CN108065964B - Ultrasonic imaging method, device and equipment and ultrasonic imaging probe - Google Patents
Ultrasonic imaging method, device and equipment and ultrasonic imaging probe Download PDFInfo
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- CN108065964B CN108065964B CN201810042073.5A CN201810042073A CN108065964B CN 108065964 B CN108065964 B CN 108065964B CN 201810042073 A CN201810042073 A CN 201810042073A CN 108065964 B CN108065964 B CN 108065964B
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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
- A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
- A61B8/4444—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device related to the probe
- A61B8/4461—Features of the scanning mechanism, e.g. for moving the transducer within the housing of the probe
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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
- A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
- A61B8/4483—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device characterised by features of the ultrasound transducer
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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
- A61B8/485—Diagnostic techniques involving measuring strain or elastic properties
Abstract
The invention discloses an ultrasonic imaging method, an ultrasonic imaging device, ultrasonic imaging equipment and an ultrasonic imaging probe, wherein the method comprises the following steps: generating a first preset electric signal to excite the Langewen vibrator arranged on the ultrasonic imaging probe body to transversely bend and vibrate according to a preset direction, wherein the Langewen vibrator drives an ultrasonic transducer at the head of the ultrasonic imaging probe body to transversely swing within a preset inclination angle range in the transverse bending vibration process; controlling the ultrasonic transducer to emit ultrasonic waves towards the tissue to be detected and receive a first ultrasonic echo signal reflected by the tissue to be detected when the ultrasonic transducer swings to at least one preset inclination angle; and determining the ultrasonic imaging information of the position of the tissue to be detected corresponding to the preset inclination angle according to the first ultrasonic echo signal. The invention can increase the field of view of the ultrasonic transducer, so that a plurality of ultrasonic transducers are not required to be arranged on the ultrasonic imaging probe, and the ultrasonic imaging probe has smaller volume and is lighter.
Description
Technical Field
The invention relates to the technical field of elastography, in particular to an ultrasonic imaging method, an ultrasonic imaging device, ultrasonic imaging equipment and an ultrasonic imaging probe.
Background
Since the change of the elastic coefficient of the same biological tissue is often related to pathological features, for example, after the normal tissue suffers from breast cancer, liver cancer and other diseases, the local elastic coefficient of the normal tissue is obviously increased. Therefore, the quantitative display of the biological tissue mechanical parameters can be used for positioning the focus and identifying the nature of the lesion, and has important medical value. The existing ultrasonic elastography technology generally includes that ultrasonic waves are transmitted to a tissue to be detected and a first ultrasonic echo signal is received, then the tissue to be detected is slightly deformed, the ultrasonic waves are transmitted to the tissue to be detected and a second ultrasonic echo signal is received, finally the first ultrasonic echo signal and the second ultrasonic echo signal are processed to obtain response parameters of the tissue to be detected, such as displacement, strain rate and speed, and then relative values of material mechanical properties, such as Young modulus, shear modulus, Poisson ratio and Ramei constant, are estimated. In order to enable the elastic information to more intuitively display the pathological features of the tissue to be detected, the elastic information of a region of the tissue to be detected is generally required to be displayed so as to determine the disease condition of the tissue to be detected through comparison of the elastic information in the region.
If elastic information of different point positions in one area of the tissue to be detected is acquired one by arranging an ultrasonic transducer on the ultrasonic imaging probe, the time consumption is longer. In the existing method, an ultrasonic transducer array is often adopted to transmit or receive ultrasonic echoes corresponding to different positions of tissues to be detected, so that elastic information in one region is acquired.
However, the existing method requires that a plurality of ultrasonic transducers must be arranged on the ultrasonic imaging probe, thereby resulting in a large and heavy volume of the ultrasonic imaging probe.
Disclosure of Invention
In view of this, embodiments of the present invention provide an ultrasound imaging method, an ultrasound imaging apparatus, an ultrasound imaging device, and an ultrasound imaging probe, so as to solve the problem that the existing ultrasound imaging probe needs to be provided with a plurality of ultrasound transducers, which results in a large volume and a heavy weight.
The invention provides an ultrasonic imaging method in a first aspect, which comprises the following steps: generating a first preset electric signal to excite the Langewen vibrator arranged on the ultrasonic imaging probe body to transversely bend and vibrate according to a preset direction, wherein the Langewen vibrator drives an ultrasonic transducer at the head of the ultrasonic imaging probe body to transversely swing within a preset inclination angle range in the transverse bending vibration process; controlling the ultrasonic transducer to emit ultrasonic waves towards the tissue to be detected and receive a first ultrasonic echo signal reflected by the tissue to be detected when the ultrasonic transducer swings to at least one preset inclination angle; and determining the ultrasonic imaging information of the position of the tissue to be detected corresponding to the preset inclination angle according to the first ultrasonic echo signal.
Optionally, after the step of controlling the ultrasonic transducer to emit ultrasonic waves toward the tissue to be detected and receive the first ultrasonic echo signal reflected by the tissue to be detected when the ultrasonic transducer swings to at least one predetermined inclination angle, the method further includes: controlling the ultrasonic transducer to emit ultrasonic waves towards the tissue to be detected and receive a second ultrasonic echo signal reflected by the tissue to be detected when the ultrasonic transducer swings to the preset inclination angle again; the step of determining the ultrasonic imaging information of the tissue position to be detected corresponding to the preset inclination angle according to the first ultrasonic echo signal comprises the following steps: determining the propagation speed of shear waves at the position of the tissue to be detected corresponding to the preset inclination angle according to the first ultrasonic echo signal and the second ultrasonic echo signal, wherein the shear waves are waveforms propagated from the deformation position to the longitudinal depth after the tissue to be detected is deformed; and determining the Young modulus of the position of the tissue to be detected corresponding to the preset inclination angle according to the propagation speed of the shear wave.
