CN111358493B - Data processing method, device, equipment and medium applied to ultrasonic imaging - Google Patents
Data processing method, device, equipment and medium applied to ultrasonic imaging Download PDFInfo
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Abstract
The application discloses a data processing method, a device, equipment and a medium applied to ultrasonic imaging. And calculating the average phase difference of the demodulation data corresponding to each initial phase according to the sequence of the ultrasonic echoes. In the process of fixed point, the influence of different initial phases on the phase precision is different, so different initial phases are adopted, the part without precision loss of the phase can translate in the depth direction along with the difference of the initial phases, each initial phase can contain different parts without precision loss of the phase, and more or even all depths are covered. And finally, determining the final phase difference according to the obtained plurality of average phase differences, so that the phase difference can weaken or even eliminate the quantization error in the fixed-point process.
Description
Technical Field
The present application relates to the field of ultrasound technologies, and in particular, to a data processing method, apparatus, device, and medium for ultrasound imaging.
Background
Two great advantages of the current medical ultrasonic imaging are that one of the two great advantages can detect and calculate the moving speed direction of the tissue and the blood flow in real time, namely ultrasonic Doppler tissue and blood flow imaging; the other is to calculate the deformation of the tissue or the propagation velocity of the shear wave of the tissue by detecting the motion of the tissue, so as to obtain the hardness distribution of the tissue or the absolute hardness of the tissue, i.e. ultrasonic elastography. The key algorithm for current ultrasound doppler tissue and blood flow imaging and ultrasound elastography is to detect and calculate the displacement and velocity of tissue or blood flow. Currently, calculating tissue or blood flow displacement and velocity based on the phase difference of the ultrasonic echoes is the most common method in ultrasonic imaging.
In the prior art, an orthogonal demodulation algorithm is used in the calculation of the phase difference of the ultrasonic echo, specifically, the following formula is adopted:
the LPF represents low-pass filtering, the RF represents an ultrasonic echo signal, cos and sin represent a cosine signal and a sine signal of a local oscillation signal respectively, the absolute values of the amplitudes of the two signals are periodically changed between 0 and 1, w represents the frequency of the local oscillation signal (generally the same as the transmission frequency), and t represents time.
Due to the requirements of the operation speed and the power consumption, the above quadrature demodulation processing is generally performed by fixed-point processing (digital signals), and the wider the fixed-point bit width of the data is, the smaller the fixed-point accuracy loss is, but the larger the occupied processor resource is. Assuming that RF is fixed-point data with a bit width of 24 bits, and local oscillator signals cos and sin dequantize data according to a bit width of 16 bits respectively, after multiplying and mixing the two (as in equation 1), if precision is not lost, a bit width of 16+24=40 bits is needed, but actually, a bit width of 40 bits is very large for consumption of hardware resources.
To solve this problem, in the prior art, the above result is generally truncated, for example, 24 bits are truncated, and in the truncation process, in order to prevent the saturation truncation of the relatively large signal, the higher 24 bits are generally truncated.
It is obvious that, in the above truncation process, assuming that a point on the RF signal has a small value and occupies only the lower 8 bits of the 24-bit width, and this point has an effective bit width of only 12 bits after multiplying (according to equation 1) the corresponding point with a small amplitude value in the local oscillator signal, for example, occupies only the lower 4 bits of the 16-bit width, and in the above truncation process (truncating and retaining the upper 24 bits), the local oscillator signal is directly truncated to 0, i.e. I and Q in equation 1 may be 0. And the phase of a certain point is calculated by the following formula:
it is clear that this directly results in the current pointThe phase is directly changed to a fixed value (
Integer multiples of). When the IQ signal corresponding to the next echo signal is subjected to phase difference calculation, an error occurs in the phase difference. If the phase difference with a large error is used as a parameter for calculating the displacement and velocity of the tissue or blood flow, a deviation of the calculation result must be caused. />
In summary, how to reduce the phase difference of the ultrasonic echo signals is an urgent problem to be solved by those skilled in the art.
