一截面1091和第二截面1092为相交的截面，在其它实施例中，如图6所示，第一截面1091和第二截面1092也为相互平行的截面。对于肌肉组织而言，第一截面和第二截面中，一个截面可以是顺着肌肉纤维方向的剖切截面，另一个截面可以是垂直于肌肉纤维方向的剖切截面。
在其中一个实例中，超声探头的位置和方向决定截面。本文中提到 的超声探头的位置为超声探头相对于生物体表面的放置位置，超声探头的方向为超声探头相对于生物体表面的空间方位，无论是放置位置的改变、还是空间方位的改变，超声探头通过变换位置和/或方向向同一感兴趣区域发射以检测该感兴趣区域的弹性结果为目的的超声波，从而可以形成至少两个不同的截面，可以实现对于同一感兴趣区域获得至少两个截面上的弹性结果。
以超声探头的换能器排列为一维时为例，当需要变换截面时，则需要用户手动调整超声探头的位置和/或方向(以下简称手动调整)。当用户将超声探头调整好放置在生物组织上的第一位置时，通过手动按压探头或振动器带动探头振动的方式沿探头的轴向按压生物组织，以使生物组织产生形变，同时发射/接收序列控制模块控制超声探头向生物组织的感兴趣区域发射第一截面上的超声波，在感兴趣区域内形成第一截面，超声探头接收第一截面的超声回波对应获得第一超声回波信号；此外，用户可以自主选择或系统自主选择调整超声探头的位置和/或方向，使超声探头位于生物组织上不同于第一位置的第二位置时，通过手动按压探头或振动器带动探头振动的方式沿探头的轴向按压生物组织，以使生物组织产生形变，同时发射/接收序列控制模块控制超声探头向生物组织的感兴趣区域发射第二截面上的超声波，在感兴趣区域内形成第二截面，超声探头接收第二截面的超声回波对应获得第二超声回波信号。
在另一些实施例中，当超声探头的换能器排列为二维矩阵时，即超声探头为面阵探头时，可通过用户手动调整超声探头的位置和/或方向来改变截面，如前述实施例所述；当然，也可通过时延控制来调整超声波的发射方向或发射平面的方向从而在同一感兴趣区域内获得至少两个截面，例如，可由发射接收序列来调整超声发射方向或发射平面从而改变截面(以下简称自动调整)。例如由发射序列定义不同于第一截面的发射换能器和/或发射方向，从而得到不同于第一截面的第二截面。这种情况下，可针对探头的同一次按压同时形成第一截面和第二截面，也可以针对探头的先后两次按压分别形成第一截面和第二截面。当然，对于二维矩阵的超声探头，也可通过用户手动调整超声探头的位置或方向来改变截面，使得先后形成第一截面和第二截面，并先后接收第一截面和第二截面的超声回波。针对前述的自动调整，可以理解为：超声探头通过发射序列的控制以不同的发射方向或发射平面向同一感兴趣区域发射以检 测该感兴趣区域的弹性结果为目的的超声波，从而形成至少两个不同的截面。
在另一些实施例中，可以利用面阵探头来自动调整，例如，利用选择面阵探头中不同空间排列的换能器组合形成至少两组换能器组，利用至少两组换能器组向生物组织中的感兴趣区域分别发射至少两个发射方向或发射平面，从而形成至少两个不同的截面。
在其中一个实施例中，本文中提到的至少两个不同的截面在生物组织或感兴趣区域内相交。也就是说，超声波在生物组织内的发射方向或发射平面相交。为了实现超声波发射方向或发射平面的相交发射，以线阵探头为例，可以采用前述所示的方式，通过调整超声探头在生物组织上的放置位置来实现。而以面阵探头为例，除了可以采用放置位置来调整，还可以采用以下方式来实现。利用超声探头向感兴趣区域发射沿第一发射方向的第一超声波，和，利用超声探头向感兴趣区域发射沿第二发射方向的第二超声波；其中，第一发射方向与第二发射方向相交。当然，第一超声波和第二超声波的发射可以通过不同组的换能器组来分别发射，而不同换能器组的空间排列不相同，换能器组间也可以存在交集。本实施例中，使生物组织产生形变的方式包括通过外力振动、超声声辐射力、和利用超声探头按压中的其中之一或两种以上的结合。