Optionally, after the step of controlling the ultrasonic transducer to emit ultrasonic waves toward the tissue to be detected and receive a first ultrasonic echo signal reflected by the tissue to be detected when swinging to at least one predetermined inclination angle, before the step of controlling the ultrasonic transducer to emit ultrasonic waves toward the tissue to be detected and receive a second ultrasonic echo signal reflected by the tissue to be detected when swinging to the predetermined inclination angle again, the method further includes: and generating an A-th preset electric signal to excite the Langewen vibrator to longitudinally vibrate, and driving the head of the ultrasonic imaging probe main body to press the tissue to be detected once every preset time interval to deform the tissue to be detected during the longitudinal vibration of the Langewen vibrator.
A second aspect of the present invention provides an ultrasonic imaging apparatus comprising: the first excitation unit is used for generating a first preset electric signal to excite the Langewen vibrator arranged on the ultrasonic imaging probe body to transversely bend and vibrate according to a preset direction, and the Langewen vibrator drives the ultrasonic transducer at the head of the ultrasonic imaging probe body to transversely swing within a preset inclination angle range in the transverse bending vibration process; the first control unit is used for controlling the ultrasonic transducer to emit ultrasonic waves towards the tissue to be detected and receive a first ultrasonic echo signal reflected by the tissue to be detected when the ultrasonic transducer swings to at least one preset inclination angle; and the determining unit is used for determining the ultrasonic imaging information of the tissue position to be detected corresponding to the preset inclination angle according to the first ultrasonic echo signal.
Optionally, the apparatus further comprises: the second control unit is used for controlling the ultrasonic transducer to emit ultrasonic waves towards the tissue to be detected and receive a second ultrasonic echo signal reflected by the tissue to be detected when the ultrasonic transducer swings to the preset inclination angle again; the determination unit includes: the first determining subunit is configured to determine, according to the first ultrasonic echo signal and the second ultrasonic echo signal, a propagation speed of a shear wave at a position of the tissue to be detected, where the position corresponds to the predetermined inclination angle, where the shear wave is a waveform propagated from a deformed position to a longitudinal depth after the tissue to be detected is deformed; and the second determining subunit is used for determining the Young modulus of the position of the tissue to be detected corresponding to the preset inclination angle according to the propagation speed of the shear wave.
A third aspect of the present invention provides an ultrasound imaging probe comprising: a main body; at least one ultrasonic transducer disposed at the head of the body for emitting ultrasonic waves and receiving ultrasonic echo signals; a langevin vibrator disposed on the main body; the Langewen vibrator can bend and vibrate under the excitation of a first preset electric signal and drive the head of the main body to swing transversely.
Optionally, the main body comprises a front part, and a front end of the langevin vibrator is fixedly connected with a rear end of the front part; alternatively, the body comprises: the front end of the Langevin oscillator is fixedly connected with the rear end of the front part; and the rear end of the Langevin oscillator is fixedly connected with the front end of the rear part.
Optionally, under the excitation of the second predetermined electrical signal, the langevin vibrator can longitudinally vibrate and drive the head of the main body to vibrate back and forth under the excitation of the second predetermined electrical signal.
A fourth aspect of the present invention provides an ultrasonic imaging apparatus comprising: the ultrasound imaging apparatus comprises an ultrasound imaging probe, a display, a memory and a processor, wherein the ultrasound imaging probe, the display, the memory and the processor are communicatively connected with each other, the memory stores computer instructions, and the processor executes the computer instructions to perform the ultrasound imaging method according to the first aspect or any one of the optional embodiments of the first aspect.
A fifth aspect of the present invention provides a computer-readable storage medium having stored thereon computer instructions for causing a computer to execute the method of ultrasound imaging according to the first aspect or any one of the alternative embodiments of the first aspect.
According to the ultrasonic imaging method, the ultrasonic imaging device, the ultrasonic imaging equipment and the ultrasonic imaging probe provided by the embodiment of the invention, the head of the main body is driven to swing transversely by utilizing the bending vibration mode of the Langewen vibrator, so that the ultrasonic transducer arranged at the head of the main body can send ultrasonic waves to a tissue position to be detected in multiple directions and receive ultrasonic echoes, ultrasonic imaging information in an area on the tissue to be detected can be acquired by one or a few ultrasonic transducers, and the field of view of the ultrasonic transducer is increased. The ultrasonic imaging probe does not need to be provided with a plurality of ultrasonic transducers, and has smaller volume and lighter weight.
