CN110680398A - Ultrasonic echo imaging method and system and ultrasonic equipment - Google Patents
Ultrasonic echo imaging method and system and ultrasonic equipment Download PDFInfo
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- CN110680398A CN110680398A CN201910963470.0A CN201910963470A CN110680398A CN 110680398 A CN110680398 A CN 110680398A CN 201910963470 A CN201910963470 A CN 201910963470A CN 110680398 A CN110680398 A CN 110680398A
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- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/08—Detecting organic movements or changes, e.g. tumours, cysts, swellings
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/48—Diagnostic techniques
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/58—Testing, adjusting or calibrating the diagnostic device
Abstract
The invention discloses an ultrasonic echo imaging method, which can distinguish a plurality of layers of tissue media of a part scanned by an ultrasonic probe based on an ultrasonic image after the ultrasonic image is obtained, determine the actual ultrasonic propagation speed of the ultrasonic wave in the plurality of layers of tissue media, and modify the ultrasonic image according to the actual ultrasonic propagation speed, thereby obtaining the ultrasonic image which represents the position information of each tissue in the part more accurately, avoiding the distortion of the ultrasonic image and further enabling the ultrasonic image to reflect the real size of each tissue in the part more accurately. The invention also discloses an ultrasonic echo imaging system and ultrasonic equipment, which have the same beneficial effects as the ultrasonic echo imaging method.
Description
Technical Field
The invention relates to the field of ultrasonic imaging, in particular to an ultrasonic echo imaging method, an ultrasonic echo imaging system and ultrasonic equipment.
Background
An ultrasonic probe is a device that transmits an ultrasonic excitation signal and receives an ultrasonic echo signal. Currently, based on the ultrasonic signals emitted and returned by an ultrasonic probe, an ultrasonic image can be obtained that represents positional information of each tissue in the site scanned by the ultrasonic probe. In the related art, in obtaining an ultrasound image based on an ultrasound signal, it is generally assumed that the propagation velocity of the ultrasound in a site is constant, and position information of each tissue in the site is determined according to the propagation velocity and the propagation time of the ultrasound in the site, and then an ultrasound image is generated based on the position information of each tissue in the site. However, the propagation speeds of the ultrasonic waves in different tissues in the region are actually different, so that the position information of each tissue in the determined region is not accurate enough, the ultrasonic image is distorted, and the actual size of each tissue in the region cannot be accurately reflected.
Therefore, how to provide a solution to the above technical problem is a problem that needs to be solved by those skilled in the art.
Disclosure of Invention
The invention aims to provide an ultrasonic echo imaging method, an ultrasonic echo imaging system and ultrasonic equipment, wherein an ultrasonic image is corrected according to the actual ultrasonic propagation speed, so that the ultrasonic image which represents the position information of each tissue in a part more accurately is obtained, the distortion of the ultrasonic image is avoided, and the ultrasonic image can reflect the real size of each tissue in the part more accurately.
In order to solve the above technical problem, the present invention provides an ultrasonic echo imaging method, including:
obtaining an ultrasonic image at a preset fixed sound velocity based on ultrasonic signals transmitted and returned by an ultrasonic probe;
determining a multi-layer tissue medium of a site scanned by the ultrasonic probe based on the ultrasonic image;
determining ultrasonic propagation speeds corresponding to the multiple layers of tissue media according to a preset medium sound velocity corresponding relation;
and correcting the ultrasonic image according to the ultrasonic propagation speed to obtain a corrected ultrasonic image.
Preferably, the process of determining a plurality of layers of tissue media of a site scanned by the ultrasonic probe based on the ultrasonic image comprises:
comparing the ultrasonic image with each standard ultrasonic image in a preset image template library to obtain a target ultrasonic image with the similarity to the ultrasonic image being greater than a preset similarity threshold value;
and taking the multilayer tissue medium corresponding to the target ultrasonic image recorded in the preset image template library as the multilayer tissue medium contained in the part scanned by the ultrasonic probe.
Preferably, the ultrasound echo imaging method further comprises:
when the target ultrasonic images cannot be compared, controlling a display screen to display comparison failure information so that an operator adjusts the scanning position of the ultrasonic probe after receiving the comparison failure information until the target ultrasonic images are compared.
