WO2019196103A1 - 超声成像方法及超声成像设备 - Google Patents

超声成像方法及超声成像设备 Download PDF

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Publication number
WO2019196103A1
WO2019196103A1 PCT/CN2018/083010 CN2018083010W WO2019196103A1 WO 2019196103 A1 WO2019196103 A1 WO 2019196103A1 CN 2018083010 W CN2018083010 W CN 2018083010W WO 2019196103 A1 WO2019196103 A1 WO 2019196103A1
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Prior art keywords
image
elastic image
sequence
frames
elastic
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PCT/CN2018/083010
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English (en)
French (fr)
Inventor
李双双
王泽兵
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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 CN201880060582.9A priority Critical patent/CN111093521B/zh
Priority to CN202210540700.4A priority patent/CN114848011B/zh
Priority to PCT/CN2018/083010 priority patent/WO2019196103A1/zh
Publication of WO2019196103A1 publication Critical patent/WO2019196103A1/zh
Priority to US17/068,744 priority patent/US11813117B2/en
Anticipated expiration legal-status Critical
Priority to US18/372,647 priority patent/US20240016479A1/en
Ceased legal-status Critical Current

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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
    • A61B8/48—Diagnostic techniques
    • A61B8/488—Diagnostic techniques involving Doppler signals
    • 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
    • A61B8/08—Clinical applications
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/08—Clinical applications
    • A61B8/0833—Clinical applications involving detecting or locating foreign bodies or organic structures
    • A61B8/085—Clinical applications involving detecting or locating foreign bodies or organic structures for locating body or organic structures, e.g. tumours, calculi, blood vessels, nodules
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
    • 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
    • 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
    • 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
    • A61B8/54—Control of the diagnostic device
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
    • G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
    • G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
    • G01S7/52019—Details of transmitters
    • G01S7/5202—Details of transmitters for pulse systems
    • G01S7/52022—Details of transmitters for pulse systems using a sequence of pulses, at least one pulse manipulating the transmissivity or reflexivity of the medium
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
    • G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
    • G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
    • G01S7/52023—Details of receivers
    • G01S7/52036—Details of receivers using analysis of echo signal for target characterisation
    • G01S7/52042—Details of receivers using analysis of echo signal for target characterisation determining elastic properties of the propagation medium or of the reflective target
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
    • G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
    • G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
    • G01S7/52085—Details related to the ultrasound signal acquisition, e.g. scan sequences

