CN108158610B - Elastic imaging method, device, equipment and ultrasonic imaging probe - Google Patents
Elastic imaging method, device, equipment and ultrasonic imaging probe Download PDFInfo
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Abstract
The invention discloses an elastography method, an elastography device, elastography equipment and an ultrasonic imaging probe, wherein the elastography method comprises the following steps: controlling an ultrasonic transducer arranged on the head of the ultrasonic imaging probe body to emit ultrasonic waves towards the tissue to be detected and receiving a first ultrasonic echo signal reflected by the tissue to be detected; generating a first preset electric signal to excite the Langeut vibrator to longitudinally vibrate, wherein the Langeut vibrator drives the head of the ultrasonic imaging probe main body to act on the tissue to be detected to deform when longitudinally vibrating; controlling an ultrasonic transducer arranged on the head of the ultrasonic imaging probe body to emit ultrasonic waves towards the tissue to be detected and receiving a second ultrasonic echo signal reflected by the tissue to be detected; and determining elastic imaging information according to the first ultrasonic echo signal and the second ultrasonic echo signal. The invention can prevent the ultrasonic imaging probe from being influenced by the magnetic field, reduce the volume of the ultrasonic imaging probe and lighten the weight of the ultrasonic imaging probe.
Description
Technical Field
The invention relates to the technical field of ultrasonic imaging, in particular to an elastic imaging method, an elastic imaging device, elastic 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 significantly increased. Therefore, the quantitative display of the mechanical parameters of the biological tissues can be used for locating the focus and identifying the nature of the lesions, and has important medical value. The existing ultrasonic elastography technology generally comprises the steps of firstly transmitting ultrasonic waves to a tissue to be detected and receiving a first ultrasonic echo signal, then enabling the tissue to be detected to generate micro deformation, then transmitting ultrasonic waves to the tissue to be detected and receiving a second ultrasonic echo signal, finally processing the first ultrasonic echo signal and the second ultrasonic echo signal to obtain response parameters such as displacement, strain rate and speed of the tissue to be detected, and further estimating relative values of mechanical properties of materials such as Young modulus, shear modulus, poisson ratio and Lame constant.
In the existing mode, the biological tissue to be detected is slightly deformed, usually, an operator holds an ultrasonic imaging probe to apply pressure to the tissue to be detected, so that the tissue to be detected is deformed; or the tissue to be detected is automatically pressed by an ultrasonic imaging probe with a motor.
However, the above-described manner of manually applying pressure by an operator makes the operation process cumbersome; the ultrasonic imaging probe with the motor is provided with the motor besides the ultrasonic transmitting module and the ultrasonic receiving module, so that the ultrasonic imaging probe is large in size and is easily influenced by a magnetic field.
Disclosure of Invention
In view of the above, the embodiments of the present invention provide an elastography method, an elastography device, an elastography apparatus, and an elastography probe, so as to solve the problem that the existing ultrasonic imaging probe using a motor is large and is easily affected by a magnetic field.
The first aspect of the present invention provides an elastography method, comprising: controlling an ultrasonic transducer arranged on the head of an ultrasonic imaging probe body to emit ultrasonic waves towards tissue to be detected and receiving a first ultrasonic echo signal reflected by the tissue to be detected; generating a first preset electric signal to excite the Langeut vibrator to longitudinally vibrate, wherein the Langeut vibrator drives the head of the ultrasonic imaging probe main body to act on the tissue to be detected to deform when longitudinally vibrating; controlling an ultrasonic transducer arranged on the head of the ultrasonic imaging probe body to emit ultrasonic waves towards the tissue to be detected and receiving a second ultrasonic echo signal reflected by the tissue to be detected; and determining elastic imaging information according to the first ultrasonic echo signal and the second ultrasonic echo signal.
Optionally, the step of determining elastographic information from the first ultrasound echo signal and the second ultrasound echo signal comprises: determining the propagation speed of a shear wave according to the first ultrasonic echo signal and the second ultrasonic echo signal, wherein the shear wave is a waveform propagated from a deformation position to a depth position after the tissue to be detected is deformed; and determining the Young modulus of the tissue to be detected according to the propagation speed of the shear wave.
Optionally, after the step of controlling the ultrasonic transducer disposed on the head of the ultrasonic imaging probe body to emit ultrasonic waves toward the tissue to be detected and receive the second ultrasonic echo signal reflected by the tissue to be detected, the method further includes: controlling an ultrasonic transducer arranged on the head of the ultrasonic imaging probe body to emit ultrasonic waves towards the tissue to be detected and receiving a third ultrasonic echo signal reflected by the tissue to be detected; the step of determining the propagation speed of the shear wave from the first ultrasonic echo signal and the second ultrasonic echo signal comprises: determining a serial number n of a corresponding sampling point of a first peak of the shear wave in the second ultrasonic echo signal according to the first ultrasonic echo signal and the second ultrasonic echo signal 1 The method comprises the steps of carrying out a first treatment on the surface of the Determining a serial number n of a corresponding sampling point of a second peak of the shear wave in the third ultrasonic echo signal according to the first ultrasonic echo signal and the third ultrasonic echo signal 2 The method comprises the steps of carrying out a first treatment on the surface of the Acquiring propagation velocity v of ultrasonic wave 0 Sampling frequency f of ultrasonic echo;
calculating a displacement s of the first peak to the second peak:acquiring a time interval t between receiving the second ultrasonic echo and receiving the third ultrasonic echo 1 The method comprises the steps of carrying out a first treatment on the surface of the Calculating the propagation speed of the shear wave: />
Optionally, the step of determining the serial number of the peak of the shear wave corresponding to the sampling point in the xth ultrasonic echo signal according to the first ultrasonic echo signal and the xth ultrasonic echo signal includes: selecting signals of the first ultrasonic echo signal and the X ultrasonic echo signal in the same and/or adjacent preset time period for multiple times, and calculating the cross-correlation value of the selected first ultrasonic echo signal and the X ultrasonic echo signal; 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 corresponding sampling point of the wave crest in the X-th ultrasonic echo signal; the X-th ultrasonic echo signal includes a second ultrasonic echo signal or a third ultrasonic echo signal.