Preferably, the process of modifying the ultrasound image according to the ultrasound propagation velocity to obtain a modified ultrasound image includes:
acquiring the propagation time of ultrasonic waves with preset fixed sound velocity in each layer of tissue medium;
obtaining a target tissue boundary of the ultrasonic image according to the ultrasonic propagation speed and the propagation time corresponding to the multiple layers of tissue media;
and modifying the tissue boundary of the ultrasonic image under the preset fixed sound velocity according to the target tissue boundary to obtain a modified ultrasonic image.
Preferably, the process of modifying the ultrasound image according to the ultrasound propagation velocity to obtain a modified ultrasound image includes:
according to the relation of preset medium distance
Finding the ultrasonic waves emitted by the ultrasonic probe to eachA depth of the tissue medium boundary; wherein D iskDepth of the ultrasonic wave emitted by the ultrasonic probe to the k-th layer tissue medium boundary, CiIs the ultrasonic propagation speed, T, of the ultrasonic wave in the ith layer tissue mediumiK is an integer greater than 1, i is 2,3, …, k is the propagation time for the ultrasound wave to propagate to the ith tissue medium boundary and return to reception;
and correcting the tissue boundary of the ultrasonic image according to the depth to obtain a corrected ultrasonic image.
Preferably, the process of determining the respective corresponding ultrasound propagation velocities of the multiple layers of tissue media according to the preset media sound velocity correspondence includes:
presetting a medium sound velocity relation table representing one-to-one correspondence between different tissue media and different ultrasonic propagation velocities;
and determining the ultrasonic propagation speeds corresponding to the multiple layers of the tissue media according to the medium sound speed relation table.
Preferably, the ultrasound echo imaging method further comprises:
acquiring a tissue strain period of a part scanned by the ultrasonic probe;
and overlapping and compounding the same-phase images of the ultrasonic images after the multiple tissue strain period corrections to obtain the overlapped and compounded ultrasonic images.
Preferably, the process of acquiring a tissue strain cycle of a site scanned by the ultrasonic probe comprises:
after a first ultrasonic image is obtained at a first moment, calculating the pixel coordinate value error of the currently obtained ultrasonic image and the first ultrasonic image at intervals of preset time until a second ultrasonic image with the pixel coordinate value error smaller than a preset error threshold value is obtained;
and obtaining the tissue strain period of the part scanned by the ultrasonic probe by making a difference between the second time corresponding to the second ultrasonic image and the first time.
Preferably, the process of performing superposition compounding on the same-phase images of the ultrasound images after the multiple tissue strain period corrections to obtain a superposition compounded ultrasound image includes:
acquiring in-phase images among the ultrasonic images after the multiple tissue strain period corrections;
and calculating the pixel coordinate values of the same-phase images to obtain an average value, and obtaining an ultrasonic image according to the average value.
In order to solve the above technical problem, the present invention further provides an ultrasonic echo imaging system, including:
the image acquisition module is used for obtaining an ultrasonic image under a preset fixed sound velocity based on ultrasonic signals transmitted and returned by the ultrasonic probe;
a medium determination module for determining a multi-layer tissue medium of a site scanned by the ultrasonic probe based on the ultrasonic image;
the speed determining module is used for determining the ultrasonic propagation speeds corresponding to the multiple layers of tissue media according to the preset medium sound speed corresponding relation;
and the image correction module is used for correcting the ultrasonic image according to the ultrasonic propagation speed to obtain a corrected ultrasonic image.
In order to solve the above technical problem, the present invention also provides an ultrasound apparatus, comprising:
the ultrasonic probe is used for transmitting an ultrasonic excitation signal and receiving an ultrasonic echo signal;
a memory for storing a computer program;
and the controller is connected with the ultrasonic probe and is used for realizing the steps of any one of the ultrasonic echo imaging methods when the computer program is executed.
The invention provides an ultrasonic echo imaging method, which can distinguish a plurality of layers of tissue media of a part scanned by an ultrasonic probe based on an ultrasonic image after the ultrasonic image is obtained, determine the actual ultrasonic propagation speed of the ultrasonic wave in the plurality of layers of tissue media, and modify the ultrasonic image according to the actual ultrasonic propagation speed, thereby obtaining the ultrasonic image which represents the position information of each tissue in the part more accurately, avoiding the distortion of the ultrasonic image and further enabling the ultrasonic image to reflect the real size of each tissue in the part more accurately.