Disclosure of Invention
The invention aims to provide a data processing method, a data processing device, data processing equipment and a data processing medium applied to ultrasonic imaging, which are used for reducing the calculation error of the phase difference of ultrasonic echo signals.
In order to solve the above technical problem, the present application provides a data processing method applied to ultrasonic imaging, including:
receiving at least 2 ultrasonic echoes corresponding to the position to be detected;
performing quadrature demodulation processing on each ultrasonic echo by using local oscillation signals of multiple initial phases to obtain multi-channel demodulation data of each ultrasonic echo; wherein the plurality of initial phases adopted by the ultrasonic echoes are consistent;
calculating an average phase difference of the demodulation data corresponding to the same initial phase;
and determining the final phase difference of the demodulated data according to the average phase difference corresponding to each initial phase.
Preferably, the determining a final phase difference according to the average phase difference comprises:
acquiring a threshold value of the current fixed-point truncation;
judging whether demodulation data with the absolute value of the real part or the imaginary part smaller than the threshold exists in each demodulation data;
if yes, eliminating the demodulated data meeting the conditions;
and calculating the average value of the average phase differences corresponding to the rest of the demodulation data as the final phase difference.
Preferably, the determining a final phase difference according to the average phase difference comprises:
calculating an average value of all the average phase differences as the final phase difference.
Preferably, before the quadrature demodulation processing, the method further includes:
and performing beam synthesis processing on each ultrasonic echo.
Preferably, the method further comprises the following steps:
and calculating the displacement and/or the speed corresponding to the position to be detected according to the final phase difference.
Preferably, the calculating an average phase difference for the demodulated data corresponding to the same initial phase comprises:
filtering the multiple paths of the demodulation data through a plurality of wall filters;
carrying out complex autocorrelation on the demodulated data after filtering processing to obtain a plurality of phases;
and calculating the average phase difference corresponding to a plurality of phases.
Preferably, the plurality of initial phases are uniformly distributed within 360 °.
In order to solve the above technical problem, the present application further provides a data processing apparatus applied to ultrasonic imaging, including:
the receiving module is used for receiving at least 2 ultrasonic echoes corresponding to the position to be detected;
the processing module is used for performing orthogonal demodulation processing on each ultrasonic echo by using local oscillation signals of multiple initial phases to obtain multi-channel demodulation data of each ultrasonic echo; the multiple initial phases adopted by the ultrasonic echoes correspond to each other;
the calculation module is used for calculating an average phase difference of the demodulation data corresponding to the same initial phase;
and the determining module is used for determining the final phase difference according to the average phase difference.
In order to solve the above technical problem, the present application further provides an ultrasonic imaging apparatus for storing a computer program;
a processor for implementing the steps of the data processing method as described for ultrasound imaging when executing the computer program.
In order to solve the above technical problem, the present application further provides a computer-readable storage medium having a computer program stored thereon, where the computer program is executed by a processor to implement the steps of the data processing method applied to ultrasound imaging.
According to the data processing method applied to ultrasonic imaging, after ultrasonic echoes are received, orthogonal demodulation processing is carried out on the same ultrasonic echo through local oscillation signals of various initial phases, so that multiple paths of demodulation data can be obtained by the ultrasonic echo every time. After all the ultrasonic echoes are processed, the average phase difference of the demodulation data corresponding to each initial phase can be calculated according to the sequence of the ultrasonic echoes. Because the local oscillator signals have different influences on the phase precision due to different initial phases in the fixed-point process, the local oscillator signals with different initial phases are adopted in the orthogonal demodulation process, so that the parts without precision loss of the phases can translate in the depth direction along with the difference of the initial phases, each initial phase can possibly contain different parts without precision loss of the phases, and more or even all depths are covered. And finally, determining the final phase difference according to the obtained plurality of average phase differences, so that the phase difference can weaken or even eliminate the quantization error in the fixed-point process.
Drawings
In order to more clearly illustrate the embodiments of the present application, the drawings needed for the embodiments will be briefly described below, and it is obvious that the drawings in the following description are only some embodiments of the present application, and that other drawings can be obtained by those skilled in the art without inventive effort.
