CN115381488B - Pulse wave conduction velocity imaging method based on ultrasonic ultrafast composite plane wave - Google Patents
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Abstract
The application provides a pulse wave conduction velocity imaging method based on ultrasonic ultrafast composite plane waves, which comprises the following steps: acquiring synthesized demodulation ultrasonic data, and performing reverse blood flow filtering treatment on the synthesized demodulation ultrasonic data to obtain a first treatment ultrasonic signal; obtaining coordinate point axial displacement information of different depths in the first processed ultrasonic signal; receiving an input signal, and performing signal processing on the input signal to obtain a second processed signal image; and compositing the second processing signal image with the axial position information of the coordinate points with different depths to obtain the pulse wave image of the axial velocity-time of the blood vessel wall. The application provides a pulse wave conduction velocity imaging method based on an ultrasonic ultrafast composite plane wave, and aims to solve the problems of choosing and calculating accuracy between the final frame frequency and the image quality of a focusing scanning method.
Description
Technical Field
The application relates to the technical field of imaging, in particular to a pulse wave conduction velocity imaging method based on ultrasonic ultrafast composite plane waves.
Background
Pulse wave velocity (Pulse wave velocity, PWV) is an important factor currently in the clinical assessment of cardiovascular disease severity, which correlates with the degree of arterial blood pressure, arterial wall stiffness, a reliable risk predictor for cardiovascular disease. Most pulse wave velocity measurement methods calculate local pulse waves, and calculate motion waveforms of the same segment of blood vessel wall to obtain a time delay curve so as to obtain pulse wave velocity. Pulse wave imaging (Pulse wave image) is one of the techniques for measuring Pulse wave velocity. Because pulse wave conduction is faster, pulse wave imaging requires higher spatial resolution and temporal resolution. The traditional ultrasonic pulse wave imaging is mostly based on a focusing scanning method, and has the defects that the linear density can restrict the frame frequency of imaging to a certain extent, the low frame frequency can lead to the shortage of time resolution and reduce the correlation between signals so as to lead to errors in the estimation of pulse wave conduction speed, in order to improve the frame frequency of imaging, the quantity of scanned wire harnesses can only be reduced, the quality of ultrasonic images and raw data can be reduced, and meanwhile, the accuracy of the estimation of pulse wave conduction speed is reduced.
Disclosure of Invention
The application aims to provide a pulse wave conduction velocity imaging method based on ultrasonic ultrafast composite plane waves, which aims to solve the problems in the background art.
In order to achieve the above purpose, the present application provides the following technical solutions: a pulse wave conduction velocity imaging method based on ultrasonic ultrafast composite plane waves comprises the following steps:
acquiring synthesized demodulation ultrasonic data, and performing reverse blood flow filtering treatment on the synthesized demodulation ultrasonic data to obtain a first treatment ultrasonic signal;
obtaining coordinate point axial displacement information of different depths in the first processed ultrasonic signal;
receiving an input signal, and performing signal processing on the input signal to obtain a second processed signal image;
and compositing the second processing signal image with the axial position information of the coordinate points with different depths to obtain the pulse wave image of the axial velocity-time of the blood vessel wall.
Further, when inverse blood flow filtering processing is performed on the synthesized demodulated ultrasonic data, filtering processing is performed through an infinite impulse response filter or a finite impulse response filter.
Further, the synthesized demodulated ultrasound data in the time domain is low-pass filtered by a Butterworth filter or a chebyshev type two filter when the infinite impulse response filter is used.
Further, when the axial displacement information of coordinate points with different depths is obtained from the first processed ultrasonic signal, the axial displacement information of each coordinate point with different depths of the whole image is obtained by analyzing the first processed ultrasonic signal from the first frame image in the slow time direction through the displacement between two adjacent frames of signals.
Further, when the displacement between two adjacent frame signals is analyzed in the slow time direction, the axial speed is obtained by analyzing and calculating the current frame and the next frame in the slow time direction according to the following formula:
wherein I represents the demodulated real part signal of the current position point, Q represents the demodulated imaginary part signal of the current position point, m represents the fast-time direction position of the current position point, n represents the current frame in the slow-time direction of the current position point, V 1D The estimated axial velocity value of the current position point is calculated, M represents the maximum coordinate in the fast time direction, N represents the maximum frame number in the slow time direction, and tan represents the tangent function.