The invention also provides an ultrasonic echo imaging system and ultrasonic equipment, which have the same beneficial effects as the ultrasonic echo imaging method.
Drawings
In order to more clearly illustrate the technical solutions in the embodiments of the present invention, the drawings needed in the prior art and 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 invention, and it is obvious for those skilled in the art to obtain other drawings without creative efforts.
Fig. 1 is a flowchart of an ultrasonic echo imaging method according to an embodiment of the present invention;
FIG. 2 is a schematic diagram of ultrasound propagating in different tissue media according to an embodiment of the present invention;
FIG. 3 is a schematic representation of an image of tissue 1/2/3 during a complete tissue strain cycle, according to an embodiment of the present invention;
fig. 4 is a schematic structural diagram of an ultrasonic echo imaging system according to an embodiment of the present invention.
Detailed Description
The core of the invention is to provide an ultrasonic echo imaging method, a system and ultrasonic equipment, which modify an ultrasonic image according to the actual ultrasonic propagation speed, thereby obtaining the ultrasonic image which represents the position information of each tissue in a part more accurately, avoiding the distortion of the ultrasonic image and further enabling the ultrasonic image to reflect the real size of each tissue in the part more accurately.
In order to make the objects, technical solutions and advantages of the embodiments of the present invention clearer, the technical solutions in the embodiments of the present invention will be clearly and completely described below with reference to the drawings in the embodiments of the present invention, and it is obvious that the described embodiments are some, but not all, embodiments of the present invention. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present invention.
Referring to fig. 1, fig. 1 is a flowchart of an ultrasonic echo imaging method according to an embodiment of the present invention.
The ultrasonic echo imaging method comprises the following steps:
step S1: based on ultrasonic signals transmitted and returned by the ultrasonic probe, an ultrasonic image is obtained at a preset fixed sound velocity.
It should be noted that the preset of the present application is set in advance, and only needs to be set once, and the reset is not needed unless the modification is needed according to the actual situation.
Specifically, during real-time scanning of the ultrasonic probe (the scanning depth of the ultrasonic probe is adjustable, and the scanning depth of the ultrasonic probe is set according to the current requirement), the ultrasonic probe transmits an ultrasonic excitation signal (i.e., the transmitted ultrasonic signal mentioned in step S1), and the ultrasonic excitation signal passes through the multi-layer tissue of the scanned part of the ultrasonic probe and reflects an ultrasonic echo signal back to the ultrasonic probe (i.e., the ultrasonic echo signal is the returned ultrasonic signal mentioned in step S1).
The signal intensity of the ultrasound echo signals reflected back under different tissues is different (for example, the signal intensity of the ultrasound echo signal returned by the bone > the signal intensity of the ultrasound echo signal returned by the blood), and is reflected on the gray value of the ultrasound image based on the ultrasound echo imaging (the stronger the signal intensity of the ultrasound echo signal, the whiter the gray value of the ultrasound image corresponding to the depth point, and the weaker the signal intensity of the ultrasound echo signal, the blacker the gray value of the ultrasound image corresponding to the depth point). In addition to the parameter of the gray scale value, the ultrasound image also needs to acquire a parameter of pixel coordinate values (x, y) representing position information of each tissue in the site, where x represents a signal width of the ultrasound signal and y represents a propagation distance of the ultrasound signal in each tissue of the site. In step S1, assuming that the propagation speed of the ultrasound signal in the site is constant, the distance y that the ultrasound signal propagates in each tissue of the site is equal to (the time when the ultrasound probe returns to the ultrasound signal — the time when the ultrasound probe transmits the ultrasound signal) × the preset fixed sound speed/2, so that an ultrasound image at the preset fixed sound speed can be obtained.
Step S2: a multi-layer tissue medium of a site swept by the ultrasound probe is determined based on the ultrasound images.
In particular, the ultrasound image can be used for distinguishing the multilayer tissue media of the part scanned by the ultrasonic probe based on the ultrasound image because the shape characteristics can be embodied by considering that the gray values of different tissues of the part reflected on the ultrasound image are different.
Step S3: and determining the ultrasonic propagation speeds corresponding to the multiple layers of tissue media according to the preset medium sound velocity corresponding relation.