Fig. 1 is a flowchart of a data processing method applied to ultrasound imaging according to an embodiment of the present application;
fig. 2 is a schematic diagram of quadrature demodulation fixed-point truncation when an initial phase is 0 according to an embodiment of the present application;
FIG. 3 is a schematic diagram of quadrature demodulation fixed-point truncation when the initial phase is π/2 according to an embodiment of the present application;
fig. 4 is a schematic diagram of a quadrature demodulation process using multiple initial phases according to an embodiment of the present application;
fig. 5 is a structural diagram of a data processing apparatus applied to ultrasonic imaging according to an embodiment of the present application;
fig. 6 is a structural diagram of an ultrasonic imaging apparatus according to an embodiment of the present application.
Detailed Description
The technical solutions in the embodiments of the present application will be clearly and completely described below with reference to the drawings in the embodiments of the present application, and it is obvious that the described embodiments are only some embodiments of the present application, and not all embodiments. All other embodiments obtained by a person of ordinary skill in the art based on the embodiments in the present application without any creative effort belong to the protection scope of the present application.
The core of the application is to provide a data processing method, a device, equipment and a medium applied to ultrasonic imaging.
In order that those skilled in the art will better understand the disclosure, the following detailed description will be given with reference to the accompanying drawings.
Fig. 1 is a flowchart of a data processing method applied to ultrasound imaging according to an embodiment of the present disclosure. As shown in fig. 1, the method includes:
s10: and receiving at least 2 ultrasonic echoes corresponding to the position to be detected.
In the concrete implementation, on waiting to detect the position, according to fixed repetition period T, repeat 2 or more than 2 times transmission ultrasonic wave to the echo that produces when the corresponding receipt takes place the ultrasonic wave at every turn, ultrasonic wave echo in this application promptly. In this embodiment, the number of times of transmission of the ultrasonic wave is not limited, and the number of times of the ultrasonic wave echo is the same as the number of times of transmission. Although the transmission of the ultrasonic wave is simpler, the ultrasonic wave echo needs to be calculated with local oscillation signals of various initial phases, so the frequency of the ultrasonic wave echo is not too much, otherwise, the calculation amount is very large. In one embodiment, the number of transmissions may be 8-16, and the number of corresponding ultrasound echoes may be 8-16.
S11: and carrying out quadrature demodulation processing on each ultrasonic echo by adopting local oscillation signals of various initial phases to obtain multi-path demodulation data of each ultrasonic echo.
Although the time for receiving each ultrasonic echo differs, it is necessary to perform quadrature demodulation processing using a plurality of initial phases that are identical for each ultrasonic echo, for example, the initial phases of local oscillation signals of the plurality of initial phases are each set to Φ 1 、φ 2 、φ 3 、φ 4 Then, each ultrasonic echo is orthogonally demodulated according to the local oscillation signal of the initial phase, that is, the multiple initial phases adopted by each ultrasonic echo are all consistent.
In this embodiment, the selection of the initial phase is not limited, and may be arbitrarily selected within 360 °, but considering the problem of the amount of calculation, the types of the local oscillation signals are not too many, and may be, for example, 6. In addition, as a preferred embodiment, the plurality of initial phases are uniformly distributed within 360 °.
S12: and calculating the average phase difference of the demodulation data corresponding to the same initial phase.
As a preferred embodiment, the calculating an average phase difference for the demodulated data corresponding to the same initial phase comprises:
filtering the multi-path demodulation data through a plurality of wall filters;
carrying out complex autocorrelation on the demodulated data after filtering processing to obtain a plurality of phases;
and calculating the average phase difference corresponding to the plurality of phases.
The wall filter is a device for adjusting the filtering frequency of a pulse wave or continuous ultrasonic wave. The low frequency signals mostly come from wall motion signals such as atrial wall, ventricular wall, vessel wall, valve and chordae motion. In order not to interfere the frequency spectrum display, it is desirable to filter out the low-frequency blood flow signals, but at the same time, some low-frequency blood flow signals with the frequencies close to the frequencies are filtered out, so the selection of the filtering frequency is different according to the detection requirement, for example, 200-400 Hz can be selected for detecting low-speed blood flow (vena cava, pulmonary vein, atrioventricular valve); the normal high-speed blood flow (ventricular outflow tract and semilunar valve) can be selected from 400 to 800Hz; high velocity jets (valvular stenosis, regurgitation, intracardiac bypass jets) are preferably 800-1600 Hz, as desired.