可以通过从超声探头发射出的超声波形成的扫描平面与超声探头表面之间的空间夹角来衡量发射方向，不同换能器组的空间排列不相同对应获得的发射方向不同，从而形成了不同超声波发射平面。因此，超声探头在生物组织的同一感兴趣区域产生沿至少两个不同方向传播的剪切波，并发射以探测该剪切波为目的的超声波，从而形成至少两个不同的截面，其中，超声探头通过变换用于发射超声波的换能器组的空间位置，来实现向同一感兴趣区域发射不同发射方向或发射平面的以检测该感兴趣区域的弹性结果为目的的超声波，从而形成至少两个不同的截面，用以对应获得不同截面对应的至少两个弹性结果。
根据第二截面的超声回波信号计算第二截面内感兴趣区域的应变量M2，从而获得第二截面对应的第二弹性计算结果。当接收到第二截面的超声回波信号时，可采用和步骤12同样的方法可计算出第二截面内感兴趣区域的应变量M2。
输出分别根据第一回波信号和第二回波信号计算获得的第一弹性结 果和第二弹性结果，在步骤16中，通过显示模块显示弹性计算结果，例如，在一些实施例中，数据处理模块响应于前述弹性结果的计算至少输出以下结果之一：
(1)根据第一弹性结果输出第一弹性分布图，和根据第二弹性结果输出第二弹性分布图；和，
(2)根据第一弹性结果与第二弹性结果输出各向异性参数。
还可以根据弹性结果输出弹性分布图，例如可以是根据超声回波信号获得生物组织中各个位置点对应的弹性结果，将各个位置点对应的弹性结果映射到各个位置点的空间分布上或统一坐标系中从而形成弹性分布图。在其中一个实施例中，超声探头通过按压生物组织产生形变以进行感兴趣区域弹性结果的检测，此弹性结果为感兴趣区域的准静态弹性参数。准静态弹性参数为应变量或应变率。数据处理模块还根据准静态弹性参数生成弹性成像数据。
在有的实施例中，在步骤15中还可以进一步计算各向异性参数。各向异性参数包括基于第一弹性结果与第二弹性结果的二次统计分析量，例如，各向异性参数至少包括：第一弹性结果与第二弹性结果的比值、第一弹性结果与第二弹性结果的差值、和第一弹性结果与第二弹性结果的比值或差值的函数等等中的其中之一。第一弹性结果与第二弹性结果的比值或差值的函数可以是比值或差值的平方、3次方等等。
例如，数据处理模块根据第一截面内感兴趣区域的应变量M1和第二截面内感兴趣区域的应变量M2计算各向异性参数，各向异性参数可以是M1和M2的差值，也可以是M1和M2的比值，还可以是差值或比值的其它函数。
步骤16，输出分别根据第一回波信号和第二回波信号计算获得的第一弹性结果和第二弹性结果，例如对处理结果进行显示。数据处理模块将弹性结果处理成可视化数据，并发送到显示模块进行显示，其显示方式可以是数字或文字，还可以是柱形图、饼状图、折线图等图形。
在有的实施例中，数据处理模块还可以根据截面内感兴趣区域的应变量生成应变式弹性图像数据，并在显示界面上显示弹性图像，同时还可以显示感兴趣区域的各向异性参数。
在有的实施例中，数据处理模块还可以进一步计算出不同截面内感兴趣区域的应变率，还可以进一步根据不同截面内感兴趣区域的应变率 计算该感兴趣区域的各向异性参数。
由于本实施例中按压生物组织的压力由手动产生或振动器产生，可能存在压力不均匀的现象，因此在改进的实施例中，超声弹性测量装置还可以包括压力传感器，压力传感器安装在超声探头上，用于感知压力，并将感知的压力反馈给数据处理模块，数据处理模块根据该压力对不同时间检测的应变进行归一化，比如时间t1，对应的应变量为S1，压力大小约为F1，时间t2，对应的应变量为S2，压力大小约为F2，则可以对时间2的应变结果进行归一化S2_new＝S2*F1/F2。
通常，根据生物组织的应变所进行的弹性成像称为准静态弹性成像，本实施例中，将准静态弹性成像过程中检测的弹性参数称为准静态弹性参数，应变量为准静态弹性参数中的一种，本领域技术人员应当理解，在计算组织的各向异性参数时，也可以根据其它准静态弹性参数，例如根据感兴趣区域在组织发生形变后的长度变化量ΔL，同样可以得到组织的各向异性参数。