Further, when the signal processing is performed on the input signal, the signal processing process includes: and adding a spatial domain window to the input signal for low-pass filtering, eliminating the intensity difference between adjacent areas, and obtaining a blurred low-sampling spatial target area image to obtain a second processing signal image.
Further, compounding the second processed signal image with the coordinate point axial position information of different depths includes:
performing transverse intensity projection on the second processed signal image according to the axial position information of the coordinate points with different depths, and calculating a coordinate curve of the central line of the target blood vessel in the target area;
dividing a coordinate curve of the central line of the target blood vessel in a target area to obtain an upper blood vessel wall area and a lower blood vessel wall area, carrying out peak search in the upper blood vessel wall area to obtain an upper blood vessel wall coordinate curve, and carrying out peak search in the lower blood vessel wall area to obtain a lower blood vessel wall coordinate curve;
and carrying out coordinate extraction in a coordinate point axial displacement map according to the upper blood vessel wall coordinate curve and the lower blood vessel wall coordinate curve to obtain a pulse wave image of blood vessel wall axial speed-time.
Further, the transverse intensity projection comprises: carrying out Gaussian blur of different scales on the second processed signal image to obtain blood vessel images of different blur scales, and carrying out downsampling of different scales on the second processed signal image to obtain blood vessel images of different downsampling scales; after Gaussian blur of different scales and downsampling of different scales are carried out on the second processing signal image to obtain blood vessel images of different blur scales and blood vessel images of different downsampling scales, the blood vessel images of different blur scales are used as type A images, the blood vessel images of different downsampling scales are used as type B images, intensity superposition processing is carried out on the type A images and the type B images in the horizontal direction of the images, and transverse intensity projection curves of the type A images and the type B images under different scales are obtained.
Further, the calculating the coordinate curve of the center line of the target blood vessel in the target area includes: and in the transverse intensity projection curves of the type A image and the type B image under different scales, searching and finding out the first two maximum coordinates by peak value searching aiming at the transverse intensity projection curves of the type A image and the type B image under each scale, determining an intermediate value coordinate according to the first two maximum coordinates, taking the intermediate value coordinate as the blood vessel center position of the current scale image, repeating for a plurality of times until each scale obtains the corresponding blood vessel center position of the current scale image, and determining the target blood vessel center line coordinate according to the blood vessel center position of the current scale image.
Further, determining the target vessel centerline coordinates from the vessel centerline position of the current scale image includes: counting the blood vessel center position of the current scale image, analyzing and determining singular values in the blood vessel center position of the current scale image, removing the singular values, and then carrying out average value acquisition on the rest data, wherein the average value is used as a target blood vessel center line coordinate.
Additional features and advantages of the application will be set forth in the description which follows, and in part will be obvious from the description, or may be learned by practice of the application. The objectives and other advantages of the application will be realized and attained by the structure particularly pointed out in the written description and claims thereof as well as the appended drawings.
The technical scheme of the application is further described in detail through the drawings and the embodiments.
Drawings
The accompanying drawings are included to provide a further understanding of the application and are incorporated in and constitute a part of this specification, illustrate the application and together with the embodiments of the application, serve to explain the application. In the drawings:
FIG. 1 is a schematic diagram of the steps of a pulse wave velocity imaging method based on an ultrasonic ultrafast composite plane wave according to the present application;
FIG. 2 is a schematic diagram of a flow chart of obtaining demodulated ultrasonic data in a pulse wave velocity imaging method based on ultrasonic ultrafast composite plane waves according to the present application;
FIG. 3 is a diagram illustrating a fourth exemplary step in an ultrasonic ultrafast composite plane wave based pulse velocity imaging method according to the present application;
fig. 4 is a diagram illustrating a result in a pulse wave velocity imaging method based on an ultrasonic ultrafast composite plane wave according to the present application.
Detailed Description
The preferred embodiments of the present application will be described below with reference to the accompanying drawings, it being understood that the preferred embodiments described herein are for illustration and explanation of the present application only, and are not intended to limit the present application.