Specifically, in practice, the propagation speeds of the ultrasonic signals in different tissue media are different, so the application sets in advance a one-to-one correspondence relationship (for short, a medium sound velocity correspondence relationship) between different tissue media and different ultrasonic propagation speeds to determine the ultrasonic propagation speeds actually corresponding to the different tissue media.
Based on this, after the multilayer tissue media of the part scanned by the ultrasonic probe are determined in step S2, the ultrasonic propagation speeds corresponding to the multilayer tissue media in practice can be determined according to the set media sound velocity correspondence, so as to lay a foundation for subsequently correcting the ultrasonic image.
Step S4: and correcting the ultrasonic image according to the ultrasonic propagation speed to obtain a corrected ultrasonic image.
Specifically, the ultrasound image obtained in step S1 is distorted due to the fixed sound speed calculation. For the ultrasound image, the fixed sound velocity is used to calculate the y value of the pixel coordinate value of the ultrasound image, and it can be understood that the reasonable calculation method of the y value of the pixel coordinate value of the ultrasound image is: the distance of the ultrasonic wave propagating in the tissue medium A should be calculated by using the ultrasonic propagation speed actually corresponding to the tissue medium A. Therefore, the ultrasound image is modified by the ultrasound propagation velocities determined in step S3 and corresponding to the multiple layers of tissue media, so as to obtain an ultrasound image representing the position information of each tissue in the site more accurately.
The invention provides an ultrasonic echo imaging method, which can distinguish a plurality of layers of tissue media of a part scanned by an ultrasonic probe based on an ultrasonic image after the ultrasonic image is obtained, determine the actual ultrasonic propagation speed of the ultrasonic wave in the plurality of layers of tissue media, and modify the ultrasonic image according to the actual ultrasonic propagation speed, thereby obtaining the ultrasonic image which represents the position information of each tissue in the part more accurately, avoiding the distortion of the ultrasonic image and further enabling the ultrasonic image to reflect the real size of each tissue in the part more accurately.
On the basis of the above-described embodiment:
as a preferred embodiment, the process of determining a multi-layer tissue medium of a site scanned by an ultrasound probe based on an ultrasound image comprises:
comparing the ultrasonic image with each standard ultrasonic image in a preset image template library to obtain a target ultrasonic image with the similarity to the ultrasonic image being greater than a preset similarity threshold value;
and taking the multilayer tissue medium corresponding to the target ultrasonic image recorded in the preset image template library as the multilayer tissue medium contained in the part scanned by the ultrasonic probe.
Specifically, an image template library may be set in advance, in which ultrasound images (referred to as standard ultrasound images) obtained by the ultrasound probe in the scanning process in the longitudinal directions of different sections are collected, and a plurality of layers of tissue media (obtained by analyzing the standard ultrasound images by an experienced doctor) of the portion scanned by the ultrasound probe corresponding to the standard ultrasound images are recorded, so as to analyze the ultrasound images obtained in step S1, and obtain the plurality of layers of tissue media of the portion scanned by the ultrasound probe corresponding to the ultrasound images.
It can be understood that, if a target ultrasound image that is substantially identical to the ultrasound image obtained in step S1 is found in the preset image template library, the ultrasound image and the target ultrasound image may be considered to be images obtained in the process of scanning the ultrasound probe in the same tangential longitudinal direction, that is, the multilayer tissue medium corresponding to the target ultrasound image may be considered to be identical to the multilayer tissue medium of the portion scanned by the ultrasound probe corresponding to the ultrasound image.
Based on the above, a similarity threshold is set in advance, and when the similarity between the ultrasound image and a standard ultrasound image in the preset image template library is greater than the set similarity threshold, the standard ultrasound image is considered as a target ultrasound image which is basically consistent with the ultrasound image. Specifically, the ultrasound image is compared with each standard ultrasound image in the preset image template library, so as to obtain a target ultrasound image with the similarity greater than the set similarity threshold. After the target ultrasonic images are compared, the multilayer tissue medium corresponding to the target ultrasonic images recorded in the preset image template library is used as the multilayer tissue medium contained in the part scanned by the ultrasonic probe corresponding to the ultrasonic images.
