CN111388011A - Ultrasonic Doppler blood flow imaging method, device, equipment and readable storage medium - Google Patents
Ultrasonic Doppler blood flow imaging method, device, equipment and readable storage mediumDownload PDFInfo
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Abstract
Description
Technical Field
The present application relates to the field of ultrasound imaging technologies, and in particular, to an ultrasound doppler blood flow imaging method, apparatus, device, and readable storage medium.
Background
One function that is important in current medical ultrasound imaging devices/systems is ultrasound doppler flow imaging. The ultrasonic Doppler blood flow imaging can observe the blood flow distribution and the blood flow dynamic distribution condition of the tested tissue or organ in real time, thereby providing important basis for the differentiation and diagnosis of tissue physiological and pathological states for doctors.
In particular, ultrasonic doppler blood flow imaging can provide the velocity and direction of blood flow in any specific two-dimensional slice or any one sampling position or sampling volume in three-dimensional volume data in real time. It should be noted that, at present, the blood flow velocity and direction for any one sampling location or sampling volume is actually the average blood flow velocity and average direction at that sampling location or within that sampling volume over that data acquisition time period. However, in practice the speed and direction of blood flow at different locations within the sampling volume, and during the data acquisition time period, will vary. For example, in the heart, blood flow velocity and blood flow findings within the blood vessel change due to the beating of the heart.
In fact, in the ultrasonic echo signal, a tissue signal corresponding to the tissue information and a blood flow signal corresponding to the blood flow information are included, and in the conventional blood flow imaging process, there is a very critical wall filter (or called wall filtering algorithm) for filtering the tissue signal and retaining the blood flow signal. Conventional wall filters are generally real filters (hereinafter simply referred to as real wall filters), such as IIR high-pass filters. Current real wall filters do not filter tissue signals and preserve blood flow signals well.
In summary, how to effectively solve the problems of effectively filtering tissue signals in echo signals and retaining blood flow signals in ultrasonic doppler blood flow imaging is a technical problem that needs to be solved urgently by those skilled in the art at present.
Disclosure of Invention
The present application provides an ultrasound doppler blood flow imaging method, an ultrasound doppler blood flow imaging device, an ultrasound doppler blood flow imaging apparatus, and a readable storage medium, so as to effectively filter tissue signals through a complex wall filter, retain blood flow signals, and perform more accurate blood flow imaging processing based on the blood flow signals.
In order to solve the technical problem, the application provides the following technical scheme:
an ultrasonic doppler flow imaging method comprising:
acquiring an orthogonal analytic signal to be subjected to ultrasonic Doppler blood flow imaging; the orthogonal analytic signals comprise tissue signals and blood flow signals;
performing low-pass filtering on the orthogonal analysis signal to obtain the tissue signal, and calculating the corresponding spectrum distribution information of the tissue signal;
generating a complex wall filter by using the frequency spectrum distribution information, and filtering the orthogonal analysis signal by using the complex wall filter to obtain the blood flow signal;
and carrying out ultrasonic Doppler blood flow imaging processing on the blood flow signal.
Preferably, generating a complex wall filter using the spectral distribution information includes:
determining a filtering parameter by using the frequency spectrum distribution information;
generating the complex wall filter corresponding to the filtering parameters.
Preferably, the spectral distribution information comprises an average phase difference of the tissue signals; determining a filtering parameter using the spectral distribution information, comprising:
and determining the strongest attenuation frequency point of the complex number wall filter by utilizing the average phase difference so as to move the strongest attenuation frequency point of the real number wall filter to the central frequency of the tissue signal to obtain the complex number wall filter.
Preferably, the spectral distribution information includes high and low frequency energy distributions of the tissue signal and a bandwidth of the tissue signal, and the determining the filtering parameter by using the spectral distribution information includes:
determining the highest point of energy in the tissue signal by using the high-low frequency energy distribution;
centering on the energy maxima and determining a cutoff frequency of the complex wall filter based on the bandwidth.
Preferably, the acquiring an orthogonal analytic signal to be subjected to ultrasonic doppler blood flow imaging includes:
transmitting ultrasonic waves in a sampling volume and collecting echoes corresponding to the ultrasonic waves;
and demodulating the echo to obtain the orthogonal analytic signal.
Preferably, demodulating the echo to obtain the quadrature analytic signal includes:
and performing beam synthesis processing on the echo, and performing demodulation processing on a synthesis result to obtain the orthogonal analysis signal.
