CN118021343A - Ultrasonic imaging method and ultrasonic imaging device - Google Patents
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Abstract
The embodiment of the application provides an ultrasonic imaging method and ultrasonic imaging equipment, wherein the ultrasonic imaging method comprises the steps of determining a target section in a B mode; starting a contrast imaging mode to obtain a plurality of first ultrasonic images, determining a plurality of reference ultrasonic images in the plurality of first ultrasonic images, wherein the tangential planes corresponding to the plurality of reference ultrasonic images are target tangential planes; obtaining a second ultrasonic image, wherein target tissues of the second ultrasonic image contain contrast microbubbles; determining a similarity between the second ultrasound image and the plurality of reference ultrasound images; determining the fixation degree of the second ultrasonic image according to the similarity, wherein the fixation degree is used for representing the approaching degree between the tangent plane corresponding to the second ultrasonic image and the target tangent plane; and displaying the second ultrasonic image and outputting the fixation degree of the second ultrasonic image. The effectiveness of the second ultrasonic image is evaluated based on the degree of fixation, and the influence of factors such as respiratory motion of a patient or probe shake on the effectiveness evaluation can be reduced or eliminated.
Description
Technical Field
The application relates to the technical field of medical equipment, in particular to an ultrasonic imaging method and ultrasonic imaging equipment.
Background
Compared with other modern medical imaging methods, the medical ultrasonic imaging has the advantages of safety, no damage, convenience, low cost and the like, can perform detection imaging and quantitative analysis of various parameters, and has wide clinical application. However, in clinical diagnosis and treatment, due to respiratory motion of a patient or shake of an ultrasonic probe, an imaging section often cannot keep the same position in a radiography process, and interference caused by section or position change can influence observation of a doctor and effectiveness of an ultrasonic image.
Disclosure of Invention
The application provides an ultrasonic imaging method and ultrasonic imaging equipment, which can determine the effectiveness of an ultrasonic image through the proximity degree between a tangent plane corresponding to the ultrasonic image and the target tangent plane.
In a first aspect, an embodiment of the present application provides an ultrasound imaging method, including:
B mode ultrasonic images are obtained in a B mode, and a target section of target tissue is determined according to the B mode ultrasonic images;
Starting a contrast imaging mode, transmitting first ultrasonic waves to the target tissue, obtaining a plurality of first ultrasonic images according to echoes of the first ultrasonic waves, and determining a plurality of reference ultrasonic images in the plurality of first ultrasonic images, wherein the tangential planes corresponding to the plurality of reference ultrasonic images are the target tangential planes;
transmitting a second ultrasonic wave to the target tissue, and obtaining a second ultrasonic image according to the echo of the second ultrasonic wave, wherein when the second ultrasonic wave is transmitted to the target tissue, the target tissue contains contrast microbubbles;
Determining a similarity between the second ultrasound image and a plurality of the reference ultrasound images;
Determining the fixation degree of the second ultrasonic image according to the similarity between the second ultrasonic image and the plurality of reference ultrasonic images, wherein the fixation degree is used for representing the proximity degree between the tangent plane corresponding to the second ultrasonic image and the target tangent plane;
and displaying the second ultrasonic image and outputting the fixation degree of the second ultrasonic image.
In a second aspect, an embodiment of the present application provides an ultrasound imaging method, including:
Acquiring a plurality of reference ultrasonic images of target tissue, wherein the plurality of reference ultrasonic images correspond to target section surfaces of the target tissue, and the positions of the target tissue in the plurality of reference ultrasonic images are different;
acquiring a second ultrasonic image of the target tissue, wherein the target tissue contains contrast microbubbles in the second ultrasonic image acquisition process;
Determining a similarity between the second ultrasound image and a plurality of the reference ultrasound images;
And determining the fixation degree of the second ultrasonic image according to the similarity between the second ultrasonic image and the plurality of reference ultrasonic images, wherein the fixation degree is used for representing the proximity degree between the tangent plane corresponding to the second ultrasonic image and the target tangent plane.
In a third aspect, an embodiment of the present application provides an ultrasound imaging method, including:
transmitting ultrasonic waves to a target tissue, and obtaining an ultrasonic image based on echo of the ultrasonic waves;
determining a plurality of reference ultrasonic images in a plurality of first ultrasonic images, wherein the first ultrasonic images are ultrasonic images acquired within a preset time period, and the plurality of reference ultrasonic images correspond to a target section of the target tissue;
Determining the similarity between a second ultrasonic image and a plurality of reference ultrasonic images, wherein the second ultrasonic image is an ultrasonic image acquired after the preset time period, and the target tissue contains contrast microbubbles in the second ultrasonic image acquisition process;
Determining the fixation degree of the second ultrasonic image according to the similarity between the second ultrasonic image and the plurality of reference ultrasonic images, wherein the fixation degree is used for representing the proximity degree between the tangent plane corresponding to the second ultrasonic image and the target tangent plane;
and displaying the second ultrasonic image and outputting the fixation degree of the second ultrasonic image.
In a fourth aspect, an embodiment of the present application provides an ultrasound imaging apparatus including:
A probe;
a transmitting circuit that excites the probe to transmit ultrasound waves to a target tissue;
The receiving circuit controls the probe to receive the ultrasonic echo so as to obtain an ultrasonic echo signal;
a display providing a display interface;
The ultrasonic imaging equipment processes the ultrasonic echo signals to obtain an ultrasonic image of the target tissue; and performing the steps of the ultrasound imaging method described previously.
In a fifth aspect, embodiments of the present application provide a computer readable storage medium storing a computer program which, when executed by a processor, causes the processor to implement the steps of the method described above.
The embodiment of the application provides an ultrasonic imaging method and ultrasonic imaging equipment, wherein the ultrasonic imaging method comprises the following steps: b mode ultrasonic images are obtained in the B mode, and a target section of target tissue is determined according to the B mode ultrasonic images; starting a contrast imaging mode, transmitting first ultrasonic waves to a target tissue, obtaining a plurality of first ultrasonic images according to echoes of the first ultrasonic waves, determining a plurality of reference ultrasonic images in the plurality of first ultrasonic images, wherein a tangent plane corresponding to the plurality of reference ultrasonic images is a target tangent plane; transmitting a second ultrasonic wave to the target tissue, and obtaining a second ultrasonic image according to the echo of the second ultrasonic wave, wherein when the second ultrasonic wave is transmitted to the target tissue, the target tissue contains contrast microbubbles; determining a similarity between the second ultrasound image and the plurality of reference ultrasound images; determining the fixation degree of the second ultrasonic image according to the similarity between the second ultrasonic image and the plurality of reference ultrasonic images, wherein the fixation degree is used for representing the proximity degree between the tangent plane corresponding to the second ultrasonic image and the target tangent plane; and displaying the second ultrasonic image and outputting the fixation degree of the second ultrasonic image. The method comprises the steps of determining a plurality of reference ultrasonic images, determining the fixation degree of a second ultrasonic image according to the similarity between the second ultrasonic image and the plurality of reference ultrasonic images, wherein the fixation degree can represent the proximity degree between the tangent plane corresponding to the second ultrasonic image and the target tangent plane, so that the effectiveness of the second ultrasonic image is evaluated based on the fixation degree, and the influence of factors such as respiratory motion of a patient or probe shake on the effectiveness evaluation can be reduced or eliminated.