Drawings
The features and advantages of the present invention will be more clearly understood by reference to the accompanying drawings, which are illustrative and not to be construed as limiting the invention in any way, and in which:
FIG. 1 shows a schematic structural diagram of an ultrasound imaging probe according to an embodiment of the present invention;
FIG. 2 shows a schematic structural diagram of another ultrasound imaging probe according to an embodiment of the present invention;
FIG. 3 shows a schematic diagram of Langewen vibrator driving longitudinal vibration of an ultrasonic imaging probe;
FIG. 4 shows a schematic diagram of a Langewen vibrator driving an ultrasonic imaging probe to bend and vibrate;
FIG. 5 shows schematic longitudinal and flexural vibrations of a Langewen vibrator;
FIG. 6 shows a flow diagram of a method of ultrasound imaging in accordance with an embodiment of the invention;
FIG. 7 shows a side view of an ultrasound imaging probe emitting ultrasound waves toward tissue to be examined;
FIG. 8 shows a schematic view of various predetermined tilt angles;
FIG. 9 is a top view of a range within which ultrasound waves emitted by an ultrasound imaging probe can receive ultrasound echoes within tissue to be examined;
FIG. 10 shows a flow diagram of another method of ultrasound imaging according to an embodiment of the invention;
FIG. 11 shows a schematic view of only one shear wave peak in the tissue to be examined;
FIG. 12 shows a detailed flowchart of step S250;
FIG. 13 shows a schematic diagram of a first ultrasonic echo signal and a second ultrasonic echo signal;
FIG. 14 shows another detailed flowchart of step S250;
FIG. 15 shows a functional block diagram of an ultrasound imaging apparatus according to an embodiment of the present invention;
FIG. 16 shows a functional block diagram of another ultrasound imaging apparatus according to an embodiment of the present invention;
fig. 17 is a schematic diagram showing a hardware configuration of an ultrasonic imaging apparatus according to an embodiment of the present invention.
Detailed Description
In order to make the objects, technical solutions and advantages of the embodiments of the present invention clearer, the technical solutions in the embodiments of the present invention will be clearly and completely described below with reference to the drawings in the embodiments of the present invention, and it is obvious that the described embodiments are some, but not all, embodiments of the present invention. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present invention.
Example one
An embodiment of the present invention provides an ultrasonic imaging probe, as shown in fig. 1 and 2, including a main body 10, at least one ultrasonic transducer 12, and a langevin transducer 13.
The ultrasonic transducer 12 is disposed on the head of the main body 10, and may be an ultrasonic transducer or an ultrasonic transducer array, and is configured to emit ultrasonic waves and receive ultrasonic echo signals. The Langewen vibrator 13 is arranged on the main body 10, and the Langewen vibrator 13 can bend and vibrate under the excitation of a first preset electric signal and drive the head of the main body 10 to swing transversely. Wherein the bending vibration means that the front end of the Langewen vibrator swings towards two sides.
According to the ultrasonic imaging probe, the head of the main body is driven to transversely swing by using the bending vibration mode of the Langewen vibrator, so that the ultrasonic transducers arranged at the head of the main body can send ultrasonic waves to the positions of tissues to be detected in multiple directions and receive ultrasonic echoes, ultrasonic imaging information in an area on the tissues to be detected can be acquired through one or a few ultrasonic transducers, and the view field of the ultrasonic transducers is increased. The ultrasonic imaging probe does not need to be provided with a plurality of ultrasonic transducers, and has smaller volume and lighter weight.
Optionally, the langevin vibrator 13 in the ultrasonic imaging probe can longitudinally vibrate and drive the head of the main body 10 to vibrate back and forth under the excitation of the second predetermined electrical signal. The longitudinal vibration refers to the movement of the front end of the Langevin vibrator towards or away from the rear end of the Langevin vibrator, and can be primary longitudinal vibration or reciprocating longitudinal vibration. The forward and backward vibrations are vibrations in the longitudinal direction of the langevin vibrator.
The longitudinal vibration mode of the Lanjiwen vibrator is utilized to drive the head of the main body to vibrate back and forth, so that the tissue to be detected can be deformed conveniently and the ultrasonic echo information can be acquired, the tissue to be detected in front of the head of the main body can be deformed without a motor, and the ultrasonic probe is not influenced by a magnetic field; the Langevin oscillator enables the piezoelectric material to deform through the inverse piezoelectric effect, and the size is small, so that the size of the ultrasonic imaging probe can be reduced, and the weight of the ultrasonic imaging probe can be reduced.
A langevin transducer is a component that is capable of vibrating according to a predetermined law when excited by a predetermined electrical signal. For example, a longitudinal vibration mode, i.e., up-and-down vibration as shown in fig. 3 and 5(a), under the excitation of a first predetermined electrical signal; a bending mode, i.e. a lateral oscillation as shown in fig. 4 and 5(b), upon excitation by a second predetermined electrical signal, or another bending mode, i.e. a back and forth oscillation as shown in fig. 5(c), upon excitation by a third predetermined electrical signal. Regarding the longitudinal and bending vibration modes of langevin vibrator, there have been studies in the prior art, such as the document "structural dynamics finite element model of langevin vibrator" (li shirong et al, proceedings of profession university of suzhou, 3 months in 2013, vol 24, No. 1), and the application herein does not limit the specific form of langevin vibrator and the specific control manner of longitudinal and bending vibration.
As an alternative to this embodiment, as shown in fig. 1, the main body 10 may include a front portion 11, and the front end of the langevin transducer 13 is fixedly connected to the rear end of the front portion 11. The rear end of the langevin transducer 13 may be fixedly arranged, for example, on the housing 14.
Alternatively, as a side-by-side alternative to the above-described alternative embodiments, the main body 10 may include a front portion 11 and a rear portion 15, as shown in fig. 2. The front end of the langevin vibrator 13 is fixedly connected with the rear end of the front part 11, and the rear end of the langevin vibrator 13 is fixedly connected with the front end of the rear part 15. The rear end of the rear portion 15 may be fixedly arranged, for example on the housing 14.