It can be understood that the average phase difference corresponding to each initial phase is the same as the calculation method in the prior art, specifically, the following formula is adopted:
wherein LPF denotes low pass filtering, RF m Representing the mth ultrasonic echo signal, m is a positive integer, cos and sin respectively represent a cosine signal and a sine signal of the local oscillator signal, the absolute amplitude values of the cosine signal and the sine signal both vary periodically between 0 and 1, w represents the frequency of the local oscillator signal (generally the same as the transmitting frequency), t represents time, phi represents the time n Denotes the nth initial phase, n being a positive integer.
Specifically, the phase of a certain point is calculated by the following formula:
the phase difference between two adjacent ultrasonic echoes corresponding to the nth initial phase can be obtained by the formula (4) as follows:
Δφ xn ＝|φ x+1,n -φ xn [ equation 5 ]
Wherein x ∈ [1, m-1] is a positive integer, and then the average phase difference corresponding to the nth initial phase is:
s13: and determining the final phase difference of the demodulated data according to the average phase difference corresponding to each initial phase.
In S12, an average phase difference corresponding to each initial phase is calculated, and if the prior art is adopted, the displacement and/or the velocity corresponding to the position to be detected is calculated by only adopting the average phase difference corresponding to one of the initial phases. In the present application, the final phase difference is determined from a plurality of average phase differences corresponding to a plurality of initial phases. Because the influence of different initial phases on the phase precision is different, in the process of orthogonal demodulation, local oscillator signals of different initial phases are adopted, so that the part without precision loss of the phases can be translated in the depth direction along with the difference of the initial phases, each initial phase can possibly contain different parts without precision loss of the phases, and more or even all depths are covered. Therefore, the final phase difference determined by adopting a plurality of average phase differences can reduce the phase difference of the ultrasonic echo signals, and the calculated displacement and/or speed corresponding to the position to be detected can be more accurate.
In order to make the technical solutions provided by the present application more clear to those skilled in the art, a comparison of quadrature demodulation processing using a single initial phase and multiple initial phases is given below. For the quadrature local oscillator signals cos and sin, the dynamic range of the values is always periodically changed between-1 and 1, and the dynamic range of the values is assumed to be-2 after the k-bit fixed point is adopted k -1 ～2 k-1 The inner period of the ultrasonic wave is continuously changed, so that the ultrasonic wave echo signal (RF in formula 3) m ) Go on to 2 k The multiplied dynamic range is amplified, so that the precision is lost as long as the bit width of the subsequent truncation is less than the bit width after amplification. However, if the method is directed to a specific bit-slicing mode, such as slicing the high bits after the quadrature demodulation processing, the precision-loss part and the non-precision-loss part are fixed.
Fig. 2 is a schematic diagram of quadrature demodulation fixed-point truncation when an initial phase is 0 according to an embodiment of the present application. Wherein the horizontal axis is depth and the vertical axis is amplitude. In the process of the orthogonal demodulation processing, a process of multiplying two signals is adopted, and actually, the dynamic range or the value range of the original ultrasonic echo signal is amplified. The conventional limitation of hardware resources is to truncate the data in the quadrature demodulation process, which actually causes distortion caused by the forced reduction of the dynamic range of the signal. As shown in fig. 2, there is no truncation accuracy loss in the portion above the truncation line, and there is a truncation accuracy loss in the portion below the truncation line, i.e., the portion below the truncation line is all truncated to 0. As can be seen from fig. 2, by comparing the precision-free part (vertical axis) of the high-order fixed-point truncation bit with the precision-free part (horizontal axis) of the phase in the depth sequence, if the precision-free part (horizontal axis) of the high-order fixed-point truncation bit is obtained, the ultrasonic echo signal in the corresponding interval is mixed with the cos and sin signals respectively without loss, so that the requirement can be met.