As shown in fig. 1, an embodiment of the present application provides a pulse wave velocity imaging method based on an ultrasonic ultrafast composite plane wave, including:
step one, obtaining synthesized demodulation ultrasonic data, and carrying out reverse blood flow filtering treatment on the synthesized demodulation ultrasonic data to obtain a first treatment ultrasonic signal;
step two, obtaining axial displacement information of coordinate points with different depths in the first processed ultrasonic signal;
step three, receiving an input signal, and performing signal processing on the input signal to obtain a second processed signal image;
and step four, compounding the second processing signal image with the axial position information of the coordinate points with different depths to obtain pulse wave images of the axial speed-time of the blood vessel wall.
The above technical solution provides a pulse wave velocity imaging method based on ultrasonic ultrafast composite plane waves, when pulse wave velocity imaging is performed, firstly, synthesized demodulated ultrasonic data is obtained, reverse blood flow filtering processing is performed on the synthesized demodulated ultrasonic data, ultrasonic signals with blood flow signals filtered are obtained, and then first processed ultrasonic signals are obtained, wherein when the synthesized demodulated ultrasonic data are obtained, as shown in fig. 2, a pulse wave measuring module is started, plane wave signals are collected, and signal processing and synthesis are performed on the plane wave signals to obtain demodulated ultrasonic data; then, in the first processing ultrasonic signals, calculating the ultrasonic signals with blood flow signals filtered from a first frame image in a slow time direction through displacement between two adjacent frames of signals, mapping pulse waves, calculating the relevant positions of the blood vessel walls, extracting full direction expansion signals, obtaining axial displacement information of each coordinate point of the whole image at different depths, obtaining axial displacement information of the coordinate points at different depths, then, when receiving input signals, performing signal processing on the input signals, and obtaining a blurred low-sampling space target area image, and obtaining a second processing signal image; and then, compounding the second processing signal image with the axial position information of the coordinate points with different depths, so that the pulse wave velocity imaging is displayed in the gray scale mode image at the same time, and further, the pulse wave image of the axial velocity-time of the blood vessel wall is obtained.
According to the technical scheme, an ultrafast plane wave composite technology in ultrasound is utilized, the frame frequency of more than 2000Hz is achieved, the pulse wave transmission speed at the beginning of the systolic period and the pulse wave transmission speed at the end of the systolic period are calculated in a segmented mode, and the pulse wave images of the axial speed-time of the vascular wall are depicted through the processing part so as to observe displacement curves of different vascular wall positions and time, so that the condition that small-area plaques are not detected is improved.
In one embodiment, the synthesized demodulated ultrasonic data is filtered by an infinite impulse response filter or a finite impulse response filter when being subjected to reverse blood flow filtering.
According to the technical scheme, when inverse blood flow filtering treatment is carried out on the synthesized demodulated ultrasonic data, inverse blood flow filtering treatment can be carried out on the synthesized demodulated ultrasonic data through an infinite impulse response filter (IIR), and inverse blood flow filtering treatment can also be carried out on the synthesized demodulated ultrasonic data through a finite impulse response Filter (FIR).
According to the technical scheme, the inverse blood flow filtering treatment is carried out on the synthesized demodulated ultrasonic data through the infinite impulse response filter or the finite impulse response filter, so that the inverse blood flow filtering treatment is not limited to one filter when the inverse blood flow filtering treatment is carried out on the synthesized demodulated ultrasonic data, the filtering treatment method is enriched, and the infinite impulse response filter or the finite impulse response filter can be selected according to actual conditions to realize the inverse blood flow filtering treatment.
In one embodiment, the synthesized demodulated ultrasonic data is subjected to low-pass filtering in the time domain through a Butterworth filter or a Chebyshev two-type filter when the synthesized demodulated ultrasonic data is subjected to reverse blood flow filtering processing by using the infinite impulse response filter.
According to the technical scheme, when the infinite impulse response filter is used for carrying out reverse blood flow filtering treatment on the synthesized demodulated ultrasonic data, the Butterworth filter is adopted for carrying out low-pass filtering on the demodulated ultrasonic data synthesized in the time domain, or the Chebyshev type two-type filter is adopted for carrying out low-pass filtering on the demodulated ultrasonic data synthesized in the time domain.
According to the technical scheme, the synthesized demodulation ultrasonic data in the time domain can be subjected to low-pass filtering by using the Butterworth filter, so that a frequency response curve in a passband is flattened to the maximum extent and has no fluctuation, the frequency response curve in the passband is gradually reduced to zero in the stopband, and the synthesized demodulation ultrasonic data in the time domain can be subjected to low-pass filtering by using the Chebyshev two-type filter, so that the frequency response amplitude in the stopband is realized.