It should be added that the ultrasonic transducer in the present application may also use a langerhans oscillator as a main body, the ultrasonic transducer is disposed at the front end of the langerhans oscillator, and the rear end of the langerhans oscillator may be fixedly disposed on the housing.
Example two
Fig. 6 shows a flow chart of an ultrasound imaging method according to an embodiment of the invention, which can be implemented by means of the ultrasound imaging probe of the first embodiment. As shown in fig. 6, the method includes the steps of:
s110: and generating a first preset electric signal to excite the Langewen vibrator arranged on the ultrasonic imaging probe body to transversely bend and vibrate according to a preset direction, and driving the ultrasonic transducer at the head of the ultrasonic imaging probe body to transversely swing within a preset inclination angle range in the transverse bending vibration process of the Langewen vibrator.
Fig. 7 shows a side view of an ultrasound imaging probe emitting ultrasound waves towards the tissue to be examined, and fig. 8 shows a schematic view of various predetermined inclination angles. Arrows OA and OB respectively indicate the maximum amplitude of the langerhans 'transducer at both sides when it oscillates transversely, and for example, the included angle θ may be 15 ° with respect to the position when it does not oscillate (position shown by OO' in fig. 7), and AA 'and BB' respectively indicate the propagation paths of the ultrasonic signals in the tissue to be detected.
S120: and controlling the ultrasonic transducer to emit ultrasonic waves towards the tissue to be detected and receive a first ultrasonic echo signal reflected by the tissue to be detected when the ultrasonic transducer swings to at least one preset inclination angle.
Fig. 9 shows a top view of a range in which ultrasonic waves emitted by an ultrasonic imaging probe can receive ultrasonic echoes in tissue to be examined. Wherein, A 'B' is the range within which the ultrasonic transducer can receive ultrasonic echoes when the Langevin oscillator drives the ultrasonic transducer to bend and vibrate in the A 'B' direction. When the Langevin oscillator is in bending vibration in the direction of A 'B', ultrasonic waves can be emitted towards the tissue to be detected at any angle and ultrasonic echoes are received, so that ultrasonic echo signals of any point on the straight line A 'B' can be acquired, and further ultrasonic imaging information of any position of the tissue to be detected on the straight line can be acquired.
S130: and determining ultrasonic imaging information of the position of the tissue to be detected corresponding to the preset inclination angle according to the first ultrasonic echo signal.
The method can obtain response parameters such as displacement, strain rate and shear wave propagation speed of the tissue to be detected according to the first ultrasonic echo signal, and further estimate relative values of material mechanical properties such as Young modulus, Poisson's ratio and the like of the tissue to be detected as ultrasonic imaging information. The ultrasound imaging information in step S130 may be not only the above-mentioned elastography (i.e. E-mode imaging) information, but also B-mode ultrasound imaging (i.e. B-mode ultrasound) information, D-mode ultrasound imaging information, blood flow imaging information, etc., and the specific form of the ultrasound imaging information is not limited in the present application.
As shown in fig. 9, C 'D' is a range within which the ultrasonic transducer can receive an ultrasonic echo when the lankee oscillator drives the ultrasonic transducer to bend and vibrate in the C 'D' direction, and E 'F' is a range … … within which the ultrasonic transducer can receive an ultrasonic echo when the lankee oscillator drives the ultrasonic transducer to bend and vibrate in the E 'F' direction, so that theoretically, under the condition that the preset inclination angle range is not changed, if the transverse bending vibration direction of the lankee oscillator is changed, an ultrasonic echo signal at any position on the tissue to be detected in the shadow part region in fig. 9 can be obtained, and then the ultrasonic imaging information of the tissue to be detected in the region can be obtained.
According to the ultrasonic imaging method, the head of the main body is driven to swing transversely by utilizing the bending vibration mode of the Langewen vibrator, so that the ultrasonic transducer arranged at the head of the main body can send ultrasonic waves to the positions of tissues to be detected in multiple directions and receive ultrasonic echoes, ultrasonic imaging information in an area on the tissues to be detected can be acquired through one or a few ultrasonic transducers, and the view field of the ultrasonic transducer is increased. The ultrasonic imaging probe does not need to be provided with a plurality of ultrasonic transducers, and has smaller volume and lighter weight.
EXAMPLE III
Fig. 10 shows a flow chart of another ultrasound imaging method according to an embodiment of the invention, which can be implemented by means of the ultrasound imaging probe of the first embodiment. As shown in fig. 10, the method includes the steps of:
s210: and generating a first preset electric signal to excite the Langewen vibrator arranged on the ultrasonic imaging probe body to transversely bend and vibrate according to a preset direction, and driving the ultrasonic transducer at the head of the ultrasonic imaging probe body to transversely swing within a preset inclination angle range in the transverse bending vibration process of the Langewen vibrator. Please refer to step S110.
S220: and controlling the ultrasonic transducer to emit ultrasonic waves towards the tissue to be detected and receive a first ultrasonic echo signal reflected by the tissue to be detected when the ultrasonic transducer swings to at least one preset inclination angle. Please refer to step S120.
S230: and generating an A-th preset electric signal to excite the Langewen vibrator to longitudinally vibrate, and driving the head of the ultrasonic imaging probe main body to press the tissue to be detected once at preset time intervals to deform the tissue to be detected during the longitudinal vibration of the Langewen vibrator.
It should be added that, in the step S230, the way of deforming the tissue to be detected is not limited to the way of driving the longitudinal vibration of the head of the main body by the longitudinal vibration of the langevin vibrator, and the longitudinal vibration of the head of the main body may be driven by a motor, or may be pressed by other devices or manually.