A second aspect of the present invention provides an elastography device, comprising: the first control unit is used for controlling an ultrasonic transducer arranged on the head of the ultrasonic imaging probe body to emit ultrasonic waves towards the tissue to be detected and receiving a first ultrasonic echo signal reflected by the tissue to be detected; the first excitation unit is used for generating a first preset electric signal to excite the Langeut vibrator to longitudinally vibrate, and the head of the ultrasonic imaging probe main body is driven to act on the tissue to be detected to deform when the Langeut vibrator longitudinally vibrates; the second control unit is used for controlling an ultrasonic transducer arranged on the head of the ultrasonic imaging probe body to emit ultrasonic waves towards the tissue to be detected and receiving a second ultrasonic echo signal reflected by the tissue to be detected; and the determining unit is used for determining elastic imaging information according to the first ultrasonic echo signal and the second ultrasonic echo signal.
A third aspect of the present invention provides an ultrasound imaging probe comprising: a main body; at least one ultrasonic transducer arranged on the head of the main body and used for transmitting ultrasonic waves and receiving ultrasonic echo signals; a lanjevin vibrator disposed on the main body; the Langevin vibrator can longitudinally vibrate and drive the head of the main body to vibrate back and forth under the excitation of a first preset electric signal.
Optionally, the main body comprises a front part, and the front end of the lanjevin vibrator is fixedly connected with the rear end of the front part; alternatively, the body includes: the front end of the Langeven vibrator is fixedly connected with the rear end of the front part; and the rear end of the Langerhan vibrator is fixedly connected with the front end of the rear part.
Optionally, under the excitation of the second predetermined electric signal, the lanjevin vibrator can bend and vibrate and drive the head of the main body to swing transversely under the excitation of the second predetermined electric signal.
A fourth aspect of the present invention provides an elastic imaging apparatus including: the device comprises an ultrasonic imaging probe, a display, a memory and a processor, wherein the ultrasonic imaging probe, the display, the memory and the processor are in communication connection, the memory stores computer instructions, and the processor executes the computer instructions, so that the elastography method of the first aspect or any optional implementation mode of the elastography method is executed.
A fifth aspect of the present invention provides a computer-readable storage medium storing computer instructions for causing the computer to perform the elastography method of the first aspect or any optional embodiment thereof.
According to the elastic imaging method, the elastic imaging device, the elastic imaging equipment and the ultrasonic imaging probe provided by the embodiment of the invention, the longitudinal vibration mode of the Langerhan 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 acquire ultrasonic echo information, and the tissue to be detected in front of the head of the main body can be deformed without adopting a motor, so that the ultrasonic imaging probe is not influenced by a magnetic field; the Langevin vibrator deforms the piezoelectric material through the inverse piezoelectric effect, and the volume is smaller, so that the volume of the ultrasonic imaging probe can be reduced, and the weight of the ultrasonic imaging probe can be lightened.
Drawings
The features and advantages of the present invention will be more clearly understood by reference to the accompanying drawings, which are illustrative and should not be construed as limiting the invention in any way, in which:
FIG. 1 shows a schematic structural diagram of an ultrasound imaging probe according to an embodiment of the invention;
FIG. 2 shows a schematic structural view of another ultrasound imaging probe according to an embodiment of the present invention;
FIG. 3 shows a schematic diagram of the ultrasonic imaging probe driven by the Langeven vibrator;
FIG. 4 shows a schematic diagram of a Langevin transducer driving bending vibration of an ultrasound imaging probe;
Fig. 5 shows a schematic diagram of longitudinal and flexural oscillations of a lanjevin vibrator;
fig. 6 shows a flowchart of an elastography method according to an embodiment of the invention;
FIG. 7 shows a flow chart of another elastography method according to an embodiment of the present invention;
FIG. 8 shows a specific flowchart of step S250;
FIG. 9 shows a schematic diagram of a first ultrasound echo signal and a second ultrasound echo signal;
fig. 10 shows another specific flowchart of step S250;
FIG. 11 shows a flowchart of another elastography method according to an embodiment of the present invention;
FIG. 12 shows a side view of an ultrasound imaging probe transmitting ultrasound waves to tissue to be examined;
FIG. 13 shows a schematic view of respective predetermined inclinations;
FIG. 14 shows a top view of the range over which ultrasound echoes can be received by ultrasound waves emitted by an ultrasound imaging probe within the tissue to be examined;
fig. 15 shows a flowchart of another elastography method according to an embodiment of the present invention;
FIG. 16 shows a schematic representation of only one shear wave peak within the tissue to be examined;
fig. 17 shows a functional block diagram of an elastography device according to an embodiment of the present invention;
fig. 18 shows a functional block diagram of another elastography device according to an embodiment of the invention;
Fig. 19 is a schematic diagram showing a hardware configuration of an elastic imaging apparatus according to an embodiment of the present invention.
Detailed Description
For the purpose of making the objects, technical solutions and advantages of the embodiments of the present invention more apparent, the technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings in the embodiments of the present invention, and it is apparent that the described embodiments are some embodiments of the present invention, but not all embodiments of the present invention. All other embodiments, which can be made by those skilled in the art based on the embodiments of the invention without making any inventive effort, are intended to fall within the scope of the invention.
Example 1
An embodiment of the present invention provides an ultrasound imaging probe comprising a body 10, at least one ultrasound transducer 12 and a lanjevin transducer 13, as shown in fig. 1 and 2.
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 for transmitting ultrasonic waves and receiving ultrasonic echo signals. The lanjev vibrator 13 is disposed on the main body 10, and the lanjev vibrator 13 can vibrate longitudinally and drive the head of the main body 10 to vibrate back and forth under the excitation of a first predetermined electric 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 one-time longitudinal vibration or reciprocating longitudinal vibration. The front-back vibration means vibration in the longitudinal direction of the langevin vibrator.
