A contrast imaging method, apparatus, device, and medium

Abstract

Embodiments of the present application disclose a contrast imaging method, device, equipment and medium, and a contrast time period and a contrast index adjustment rule matched with a to-be-imaged object are acquired. In the case of ensuring that a frame rate is unchanged, in order to improve a contrast microbubble development duration, when entering a target contrast time period, a contrast index is dynamically adjusted according to the contrast index adjustment rule, and ultrasonic contrast imaging is performed on the to-be-imaged object based on the adjusted contrast index. When exiting the target contrast time period, ultrasonic contrast imaging is performed on the to-be-imaged object according to a current contrast index. By setting the contrast time period, the contrast imaging process can be divided into stages, and the requirements for contrast imaging are different in different stages. By adjusting the contrast index in the target contrast time period, the contrast microbubble development duration is effectively prolonged while the ultrasonic contrast imaging effect is ensured, thereby meeting the contrast imaging requirements of the to-be-imaged object.

Description

Technical Field

[0001] This application relates to the field of contrast imaging technology, and in particular to a contrast imaging method, apparatus, device and computer-readable storage medium. Background Technology

[0002] Currently, the contrast imaging function of ultrasound imaging systems maintains a fixed frame rate when parameters remain constant. In practical applications, many lesions require observation of perfusion details, especially in liver applications where arterial perfusion is particularly important. Traditional methods perform ultrasound contrast imaging at a fixed low frame rate, which cannot guarantee good temporal resolution in the early stages of contrast agent infusion.

[0003] To improve the observational results during the early stages of microbubble perfusion in contrast imaging, a new contrast imaging mode has been proposed, with a default frame rate of up to 50 frames per second. Higher frame rates can be achieved depending on the selected image region size. While maintaining high frame rate imaging can address the temporal resolution issue in fixed low frame rate contrast imaging, achieving high frame rate imaging requires increasing the number of emission times per unit cycle, which shortens the microbubble perfusion time. For applications requiring observation of longer perfusion times, the contrast imaging quality will be affected, thus impacting clinical diagnosis.

[0004] It is evident that how to extend the duration of contrast microbubble imaging while ensuring high frame rate ultrasound contrast imaging is a problem that needs to be solved by those skilled in the art. Summary of the Invention

[0005] The purpose of this application is to provide a contrast imaging method, apparatus, device, and computer-readable storage medium that can effectively guarantee the imaging effect of contrast imaging.

[0006] To address the aforementioned technical problems, embodiments of this application provide a contrast imaging method, comprising:

[0007] Obtain the contrast imaging time period and contrast imaging index adjustment rules that match the object to be imaged; wherein, the contrast imaging time period includes the target contrast imaging time period that affects the duration of contrast microbubble imaging; the contrast imaging index includes parameters that affect the contrast imaging signal intensity;

[0008] When entering the target contrast imaging time period, the contrast imaging index is dynamically adjusted according to the contrast imaging index adjustment rules, and ultrasound contrast imaging is performed on the object to be imaged based on the adjusted contrast imaging index.

[0009] When exiting the target contrast imaging time period, ultrasound contrast imaging is performed on the object to be imaged based on the current contrast indicators.

[0010] Optionally, the target imaging time period includes a time period formed by a first target time and a second target time, wherein the first target time is shorter than the second target time;

[0011] The step of dynamically adjusting the angiography indicators according to the angiography indicator adjustment rules when entering the target angiography time period includes:

[0012] When the angiography microbubble perfusion time reaches the first target time, the angiography index is dynamically adjusted according to the angiography index adjustment rules.

[0013] The step of performing ultrasound contrast imaging on the object to be imaged based on the current contrast indicators when exiting the target contrast imaging time period includes:

[0014] When the contrast microbubble perfusion time reaches the second target time, ultrasound contrast imaging is performed on the object to be imaged based on the current contrast index corresponding to the second target time.

[0015] Optionally, the imaging parameters include the number of spatial composites;

[0016] The adjustment of the contrast indicators according to the aforementioned contrast indicator adjustment rules includes:

[0017] The rate of increase in the number of spatial composites is determined according to the aforementioned imaging index adjustment rules.

[0018] The spatial recombination number is adjusted upward in real time based on the rate of increase of the recombination number.

[0019] Optionally, the imaging metrics include frame correlation coefficients;

[0020] The adjustment of the contrast indicators according to the aforementioned contrast indicator adjustment rules includes:

[0021] The coefficient increase rate corresponding to the frame correlation coefficient is determined according to the aforementioned imaging index adjustment rules;

[0022] The frame correlation coefficient is adjusted upward in real time based on the coefficient increase rate.

[0023] Optionally, the imaging parameters include microvascular imaging time;

[0024] The adjustment of the contrast indicators according to the aforementioned contrast indicator adjustment rules includes:

[0025] Select a target imaging time that matches the target angiography time period from the set time ranges; wherein, the time ranges include imaging times corresponding to different angiography time periods;

[0026] The microvascular imaging time is adjusted to the target imaging time.