As a modification of step S230, the tissue to be detected may be pressed only once to be deformed once. Accordingly, the shear wave in the tissue to be detected has only one peak, and the shear wave velocity cannot be obtained according to the attenuation of one peak after a short period of time. Fig. 11 shows a schematic diagram of only one shear wave peak in the tissue to be examined, wherein the solid curve represents the peak position at the current time and the dashed curve represents the peak position at the past time.
Therefore, in the step S230, the tissue to be detected is pressed once at each preset time interval to deform the tissue to be detected, so that the shear wave in the tissue to be detected can have a plurality of wave crests, the duration of the shear wave in the tissue to be detected is long, the detection time of the shear wave is prolonged, and the ultrasonic echo signals at a plurality of positions can be conveniently obtained in the subsequent langevin vibrator bending vibration process. Fig. 7 and 9 are schematic diagrams showing a plurality of shear wave peaks in tissue to be detected, wherein a solid curve represents a peak position at a current time and a dotted curve represents a valley position at the current time.
S240: and controlling the ultrasonic transducer to emit ultrasonic waves towards the tissue to be detected and receive a second ultrasonic echo signal reflected by the tissue to be detected when the ultrasonic transducer swings to the preset inclination angle again.
The ultrasonic wave propagation velocity is much greater than the shear wave propagation velocity. Taking the tissue to be detected with a depth of 20cm as an example, the propagation speed of the shear wave is about 5m/s, and the duration of excitation of the shear wave is set to 0.2/5 to 0.04 s. The propagation velocity of ultrasonic wave is about 1540m/s, and the ultrasonic wave is emittedAnd the maximum detection time returned once is: 0.2 × 2/1540 ═ 2.5 × 10-4And S. The bending vibration working frequency of the Langevin vibrator is about 65Hz, the bending angle range is-15 degrees to 15 degrees, the half period from-15 degrees to 15 degrees is adopted, ultrasonic signals on 15 straight lines (one straight line corresponds to each preset inclination angle) are collected in the angle range (the ultrasonic signals are emitted and collected every 2 degrees), and the scanning time on each straight line is 1/65/2/15-5.13-10-4And s, the ultrasonic signals can be transmitted and received for 2 times on the same straight line.
Referring to fig. 8, assuming that the inclination angle of the lange weng vibrator transverse bending vibration is θ, and transmitting ultrasonic waves once every Δ and receiving ultrasonic echoes, the number of times of ultrasonic waves transmitted in a half period of the lange weng vibrator bending vibration (from- θ to + θ is a half period) is θ
The scan time on each line is
Suppose that the depth of the tissue to be detected is H and the propagation velocity of the ultrasonic wave is vuThe maximum detection time for the ultrasonic wave to be transmitted and returned once is
It follows that only the design needs to satisfy
The ultrasonic waves can be transmitted once every delta angle and the ultrasonic echoes can be received; if the ultrasonic wave needs to be transmitted for n times at an angle of delta and the ultrasonic echo needs to be received, the design is needed
S250: and determining the propagation speed of the shear wave at the position of the tissue to be detected corresponding to the preset inclination angle according to the first ultrasonic echo signal and the second ultrasonic echo signal, wherein the shear wave is a waveform propagated from the deformation position to the longitudinal depth after the tissue to be detected is deformed.
As shown in fig. 3(d), after the surface of the tissue to be detected is deformed, the internal shear wave is generated and propagates outwards from the deformation point in a spherical form.
For the same preset inclination angle position, by taking the first ultrasonic echo signal as a reference, the shear wave peak position at the first time t1 can be determined according to the first ultrasonic echo signal and the second ultrasonic echo signal; with reference to the first ultrasonic echo signal, the shear wave peak position at the second time t2 can be determined from the first ultrasonic echo signal and the third ultrasonic echo signal. And determining the propagation speed of the shear wave according to the displacement of the wave crest and the time difference between the t2 moment and the t1 moment.
S260: and determining the Young modulus of the position of the tissue to be detected corresponding to the preset inclination angle according to the propagation speed of the shear wave.
The relationship between young's modulus and shear wave is: e ═ 3 ρ ═ Vs 2. Wherein E is Young's modulus; rho is the density (kg/m) of the tissue to be detected3) Is a constant number; vsIs the propagation velocity of the shear wave. Therefore, the Young modulus of the tissue to be detected can be determined according to the propagation speed of the shear wave.
As an alternative implementation of this embodiment, as shown in fig. 12, step S250 includes S251, S252, S253, S254, S255, and S256.
S251: determining the serial number n of the corresponding sampling point of the first peak of the shear wave in the second ultrasonic echo signal according to the first ultrasonic echo signal and the second ultrasonic echo signal1。
As shown in fig. 13, the ultrasonic echo signals are acquired at a predetermined sampling frequency, the ultrasonic echo amplitude value at an earlier sampling time in the ultrasonic echo signals corresponds to a shallower tissue in the tissue to be detected, and the ultrasonic echo amplitude value at a later sampling time corresponds to a deeper tissue in the tissue to be detected.
Step S251 may select signals of the first ultrasonic echo signal and the second ultrasonic echo signal in the same and/or adjacent predetermined time periods (which may be selected by using a window function, where the length of the window function is the predetermined time period) multiple times, and calculate a cross-correlation value between the selected first ultrasonic echo signal and the selected second ultrasonic echo signal. And when the cross-correlation value is smaller than a preset value, determining the serial number of the sampling point in a preset time period corresponding to the cross-correlation value as the serial number of the sampling point corresponding to the peak in the second ultrasonic echo signal.