According to the ultrasonic imaging probe, the longitudinal vibration mode of the Langerhans 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 acquire ultrasonic echo information, and the tissue to be detected in front of the head of the main body can be deformed without adopting a motor, so that the ultrasonic imaging probe is not influenced by a magnetic field; the Langevin vibrator deforms the piezoelectric material through the inverse piezoelectric effect, and the volume is smaller, so that the volume of the ultrasonic imaging probe can be reduced, and the weight of the ultrasonic imaging probe can be lightened.
Alternatively, the langevin vibrator 13 in the ultrasonic imaging probe can bend and vibrate and drive the head of the main body 10 to swing laterally under the excitation of the second predetermined electric signal. Wherein bending vibration means that the front end of the Langeven vibrator swings towards two sides.
The head of the main body is driven to swing transversely by using the bending vibration mode of the Langevin vibrator, so that an ultrasonic transducer arranged at the head of the main body can send ultrasonic waves to the tissue to be detected in a plurality of directions and receive ultrasonic echoes, ultrasonic imaging information in a region on the tissue to be detected can be obtained by one or less ultrasonic transducers, and the field of view of the ultrasonic transducer can be increased. The ultrasonic imaging probe does not need to be provided with a plurality of ultrasonic transducers, and has smaller volume and lighter weight.
The lanjevin vibrator is a component capable of vibrating according to a predetermined rule under excitation of a predetermined electric signal. For example, in a longitudinal vibration mode under excitation of a first predetermined electric signal, i.e., up-and-down vibration as shown in fig. 3 and 5 (a); in a flexural vibration mode, i.e., lateral oscillation as shown in fig. 4 and 5 (b), under the excitation of a second predetermined electrical signal, or in another flexural vibration mode, i.e., back and forth oscillation as shown in fig. 5 (c), under the excitation of a third predetermined electrical signal. Regarding the longitudinal and flexural modes of the langevin vibrator, studies have been made in the prior art, for example, in the literature "limited-element model of structural dynamics of langevin vibrator" (Li Zhirong et al, university of occupational university of soviet, 2013, 24, 1 st edition), and the present application is not limited to the specific form of langevin vibrator, the specific control mode of longitudinal and flexural vibration.
As an alternative implementation of this embodiment, as shown in fig. 1, the main body 10 may include a front portion 11, and then the front end of the lanjevin transducer 13 is fixedly connected to the rear end of the front portion 11. The rear end of the lanjev vibrator 13 may be fixedly arranged, for example, on the housing 14.
Alternatively, as a side-by-side alternative to the alternative embodiment described above, the body 10 may include a front portion 11 and a rear portion 15, as shown in fig. 2. The front end of the langevin oscillator 13 is fixedly connected to the rear end of the front portion 11, and the rear end of the langevin oscillator 13 is fixedly connected to the front end of the rear portion 15. The rear end of the rear portion 15 may be fixedly disposed, such as fixedly disposed on the housing 14.
It should be noted that, the ultrasonic transducer in the present application may also use the langevin oscillator as a main body, the ultrasonic transducer is disposed at the front end of the langevin oscillator, and the rear end of the langevin oscillator may be fixedly disposed on the housing.
Example two
Fig. 6 shows a flowchart of an elastography method according to an embodiment of the present invention. The method may be implemented by means of the ultrasound imaging probe described in embodiment one. As shown in fig. 6, the method includes the steps of:
s110: an ultrasonic transducer arranged on the head of the ultrasonic imaging probe body is controlled to emit ultrasonic waves towards the tissue to be detected and receive a first ultrasonic echo signal reflected by the tissue to be detected.
The ultrasonic transducer 12 provided at the head of the ultrasonic imaging probe body 10 may be an ultrasonic transducer or an ultrasonic transducer array.
Step S110 obtains a first ultrasonic echo signal reflected by the tissue to be detected before deforming the tissue to be detected, and the first ultrasonic echo signal can be used as a reference signal.
S120: and generating a first preset electric signal to excite the Langeut vibrator to longitudinally vibrate, wherein the head of the ultrasonic imaging probe body is driven to act on the tissue to be detected to deform during the longitudinal vibration of the Langeut vibrator.
In fig. 1 and fig. 2, 50 is a tissue to be detected, and as shown in fig. 3, when the head of the main body 10 approaches the tissue to be detected after the longitudinal vibration of the langevin vibrates the head of the main body 10 back and forth, the tissue to be detected can be deformed.
S130: and controlling an ultrasonic transducer arranged on the head of the ultrasonic imaging probe body to emit ultrasonic waves towards the tissue to be detected and receiving a second ultrasonic echo signal reflected by the tissue to be detected.
S140: elastic imaging information is determined from the first ultrasonic echo signal and the second ultrasonic echo signal.
According to the first echo signal and the second ultrasonic echo signal respectively reflected before and after deformation of the tissue to be detected, response parameters such as displacement, strain rate, shear wave propagation speed and the like of the tissue to be detected can be obtained, and further, relative values of mechanical properties of materials such as Young modulus and Poisson's ratio of the tissue to be detected are estimated to serve as elastography information.
According to the elastic imaging method, the longitudinal vibration mode of the Langerhans 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 acquire ultrasonic echo information, and the tissue to be detected in front of the head of the main body can be deformed without adopting a motor, so that the ultrasonic imaging probe is not influenced by a magnetic field; the Langevin vibrator deforms the piezoelectric material through the inverse piezoelectric effect, and the volume is smaller, so that the volume of the ultrasonic imaging probe can be reduced, and the weight of the ultrasonic imaging probe can be lightened.