It is to be understood that both the foregoing general description and the following detailed description are exemplary and explanatory only and are not restrictive of the disclosure of embodiments of the application.
Drawings
In order to more clearly illustrate the technical solutions of the embodiments of the present application, the drawings required for the description of the embodiments will be briefly described below, and it is obvious that the drawings in the following description are some embodiments of the present application, and other drawings may be obtained according to these drawings without inventive effort for a person skilled in the art.
FIG. 1 is a schematic flow chart of an ultrasound imaging method according to an embodiment of the present application;
FIG. 2 is a schematic block diagram of an ultrasound imaging device in one embodiment;
FIG. 3 is a flow chart of an ultrasound imaging method according to another embodiment of the present application;
fig. 4 is a flow chart of an ultrasound imaging method according to another embodiment of the present application.
Detailed Description
The following description of the embodiments of the present application will be made clearly and fully with reference to the accompanying drawings, in which it is evident that the embodiments described are some, but not all embodiments of the application. All other embodiments, which can be made by those skilled in the art based on the embodiments of the application without making any inventive effort, are intended to be within the scope of the application.
The flow diagrams depicted in the figures are merely illustrative and not necessarily all of the elements and operations/steps are included or performed in the order described. For example, some operations/steps may be further divided, combined, or partially combined, so that the order of actual execution may be changed according to actual situations.
Some embodiments of the present application are described in detail below with reference to the accompanying drawings. The following embodiments and features of the embodiments may be combined with each other without conflict.
Referring to fig. 1, fig. 1 is a flow chart of an ultrasonic imaging method according to an embodiment of the application. The method can be applied to ultrasonic imaging equipment and is used for displaying the degree of fixation for representing the proximity degree between the tangent plane corresponding to the ultrasonic image and the target tangent plane when the ultrasonic image is displayed.
Fig. 2 is a schematic block diagram of an ultrasound imaging apparatus according to an embodiment of the present application. The ultrasound imaging device 10 may include a probe 100, a transmit circuit 101, a transmit/receive select switch 102, a receive circuit 103, a beam combining circuit 104, a processor 105, and a display 106. The transmitting circuit 101 may excite the probe 100 to transmit ultrasonic waves to the target tissue; the receiving circuit 103 may control the probe 100 to receive the ultrasonic echo returned from the target tissue, thereby obtaining an ultrasonic echo signal; the ultrasonic echo signal is subjected to beam forming processing by a beam forming circuit 104 and then sent to a processor 105. The processor 105 may process the ultrasound echo signals to obtain an ultrasound image or other data of the target tissue. The ultrasound images obtained by the processor 105 may be stored in the memory 107. These ultrasound images may be displayed on a display 106.
For example, an ultrasound imaging device includes one or more processors 105, the one or more processors 105 working individually or together to perform the steps of the ultrasound imaging method of embodiments of the present application.
The processor 105 may be configured to execute a computer program stored in the memory 107, and when executing the computer program, implement the steps of any of the ultrasound imaging methods provided by the embodiments of the present application.
As shown in fig. 1, the ultrasonic imaging method according to the embodiment of the present application includes steps S110 to S160.
S110, acquiring a B-mode ultrasonic image in a B-mode, and determining a target section of a target tissue according to the B-mode ultrasonic image.
In some embodiments, the default inspection mode of the ultrasound imaging apparatus is the B-mode, and in other embodiments, the inspection mode may be determined to be the B-mode according to a mode setting operation by a user.
Some acoustic interfaces exist in the human body, the acoustic interfaces carry out echo reflection on ultrasonic waves emitted by the probe, the back reflection or scattering signals are received by the probe so as to obtain ultrasonic echo signals, and B-mode ultrasonic images can be obtained through imaging according to the ultrasonic echo signals. The B-mode ultrasonic image can clearly display various sectional images of various organs and surrounding organs, and the image is rich in sense of reality and is close to the anatomical real structure, so that the early diagnosis can be definitely carried out by applying the ultrasonic.
In some embodiments, the target section may be determined from a target tissue in the B-mode ultrasound image. For example, when the target tissue comprises a heart, determining a target section of the target tissue comprises at least one of: a parasternal left ventricular long axis section, a parasternal right ventricular inflow channel section, a parasternal aortic short axis section, a left ventricular short axis section (mitral valve level, papillary muscle level, apex level).
In some embodiments, the B-mode ultrasound image may be displayed by a display, and a section identifier of the candidate region may also be displayed, and the target section may be determined according to the section identifier selected by the user. For example, the target section to be acquired may be confirmed in the B mode according to the habit of the doctor.
S120, starting a contrast imaging mode, transmitting first ultrasonic waves to the target tissue, obtaining a plurality of first ultrasonic images according to echoes of the first ultrasonic waves, and determining a plurality of reference ultrasonic images in the plurality of first ultrasonic images, wherein the tangential planes corresponding to the plurality of reference ultrasonic images are the target tangential planes.
Contrast imaging, otherwise known as ultrasound contrast (ultrasonic contrast) imaging, is a technique that uses contrast agents to enhance the backscattered echoes, significantly improving the resolution, sensitivity and specificity of ultrasound diagnosis. In contrast imaging mode, it is generally necessary to push an ultrasound contrast agent into a human body, where the ultrasound contrast agent is a diagnostic agent capable of significantly enhancing a blood flow signal and improving contrast of perfusion tissue, and ultrasound contrast imaging uses its characteristic contrast to enhance the blood flow signal and reflect the blood flow perfusion state of regional tissue in real time, so as to effectively distinguish lesions from normal tissue, and detect hemodynamic parameters. With the improvement of instrument performance and the appearance of novel acoustic contrast agents, ultrasonic contrast can effectively enhance two-dimensional ultrasonic images and blood flow Doppler signals of parenchymal organs such as cardiac muscle, liver, kidney, brain and the like, reflect and observe the blood flow perfusion condition of normal tissues and pathological tissues, and become an important and promising development direction of ultrasonic diagnosis.