在另一些实施例中，超声探头在生物组织的同一感兴趣区域同时或先后产生沿至少两个不同方向传播的剪切波，并发射以探测该剪切波为目的的超声波，从而形成至少两个不同的截面，超声弹性测量装置100检测不同截面的剪切波弹性参数，根据剪切波弹性参数计算感兴趣区域的各向异性参数。剪切波可以通过各种方式生成，例如通过超声探头向组织发射声波(例如超声脉冲波)从而在组织内部产生横向传播的剪切波，或通过超声探头冲击组织而产生在组织内部沿纵向传播的剪切波。本实施例的处理流程如图7所示，包括以下步骤：
步骤20，向生物组织发射声辐射力用于使生物组织产生形变。
本实施例中，超声探头还用于发射脉冲波，当用户将超声探头放置在生物组织上时，超声探头向生物组织发射脉冲波。如图8所示，超声探头101紧贴组织160的表面110，当超声探头101产生的脉冲波120冲击组织160时，由于脉冲波的波束特性，在组织160内形成聚焦点130，聚焦点130产生沿波束方向的位移，由于组织之间的粘连，因此在聚焦点130附近形成横向的剪切波140和150。在另一具体实施例中，剪切波也可以通过振动器带动探头振动以冲击组织而产生，这种剪切波弹性成像称为瞬时弹性成像。
步骤21，生成剪切波弹性成像的发射接收序列，控制超声探头向生 物组织发射第一超声波用以在生物组织内形成第一截面，接收所述第一超声波的回波，获得第一回波信号，用以检测第一截面的超声回波。本实施例中，采用剪切波弹性参数来计算各向异性参数，因此发射接收序列与进行剪切波弹性成像的发射接收序列相同，例如发射序列除了包括用于确定发射用的换能器参数和通常的发射超声波的参数外，还包括发射超声波的深度、聚焦位置、时长等，接收序列包括用于确定接收用的换能器参数、接收的角度、深度等。
在产生剪切波时，同时发射/接收序列控制模块控制超声探头向组织的感兴趣区域发射超声波并使超声波持续一段时间，该超声波扫描感兴趣区域并形成第一截面，超声探头同时接收第一截面的超声回波，获得第一回波信号。
步骤22，根据第一截面对应的第一回波信号计算第一截面内感兴趣区域的剪切波弹性参数，作为第一弹性结果。剪切波弹性参数为剪切波传播速度、杨氏模量值或剪切模量值。
数据处理模块根据所接收的回波信号，可以将剪切波传播过程中一段时间内组织的设定深度的部位的位移量计算出来，如图9所示，第一截面1091扫过剪切波的路径，通过对C点的检测可得知剪切波是否到达了C点。当C点的位移最大时，认为剪切波140到达C点，或者C点的移动速度最快时认为剪切波140到达C点，或者C点运动的相位到达了某个特定值的时刻认为是剪切波到达了该位置。可采用各种方法计算剪切波的传播速度，例如，通过剪切波140到达C点的时间可定位出剪切波的传播路径或传播轨迹，可绘制出剪切波轨迹图，根据剪切波的轨迹线可得到剪切波传播路径上各点的斜率，斜率即为剪切波的传播速度。
对于各向同性的弹性体，剪切波传播速度与杨氏模量、剪切模量间有以下近似的关系：
E＝3ρc2＝3G
其中，c表示剪切波速度，ρ表示组织密度，E表示组织的杨氏模量值，G表示组织的剪切模量。通常情况下，ρ取值为水的密度值，因此，当得到剪切波传播速度后，可进一步计算出其他弹性相关参数，比如杨氏模量、剪切模量等。
步骤23，检测第二截面的超声回波。采用与实施例一步骤13中的 同样的方法变换截面，得到第二截面的超声回波。在生物组织产生形变时，控制超声探头向感兴趣区域发射第二超声波用于在生物组织中形成第二截面，接收第二超声波的回波，获得第二截面对应的第二回波信号。
采用手动调整方式时，当用户将超声探头调整好放置在生物组织上时，通过向组织发射脉冲波或通过探头冲击组织的方式产生在组织内部传播的剪切波，同时发射/接收序列控制模块控制超声探头向组织的感兴趣区域发射超声波并使超声波持续一段时间，该超声波扫描感兴趣区域并形成第二截面，超声探头同时接收第二截面的超声回波。