[0027] Optionally, the step of performing ultrasound contrast imaging on the object to be imaged based on the adjusted contrast parameters includes:

[0028] Based on the target imaging time and the set frame rate, the number of image overlays is determined;

[0029] In the microvascular imaging stage, ultrasound images that meet the image overlay requirements are pixel-overlayed to obtain an ultrasound contrast image of the object to be imaged.

[0030] Optionally, after obtaining the contrast time period and contrast index adjustment rules matching the object to be imaged, the method further includes:

[0031] When entering the target imaging time period, the fusion ratio of the nonlinear fundamental signal and the nonlinear harmonic signal is adjusted according to the fusion coefficients corresponding to the nonlinear fundamental signal and the nonlinear harmonic signal, respectively.

[0032] The nonlinear fundamental signal and the nonlinear harmonic signal are fused based on the adjusted fusion ratio to obtain the corresponding enhanced imaging image.

[0033] Optionally, before adjusting the fusion ratio of the nonlinear fundamental signal and the nonlinear harmonic signal according to the respective fusion coefficients of the nonlinear fundamental signal and the nonlinear harmonic signal, the method further includes:

[0034] Query the correspondence between imaging depth and fusion coefficient to determine the target fusion coefficient that matches the current imaging depth;

[0035] The step of adjusting the fusion ratio of the nonlinear fundamental signal and the nonlinear harmonic signal according to their respective fusion coefficients includes:

[0036] The fusion ratio of the nonlinear fundamental signal and the nonlinear harmonic signal is adjusted according to the target fusion coefficient.

[0037] Optionally, the fusion coefficient includes a first fusion coefficient corresponding to the nonlinear fundamental signal and a second fusion coefficient corresponding to the nonlinear harmonic signal; the method for setting the fusion coefficient includes:

[0038] Based on the time value corresponding to the target angiography time period and the intensity value of the set nonlinear fundamental wave signal, the first initial slope is determined;

[0039] The product of the first initial slope and the set first adjustable parameter is used as the first fusion coefficient;

[0040] The second initial slope is determined based on the time value corresponding to the target angiography time period and the intensity value of the set nonlinear harmonic signal.

[0041] The product of the second initial slope and the set second adjustable parameter is used as the second fusion coefficient.

[0042] Optionally, the fusion coefficient includes a first fusion coefficient corresponding to the nonlinear fundamental signal and a second fusion coefficient corresponding to the nonlinear harmonic signal; the method for setting the fusion coefficient includes:

[0043] The product of the set first adjustment function and the initial weight value of the nonlinear fundamental signal is used as the first fusion coefficient; wherein, the first adjustment function is a monotonically increasing parabolic function or a monotonically increasing exponential function.

[0044] The product of the set second adjustment function and the initial weight of the nonlinear harmonic signal is used as the second fusion coefficient; wherein, the second adjustment function is a monotonically decreasing parabolic function or a monotonically decreasing exponential function.

[0045] Optionally, after fusing the nonlinear fundamental signal and the nonlinear harmonic signal based on the adjusted fusion ratio to obtain the corresponding enhanced contrast image, the method further includes:

[0046] The enhanced contrast image and the ultrasound contrast image obtained based on contrast indicators are fused to obtain the fused contrast image.

[0047] This application also provides an imaging device for contrast imaging, including an acquisition unit, an adjustment unit, a first imaging unit, and a second imaging unit;

[0048] The acquisition unit is used to acquire the contrast time period and contrast index adjustment rules that match the object to be imaged; wherein, the contrast time period includes the target contrast time period that affects the duration of contrast microbubble imaging; the contrast index includes parameters that affect the contrast signal intensity.

[0049] The adjustment unit is used to dynamically adjust the contrast indicators according to the contrast indicator adjustment rules when entering the target contrast time period.

[0050] The first imaging unit is used to perform ultrasound contrast imaging on the object to be imaged based on the adjusted contrast indicators when entering the target contrast imaging time period.

[0051] The second imaging unit is used to perform ultrasound contrast imaging on the object to be imaged based on the current contrast indicators when exiting the target contrast imaging time period.

[0052] Optionally, the target imaging time period includes a time period formed by a first target time and a second target time, wherein the first target time is shorter than the second target time;

[0053] The adjustment unit is used to dynamically adjust the angiography index according to the angiography index adjustment rules when the angiography microbubble perfusion time reaches the first target time.

[0054] The second imaging unit is used to perform ultrasound contrast imaging on the object to be imaged based on the current contrast index corresponding to the second target time when the contrast microbubble perfusion time reaches the second target time.