Whether B-mode imaging or ultrasound contrast imaging relies on the imaging technique and clinical experience of the examining physician, the acquisition of high quality ultrasound images not only requires reliable ultrasound probe performance, but also presents challenges to the physician's expertise. In clinical diagnosis and treatment, due to respiratory motion of a patient or probe shake and the like, an imaging section often cannot keep the same position in the process of radiography, and the interference caused by section or position change can influence the observation of doctors and the effectiveness of video data.
In some embodiments, the first ultrasound image comprises a first tissue image, or the first tissue image and the first contrast image. I.e. the first ultrasound wave may be used for generating the first tissue image, or for generating both tissue images and contrast images.
In some embodiments, the plurality of reference images includes all or part of the images in the first tissue image in the tissue imaging mode.
In some embodiments, the plurality of reference images includes all or part of the images in the first tissue image in the contrast imaging mode.
The embodiment of the application can determine a plurality of reference ultrasonic images, and the positions of the target tissues in the plurality of reference ultrasonic images are generally different because the transmission moments of the first ultrasonic waves corresponding to the plurality of reference ultrasonic images are different. By evaluating the effectiveness of the ultrasound image based on the plurality of reference ultrasound images, the impact of factors such as respiratory motion of the patient or probe jitter on the effectiveness evaluation can be reduced or eliminated.
In some embodiments, the plurality of first ultrasound images are ultrasound images acquired over a period of time; illustratively, the plurality of reference ultrasound images are ultrasound images acquired at different times over a period of time; the positions of the target tissue in the obtained plurality of reference ultrasound images are different due to respiratory motion of the patient or probe jitter. The certain duration may be a preset duration, or may be a duration determined based on a user operation, for example, an image acquisition end instruction for triggering the first ultrasound image based on the user operation.
Illustratively, the predetermined time period is greater than or equal to the duration of one respiratory cycle. The duration of the respiratory cycle may be a preset duration, or may be a respiratory cycle of the patient detected. For example, the plurality of reference ultrasound images are first ultrasound images acquired at a plurality of preset time points of the respiratory cycle.
Illustratively, after entering the contrast imaging mode, the ultrasound imaging device is controlled to acquire a plurality of reference ultrasound images within 1 to 2 respiratory cycles according to the periodic law of respiratory motion of the patient, wherein the plurality of reference ultrasound images can be used as a reference slice reference image set.
In some embodiments, the determining a plurality of reference ultrasound images in the plurality of first ultrasound images includes: and displaying a plurality of first ultrasonic images, and determining a plurality of reference ultrasonic images in the plurality of first ultrasonic images according to image acquisition control operation of a user.
Alternatively, a prompt message may be output to prompt the user to control the ultrasound imaging device to generate a plurality of the first ultrasound images in a duration greater than or equal to one respiratory cycle, and determine a plurality of reference ultrasound images in the plurality of first ultrasound images.
Illustratively, the determining a plurality of reference ultrasound images in the plurality of first ultrasound images further includes: and outputting first prompt information, wherein the first prompt information is used for prompting a user to perform the image acquisition control operation according to the displacement of the target tissue in the first ultrasonic image.
For example, when the reference ultrasound image is acquired, the user preferably has a certain ultrasound imaging experience, and can accurately observe the tissue characteristics of the first ultrasound image and grasp the periodic displacement of the target tissue due to respiratory motion, for example, acquire the reference ultrasound image at a plurality of preset time points in the respiratory cycle. After selecting the target section, the user may select the start and end time points for acquiring the reference ultrasound image based on the displacement change of the target tissue while observing the tissue image in the contrast imaging mode, such as the tissue characteristics of the first ultrasound image. The reference slice baseline image set should include a plurality of reference ultrasound images that vary at least one complete continuous cycle.
In some embodiments, the determining a plurality of reference ultrasound images in the plurality of first ultrasound images includes: and carrying out image recognition on the plurality of first ultrasonic images, and determining a plurality of reference ultrasonic images according to image recognition results. For example, the ultrasound imaging device may determine a plurality of reference ultrasound images from among the plurality of first ultrasound images by performing image recognition on the first ultrasound images; for example, a displacement of the target tissue in the first ultrasound image may be identified, and a plurality of reference ultrasound images may be determined from the displacement of the target tissue in the first ultrasound image, wherein the positions of the target tissue in at least two of the reference ultrasound images are different.
S130, transmitting a second ultrasonic wave to the target tissue, and obtaining a second ultrasonic image according to the echo of the second ultrasonic wave, wherein when the second ultrasonic wave is transmitted to the target tissue, the target tissue contains contrast microbubbles.
Specifically, a bolus of ultrasound contrast agent has been made at the time the second ultrasound image was acquired. In some embodiments, one or more bolus injections of ultrasound contrast agent may be made; wherein, the first bolus of the ultrasound contrast agent may be performed after determining the plurality of reference ultrasound images in step S120, or may be performed before initiating the contrast imaging mode in step S120; after a period of ultrasound contrast agent bolus, contrast microbubbles of the ultrasound contrast agent enter the target tissue.
In some embodiments, the second ultrasound image comprises a second contrast image and a second tissue image.
The plurality of first ultrasound images are ultrasound images acquired within a preset time period, the second ultrasound images are ultrasound images acquired after the preset time period, and the target tissue contains contrast microbubbles in the second ultrasound image acquisition process, for example, the contrast microbubbles of an ultrasound contrast agent enter the target tissue after the preset time period.
In order to ensure that contrast microbubbles are present in the target tissue continuously throughout the imaging period of the second ultrasound image, the acoustic field mechanical index (MECHANICAL INDEX, MI) of the second ultrasound waves emitted towards the target tissue is low and/or the emission frequency is low, to prevent rapid rupture of ultrasound contrast agent under the influence of a high mechanical index acoustic field, for example, the acoustic field mechanical index of the second ultrasound waves emitted towards the target tissue is controlled to be around 0.1.
In some embodiments, the second ultrasound image comprises a contrast image and a tissue image. Illustratively, when acquiring the second ultrasound image, the ultrasound imaging device performs duplex imaging or triplex imaging, e.g. the second ultrasound transmitted to the target tissue during duplex imaging comprises a first ultrasound sequence and a second ultrasound sequence, wherein echoes of the first ultrasound sequence are used for generating the contrast image and echoes of the second ultrasound are used for generating the tissue image. The contrast image and the tissue image are respectively obtained by simultaneously carrying out contrast imaging (common frame rate contrast imaging, high frame rate contrast imaging and super-resolution contrast imaging) and non-contrast imaging combination (pulse Doppler imaging, color Doppler imaging and the like), and the blood flow condition of the large blood vessels in the scanning section can be observed through the tissue image while the perfusion of the contrast agent microbubbles in the tissue capillaries can be observed through the contrast image.