In one embodiment provided by the application, when the coordinate point axial displacement information of different depths is obtained in the first processed ultrasonic signal, the first processed ultrasonic signal is analyzed from the first frame image in the slow time direction through the displacement between two adjacent frames of signals, so that the coordinate point axial displacement information of the whole image at different depths is obtained.
According to the technical scheme, when the coordinate point axial displacement information of different depths is obtained in the first processed ultrasonic signals, the first processed ultrasonic signals are analyzed and calculated in the slow time direction from the first frame of images through the displacement between two adjacent frames of signals, and the coordinate point axial displacement information of the whole image at different depths is obtained.
According to the technical scheme, the coordinate point axial displacement information of different depths is obtained from the first frame image by the first processing ultrasonic signal, so that comprehensive calculation can be performed from head to tail comprehensively aiming at the first processing ultrasonic signal, the obtained coordinate point axial displacement information of different depths can embody the whole image information, meanwhile, the conversion of the image and the data information is realized, the data information is extracted from the image, and the follow-up data operation and processing are facilitated.
In one embodiment provided by the application, when the displacement between two adjacent frame signals is analyzed in the slow time direction, the axial speed is obtained by analyzing and calculating the current frame and the next frame in the slow time direction according to the following formula:
wherein I represents the demodulated real part signal of the current position point, Q represents the demodulated imaginary part signal of the current position point, m represents the fast-time direction position of the current position point, n represents the current frame in the slow-time direction of the current position point, V 1D The estimated axial velocity value of the current position point is calculated, M represents the maximum coordinate in the fast time direction, N represents the maximum frame number in the slow time direction, and tan represents the tangent function.
According to the technical scheme, when the displacement between two adjacent frame signals is calculated in the slow time direction, the point-point correlation analysis calculation is carried out on the current frame n and the next frame n+1 in the slow time direction through the following formula, so that the axial speed is obtained:
wherein I represents the demodulated real part signal of the current position point, Q represents the demodulated imaginary part signal of the current position point, m represents the position of the current position point in the fast direction, and n represents the position of the current position point in the slow directionFront frame, V 1D The estimated axial velocity value of the current position point is calculated, M represents the maximum coordinate in the fast time direction, N represents the maximum frame number in the slow time direction, and tan represents the tangent function.
According to the technical scheme, the axial speed of each position point can be obtained by carrying out point-point correlation analysis and calculation in the slow time direction, so that the calculation complexity is reduced, the calculated estimated result is lower, the accuracy is reduced to a certain extent, the ultrafast composite plane wave provides a frame frequency of more than 2000Hz per second, the minimum width limit of pulse wave signal acquisition is broken through, and the pulse wave speed can be measured more accurately under the condition of ensuring the signal quality.
In one embodiment of the present application, when performing signal processing on the input signal, the signal processing process includes: and adding a spatial domain window to the input signal for low-pass filtering, eliminating the intensity difference between adjacent areas, and obtaining a blurred low-sampling spatial target area image to obtain a second processing signal image.
The above technical solution includes: and performing low-pass filtering on the input signal by adding a spatial domain window, eliminating intensity difference between adjacent areas, and obtaining a blurred low-sampling spatial target area image to obtain a second processing signal image.
According to the technical scheme, the intensity difference between adjacent areas is eliminated by adding the spatial domain window to the input signal, so that the doping of irrelevant factors in the input signal is reduced, the main characteristics of the input signal are highlighted, and the accuracy of the second processed signal image is improved.
As shown in fig. 3, in one embodiment of the present application, the compounding the second processed signal image with the coordinate point axial position information of different depths includes:
s401, performing transverse intensity projection on the second processing signal image according to the axial position information of the coordinate points with different depths, and calculating a coordinate curve of the central line of the target blood vessel in the target area;
s402, dividing a coordinate curve of the central line of the target blood vessel in a target area to obtain an upper blood vessel wall area and a lower blood vessel wall area, carrying out peak search in the upper blood vessel wall area to obtain an upper blood vessel wall coordinate curve, and carrying out peak search in the lower blood vessel wall area to obtain a lower blood vessel wall coordinate curve;
s403, carrying out coordinate extraction in a coordinate point axial displacement map according to the upper blood vessel wall coordinate curve and the lower blood vessel wall coordinate curve to obtain a pulse wave image of blood vessel wall axial speed-time.