采用自动调整方式时，可针对产生的同一个剪切波同时形成第一截面和第二截面，也可以两个不同的剪切波分别形成第一截面和第二截面，两个不同的剪切波可以同时产生，也可以不同时产生。例如，在其中一个实施例中，向生物组织发射第一次超声波束，使生物组织产生形变，控制超声探头向感兴趣区域发射前述第一超声波，用以获得第一回波信号；向生物组织发射第二次超声波束，使生物组织产生形变，控制超声探头向感兴趣区域发射前述第二超声波，用以获得第二回波信号。第一次超声波束与第二超声波束在生物组织内聚焦的位置不同，或者在生物组织内产生的剪切波不同。其中，向生物组织发射第一次超声波束在生物组织内产生第一剪切波，控制超声探头向第一剪切波行经的感兴趣区域发射前述第一超声波，从而获得第一回波信号。向生物组织发射第二次超声波束在生物组织内产生第二剪切波，控制超声探头向第二剪切波行经的感兴趣区域发射前述第二超声波，从而获得第二回波信号。这里的第一剪切波和第二剪切波的传播方向可以相同，也可以不相同。第一剪切波行经的感兴趣区域与第二剪切波行经的感兴趣区域为同一个感兴趣区域。在其中一个实施例中，超声探头在生物组织的同一感兴趣区域产生沿至少两个不同方向传播的剪切波，并发射以探测该剪切波为目的的超声波，从而形成至少两个不同的截面。有关第一超声波和第二超声波如何形成不同的两个截面可以参见前文相关说明。前文提到的第一剪切波和第二剪切波可以同时产生或先后产生。
步骤24，根据第二截面对应的第二超声回波信号计算第二截面内感兴趣区域的剪切波弹性参数，作为第二弹性结果。关于第二弹性结果的计算过程可以参见前述步骤22的相关说明。第一弹性结果和第二弹性结果可以直接输出到显示模块进行显示，例如在同一个显示界面上进行显 示，以方便医生对两个截面的弹性结果进行对比。在本实施例中，还可以执行步骤25。
步骤25，计算各向异性参数。数据处理模块根据第一截面内感兴趣区域的剪切波弹性参数N1和第二截面内感兴趣区域的剪切波弹性参数N2计算各向异性参数，各向异性参数可以是N1和N2的差值，也可以是N1和N2的比值，还可以是差值或比值的其它函数。
步骤26，输出分别根据第一回波信号和第二回波信号计算获得的第一弹性结果和第二弹性结果，例如对处理结果进行显示。例如通过显示模块输出弹性计算结果，例如，在一些实施例中，数据处理模块响应于前述弹性结果的计算至少输出以下结果之一：
(1)根据第一弹性结果输出第一弹性分布图，和根据第二弹性结果输出第二弹性分布图；和，
(2)根据第一弹性结果与第二弹性结果输出各向异性参数。例如，显示根据第一弹性结果和第二弹性结果计算获得的各向异性参数。步骤26具体可参见前文所述的步骤15。
在其中一个实施例中，超声探头通过在生物组织产生剪切波以进行感兴趣区域弹性结果的检测，则计算获得的弹性结果为感兴趣区域的剪切波弹性参数。剪切波弹性参数为剪切波传播速度、杨氏模量值或剪切模量值
在有的实施例中，数据处理模块还可以将某个截面内感兴趣区域的剪切波弹性参数输出至显示模块进行显示，同时显示感兴趣区域的各向异性参数。显示方式包括文字、数字和/或图形方式。
在有的实施例中，用户还可以选定多个感兴趣区域，超声弹性测量装置采用上述方式计算出多个感兴趣区域的各向异性参数，进行对比显示，或显示多个感兴趣区域的各向异性参数分布图。
对于一维的超声探头，每检测一个截面的弹性参数，则需要组织产生一次形变。对于二维或三维的超声探头，其可以每检测一个截面的弹性参数，组织产生一次形变，但也可以在组织产生一次形变后，通过发射/接收序列控制模块产生的发射序列和接收序列，同时形成不同的截面，实现同时接收不同截面的超声回波，从而可不需要组织产生多次形变。
上述实施例中，为方便理解，以两个不同的截面为例进行了描述， 本领域技术人员应当理解，也可以采用同一感兴趣区域的更多个不同截面的超声回波计算该感兴趣区域的各向异性参数。