In some embodiments, the reference ultrasound image comprises an image of tissue in the first ultrasound image.
S140, determining the similarity between the second ultrasonic image and a plurality of reference ultrasonic images.
In some embodiments, the determining the similarity between the second ultrasound image and the plurality of reference ultrasound images comprises: a similarity between the second tissue image and the plurality of tissue reference images is determined. Wherein the plurality of reference ultrasound images includes a plurality of tissue reference images and the second ultrasound image includes a second tissue image and a second contrast image. Wherein the plurality of tissue reference images are all or part of the first tissue image, and the method for determining the tissue reference images from the first tissue image refers to the method for determining the reference images from the first ultrasound image.
In some embodiments, the determining the similarity between the second ultrasound image and the plurality of reference ultrasound images comprises: a similarity between a tissue image in the second ultrasound image and the plurality of reference ultrasound images is determined. Illustratively, the reference ultrasound image includes a tissue image, and a similarity between the tissue image in the second ultrasound image and the tissue image in the reference ultrasound image is determined.
By determining the similarity between the tissue image in the second ultrasound image and the plurality of reference ultrasound images, the similarity may be enabled to represent the similarity between the target tissue in the second ultrasound image and the target tissue in the plurality of reference ultrasound images, such as the similarity between shape, size and/or position.
In some embodiments, the similarity between the second ultrasound image and the plurality of reference ultrasound images may be determined according to at least one of the following similarity determinations: normalized cross-correlation algorithm, sine and cosine similarity method, singular value decomposition method, eigenvalue method, matrix decomposition method, and deep learning method.
Optionally, the determining the similarity between the second ultrasound image and the reference ultrasound image includes: determining a target similarity determination method in a plurality of preset similarity determination methods according to user operation, or acquiring a preset target similarity determination method, such as a normalized cross-correlation algorithm; and determining a similarity between the second ultrasound image and the reference ultrasound image based on the target similarity determination. For example, a plurality of similarity determination methods may be provided for selection by a user, or a preset target similarity determination method may be selected under a default configuration, such as a sample-based cross-correlation algorithm as the target similarity determination method.
For example, the similarity between the second ultrasound image and the reference ultrasound image may be determined based on a normalized cross-correlation algorithm. The normalized cross-correlation algorithm is a classical statistical matching algorithm, and the degree of matching can be determined by calculating the cross-correlation values of the reference ultrasound image and the second ultrasound image.
For example, in order to reduce the amount of calculation when determining the similarity and improve the calculation efficiency, the reference ultrasound image and the second ultrasound image may be subjected to preset processing to reduce the data amount of the images, and the similarity between the images after the preset processing may be determined. For example, the determining the similarity between the second ultrasound image and a plurality of the reference ultrasound images includes: performing preset processing on the reference ultrasonic image to obtain a first target image, wherein the data size of the first target image is smaller than that of the reference ultrasonic image; the second ultrasonic image is subjected to the preset processing to obtain a second target image, and the data size of the second target image is smaller than that of the second ultrasonic image; and determining the similarity between the second target image and the first target image, and determining the similarity between the second ultrasonic image and the reference ultrasonic image according to the similarity between the second target image and the first target image.
For example, the preset process includes at least one of: image sampling processing, region of interest identification processing, and image graying processing. The data volume of the image may be reduced and key information in the image, such as the shape, size and/or location of the target tissue, may also be maintained.
For example, in view of the fact that the ultrasound imaging device should reduce the overall engineering amount of the algorithm and increase the processing rate as much as possible in a specific implementation, the data source should choose the back-end processing data as much as possible, reduce the calculation amount and the calculation steps, and determine the similarity between the second ultrasound image and the plurality of reference ultrasound images based on the sampled normalized cross-correlation algorithm. In order to reduce the calculation amount of the similarity calculation process, the data amount of the image may be reduced by sampling to reduce the resolution.
Firstly, sampling processing is carried out on a reference ultrasonic image, for example, the sampling proportion of the transverse direction and the longitudinal direction can be adjusted through parameters or a method of interval sampling is adopted, the data volume is reduced as much as possible on the premise of ensuring that the image is not distorted, and then the same sampling processing is carried out on a second ultrasonic image acquired in real time. For example, the first target image and the second target image after sampling are m×n in size, and the normalized cross-correlation coefficient between the first target image and the second target image can be obtained by calculating the correlation function of equation (1):
Wherein, Is the average of the first target image P (x, y) and the second target image Q (x, y); the value range of the normalized cross-correlation coefficient gamma, namely the scale of the correlation function is [ -1,1], and the closer the normalized cross-correlation coefficient gamma is to 1, the stronger the correlation between the first target image and the second target image is, and the greater the similarity is.
Optionally, the calculation amount can be further reduced by converting the two-dimensional correlation operation in the formula (1) into the one-dimensional correlation calculation. Specifically, the first target image P (x, y) and the second target image Q (x, y) are averaged by column vectors, and the average value of the column vectors is taken as a one-dimensional row vector and is recorded as:
Then, equation (1) becomes
Wherein,Is the average of u (y) and v (y).
And S150, determining the fixation degree of the second ultrasonic image according to the similarity between the second ultrasonic image and the plurality of reference ultrasonic images, wherein the fixation degree is used for representing the proximity degree between the tangent plane corresponding to the second ultrasonic image and the target tangent plane.
In some embodiments, the degree of fixation of the second ultrasound image is positively correlated with the degree of similarity between the second ultrasound image and the plurality of reference ultrasound images, i.e., the greater the degree of similarity between the second ultrasound image and the plurality of reference ultrasound images, the greater the degree of fixation of the second ultrasound image.
Illustratively, the determining the degree of fixation of the second ultrasound image according to the degree of similarity between the second ultrasound image and the plurality of reference ultrasound images includes: determining the maximum value of the similarity corresponding to a plurality of reference ultrasonic images according to the similarity between the second ultrasonic image and each reference ultrasonic image; determining the fixation degree of the second ultrasonic image according to the maximum value of the similarity corresponding to the plurality of reference ultrasonic images, wherein the fixation degree of the second ultrasonic image is positively correlated with the maximum value of the similarity; or carrying out weighted summation on the similarity between the second ultrasonic image and each reference ultrasonic image, and determining the fixation degree of the second ultrasonic image according to the weighted summation result, wherein the fixation degree of the second ultrasonic image is positively correlated with the weighted summation result.
In some embodiments, the degree of fixation may be the degree of similarity itself.