Definitions

  • the present application relates to the field of medical ultrasound imaging, and in particular to an ultrasound imaging method and an ultrasound imaging apparatus.
  • Ultrasound elastography is one of the hotspots of clinical research in recent years. It mainly reflects the elasticity and softness of tissues. It has been applied more and more in the auxiliary detection of cancerous lesions, benign and malignant discrimination and prognosis evaluation. According to different imaging principles, ultrasound elastography is mainly divided into two categories: one is strain-type elastic imaging technology, and the other is shear wave elastic imaging technology.
  • the strain-type elastography method mainly produces a certain deformation by pressing the tissue by the probe, and then calculates and images the parameters related to the tissue elasticity such as strain and strain rate, and indirectly reflects the elasticity difference between different tissues. Since the strain parameters are sensitive to pressure, the pressure applied by the probe in this method needs to be as uniform as possible, which places high demands on the operator's technique.
  • the shear wave elastography method mainly reflects the difference in hardness between tissues by generating a shear wave propagation inside the tissue and detecting its propagation parameters (such as propagation speed) for imaging. This type of elastography has improved stability and repeatability because it no longer relies on the operator's specific pressure on the tissue, and quantitative measurements make the diagnosis of the doctor more convenient and objective.
  • the shear wave elastography method based on acoustic radiation force is a more versatile method on the market. It mainly transmits special shear pulses to the inside of the tissue, and the shear wave is generated in the tissue based on the acoustic radiation force effect. Ultrasonic detection sequence is used to record the propagation process of the above shear wave, and finally calculate the parameters related to tissue elasticity to realize elastic imaging.
  • This elastography method can currently achieve real-time image display, but due to the safe output limitation of ultrasonic energy, the actual refresh frame rate of the elastic image is low.
  • the present application provides an ultrasonic imaging method and an ultrasonic imaging apparatus, which perform an inter-frame processing on the obtained elastic echo data or an elastic image to form a new elastic image, thereby improving the display frame rate of the elastic image.
  • a first aspect of the present application provides an ultrasound imaging method, the method comprising:
  • the inter-frame processing process includes determining at least one frame of the target elastic image according to the at least two frames of the elastic image to obtain a second elastic image frame sequence, and displaying the second elastic image frame sequence; wherein the first The number of frames of the second elastic image frame sequence is greater than the number of frames of the first elastic image frame sequence.
  • a second aspect of the present application provides an ultrasound imaging method, the method comprising:
  • the first elastic image frame sequence comprising at least two frames of elastic images
  • the inter-frame process includes: determining at least one frame of the target elastic image according to the at least two frames of the elastic image to obtain a second elastic image frame sequence, and displaying the second elastic image frame sequence; wherein the second elastic image frame sequence The number of frames is greater than the number of frames of the first elastic image frame sequence.
  • a third aspect of the present application provides an ultrasound imaging method, the method comprising:
  • a third sequence of image frames of the first mode is displayed.
  • a fourth aspect of the present application provides an ultrasound imaging apparatus, the ultrasound imaging apparatus comprising:
  • a transmit/receive sequence controller that activates the ultrasonic probe to transmit a first ultrasonic wave to a target area of the object to be tracked to track a shear wave propagating within the target area; and receive a return from the target area The ultrasonic echo of the first ultrasonic wave to obtain first echo data;
  • the processor obtains a first elastic image frame sequence of the target area according to the first echo data, and performs an inter-frame processing process; the first elastic image frame sequence includes at least two frames of elastic images;
  • the inter-frame processing includes determining at least one frame target elasticity image according to the at least two frames of elasticity images to obtain a second elastic image frame sequence, and displaying the second elastic image frame sequence; wherein the second elastic image frame sequence is The number of frames is greater than the number of frames of the first sequence of elastic image frames.
  • a fifth aspect of the present application provides an ultrasound imaging apparatus, the ultrasound imaging apparatus comprising:
  • the display displaying a first sequence of elastic image frames, the first sequence of elastic image frames comprising at least two frames of elastic images;
  • a processor that receives the first operation and performs an inter processing process according to the first operation
  • the inter-frame process includes: determining at least one frame of the target elastic image according to the at least two frames of the elastic image to obtain a second elastic image frame sequence, and displaying the second elastic image frame sequence; wherein the second elastic image frame sequence The number of frames is greater than the number of frames of the first elastic image frame sequence.
  • a sixth aspect of the present application provides an ultrasound imaging apparatus, the ultrasound imaging apparatus comprising:
  • a transmit/receive sequence controller that activates the ultrasonic probe to transmit a first ultrasonic wave to a target region of the object to be measured, and receive an ultrasonic echo of the first ultrasonic wave returned from the target region to obtain a first Echo data
  • the processor obtaining a first image frame sequence of the first mode of the target region according to the first echo data
  • the transmitting/receiving sequence controller excites the ultrasonic probe to transmit a second ultrasonic wave to a target area of the object to be measured, and receive an ultrasonic echo of the second ultrasonic wave returned from the target area to obtain second echo data;
  • the processor obtains a second image frame sequence of the second mode of the target region according to the second echo data
  • the processor determines at least one frame of the target image of the first mode according to the first image frame sequence and the second image frame sequence to obtain a third image frame sequence of the first mode; wherein the frame of the third image frame sequence The number is greater than the number of frames of the first sequence of image frames;
  • a display that displays a third sequence of image frames of the first mode.
  • a first ultrasonic wave is transmitted to a target area of the measured object to track a shear wave propagating in the target area; and an ultrasonic echo of the first ultrasonic wave returned from the target area is received.
  • the number of frames of the second elastic image frame sequence obtained is larger than the number of frames of the original first elastic image frame sequence. Therefore, the display frame rate of the obtained second elastic image frame sequence is higher than the display frame rate of the original first elastic image frame sequence, thereby increasing the display frame rate of the elastic image.
  • FIG. 1 is a schematic structural view of an ultrasonic imaging apparatus provided by the present application.
  • FIG. 2 is a schematic flow chart of an ultrasonic imaging method provided by the present application.
  • FIG. 3 is a schematic diagram of a transmit/receive sequence frame provided by the present application.
  • FIG. 5 is a schematic diagram of frame shifts provided by the present application.
  • FIG. 6 is another schematic structural diagram of an ultrasonic imaging apparatus provided by the present application.
  • FIG. 7 is another schematic flowchart of an ultrasonic imaging method provided by the present application.
  • FIG. 8 is another schematic flow chart of the ultrasonic imaging method provided by the present application.
  • FIG. 1 is a block diagram showing the structure of an ultrasonic imaging apparatus 10 in an embodiment of the present application.
  • the ultrasound imaging apparatus 10 may include an ultrasound probe 100, a transmit/receive selection switch 101, a transmit/receive sequence controller 102, a processor 103, and a display 104.
  • the transmit/receive sequence controller 102 can excite the ultrasonic probe 100 to transmit ultrasonic waves to a target object, and can also control the ultrasonic probe 100 to receive ultrasonic echoes returned from the target object, thereby obtaining an ultrasonic echo signal.
  • the processor 103 processes the ultrasonic echo signal to obtain an ultrasound image of the target object.
  • the ultrasound images obtained by processor 103 can be stored in memory 105, which can be displayed on display 104.
  • the display 104 of the ultrasonic imaging device 10 may be a touch display screen, a liquid crystal display, or the like, or may be an independent display device such as a liquid crystal display or a television independent of the ultrasonic imaging device 10 . It is a display on electronic devices such as mobile phones and tablets.
  • the memory 105 of the foregoing ultrasound imaging apparatus 10 may be a flash memory card, a solid state memory, a hard disk, or the like.
  • the embodiment of the present application further provides a computer readable storage medium, where the computer readable storage medium stores a plurality of program instructions, and after the plurality of program instructions are executed by the processor 103, the ultrasound in each embodiment of the present application may be performed. Part or all of the steps in the imaging method or any combination of the steps therein.
  • the computer readable storage medium can be a memory 105, which can be a nonvolatile storage medium such as a flash memory card, solid state memory, hard disk, or the like.
  • the processor 105 of the foregoing ultrasound imaging apparatus 10 may be implemented by software, hardware, firmware, or a combination thereof, and may use a circuit, a single or multiple application specific integrated circuits (ASICs), a single or a plurality of general purpose integrated circuits, single or multiple microprocessors, single or multiple programmable logic devices, or a combination of the foregoing circuits or devices, or other suitable circuits or devices such that the processor 105 can perform the various implementations described above The corresponding steps of the ultrasound imaging method in the example.
  • ASICs application specific integrated circuits
  • an ultrasound imaging method provided by an embodiment of the present application is applied to an ultrasound imaging apparatus 10, and is particularly suitable for an ultrasound imaging apparatus 10 including a touch display screen.
  • the ultrasonic imaging apparatus 10 can generate an elastic image using ultrasonic echo data, and can also generate a conventional ultrasonic B image or a Doppler image or the like using the ultrasonic echo data.
  • Embodiments of the ultrasound imaging method in this application include:
  • the ultrasonic imaging apparatus 10 excites the ultrasonic probe 100 to emit a first ultrasonic wave to a target area of the object to be measured by the transmitting/receiving sequence controller 102 to track the shear wave propagating in the target area.
  • the target area can be determined according to the requirements of the elastic measurement, and the determination manner can be determined by using various conventional imaging detection methods such as conventional two-dimensional B-mode imaging, conventional elastic imaging E mode, and the like, or can be selected according to the detection requirements.
  • the number of the target areas may be one or more.
  • the respective longitudinal depths or lateral positions of the plurality of target areas may be different.
  • the shear wave can be generated using external vibrations, such as using external vibrations to generate shear waves into the deep tissue of the target area.
  • an ultrasonic pulse acoustic radiation force effect may be used to generate a shear wave inside the tissue of the target region; or a physiological motion (for example, a heart beat, a blood vessel beat, etc.) in the measured object may be utilized to generate a shear wave; Etc., not described in detail here.
  • This specification is only a brief description of one of the more common methods: ultrasonic shear wave elastography based on acoustic radiation force.
  • the ultrasonic shear wave elastography with acoustic radiation force, the shear wave propagating in the target region can be excited by the transmitting/receiving sequence controller 102 of the present embodiment to transmit the ultrasonic probe 100 to the tissue for a specific waveform, length, and specific frequency.
  • An ultrasonic pulse that produces an acoustic radiation force effect inside the tissue which in turn produces shear waves that propagate through the tissue.
  • a series of ultrasound waves are then transmitted to the tissue for tracking the propagation of the shear waves described above in the tissue. It is also possible to transmit an ultrasonic pulse of a specific waveform, length, and specific frequency to the tissue by other ultrasonic devices, and the same effect can be achieved based on the acoustic radiation force effect generated by the ultrasonic pulse.
  • the processor 103 controls the ultrasonic probe 100 to receive the ultrasonic echo of the first ultrasonic wave returned from the target area by the transmission/reception sequence controller 102 to obtain first echo data.
  • the processor 103 processes the first echo data obtained in step 202 to obtain at least two frames of elastic images of the target area to form an elastic image frame sequence.
  • the processor 103 performs an inter-frame processing.
  • the inter-frame processing includes determining at least one frame target elasticity image according to the at least two frames of elasticity images to obtain a second elastic image frame sequence, and displaying the second elastic image frame sequence; wherein the second elastic image frame sequence is The number of frames is greater than the number of frames of the first sequence of elastic image frames.
  • the processor 103 calculates at least one frame of the target elastic image according to the at least two frames of the elastic image obtained in step 203 to obtain a second elastic image frame sequence.
  • the second elastic image frame sequence may include all or part of the sequence of the at least one frame target elastic image and the first elastic image frame; or may include only the at least one frame target elastic image.
  • the first elastic image frame sequence is E1, E2.
  • the second elastic image frame sequence may be E1, EX, E2; wherein EX represents a frame of the target elastic image in the at least one frame target elastic image.
  • the first elastic image frame sequence is E1, E2, E3.
  • the second elastic image frame sequence may be E1, EX, EY, EZ, E3; wherein EX, EY, EZ represents a three-frame target elastic image in the at least one frame target elastic image.
  • the above elastic images can be combined with other types of images to simultaneously display a plurality of imaging modes.
  • the embodiment in combination with a B-type, a C-type, or a PW-type image, the embodiment is not limited.
  • elastography hereinafter referred to as E-type imaging
  • B-type imaging in combination with a B-type image, elastography (hereinafter referred to as E-type imaging) and B-type imaging can be simultaneously achieved.
  • the ultrasound imaging apparatus 10 excites the ultrasound probe 100 to transmit a second ultrasound wave to a target area of the object to be measured by the transmission/reception sequence controller 102; and controls the ultrasound probe 100 to receive from the transmission/reception sequence controller 102.
  • the ultrasonic echo of the second ultrasonic wave returned by the target area is used to obtain second echo data.
  • This second echo data can be used to implement Type B imaging or C-type imaging.
  • the first echo data described above can be used to implement E-type imaging.
  • the processor 103 processes the obtained second echo data to obtain a B-type image frame sequence or a C-type image frame sequence of the target area; and the control display 104 displays the B-type image frame sequence or the C-type image frame sequence. In this way, B-type imaging and E-type imaging, or C-type imaging and E-type imaging are realized.
  • the ultrasound imaging apparatus 10 needs to transmit/receive at least two types of ultrasound sequence frames, such as B-sequence frames and E-sequence frames.
  • the B-sequence frame refers to an ultrasound transmit-receive sequence for generating a frame of conventional B-type imaging, and the specific imaging sequence composition thereof is not detailed herein.
  • the E-sequence frame refers to an ultrasound transmit receive sequence used to generate one frame of E-type imaging.
  • the E-sequence frame first includes an ultrasonic pulse for generating a shear wave, and under the action of the ultrasonic pulse, a shear wave is generated to propagate inside the tissue. Then it is necessary to transmit a series of detection pulses to the internal target area of the tissue for a period of time, and receive the ultrasonic echo signals thereof for recording the propagation process of the shear waves in the tissue.
  • the generation of the shear waves is described in the relevant step in step 201. I will not elaborate on it.
  • the ultrasonic echo signals of the B-sequence frames can be used to implement B-type imaging
  • the ultrasonic echo signals of the E-sequence frames can be used to implement E-type imaging.
  • two sequence frames can be alternately performed, and the transmission frame rate of the B-sequence frame is different from the transmission frame rate of the E-sequence frame.
  • a multi-frame B-sequence frame is often included between two consecutively repeated E-sequence frames. As shown in Figure 3, each sequence frame means that a complete image display can be performed.
  • the method for determining the at least one frame of the target elastic image to obtain the second elastic image frame sequence may be various, which is not limited in this embodiment.
  • the at least one frame target elastic image may be determined by interpolation or according to a fixed weighting coefficient set by the system, and the at least one frame target elastic image may be generated between adjacent two frames of the elastic images of the first elastic image frame sequence.
  • the processor 103 may determine the first elastic image and the second elastic image from at least two frames of the elastic image of the first elastic image frame sequence; wherein the first elastic image and the second elastic image may be adjacent
  • the elastic image may also be an elastic image that is not adjacent.
  • the processor 103 determines a time interval of the first elastic image and the second elastic image; and generates at least one frame target elastic image according to the time interval of the first elastic image and the second elastic image to obtain the second elastic image frame sequence .
  • the time interval between each type of sequence frame may be fixed, for example, the time interval between any two adjacent B sequence frames is fixed, between any two adjacent E sequence frames.
  • the time interval is also fixed. But the two time intervals can be different. Therefore, in FIG. 3, taking the B series frame as an example, the time interval is the same regardless of whether or not E sequence frames are inserted between two adjacent B sequence frames. The shorter the time interval, the higher the transmission frame rate.
  • the transmit frame rate of the B-sequence frame is higher than the transmit frame rate of the E-sequence frame.
  • interpolation may be performed using B-sequence frames or C-sequence frames interspersed with E-sequence frames.
  • the generating the at least one frame target elastic image according to the time interval of the first elastic image and the second elastic image includes:
  • each E-sequence frame can be calculated to obtain an E-type image, so the display frame rate of the E-type image is also low.
  • the transmission frame rate of the B-sequence frame may be higher than the transmission frame rate of the E-sequence frame, so the display frame rate of the B-sequence frame is relatively higher.
  • the ultrasonic imaging device 10 can synchronously display the image results corresponding to the adjacent B-sequence frame and the E-sequence frame, so that the user can refer to the B-type image and the E-type image at the same time.
  • the B-type image contains tissue structure information
  • the E-type image contains tissue hardness related information. Therefore, most B-type images do not have a corresponding synchronous E-type image to choose from.