Fig. 3 is a schematic diagram of quadrature demodulation fixed-point truncation when the initial phase is pi/2 according to an embodiment of the present application. As shown in fig. 3, when the phase of the local oscillator signal is changed, for example, after the phase is pi/2, the corresponding phase non-precision loss interval and the position on the depth axis are changed. That is, the intervals without precision loss corresponding to different initial phases are different, and if the intervals without precision loss of a plurality of phases are pieced together, the accuracy of the final phase difference can be correspondingly improved, even no error is realized.
Fig. 4 is a schematic diagram of a quadrature demodulation process using multiple initial phases according to an embodiment of the present disclosure. As shown in fig. 4, the m-th ultrasonic echo is quadrature-demodulated at multiple initial phases to obtain multi-channel demodulated data, i.e. the m-th ultrasonic echo is quadrature-demodulated at multiple initial phases
According to the data processing method applied to ultrasonic imaging, after ultrasonic echoes are received, orthogonal demodulation processing is carried out on the same ultrasonic echo through local oscillation signals of various initial phases, and therefore each time of ultrasonic echo can obtain multi-path demodulation data. After all the ultrasonic echoes are processed, the average phase difference of the demodulation data corresponding to each initial phase can be calculated according to the sequence of the ultrasonic echoes. Because the local oscillator signals have different influences on the phase precision due to different initial phases in the fixed-point process, the local oscillator signals with different initial phases are adopted in the orthogonal demodulation process, so that the parts without precision loss of the phases can translate in the depth direction along with the difference of the initial phases, each initial phase can possibly contain different parts without precision loss of the phases, and more or even all depths are covered. And finally, determining a final phase difference according to the obtained plurality of average phase differences, so that the phase difference can weaken and even eliminate quantization errors in the fixed point process.
In the above embodiments, how to obtain the final phase difference by the multiple average phase differences obtained from the multiple initial phases is not limited, and two implementation manners are given in the present application, and it can be understood that other manners besides the following two implementation manners may also be adopted without affecting the implementation of the technical solution of the present application.
In a first mode
On the basis of the above-described embodiment, as a preferred implementation, determining the final phase difference from the average phase difference includes:
acquiring a current fixed-point truncation threshold;
judging whether demodulation data with the absolute value of the real part or the imaginary part smaller than a threshold exists in each demodulation data;
if yes, eliminating the demodulation data meeting the above conditions;
and calculating the average value of the average phase differences corresponding to the rest of the demodulation data as the final phase difference.
In the method for determining the final phase difference provided in this embodiment, first, a part of the average phase differences are screened according to the screened demodulation data, and then the screened average phase differences are averaged to obtain the final phase difference. The method is suitable for demodulating dataAccording to the method, the absolute value of the real part or the imaginary part is smaller than the threshold value, and the calculation amount is reduced to a certain extent. In a specific implementation, the threshold for fixed-point truncation may be 2 16 That is, during the digitization process, the truncated bit width is 16 bits.
Mode two
On the basis of the above-described embodiment, as a preferred implementation, determining the final phase difference from the average phase difference includes:
the average value of all the average phase differences is calculated as the final phase difference.
In this embodiment, all the calculated average phase differences are involved in the calculation of the final phase difference, and this method requires a slightly larger amount of calculation but does not require screening.
In addition to the above embodiments, as a preferred embodiment, before performing the quadrature demodulation processing, the method further includes:
each ultrasonic echo is subjected to beam synthesis processing.
In a specific implementation, after obtaining the ultrasonic echo, the ultrasonic echo may be directly subjected to the quadrature demodulation processing as in the above embodiment, or may be subjected to the beam synthesis processing first and then to the quadrature demodulation processing. The beam forming process has the function of enhancing the signal-to-noise ratio of signals and reducing interference.
In addition to the above embodiments, as a preferred embodiment, the method further includes:
and calculating the displacement and/or the speed corresponding to the position to be detected according to the final phase difference.
In a specific implementation, a plurality of phase angles may be calculated by using the final phase difference, and assuming that the phase angle is a phase angle corresponding to the center frequency of the ultrasonic wave, the displacement corresponding to the phase angle is calculated according to the known propagation speed of the ultrasonic wave, and the displacement and/or the speed of the position to be detected is calculated by using the transmitted cycle time T.