Preferably, the ultrasonic doppler blood flow imaging processing is performed on the blood flow signal, and includes:
performing complex autocorrelation calculation on the blood flow signal, and calculating a phase angle for a result of the complex autocorrelation; the phase angle is the phase difference of adjacent sampling interval data after filtering by using the complex wall filter, and the phase angle can reflect the size and the direction of Doppler frequency shift caused by blood flow movement;
calculating the velocity value and the velocity direction of the blood flow movement by using the phase angle, the ultrasonic wave propagation velocity and the ultrasonic wave frequency;
and carrying out ultrasonic Doppler blood flow imaging by using the speed value and the speed direction.
An ultrasonic doppler flow imaging apparatus comprising:
the orthogonal analysis signal acquisition module is used for acquiring an orthogonal analysis signal to be subjected to ultrasonic Doppler blood flow imaging; the orthogonal analytic signals comprise tissue signals and blood flow signals;
the frequency spectrum distribution information acquisition module is used for carrying out low-pass filtering on the orthogonal analysis signal to obtain the tissue signal and calculating frequency spectrum distribution information corresponding to the tissue signal;
a blood flow signal acquisition module, configured to generate a complex wall filter using the spectrum distribution information, and filter the orthogonal analysis signal using the complex wall filter to obtain the blood flow signal; the complex number wall filter is a wall filter which expands an imaginary number on the basis of a real number wall filter;
and the blood flow imaging module is used for carrying out ultrasonic Doppler blood flow imaging processing on the blood flow signals.
An ultrasonic doppler blood flow imaging device comprising:
an ultrasonic transmitter for transmitting ultrasonic waves within the deployment volume;
the ultrasonic receiver is used for receiving the echo corresponding to the ultrasonic wave;
a memory for storing a computer program;
a processor for implementing the steps of the above-mentioned ultrasound doppler blood flow imaging method when executing the computer program.
An ultrasonic doppler blood flow imaging device comprising:
a memory for storing a computer program;
a processor for implementing the steps of the above-mentioned ultrasound doppler blood flow imaging method when executing the computer program.
A readable storage medium having stored thereon a computer program which, when being executed by a processor, carries out the steps of the above-mentioned ultrasound doppler blood flow imaging method.
By applying the method provided by the embodiment of the application, the orthogonal analytic signal to be subjected to the ultrasonic Doppler blood flow imaging is obtained; the orthogonal analysis signals comprise tissue signals and blood flow signals; carrying out low-pass filtering on the orthogonal analysis signal to obtain an organization signal, and calculating corresponding spectrum distribution information of the organization signal; generating a plurality of wall filters by using the frequency spectrum distribution information, and filtering the orthogonal analysis signal by using the plurality of wall filters to obtain a blood flow signal; and carrying out ultrasonic Doppler blood flow imaging processing on the blood flow signals.
It has been found that the amplitude-frequency response of a real wall filter is symmetric about 0Hz in both positive and negative frequencies. However, the positive and negative frequency components of the actual tissue signal and blood flow signal are not symmetric about 0Hz, so the real number wall filter cannot well filter the tissue signal and retain the blood flow signal. In addition, under different hemodynamic scenes, the distribution ratio of positive and negative frequency components of the tissue signal and the blood flow signal is different, so in order to filter the tissue signal to the maximum extent and retain the blood flow signal, the scheme provides that according to the positive and negative frequency distribution of the tissue signal and the blood flow signal, the orthogonal analysis signal to be subjected to blood flow imaging is processed by a complex wall filter capable of adaptively adjusting a filter stop band and a filter pass band, so that a more accurate blood flow signal is obtained, and the blood flow imaging is more in line with the actual situation. Specifically, after orthogonal analysis signals including tissue signals and blood flow signals are acquired; the orthogonal analysis signal can be subjected to low-pass filtering to obtain an organization signal, and spectrum distribution information corresponding to the organization signal is calculated; generating a complex wall filter based on the frequency spectrum distribution information, and finally filtering the orthogonal analytic signal by using the complex wall filter to obtain a blood flow signal; the blood flow signal is subjected to ultrasonic Doppler blood flow imaging processing, so that a more accurate imaging result, namely more accurate blood flow speed and blood flow direction can be obtained.
Accordingly, the embodiment of the present application further provides an ultrasound doppler blood flow imaging device, an apparatus and a readable storage medium corresponding to the ultrasound doppler blood flow imaging method, which have the above technical effects and are not described herein again.
Drawings
In order to more clearly illustrate the embodiments of the present application or the technical solutions in the prior art, the drawings used in the description of the embodiments or the prior art will be briefly described below, it is obvious that the drawings in the following description are only some embodiments of the present application, and for those skilled in the art, other drawings can be obtained according to the drawings without creative efforts.