More specifically, the comparison process between the ultrasound image and the standard ultrasound image includes: and extracting the shape characteristics of the ultrasonic image and the standard ultrasonic image, and comparing the shape characteristics of the ultrasonic image and the standard ultrasonic image to obtain the similarity of the shape characteristics of the ultrasonic image and the standard ultrasonic image (as the similarity of the ultrasonic image and the standard ultrasonic image).
As a preferred embodiment, the ultrasonic echo imaging method further comprises:
when the target ultrasonic images cannot be compared, the display screen is controlled to display comparison failure information, so that an operator can adjust the scanning position of the ultrasonic probe after receiving the comparison failure information until the target ultrasonic images are compared.
Further, in the process that an operator operates the ultrasonic probe, the ultrasonic probe may be placed in an irregular state, so that the difference between the obtained ultrasonic image and the standard ultrasonic image in the preset image template library is far, and the target ultrasonic image cannot be compared finally, so that when the target ultrasonic image cannot be compared, the control display screen displays comparison failure information for the operator to check. After receiving the comparison failure information, the operator adjusts the scanning position of the ultrasonic probe, waits for a period of time to check the display information of the display screen, and if the comparison failure information is withdrawn from the display screen, the comparison result shows that the target ultrasonic image is obtained through comparison; if the display screen still displays the comparison failure information, which indicates that the target ultrasonic image still cannot be compared, the scanning position of the ultrasonic probe is adjusted again until the target ultrasonic image is compared.
As a preferred embodiment, the process of modifying an ultrasound image according to an ultrasound propagation velocity to obtain a modified ultrasound image includes:
acquiring the propagation time of ultrasonic waves with preset fixed sound velocity in each layer of tissue medium;
obtaining a target tissue boundary of the ultrasonic image according to the ultrasonic propagation speed and propagation time corresponding to the multiple layers of tissue media respectively;
and correcting the tissue boundary of the ultrasonic image under the preset fixed sound velocity according to the target tissue boundary to obtain a corrected ultrasonic image.
Specifically, considering that the boundary of the multilayer tissue medium obtained by calculation is the actual tissue boundary of the ultrasound image based on the respective actually corresponding ultrasound propagation velocities of the multilayer tissue medium, the target tissue boundary of the ultrasound image, that is, the actual target position of the tissue boundary of the ultrasound image, is obtained according to the respective actually corresponding ultrasound propagation velocities of the multilayer tissue medium and the propagation time of the ultrasound wave in the respective layers of tissue medium in the present application; and then, correcting the tissue boundary of the ultrasonic image obtained at the fixed sound velocity before the target tissue boundary, thereby obtaining a corrected ultrasonic image.
The propagation time of the ultrasonic waves in each layer of tissue medium is: the propagation time used for calculating the ultrasound image at the preset fixed sound velocity is the same as the propagation time used for calculating the ultrasound image at the actual sound velocity.
As a preferred embodiment, the process of modifying an ultrasound image according to an ultrasound propagation velocity to obtain a modified ultrasound image includes:
according to the relation of preset medium distance
The depth from the ultrasonic wave emitted by the ultrasonic probe to the boundary of each tissue medium is obtained; wherein D iskDepth of ultrasonic wave emitted by ultrasonic probe to k layer tissue medium boundary, CiFor ultrasonic waves on the ith layerSpeed of propagation of ultrasound, T, of tissue mediumiK is an integer greater than 1, i is 2,3, …, k is the propagation time for the ultrasound wave to propagate to the ith tissue medium boundary and return to reception;
and correcting the tissue boundary of the ultrasonic image according to the depth to obtain a corrected ultrasonic image.
Specifically, referring to fig. 2, fig. 2 is a schematic view illustrating propagation of an ultrasonic wave in different tissue media according to an embodiment of the present invention. Depth of ultrasonic wave emitted from ultrasonic probe to layer 1 tissue medium boundary (ultrasonic probe to A)1A distance of (A)1Lower boundary of layer 1 tissue medium, i.e. the boundary between layer 1 tissue medium and layer 2 tissue medium): d1＝(C1*T1) 2; depth of ultrasonic wave emitted from ultrasonic probe to boundary of layer 2 tissue medium (ultrasonic probe to A)2A distance of (A)2Lower boundary of layer 2 tissue medium, i.e. the boundary between layer 2 tissue medium and layer 3 tissue medium):
D2＝D1+C2*(T2-T1) 2; the depth of the ultrasonic wave emitted from the ultrasonic probe to the k-th layer tissue medium boundary (the ultrasonic probe is to A)kDistance (c):
based on this, the application is in accordance with
The depth of the ultrasonic wave emitted by the ultrasonic probe to the boundary of each tissue medium, namely the y value of the pixel coordinate value of the ultrasonic image is obtained (medium distance relational expression), thereby realizing the correction of the ultrasonic image.