Determining the degree of fixation of the second ultrasound image according to the similarity between the second ultrasound image and the plurality of reference ultrasound images may enable the degree of fixation to be represented by the similarity between tissue characteristics, such as shape, size, and position, of the target tissue when the second ultrasound image and the reference ultrasound images are acquired, so that the degree of fixation may be used to represent the degree of proximity between the tangent plane to which the second ultrasound image corresponds and the target tangent plane.
Illustratively, the greater the degree of fixation of the second ultrasound image, the closer the corresponding tangent plane of the second ultrasound image is to the target tangent plane, and the higher the quality of the second ultrasound image; the smaller the fixation degree of the second ultrasonic image is, the larger the deviation between the tangent plane corresponding to the second ultrasonic image and the target tangent plane is, and the lower the quality of the second ultrasonic image is.
Illustratively, when the similarity between the second ultrasound image and the plurality of reference ultrasound images is between 0.9 and 1.0, determining that the degree of fixation of the second ultrasound image is five stars, which means that the tangent plane corresponding to the second ultrasound image is fixed with the target tangent plane, and if the tangent plane corresponding to the second ultrasound image coincides with the target tangent plane; when the similarity between the second ultrasonic image and the plurality of reference ultrasonic images is between 0.8 and 0.9, determining that the degree of fixation of the second ultrasonic image is four stars, wherein the tangent plane corresponding to the second ultrasonic image is very close to the target tangent plane and is only slightly deviated; when the similarity between the second ultrasonic image and the plurality of reference ultrasonic images is between 0.6 and 0.8, determining that the degree of fixation of the second ultrasonic image is samsung, and indicating that the tangent plane corresponding to the second ultrasonic image is relatively close to the target tangent plane and has partial offset; when the similarity between the second ultrasonic image and the plurality of reference ultrasonic images is between 0.2 and 0.6, determining that the degree of fixation of the second ultrasonic image is two stars, wherein the fact that the tangent plane corresponding to the second ultrasonic image is not close to the target tangent plane is greatly offset; and when the similarity between the second ultrasonic image and the plurality of reference ultrasonic images is between 0 and 0.2, determining the fixation degree of the second ultrasonic image as one star, wherein the tangent plane corresponding to the second ultrasonic image is not close to the target tangent plane, namely completely offset. Of course, the scope threshold of the similarity may be different, for example, different similarity determination methods may determine different scope thresholds; there may be more or less levels of fixity, such as being divided into ten levels.
Alternatively, by determining the appropriate range threshold and/or level of immobilization, it is also possible that image changes introduced before and after ultrasound contrast agent perfusion do not significantly affect the immobilization assessment when there is only respiratory motion with the immobilization of the slice.
And S160, displaying the second ultrasonic image and outputting the fixation degree of the second ultrasonic image.
In some embodiments, displaying the second ultrasound image by a display; the outputting the degree of fixation of the second ultrasound image includes: outputting the degree of fixation of the second ultrasound image by at least one of: sound, text, color, graphics, and feel. The degree of fixation may be output in the form of sound, for example, through a speaker or a buzzer, or may be output through indicator lamps of different positions and/or different colors, or may be output through a display, for example, when the display displays the second ultrasound image, the degree of fixation of the text and/or the graphic is displayed at a preset position of the second ultrasound image, or the degree of fixation of the corresponding text and/or graphic is output at a pop-up window, which is not limited to this, of course.
For example, in the contrast imaging process, the user may determine the state of the section corresponding to the second ultrasound image through the degree of fixation of the second ultrasound image, and make corresponding control or adjustment. For example, when the degree of fixation of the second ultrasonic image is larger, the second ultrasonic image can be determined to be a target image meeting the quality requirement, and the ultrasonic imaging device can be controlled to store the second ultrasonic image, namely, a mapping.
In some embodiments, the ultrasound image comprises a plurality of second ultrasound images. For example, the second ultrasound image may be periodically acquired according to a preset period.
Illustratively, said determining a similarity between said second ultrasound image and a plurality of said reference ultrasound images comprises: determining a similarity between a plurality of said second ultrasound images and said plurality of said reference ultrasound images; the determining the fixing degree of the second ultrasonic image according to the similarity between the second ultrasonic image and the reference ultrasonic images comprises the following steps: determining a degree of fixation of the plurality of second ultrasound images based on the degree of similarity between the plurality of second ultrasound images and the plurality of reference ultrasound images; the displaying the second ultrasonic image and outputting the fixation degree of the second ultrasonic image includes: and displaying a plurality of the second ultrasonic images and outputting the fixation degree of the second ultrasonic images.
For example, the degree of fixation of the second ultrasound images of the fixed time may be determined at fixed time intervals with respect to the degree of similarity between the plurality of second ultrasound images acquired according to the fixed time and the plurality of reference ultrasound images; that is, a set of a plurality of second ultrasound images may determine a degree of fixation that may be used to indicate how close the corresponding section of the plurality of second ultrasound images is to the target section.
For example, the similarity and the degree of fixation between each second ultrasound image and a plurality of the reference ultrasound images may be determined.
Optionally, the method further comprises: when the fixation degree of the second ultrasonic image is smaller than or equal to a preset low-quality threshold value, determining scanning angle deviation and deflection angle deviation of an ultrasonic probe corresponding to the second ultrasonic image according to the second ultrasonic image and at least one reference ultrasonic image; and outputting the scanning angle deviation and the deflection angle deviation of the ultrasonic probe corresponding to the second ultrasonic image and/or outputting the scanning guide information corresponding to the scanning angle deviation and the deflection angle deviation when the second ultrasonic image is displayed. By outputting the prompt information of the scanning angle deviation and the deflection angle deviation of the ultrasonic probe when the degree of proximity between the tangent plane of the second ultrasonic image and the target tangent plane is smaller, namely the deviation is larger, the user can be helped to judge the difference between the tangent plane of the second ultrasonic image and the target tangent plane corresponding to the expected image result, for example, the doctor can adjust the position and the angle of the probe according to the scanning guide information to enable the tangent plane of the second ultrasonic image to gradually approach the target tangent plane, and when the degree of proximity of the second ultrasonic image is larger than the low quality threshold, the degree of proximity between the tangent plane corresponding to the second ultrasonic image and the target tangent plane is output to prompt the quality of the current second ultrasonic image of the user.