Example III
Fig. 7 shows a flowchart of another elastography method according to an embodiment of the present invention. The method may be implemented by means of the ultrasound imaging probe described in embodiment one. As shown in fig. 7, the method includes the steps of:
s210: an ultrasonic transducer arranged on the head of the ultrasonic imaging probe body is controlled to emit ultrasonic waves towards the tissue to be detected and receive a first ultrasonic echo signal reflected by the tissue to be detected. Please refer to step S110.
S220: and generating a first preset electric signal to excite the Langeut vibrator to longitudinally vibrate, wherein the head of the ultrasonic imaging probe body is driven to act on the tissue to be detected to deform during the longitudinal vibration of the Langeut vibrator. Please refer to step S120.
S230: and controlling an ultrasonic transducer arranged on the head of the ultrasonic imaging probe body to emit ultrasonic waves towards the tissue to be detected and receiving a second ultrasonic echo signal reflected by the tissue to be detected.
S240: and controlling an ultrasonic transducer arranged on the head of the ultrasonic imaging probe body to emit ultrasonic waves towards the tissue to be detected and receiving a third ultrasonic echo signal reflected by the tissue to be detected.
S250: and determining the propagation speed of a shear wave according to the first ultrasonic echo signal, the second ultrasonic echo signal and the third ultrasonic echo signal, wherein the shear wave is a waveform propagated from a deformation position to a depth position 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, shear waves generated inside propagate outwards from the deformed point in the form of a sphere.
For the same preset inclination angle position, the first ultrasonic echo signal is taken as a reference, and the shear wave crest position at the first moment t1 can be determined according to the first ultrasonic echo signal and the second ultrasonic echo signal; and by taking the first ultrasonic echo signal as a reference, determining the shear wave crest position at the second time t2 according to 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 time t2 and the time t 1.
S260: and determining the Young modulus of the tissue to be detected according to the propagation speed of the shear wave.
The relationship between Young's modulus and shear wave is: e=3×ρ×v s 2 . Wherein E is Young's modulus; ρ is the density (kg/m) of the tissue to be examined 3 ) Is constant; v (V) s Is the propagation velocity of the shear wave. From this, the Young's modulus of the tissue to be examined can be determined from the propagation velocity of the shear wave.
As an alternative implementation of the present embodiment, as shown in fig. 13, step S250 includes S251, S252, S253, S254, S255, and S256.
S251: determining a serial number n of a corresponding sampling point of a first peak of the shear wave in the second ultrasonic echo signal according to the first ultrasonic echo signal and the second ultrasonic echo signal 1 。
As shown in fig. 9, an ultrasonic echo signal is acquired at a predetermined sampling frequency, wherein an ultrasonic echo amplitude of an earlier sampling time in the ultrasonic echo signal corresponds to a shallower tissue in the tissue to be detected, and an ultrasonic echo amplitude of 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 within the same and/or adjacent predetermined time periods (may be selected by using a window function, where the length of the window function is the predetermined time period), and calculate a cross-correlation value of the selected first ultrasonic echo signal and the selected second ultrasonic echo signal. And when the cross-correlation value is smaller than the preset value, determining the serial number of the sampling point in the preset time period corresponding to the cross-correlation value as the serial number of the corresponding sampling point of the wave crest in the second ultrasonic echo signal.
For example, as shown in fig. 9, a cross-correlation value can be calculated by selecting the first ultrasonic echo signal and the second ultrasonic echo signal in the A2-A1 time period through a hanning window; and then selecting a first ultrasonic echo signal in the A2-A1 time period and a second ultrasonic echo signal in the B2-B1 time period 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 C is XX (N) is a cross-correlation value, N is a set of sampling points within a predetermined period of time, RF 1 (N) is the amplitude, RF, of the nth sample point within the set of sample points N in the first ultrasonic echo signal 2 (N) is the amplitude of the nth sampling point within the set of sampling points N in the second ultrasonic echo signal,for the average value of the corresponding amplitudes of all sampling points in the set N of sampling points in the first ultrasonic echo signal,/>And the average value of the corresponding amplitudes of all 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 the same theoretically, and the cross correlation value should be 1 (or be affected by other factors, less than 1 but close to 1) in the same period of time. The tissue to be detected at the peak position of the shear wave on the second ultrasonic echo signal is extruded under the influence of the shear wave, and the cross correlation value of the ultrasonic echo signal at the peak position and the first ultrasonic echo signal in the same or adjacent time periods is smaller, namely the difference between the ultrasonic echo signal and the first ultrasonic echo signal is larger. According to the method and the device, the positions corresponding to the shear wave peaks can be rapidly determined through the cross-correlation values of the first ultrasonic echo signals and the second ultrasonic echo signals in the same or adjacent preset time periods.
S252: determining the sequence of the second peak of the shear wave corresponding to the sampling point in the third ultrasonic echo signal according to the first ultrasonic echo signal and the third ultrasonic echo signalNumber n 2 。
Step S252 may select signals of the first ultrasonic echo signal and the third ultrasonic echo signal within the same and/or adjacent predetermined time periods multiple times, and calculate a cross-correlation value of the selected first ultrasonic echo signal and third ultrasonic echo signal. And when the cross-correlation value is smaller than the preset value, determining the serial number of the sampling point in the preset time period corresponding to the cross-correlation value as the serial number of the corresponding sampling point of the wave crest in the third ultrasonic echo signal. In particular, please refer to step S251.
S253: acquiring propagation velocity v of ultrasonic wave 0 The sampling frequency f of the ultrasound echo.
S254: calculating the displacement s from the first peak to the second peak:
s255: acquiring a time interval t between receiving the second ultrasonic echo and receiving the third ultrasonic echo 1 。
S256: calculating the propagation speed of the shear wave:
as a parallel alternative to the above alternative, as shown in fig. 10, step S250 may include only S257, S258, and S259.
S257: determining a serial number n of a corresponding sampling point of a first peak of the shear wave in the second ultrasonic echo signal according to the first ultrasonic echo signal and the second ultrasonic echo signal 1 。
S258: acquiring propagation velocity v of ultrasonic wave 0 The sampling frequency f of the ultrasound echo.