  • the processor 103 determines that the number of frames of the B-type image associated with the first elastic image and the second elastic image may be the first elastic image and the second elastic image. The sum of the interpolated B-type image, the B-type image adjacent to the first elastic image, and the number of frames of the B-type image adjacent to the second elastic image.
  • the first elastic image and the second elastic image may be adjacent two-frame E-type images.
  • the processor 103 passes the adjacent two frames of the E-type image (hereinafter referred to as the first E-type image and the second E-type image) or the echo data of the two-frame E-sequence frame and the first E-type image and the second E-type
  • the number of frames of the B-type image associated with the image is calculated, and the E-sequence frame corresponding to the B-sequence frame inserted in the middle is calculated. As shown in FIG.
  • the E1 sequence frame is the E-sequence frame associated with the B1 sequence frame
  • the E2 sequence is The frame is the E-sequence frame associated with the B2 sequence frame
  • the B2 sequence frame and the B3 sequence frame have no associated E-sequence frames, so the associated E-sequence frame needs to be calculated by inter-frame processing.
  • the interframe processing there are many ways to calculate the interframe processing, and the interpolation method is taken as an example for illustration.
  • the B-sequence frames between two adjacent E-sequence frames have their respective times fixed, and can be directly interpolated according to the distance between the corresponding time of each B-sequence frame and the two E-sequence frame times.
  • an E-sequence frame associated with each B-sequence frame is calculated. As shown in FIG. 4, if the time intervals between the B1, B2, B3, and B4 sequence frames are all equal, the results of the interpolation calculation are as follows:
  • each B-sequence frame has an associated E-sequence frame, and the display frame rate of the E-type image is increased to be consistent with the B-type image display frame rate.
  • a B-sequence frame between two adjacent E-sequence frames may have a target tissue motion during imaging, resulting in a large displacement between B-sequence frames.
  • Interpolation is only performed according to the time interval, and the position of the B-sequence frame cannot be well matched. Therefore, further calculations can be made in conjunction with the tracking method.
  • generating the at least one frame target elasticity image according to the number of frames of the B-type image or the number of frames of the C-type image and the time interval of the first elastic image and the second elastic image includes:
  • the tracking method can be used to first determine the displacement generated after the target tissue is in motion, and continue to be based on the above-mentioned scenarios in which B-type imaging and E-type imaging can be simultaneously performed.
  • the tracking method can be used to calculate the displacement-related parameters between the B-sequence frames, and the E-sequence frames are adjusted according to the direction and amplitude of the displacement, and then interpolated in combination with the time interval. If the position of the B2 sequence frame changes relative to the B1 sequence frame as shown in FIG. 4, the whole distance is shifted by a certain distance. As shown in FIG. 5, each data point in the E sequence frame associated with the B2 sequence frame is calculated by interpolation ( For example, when the local data point is shown, the E data information at the same position as the data point in the B1 and B4 sequence frames should be taken.
  • FIG. 5 is only shown as an example. In practical applications, the displacement direction and amplitude of each local data point position in the B-sequence frame may be different. Therefore, the local data points may be separately calculated and processed as needed.
  • generating the at least one frame target elastic image according to the time interval of the first elastic image and the second elastic image comprises:
  • two frames of adjacent elastic images a first E-type image E1 and a second E-type image E2, calculate a third E-type image E3 and a fourth E-type image E4 according to preset weighting coefficients.
  • the display frame rate of the E-type image is improved.
  • the manner of generating at least one frame of the target elastic image by using the preset weighting coefficient to increase the display frame rate can be applied to the simplex working mode.
  • the simplex mode of operation may include: generating a B-sequence frame to achieve an operational mode of B-type imaging, generating a C-sequence frame to achieve an operational mode of C-type imaging, generating an E-sequence frame to achieve an E-type imaging mode of operation, or generating PW sequence frames to achieve PW-type imaging mode of operation.
  • the E sequence frame associated with the B sequence frame is calculated by the interframe processing, it is not necessary to calculate the associated E sequence frame for each B sequence frame, and the associated E can be calculated only for the partial B sequence frame.
  • the sequence frame, the number of frames of the final E-sequence frame thus formed is increased, and thus the display frame rate of the E-type image is also improved.
  • an ultrasound sequence for performing color Doppler imaging may be simultaneously inserted.
  • a C-sequence frame or the like it is not limited to the combination of each type of sequence frames.
  • the ultrasonic imaging method of the present application can directly display a new high frame rate E-type image after inter-frame processing in real-time imaging. It is also possible to display the original E-type image first in real-time imaging. After the image acquisition is completed, the user can start inter-frame processing by the operation of a control button or a button to form a new high-frame rate E-type image.
  • the method further includes:
  • the first elastic image frame sequence is displayed; the first elastic image frame sequence can be understood as an original E-type image.
  • the inter-frame processing process includes:
  • the user initiates inter-frame processing by a control button, a button or a voice indication to form a new high frame rate E-type image and displays a new high frame rate E-type image.
  • the inter-frame processing process is understood by referring to the related description in step 204, and details are not described herein again.
  • the original E-type image and the high frame rate E-type image can also be freely switched.
  • the ultrasound imaging method further includes:
  • the switching process includes: switching a currently displayed first elastic image frame sequence to display a second elastic image frame sequence; or, displaying the second currently displayed frame
  • the sequence of elastic image frames is switched to display a sequence of first elastic image frames.
  • the user displays the new high frame rate E-type image after the inter-frame processing is started by the operation of the control button, the button or the voice indication, and the user can further display the currently displayed by buttons, buttons or voice instructions.
  • the new high frame rate E-type image is switched to display the original E-type image.
  • the original E-type image and the new high-frame rate E-type image can be freely switched by operations such as buttons, buttons, or voice indications, and the operation mode and switching frequency are not limited herein.
  • the ultrasonic imaging method of the present application can also be extended to other imaging modes having at least two different ultrasound sequence frames at the same time, for example, when a B-sequence frame and a C-sequence frame appear simultaneously in the color blood flow mode, the ultrasound of the present application can be passed at this time.
  • the imaging method performs inter-frame processing on the B-sequence frame and/or the C-sequence frame to improve the display frame rate.
  • the B-sequence frame and the PW sequence frame may be inter-frame processed by the ultrasonic imaging method of the present application to improve the display frame rate.
  • the ultrasound imaging apparatus 10 transmits a first ultrasonic wave to a target area of the object to be measured by the transmission/reception sequence controller 102 to track a shear wave propagating in the target area; receiving from the target area Returning the ultrasonic echo of the first ultrasonic wave to obtain first echo data; obtaining, by the processor 103, the first elastic image frame sequence of the target region according to the first echo data; determining according to the at least two frames of the elastic image At least one frame of the target elastic image to obtain a second elastic image frame sequence, and displaying the second elastic image frame sequence.
  • the sequence of the second elastic image frame can be understood by referring to the description of the above step 204, and details are not described herein again.
  • the display frame rate of the obtained second elastic image frame sequence is higher than the display frame rate of the original first elastic image frame sequence, thereby increasing the display frame rate of the elastic image.
  • FIG. 6 is a block diagram showing the structure of an ultrasound imaging apparatus 60 in the embodiment of the present application.
  • the ultrasound imaging device 60 can include a processor 601 and a display 602.
  • the processor 601 can process the obtained ultrasonic echo signals to obtain an ultrasound image of the target object.
  • the ultrasound images obtained by processor 601 can be stored in memory 603, which can be displayed on display 602.
  • the display 602 of the ultrasonic imaging device 60 may be a touch display screen, a liquid crystal display, or the like, or may be an independent display device such as a liquid crystal display or a television independent of the ultrasonic imaging device 60, or may be a mobile phone. Display on electronic devices such as tablets.
  • the memory 603 of the foregoing ultrasonic imaging device 60 may be a flash memory card, a solid state memory, a hard disk, or the like.
  • the embodiment of the present application further provides a computer readable storage medium, where the computer readable storage medium stores a plurality of program instructions, and after the plurality of program instructions are executed by the processor 601, the ultrasound in each embodiment of the present application may be performed. Part or all of the steps in the imaging method or any combination of the steps therein.
  • the computer readable storage medium can be a memory 603, which can be a nonvolatile storage medium such as a flash memory card, solid state memory, hard disk, or the like.
  • the processor 601 of the foregoing ultrasonic imaging device 60 may be implemented by software, hardware, firmware, or a combination thereof, and may use a circuit, a single or multiple application specific integrated circuits (ASICs), a single or a plurality of general purpose integrated circuits, single or multiple microprocessors, single or multiple programmable logic devices, or a combination of the foregoing circuits or devices, or other suitable circuits or devices such that the processor 601 can perform the various implementations described above The corresponding steps of the ultrasound imaging method in the example.
  • ASICs application specific integrated circuits
  • an ultrasound imaging method provided by an embodiment of the present application is applied to an ultrasound imaging apparatus 60, and is particularly suitable for an ultrasound imaging apparatus 60 including a touch display screen.
  • the ultrasonic imaging apparatus 60 may generate an elastic image using ultrasonic echo data, or may generate a conventional ultrasonic B image or a Doppler image or the like using the ultrasonic echo data.
  • Embodiments of the ultrasound imaging method in this application include:
  • the present application also provides an ultrasound imaging method, please refer to FIG. 7, the method includes:
  • the first elastic image frame sequence can be obtained by: transmitting, by the ultrasonic probe, a first ultrasonic wave to a target area of the object to be tracked to track a shear wave propagating in the target area; and receiving the first return from the target area An ultrasonic echo of the ultrasonic wave to obtain first echo data; and obtaining a first elastic image frame sequence of the target region based on the first echo data.
  • the first elastic image frame sequence may be an elastic image stored locally or an elastic image acquired in real time.
  • the ultrasound imaging device 60 may directly acquire the first stored sequence of elastic image frames, or may obtain the first sequence of elastic image frames by wired or wireless data transmission. Further, the ultrasound imaging device 60 controls the display 602 to display the first sequence of elastic image frames.
  • the inter-frame process includes: determining at least one frame of the target elastic image according to the at least two frames of the elastic image to obtain a second elastic image frame sequence, and displaying the second elastic image frame sequence; wherein the second elastic image frame sequence The number of frames is greater than the number of frames of the first elastic image frame sequence.
  • the user initiates an inter-frame process by a control button, a button, or a voice indication to form a new high frame rate elastic image, and displays a new high frame rate elastic image.
  • the inter-frame processing process is understood by referring to the related description of step 204 in the foregoing embodiment, and details are not described herein again.
  • the first elastic image frame sequence is obtained, and the first elastic image frame sequence is displayed; the first elastic image frame sequence includes at least two frames of elastic images; and the first operation is received, according to the at least The two-frame elastic image determines at least one frame of the target elastic image to obtain a second elastic image frame sequence, and displays the second elastic image frame sequence.
  • the sequence of the second elastic image frame can be understood by referring to the description of the above step 204, and details are not described herein again.
  • the display frame rate of the obtained second elastic image frame sequence is higher than the display frame rate of the original first elastic image frame sequence, thereby increasing the display frame rate of the elastic image.
  • the original elastic image and the high frame rate elastic image can also be freely switched.
  • the ultrasound imaging method further includes:
  • the switching process includes: switching a currently displayed first elastic image frame sequence to display a second elastic image frame sequence; or: displaying the currently displayed first The second elastic image frame sequence is switched to display the first elastic image frame sequence.
  • a new high frame rate elastic image is displayed, and the user can further display the new display by buttons, buttons, or voice instructions.
  • the high frame rate elastic image is switched to display the original elastic image.
  • the original elastic image and the new high frame rate elastic image can be freely switched by operations such as buttons, buttons or voice instructions, and the operation mode and switching frequency are not limited here.
  • the present application also provides an ultrasound imaging method to which the ultrasound imaging apparatus 10 is applied.
  • the method includes:
  • the ultrasound imaging apparatus 10 excites the ultrasound probe 100 to transmit a first ultrasonic wave to a target area of the object to be measured, and receive an ultrasonic echo of the first ultrasonic wave returned from the target area by the transmitting/receiving sequence controller 102. Obtain the first echo data.
  • the processor 103 processes the first echo data obtained in step 802 to obtain at least two frames of elastic images of the target area, and forms a first image frame sequence of the first mode of the target area.
  • the ultrasound imaging apparatus 10 excites the ultrasound probe 100 to transmit a second ultrasonic wave to a target area of the object to be measured, and receive an ultrasonic echo of the second ultrasonic wave returned from the target area by the transmitting/receiving sequence controller 102. Obtain second echo data.
  • the processor 103 processes the second echo data obtained in step 803 to obtain at least two frames of elastic images of the target area, and forms a second image frame sequence of the second mode of the target area.
  • the first mode and the second mode may be an operation mode for generating a B-sequence frame to implement B-type imaging, an operation mode for generating a C-sequence frame to implement C-type imaging, an operation mode for generating an E-sequence frame to realize E-type imaging, And any combination of the two modes of operation, such as generating a PW sequence frame to achieve a PW-type imaging mode of operation.
  • the first mode is an operation mode for generating an E-sequence frame to implement E-type imaging
  • the second mode is an operation mode for generating a B-sequence frame to implement B-type imaging; for example, the first mode is to generate a C-sequence frame to implement C.
  • the mode of operation of the type imaging, the second mode is the mode of operation for generating B-sequence frames to achieve B-mode imaging.
  • the processor 103 calculates at least one frame of the target image of the first mode according to the first image frame sequence and the second image frame sequence to obtain a third image frame sequence of the first mode.
  • the third image frame sequence may include all or part of the target image of the first mode and the first image frame of the at least one frame; or may include only the target image of the first mode of the at least one frame.
  • the first image frame sequence is E1, E2.
  • the third image frame sequence may be E1, EX, E2; wherein EX represents a frame of the target image in the target image of the first mode of the at least one frame.
  • the first image frame sequence is E1, E2, E3.
  • the third image frame sequence may be E1, EX, EY, EZ, E3; wherein EX, EY, EZ represents three frame target images in the target image of the at least one frame of the first mode.
  • the processor 103 controls the display 104 to display a third sequence of image frames of the first mode.
  • the computer program product includes one or more computer instructions.
  • the computer can be a general purpose computer, a special purpose computer, a computer network, or other programmable device.
  • the computer instructions can be stored in a computer readable storage medium or transferred from one computer readable storage medium to another computer readable storage medium, for example, the computer instructions can be wired from a website site, computer, server or data center (for example, coaxial cable, optical fiber, digital subscriber line (DSL)) or wireless (eg infrared, wireless, microwave, etc.) to another website site, computer, server or data center.
  • DSL digital subscriber line
  • the computer readable storage medium can be any available media that can be stored by a computer or a data storage device such as a server, data center, or the like that includes one or more available media.
  • the usable medium may be a magnetic medium (eg, a floppy disk, a hard disk, a magnetic tape), an optical medium (eg, a DVD), or a semiconductor medium (such as a solid state disk (SSD)).
  • the disclosed system, apparatus, and method may be implemented in other manners.
  • the device embodiments described above are merely illustrative.
  • the division of the unit is only a logical function division.
  • there may be another division manner for example, multiple units or components may be combined or may be Integrate into another system, or some features can be ignored or not executed.
  • the mutual coupling or direct coupling or communication connection shown or discussed may be an indirect coupling or communication connection through some interface, device or unit, and may be in an electrical, mechanical or other form.
  • the units described as separate components may or may not be physically separated, and the components displayed as units may or may not be physical units, that is, may be located in one place, or may be distributed to multiple network units. Some or all of the units may be selected according to actual needs to achieve the purpose of the solution of the embodiment.
  • each functional unit in each embodiment of the present application may be integrated into one processing unit, or each unit may exist physically separately, or two or more units may be integrated into one unit.
  • the above integrated unit can be implemented in the form of hardware or in the form of a software functional unit.
  • the integrated unit if implemented in the form of a software functional unit and sold or used as a standalone product, can be stored in a computer readable storage medium.
  • a computer readable storage medium A number of instructions are included to cause a computer device (which may be a personal computer, server, or network device, etc.) to perform all or part of the steps of the method of various embodiments of the present application.
  • the foregoing storage medium includes: a U disk, a mobile hard disk, a read-only memory (ROM), a random access memory (RAM), a magnetic disk, or an optical disk, and the like, which can store program code. .