更进一步地，在一些实施例中当然可以采用其他方式来获得相应的弹性测量结果，例如采用核磁共振MR也可以得到弹性分布或测量出弹性结果，通过调整不用的测量方向或界面。例如，在其中一个实施例中，还提供了一种弹性对比测量方法，其包括以下步骤：
步骤A1，在感兴趣区域内形成第一截面，根据第一截面计算感兴趣区域对应的第一弹性结果；
步骤A2，在感兴趣区域内形成第二截面，根据第二截面计算感兴趣区域对应的第二弹性结果；
步骤A3，根据所述第一弹性结果和第二弹性结果计算感兴趣区域的各向异性参数；
步骤A4，响应于弹性结果的计算，输出至少以下结果之一：
(1)根据所述第一弹性结果输出第一弹性分布图，和根据所述第二弹性结果输出第二弹性分布图；和，
(2)根据所述第一弹性结果与第二弹性结果显示各向异性参数。
步骤A3中，各向异性参数包括基于第一弹性结果与第二弹性结果的二次统计分析量，例如，各向异性参数至少包括：第一弹性结果与第二弹性结果的比值、第一弹性结果与第二弹性结果的差值、和第一弹性结果与第二弹性结果的比值或差值的函数等等中的其中之一。第一弹性结果与第二弹性结果的比值或差值的函数可以是比值或差值的平方、3次方等等。
本实施例中的弹性分布图是根据感兴趣区域内各个位置点对应的弹性结果，映射到感兴趣区域的空间位置分布上而形成的弹性分布图。
上述步骤A1还可参见前文相关步骤10至步骤12的相关说明，或者步骤20至步骤22的相关说明。上述步骤A2还可参见前文相关步骤13至步骤14的相关说明，或者步骤23至步骤24的相关说明。
依据本发明的实施例，当超声设备经用户操作进入多截面测试模式(例如可以是组织各向异性测量模式或弹性对比模式)时，系统对用户连续采集的两个不同截面的超声回波信号进行处理，或对用户通过按键或触摸屏选定的两个不同截面的超声回波信号进行处理，从而获得该两个截面的弹性结果，或者先得到更多个截面的弹性结果，然后在更多个 弹性结果中选定两个。然后系统对两个截面的弹性结果进行关联处理，以便将两个截面的弹性结果进行对比。关联处理例如可以是将两个截面的弹性结果进行同屏显示，以便用户通过同屏观察即可了解两个不同截面的弹性结果，其中弹性结果可以是图像，也可以是数值、文字或图表。关联处理还可以是对两个截面的弹性结果进行运算，然后输出各向异性参数。
根据前述方法或设备/装置论述，可以了解针对每个感兴趣区域对应的第一弹性结果和第二弹性结果可以获得每个感兴趣区域对应的各向异性参数，当存在多个感兴趣区域时，则可以对应获得多个感性区域对应的多个各向异性参数，因此，在其中一个实施例中，还可以输出多个各向异性参数，每个各向异性参数对应一个感兴趣区域。例如，系统根据需要，可以将不同目标区域(目标区域可以包括多个感兴趣区域)的各项各向异性参数计算出来后，进行目标区域中不同感兴趣区域之间的对比显示，或者生成多个感兴趣区域内各向异性参数分布图。又例如，在其中一个实施例中，按照多个感兴趣区域的空间位置分布，将多个感兴趣区域分别对应的各向异性参数映射到同一坐标系中，获得多个感性区域对应的各向异性参数的分布图，然后进行输出显示。
此外，前述提到的发射和接收模块可以用于在生物组织产生形变时，控制超声探头向感兴趣区域发射第一超声波，并接收所述第一超声波的回波，获得第一回波信号；在生物组织产生形变时，控制超声探头向所述感兴趣区域发射第二超声波，接收所述第二超声波的回波，获得第二回波信号。而数据处理模块用于计算第一弹性结果和第二弹性结果，以及还可以用于计算获得弹性分布图和各向异性参数。当然，发射/接收序列控制模块(102)、回波处理模块(104)和发射和接收模块(103)以及数据处理模块(105)可以集成在同一个板卡或多个板卡上，或者，发射/接收序列控制模块(102)、回波处理模块(104)，和，发射和接收模块(103)以及数据处理模块(105)中的计算过程的部分或全部可以集成在一个或多个处理器中实现。