As a preferred embodiment, the process of determining the ultrasound propagation velocities corresponding to the multiple layers of tissue media according to the preset media sound velocity correspondence includes:
presetting a medium sound velocity relation table representing one-to-one correspondence between different tissue media and different ultrasonic propagation velocities;
and determining the ultrasonic propagation speeds corresponding to the multiple layers of tissue media according to the medium sound speed relation table.
Specifically, the method and the device can embody the one-to-one correspondence between different tissue media and different ultrasonic propagation speeds in a table form, and after the multiple layers of tissue media are determined, the ultrasonic propagation speeds corresponding to the multiple layers of tissue media are determined in a table look-up mode.
As a preferred embodiment, the ultrasonic echo imaging method further comprises:
acquiring a tissue strain period of a part scanned by an ultrasonic probe;
and overlapping and compounding the same-phase images of the ultrasonic images after the multiple tissue strain period corrections to obtain the overlapped and compounded ultrasonic images.
Further, considering that some interference signals may be doped in the process of obtaining an ultrasound image, which may cause that a tissue boundary of the ultrasound image is not clear enough and noise exists in the ultrasound image, in the prior art, a continuous time image sequence compounding mode is usually adopted to improve a spatial resolution of the ultrasound image and weaken the noise existing in the ultrasound image, however, a part scanned by an ultrasound probe usually has periodic tissue strain (such as periodic heartbeat), and the continuous time image sequence compounding mode may cause image overfitting, reduce image detail information, and cause that an ultrasound echo imaging effect is poor.
Based on this, this application adopts the compound mode of multiunit tissue strain cycle same phase image stack to promote supersound echo imaging effect. Specifically, the tissue strain cycle of the part scanned by the ultrasonic probe is firstly acquired, then the same-phase images among the ultrasonic images corrected by the multiple tissue strain cycles are acquired, and the multiple same-phase images are superposed and compounded to obtain the superposed and compounded ultrasonic images. The multi-period same-phase image superposition compounding mode is suitable for the periodic tissue strain rule of the part and cannot cover image detail information, and therefore the ultrasonic echo imaging effect is improved.
Referring to fig. 3, fig. 3 shows a structure 1/2/3 in a complete structure according to an embodiment of the present inventionImaging schematic in varying periods. In FIG. 3, at tiAt that time, the image boundary of the tissue 1 is not clear enough, and the image of the tissue 3 has dot noise, which goes through a tissue strain period T (at T)iTime tT+i-1Time, deformation of the tissue 1, 2, 3) and then at tT+iAt the moment, the image boundary of the tissue 1 is clear, and the image of the tissue 3 has no dot noise, so that the effects of enhancing the spatial resolution of an ultrasonic image and reducing the image noise are achieved by superposing and compounding multi-period same-phase images.
As a preferred embodiment, the process of acquiring a tissue strain cycle of a site scanned by an ultrasonic probe comprises:
after a first ultrasonic image is obtained at a first moment, pixel coordinate value errors of the currently obtained ultrasonic image and the first ultrasonic image are obtained every other preset time until a second ultrasonic image with the pixel coordinate value errors smaller than a preset error threshold value is obtained;
and subtracting the first time from the second time corresponding to the second ultrasonic image to obtain the tissue strain period of the part scanned by the ultrasonic probe.
Specifically, the pixel coordinate value error is obtained by subtracting the pixel coordinate value of the currently obtained ultrasound image from the pixel coordinate value of the first ultrasound image at preset time intervals (according to empirical setting, it can be set that the pixel coordinate value error is obtained at every other frame); then comparing the error of the pixel coordinate value with a preset error threshold, and when the error of the pixel coordinate value is not less than the preset error threshold, considering that the tissue forms of the parts corresponding to the currently obtained ultrasonic image and the first ultrasonic image are inconsistent, which indicates that a new tissue strain period is not entered; and when the error of the pixel coordinate value is smaller than a preset error threshold value, the tissue forms of the parts corresponding to the currently obtained ultrasonic image and the first ultrasonic image are basically consistent, and a new tissue strain period starts to enter.