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Abstract

一种超声成像方法及超声成像设备(10，60)，通过对所获得的弹性回波数据或弹性图像进行帧间处理，形成新的弹性图像，从而提升弹性图像的显示帧率。超声成像方法包括：向被测对象的目标区域发射第一超声波，以跟踪在该目标区域内传播的剪切波（201）；接收从该目标区域返回的该第一超声波的超声回波，以获得第一回波数据（202）；根据该第一回波数据获得该目标区域的第一弹性图像帧序列（203）；根据该至少两帧弹性图像确定至少一帧目标弹性图像，以获得第二弹性图像帧序列，并显示该第二弹性图像帧序列（204）。

Description

超声成像方法及超声成像设备 技术领域
本申请涉及医用超声成像领域，尤其涉及一种超声成像方法及超声成像设备。
背景技术
超声弹性成像是近年来临床研究关心的热点之一，主要反映组织的弹性和软硬程度，在组织癌症病变的辅助检测、良恶性判别和预后恢复评价等方面得到越来越多应用。按成像原理的不同，超声弹性成像技术主要分为两类：一类是应变式弹性成像技术，另一类是剪切波式弹性成像技术。
其中，应变式弹性成像方法主要通过探头按压组织产生一定的形变，再将应变量、应变率等与组织弹性相关的参数计算出来并成像，间接反映不同组织间的弹性差异。由于应变参数对压力敏感，因此这种方法中通过探头施加的压力需要尽量均匀稳定，从而对操作者的手法提出了较高的要求。剪切波式弹性成像方法主要通过在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)进行成像的方法来反映组织间的硬度差异。由于不再依赖操作者对组织的特定施压，这种弹性成像方式在稳定性和重复性方面有所改善，而且定量的测量结果使得医生的诊断更加方便客观。
其中，基于声辐射力的剪切波弹性成像方法是市场上比较多用的一种方法，它主要通过向组织内部发射特殊超声脉冲，基于声辐射力效应产生剪切波在组织内传播，再通过超声检测序列来记录上述剪切波的传播过程，最终计算出与组织弹性相关的参数，实现弹性成像。这种弹性成像方法目前可以做到实时图像显示，但是由于超声能量的安全输出限制，弹性图像的实际刷新帧率较低。
发明内容
本申请提供了一种超声成像方法及超声成像设备，通过对所获得的弹性回波数据或弹性图像进行帧间处理，形成新的弹性图像，从而提升弹性图像的显示帧率。
本申请第一方面提供了一种超声成像方法，该方法包括：
向被测对象的目标区域发射第一超声波，以跟踪在该目标区域内传播的剪切波；
接收从该目标区域返回的该第一超声波的超声回波，以获得第一回波数据；
根据该第一回波数据获得该目标区域的第一弹性图像帧序列，该第一弹性图像帧序列包含至少两帧弹性图像；
执行帧间处理过程；该帧间处理过程包括根据该至少两帧弹性图像确定至少一帧目标弹性图像，以获得第二弹性图像帧序列，以及显示该第二弹性图像帧序列；其中，该第二弹性图像帧序列的帧数量大于该第一弹性图像帧序列的帧数量。
本申请第二方面提供了一种超声成像方法，该方法包括：
显示第一弹性图像帧序列，该第一弹性图像帧序列包含至少两帧弹性图像；
接收第一操作，并根据该第一操作执行帧间处理过程；
该帧间处理过程包括：根据该至少两帧弹性图像确定至少一帧目标弹性图像，以获得第二弹性图像帧序列，以及显示该第二弹性图像帧序列；其中，该第二弹性图像帧序列的帧数量大于该第一弹性图像帧序列的帧数量。
本申请第三方面提供了一种超声成像方法，该方法包括：
向被测对象的目标区域发射第一超声波、接收从该目标区域返回的该第一超声波的超声回波，以获得第一回波数据；
根据该第一回波数据获得该目标区域的第一模式的第一图像帧序列；
向被测对象的目标区域发射第二超声波、接收从该目标区域返回的该第二超声波的超声回波，以获得第二回波数据；
根据该第二回波数据获得该目标区域的第二模式的第二图像帧序列；
根据该第一图像帧序列和该第二图像帧序列确定至少一帧第一模式的目标图像，以获得第一模式的第三图像帧序列；其中，该第三图像帧序列的帧数量大于该第一图像帧序列的帧数量；
显示该第一模式的第三图像帧序列。
本申请第四方面提供了一种超声成像设备，该超声成像设备包括：
超声探头；
发射/接收序列控制器，该发射/接收序列控制器激励该超声探头向被测对象的目标区域发射第一超声波，以跟踪在该目标区域内传播的剪切波；以及接收从该目标区域返回的该第一超声波的超声回波以获得第一回波数据；
处理器，该处理器根据该第一回波数据获得该目标区域的第一弹性图像帧序列，并执行帧间处理过程；该第一弹性图像帧序列包含至少两帧弹性图像；
该帧间处理过程包括根据该至少两帧弹性图像确定至少一帧目标弹性图像，以获得第二弹性图像帧序列，以及显示该第二弹性图像帧序列；其中，该第二弹性图像帧序列的帧数量大于该第一弹性图像帧序列的帧数量。
本申请第五方面提供了一种超声成像设备，该超声成像设备包括：
显示器，该显示器显示第一弹性图像帧序列，该第一弹性图像帧序列包含至少两帧弹性图像；
处理器，该处理器接收第一操作，并根据该第一操作执行帧间处理过程；
该帧间处理过程包括：根据该至少两帧弹性图像确定至少一帧目标弹性图像，以获得第二弹性图像帧序列，以及显示该第二弹性图像帧序列；其中，该第二弹性图像帧序列的帧数量大于该第一弹性图像帧序列的帧数量。
本申请第六方面提供了一种超声成像设备，该超声成像设备包括：
超声探头；
发射/接收序列控制器，该发射/接收序列控制器激励该超声探头向被测对象的目标区域发射第一超声波、接收从该目标区域返回的该第一超声波的超声回波，以获得第一回波数据；
处理器，该处理器根据该第一回波数据获得该目标区域的第一模式的第一图像帧序列；
该发射/接收序列控制器激励该超声探头向被测对象的目标区域发射第二超声波、接收从该目标区域返回的该第二超声波的超声回波，以获得第二回波数据；
该处理器根据该第二回波数据获得该目标区域的第二模式的第二图像帧序列；
该处理器根据该第一图像帧序列和该第二图像帧序列确定至少一帧第一 模式的目标图像，以获得第一模式的第三图像帧序列；其中，该第三图像帧序列的帧数量大于该第一图像帧序列的帧数量；
显示器，该显示器显示该第一模式的第三图像帧序列。
本申请实施例提供的技术方案中，向被测对象的目标区域发射第一超声波，以跟踪在该目标区域内传播的剪切波；接收从该目标区域返回的该第一超声波的超声回波，以获得第一回波数据；根据该第一回波数据获得该目标区域的第一弹性图像帧序列；根据该至少两帧弹性图像确定至少一帧目标弹性图像，以获得第二弹性图像帧序列，并显示该第二弹性图像帧序列。由于经过帧间处理过程后，得到的第二弹性图像帧序列的帧数量大于原来的第一弹性图像帧序列的帧数量。因此，得到的第二弹性图像帧序列的显示帧率比原来的第一弹性图像帧序列的显示帧率高，从而提升了弹性图像的显示帧率。
附图说明
图1为本申请提供的超声成像设备的一个结构示意图；
图2为本申请提供的超声成像方法的一个流程示意图；
图3为本申请提供的发射/接收序列帧的一个示意图；
图4为本申请提供的帧间处理的一个示意图；
图5为本申请提供的帧位移的一个示意图；
图6为本申请提供的超声成像设备的另一结构示意图；
图7为本申请提供的超声成像方法的另一流程示意图；
图8为本申请提供的超声成像方法的另一流程示意图。
具体实施方式
下面将结合本申请实施例中的附图，对本申请实施例中的技术方案进行清楚、完整地描述，显然，所描述的实施例仅仅是本申请一部分实施例，而不是全部的实施例。
本申请的说明书和权利要求书及上述附图中的术语“第一”、“第二”、“第三”、“第四”等(如果存在)是用于区别类似的对象，而不必用于描述特定的顺序或先后次序。应该理解这样使用的数据在适当情况下可以互换，以便这里描述的实施例能够以除了在这里图示或描述的内容以外的顺序实施。此外，术语“包括”和“具有”以及他们的任何变形，意图在于覆盖不排他的包含，例如，包含了 一系列步骤或单元的过程、方法、系统、产品或设备不必限于清楚地列出的那些步骤或单元，而是可包括没有清楚地列出的或对于这些过程、方法、产品或设备固有的其它步骤或单元。
图1为本申请实施例中的超声成像设备10的结构框图示意图。该超声成像设备10可以包括超声探头100、发射/接收选择开关101、发射/接收序列控制器102、处理器103和显示器104。发射/接收序列控制器102可以激励超声探头100向目标对象发射超声波，还可以控制超声探头100接收从目标对象返回的超声回波，从而获得超声回波信号。处理器103对该超声回波信号进行处理，以获得目标对象的超声图像。处理器103获得的超声图像可以存储于存储器105中，这些超声图像可以在显示器104上显示。
本申请实施例中，前述的超声成像设备10的显示器104可为触摸显示屏、液晶显示屏等，也可以是独立于超声成像设备10之外的液晶显示器、电视机等独立显示设备，也可为手机、平板电脑等电子设备上的显示屏。
本申请实施例中，前述的超声成像设备10的存储器105可为闪存卡、固态存储器、硬盘等。
本申请实施例还提供一种计算机可读存储介质，该计算机可读存储介质存储有多条程序指令，该多条程序指令被处理器103调用执行后，可执行本申请各个实施例中的超声成像方法中的部分步骤或全部步骤或其中步骤的任意组合。
一个实施例中，该计算机可读存储介质可为存储器105，其可以是闪存卡、固态存储器、硬盘等非易失性存储介质。
本申请实施例中，前述的超声成像设备10的处理器105可以通过软件、硬件、固件或者其组合实现，可以使用电路、单个或多个专用集成电路(application specific integrated circuits，ASIC)、单个或多个通用集成电路、单个或多个微处理器、单个或多个可编程逻辑器件、或者前述电路或器件的组合、或者其他适合的电路或器件，从而使得该处理器105可以执行前述各个实施例中的超声成像方法的相应步骤。
下面对本申请中的超声成像方法进行详细描述，请参阅图2，本申请实施例提供的一种超声成像方法，该方法应用于超声成像设备10，特别适用于包 含触摸显示屏的超声成像设备10，用于可以利用接触触摸显示屏来输入触屏操作。该超声成像设备10可利用超声回波数据生成弹性图像，也可以利用超声回波数据生成常规的超声B图像或者多普勒图像等等。本申请中的超声成像方法实施例包括：
201、向被测对象的目标区域发射第一超声波，以跟踪在该目标区域内传播的剪切波。
本实施例中，超声成像设备10通过该发射/接收序列控制器102激励该超声探头100向被测对象的目标区域发射第一超声波，以跟踪在该目标区域内传播的剪切波。该目标区域可根据弹性测量的需求确定，确定方式如可采用常规二维B模式成像、常规弹性成像E模式等各类适用成像检测方式初步检测后确定，也可根据检测需求选定。
一个实施例中，该目标区域的数量可以为一个或者多个。当目标区域的数量为多个时，多个目标区域的各自纵向深度或横向位置可以不同。
其中，剪切波的产生方式可参考如下说明。一个实施例中，剪切波可以利用外部振动产生，例如利用外部振动产生剪切波传入目标区域的组织深部。或者也可以利用超声脉冲声辐射力效应在目标区域的组织内部产生剪切波；或者也可以利用被测对象内的组织生理运动(例如，心脏搏动、血管搏动等等)产生剪切波；等等，此处不做详细描述。本说明书仅举例简述其中一种比较常用的方法：基于声辐射力的超声剪切波弹性成像。
以声辐射力的超声剪切波弹性成像，在该目标区域内传播的剪切波可通过本实施例的发射/接收序列控制器102激励超声探头100向组织发射一个特定波形、长度、特定频率的超声脉冲，该超声脉冲会在组织内部产生声辐射力效应，进而产生剪切波在组织中传播。然后向该组织发射一系列超声波用于跟踪检测上述剪切波在组织中的传播过程。也可以通过其他超声设备向该组织发射一个特定波形、长度、特定频率的超声脉冲，基于该超声脉冲产生的声辐射力效应，同样能达到相同的效果。
202、接收从该目标区域返回的该第一超声波的超声回波，以获得第一回波数据。