本申请中所涉及的功能既可通过上述实施例中描述的程序的方式实现，也可通过硬件的方式实现，例如通过门电路搭建成专用集成电路。本领域技术人员可以理解，上述实施方式中各种程序可以存储于一计算机可读存储介质中，存储介质可以包括：只读存储器、随机存储器、磁 盘或光盘等，数据处理模块可通过执行程序实现上述功能。
以上应用了具体个例对本发明进行阐述，只是用于帮助理解本发明，并不用以限制本发明。对于本发明所属技术领域的技术人员，依据本发明的思想，还可以做出若干简单推演、变形或替换。

Claims (34)

  1. 一种超声弹性测量装置，其特征在于包括：
    超声探头(101)，其包括至少一个换能器，所述换能器中第一部分用于向感兴趣区域发射以检测同一感兴趣区域的弹性结果为目的的超声波，以在该感兴趣区域形成至少两个不同的截面，所述换能器中的第二部分用于接收由生物组织返回的超声回波，所述超声回波包括该感兴趣区域的至少两个不同截面的超声回波；
    发射/接收序列控制模块(102)，用于产生控制相应换能器发射超声波的发射序列和控制相应换能器接收超声回波的接收序列；
    回波处理模块(104)，用于对超声回波进行处理；
    发射和接收模块(103)，其分别与超声探头、发射/接收序列控制模块和回波处理模块电连接，用于将发射/接收序列控制模块产生的发射序列传输给超声探头，并将超声探头接收的超声回波传输给回波处理模块；
    数据处理模块(105)，其与回波处理模块连接，所述数据处理模块用于分别根据至少两个不同截面的超声回波，计算与各个截面对应的弹性结果。
  2. 如权利要求1所述的装置，其特征在于，采用以下两个方式之一实现形成至少两个不同的截面：
    所述超声探头通过变换位置和/或方向向同一感兴趣区域发射以检测该感兴趣区域的弹性结果为目的的超声波，从而形成至少两个不同的截面；和，
    所述超声探头通过以不同的发射方向或发射平面向同一感兴趣区域发射以检测该感兴趣区域的弹性结果为目的的超声波，从而形成至少两个不同的截面。
  3. 如权利要求2所述的装置，其特征在于，所述至少两个不同截面在生物组织内相交或为相互平行的面，或者，所述不同的发射方向或发射平面相交。
  4. 如权利要求1或2所述的装置，其特征在于，所述超声探头通过按压生物组织产生形变以进行感兴趣区域弹性结果的检测，所述弹性结果为感兴趣区域的准静态弹性参数。
  5. 如权利要求4所述的装置，其特征在于，所述准静态弹性参数 为应变量或应变率。
  6. 如权利要求5所述的装置，其特征在于，所述数据处理模块还根据准静态弹性参数生成弹性成像数据。
  7. 如权利要求1或2所述的装置，其特征在于，所述超声探头通过在生物组织产生剪切波以进行感兴趣区域弹性结果的检测，所述弹性结果为感兴趣区域的剪切波弹性参数。
  8. 如权利要求7所述的装置，其特征在于，所述剪切波弹性参数为剪切波传播速度、杨氏模量值或剪切模量值。
  9. 如权利要求1所述的装置，其特征在于，所述超声探头在生物组织的同一感兴趣区域产生沿至少两个不同方向传播的剪切波，并发射以探测该剪切波为目的的超声波，从而形成至少两个不同的截面。
  10. 如权利要求9所述的装置，其特征在于，所述剪切波同时产生或失后产生。
  11. 如权利要求1所述的装置，其特征在于，所述数据处理模块还用于根据至少两个弹性结果计算感兴趣区域的各向异性参数。
  12. 如权利要求1或11所述的装置，其特征在于，所述装置还包括输出模块，所述输出模块响应于计算获得的弹性结果输出至少以下结果之一：
    (1)根据与各个截面对应的弹性结果输出至少两个弹性分布图；和，
    (2)根据与各个截面对应的弹性结果输出感兴趣区域的各向异性参数。
  13. 如权利要求12所述的装置，其特征在于，所述输出模块对各向异性参数的显示方式包括文字、数字和/或图形方式。
  14. 如权利要求1所述的装置，其特征在于，数据处理模块还根据超声回波生成超声图像数据并输出至显示模块显示，所述感兴趣区域由用户在超声图像上选定。