Fig. 1 is a flowchart of an implementation of an ultrasonic doppler blood flow imaging method in an embodiment of the present application;
FIG. 2 is a schematic diagram of the amplitude-frequency response of a real wall filter;
FIG. 3 is a schematic diagram of an orthogonal analytic signal;
FIG. 4 is a schematic diagram of a conventional ultrasonic Doppler blood flow detection process;
fig. 5 is a schematic diagram of a frequency distribution of an IQ signal after frequency down-shifting (DwnMix);
FIG. 6 is a flowchart illustrating an embodiment of a method for ultrasonic Doppler blood flow imaging according to the present disclosure;
fig. 7 is a schematic diagram of the filtering effect of a real wall filter further optimized in the present application;
FIG. 8 is a schematic structural diagram of an ultrasonic Doppler blood flow imaging apparatus according to an embodiment of the present application;
FIG. 9 is a schematic structural diagram of an ultrasonic Doppler blood flow imaging apparatus according to an embodiment of the present application;
fig. 10 is a schematic structural diagram of an ultrasound doppler blood flow imaging apparatus in an embodiment of the present application.
Detailed Description
The core of the application is to provide an ultrasonic Doppler blood flow imaging method, so that the blood flow imaging result is more accurate by effectively filtering tissue signals and retaining blood flow signals. Another core of the present application is to provide an ultrasound doppler blood flow imaging apparatus, device and readable storage medium corresponding to the ultrasound doppler blood flow imaging method, which also have the technical effects of the ultrasound doppler blood flow imaging method.
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. It is to be understood that the embodiments described are only a few embodiments of the present application and not all embodiments. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present application.
Referring to fig. 1, fig. 1 is a flowchart illustrating an ultrasonic doppler blood flow imaging method according to an embodiment of the present application, the method including the following steps:
s101, obtaining an orthogonal analysis signal to be subjected to ultrasonic Doppler blood flow imaging.
Wherein the orthogonal analytic signals comprise tissue signals and blood flow signals.
The orthogonal analysis signal is a signal obtained by analyzing a detected echo after transmitting ultrasonic waves to the part to be detected, and because the ultrasonic waves can generate echoes when meeting tissues and organs, the orthogonal analysis signal has a tissue signal and a blood flow signal.
Specifically, the process of acquiring the orthogonal analytic signal may include:
step one, transmitting ultrasonic waves in a sampling volume and collecting echo waves corresponding to the ultrasonic waves;
and step two, demodulating the echo to obtain an orthogonal analytic signal.
For convenience of description, the above two steps will be described in combination.
The sampling volume can be replaced by a sampling position, namely, ultrasonic waves can be emitted at the sampling position or in the sampling volume, and then echoes corresponding to the ultrasonic waves are collected. Specifically, the ultrasound wave may be transmitted more than Ens times (Ens > ═ 2) in a fixed repetition period T, and the echo generated by each transmission of the ultrasound wave may be detected and collected correspondingly.
After the echoes are obtained, the echoes can be analyzed to obtain quadrature analytic signals.
Specifically, the specific implementation of demodulating the echo may include, but is not limited to, the following two ways:
mode 1: and performing beam synthesis processing on the echo, and performing demodulation processing on a synthesis result to obtain an orthogonal analysis signal.
Mode 2: and directly demodulating the echo to obtain an orthogonal analytic signal.
That is, the process of demodulating the echoes obtained by the multiple transmission and reception to obtain the orthogonal analytic signal may include an advanced beam synthesis process, and then performing a demodulation process to obtain a demodulated orthogonal analytic signal (for convenience of description, hereinafter, referred to as an IQ signal); or directly demodulating the echo to obtain an IQ signal. Thus, the Ens number of temporal IQ sequences (i.e., IQ signals) are obtained at each sampling volume or sampling position.
S102, low-pass filtering is carried out on the orthogonal analysis signal to obtain a tissue signal, and spectrum distribution information corresponding to the tissue signal is calculated.
After obtaining an orthogonal analysis signal, i.e. an IQ signal, the IQ signal is subjected to a shunt processing, one path is used for performing low-pass filtering on the IQ signal, and the filtered signal is an organization signal. When the IQ signals are low-pass filtered, the filtering parameters of the low-pass filter can be set according to the current adopted position or the tissue characteristics corresponding to the sampling volume, so as to obtain more complete tissue signals.
After the tissue signal is obtained, the spectrum distribution information corresponding to the tissue signal can be calculated. Specifically, calculating the spectrum distribution information corresponding to the tissue signal may specifically include processing the tissue signal to obtain the spectrum distribution information; the spectral distribution information includes an average phase difference of the tissue signal, a high and low frequency energy distribution of the tissue signal, and a bandwidth of the tissue signal. That is, after obtaining the tissue signal, parameter calculations may be performed, such as including average phase difference, bandwidth, and frequency profile, etc. To obtain information on the spectral distribution of the tissue signal. For example, the average phase difference of the tissue signal (which may be denoted as ang1) may be obtained by performing a complex cross-correlation calculation on the IQ signal.