In the above embodiments, the data processing method applied to the ultrasonic imaging is described in detail, and the present application also provides embodiments corresponding to the access device for storing data in the dual-active mode.
Fig. 5 is a structural diagram of a data processing apparatus applied to ultrasonic imaging according to an embodiment of the present application. As shown in fig. 5, the apparatus includes:
the receiving module 10 is configured to receive at least 2 ultrasonic echoes corresponding to a position to be detected;
the processing module 11 is configured to perform quadrature demodulation processing on each ultrasonic echo by using local oscillation signals of multiple initial phases to obtain multiple paths of demodulation data of each ultrasonic echo; wherein, the multiple initial phases adopted by each ultrasonic echo correspond to each other;
a calculating module 12, configured to calculate an average phase difference for demodulation data corresponding to the same initial phase;
and a determining module 13, configured to determine a final phase difference according to the average phase difference.
In a preferred embodiment, the processing module 11 is further configured to perform a beamforming process on each of the ultrasound echoes before performing the quadrature demodulation process.
In a preferred embodiment, the calculating module 12 is further configured to calculate a displacement and/or a velocity corresponding to the position to be detected according to the final phase difference.
Since the embodiment of the apparatus portion and the embodiment of the method portion correspond to each other, please refer to the description of the embodiment of the method portion for the embodiment of the apparatus portion, and details are not repeated here.
The application provides a be applied to ultrasonic imaging's data processing apparatus, after receiving the ultrasonic wave echo, carry out quadrature demodulation processing through the local oscillator signal of multiple initial phase to same ultrasonic wave echo for each ultrasonic wave echo just can obtain multichannel demodulation data. After all the ultrasonic echoes are processed, the average phase difference of the demodulation data corresponding to each initial phase can be calculated according to the sequence of the ultrasonic echoes. Because the local oscillator signals have different influences on the phase precision due to different initial phases in the process of fixed point processing, the local oscillator signals with different initial phases are adopted in the process of orthogonal demodulation processing, so that the parts without precision loss of the phases can translate in the depth direction along with the difference of the initial phases, each initial phase can contain the parts without precision loss of the different phases, and more or even all depths can be covered. And finally, determining the final phase difference according to the obtained plurality of average phase differences, so that the phase difference can weaken or even eliminate the quantization error in the fixed-point process.
In addition, the present application also provides an ultrasound imaging apparatus comprising a memory for storing a computer program;
a processor for implementing the steps of the data processing method applied to ultrasonic imaging as mentioned in the above embodiments when executing the computer program. Fig. 6 is a structural diagram of an ultrasonic imaging apparatus according to an embodiment of the present application, and as shown in fig. 6, the ultrasonic imaging apparatus includes: a memory 20 and a processor 21.
The processor 21 may include one or more processing cores, such as a 4-core processor, an 8-core processor, and the like. The processor 21 may be implemented in at least one hardware form of a DSP (Digital Signal Processing), an FPGA (Field-Programmable Gate Array), and a PLA (Programmable Logic Array). The processor 21 may also include a main processor and a coprocessor, where the main processor is a processor for Processing data in an awake state, and is also called a Central Processing Unit (CPU); a coprocessor is a low power processor for processing data in a standby state. In some embodiments, the processor 21 may be integrated with a GPU (Graphics Processing Unit), which is responsible for rendering and drawing the content required to be displayed on the display screen. In some embodiments, the processor 21 may further include an AI (Artificial Intelligence) processor for processing a calculation operation related to machine learning.
The memory 20 may include one or more computer-readable storage media, which may be non-transitory. Memory 20 may also include high speed random access memory, as well as non-volatile memory, such as one or more magnetic disk storage devices, flash memory storage devices. In this embodiment, the memory 20 is at least used for storing a computer program 201, wherein after being loaded and executed by the processor 21, the computer program can implement the relevant steps of the data processing method applied to ultrasound imaging disclosed in any one of the foregoing embodiments. In addition, the resources stored in the memory 20 may also include an operating system 202, data 203, and the like, and the storage manner may be a transient storage manner or a permanent storage manner. Operating system 202 may include, among others, windows, unix, linux, and the like. Data 203 may include, but is not limited to, multiplexed demodulated data, and the like.