The ultrasonic imaging method provided by the embodiment of the application comprises the following steps: b mode ultrasonic images are obtained in a B mode, and a target section of target tissue is determined according to the B mode ultrasonic images; starting a contrast imaging mode, transmitting first ultrasonic waves to the target tissue, obtaining a plurality of first ultrasonic images according to echoes of the first ultrasonic waves, and determining a plurality of reference ultrasonic images in the plurality of first ultrasonic images, wherein the tangential planes corresponding to the plurality of reference ultrasonic images are the target tangential planes; transmitting a second ultrasonic wave to the target tissue, and obtaining a second ultrasonic image according to the echo of the second ultrasonic wave, wherein when the second ultrasonic wave is transmitted to the target tissue, the target tissue contains contrast microbubbles; determining a similarity between the second ultrasound image and a plurality of the reference ultrasound images; determining the fixation degree of the second ultrasonic image according to the similarity between the second ultrasonic image and the plurality of reference ultrasonic images, wherein the fixation degree is used for representing the proximity degree between the tangent plane corresponding to the second ultrasonic image and the target tangent plane; and displaying the second ultrasonic image and outputting the fixation degree of the second ultrasonic image. The method comprises the steps of determining a plurality of reference ultrasonic images, and determining the fixation degree of a second ultrasonic image according to the similarity between the second ultrasonic image and the plurality of reference ultrasonic images, wherein the fixation degree can represent the proximity degree between the tangent plane corresponding to the second ultrasonic image and the target tangent plane, so that the effectiveness of the second ultrasonic image is evaluated based on the fixation degree, and the influence of factors such as respiratory motion of a patient or probe shake on the effectiveness evaluation can be reduced or eliminated.
For example, when the plurality of reference ultrasound images are acquired, the target tissue in the plurality of reference ultrasound images may be located at different positions, such as a, b, c, d, respectively, due to respiratory motion of the patient or probe jitter; when the probe bit displacement and/or the direction does not deviate obviously, the position of the target tissue in the second ultrasonic image is approximately close to the position of the target tissue in at least one reference ultrasonic image when the second ultrasonic image is acquired, for example, the position of the target tissue in the second ultrasonic image is b at one moment in the breathing cycle of a patient, and the position of the target tissue in the second ultrasonic image is c at the other moment; in this case, the degree of fixation and the effectiveness of the second ultrasound image can be accurately evaluated without being affected by the respiratory motion of the patient or the probe shake.
Compared with the method that a standardized section acquired and stored in advance is used as a reference basis, the method and the device for determining the multiple reference ultrasonic images in the first ultrasonic image, the error caused by different individual differences and the tissue structure difference between benign cases and malignant cases are avoided, evaluation is more accurate, guiding effect is better, and the use scene is wider.
Referring to fig. 3 in combination with the foregoing embodiments, fig. 3 is a flow chart of an ultrasonic imaging method according to another embodiment of the present application.
As shown in fig. 3, the ultrasonic imaging method according to the embodiment of the present application includes steps S210 to S250.
And S210, transmitting ultrasonic waves to target tissues, and obtaining ultrasonic images based on the echoes of the ultrasonic waves.
In some embodiments, the transmitting ultrasound waves to the target tissue, deriving an ultrasound image based on echoes of the ultrasound waves, comprises: in a contrast imaging mode, transmitting ultrasonic waves to target tissue, and obtaining an ultrasonic image based on echo of the ultrasonic waves, wherein the ultrasonic image comprises a first ultrasonic image of the target tissue and a second ultrasonic image of the target tissue, and the acquisition time of the first ultrasonic image is earlier than that of the second ultrasonic image. I.e. the first ultrasound image and the second ultrasound image may each be an ultrasound image acquired in the contrast imaging mode.
In some embodiments, the first ultrasound image is an ultrasound image acquired within a preset time period. Illustratively, the plurality of reference ultrasound images are ultrasound images acquired at different times within a preset time period; the positions of the target tissue in the obtained plurality of reference ultrasound images are different due to respiratory motion of the patient or probe jitter. Illustratively, the predetermined time period is greater than or equal to the duration of one respiratory cycle. The duration of the respiratory cycle may be a preset duration, or may be a respiratory cycle of the patient detected. For example, the plurality of reference ultrasound images are first ultrasound images acquired at a plurality of preset time points of the respiratory cycle.
In other embodiments, the transmitting ultrasound waves to the target tissue, obtaining an ultrasound image based on echoes of the ultrasound waves, comprises: transmitting ultrasonic waves to a target tissue in a first imaging mode within the preset time period, and obtaining a first ultrasonic image of the target tissue based on echo of the ultrasonic waves; and after the preset time period, transmitting ultrasonic waves to target tissue in a second imaging mode, and obtaining a second ultrasonic image of the target tissue based on the echo of the ultrasonic waves. I.e. the imaging mode of the second ultrasound image may be different from the imaging mode of the first ultrasound image.
Illustratively, the sound field mechanical index when ultrasound is emitted in the second imaging mode is lower than the sound field mechanical index when ultrasound is emitted in the first imaging mode; and/or the emission frequency when the ultrasonic wave is emitted in the second imaging mode is lower than the emission frequency when the ultrasonic wave is emitted in the first imaging mode. For example, the second imaging mode is a contrast imaging mode and the first imaging mode is a B mode. The second ultrasound waves emitted to the target tissue have a lower sound field mechanical index (MECHANICAL INDEX, MI) and/or a lower emission frequency to prevent rapid rupture of the ultrasound contrast agent under the influence of the high mechanical index sound field, which ensures that contrast microbubbles persist in the target tissue throughout the imaging period of the second ultrasound image. The first ultrasonic image acquired in the first imaging mode has better image performance, clearer tissue characteristics and better referential.
S220, determining a plurality of reference ultrasonic images in a plurality of first ultrasonic images, wherein the first ultrasonic images are ultrasonic images acquired within a preset time period, and the plurality of reference ultrasonic images correspond to the target section of the target tissue.
S230, determining similarity between a second ultrasonic image and a plurality of reference ultrasonic images, wherein the second ultrasonic image is an ultrasonic image acquired after the preset time period, and the target tissue contains contrast microbubbles in the second ultrasonic image acquisition process.
S240, determining the fixation degree of the second ultrasonic image according to the similarity between the second ultrasonic image and the plurality of reference ultrasonic images, wherein the fixation degree is used for representing the proximity degree between the tangent plane corresponding to the second ultrasonic image and the target tangent plane.
S250, displaying the second ultrasonic image and outputting the fixation degree of the second ultrasonic image.
The steps S220 to S250 may refer to the description of the corresponding embodiment of fig. 1, and are not described herein.
The specific principle and implementation manner of the ultrasonic imaging method provided by the embodiment of the application are similar to those of the ultrasonic imaging method of the previous embodiment, and are not repeated here.
Referring to fig. 4 in combination with the foregoing embodiments, fig. 4 is a flow chart of an ultrasonic imaging method according to another embodiment of the present application.
As shown in fig. 4, the ultrasonic imaging method according to the embodiment of the present application includes steps S310 to S340.
S310, acquiring a plurality of reference ultrasonic images of target tissue, wherein the plurality of reference ultrasonic images correspond to target section surfaces of the target tissue, and the positions of the target tissue in the plurality of reference ultrasonic images are different.