S259: calculating the displacement s of the shear wave from the deformation point to the first peak:
s2510: obtaining a time interval t between the time when the deformation of the tissue to be detected is ended and the time when the second ultrasonic echo is received 2 。
S2511: calculating the propagation speed of the shear wave:
the method embodiment provides a method for determining the elastographic information of a certain position on the tissue to be detected according to the ultrasonic echo signals of the certain position.
However, it takes a long time to acquire the elastic information of different point positions in a region of the tissue to be detected one by providing one ultrasonic transducer on the ultrasonic imaging probe. The existing mode often adopts an ultrasonic transducer array to transmit or receive ultrasonic echoes corresponding to different positions of the tissue to be detected, so that elastic information in a region is acquired. However, the existing approaches require that multiple ultrasound transducers must be provided on the ultrasound imaging probe, resulting in a larger, more cumbersome ultrasound imaging probe. Therefore, the field of view of the ultrasonic transducer can be increased by adopting the Langeut vibrator bending vibration, so that a plurality of ultrasonic transducers are not required to be arranged on an ultrasonic imaging probe, and the ultrasonic imaging probe has small size and light weight. For example, the following fourth embodiment or fifth embodiment may be adopted.
Example IV
Fig. 11 shows a flow chart of another elastography method according to an embodiment of the invention, which can be implemented by means of the ultrasound imaging probe of embodiment one. As shown in fig. 11, the method includes the steps of:
s310: the ultrasonic transducer of the head of the ultrasonic imaging probe body is driven to transversely swing within a preset inclination angle range in the process of transversely bending and vibrating the Langerhan vibrator arranged on the ultrasonic imaging probe body according to a preset direction.
Fig. 12 shows a side view of an ultrasonic imaging probe emitting ultrasonic waves to a tissue to be detected, and fig. 13 shows a schematic view of respective predetermined inclinations. Arrows OA and OB represent the maximum amplitude on both sides of the langevin oscillator when it is laterally oscillated, for example, the included angle θ may be 15 ° with respect to the position when it is not oscillated (the position shown as OO ' in fig. 12), and AA ' and BB ' are the propagation paths of the ultrasonic signals in the tissue to be detected, respectively.
S320: the ultrasonic transducer is controlled to emit ultrasonic waves towards the tissue to be detected when swinging to at least one preset inclination angle and receive a first ultrasonic echo signal reflected by the tissue to be detected.
Fig. 14 shows a top view of the range over which ultrasound echoes can be received by ultrasound waves emitted by an ultrasound imaging probe within the tissue to be examined. Wherein A 'B' is the range in which ultrasonic echo can be received by the ultrasonic transducer when the ultrasonic transducer is driven by the Langevin vibrator to bend and vibrate in the A 'B' direction. When the Langevin vibrator is bent and vibrated in the direction A 'B', ultrasonic waves can be emitted towards the tissue to be detected at any angle and ultrasonic echoes can be received, ultrasonic echo signals of any point on the straight line A 'B' can be obtained, and then the elastography information of any position of the tissue to be detected on the straight line can be obtained.
S330: and determining the elastography information of the tissue position to be detected corresponding to the preset inclination angle according to the first ultrasonic echo signal. Please refer to step S140.
As shown in fig. 14, C 'D' is a range in which the ultrasonic transducer can receive an ultrasonic echo when the ultrasonic transducer is driven by the lanjevin vibrator to bend in the direction C 'D', and E 'F' is a range … … in which the ultrasonic transducer can receive an ultrasonic echo when the ultrasonic transducer is driven by the lanjevin vibrator to bend in the direction E 'F', so that theoretically, if the transverse bending direction of the lanjevin vibrator is converted under the condition that the preset inclination angle range is unchanged, an ultrasonic echo signal of any position on the tissue to be detected in the shadow area in fig. 14 can be obtained, and then the elastography information of the tissue to be detected in the area can be obtained.
According to the elastic imaging method, the bending vibration mode of the Langevin vibrator is utilized to drive the head of the main body to transversely swing, so that the ultrasonic transducer arranged on the head of the main body can send ultrasonic waves to the tissue positions to be detected in multiple directions and receive ultrasonic echoes, elastic imaging information in a region on the tissue to be detected can be obtained through one or fewer 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.
Example five
Fig. 15 shows a flow chart of another elastography method according to an embodiment of the invention, which can be implemented by means of the ultrasound imaging probe of embodiment one. As shown in fig. 15, the method includes the steps of:
s410: the ultrasonic transducer of the head of the ultrasonic imaging probe body is driven to transversely swing within a preset inclination angle range in the process of transversely bending and vibrating the Langerhan vibrator arranged on the ultrasonic imaging probe body according to a preset direction. Please refer to step S310.
S420: the ultrasonic transducer is controlled to emit ultrasonic waves towards the tissue to be detected when swinging to at least one preset inclination angle and receive a first ultrasonic echo signal reflected by the tissue to be detected. Please refer to step S320.
S430: and generating a first preset electric signal to excite the Langeut vibrator to longitudinally vibrate, wherein the Langeut 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.
It should be noted that, the method of deforming the tissue to be detected in the step S430 is not limited to the method of using the langevin vibrator to drive the main body head to vibrate longitudinally, but may also use a motor to drive the main body head to vibrate longitudinally, or may also use other devices to press or press manually.
As a modification of step S430, the tissue to be detected may be pressed only once to deform 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 short-term attenuation of one peak. Fig. 16 shows a schematic representation of only one shear wave peak in the tissue to be examined, wherein the solid curve represents the peak position at the current moment and the dashed curve represents the peak position at the past moment.