For example, as shown in fig. 13, the cross-correlation value may be calculated by selecting the first ultrasonic echo signal and the second ultrasonic echo signal in a time period a2-a1 through a hanning window; and then selecting a first ultrasonic echo signal in the time period of A2-A1 and a second ultrasonic echo signal in the time period of B2-B1 to calculate a cross-correlation value, namely, the window of the first ultrasonic echo signal is unchanged, and moving the window of the second ultrasonic echo signal backwards.
The cross-correlation calculation formula may be:
wherein, CXX(N) is the cross-correlation value, N is the set of sample points within a predetermined time period, RF1(N) is the amplitude, RF, of the nth sample point within the set N of sample points in the first ultrasonic echo signal2(N) is the amplitude of the nth sample point within the set N of sample points in the second ultrasonic echo signal,
is the average value of the corresponding amplitudes of all the sampling points in the set N of sampling points in the first ultrasonic echo signal,
and averaging the corresponding amplitudes of all the sampling points in the set N of the sampling points in the second ultrasonic echo signal.
In general, if the tissue to be detected is not deformed, the first ultrasonic echo signal and the second ultrasonic echo signal should be theoretically the same, and the cross-correlation value in the same time period should be 1 (or less than 1 but close to 1 due to other factors). Under the influence of shear waves, the tissue to be detected at the shear wave peak position on the second ultrasonic echo signal is squeezed, and the ultrasonic echo signal at the wave peak position and the first ultrasonic echo signal have small cross correlation value in the same or adjacent time period, namely, the difference between the ultrasonic echo signal and the first ultrasonic echo signal is large. According to the method and the device, the position corresponding to the shear wave crest can be quickly determined through the cross correlation value of the first ultrasonic echo signal and the second ultrasonic echo signal in the same or adjacent preset time period.
S252: determining the serial number n of the corresponding sampling point of the second peak of the shear wave in the third ultrasonic echo signal according to the first ultrasonic echo signal and the third ultrasonic echo signal2。
Step S252 may select signals of the first ultrasonic echo signal and the third ultrasonic echo signal in the same and/or adjacent predetermined time periods multiple times, and calculate a cross-correlation value of the selected first ultrasonic echo signal and the third ultrasonic echo signal. And when the cross-correlation value is smaller than a preset value, determining the serial number of the sampling point in a preset time period corresponding to the cross-correlation value as the serial number of the sampling point corresponding to the peak in the third ultrasonic echo signal. Please refer to step S251.
S253: acquiring the propagation velocity v of an ultrasonic wave0And the sampling frequency f of the ultrasonic echo.
S254: calculating the displacement s from the first peak to the second peak:
s255: obtaining the time interval t between the reception of the second ultrasonic echo and the reception of the third ultrasonic echo1。
S256: calculating the propagation velocity of the shear wave:
as a parallel alternative to the above alternative embodiments, step S250 may include only S257, S258, and S259 as shown in fig. 14.
S257: determining the serial number n of the corresponding sampling point of the first peak of the shear wave in the second ultrasonic echo signal according to the first ultrasonic echo signal and the second ultrasonic echo signal1。
S258: acquiring the propagation velocity v of an ultrasonic wave0Super, superThe sampling frequency f of the acoustic echo.
S259: calculating the displacement s of the shear wave from the deformation point to the first peak:
s2510: obtaining the time interval t between the time when the deformation of the tissue to be detected is finished and the time when the second ultrasonic echo is received2。
S2511: calculating the propagation velocity of the shear wave:
example four
Fig. 15 is a schematic block diagram of an ultrasound imaging apparatus according to an embodiment of the present invention, which may be used to implement the ultrasound imaging method described in the second embodiment or the third embodiment, or any alternative implementation thereof. As shown in fig. 15, the apparatus includes a first excitation unit 10, a first control unit 20, and a determination unit 30.
The first excitation unit 10 is configured to generate a first predetermined electrical signal to excite the lange wen vibrator disposed on the ultrasound imaging probe body to transversely bend and vibrate in a predetermined direction, and the lange wen vibrator drives the ultrasound transducer at the head of the ultrasound imaging probe body to transversely swing within a range of a preset inclination angle during transverse bending and vibration.
The first control unit 20 is configured to control the ultrasonic transducer to emit ultrasonic waves toward the tissue to be detected and receive a first ultrasonic echo signal reflected by the tissue to be detected when the ultrasonic transducer swings to at least one predetermined inclination angle.
The determining unit 30 is configured to determine the ultrasound imaging information of the tissue position to be detected corresponding to the predetermined inclination angle according to the first ultrasound echo signal.
The ultrasonic imaging device can increase the field of view of the ultrasonic transducer, so that the ultrasonic imaging probe is not required to be provided with a plurality of ultrasonic transducers, and has smaller volume and lighter weight. Please refer to example two specifically.
As an alternative to this embodiment, as shown in fig. 16, the apparatus further includes a second control unit 40 for controlling the ultrasonic transducer to emit ultrasonic waves toward the tissue to be detected and receive a second ultrasonic echo signal reflected by the tissue to be detected when the ultrasonic transducer swings to the predetermined inclination angle again.