Illustratively, the plurality of reference ultrasound images are ultrasound images acquired at different times in a tissue imaging mode or in a contrast imaging mode.
S320, acquiring a second ultrasonic image of the target tissue, wherein the target tissue contains contrast microbubbles in the second ultrasonic image acquisition process.
S330, determining the similarity between the second ultrasonic image and a plurality of reference ultrasonic images.
S340, determining the fixation degree of the second ultrasonic image according to the similarity between the second ultrasonic image and the plurality of reference ultrasonic images, wherein the fixation degree is used for representing the proximity degree between the tangent plane corresponding to the second ultrasonic image and the target tangent plane.
The specific principle and implementation manner of the ultrasonic imaging method provided by the embodiment of the application are similar to those of the ultrasonic imaging method of the previous embodiment, and are not repeated here.
Referring to fig. 2 in conjunction with the above examples, fig. 2 is a schematic block diagram of ultrasound imaging apparatus 10 in one embodiment.
As shown in fig. 2, the ultrasound imaging apparatus 10 includes at least a probe 100; a transmitting circuit 101, the transmitting circuit 101 exciting the probe 100 to transmit ultrasonic waves to a target tissue; a receiving circuit 103, wherein the receiving circuit 103 controls the probe 100 to receive ultrasonic echo so as to obtain an ultrasonic echo signal; and a display 103 for providing a display interface.
The ultrasound imaging device 10 processes the ultrasound echo signals to obtain an ultrasound image of the target tissue. For example, referring to fig. 2, the beam forming circuit 104 in the ultrasonic imaging apparatus 10 performs beam forming processing on the ultrasonic echo signals, and then sends the processed ultrasonic echo signals to the processor 105. The processor 105 may process the ultrasound echo signals to obtain an ultrasound image of the target tissue.
The ultrasound imaging apparatus 10 is also adapted to perform the steps of the ultrasound imaging method described previously,
For example, the ultrasound imaging apparatus includes one or more processors 105, the one or more processors 105 working individually or together to perform the steps of the ultrasound imaging method.
The processor 105 may be configured to execute a computer program stored in the memory 107, and when executing the computer program, implement the steps of any of the ultrasound imaging methods provided by the embodiments of the present application.
The specific principle and implementation manner of the ultrasonic imaging device provided by the embodiment of the present application are similar to those of the ultrasonic imaging method of the foregoing embodiment, and are not repeated here.
The embodiment of the present application also provides a computer readable storage medium storing a computer program, where the computer program when executed by a processor causes the processor to implement the steps of the ultrasound imaging method provided in the above embodiment.
The computer readable storage medium may be an internal storage unit of the ultrasound imaging device according to any of the foregoing embodiments, for example, a hard disk or a memory of the ultrasound imaging device. The computer readable storage medium may also be an external storage device of the ultrasound imaging device, such as a plug-in hard disk, a smart memory card (SMART MEDIA CARD, SMC), a Secure Digital (SD) card, a flash memory card (FLASH CARD), etc. that are provided on the ultrasound imaging device.
It is to be understood that the terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the application.
It should also be understood that the term "and/or" as used in the present application and the appended claims refers to any and all possible combinations of one or more of the associated listed items, and includes such combinations.
While the application has been described with reference to certain preferred embodiments, it will be understood by those skilled in the art that various changes and substitutions of equivalents may be made and equivalents will be apparent to those skilled in the art without departing from the scope of the application. Therefore, the protection scope of the application is subject to the protection scope of the claims.
Claims (18)
1. An ultrasound imaging method, comprising:
B mode ultrasonic images are obtained in a B mode, and a target section of target tissue is determined according to the B mode ultrasonic images;
Starting a contrast imaging mode, transmitting first ultrasonic waves to the target tissue, obtaining a plurality of first ultrasonic images according to echoes of the first ultrasonic waves, and determining a plurality of reference ultrasonic images in the plurality of first ultrasonic images, wherein the tangential planes corresponding to the plurality of reference ultrasonic images are the target tangential planes;
transmitting a second ultrasonic wave to the target tissue, and obtaining a second ultrasonic image according to the echo of the second ultrasonic wave, wherein when the second ultrasonic wave is transmitted to the target tissue, the target tissue contains contrast microbubbles;
Determining a similarity between the second ultrasound image and a plurality of the reference ultrasound images;
Determining the fixation degree of the second ultrasonic image according to the similarity between the second ultrasonic image and the plurality of reference ultrasonic images, wherein the fixation degree is used for representing the proximity degree between the tangent plane corresponding to the second ultrasonic image and the target tangent plane;
and displaying the second ultrasonic image and outputting the fixation degree of the second ultrasonic image.
2. An ultrasound imaging method, comprising:
Acquiring a plurality of reference ultrasonic images of target tissue, wherein the plurality of reference ultrasonic images correspond to target section surfaces of the target tissue, and the positions of the target tissue in the plurality of reference ultrasonic images are different;
acquiring a second ultrasonic image of the target tissue, wherein the target tissue contains contrast microbubbles in the second ultrasonic image acquisition process;
Determining a similarity between the second ultrasound image and a plurality of the reference ultrasound images;
And determining the fixation degree of the second ultrasonic image according to the similarity between the second ultrasonic image and the plurality of reference ultrasonic images, wherein the fixation degree is used for representing the proximity degree between the tangent plane corresponding to the second ultrasonic image and the target tangent plane.
3. An ultrasound imaging method, comprising:
transmitting ultrasonic waves to a target tissue, and obtaining an ultrasonic image based on echo of the ultrasonic waves;
determining a plurality of reference ultrasonic images in a plurality of first ultrasonic images, wherein the first ultrasonic images are ultrasonic images acquired within a preset time period, and the plurality of reference ultrasonic images correspond to a target section of the target tissue;
Determining the similarity between a second ultrasonic image and a plurality of reference ultrasonic images, wherein the second ultrasonic image is an ultrasonic image acquired after the preset time period, and the target tissue contains contrast microbubbles in the second ultrasonic image acquisition process;
Determining the fixation degree of the second ultrasonic image according to the similarity between the second ultrasonic image and the plurality of reference ultrasonic images, wherein the fixation degree is used for representing the proximity degree between the tangent plane corresponding to the second ultrasonic image and the target tangent plane;
and displaying the second ultrasonic image and outputting the fixation degree of the second ultrasonic image.
4. A method of ultrasound imaging according to claim 3, wherein the predetermined time period is greater than or equal to the duration of one respiratory cycle.