S103, generating a complex wall filter by using the frequency spectrum distribution information, and filtering the orthogonal analysis signal by using the complex wall filter to obtain a blood flow signal.
The complex number wall filter is a wall filter with an imaginary number expanded on the basis of a real number wall filter.
Due to the complex filter, the amplitude-frequency response is not limited to be symmetric about 0Hz at positive and negative frequencies, while the amplitude-frequency response of the real filter is limited to be symmetric about 0Hz at positive and negative frequencies as shown in fig. 2. The distribution of the IQ signals is shown in fig. 3, and it can be seen that the tissue signal and the blood flow signal are not symmetrical about 0Hz in positive and negative frequencies. Based on this, the complex number wall filter is generated in the present application, and the existing real number wall filter is replaced, so as to perform better filtering processing.
Specifically, in order to achieve better filtering processing, in the present application, a complex wall filter is generated based on spectral distribution information corresponding to a tissue signal obtained by filtering. Then, the other path of IQ signal is filtered by a complex wall filter, so as to obtain a blood flow signal without tissue signal.
The generating process of the complex wall filter may specifically include:
step one, determining a filtering parameter by using frequency spectrum distribution information;
and step two, generating a complex wall filter corresponding to the filtering parameters.
For convenience of description, the above two steps will be described in combination.
After obtaining the spectral distribution information of the tissue signal, determining the filtering parameters of the complex wall filter to be generated based on the spectral distribution information, so that the complex wall filter generated based on the filtering parameters can filter the tissue signal to the maximum extent and retain the blood flow signal.
The following describes specific implementations of determining the filtering parameters of the complex wall filter by taking several specific spectrum distribution information as examples:
in a first mode
The strongest attenuation frequency point of the complex wall filter is set by the average phase difference. The strongest attenuation frequency point of the complex number wall filter can be determined by utilizing the average phase difference so as to move the strongest attenuation frequency point of the real number wall filter to the central frequency of the tissue signal to obtain the complex number wall filter. For convenience of explanation, the following describes in detail the strongest attenuation frequency point of the complex number wall filter set by averaging the phase difference, with reference to the filtering processing mode of the existing real number wall filter:
assuming that a real wall filter in conventional doppler blood flow imaging is represented by Kmat, and a adaptively generated complex wall filter in the present application is represented by Kmat cmplx, the strongest attenuation frequency point of the complex wall filter is set by averaging the phase difference, and the following formula can be specifically referred to:
Mix(i)＝ej((i-1)×ang1)i∈[0,L-1]
KmatCmplx＝Kmat(i)×Mix(i) i∈[0,L-1]
in the above formula, ang1 is the average phase difference of the tissue, L represents the number of times of calculating the transmitted and received ultrasonic echoes to realize the doppler shift detection, and j is an imaginary identifier in a mathematical complex number.
The main purpose here is to adaptively adjust the strongest attenuation frequency point of the wall filter according to the central frequency of the tissue signal in the IQ signal, and since the strongest attenuation frequency point of the real number wall filter is always 0Hz, the strongest attenuation frequency point of the wall filter is moved to the central frequency of the tissue signal in the application, so that the tissue signal can be suppressed most strongly.
With reference to fig. 3, 4 and 5, fig. 4 is a schematic flow chart of a conventional ultrasonic doppler blood flow detection process; fig. 5 is a schematic diagram of a frequency distribution of an IQ signal after frequency down-shifting (DwnMix); for the IQ sequence in time, the IQ sequence is processed in two paths. The first path firstly carries out low-pass filtering to filter blood flow signals, and then calculates autocorrelation to obtain the average phase difference ang1 of tissue signals acquired twice in the IQ signals. Inverting the average phase difference of the tissue signal; and performing a frequency down shift (DwnMix) operation on the second path of IQ data to obtain a new data sequence, which is abbreviated as DmIQ herein. The down-shift (DwnMix) is to shift all frequency components of the signal, and is to shift the center frequency of the tissue signal in the signal from a position other than 0Hz to a position 0Hz, so that the real-number wall filter can better suppress the tissue signal (because the attenuation rate of the conventional real-number wall filter is the maximum at 0 Hz).
DwnM(i)＝e-j((i-1)×ang1)i∈[0,Ens-1]
DmIQ＝IQ(i)×DwnM(i) i∈[0,Ens-1]
In the above formula, ang1 is the average phase difference of the tissue, Ens represents the number of times of calculating the transmission and reception of the ultrasonic echo for realizing the doppler shift detection, j is an imaginary identifier in a mathematical complex number, and IQ represents an analytic signal sequence including a tissue signal and a blood flow signal.