The determination unit 30 comprises a first determination subunit 31 and a second determination subunit 32. The first determining subunit 31 is configured to determine, according to the first ultrasonic echo signal and the second ultrasonic echo signal, a propagation speed of a shear wave at a position of the tissue to be detected corresponding to the predetermined inclination angle, where the shear wave is a waveform propagated from the deformed position to the longitudinal depth after the tissue to be detected is deformed. The second determining subunit 32 is configured to determine, according to the propagation speed of the shear wave, the young's modulus of the tissue position to be detected corresponding to the predetermined inclination angle.
As an alternative implementation of this embodiment, as shown in fig. 16, the apparatus further includes: and the second excitation unit 50 is used for generating an A-th preset electric signal to excite the Langewen vibrator to longitudinally vibrate, and the Langewen vibrator drives the head of the ultrasonic imaging probe main body to press the tissue to be detected once at preset time intervals to deform the tissue to be detected during longitudinal vibration.
Fig. 17 is a schematic diagram of a hardware structure of an ultrasound imaging apparatus for performing an ultrasound imaging method according to an embodiment of the present invention, as shown in fig. 17, the apparatus includes an ultrasound imaging probe 1710, a display 1720, one or more processors 1730, and a memory 1740, where one processor 1730 is taken as an example in fig. 17.
The ultrasound imaging probe 1710, the display 1720, the processor 1730, and the memory 1740 may be connected by a bus or other means, such as by a bus in fig. 17.
The ultrasound imaging probe 1710, which may be the one described in the first embodiment, is configured to emit ultrasound waves to the tissue to be detected and acquire ultrasound echo signals. Display 1720 is used to display ultrasound imaging information of the tissue to be examined.
It should be added that the processor 1730 may be disposed outside the ultrasound imaging probe 1710, or may be disposed inside the ultrasound imaging probe 1710.
The memory 1740 serves as a non-transitory computer readable storage medium and may be used to store non-transitory software programs, non-transitory computer executable programs, and modules, such as program instructions/modules corresponding to the ultrasound imaging method in the embodiments of the present application (e.g., the first excitation unit 10, the first control unit 20, and the determination unit 30 shown in fig. 15). The processor 1730 executes the non-transitory software programs, instructions and modules stored in the memory 1740 to execute various functional applications of the server and data processing, i.e., to implement the ultrasound imaging method of the above-described method embodiment.
The memory 1740 may include a program storage area and a data storage area, wherein the program storage area may store an operating system, an application program required for at least one function; the storage data area may store data created according to use of the processing apparatus operated by the list items, and the like. In addition, the memory 1740 may include high-speed random access memory, and may also include non-transitory memory, such as at least one magnetic disk storage device, flash memory device, or other non-transitory solid-state storage device. In some embodiments, memory 1740 may optionally include memory located remotely from processor 1730, which may be connected through a network to a processing device operating on list items. Examples of such networks include, but are not limited to, the internet, intranets, local area networks, mobile communication networks, and combinations thereof.
The one or more modules are stored in the memory 1740 and, when executed by the one or more processors 1730, perform the methods illustrated in fig. 6 and 10.
The product can execute the method provided by the embodiment of the invention, and has corresponding functional modules and beneficial effects of the execution method. For details of the technology that are not described in detail in this embodiment, reference may be made to the related description in the embodiments shown in fig. 6 and fig. 10.
Embodiments of the present invention further provide a non-transitory computer storage medium, where computer-executable instructions are stored, and the computer-executable instructions may execute the ultrasound imaging method in any of the above method embodiments. The storage medium may be a magnetic Disk, an optical Disk, a Read-Only Memory (ROM), a Random Access Memory (RAM), a Flash Memory (Flash Memory), a Hard Disk (Hard Disk Drive, abbreviated as HDD), a Solid State Drive (SSD), or the like; the storage medium may also comprise a combination of memories of the kind described above.
It will be understood by those skilled in the art that all or part of the processes of the methods of the embodiments described above can be implemented by a computer program, which can be stored in a computer-readable storage medium, and when executed, can include the processes of the embodiments of the methods described above. The storage medium may be a magnetic disk, an optical disk, a read-only memory (ROM), a Random Access Memory (RAM), or the like.
Although the embodiments of the present invention have been described in conjunction with the accompanying drawings, those skilled in the art may make various modifications and variations without departing from the spirit and scope of the invention, and such modifications and variations fall within the scope defined by the appended claims.