For this reason, the step S430 presses the tissue to be detected once at each predetermined time interval to deform the tissue to be detected, so that the shear wave in the tissue to be detected can have multiple peaks, 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 acquisition of ultrasonic echo signals at multiple positions in the subsequent langevin vibrator bending and vibrating process is facilitated. Fig. 12 and 14 show schematic diagrams of a plurality of shear wave peaks in a tissue to be detected, wherein a solid curve represents a peak position at a current time and a dotted curve represents a trough position at the current time.
S440: and controlling the ultrasonic transducer to emit ultrasonic waves towards the tissue to be detected when swinging to the preset inclination angle again, and receiving a second ultrasonic echo signal reflected by the tissue to be detected.
The ultrasonic wave propagation velocity is much greater than the shear wave propagation velocity. Taking a 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 continuous excitation time of the shear wave is set to 0.2/5=0.04 s. The ultrasonic wave propagation speed is about 1540m/s, and the maximum detection time for transmitting and returning the ultrasonic wave once is as follows: 0.2 x 2/1540=2.5 x 10 -4 s. The bending vibration working frequency of the Langevin vibrator is about 65Hz, the bending angle ranges from-15 degrees to 15 degrees, ultrasonic signals (ultrasonic signals are emitted and acquired every 2 degrees) on 15 straight lines (each preset inclination angle corresponds to one straight line) are acquired in the angle range, and the scanning time on each straight line is 1/65/2/15=5.13×10 -4 s, can meet the requirement of transmitting and receiving 2 times of ultrasonic signals on the same straight line.
Referring to fig. 13, assuming that the inclination angle of the langevin vibrator in the transverse bending direction is θ, ultrasonic waves are transmitted once every Δ angle and ultrasonic echoes are received, the number of times of ultrasonic waves transmitted in a half cycle of the langevin vibrator bending (half cycle from- θ to +θ) isThe scanning time on each line is +.>Assuming that the depth of the tissue to be detected is H, the propagation speed of the ultrasonic wave is v u The maximum detection time of the ultrasonic wave emitted and returned once is +.>It follows that only the design is required to satisfyThe ultrasonic wave can be transmitted once every delta angle and the ultrasonic echo can be received; if n ultrasonic waves are required to be transmitted and ultrasonic echoes are required to be received every delta angle, the design of +.>
S450: 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 depth after the tissue to be detected is deformed. Please refer to step S250.
S460: and determining the Young modulus of the tissue position to be detected corresponding to the preset inclination angle according to the propagation speed of the shear wave. Please refer to step S260.
Example six
Fig. 17 shows a schematic block diagram of an elastography device according to an embodiment of the invention, which may be used to implement the elastography method of embodiment two or embodiment three, or any of its alternative implementations. As shown in fig. 17, the apparatus includes a first control unit 10, a first excitation unit 20, a second control unit 30, and a determination unit 40.
The first control unit 10 is used for controlling an ultrasonic transducer arranged on the head of the ultrasonic imaging probe body to emit ultrasonic waves towards the tissue to be detected and receiving a first ultrasonic echo signal reflected by the tissue to be detected.
The first excitation unit 20 is configured to generate a first predetermined electrical signal to excite the langevin vibrator to vibrate longitudinally, and drive the head of the ultrasonic imaging probe body to act on the tissue to be detected to deform during the longitudinal vibration of the langevin vibrator.
The second control unit 30 is configured to control an ultrasonic transducer disposed on the head of the ultrasonic imaging probe body to emit ultrasonic waves toward the tissue to be detected and to receive a second ultrasonic echo signal reflected by the tissue to be detected.
The determining unit 40 is configured to determine elastographic information from the first ultrasound echo signal and the second ultrasound echo signal.
The elastic imaging device can enable the ultrasonic imaging probe not to be affected by the magnetic field, and can reduce the volume of the ultrasonic imaging probe and the weight of the ultrasonic imaging probe. Please refer to the second embodiment.
As an alternative implementation of the present embodiment, as shown in fig. 18, the determining unit 40 includes a first determining subunit 41 and a second determining subunit 42. The first determining subunit 41 is configured to determine a propagation speed of a shear wave according to the first ultrasonic echo signal and the second ultrasonic echo signal, where the shear wave is a waveform propagated from a deformation position to a depth after the tissue to be detected is deformed. The second determination subunit 42 is configured to determine the young's modulus of the tissue to be detected according to the propagation speed of the shear wave.
As an alternative implementation of this embodiment, as shown in fig. 18, the apparatus further includes a third control unit 50 for controlling the ultrasonic transducer provided at the head of the ultrasonic imaging probe body to emit ultrasonic waves toward the tissue to be detected and to receive the third ultrasonic echo signal reflected by the tissue to be detected.
The first determination subunit 41 includes a third determination subunit 411, a fourth determination subunit 412, a first acquisition subunit 413, a first calculation subunit 414, a second acquisition subunit 415, and a second calculation subunit 416. The third determining subunit 411 is configured to determine, according to the first ultrasonic echo signal and the second ultrasonic echo signal, a sequence number n1 of a corresponding sampling point of the first peak of the shear wave in the second ultrasonic echo signal. The fourth determining subunit 412 is configured to determine a sequence 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 signal 2 . The first acquisition subunit 413 is configured to acquire propagation velocity v of the ultrasonic wave 0 The sampling frequency f of the ultrasound echo.
The first calculating subunit 414 is configured to calculate a displacement s from the first peak to the second peak:the second acquisition subunit 415 is configured to acquire a time interval t between receiving the second ultrasonic echo and receiving the third ultrasonic echo 1 . The second calculation subunit 416 is configured to calculate a propagation velocity of the shear wave: />
Alternatively, as shown in fig. 18, the third determination subunit 411 includes a third calculation subunit and a fifth determination subunit. The third calculation subunit is used for selecting signals of the first ultrasonic echo signal and the second ultrasonic echo signal in the same and/or adjacent preset time period for a plurality of times, and calculating the cross-correlation value of the selected first ultrasonic echo signal and second ultrasonic echo signal. And the fifth determining subunit is used for determining the serial number of the sampling point in the preset time period corresponding to the cross-correlation value as the serial number of the corresponding sampling point of the wave crest in the second ultrasonic echo signal when the cross-correlation value is smaller than the preset value.