  15. 一种弹性对比测量方法，其特征在于包括：
    在生物组织产生形变时，控制超声探头向感兴趣区域发射第一超声波；
    接收所述第一超声波的回波，获得第一回波信号；
    在生物组织产生形变时，控制超声探头向所述感兴趣区域发射第二超声波；
    接收所述第二超声波的回波，获得第二回波信号；
    根据所述第一回波信号，获得所述感兴趣区域中第一截面对应的第一弹性结果；
    根据所述第二回波信号，获得所述感兴趣区域中第二截面对应的第二弹性结果，其中第一截面不同于第二截面；
    输出所述第一弹性结果和第二弹性结果。
  16. 根据权利要求15所述的弹性对比测量方法，其特征在于，所述方法还包括：
    响应于所述弹性结果的计算至少输出以下结果之一：
    (1)根据所述第一弹性结果输出第一弹性分布图，和根据所述第二弹性结果输出第二弹性分布图；和，
    (2)根据所述第一弹性结果与第二弹性结果输出各向异性参数。
  17. 根据权利要求15所述的弹性对比测量方法，其特征在于，所述第一截面和第二截面在生物组织内相交。
  18. 根据权利要求15所述的弹性对比测量方法，其特征在于，在超声探头位于第一位置处时使生物组织产生形变，控制超声探头向感兴趣区域发射所述第一超声波；在超声探头位于第二位置处时使生物组织产生形变时，控制超声探头向所述感兴趣区域发射所述第二超声波，所述第一位置不同于第二位置。
  19. 根据权利要求15所述的弹性对比测量方法，其特征在于，所述控制超声探头向所述感兴趣区域发射第一超声波包括：
    利用超声探头向所述感兴趣区域发射沿第一发射方向的第一超声波；和，
    所述控制超声探头向所述感兴趣区域发射第二超声波包括：
    利用超声探头向所述感兴趣区域发射沿第二发射方向的第二超声波；其中，第一发射方向与第二发射方向相交。
  20. 根据权利要求16所述的弹性对比测量方法，其特征在于，所述各向异性参数包括基于第一弹性结果与第二弹性结果的二次统计分析量。
  21. 根据权利要求16所述的弹性对比测量方法，其特征在于，所述各向异性参数至少包括：所述第一弹性结果与第二弹性结果的比值、所述第一弹性结果与第二弹性结果的差值、和所述第一弹性结果与第二 弹性结果的比值或差值的函数中的其中之一。
  22. 根据权利要求15所述的弹性对比测量方法，其特征在于，使所述生物组织产生形变的方式包括通过外力振动、超声声辐射力、和利用超声探头按压中的其中之一或两种以上的结合。
  23. 根据权利要求15所述的弹性对比测量方法，其特征在于，所述在生物组织产生形变时，控制超声探头向感兴趣区域发射第一超声波包括：
    向生物组织发射第一次超声波束，使在生物组织内产生第一剪切波，控制超声探头向第一剪切波行经的感兴趣区域发射所述第一超声波；和，所述在生物组织产生形变时，控制超声探头向所述感兴趣区域发射第二超声波包括：
    向生物组织发射第二次超声波束，使在生物组织内产生第二剪切波，控制超声探头向第二剪切波行经的感兴趣区域发射所述第二超声波；
    其中，第一剪切波行经的感兴趣区域与第二剪切波行经的感兴趣区域为同一个感兴趣区域。
  24. 根据权利要求23所述的弹性对比测量方法，其特征在于，所述第一剪切波和第二剪切波的传播方向不相同。
  25. 根据权利要求16所述的弹性对比测量方法，其特征在于，感兴趣区域有多个，所述方法包括：根据每个感兴趣区域对应的第一弹性结果和第二弹性结果获得每个感兴趣区域对应的各向异性参数，从而得到多个感性区域对应的多个各向异性参数，输出多个各向异性参数。
  26. 根据权利要求25所述的弹性对比测量方法，其特征在于，所述输出多个各向异性参数包括：
    按照所述多个感兴趣区域的空间位置分布，将多个感兴趣区域分别对应的各向异性参数映射到同一坐标系中，获得多个感性区域对应的各向异性参数的分布图。
  27. 一种弹性对比测量方法，其特征在于包括：