Based on the above, after the second ultrasonic image with the pixel coordinate value error smaller than the preset error threshold is obtained, the difference between the second moment corresponding to the second ultrasonic image and the first moment is obtained, and the difference value between the second moment and the first moment is the tissue strain period of the part scanned by the ultrasonic probe.
As a preferred embodiment, the process of performing superposition compounding on the in-phase images of a plurality of ultrasound images after the tissue strain period correction to obtain a superposition compounded ultrasound image includes:
acquiring in-phase images among the ultrasonic images after the multiple tissue strain period corrections;
and calculating the average value of the pixel coordinate values of the images with the same phase, and obtaining an ultrasonic image according to the average value.
Specifically, the ultrasound images after a plurality of tissue strain period corrections are superposed and compounded on the same-phase images, specifically, the average value of pixel coordinate values of a plurality of same-phase images is obtained, and then an ultrasound image is generated according to the average value, so that superposed and compounded on a plurality of same-phase images are realized.
Referring to fig. 4, fig. 4 is a schematic structural diagram of an ultrasonic echo imaging system according to an embodiment of the present invention.
The ultrasonic echo imaging system comprises:
the ultrasonic imaging system comprises an image acquisition module 1, a sound acquisition module and a sound processing module, wherein the image acquisition module is used for acquiring an ultrasonic image under a preset fixed sound velocity based on ultrasonic signals transmitted and returned by an ultrasonic probe;
the medium determining module 2 is used for determining a multilayer tissue medium of a part scanned by the ultrasonic probe based on the ultrasonic image;
the speed determining module 3 is used for determining the ultrasonic propagation speeds corresponding to the multiple layers of tissue media according to the preset medium sound speed corresponding relation;
and the image correction module 4 is used for correcting the ultrasonic image according to the ultrasonic propagation speed to obtain a corrected ultrasonic image.
For the introduction of the ultrasonic echo imaging system provided by the present invention, reference is made to the above-mentioned embodiment of the ultrasonic echo imaging method, and the present invention is not described herein again.
The present invention also provides an ultrasound device comprising:
the ultrasonic probe is used for transmitting an ultrasonic excitation signal and receiving an ultrasonic echo signal;
a memory for storing a computer program;
and the controller is connected with the ultrasonic probe and is used for realizing the steps of any one of the ultrasonic echo imaging methods when executing the computer program.
For the introduction of the ultrasonic device provided by the present invention, please refer to the above-mentioned embodiment of the ultrasonic echo imaging method, and the present invention is not described herein again.
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 phrase "comprising an … …" does not exclude the presence of other identical elements in a process, method, article, or apparatus that comprises the element.
The previous description of the disclosed embodiments is provided to enable any person skilled in the art to make or use the present invention. Various modifications to these embodiments will be readily apparent to those skilled in the art, and the generic principles defined herein may be applied to other embodiments without departing from the spirit or scope of the invention. Thus, the present invention is not intended to be limited to the embodiments shown herein but is to be accorded the widest scope consistent with the principles and novel features disclosed herein.
Claims (11)
1. An ultrasonic echo imaging method, comprising:
obtaining an ultrasonic image at a preset fixed sound velocity based on ultrasonic signals transmitted and returned by an ultrasonic probe;
determining a multi-layer tissue medium of a site scanned by the ultrasonic probe based on the ultrasonic image;
determining ultrasonic propagation speeds corresponding to the multiple layers of tissue media according to a preset medium sound velocity corresponding relation;
and correcting the ultrasonic image according to the ultrasonic propagation speed to obtain a corrected ultrasonic image.
2. The ultrasonic echo imaging method of claim 1, wherein the process of determining a multi-layer tissue medium of a site swept by the ultrasonic probe based on the ultrasonic image comprises:
comparing the ultrasonic image with each standard ultrasonic image in a preset image template library to obtain a target ultrasonic image with the similarity to the ultrasonic image being greater than a preset similarity threshold value;
and taking the multilayer tissue medium corresponding to the target ultrasonic image recorded in the preset image template library as the multilayer tissue medium contained in the part scanned by the ultrasonic probe.