Alternatively, as shown in fig. 18, the fourth determination subunit 412 includes a third calculation subunit and a fifth determination subunit. The third calculation subunit is used for selecting signals of the first ultrasonic echo signal and the third ultrasonic echo signal in the same and/or adjacent preset time period for a plurality of times, and calculating the cross-correlation value of the selected first ultrasonic echo signal and the third ultrasonic echo signal. And the fifth determining subunit is used for determining the serial number of the sampling point in the preset time period corresponding to the cross-correlation value as the serial number of the corresponding sampling point of the wave crest in the third ultrasonic echo signal when the cross-correlation value is smaller than the preset value.
Fig. 19 is a schematic diagram of a hardware structure of an elastography device for performing an elastography method according to an embodiment of the present invention, as shown in fig. 19, where the device includes an ultrasound imaging probe 1910, a display 1920, one or more processors 1930, and a memory 1940, and one processor 1930 is illustrated in fig. 19.
The ultrasound imaging probe 1910, display 1920, processor 1930 and memory 1940 may be connected by a bus or other means, for example in fig. 19.
The ultrasound imaging probe 1910 may be as described in the first embodiment for transmitting ultrasound waves to the tissue to be examined and acquiring ultrasound echo signals. The display 1920 is used for displaying elastographic information of the tissue to be detected.
Processor 1930 may be a central processing unit (Central Processing Unit, CPU). Processor 1930 may also be other general purpose processors, digital signal processors (Digital Signal Processor, DSP), application specific integrated circuits (App 1ication Specific Integrated Circuit, ASIC), field programmable gate arrays (Field-Programmable Gate Array, FPGA) or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components, or a combination thereof. A general purpose processor may be a microprocessor or the processor may be any conventional processor or the like.
It should be noted that the processor 1930 may be disposed outside the ultrasound imaging probe 1910 or may be disposed inside the ultrasound imaging probe 1910.
The memory 1940 is used as a non-transitory computer readable storage medium, and may be used to store a non-transitory software program, a non-transitory computer executable program, and modules, such as program instructions/modules (e.g., the first control unit 10, the first excitation unit 20, the second control unit 30, and the determination unit 40 shown in fig. 17) corresponding to the elastography method in the embodiment of the present application. The processor 1930 executes various functional applications of the server and data processing, i.e., implements the elastography method of the method embodiments described above, by running non-transitory software programs, instructions, and modules stored in the memory 1940.
Memory 1940 may include a storage program area that may store an operating system, at least one application program required for functionality, and a storage data area; the storage data area may store data created according to the use of the processing apparatus operated by the list item, or the like. In addition, memory 1940 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 1940 optionally includes memory located remotely from processor 1930, which may be connected to the list item operated processing device via a network. 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 1940 that, when executed by the one or more processors 1930, perform the methods illustrated in fig. 6, 10.
The product can execute the method provided by the embodiment of the invention, and has the corresponding functional modules and beneficial effects of the execution method. Technical details which are not described in detail in the present embodiment can be found in the embodiments shown in fig. 6 and 10.
The embodiment of the invention also provides a non-transitory computer storage medium, which stores computer executable instructions that can execute the elastography method in any of the above method embodiments. Wherein the storage medium may be a magnetic Disk, an optical Disk, a Read-Only Memory (ROM), a random access Memory (Random Access Memory, RAM), a Flash Memory (Flash Memory), a Hard Disk (HDD), or a Solid State Drive (SSD); the storage medium may also comprise a combination of memories of the kind described above.
It will be appreciated by those skilled in the art that implementing all or part of the above-described embodiment method may be implemented by a computer program to instruct related hardware, where the program may be stored in a computer readable storage medium, and the program may include the above-described embodiment method when executed. 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 embodiments of the present invention have been described in connection with the accompanying drawings, various modifications and variations may be made by those skilled in the art without departing from the spirit and scope of the invention, and such modifications and variations are within the scope of the invention as defined by the appended claims.
Claims (6)
1. An elastography method, comprising:
controlling an ultrasonic transducer arranged on the head of an ultrasonic imaging probe body to emit ultrasonic waves towards tissue to be detected and receiving a first ultrasonic echo signal reflected by the tissue to be detected;
generating a first preset electric signal to excite the Langeut vibrator to longitudinally vibrate, wherein the Langeut vibrator drives the head of the ultrasonic imaging probe main body to act on the tissue to be detected to deform when longitudinally vibrating;
controlling an ultrasonic transducer arranged on the head of the ultrasonic imaging probe body to emit ultrasonic waves towards the tissue to be detected and receiving a second ultrasonic echo signal reflected by the tissue to be detected;
determining elastic imaging information according to the first ultrasonic echo signal and the second ultrasonic echo signal;
the step of determining elastographic information from the first ultrasound echo signal and the second ultrasound echo signal comprises:
Determining the propagation speed of a shear wave according to the first ultrasonic echo signal and the second ultrasonic echo signal, wherein the shear wave is a waveform propagated from a deformation position to a depth position after the tissue to be detected is deformed;
determining Young modulus of the tissue to be detected according to the propagation speed of the shear wave;
after the step of controlling the ultrasonic transducer arranged on the head of the ultrasonic imaging probe body to emit ultrasonic waves towards the tissue to be detected and receiving the second ultrasonic echo signal reflected by the tissue to be detected, the method further comprises the following steps: controlling an ultrasonic transducer arranged on the head of the ultrasonic imaging probe body to emit ultrasonic waves towards the tissue to be detected and receiving a third ultrasonic echo signal reflected by the tissue to be detected;
the step of determining the propagation speed of the shear wave from the first ultrasonic echo signal and the second ultrasonic echo signal comprises:
based on the first ultrasonic echo signal and the first ultrasonic echo signalDetermining a serial number n of a sampling point corresponding to a first peak of the shear wave in the second ultrasonic echo signal by the second ultrasonic echo signal 1 ；
Determining a serial number n of a corresponding sampling point of a second peak of the shear wave in the third ultrasonic echo signal according to the first ultrasonic echo signal and the third ultrasonic echo signal 2 ；
Acquiring propagation velocity v of ultrasonic wave 0 Sampling frequency f of ultrasonic echo;
calculating a displacement s of the first peak to the second peak:
acquiring a time interval t between receiving the second ultrasonic echo and receiving the third ultrasonic echo 1 ；
Calculating the propagation speed of the shear wave:
2. the elastography method of claim 1, wherein determining a sequence number of a corresponding sampling point of the first peak of the shear wave in the second ultrasonic echo signal from the first ultrasonic echo signal and the second ultrasonic echo signal comprises:
selecting signals of the first ultrasonic echo signal and the second ultrasonic echo signal in the same and/or adjacent preset time period for multiple times, and calculating the cross-correlation value of the selected first ultrasonic echo signal and 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 the preset time period corresponding to the cross-correlation value as the serial number of the corresponding sampling point of the first wave crest in the second ultrasonic echo signal.