本实施例中，该处理器103通过发射/接收序列控制器102控制超声探头 100接收从目标区域返回的该第一超声波的超声回波，以获得第一回波数据。
203、根据该第一回波数据获得该目标区域的第一弹性图像帧序列，该第一弹性图像帧序列包含至少两帧弹性图像。
本实施例中，该处理器103对步骤202得到的第一回波数据进行处理，以获得该目标区域的至少两帧弹性图像，形成弹性图像帧序列。
204、执行帧间处理过程。
本实施例中，处理器103执行帧间处理过程。该帧间处理过程包括根据该至少两帧弹性图像确定至少一帧目标弹性图像，以获得第二弹性图像帧序列，以及显示该第二弹性图像帧序列；其中，该第二弹性图像帧序列的帧数量大于该第一弹性图像帧序列的帧数量。
需要说明的是，处理器103根据步骤203得到的至少两帧弹性图像计算得到至少一帧目标弹性图像，以获得第二弹性图像帧序列。需要说明的是，第二弹性图像帧序列可以包含上述至少一帧目标弹性图像和上述第一弹性图像帧的全部或者部分序列；也可以仅包含上述至少一帧目标弹性图像。比如，第一弹性图像帧序列为E1，E2。第二弹性图像帧序列可以为E1，EX，E2；其中，EX代表上述至少一帧目标弹性图像中的一帧目标弹性图像。再比如，第一弹性图像帧序列为E1，E2，E3。第二弹性图像帧序列可以为E1，EX，EY，EZ，E3；其中，EX，EY，EZ代表上述至少一帧目标弹性图像中的三帧目标弹性图像。由于经过帧间处理过程后，得到的第二弹性图像帧序列的帧数量大于原来的第一弹性图像帧序列的帧数量。因此，得到的第二弹性图像帧序列的显示帧率比原来的第一弹性图像帧序列的显示帧率高，从而提升了弹性图像的显示帧率。
上述弹性图像可以和其他类型的图像结合，以同时实现多种成像模式的显示。例如与B型、C型或者PW型图像结合，本实施例不做限定。例如与B型图像结合，可以同时实现弹性成像(以下简称E型成像)和B型成像。
一个实施例中，超声成像设备10通过该发射/接收序列控制器102激励该超声探头100向被测对象的目标区域发射第二超声波；并通过发射/接收序列控制器102控制超声探头100接收从目标区域返回的该第二超声波的超声回波，以获得第二回波数据。该第二回波数据可用于实现B型成像或者C型成 像。上述第一回波数据可用于实现E型成像。
该处理器103对得到的第二回波数据进行处理，以获得该目标区域的B型图像帧序列或者C型图像帧序列；控制显示器104显示该B型图像帧序列或者C型图像帧序列。如此，实现B型成像和E型成像，或者C型成像和E型成像。
以同时实现B型成像和E型成像为例，超声成像设备10需发射/接收至少两种超声序列帧，例如B序列帧和E序列帧。其中，B序列帧指用于生成一帧常规B型成像的超声发射接收序列，本文不详述其具体成像序列组成。E序列帧指用于生成一帧E型成像的超声发射接收序列。以基于声辐射力的剪切波弹性成像技术为例，E序列帧中首先包含用于产生剪切波的超声脉冲，在该超声脉冲的作用下，会产生剪切波在组织内部传播。然后需要持续一段时间向组织内部目标区域发射一系列检测脉冲，并接收其超声回波信号，用于记录剪切波在组织中的传播过程，剪切波的产生参考步骤201中相关说明，此处不做详述。其中，B序列帧的超声回波信号可用于实现B型成像，E序列帧的超声回波信号可用于实现E型成像。实时成像中，两种序列帧可先后交替进行，B序列帧的发射帧率与E序列帧的发射帧率不同。在相邻两次重复的E序列帧之间，往往包含多帧B序列帧。如图3所示，每个序列帧意味着可以进行一幅完整的图像显示。
其中，确定至少一帧目标弹性图像以获得第二弹性图像帧序列的方式可以有多种，本实施例不做限定。例如可以通过插值法或者根据系统设定的固定加权系数确定至少一帧目标弹性图像，在第一弹性图像帧序列的各相邻两帧弹性图像间生成该至少一帧目标弹性图像。
一个实施例中，处理器103可从第一弹性图像帧序列的至少两帧弹性图像中确定第一弹性图像和第二弹性图像；其中，第一弹性图像和第二弹性图像可以是相邻的弹性图像，也可以是不相邻的弹性图像。
处理器103确定该第一弹性图像和第二弹性图像的时间间隔；并根据该第一弹性图像和第二弹性图像的时间间隔生成至少一帧目标弹性图像，以获得该第二弹性图像帧序列。
一个实施例中，各类型的序列帧之间的时间间隔可为固定的，比如任意两 个相邻B序列帧之间的时间间隔是固定的，任意两个相邻的E序列帧之间的时间间隔也是固定的。但两种时间间隔可以不同。因此图3中，以B系列帧为例，不论两个相邻B序列帧之间是否插有E序列帧，其时间间隔都是相同的。时间间隔越短，意味着发射帧率越高。一个实施例中，B序列帧的发射帧率高于E序列帧的发射帧率。
一个实施例中，可以利用E序列帧间插有的B序列帧或者C序列帧进行插值法的计算。
上述根据该第一弹性图像和第二弹性图像的时间间隔生成至少一帧目标弹性图像包括：
确定与该第一弹性图像和第二弹性图像关联的B型图像的帧数量或者C型图像的帧数量；
根据该B型图像的帧数量或者C型图像的帧数量以及该第一弹性图像和第二弹性图像的时间间隔生成至少一帧目标弹性图像。
需要说明的是，由于E序列帧的发射帧率较低，每个E序列帧可以计算获得一幅E型图像，因此E型图像的显示帧率也会较低。但是B序列帧的发射帧率可高于E序列帧的发射帧率，因此B序列帧的显示帧率相对更高。
以同时实现B型成像和E型成像为例，超声成像设备10可将相邻的B序列帧和E序列帧对应的图像结果同步显示，方便用户同时参考B型图像和E型图像。B型图像包含组织结构信息，E型图像包含组织硬度相关信息。因此会出现大部分B型图像没有对应的同步E型图像可供选择。
基于上述可同时实现B型成像和E型成像的场景，处理器103确定与该第一弹性图像和第二弹性图像关联的B型图像的帧数量可以是第一弹性图像和第二弹性图像之间插入的B型图像、与第一弹性图像相邻的B型图像以及与第二弹性图像相邻的B型图像的帧数量之和。
其中，第一弹性图像和第二弹性图像可以是相邻的两帧E型图像。处理器103通过相邻两帧E型图像(以下称为第一E型图像和第二E型图像)或者两帧E序列帧的回波数据以及与该第一E型图像和第二E型图像关联的B型图像的帧数量，计算出与中间插入的B序列帧各自对应的E序列帧，如图4举例所示，假设E1序列帧是B1序列帧相关联的E序列帧，E2序列帧是B2序 列帧相关联的E序列帧，但是B2序列帧和B3序列帧则没有相关联的E序列帧，因此需要通过帧间处理计算出相关联的E序列帧。
帧间处理的计算方法可以有许多种，以插值法为例加以说明。两个相邻E序列帧之间的B序列帧，其各自的时刻是固定的，可以直接根据各B序列帧的所对应的时刻与前后2个E序列帧时刻之间的远近关系，通过插值方法，计算出与各B序列帧相关联的E序列帧。如图4中所示，假如B1、B2、B3和B4序列帧之间的时间间隔都是等同的，则插值计算后的结果参考如下：
B1序列帧相关联的E序列帧为Enew1＝E1；
B2序列帧相关联的E序列帧为Enew2＝E1+(E2-E1)*1/3；
B3序列帧相关联的E序列帧为Enew3＝E1+(E2-E1)*2/3；
B4序列帧相关联的E序列帧为Enew4＝E2。
可见，经过帧间处理之后，每个B序列帧都有了相关联的E序列帧，E型图像的显示帧率提升到了与B型图像显示帧率一致。
当然，当B序列帧之间的时间间隔不等同时，依然可以按照各自时间间隔的长短进行类似插值计算处理，此处不做详述。
基于上述插值法的相关说明，在一个场景中，两个相邻E序列帧之间的B序列帧，成像期间有可能目标组织发生了运动，导致B序列帧之间有较大的位移，此时仅仅根据时间间隔来进行插值，不能很好的匹配B序列帧的位置。因此，可结合追踪法做进一步计算。一个实施例中，该根据该B型图像的帧数量或者C型图像的帧数量以及该第一弹性图像和第二弹性图像的时间间隔生成至少一帧目标弹性图像包括：
根据至少两帧该B型图像或者至少两帧该C型图像确定该目标区域的位移；
根据该B型图像的帧数量或者C型图像的帧数量、该目标区域的位移以及该第一弹性图像和第二弹性图像的时间间隔生成至少一帧目标弹性图像。
需要说明的是，可利用追踪法首先确定目标组织发生运动后产生的位移，继续基于上述可同时实现B型成像和E型成像的场景。利用追踪法可先计算出B序列帧之间的位移相关参数，根据位移的方向、幅度来对E序列帧做相应的调整，再结合时间间隔进行插值。假如图4中B2序列帧相对于B1序列 帧发生了位置的改变，整体平移了一定距离，如图5中所示，则在插值计算与B2序列帧相关联的E序列帧中各数据点(例如图示局部数据点)时，应该取B1、B4序列帧中与该数据点同样位置处的E数据信息。
图5所示仅作举例示意，实际应用中，B序列帧中各局部数据点位置的位移方向和幅度可能是不同的，因此，可根据需要对各局部数据点分开计算处理。
当然，也有一些其他的方法来做帧间处理，比如根据系统设定的固定加权系数来计算B序列帧相关联的E序列帧等，本申请并不局限于使用插值法等计算方法。一个实施例中，该根据该第一弹性图像和第二弹性图像的时间间隔生成至少一帧目标弹性图像包括：
根据该第一弹性图像和第二弹性图像的时间间隔以及预设加权系数生成至少一帧目标弹性图像。
例如，两帧相邻的弹性图像，第一E型图像E1和第二E型图像E2，按照预设加权系数计算出第三E型图像E3和第四E型图像E4。可见，经过帧间处理之后，E序列帧的帧数得以提高，因此，E型图像的显示帧率得以提升。需要说明的是，通过预设加权系数生成至少一帧目标弹性图像以提升显示帧率的方式可应用于单工的工作模式。该单工的工作模式可包括：产生B序列帧以实现B型成像的工作模式、产生C序列帧以实现C型成像的工作模式、产生E序列帧以实现E型成像的工作模式、或者产生PW序列帧以实现PW型成像的工作模式。
上述通过帧间处理计算B序列帧相关联的E序列帧时，并不一定需要将每个B序列帧都计算出相关联的E序列帧，可只对部分B序列帧计算出相关联的E序列帧，这样形成的最终E序列帧的帧数提高了，因此E型图像的显示帧率也会得到提高。
一个实施例中，在本申请的超声成像设备10，除了产生B序列帧和E序列帧，以同时实现B型成像和E型成像外，还可以同时插入进行彩超多普勒成像的超声序列，以产生C序列帧等，此处不限定各类型的序列帧之间互相结合。
本申请的超声成像方法，可以在实时成像时即直接显示帧间处理后的新的高帧率E型图像。也可以选择在实时成像时先显示原始E型图像，图像采集 结束后，再由用户通过控制按钮或者按键等操作来启动帧间处理形成新的高帧率E型图像。
一个实施例中，该根据该第一回波数据获得该目标区域的第一弹性图像帧序列后，该方法还包括：
显示该第一弹性图像帧序列；该第一弹性图像帧序列可以理解为原始E型图像。
该执行帧间处理过程包括：
接收第一操作，并根据该第一操作执行该帧间处理过程。例如用户通过控制按钮、按键或者语音指示等操作来启动帧间处理形成新的高帧率E型图像，并显示新的高帧率E型图像。帧间处理过程参考步骤204相关说明进行理解，此处不再赘述。
一个实施例中，原始E型图像与高帧率E型图像也可实现自由切换。该超声成像方法进一步包括：
接收第一切换指令，并根据该第一切换指令执行切换过程；该切换过程包括：将当前显示的第一弹性图像帧序列切换为显示第二弹性图像帧序列；或者，将当前显示的第二弹性图像帧序列切换为显示第一弹性图像帧序列。
需要说明的是，用户通过控制按钮、按键或者语音指示等操作来启动帧间处理后，显示新的高帧率E型图像，用户还可以进一步通过按钮、按键或者语音指示等操作将当前显示的新的高帧率E型图像切换为显示原始的E型图像。原始的E型图像和新的高帧率E型图像可通过按钮、按键或者语音指示等操作实现自由的切换，此处不限定操作方式以及切换频率。
本申请的超声成像方法，还可以拓展至其他同时具有至少2种不同超声序列帧的成像模式，比如彩色血流模式下同时出现B序列帧和C序列帧时，此时可以通过本申请的超声成像方法对B序列帧和/或C序列帧进行帧间处理，提升显示帧率。