    在感兴趣区域内形成第一截面，根据第一截面计算感兴趣区域对应的第一弹性结果；
    在感兴趣区域内形成第二截面，根据第二截面计算感兴趣区域对应的第二弹性结果；
    根据所述第一弹性结果和第二弹性结果计算感兴趣区域的各向异 性参数；
    响应于弹性结果的计算输出至少以下结果之一：
    (1)根据所述第一弹性结果输出第一弹性分布图，和根据所述第二弹性结果输出第二弹性分布图；和，
    (2)根据所述第一弹性结果与第二弹性结果显示各向异性参数。
  28. 根据权利要求27所述的弹性对比测量方法，其特征在于，所述第一截面和第二截面在生物组织内相交或为相互平行的面。
  29. 根据权利要求27所述的弹性对比测量方法，其特征在于，所述向异性参数至少包括：所述第一弹性结果与第二弹性结果的比值、所述第一弹性结果与第二弹性结果的差值、和所述第一弹性结果与第二弹性结果的比值或差值的函数等等中的其中之一。
  30. 根据权利要求27所述的弹性对比测量方法，其特征在于，所述方法还包括：
    根据每个感兴趣区域对应的第一弹性结果和第二弹性结果获得每个感兴趣区域对应的各向异性参数，从而得到多个感性区域对应的多个各向异性参数，输出多个各向异性参数。
  31. 根据权利要求30所述的弹性对比测量方法，其特征在于，所述输出多个各向异性参数包括：
    按照所述多个感兴趣区域的空间位置分布，将多个感兴趣区域分别对应的各向异性参数映射到同一坐标系中，获得多个感性区域对应的各向异性参数的分布图进行显示。
  32. 一种超声弹性测量装置，其特征在于包括：
    超声探头，其包括至少一个换能器，所述换能器中第一部分用于向感兴趣区域发射以检测同一感兴趣区域的弹性结果为目的的超声波，以在该感兴趣区域形成至少两个不同的截面，所述换能器中的第二部分用于接收由生物组织返回的超声回波，所述超声回波包括该感兴趣区域的至少两个不同截面的超声回波；
    发射和接收模块，其与超声探头电连接，用于在生物组织产生形变时，控制超声探头向感兴趣区域发射第一超声波，并接收所述第一超声波的回波，获得第一回波信号；在生物组织产生形变时，控制超声探头向所述感兴趣区域发射第二超声波，接收所述第二超声波的回波，获得第二回波信号；
    数据处理模块，用于根据所述第一回波信号，获得所述感兴趣区域中第一截面对应的第一弹性结果；根据所述第二回波信号，获得所述感兴趣区域中不同于第一截面的第二截面对应的第二弹性结果，输出所述第一弹性结果和第二弹性结果。
  33. 根据权利要求32所述的装置，其特征在于，还包括输出模块，所述输出模块响应于第一弹性结果和第二弹性结果输出至少以下结果之一：
    (1)根据所述第一弹性结果输出第一弹性分布图，和根据所述第二弹性结果输出第二弹性分布图；和，
    (2)根据所述第一弹性结果与第二弹性结果输出各向异性参数。
  34. 一种超声弹性测量装置，其特征在于包括：
    超声探头，其包括至少一个换能器，所述换能器用于向感兴趣区域发射超声波，在同一感兴趣区域内形成第一截面和第二截面；和，
    数据处理模块，用于根据第一截面计算感兴趣区域对应的第一弹性结果，根据第二截面计算感兴趣区域对应的第二弹性结果，根据所述第一弹性结果和第二弹性结果计算感兴趣区域的各向异性参数，响应于弹性结果的计算输出至少以下结果之一：
    (1)根据所述第一弹性结果输出第一弹性分布图，和根据所述第二弹性结果输出第二弹性分布图；和，
    (2)根据所述第一弹性结果与第二弹性结果显示各向异性参数。
PCT/CN2017/106897 2017-10-19 2017-10-19 一种超声弹性测量装置及弹性对比测量方法 Ceased WO2019075697A1 (zh)

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