For DmIQ, a real number wall filtering process is performed to obtain wall-filtered data, which is referred to as WfDmIQ. For the WfDmIQ data, an up-shift (UpMix) is performed using the tissue average phase difference ang1 to obtain new IQ data, which is referred to as WfIQ data. The up-shift is referred to as the down-shift, and since the entire signal frequency is shifted to better filter the tissue signal by real wall filtering, in order to recover the true frequency of the signal, the down-shifted, wall-filtered signal must be shifted in equal and opposite signs to recover the true frequency of all signals:
UpM(i)＝ej((i-1)×ang1)i∈[0,Ens-1]
WfIQ＝WfDmIQ(i)×UpM(i) i∈[0,Ens-1]
finally, complex autocorrelation calculation is carried out on the WfIQ data, a phase angle is calculated on the result of the complex autocorrelation, the phase angle is called ang2, and then the ang2, the ultrasonic wave propagation speed and the ultrasonic wave frequency are used for calculating the movement speed of the blood flow.
Obviously, in the prior art, the following two disadvantages exist in the way of performing a down-shift, a wall-filtering, and then an up-shift on the signal:
disadvantage 1: the current method needs to perform up-shift frequency on IQ signals, then perform real number wall filtering, then perform down-shift frequency, then use complex autocorrelation to further calculate phase difference, and then calculate to obtain blood flow velocity. The whole process is complex, and errors are easy to occur when concrete engineering is realized.
And (2) disadvantage: real wall filtering is used, and the amplitude-frequency response of real wall filtering is still left-right symmetric (as shown in fig. 2). Even if the average frequency of the tissue signal is shifted down to 0Hz after the frequency shift is performed, it is obvious from fig. 5 that although the average frequency is at 0Hz, the distribution of the positive and negative frequency portions is obviously inconsistent. Therefore, at this time, the tissue signal is filtered out by using the conventional real-number wall filtering (as shown in fig. 2) formed by stacking amplitude-frequency curves, so that the tissue signal is difficult to be filtered out.
Mode two
In the embodiment of the present application, as shown in fig. 6, in the specific processing flow, the filtering parameters of the complex wall filter can be adaptively determined according to not only the center frequency of the tissue signal, but also the energy distribution of high and low frequencies of the tissue signal and the bandwidth of the tissue signal. The specific filtering parameter determining process comprises the following steps:
determining the highest point of energy in a tissue signal by utilizing high-frequency and low-frequency energy distribution;
and step two, taking the highest point of energy as a center, and determining the cutoff frequency of the complex wall filter based on the bandwidth.
For example, the following steps are carried out: the fourier transform can be used to calculate the frequency point position of-6 dB (or use other values, such as-5 dB; or directly use the bandwidth of the tissue signal) up and down with the point with the highest energy in the tissue signal frequency as the center, to adjust and determine the cut-off frequency of the wall filter, and of course, the filter parameters such as the bandwidth, the pass band and the stop band can be set, so as to obtain the further optimized real wall filter shown in fig. 7.
In the present application, the generated complex wall filter is used to perform wall filter filtering on the IQ signal to obtain an IQ signal after wall filtering, i.e., a blood flow signal, which is referred to as WfIQ in the present application.
And S104, carrying out ultrasonic Doppler blood flow imaging processing on the blood flow signals.
In the application, after a more accurate blood flow signal is obtained, ultrasonic doppler blood flow imaging processing can be performed on the blood flow signal. The specific blood flow imaging processing process comprises the following steps:
step one, performing complex autocorrelation calculation on blood flow signals, and calculating a phase angle of a result of the complex autocorrelation; the phase angle is the phase difference of adjacent sampling interval data after filtering by using a complex wall filter, and can reflect the size and the direction of Doppler frequency shift caused by blood flow movement;
calculating a speed value and a speed direction of the blood flow movement by utilizing the phase angle, the ultrasonic wave propagation speed and the ultrasonic wave frequency;
and step three, performing ultrasonic Doppler blood flow imaging by using the speed value and the speed direction.
For convenience of description, the above three steps will be described in combination.
For WfIQ, complex autocorrelation calculation is performed, and a phase angle is calculated for the result of the complex autocorrelation, referred to herein as ang2, and then the velocity direction and velocity value of blood flow movement, i.e., the blood flow velocity in vector form, are calculated using ang2, the ultrasound propagation velocity and the ultrasound frequency. It should be noted that the phase angle here refers to the phase difference of the data of adjacent sampling intervals after wall filtering, which directly reflects the magnitude and direction of the doppler shift caused by blood flow movement.