再比如多普勒模式下同时出现B序列帧和PW序列帧时，此时可以通过本申请的超声成像方法对B序列帧和/或PW序列帧进行帧间处理，提升显示帧率。
本申请提供的超声成像方法，超声成像设备10通过发射/接收序列控制器 102向被测对象的目标区域发射第一超声波，以跟踪在该目标区域内传播的剪切波；接收从该目标区域返回的该第一超声波的超声回波，以获得第一回波数据；通过处理器103根据该第一回波数据获得该目标区域的第一弹性图像帧序列；根据该至少两帧弹性图像确定至少一帧目标弹性图像，以获得第二弹性图像帧序列，并显示该第二弹性图像帧序列。该第二弹性图像帧序列可参考上述步骤204相关说明进行理解，此处不再赘述。由于经过帧间处理过程后，得到的第二弹性图像帧序列的帧数量大于原来的第一弹性图像帧序列的帧数量。因此，得到的第二弹性图像帧序列的显示帧率比原来的第一弹性图像帧序列的显示帧率高，从而提升了弹性图像的显示帧率。
图6为为本申请实施例中的超声成像设备60的结构框图示意图。该超声成像设备60可以包括处理器601和显示器602。处理器601可以对获得的超声回波信号进行处理，以获得目标对象的超声图像。处理器601获得的超声图像可以存储于存储器603中，这些超声图像可以在显示器602上显示。
本申请实施例中，超声成像设备60的显示器602可为触摸显示屏、液晶显示屏等，也可以是独立于超声成像设备60之外的液晶显示器、电视机等独立显示设备，也可为手机、平板电脑等电子设备上的显示屏。
本申请实施例中，前述的超声成像设备60的存储器603可为闪存卡、固态存储器、硬盘等。
本申请实施例还提供一种计算机可读存储介质，该计算机可读存储介质存储有多条程序指令，该多条程序指令被处理器601调用执行后，可执行本申请各个实施例中的超声成像方法中的部分步骤或全部步骤或其中步骤的任意组合。
一个实施例中，该计算机可读存储介质可为存储器603，其可以是闪存卡、固态存储器、硬盘等非易失性存储介质。
本申请实施例中，前述的超声成像设备60的处理器601可以通过软件、硬件、固件或者其组合实现，可以使用电路、单个或多个专用集成电路(application specific integrated circuits，ASIC)、单个或多个通用集成电路、单个或多个微处理器、单个或多个可编程逻辑器件、或者前述电路或器件的组合、或者其他适合的电路或器件，从而使得该处理器601可以执行前述各个实施例 中的超声成像方法的相应步骤。
下面对本申请中的超声成像方法进行详细描述，请参阅图7，本申请实施例提供的一种超声成像方法，该方法应用于超声成像设备60，特别适用于包含触摸显示屏的超声成像设备60，用于可以利用接触触摸显示屏来输入触屏操作。该超声成像设备60可利用超声回波数据生成弹性图像，也可以利用超声回波数据生成常规的超声B图像或者多普勒图像等等。本申请中的超声成像方法实施例包括：
本申请还提供了一种超声成像方法，请参阅图7，该方法包括：
701、获取第一弹性图像帧序列，并显示该第一弹性图像帧序列，该第一弹性图像帧序列包含至少两帧弹性图像。
该第一弹性图像帧序列可以通过如下方式得到：通过超声探头向被测对象的目标区域发射第一超声波，以跟踪在该目标区域内传播的剪切波；接收从该目标区域返回的该第一超声波的超声回波，以获得第一回波数据；根据该第一回波数据获得该目标区域的第一弹性图像帧序列。该第一弹性图像帧序列可以是储存在本地的弹性图像，或者是实时获取的弹性图像。该超声成像设备60可以直接获取本地存储的第一弹性图像帧序列，也可以是通过有线或者无线的数据传输获得该第一弹性图像帧序列。进一步的，该超声成像设备60控制显示器602显示该第一弹性图像帧序列。
702、接收第一操作，并根据该第一操作执行帧间处理过程。
该帧间处理过程包括：根据该至少两帧弹性图像确定至少一帧目标弹性图像，以获得第二弹性图像帧序列，以及显示该第二弹性图像帧序列；其中，该第二弹性图像帧序列的帧数量大于该第一弹性图像帧序列的帧数量。例如用户通过控制按钮、按键或者语音指示等操作来启动帧间处理过程形成新的高帧率弹性图像，并显示新的高帧率弹性图像。帧间处理过程参考上述实施例步骤204相关说明进行理解，此处不再赘述。
本申请实施例提供的技术方案中，获取第一弹性图像帧序列，并显示该第一弹性图像帧序列；该第一弹性图像帧序列包含至少两帧弹性图像；接收第一操作，根据该至少两帧弹性图像确定至少一帧目标弹性图像，以获得第二弹性图像帧序列，并显示该第二弹性图像帧序列。该第二弹性图像帧序列可参考上 述步骤204相关说明进行理解，此处不再赘述。由于经过帧间处理过程后，得到的第二弹性图像帧序列的帧数量大于原来的第一弹性图像帧序列的帧数量。因此，得到的第二弹性图像帧序列的显示帧率比原来的第一弹性图像帧序列的显示帧率高，从而提升了弹性图像的显示帧率。
一个实施例中，原始弹性图像与高帧率弹性图像也可实现自由切换。该超声成像方法进一步包括：
接收第一切换指令，并根据该第一切换指令执行切换过程；该切换过程包括：将当前显示的第一弹性图像帧序列切换为显示第二弹性图像帧序列；或者，将当前显示的该第二弹性图像帧序列切换为显示第一弹性图像帧序列。
需要说明的是，用户通过控制按钮、按键或者语音指示等操作来启动帧间处理后，显示新的高帧率弹性图像，用户还可以进一步通过按钮、按键或者语音指示等操作将当前显示的新的高帧率弹性图像切换为显示原始的弹性图像。原始的弹性图像和新的高帧率弹性图像可通过按钮、按键或者语音指示等操作实现自由的切换，此处不限定操作方式以及切换频率。
本申请还提供了一种超声成像方法，超声成像设备10适用该方法，请参阅图8，该方法包括：
801、向被测对象的目标区域发射第一超声波、接收从该目标区域返回的该第一超声波的超声回波，以获得第一回波数据。
本实施例中，超声成像设备10通过该发射/接收序列控制器102激励该超声探头100向被测对象的目标区域发射第一超声波、接收从目标区域返回的该第一超声波的超声回波，以获得第一回波数据。
802、根据该第一回波数据获得该目标区域的第一模式的第一图像帧序列。
本实施例中，处理器103对步骤802得到的第一回波数据进行处理，以获得该目标区域的至少两帧弹性图像，形成该目标区域的第一模式的第一图像帧序列。
803、向被测对象的目标区域发射第二超声波、接收从该目标区域返回的该第二超声波的超声回波，以获得第二回波数据。
本实施例中，超声成像设备10通过该发射/接收序列控制器102激励该超声探头100向被测对象的目标区域发射第二超声波、接收从目标区域返回的该 第二超声波的超声回波，以获得第二回波数据。
804、根据该第二回波数据获得该目标区域的第二模式的第二图像帧序列。
本实施例中，处理器103对步骤803得到的第二回波数据进行处理，以获得该目标区域的至少两帧弹性图像，形成该目标区域的第二模式的第二图像帧序列。
该第一模式和该第二模式可以是产生B序列帧以实现B型成像的工作模式、产生C序列帧以实现C型成像的工作模式、产生E序列帧以实现E型成像的工作模式、以及产生PW序列帧以实现PW型成像的工作模式等四种工作模式中的任意两种组合。比如，第一模式为产生E序列帧以实现E型成像的工作模式，第二模式为产生B序列帧以实现B型成像的工作模式；再比如，第一模式为产生C序列帧以实现C型成像的工作模式，第二模式为产生B序列帧以实现B型成像的工作模式。
805、根据该第一图像帧序列和该第二图像帧序列确定至少一帧第一模式的目标图像，以获得第一模式的第三图像帧序列；其中，该第三图像帧序列的帧数量大于该第一图像帧序列的帧数量。
本实施例中，处理器103根据该第一图像帧序列和该第二图像帧序列计算出至少一帧第一模式的目标图像，以获得第一模式的第三图像帧序列。需要说明的是，第三图像帧序列可以包含上述至少一帧第一模式的目标图像和上述第一图像帧的全部或者部分序列；也可以仅包含上述至少一帧第一模式的目标图像。比如，第一图像帧序列为E1，E2。第三图像帧序列可以为E1，EX，E2；其中，EX代表上述至少一帧第一模式的目标图像中的一帧目标图像。再比如，第一图像帧序列为E1，E2，E3。第三图像帧序列可以为E1，EX，EY，EZ，E3；其中，EX，EY，EZ代表上述至少一帧第一模式的目标图像中的三帧目标图像。由于经过帧间处理过程后，得到的第三图像帧序列的帧数量大于原来的第一图像帧序列的帧数量。因此，得到的第三图像帧序列的显示帧率比原来的第一图像帧序列的显示帧率高，从而提升了超声图像的显示帧率。
806、显示该第一模式的第三图像帧序列。
处理器103控制显示器104显示该第一模式的第三图像帧序列。
在上述实施例中，可以全部或部分地通过软件、硬件、固件或者其任意组 合来实现。当使用软件实现时，可以全部或部分地以计算机程序产品的形式实现。
该计算机程序产品包括一个或多个计算机指令。在计算机上加载和执行该计算机程序指令时，全部或部分地产生按照本发明实施例该的流程或功能。该计算机可以是通用计算机、专用计算机、计算机网络、或者其他可编程装置。该计算机指令可以存储在计算机可读存储介质中，或者从一个计算机可读存储介质向另一计算机可读存储介质传输，例如，该计算机指令可以从一个网站站点、计算机、服务器或数据中心通过有线(例如同轴电缆、光纤、数字用户线(digital subscriber line，DSL))或无线(例如红外、无线、微波等)方式向另一个网站站点、计算机、服务器或数据中心进行传输。该计算机可读存储介质可以是计算机能够存储的任何可用介质或者是包含一个或多个可用介质集成的服务器、数据中心等数据存储设备。该可用介质可以是磁性介质，(例如，软盘、硬盘、磁带)、光介质(例如，DVD)、或者半导体介质(例如固态硬盘solid state disk(SSD))等。
所属领域的技术人员可以清楚地了解到，为描述的方便和简洁，上述描述的系统，装置和单元的具体工作过程，可以参考前述方法实施例中的对应过程，在此不再赘述。
在本申请所提供的几个实施例中，应该理解到，所揭露的系统，装置和方法，可以通过其它的方式实现。例如，以上所描述的装置实施例仅仅是示意性的，例如，该单元的划分，仅仅为一种逻辑功能划分，实际实现时可以有另外的划分方式，例如多个单元或组件可以结合或者可以集成到另一个系统，或一些特征可以忽略，或不执行。另一点，所显示或讨论的相互之间的耦合或直接耦合或通信连接可以是通过一些接口，装置或单元的间接耦合或通信连接，可以是电性，机械或其它的形式。
该作为分离部件说明的单元可以是或者也可以不是物理上分开的，作为单元显示的部件可以是或者也可以不是物理单元，即可以位于一个地方，或者也可以分布到多个网络单元上。可以根据实际的需要选择其中的部分或者全部单元来实现本实施例方案的目的。
另外，在本申请各个实施例中的各功能单元可以集成在一个处理单元中， 也可以是各个单元单独物理存在，也可以两个或两个以上单元集成在一个单元中。上述集成的单元既可以采用硬件的形式实现，也可以采用软件功能单元的形式实现。
该集成的单元如果以软件功能单元的形式实现并作为独立的产品销售或使用时，可以存储在一个计算机可读取存储介质中。基于这样的理解，本申请的技术方案本质上或者说对现有技术做出贡献的部分或者该技术方案的全部或部分可以以软件产品的形式体现出来，该计算机软件产品存储在一个存储介质中，包括若干指令用以使得一台计算机设备(可以是个人计算机，服务器，或者网络设备等)执行本申请各个实施例该方法的全部或部分步骤。而前述的存储介质包括：U盘、移动硬盘、只读存储器(read-only memory，ROM)、随机存取存储器(random access memory，RAM)、磁碟或者光盘等各种可以存储程序代码的介质。
以上该，以上实施例仅用以说明本申请的技术方案，而非对其限制；尽管参照前述实施例对本申请进行了详细的说明，本领域的普通技术人员应当理解：其依然可以对前述各实施例所记载的技术方案进行修改，或者对其中部分技术特征进行等同替换；而这些修改或者替换，并不使相应技术方案的本质脱离本申请各实施例技术方案的精神和范围。