According to the technical scheme, when the second processing signal image is compounded with the axial position information of the coordinate points with different depths, transverse intensity projection is carried out on the second processing signal image in the blurred low-sampling space target area image, and the coordinate curve of the central line of the target blood vessel in the target area is calculated according to the image subjected to the transverse intensity projection, so that the coordinate curve of the central line of the target blood vessel in the target area is obtained; dividing a coordinate curve of a target blood vessel center line in a target region to obtain an upper blood vessel wall region and a lower blood vessel wall region, performing peak search in the upper blood vessel wall region to obtain an upper blood vessel wall coordinate curve, and performing peak search in the lower blood vessel wall region to obtain a lower blood vessel wall coordinate curve; finally, according to the upper vessel wall coordinate curve and the lower vessel wall coordinate curve, carrying out coordinate extraction in a coordinate point axial displacement map to obtain a pulse wave image of the vessel wall axial speed-time, wherein the output result of the pulse wave image of the vessel wall axial speed-time is shown in fig. 4.
In one embodiment provided by the present application, the transverse intensity projection includes: carrying out Gaussian blur of different scales on the second processed signal image to obtain blood vessel images of different blur scales, and carrying out downsampling of different scales on the second processed signal image to obtain blood vessel images of different downsampling scales; after Gaussian blur of different scales and downsampling of different scales are carried out on the second processing signal image to obtain blood vessel images of different blur scales and blood vessel images of different downsampling scales, the blood vessel images of different blur scales are used as type A images, the blood vessel images of different downsampling scales are used as type B images, intensity superposition processing is carried out on the type A images and the type B images in the horizontal direction of the images, and transverse intensity projection curves of the type A images and the type B images under different scales are obtained.
According to the technical scheme, when the transverse intensity projection is carried out on the second processing signal image, two kinds of processing are carried out on the second processing signal image, one kind of processing is carried out on the second processing signal image through Gaussian blur with different scales, so that blood vessel images with different blur scales are obtained; one is to downsample the second processed signal image at a different scale to obtain a vessel image at a different downsampled scale. After Gaussian blur of different scales and downsampling of different scales are carried out on the second processed signal image to obtain blood vessel images of different blur scales and blood vessel images of different downsampling scales, the blood vessel images of different blur scales are used as type A images, the blood vessel images of different downsampling scales are used as type B images, intensity superposition processing is carried out on the type A images and the type B images in the horizontal direction of the images, and transverse intensity projection curves of the type A images and the type B images under different scales are obtained.
According to the technical scheme, the second processing signal image is subjected to transverse intensity projection, so that the second processing signal image projects a plurality of images with different indexes under different scales on the basis of the low-sampling space target area image, the second processing signal image is enriched, the comprehensiveness of the second processing signal image is improved, and the calculated coordinate curve of the center line of the target blood vessel in the target area is more accurate. The blood vessel images with different fuzzy scales are used as the type A image, the blood vessel images with different downsampling scales are used as the type B image, the blood vessel images with different fuzzy scales and the blood vessel images with different downsampling scales are conveniently distinguished, and the carotid PWV measurement needs to be kept horizontal with the probe transmitting direction by carrying out intensity superposition processing on the type A image and the type B image in the image horizontal direction, so that the common habit is met.
In one embodiment of the present application, the calculating the coordinate curve of the center line of the target blood vessel in the target area includes: and in the transverse intensity projection curves of the type A image and the type B image under different scales, searching and finding out the first two maximum coordinates by peak value searching aiming at the transverse intensity projection curves of the type A image and the type B image under each scale, determining an intermediate value coordinate according to the first two maximum coordinates, taking the intermediate value coordinate as the blood vessel center position of the current scale image, repeating for a plurality of times until each scale obtains the corresponding blood vessel center position of the current scale image, and determining the target blood vessel center line coordinate according to the blood vessel center position of the current scale image.