By applying the method provided by the embodiment of the application, the orthogonal analytic signal to be subjected to the ultrasonic Doppler blood flow imaging is obtained; the orthogonal analysis signals comprise tissue signals and blood flow signals; carrying out low-pass filtering on the orthogonal analysis signal to obtain an organization signal, and calculating corresponding spectrum distribution information of the organization signal; generating a plurality of wall filters by using the frequency spectrum distribution information, and filtering the orthogonal analysis signal by using the plurality of wall filters to obtain a blood flow signal; and carrying out ultrasonic Doppler blood flow imaging processing on the blood flow signals.
It has been found that the amplitude-frequency response of a real wall filter is symmetric about 0Hz in both positive and negative frequencies. However, the positive and negative frequency components of the actual tissue signal and blood flow signal are not symmetric about 0Hz, so the real number wall filter cannot well filter the tissue signal and retain the blood flow signal. In addition, under different hemodynamic scenes, the distribution ratio of positive and negative frequency components of the tissue signal and the blood flow signal is different, so in order to filter the tissue signal to the maximum extent and retain the blood flow signal, the method proposes that according to the positive and negative frequency distribution of the tissue signal and the blood flow signal, a complex wall filter capable of adaptively adjusting a filter stop band and a filter pass band is used for processing an orthogonal analytic signal to be subjected to blood flow imaging so as to obtain a more accurate blood flow signal, so that the blood flow imaging is more in line with the actual situation. Specifically, after orthogonal analysis signals including tissue signals and blood flow signals are acquired; the orthogonal analysis signal can be subjected to low-pass filtering to obtain an organization signal, and spectrum distribution information corresponding to the organization signal is calculated; generating a complex wall filter based on the frequency spectrum distribution information, and finally filtering the orthogonal analytic signal by using the complex wall filter to obtain a blood flow signal; the blood flow signal is subjected to ultrasonic Doppler blood flow imaging processing, so that a more accurate imaging result, namely more accurate blood flow speed and blood flow direction can be obtained.
Corresponding to the above method embodiments, the present application further provides an ultrasonic doppler blood flow imaging apparatus, and the ultrasonic doppler blood flow imaging apparatus described below and the ultrasonic doppler blood flow imaging method described above may be referred to correspondingly.
Referring to fig. 8, the apparatus includes the following modules:
an orthogonal analysissignal acquisition module 101, configured to acquire an orthogonal analysis signal to be subjected to ultrasonic doppler blood flow imaging; the orthogonal analysis signals comprise tissue signals and blood flow signals;
the frequency spectrum distributioninformation acquisition module 102 is configured to perform low-pass filtering on the orthogonal analysis signal to obtain an organization signal, and calculate frequency spectrum distribution information corresponding to the organization signal;
a blood flowsignal obtaining module 103, configured to generate a complex wall filter by using the spectrum distribution information, and filter the orthogonal analysis signal by using the complex wall filter to obtain a blood flow signal; the complex number wall filter is a wall filter which expands imaginary numbers on the basis of a real number wall filter;
and the bloodflow imaging module 104 is used for performing ultrasonic doppler blood flow imaging processing on the blood flow signals.
By applying the device provided by the embodiment of the application, the orthogonal analytic signal to be subjected to the ultrasonic Doppler blood flow imaging is obtained; the orthogonal analysis signals comprise tissue signals and blood flow signals; carrying out low-pass filtering on the orthogonal analysis signal to obtain an organization signal, and calculating corresponding spectrum distribution information of the organization signal; generating a plurality of wall filters by using the frequency spectrum distribution information, and filtering the orthogonal analysis signal by using the plurality of wall filters to obtain a blood flow signal; the complex number wall filter is a wall filter which expands imaginary numbers on the basis of a real number wall filter; and carrying out ultrasonic Doppler blood flow imaging processing on the blood flow signals.
It has been found that the amplitude-frequency response of a real wall filter is symmetric about 0Hz in both positive and negative frequencies. However, the positive and negative frequency components of the actual tissue signal and blood flow signal are not symmetric about 0Hz, so the real number wall filter cannot well filter the tissue signal and retain the blood flow signal. In addition, under different hemodynamic scenes, the distribution ratio of positive and negative frequency components of the tissue signal and the blood flow signal is different, so in order to filter the tissue signal to the maximum extent and retain the blood flow signal, the method proposes that according to the positive and negative frequency distribution of the tissue signal and the blood flow signal, a complex wall filter capable of adaptively adjusting a filter stop band and a filter pass band is used for processing an orthogonal analytic signal to be subjected to blood flow imaging so as to obtain a more accurate blood flow signal, so that the blood flow imaging is more in line with the actual situation. Specifically, after orthogonal analysis signals including tissue signals and blood flow signals are acquired; the orthogonal analysis signal can be subjected to low-pass filtering to obtain an organization signal, and spectrum distribution information corresponding to the organization signal is calculated; generating a complex wall filter based on the frequency spectrum distribution information, and finally filtering the orthogonal analytic signal by using the complex wall filter to obtain a blood flow signal; the blood flow signal is subjected to ultrasonic Doppler blood flow imaging processing, so that a more accurate imaging result, namely more accurate blood flow speed and blood flow direction can be obtained.