Claims (24)

  1. 一种超声成像方法，其特征在于，包括：
    向被测对象的目标区域发射第一超声波，以跟踪在所述目标区域内传播的剪切波；
    接收从所述目标区域返回的所述第一超声波的超声回波，以获得第一回波数据；
    根据所述第一回波数据获得所述目标区域的第一弹性图像帧序列，所述第一弹性图像帧序列包含至少两帧弹性图像；
    执行帧间处理过程；所述帧间处理过程包括根据所述至少两帧弹性图像确定至少一帧目标弹性图像，以获得第二弹性图像帧序列，以及显示所述第二弹性图像帧序列；其中，所述第二弹性图像帧序列的帧数量大于所述第一弹性图像帧序列的帧数量。
  2. 根据权利要求1所述的方法，其特征在于，所述方法还包括：
    向被测对象的目标区域发射第二超声波；
    接收从所述目标区域返回的所述第二超声波的超声回波，以获得第二回波数据；
    根据所述第二回波数据获得所述目标区域的B型图像帧序列或者C型图像帧序列；
    显示所述B型图像帧序列或者C型图像帧序列。
  3. 根据权利要求1或2所述的方法，其特征在于，所述根据所述至少两帧弹性图像确定至少一帧目标弹性图像，以获得第二弹性图像帧序列包括：
    从所述至少两帧弹性图像中确定第一弹性图像和第二弹性图像；
    确定所述第一弹性图像和第二弹性图像的时间间隔；
    根据所述第一弹性图像和第二弹性图像的时间间隔生成至少一帧目标弹性图像，以获得所述第二弹性图像帧序列。
  4. 根据权利要求3所述的方法，其特征在于，所述根据所述第一弹性图 像和第二弹性图像的时间间隔生成至少一帧目标弹性图像包括：
    根据所述第一弹性图像和第二弹性图像的时间间隔以及预设加权系数生成至少一帧目标弹性图像。
  5. 根据权利要求3所述的方法，其特征在于，所述根据所述第一弹性图像和第二弹性图像的时间间隔生成至少一帧目标弹性图像包括：
    确定与所述第一弹性图像和第二弹性图像关联的所述目标区域的B型图像的帧数量或者所述目标区域的C型图像的帧数量；
    根据所述B型图像的帧数量或者C型图像的帧数量以及所述第一弹性图像和第二弹性图像的时间间隔生成至少一帧目标弹性图像。
  6. 根据权利要求5所述的方法，其特征在于，所述根据所述B型图像的帧数量或者C型图像的帧数量以及所述第一弹性图像和第二弹性图像的时间间隔生成至少一帧目标弹性图像包括：
    根据至少两帧所述B型图像或者至少两帧所述C型图像确定所述目标区域的位移；
    根据所述B型图像的帧数量或者C型图像的帧数量、所述目标区域的位移以及所述第一弹性图像和第二弹性图像的时间间隔生成至少一帧目标弹性图像。
  7. 根据权利要求1所述的方法，其特征在于，所述根据所述第一回波数据获得所述目标区域的第一弹性图像帧序列后，所述方法还包括：
    显示所述第一弹性图像帧序列；
    所述执行帧间处理过程包括：
    接收第一操作，并根据所述第一操作执行所述帧间处理过程。
  8. 根据权利要求7所述的方法，其特征在于，所述方法还包括：
    接收第一切换指令，并根据所述第一切换指令执行切换过程；
    所述切换过程包括：将当前显示的第一弹性图像帧序列切换为显示第二弹 性图像帧序列；或者，将当前显示的第二弹性图像帧序列切换为显示第一弹性图像帧序列。
  9. 根据权利要求1所述的方法，其特征在于，在向被测对象的目标区域发射第一超声波之前还包括：
    产生在所述目标区域内传播的剪切波。
  10. 一种超声成像方法，其特征在于，包括：
    获取第一弹性图像帧序列，并显示所述第一弹性图像帧序列；所述第一弹性图像帧序列包含至少两帧弹性图像；
    接收第一操作，并根据所述第一操作执行帧间处理过程；
    所述帧间处理过程包括：根据所述至少两帧弹性图像确定至少一帧目标弹性图像，以获得第二弹性图像帧序列，以及显示所述第二弹性图像帧序列；其中，所述第二弹性图像帧序列的帧数量大于所述第一弹性图像帧序列的帧数量。
  11. 根据权利要求10所述的方法，其特征在于，所述方法还包括：
    接收第一切换指令，并根据所述第一切换指令执行切换过程；
    所述切换过程包括：将当前显示的第一弹性图像帧序列切换为显示第二弹性图像帧序列；或者，将当前显示的所述第二弹性图像帧序列切换为显示第一弹性图像帧序列。
  12. 一种超声成像方法，其特征在于，包括：
    向被测对象的目标区域发射第一超声波、接收从所述目标区域返回的所述第一超声波的超声回波，以获得第一回波数据；
    根据所述第一回波数据获得所述目标区域的第一模式的第一图像帧序列；
    向被测对象的目标区域发射第二超声波、接收从所述目标区域返回的所述第二超声波的超声回波，以获得第二回波数据；
    根据所述第二回波数据获得所述目标区域的第二模式的第二图像帧序列；
    根据所述第一图像帧序列和所述第二图像帧序列确定至少一帧第一模式的目标图像，以获得第一模式的第三图像帧序列；其中，所述第三图像帧序列的帧数量大于所述第一图像帧序列的帧数量；
    显示所述第一模式的第三图像帧序列。
  13. 一种超声成像设备，其特征在于，包括：
    超声探头；
    发射/接收序列控制器，所述发射/接收序列控制器激励所述超声探头向被测对象的目标区域发射第一超声波，以跟踪在所述目标区域内传播的剪切波；以及接收从所述目标区域返回的所述第一超声波的超声回波以获得第一回波数据；
    处理器，所述处理器根据所述第一回波数据获得所述目标区域的第一弹性图像帧序列，并执行帧间处理过程；所述第一弹性图像帧序列包含至少两帧弹性图像；
    所述帧间处理过程包括根据所述至少两帧弹性图像确定至少一帧目标弹性图像，以获得第二弹性图像帧序列，以及显示所述第二弹性图像帧序列；其中，所述第二弹性图像帧序列的帧数量大于所述第一弹性图像帧序列的帧数量。
  14. 根据权利要求13所述的超声成像设备，其特征在于，
    所述发射/接收序列控制器还激励所述超声探头向被测对象的目标区域发射第二超声波，以及接收从所述目标区域返回的所述第二超声波的超声回波以获得第二回波数据；
    所述处理器还根据所述第二回波数据获得所述目标区域的B型图像帧序列或者C型图像帧序列；以及控制显示器显示所述B型图像帧序列或者C型图像帧序列。
  15. 根据权利要求13或14所述的超声成像设备，其特征在于，所述处理器根据所述至少两帧弹性图像确定至少一帧目标弹性图像，以获得第二弹性图 像帧序列包括：
    所述处理器从所述至少两帧弹性图像中确定第一弹性图像和第二弹性图像；确定所述第一弹性图像和第二弹性图像的时间间隔；以及根据所述第一弹性图像和第二弹性图像的时间间隔生成至少一帧目标弹性图像，以获得所述第二弹性图像帧序列。
  16. 根据权利要求15所述的超声成像设备，其特征在于，所述处理器根据所述第一弹性图像和第二弹性图像的时间间隔生成至少一帧目标弹性图像包括：
    所述处理器根据所述第一弹性图像和第二弹性图像的时间间隔以及预设加权系数生成至少一帧目标弹性图像。
  17. 根据权利要求15所述的超声成像设备，其特征在于，所述处理器根据所述第一弹性图像和第二弹性图像的时间间隔生成至少一帧目标弹性图像包括：
    所述处理器确定与所述第一弹性图像和第二弹性图像关联的所述目标区域的B型图像的帧数量或者所述目标区域的C型图像的帧数量；以及根据所述B型图像的帧数量或者C型图像的帧数量以及所述第一弹性图像和第二弹性图像的时间间隔生成至少一帧目标弹性图像。
  18. 根据权利要求17所述的超声成像设备，其特征在于，所述处理器根据所述B型图像的帧数量或者C型图像的帧数量以及所述第一弹性图像和第二弹性图像的时间间隔生成至少一帧目标弹性图像包括：
    所述处理器根据至少两帧所述B型图像或者至少两帧所述C型图像确定所述目标区域的位移；以及根据所述B型图像的帧数量或者C型图像的帧数量、所述目标区域的位移以及所述第一弹性图像和第二弹性图像的时间间隔生成至少一帧目标弹性图像。
  19. 根据权利要求13所述的超声成像设备，其特征在于，所述处理器还 执行如下步骤：
    所述处理器控制显示器显示所述第一弹性图像帧序列；
    所述处理器执行帧间处理过程包括：
    所述处理器接收第一操作，并根据所述第一操作执行所述帧间处理过程。
  20. 根据权利要求19所述的超声成像设备，其特征在于，所述处理器还执行如下步骤：
    所述处理器接收第一切换指令，并根据所述第一切换指令执行切换过程；
    所述切换过程包括：将当前显示的第一弹性图像帧序列切换为显示第二弹性图像帧序列；或者，将当前显示的第二弹性图像帧序列切换为显示第一弹性图像帧序列。
  21. 根据权利要求13所述的超声成像设备，其特征在于，所述超声成像设备还执行如下步骤：
    产生在所述目标区域内传播的剪切波。
  22. 一种超声成像设备，其特征在于，包括：
    处理器，所述处理器获取第一弹性图像帧序列，并控制显示器显示第一弹性图像帧序列；所述第一弹性图像帧序列包含至少两帧弹性图像；
    所述处理器接收第一操作，并根据所述第一操作执行帧间处理过程；
    所述帧间处理过程包括：根据所述至少两帧弹性图像确定至少一帧目标弹性图像，以获得第二弹性图像帧序列，以及显示所述第二弹性图像帧序列；其中，所述第二弹性图像帧序列的帧数量大于所述第一弹性图像帧序列的帧数量。
  23. 根据权利要求22所述的超声成像设备，其特征在于，所述处理器还执行如下步骤：
    所述处理器接收第一切换指令，并根据所述第一切换指令执行切换过程；
    所述切换过程包括：将当前显示的第一弹性图像帧序列切换为显示第二弹 性图像帧序列；或者，将当前显示的所述第二弹性图像帧序列切换为显示第一弹性图像帧序列。
  24. 一种超声成像设备，其特征在于，包括：
    超声探头；
    发射/接收序列控制器，所述发射/接收序列控制器激励所述超声探头向被测对象的目标区域发射第一超声波、接收从所述目标区域返回的所述第一超声波的超声回波，以获得第一回波数据；
    处理器，所述处理器根据所述第一回波数据获得所述目标区域的第一模式的第一图像帧序列；
    所述发射/接收序列控制器激励所述超声探头向被测对象的目标区域发射第二超声波、接收从所述目标区域返回的所述第二超声波的超声回波，以获得第二回波数据；
    所述处理器根据所述第二回波数据获得所述目标区域的第二模式的第二图像帧序列；
    所述处理器根据所述第一图像帧序列和所述第二图像帧序列确定至少一帧第一模式的目标图像，以获得第一模式的第三图像帧序列；其中，所述第三图像帧序列的帧数量大于所述第一图像帧序列的帧数量；
    显示器，所述显示器显示所述第一模式的第三图像帧序列。
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Publication number Priority date Publication date Assignee Title
CN114569153A (zh) * 2020-11-30 2022-06-03 深圳迈瑞生物医疗电子股份有限公司 弹性测量方法、基于弹性图像的匹配方法和超声成像系统