Claims (8)
1. An ultrasound imaging method, comprising:
generating a first preset electric signal to excite a Langewen vibrator arranged on an ultrasonic imaging probe main body to transversely bend and vibrate according to a preset direction, wherein an ultrasonic transducer at the head of the ultrasonic imaging probe main body is driven to transversely swing within a preset inclination angle range in the transverse bending vibration process of the Langewen vibrator;
controlling the ultrasonic transducer to emit ultrasonic waves towards the tissue to be detected and receive a first ultrasonic echo signal reflected by the tissue to be detected when the ultrasonic transducer swings to a plurality of preset inclination angles;
controlling the ultrasonic transducer to emit ultrasonic waves towards the tissue to be detected and receive a second ultrasonic echo signal reflected by the tissue to be detected when the ultrasonic transducer swings to the preset inclination angle again;
determining the propagation speed of shear waves at the position of the tissue to be detected corresponding to the preset inclination angle according to the first ultrasonic echo signal and the second ultrasonic echo signal, wherein the shear waves are waveforms propagated from the deformation position to the longitudinal depth after the tissue to be detected is deformed;
determining the Young modulus of the position of the tissue to be detected corresponding to the preset inclination angle according to the propagation speed of the shear wave;
wherein the propagation velocity of the shear wave is calculated by the following steps:
determining the serial number n of the corresponding sampling point of the first peak of the shear wave in the second ultrasonic echo signal according to the cross-correlation value of the first ultrasonic echo signal and the second ultrasonic echo signal1；
Acquiring the propagation velocity v of an ultrasonic wave0Sampling frequency f of the ultrasonic echo;
calculating the displacement s of the shear wave from the deformation point to the first peak:
obtaining the time interval t between the time when the deformation of the tissue to be detected is finished and the time when the second ultrasonic echo is received2；
Calculating the propagation velocity of the shear wave:
2. the ultrasonic imaging method according to claim 1, wherein after the step of controlling the ultrasonic transducer to emit ultrasonic waves toward the tissue to be detected and receive the first ultrasonic echo signal reflected by the tissue to be detected when swinging to a plurality of predetermined inclination angles, before the step of controlling the ultrasonic transducer to emit ultrasonic waves toward the tissue to be detected and receive the second ultrasonic echo signal reflected by the tissue to be detected when swinging to the predetermined inclination angle again, the method further comprises:
and generating a second preset electric signal to excite the Langewen vibrator to longitudinally vibrate, and driving the head of the ultrasonic imaging probe main body to press the tissue to be detected once every preset time interval to deform the tissue to be detected during the longitudinal vibration of the Langewen vibrator.
3. An ultrasound imaging apparatus, comprising:
the ultrasonic imaging probe comprises a first excitation unit, a second excitation unit and a third excitation unit, wherein the first excitation unit is used for generating a first preset electric signal to excite a Langewen vibrator arranged on an ultrasonic imaging probe body to transversely bend and vibrate according to a preset direction, and the Langewen vibrator drives an ultrasonic transducer at the head of the ultrasonic imaging probe body to transversely swing within a preset inclination angle range in the transverse bending vibration process;
the first control unit is used for controlling the ultrasonic transducer to emit ultrasonic waves towards the tissue to be detected and receive a first ultrasonic echo signal reflected by the tissue to be detected when the ultrasonic transducer swings to a plurality of preset inclination angles;
the second control unit is used for controlling the ultrasonic transducer to emit ultrasonic waves towards the tissue to be detected and receive a second ultrasonic echo signal reflected by the tissue to be detected when the ultrasonic transducer swings to the preset inclination angle again;
the first determining subunit is configured to determine, according to the first ultrasonic echo signal and the second ultrasonic echo signal, a propagation speed of a shear wave at a position of the tissue to be detected, where the position corresponds to the predetermined inclination angle, where the shear wave is a waveform propagated from a deformed position to a longitudinal depth after the tissue to be detected is deformed;
the second determining subunit is used for determining the Young modulus of the position of the tissue to be detected corresponding to the preset inclination angle according to the propagation speed of the shear wave;
wherein the propagation velocity of the shear wave is calculated by the following steps:
based on the first ultrasonic echo signal and the second ultrasonic echo signalDetermining the serial number n of a corresponding sampling point of a first peak of a shear wave in a second ultrasonic echo signal by using the cross-correlation value of the ultrasonic echo signals1；
Acquiring the propagation velocity v of an ultrasonic wave0Sampling frequency f of the ultrasonic echo;
calculating the displacement s of the shear wave from the deformation point to the first peak:
obtaining the time interval t between the time when the deformation of the tissue to be detected is finished and the time when the second ultrasonic echo is received2；
Calculating the propagation velocity of the shear wave:
4. an ultrasound imaging apparatus, comprising: an ultrasound imaging probe, a display, a memory and a processor, wherein the ultrasound imaging probe, the display, the memory and the processor are communicatively connected to each other, the memory has stored therein computer instructions, and the processor executes the computer instructions to perform the ultrasound imaging method of claim 1 or 2.
5. The ultrasound imaging apparatus of claim 4, wherein the ultrasound imaging probe comprises:
a main body;
at least one ultrasonic transducer disposed at the head of the body for emitting ultrasonic waves and receiving ultrasonic echo signals;
a langevin vibrator disposed on the main body; the Langewen vibrator can bend and vibrate under the excitation of a first preset electric signal and drive the head of the main body to swing transversely.
6. The ultrasonic imaging apparatus of claim 5, wherein the body comprises a front portion, a front end of the langevin transducer being fixedly connected to a rear end of the front portion; alternatively, the body comprises:
the front end of the Langevin oscillator is fixedly connected with the rear end of the front part;
and the rear end of the Langevin oscillator is fixedly connected with the front end of the rear part.
7. The ultrasonic imaging device of claim 4, wherein the langevin transducer, under excitation by a second predetermined electrical signal, is capable of longitudinal vibration and of causing the head of the body to vibrate back and forth under excitation by the second predetermined electrical signal.
8. A computer-readable storage medium storing computer instructions for causing a computer to perform the ultrasound imaging method of claim 1 or 2.
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| CN109805959A (en) * | 2019-02-22 | 2019-05-28 | 无锡海斯凯尔医学技术有限公司 | The control method and device of signal transmission |
| CN109828030B (en) * | 2019-03-28 | 2021-07-27 | 烟台中凯检测科技有限公司 | Reflector morphology extraction system and method based on sound field characteristics |
| CN110664434B (en) * | 2019-09-23 | 2021-08-17 | 上海交通大学 | Skeletal muscle-oriented nonlinear acoustic parameter in-vivo measurement technology |
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