In a specific embodiment of the present application, the blood flowsignal obtaining module 103 is specifically configured to determine a filtering parameter by using the spectrum distribution information; a complex wall filter corresponding to the filter parameters is generated.
In a specific embodiment of the present application, the spectrum distribution information includes an average phase difference of the tissue signal, and the blood flowsignal obtaining module 103 is specifically configured to determine a strongest attenuation frequency point of the complex-wall filter by using the average phase difference, so as to shift the strongest attenuation frequency point of the real-wall filter to a center frequency of the tissue signal, thereby obtaining the complex-wall filter.
In a specific embodiment of the present application, the spectrum distribution information includes high and low frequency energy distributions of the tissue signal and a bandwidth of the tissue signal, and the blood flowsignal obtaining module 103 is specifically configured to determine an energy peak in the tissue signal by using the high and low frequency energy distributions; the cutoff frequency of the complex wall filter is determined based on the bandwidth, centered at the highest point of energy.
In a specific embodiment of the present application, the orthogonal analyticsignal obtaining module 101 is specifically configured to emit an ultrasonic wave in a sampling volume and collect an echo corresponding to the ultrasonic wave; and demodulating the echo to obtain an orthogonal analytic signal.
In an embodiment of the present application, the orthogonal analysissignal obtaining module 101 is specifically configured to perform beamforming processing on the echo, and demodulate the synthesis result to obtain the orthogonal analysis signal.
In an embodiment of the present application, the bloodflow imaging module 104 is specifically configured to perform a complex autocorrelation calculation on the blood flow signal, and calculate a phase angle for a result of the complex autocorrelation; the phase angle is the phase difference of adjacent sampling interval data after filtering by using a complex wall filter, and can reflect the size and the direction of Doppler frequency shift caused by blood flow movement; calculating the velocity value and the velocity direction of the blood flow movement by using the phase angle, the ultrasonic wave propagation velocity and the ultrasonic wave frequency; ultrasonic doppler blood flow imaging is performed using velocity values and velocity directions.
Corresponding to the above method embodiments, the present application further provides an ultrasonic doppler blood flow imaging apparatus, and a piece of ultrasonic doppler blood flow imaging apparatus described below and a piece of ultrasonic doppler blood flow imaging method described above may be referred to correspondingly.
Referring to fig. 9, the ultrasonic doppler blood flow imaging apparatus includes:
anultrasonic transmitter 310 for transmitting ultrasonic waves within the deployment volume;
anultrasonic receiver 320 for receiving an echo corresponding to the ultrasonic wave;
amemory 332 for storing a computer program;
aprocessor 322 for implementing the steps of the ultrasound doppler flow imaging method of the above-described method embodiments when executing a computer program. It should be noted that 310 and 320 may be the same entity.
Specifically, referring to fig. 10, a schematic structural diagram of an ultrasonic doppler blood flow imaging apparatus provided in this embodiment is shown, which may generate relatively large differences due to different configurations or performances, and may include one or moreultrasonic transmitters 310, one or moreultrasonic receivers 320, one or more processors (CPUs) 322 (e.g., one or more processors), and amemory 332.Memory 332 may be, among other things, transient or persistent storage. Still further, thecentral processor 322 may be configured to communicate with thememory 332 to execute a series of instruction operations in thememory 332 on the ultrasound dopplerflow imaging device 301.
The ultrasound dopplerflow imaging device 301 may also include one ormore power supplies 326, one or more wired or wireless network interfaces 350, one or more input-output interfaces 358, and/or one ormore operating systems 341, for example, Windows server, Mac OS XTM, UnixTM, <tttranslation = L "&tttl/t >ttinuxtm, FreeBSDTM, or the like.
The steps in the ultrasonic doppler blood flow imaging method described above may be implemented by the structure of an ultrasonic doppler blood flow imaging apparatus.
Corresponding to the above method embodiments, the present application further provides a readable storage medium, and a readable storage medium described below and an ultrasound doppler blood flow imaging method described above may be correspondingly referred to.
A readable storage medium, on which a computer program is stored which, when being executed by a processor, carries out the steps of the ultrasound doppler flow imaging method of the above-mentioned method embodiment.
The readable storage medium may be a usb disk, a removable hard disk, a Read-Only Memory (ROM), a Random Access Memory (RAM), a magnetic disk or an optical disk, and various other readable storage media capable of storing program codes.