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20080285819A1 (en) * 2006-08-30 2008-11-20 The Trustees Of Columbia University In The City Of New York Systems and method for composite elastography and wave imaging
CN101732073A (zh) * 2008-11-26 2010-06-16 Ge医疗系统环球技术有限公司 超声波诊断装置和程序
CN102283679A (zh) * 2011-08-04 2011-12-21 中国科学院深圳先进技术研究院 弹性测量的超声成像系统及测量生物组织弹性的方法
CN102378010A (zh) * 2011-11-15 2012-03-14 无锡港湾网络科技有限公司 一种视频数据还原的插帧方法
CN102525552A (zh) * 2010-11-16 2012-07-04 日立阿洛卡医疗株式会社 超声波图像处理装置
US20170079619A1 (en) * 2015-09-21 2017-03-23 Edan Instruments, Inc. Snr improvement and operator-independence using time-varying frame-selection for strain estimation

Family Cites Families (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP3144819B2 (ja) * 1991-04-17 2001-03-12 株式会社東芝 超音波診断装置
US20070016029A1 (en) * 2005-07-15 2007-01-18 General Electric Company Physiology workstation with real-time fluoroscopy and ultrasound imaging
US9339256B2 (en) * 2007-10-01 2016-05-17 Maui Imaging, Inc. Determining material stiffness using multiple aperture ultrasound
JP5486257B2 (ja) * 2009-09-28 2014-05-07 富士フイルム株式会社 超音波診断装置及び弾性指標算出方法
JP5649083B2 (ja) * 2010-07-14 2015-01-07 株式会社日立メディコ 超音波画像の画像復元方法およびその装置並びに超音波診断装置
EP2599444B1 (en) * 2011-12-01 2017-08-02 Theraclion SA Method and device for determining the elastic modulus of a biological tissue
WO2013183651A1 (ja) * 2012-06-05 2013-12-12 株式会社東芝 超音波診断装置及び画像処理装置
EP3235437A4 (en) * 2014-12-19 2018-09-12 Olympus Corporation Ultrasonic observation device
JP6361528B2 (ja) 2015-03-03 2018-07-25 コニカミノルタ株式会社 超音波処理装置
JP2017079977A (ja) * 2015-10-27 2017-05-18 コニカミノルタ株式会社 超音波診断装置、および、超音波信号処理方法
JP6771095B2 (ja) * 2016-09-12 2020-10-21 コーニンクレッカ フィリップス エヌ ヴェＫｏｎｉｎｋｌｉｊｋｅ Ｐｈｉｌｉｐｓ Ｎ．Ｖ． 超音波イメージング・システム及び方法

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20080285819A1 (en) * 2006-08-30 2008-11-20 The Trustees Of Columbia University In The City Of New York Systems and method for composite elastography and wave imaging
CN101732073A (zh) * 2008-11-26 2010-06-16 Ge医疗系统环球技术有限公司 超声波诊断装置和程序
CN102525552A (zh) * 2010-11-16 2012-07-04 日立阿洛卡医疗株式会社 超声波图像处理装置
CN102283679A (zh) * 2011-08-04 2011-12-21 中国科学院深圳先进技术研究院 弹性测量的超声成像系统及测量生物组织弹性的方法
CN102378010A (zh) * 2011-11-15 2012-03-14 无锡港湾网络科技有限公司 一种视频数据还原的插帧方法
US20170079619A1 (en) * 2015-09-21 2017-03-23 Edan Instruments, Inc. Snr improvement and operator-independence using time-varying frame-selection for strain estimation

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