When the coordinate curve of the central line of the target blood vessel in the target area is calculated, the transverse intensity projection curves of the type A image and the type B image are firstly analyzed according to the following steps for each of different scales: selecting a scale as a current scale, taking the current scale as a research object, determining the most value of a transverse intensity projection curve of a type A image and a type B image under the current scale, searching from a starting position by a peak value searching method to obtain first two maximum value coordinates, determining an intermediate value coordinate according to the first two maximum value coordinates, and taking the intermediate value coordinate as the center position of a blood vessel of the current scale image, namely: and determining the central line coordinates of the target blood vessel according to the central position of the blood vessel of the current scale image after the central position of the blood vessel of the current scale image is obtained by each scale in different scales.
According to the technical scheme, the influence of different scale images on the central line coordinates of the blood vessel can be considered by determining the central line coordinates of the target blood vessel according to the central positions of the blood vessel of the plurality of current scale images, so that the central line coordinates of the blood vessel are more accurate, the transverse intensity projection curves of the type A images and the type B images in different scales are analyzed by adopting the same method, the central positions of the blood vessel of the plurality of current scale images have the same standard, and the transverse intensity projection curves of the type A images and the type B images in different scales can be analyzed simultaneously, so that the time consumption is reduced, and the central positions of the blood vessel of the plurality of current scale images are obtained rapidly. Furthermore, the data acquisition time required to obtain the first two maximum coordinates is extremely short, approximately equal to 1 second, but includes a complete cardiac cycle, thereby minimizing the signal interference introduced by the subject's respiration.
In one embodiment of the present application, determining the target vessel centerline coordinates according to the vessel centerline position of the current scale image includes: counting the blood vessel center position of the current scale image, analyzing and determining singular values in the blood vessel center position of the current scale image, removing the singular values, and then carrying out average value acquisition on the rest data, wherein the average value is used as a target blood vessel center line coordinate.
According to the technical scheme, when the central line coordinates of the target blood vessel are determined according to the central positions of the blood vessels of the current scale images, statistics is carried out on the central positions of the blood vessels of the corresponding current scale images obtained by each scale, the central positions of the blood vessels of the current scale images are analyzed, singular values in the central positions of the blood vessels of the current scale images are determined, then the central positions of the blood vessels of the rest current scale images are subjected to mean value calculation after the singular values are removed, so that the mean value of the central positions of the blood vessels of the current scale images is obtained, and at the moment, the obtained mean value of the central positions of the blood vessels of the current scale images is taken as the central line coordinates of the target blood vessel.
According to the technical scheme, the mean value of the blood vessel center position of the current scale image is used as the target blood vessel center line coordinate, so that the target blood vessel center line coordinate can reflect the overall trend of the blood vessel center position of the current scale image, errors are reduced, mean value calculation is carried out on the blood vessel center position of the rest current scale image after singular value elimination, the mean value accuracy is effectively improved, the influence of the singular value on the mean value is avoided, and meanwhile, the accuracy of the target blood vessel center line coordinate can be ensured.
It will be appreciated by those skilled in the art that the first and second aspects of the present application refer only to different phases of application.
Other embodiments of the disclosure will be apparent to those skilled in the art from consideration of the specification and practice of the disclosure disclosed herein. This application is intended to cover any adaptations, uses, or adaptations of the disclosure following, in general, the principles of the disclosure and including such departures from the present disclosure as come within known or customary practice within the art to which the disclosure pertains. It is intended that the specification and examples be considered as exemplary only, with a true scope and spirit of the disclosure being indicated by the following claims.
It is to be understood that the present disclosure is not limited to the precise arrangements and instrumentalities shown in the drawings, and that various modifications and changes may be effected without departing from the scope thereof. The scope of the present disclosure is limited only by the appended claims.