In some embodiments, the diagnostic device 20 may further include a display 22, an input/output interface 23, a communication interface 24, a power supply 25, and a communication bus 26.
Those skilled in the art will appreciate that the configuration shown in figure 6 is not limiting to ultrasound imaging devices and may include more or fewer components than those shown.
The ultrasonic imaging device provided by the embodiment of the application comprises a memory and a processor, wherein when the processor executes a program stored in the memory, the following method can be realized: after the ultrasonic echoes are received, orthogonal demodulation processing is carried out on the same ultrasonic echoes through local oscillation signals of various initial phases, so that multi-channel demodulation data can be obtained through each ultrasonic echo. After all the ultrasonic echoes are processed, the average phase difference of the demodulation data corresponding to each initial phase can be calculated according to the sequence of the ultrasonic echoes. Because the local oscillator signals have different influences on the phase precision due to different initial phases in the fixed-point process, the local oscillator signals with different initial phases are adopted in the orthogonal demodulation process, so that the parts without precision loss of the phases can translate in the depth direction along with the difference of the initial phases, each initial phase can possibly contain different parts without precision loss of the phases, and more or even all depths are covered. And finally, determining the final phase difference according to the obtained plurality of average phase differences, so that the phase difference can weaken or even eliminate the quantization error in the fixed-point process.
Finally, the application also provides a corresponding embodiment of the computer readable storage medium. The computer-readable storage medium has stored thereon a computer program which, when being executed by a processor, carries out the steps of the data processing method applied to ultrasound imaging as set forth in the above-mentioned method embodiments.
It is understood that, if the method in the above embodiments is implemented in the form of software functional units and sold or used as a stand-alone product, it can be stored in a computer readable storage medium. Based on such understanding, the technical solutions of the present application may be embodied in the form of a software product, which is stored in a storage medium and executes all or part of the steps of the methods described in the embodiments of the present application, or all or part of the technical solutions. And the aforementioned storage medium includes: various media capable of storing program codes, such as a usb disk, a removable hard disk, a Read-Only Memory (ROM), a Random Access Memory (RAM), a magnetic disk, or an optical disk.
The computer-readable storage medium provided in this embodiment stores a computer program, and when the computer program is executed by a processor, the computer program can implement the following method: after the ultrasonic echoes are received, orthogonal demodulation processing is carried out on the same ultrasonic echoes through local oscillation signals of various initial phases, so that multi-channel demodulation data can be obtained through each ultrasonic echo. After all the ultrasonic echoes are processed, the average phase difference of the demodulation data corresponding to each initial phase can be calculated according to the sequence of the ultrasonic echoes. Because the local oscillator signals have different influences on the phase precision due to different initial phases in the fixed-point process, the local oscillator signals with different initial phases are adopted in the orthogonal demodulation process, so that the parts without precision loss of the phases can translate in the depth direction along with the difference of the initial phases, each initial phase can possibly contain different parts without precision loss of the phases, and more or even all depths are covered. And finally, determining a final phase difference according to the obtained plurality of average phase differences, so that the phase difference can weaken and even eliminate quantization errors in the fixed point process.
The data processing method, apparatus, device and medium applied to ultrasound imaging provided by the present application are described in detail above. The embodiments are described in a progressive manner in the specification, each embodiment focuses on differences from other embodiments, and the same and similar parts among the embodiments are referred to each other. The device disclosed in the embodiment corresponds to the method disclosed in the embodiment, so that the description is simple, and the relevant points can be referred to the description of the method part. It should be noted that, for those skilled in the art, without departing from the principle of the present application, the present application can also make several improvements and modifications, and those improvements and modifications also fall into the protection scope of the claims of the present application.