3. The ultrasonic echo imaging method according to claim 2, further comprising:
when the target ultrasonic images cannot be compared, controlling a display screen to display comparison failure information so that an operator adjusts the scanning position of the ultrasonic probe after receiving the comparison failure information until the target ultrasonic images are compared.
4. The method of ultrasonic echo imaging according to claim 1, wherein said modifying the ultrasonic image according to the ultrasonic propagation velocity to obtain a modified ultrasonic image comprises:
acquiring the propagation time of ultrasonic waves with preset fixed sound velocity in each layer of tissue medium;
obtaining a target tissue boundary of the ultrasonic image according to the ultrasonic propagation speed and the propagation time corresponding to the multiple layers of tissue media;
and modifying the tissue boundary of the ultrasonic image under the preset fixed sound velocity according to the target tissue boundary to obtain a modified ultrasonic image.
5. The method of ultrasonic echo imaging according to claim 4, wherein said process of modifying the ultrasonic image according to the ultrasonic propagation velocity to obtain a modified ultrasonic image comprises:
according to the relation of preset medium distance
The depth from the ultrasonic wave emitted by the ultrasonic probe to each tissue medium boundary is obtained; wherein D iskDepth of the ultrasonic wave emitted by the ultrasonic probe to the k-th layer tissue medium boundary, CiIs the ultrasonic propagation speed, T, of the ultrasonic wave in the ith layer tissue mediumiK is an integer greater than 1, i is 2,3, …, k is the propagation time for the ultrasound wave to propagate to the ith tissue medium boundary and return to reception;
and correcting the tissue boundary of the ultrasonic image according to the depth to obtain a corrected ultrasonic image.
6. The ultrasonic echo imaging method according to claim 1, wherein the process of determining the respective ultrasonic propagation velocities corresponding to the plurality of layers of the tissue medium according to the preset medium sound velocity correspondence includes:
presetting a medium sound velocity relation table representing one-to-one correspondence between different tissue media and different ultrasonic propagation velocities;
and determining the ultrasonic propagation speeds corresponding to the multiple layers of the tissue media according to the medium sound speed relation table.
7. The ultrasonic echo imaging method of any one of claims 1 to 6, further comprising:
acquiring a tissue strain period of a part scanned by the ultrasonic probe;
and overlapping and compounding the same-phase images of the ultrasonic images after the multiple tissue strain period corrections to obtain the overlapped and compounded ultrasonic images.
8. The method of ultrasonic echo imaging according to claim 7, wherein the process of acquiring a tissue strain cycle of a site scanned by the ultrasonic probe comprises:
after a first ultrasonic image is obtained at a first moment, calculating the pixel coordinate value error of the currently obtained ultrasonic image and the first ultrasonic image at intervals of preset time until a second ultrasonic image with the pixel coordinate value error smaller than a preset error threshold value is obtained;
and obtaining the tissue strain period of the part scanned by the ultrasonic probe by making a difference between the second time corresponding to the second ultrasonic image and the first time.
9. The method of ultrasonic echo imaging according to claim 7, wherein the process of performing superposition compounding of the in-phase images on the ultrasound images after the plurality of tissue strain period corrections to obtain a superposition compounded ultrasound image comprises:
acquiring in-phase images among the ultrasonic images after the multiple tissue strain period corrections;
and calculating the pixel coordinate values of the same-phase images to obtain an average value, and obtaining an ultrasonic image according to the average value.
10. An ultrasonic echo imaging system, comprising:
the image acquisition module is used for obtaining an ultrasonic image under a preset fixed sound velocity based on ultrasonic signals transmitted and returned by the ultrasonic probe;
a medium determination module for determining a multi-layer tissue medium of a site scanned by the ultrasonic probe based on the ultrasonic image;
the speed determining module is used for determining the ultrasonic propagation speeds corresponding to the multiple layers of tissue media according to the preset medium sound speed corresponding relation;
and the image correction module is used for correcting the ultrasonic image according to the ultrasonic propagation speed to obtain a corrected ultrasonic image.
11. An ultrasound device, comprising:
the ultrasonic probe is used for transmitting an ultrasonic excitation signal and receiving an ultrasonic echo signal;
a memory for storing a computer program;
a controller connected to the ultrasound probe for, when executing the computer program, implementing the steps of the ultrasound echo imaging method according to any of claims 1-9.
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