Claims (8)
1. The pulse wave conduction velocity imaging method based on the ultrasonic ultrafast composite plane wave is characterized by comprising the following steps of:
acquiring synthesized demodulation ultrasonic data, and performing reverse blood flow filtering treatment on the synthesized demodulation ultrasonic data to obtain a first treatment ultrasonic signal;
obtaining coordinate point axial displacement information of different depths in the first processed ultrasonic signal; when coordinate point axial displacement information of different depths is obtained in the first processing ultrasonic signal, the first processing ultrasonic signal is analyzed from a first frame image in a slow time direction through displacement between two adjacent frames of signals, so that axial displacement information of each coordinate point of the whole image in different depths is obtained, an ultrafast composite plane wave is realized to provide a frame frequency of more than 2000Hz per second, the limit of the minimum width of pulse wave signal acquisition is broken through, and the pulse wave velocity can be measured more accurately under the condition of ensuring the signal quality; when the displacement between two adjacent frame signals is analyzed in the slow time direction, the axial speed is obtained by analyzing and calculating the current frame and the next frame in the slow time direction according to the following formula:
a demodulated real part signal representing the current position point, < >>Demodulated imaginary signal representing the current position point, < ->Indicating the current position point fast time direction position, +.>Indicating the current frame in the slow direction of the current position point,/-, and>representing the calculation of the axial velocity estimate of the current position point, for example>Represents the maximum coordinate in the fast time direction, +.>Represents the maximum number of frames in the slow time direction, < ->Representing a tangent function;
receiving an input signal, and performing signal processing on the input signal to obtain a second processed signal image;
and compositing the second processing signal image with the axial position information of the coordinate points with different depths to obtain the pulse wave image of the axial velocity-time of the blood vessel wall.
2. The pulse wave velocity imaging method according to claim 1, wherein the synthesized demodulated ultrasonic data is subjected to a reverse flow filtering process by an infinite impulse response filter or a finite impulse response filter.
3. The pulse wave velocity imaging method according to claim 2, wherein the synthesized demodulated ultrasound data in the time domain is low-pass filtered by a butterworth filter or chebyshev type two filter when the infinite impulse response filter is used.
4. The pulse wave velocity imaging method according to claim 1, wherein when signal processing is performed on the input signal, a process of the signal processing includes: and adding a spatial domain window to the input signal for low-pass filtering, eliminating the intensity difference between adjacent areas, and obtaining a blurred low-sampling spatial target area image to obtain a second processing signal image.
5. The pulse wave velocity imaging method according to claim 1, wherein compositing the second processed signal image with the coordinate point axial position information of the different depths includes:
performing transverse intensity projection on the second processed signal image according to the axial position information of the coordinate points with different depths, and calculating a coordinate curve of the central line of the target blood vessel in the target area;
dividing a coordinate curve of the central line of the target blood vessel in a target area to obtain an upper blood vessel wall area and a lower blood vessel wall area, carrying out peak search in the upper blood vessel wall area to obtain an upper blood vessel wall coordinate curve, and carrying out peak search in the lower blood vessel wall area to obtain a lower blood vessel wall coordinate curve;
and carrying out coordinate extraction in a coordinate point axial displacement map according to the upper blood vessel wall coordinate curve and the lower blood vessel wall coordinate curve to obtain a pulse wave image of blood vessel wall axial speed-time.
6. The pulse wave velocity imaging method of claim 5, wherein the transverse intensity projection comprises: carrying out Gaussian blur of different scales on the second processed signal image to obtain blood vessel images of different blur scales, and carrying out downsampling of different scales on the second processed signal image to obtain blood vessel images of different downsampling scales; after Gaussian blur of different scales and downsampling of different scales are carried out on the second processing signal image to obtain blood vessel images of different blur scales and blood vessel images of different downsampling scales, the blood vessel images of different blur scales are used as type A images, the blood vessel images of different downsampling scales are used as type B images, intensity superposition processing is carried out on the type A images and the type B images in the horizontal direction of the images, and transverse intensity projection curves of the type A images and the type B images under different scales are obtained.
7. The method of pulse wave velocity imaging according to claim 6, wherein calculating a coordinate curve of a centerline of a target blood vessel in a target region comprises: and in the transverse intensity projection curves of the type A image and the type B image under different scales, searching and finding out the first two maximum coordinates by peak value searching aiming at the transverse intensity projection curves of the type A image and the type B image under each scale, determining an intermediate value coordinate according to the first two maximum coordinates, taking the intermediate value coordinate as the blood vessel center position of the current scale image, repeating for a plurality of times until each scale obtains the corresponding blood vessel center position of the current scale image, and determining the target blood vessel center line coordinate according to the blood vessel center position of the current scale image.
8. The pulse wave velocity imaging method of claim 7, wherein determining target vessel centerline coordinates from vessel center locations of the current scale image comprises: counting the blood vessel center position of the current scale image, analyzing and determining singular values in the blood vessel center position of the current scale image, removing the singular values, and then carrying out average value acquisition on the rest data, wherein the average value is used as a target blood vessel center line coordinate.
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