5. The method of any of claims 1-3, wherein the plurality of reference images comprises a plurality of tissue reference images and the second ultrasound image comprises a second tissue image and a second contrast image;
The determining similarity between the second ultrasound image and a plurality of the reference ultrasound images includes:
A similarity between the second tissue image and the plurality of tissue reference images is determined.
6. The ultrasound imaging method of claim 1 or 3, wherein the determining a plurality of reference ultrasound images from among the plurality of first ultrasound images comprises:
Displaying a plurality of first ultrasonic images, and determining a plurality of reference ultrasonic images in the plurality of first ultrasonic images according to image acquisition control operation of a user; or (b)
And carrying out image recognition on the plurality of first ultrasonic images, and determining a plurality of reference ultrasonic images according to image recognition results.
7. The method of ultrasound imaging of claim 6, wherein the determining a plurality of reference ultrasound images from among the plurality of first ultrasound images further comprises:
and outputting first prompt information, wherein the first prompt information is used for prompting a user to perform the image acquisition control operation according to the displacement of the target tissue in the first ultrasonic image.
8. The method of ultrasound imaging of claim 3, wherein the transmitting ultrasound waves to the target tissue, deriving an ultrasound image based on echoes of the ultrasound waves, comprises:
in contrast imaging mode, ultrasound waves are emitted to a target tissue, and an ultrasound image is obtained based on echoes of the ultrasound waves.
9. The method of ultrasound imaging of claim 3, wherein the transmitting ultrasound waves to the target tissue, deriving an ultrasound image based on echoes of the ultrasound waves, comprises:
transmitting ultrasonic waves to a target tissue in a first imaging mode within the preset time period, and obtaining a first ultrasonic image of the target tissue based on echo of the ultrasonic waves;
After the preset time period, transmitting ultrasonic waves to a target tissue in a second imaging mode, and obtaining a second ultrasonic image of the target tissue based on the echo of the ultrasonic waves;
Wherein a sound field mechanical index when the ultrasonic wave is emitted in the second imaging mode is lower than a sound field mechanical index when the ultrasonic wave is emitted in the first imaging mode; and/or
The transmission frequency when transmitting the ultrasonic wave in the second imaging mode is lower than the transmission frequency when transmitting the ultrasonic wave in the first imaging mode.
10. The ultrasound imaging method of claim 1 or 3, wherein the outputting the degree of fixation of the second ultrasound image comprises:
Outputting the degree of fixation of the second ultrasound image by at least one of: sound, text, color, graphics, and feel.
11. The method of ultrasound imaging according to any of claims 1 to 10, wherein the ultrasound image comprises a plurality of second ultrasound images,
The determining similarity between the second ultrasound image and a plurality of the reference ultrasound images includes:
determining a similarity between a plurality of said second ultrasound images and said plurality of said reference ultrasound images;
The determining the fixing degree of the second ultrasonic image according to the similarity between the second ultrasonic image and the reference ultrasonic images comprises the following steps:
determining a degree of fixation of the plurality of second ultrasound images based on the degree of similarity between the plurality of second ultrasound images and the plurality of reference ultrasound images;
The displaying the second ultrasonic image and outputting the fixation degree of the second ultrasonic image includes:
And displaying a plurality of the second ultrasonic images and outputting the fixation degree of the second ultrasonic images.
12. The ultrasound imaging method of any of claims 1-10, wherein the determining the degree of fixation of the second ultrasound image based on the degree of similarity between the second ultrasound image and the plurality of reference ultrasound images comprises:
Determining the maximum value of the similarity corresponding to a plurality of reference ultrasonic images according to the similarity between the second ultrasonic image and each reference ultrasonic image; determining the fixation degree of the second ultrasonic image according to the maximum value of the similarity corresponding to the plurality of reference ultrasonic images, wherein the fixation degree of the second ultrasonic image is positively correlated with the maximum value of the similarity; or alternatively
And carrying out weighted summation on the similarity between the second ultrasonic image and each reference ultrasonic image, and determining the fixation degree of the second ultrasonic image according to the weighted summation result, wherein the fixation degree of the second ultrasonic image is positively correlated with the weighted summation result.
13. The method of ultrasound imaging according to any of claims 1 to 10, wherein the second ultrasound image comprises a contrast image and a tissue image,
The determining similarity between the second ultrasound image and a plurality of the reference ultrasound images includes:
a similarity between the tissue image and the plurality of reference ultrasound images is determined.
14. The ultrasound imaging method of any of claims 1-10, wherein the determining a similarity between the second ultrasound image and a plurality of the reference ultrasound images comprises:
performing preset processing on the reference ultrasonic image to obtain a first target image, wherein the data size of the first target image is smaller than that of the reference ultrasonic image;
the second ultrasonic image is subjected to the preset processing to obtain a second target image, and the data size of the second target image is smaller than that of the second ultrasonic image;
determining the similarity between the second target image and the first target image, and determining the similarity between the second ultrasonic image and the reference ultrasonic image according to the similarity between the second target image and the first target image;
Wherein the preset process includes at least one of: image sampling processing, region of interest identification processing, and image graying processing.
15. The ultrasound imaging method of any of claims 1-10, wherein the determining a similarity between the second ultrasound image and the reference ultrasound image comprises:
determining a target similarity determination method in a plurality of preset similarity determination methods according to user operation, or acquiring a preset target similarity determination method;
Determining a similarity between the second ultrasound image and the reference ultrasound image based on the target similarity determination;
Wherein the similarity determination method comprises at least one of the following: normalized cross-correlation algorithm, sine and cosine similarity method, singular value decomposition method, eigenvalue method, matrix decomposition method, and deep learning method.
16. The ultrasound imaging method of any of claims 1-10, wherein the method further comprises:
When the fixation degree of the second ultrasonic image is smaller than or equal to a preset low-quality threshold value, determining scanning angle deviation and deflection angle deviation of an ultrasonic probe corresponding to the second ultrasonic image according to the second ultrasonic image and at least one reference ultrasonic image;
And outputting the scanning angle deviation and the deflection angle deviation of the ultrasonic probe corresponding to the second ultrasonic image and/or outputting the scanning guide information corresponding to the scanning angle deviation and the deflection angle deviation when the second ultrasonic image is displayed.
17. An ultrasound imaging apparatus, comprising:
A probe;
a transmitting circuit that excites the probe to transmit ultrasound waves to a target tissue;
The receiving circuit controls the probe to receive the ultrasonic echo so as to obtain an ultrasonic echo signal;
a display providing a display interface;
The ultrasonic imaging equipment processes the ultrasonic echo signals to obtain an ultrasonic image of the target tissue; and performing:
the method of ultrasound imaging of any of claims 1 to 16.
18. A computer readable storage medium storing a computer program which, when executed by a processor, causes the processor to implement:
the method of ultrasound imaging of any of claims 1 to 16.
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