Those of skill would further appreciate that the various illustrative elements and algorithm steps described in connection with the embodiments disclosed herein may be implemented as electronic hardware, computer software, or combinations of both, and that the various illustrative components and steps have been described above generally in terms of their functionality in order to clearly illustrate this interchangeability of hardware and software. Whether such functionality is implemented as hardware or software depends upon the particular application and design constraints imposed on the implementation. Skilled artisans may implement the described functionality in varying ways for each particular application, but such implementation decisions should not be interpreted as causing a departure from the scope of the present application.
Claims (10)
1. An ultrasonic doppler blood flow imaging method, comprising:
acquiring an orthogonal analytic signal to be subjected to ultrasonic Doppler blood flow imaging; the orthogonal analytic signals comprise tissue signals and blood flow signals;
performing low-pass filtering on the orthogonal analysis signal to obtain the tissue signal, and calculating the corresponding spectrum distribution information of the tissue signal;
generating a complex wall filter by using the frequency spectrum distribution information, and filtering the orthogonal analysis signal by using the complex wall filter to obtain the blood flow signal;
and carrying out ultrasonic Doppler blood flow imaging processing on the blood flow signal.
2. The ultrasonic doppler blood flow imaging method of claim 1, wherein generating a complex wall filter using the spectral distribution information comprises:
determining a filtering parameter by using the frequency spectrum distribution information;
generating the complex wall filter corresponding to the filtering parameters.
3. The method of ultrasonic doppler blood flow imaging according to claim 2 wherein said spectral distribution information comprises an average phase difference of said tissue signals; determining a filtering parameter using the spectral distribution information, comprising:
and determining the strongest attenuation frequency point of the complex number wall filter by utilizing the average phase difference so as to move the strongest attenuation frequency point of the real number wall filter to the central frequency of the tissue signal to obtain the complex number wall filter.
4. The method of ultrasonic doppler blood flow imaging according to claim 2, wherein said spectral distribution information includes high and low frequency energy distributions of said tissue signal and a bandwidth of said tissue signal, and using said spectral distribution information to determine filtering parameters comprises:
determining the highest point of energy in the tissue signal by using the high-low frequency energy distribution;
centering on the energy maxima and determining a cutoff frequency of the complex wall filter based on the bandwidth.
5. The method of claim 1, wherein said obtaining quadrature resolved signals to be subjected to ultrasonic doppler flow imaging comprises:
transmitting ultrasonic waves in a sampling volume and collecting echoes corresponding to the ultrasonic waves;
and demodulating the echo to obtain the orthogonal analytic signal.
6. The method of claim 5, wherein demodulating the echo to obtain the quadrature resolved signal comprises:
and performing beam synthesis processing on the echo, and performing demodulation processing on a synthesis result to obtain the orthogonal analysis signal.
7. The ultrasonic doppler flow imaging method of claim 1, wherein performing ultrasonic doppler flow imaging processing on the flow signal comprises:
performing complex autocorrelation calculation on the blood flow signal, and calculating a phase angle for a result of the complex autocorrelation; the phase angle is the phase difference of adjacent sampling interval data after filtering by using the complex wall filter, and the phase angle can reflect the size and the direction of Doppler frequency shift caused by blood flow movement;
calculating the velocity value and the velocity direction of the blood flow movement by using the phase angle, the ultrasonic wave propagation velocity and the ultrasonic wave frequency;
and carrying out ultrasonic Doppler blood flow imaging by using the speed value and the speed direction.
8. An ultrasonic doppler blood flow imaging device, comprising:
the orthogonal analysis signal acquisition module is used for acquiring an orthogonal analysis signal to be subjected to ultrasonic Doppler blood flow imaging; the orthogonal analytic signals comprise tissue signals and blood flow signals;
the frequency spectrum distribution information acquisition module is used for carrying out low-pass filtering on the orthogonal analysis signal to obtain the tissue signal and calculating frequency spectrum distribution information corresponding to the tissue signal;
a blood flow signal acquisition module, configured to generate a complex wall filter using the spectrum distribution information, and filter the orthogonal analysis signal using the complex wall filter to obtain the blood flow signal; the complex number wall filter is a wall filter which expands an imaginary number on the basis of a real number wall filter;
and the blood flow imaging module is used for carrying out ultrasonic Doppler blood flow imaging processing on the blood flow signals.
9. An ultrasonic doppler blood flow imaging device, comprising:
an ultrasonic transmitter for transmitting ultrasonic waves within the deployment volume;
the ultrasonic receiver is used for receiving the echo corresponding to the ultrasonic wave;
a memory for storing a computer program;
a processor for implementing the steps of the ultrasound doppler flow imaging method according to any one of claims 1 to 7 when executing the computer program.
10. A readable storage medium, having stored thereon a computer program which, when being executed by a processor, carries out the steps of the ultrasound doppler flow imaging method according to any one of claims 1 to 7.
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