3. The elastography method of claim 1, wherein determining a sequence number of a second peak of the shear wave in the third ultrasound echo signal corresponding to a sampling point in the third ultrasound echo signal from the first ultrasound echo signal and the third ultrasound echo signal comprises:
Selecting signals of the first ultrasonic echo signal and the third ultrasonic echo signal in the same and/or adjacent preset time period for multiple times, and calculating the cross-correlation value of the selected first ultrasonic echo signal and 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 the preset time period corresponding to the cross-correlation value as the serial number of the corresponding sampling point of the second wave crest in the third ultrasonic echo signal.
4. An elastographic device, comprising:
the first control unit is used for controlling an ultrasonic transducer arranged on the head of the ultrasonic imaging probe body to emit ultrasonic waves towards the tissue to be detected and receiving a first ultrasonic echo signal reflected by the tissue to be detected;
the first excitation unit is used for generating a first preset electric signal to excite the Langeut vibrator to longitudinally vibrate, and the head of the ultrasonic imaging probe main body is driven to act on the tissue to be detected to deform during the longitudinal vibration of the Langeut vibrator;
the second control unit is used for controlling an ultrasonic transducer arranged on the head of the ultrasonic imaging probe body to emit ultrasonic waves towards the tissue to be detected and receiving a second ultrasonic echo signal reflected by the tissue to be detected;
A determining unit for determining elastic imaging information according to the first ultrasonic echo signal and the second ultrasonic echo signal;
the determining elasticity imaging information according to the first ultrasonic echo signal and the second ultrasonic echo signal comprises:
determining the propagation speed of a shear wave according to the first ultrasonic echo signal and the second ultrasonic echo signal, wherein the shear wave is a waveform propagated from a deformation position to a depth position after the tissue to be detected is deformed;
determining Young modulus of the tissue to be detected according to the propagation speed of the shear wave;
after the step of controlling the ultrasonic transducer arranged on the head of the ultrasonic imaging probe body to emit ultrasonic waves towards the tissue to be detected and receiving the second ultrasonic echo signal reflected by the tissue to be detected, the method further comprises the following steps: controlling an ultrasonic transducer arranged on the head of the ultrasonic imaging probe body to emit ultrasonic waves towards the tissue to be detected and receiving a third ultrasonic echo signal reflected by the tissue to be detected;
the step of determining the propagation speed of the shear wave from the first ultrasonic echo signal and the second ultrasonic echo signal comprises:
determining a serial number n of a corresponding sampling point of a first peak of the shear wave in the second ultrasonic echo signal according to the first ultrasonic echo signal and the second ultrasonic echo signal 1 ；
Determining a serial number n of a corresponding sampling point of a second peak of the shear wave in the third ultrasonic echo signal according to the first ultrasonic echo signal and the third ultrasonic echo signal 2 ；
Acquiring propagation velocity v of ultrasonic wave 0 Sampling frequency f of ultrasonic echo;
calculating a displacement s of the first peak to the second peak:
acquiring a time interval t between receiving the second ultrasonic echo and receiving the third ultrasonic echo 1 ；
Calculating the propagation speed of the shear wave:
5. an elastic imaging apparatus, characterized by comprising: an ultrasound imaging probe, a display, a memory and a processor, the ultrasound imaging probe, the display, the memory and the processor being communicatively coupled to each other, the memory having stored therein computer instructions, the processor executing the computer instructions to perform the elastography method of any of claims 1-3.
6. A computer-readable storage medium, characterized in that the computer-readable storage medium stores computer instructions for causing the computer to execute the elastography method of any of claims 1-3.
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| CN108065964B (en) * | 2018-01-16 | 2021-04-20 | 中国科学院苏州生物医学工程技术研究所 | Ultrasonic imaging method, device and equipment and ultrasonic imaging probe |
| CN111401108B (en) * | 2019-01-02 | 2021-04-06 | 无锡海斯凯尔医学技术有限公司 | Slope parameter extraction method and device and computer readable storage medium |
| CN109717904B (en) * | 2019-01-30 | 2024-02-23 | 清华大学 | Elastography system |
| CN109717905B (en) * | 2019-01-30 | 2024-02-23 | 清华大学 | Probe for elastography |
| CN110301939A (en) * | 2019-07-15 | 2019-10-08 | 无锡海斯凯尔医学技术有限公司 | Imaging of tissue and parameter detecting system |
| CN114126492A (en) * | 2020-05-14 | 2022-03-01 | 深圳迈瑞生物医疗电子股份有限公司 | Ultrasonic imaging equipment and method |
| CN114216857B (en) * | 2021-11-25 | 2023-12-22 | 长江存储科技有限责任公司 | Method for detecting film |
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