It is further noted that, in the present specification, relational terms such as first and second, and the like are used solely to distinguish one entity or action from another entity or action without necessarily requiring or implying any actual such relationship or order between such entities or actions. Also, the terms "comprises," "comprising," or any other variation thereof, are intended to cover a non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements does not include only those elements but may include other elements not expressly listed or inherent to such process, method, article, or apparatus. Without further limitation, an element defined by the phrases "comprising a," "8230," "8230," or "comprising" does not exclude the presence of additional like elements in a process, method, article, or apparatus that comprises the element.
Claims (9)
1. A data processing method for ultrasound imaging, comprising:
receiving at least 2 ultrasonic echoes corresponding to the position to be detected;
performing quadrature demodulation processing on each ultrasonic echo by using local oscillation signals of multiple initial phases to obtain multi-channel demodulation data of each ultrasonic echo; wherein the plurality of initial phases adopted by the ultrasonic echoes are consistent;
calculating an average phase difference of the demodulation data corresponding to the same initial phase;
determining the final phase difference of the demodulated data according to the average phase difference corresponding to each initial phase;
the calculating an average phase difference for the demodulated data corresponding to the same initial phase comprises:
filtering the multiple paths of the demodulation data through a plurality of wall filters;
carrying out complex autocorrelation on the demodulated data after filtering processing to obtain a plurality of phases;
calculating an average phase difference corresponding to a plurality of phases; the filtering frequency of the wall filter is set according to the detection requirement.
2. The data processing method of claim 1, wherein determining a final phase difference from the average phase difference comprises:
acquiring a threshold value of the current fixed-point truncation;
judging whether demodulation data with the absolute value of a real part or an imaginary part smaller than the threshold exists in each demodulation data;
if yes, eliminating the demodulation data meeting the above conditions;
and calculating the average value of the average phase differences corresponding to the rest of the demodulation data as the final phase difference.
3. The data processing method of claim 1, wherein determining a final phase difference from the average phase difference comprises:
calculating an average value of all the average phase differences as the final phase difference.
4. The data processing method according to claim 1, further comprising, before performing the quadrature demodulation processing:
and performing beam synthesis processing on each ultrasonic echo.
5. The data processing method of claim 1, further comprising:
and calculating the displacement and/or the speed corresponding to the position to be detected according to the final phase difference.
6. The data processing method according to any one of claims 1 to 5, wherein the plurality of initial phases are uniformly distributed within 360 °.
7. A data processing apparatus for ultrasound imaging, comprising:
the receiving module is used for receiving at least 2 ultrasonic echoes corresponding to the position to be detected;
the processing module is used for performing orthogonal demodulation processing on each ultrasonic echo by using local oscillation signals of multiple initial phases to obtain multi-channel demodulation data of each ultrasonic echo; the multiple initial phases adopted by the ultrasonic echoes correspond to each other;
the calculation module is used for calculating an average phase difference of the demodulation data corresponding to the same initial phase;
the determining module is used for determining the final phase difference according to the average phase difference;
calculating an average phase difference of the demodulated data corresponding to the same initial phase, including filtering the multi-path demodulated data by a plurality of wall filters; carrying out complex autocorrelation on the demodulated data after filtering processing to obtain a plurality of phases; calculating an average phase difference corresponding to a plurality of phases; the filtering frequency of the wall filter is set according to the detection requirement.
8. An ultrasound imaging apparatus comprising a memory for storing a computer program;
a processor for implementing the steps of the data processing method for ultrasound imaging as claimed in any one of claims 1 to 6 when executing the computer program.
9. A computer-readable storage medium, characterized in that a computer program is stored on the computer-readable storage medium, which computer program, when being executed by a processor, carries out the steps of the data processing method for ultrasound imaging as claimed in any one of claims 1 to 6.
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| JP4567842B2 (en) * | 2000-04-10 | 2010-10-20 | 株式会社東芝 | Ultrasonic diagnostic equipment |
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| JP2003033352A (en) * | 2001-07-23 | 2003-02-04 | Matsushita Electric Ind Co Ltd | Signal-processing method for ultrasonic somatometry equipment |
| JP2009200807A (en) * | 2008-02-21 | 2009-09-03 | Nec Corp | Signal generating apparatus and method |
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