[0055] Optionally, the imaging parameters include the number of spatial composites;

[0056] The adjustment unit includes a first determining subunit and a first adjusting subunit;

[0057] The first determining subunit is used to determine the rate of increase in the number of composites corresponding to the number of spatial composites according to the imaging index adjustment rules;

[0058] The first adjustment subunit is used to adjust the spatial recombination number in real time according to the recombination number increase rate.

[0059] Optionally, the imaging metrics include frame correlation coefficients;

[0060] The adjustment unit includes a second determining subunit and a second upward adjustment subunit;

[0061] The second determining subunit is used to determine the coefficient increase rate corresponding to the frame correlation coefficient according to the imaging index adjustment rule;

[0062] The second adjustment subunit is used to adjust the frame correlation coefficient in real time according to the coefficient increase rate.

[0063] Optionally, the imaging parameters include microvascular imaging time;

[0064] The adjustment unit includes selecting a sub-unit and acting as a sub-unit;

[0065] The selection subunit is used to select a target imaging time that matches the target angiography time period from a set time range; wherein, the time range includes the imaging time corresponding to each of the different angiography time periods;

[0066] The subunit is used to adjust the microvascular imaging time to the target imaging time.

[0067] Optionally, the first imaging unit includes a determining subunit and a superimposing subunit;

[0068] The determining subunit is used to determine the number of image overlays based on the target imaging time and the set frame rate;

[0069] The overlay subunit is used to perform pixel overlay processing on ultrasound images that meet the image overlay number during the microvascular imaging stage to obtain an ultrasound contrast image of the object to be imaged.

[0070] Optionally, it also includes a scaling unit and a fusion unit;

[0071] The ratio adjustment unit is used to adjust the fusion ratio of the nonlinear fundamental signal and the nonlinear harmonic signal according to the fusion coefficients corresponding to the nonlinear fundamental signal and the nonlinear harmonic signal when entering the target imaging time period.

[0072] The fusion unit is used to fuse the nonlinear fundamental signal and the nonlinear harmonic signal based on the adjusted fusion ratio to obtain the corresponding enhanced imaging image.

[0073] Optionally, a query unit may also be included;

[0074] The query unit is used to query the correspondence between imaging depth and fusion coefficient, and determine the target fusion coefficient that matches the current imaging depth.

[0075] The ratio adjustment unit is used to adjust the fusion ratio of the nonlinear fundamental signal and the nonlinear harmonic signal according to the target fusion coefficient.

[0076] Optionally, the fusion coefficient includes a first fusion coefficient corresponding to the nonlinear fundamental signal and a second fusion coefficient corresponding to the nonlinear harmonic signal; for the process of setting the fusion coefficient, the device includes a first slope determination unit, a first input unit, a second slope determination unit, and a second input unit;

[0077] The first slope determination unit is used to determine the first initial slope based on the time value corresponding to the target angiography time period and the intensity value of the set nonlinear fundamental wave signal.

[0078] The first unit is used to take the product of the first initial slope and the set first adjustable parameter as the first fusion coefficient;

[0079] The second slope determination unit is used to determine the second initial slope based on the time value corresponding to the target imaging time period and the intensity value of the set nonlinear harmonic signal.

[0080] The second unit is used to take the product of the second initial slope and the set second adjustable parameter as the second fusion coefficient.

[0081] Optionally, the fusion coefficient includes a first fusion coefficient corresponding to the nonlinear fundamental signal and a second fusion coefficient corresponding to the nonlinear harmonic signal; for the process of setting the fusion coefficient, the device includes a third serving unit and a fourth serving unit;

[0082] The third unit is used to take the product of the set first adjustment function and the initial weight value of the nonlinear fundamental signal as the first fusion coefficient; wherein, the first adjustment function is a monotonically increasing parabolic function or a monotonically increasing exponential function.

[0083] The fourth unit is used to take the product of the set second adjustment function and the initial weight value of the nonlinear harmonic signal as the second fusion coefficient; wherein the second adjustment function is a monotonically decreasing parabolic function or a monotonically decreasing exponential function.

[0084] Optionally, it also includes an image fusion unit;

[0085] The image fusion unit is used to fuse the enhanced contrast image and the ultrasound contrast image obtained based on contrast indicators to obtain the fused contrast image.

[0086] This application also provides an electronic device, including:

[0087] Memory, used to store computer programs;

[0088] A processor for executing the computer program to implement the steps of the contrast imaging method described above.

[0089] This application also provides a computer-readable storage medium storing a computer program, which, when executed by a processor, implements the steps of the contrast imaging method described above.

[0090] As can be seen from the above technical solution, the imaging time period and imaging index adjustment rules are obtained to match the imaging target. The imaging time period includes the target imaging time period that affects the duration of microbubble imaging; the imaging index includes parameters that affect the intensity of the imaging signal. Based on different perfusion stages of imaging, the imaging time period can be divided into a first stage before entering the target imaging time period, a second stage before entering the target imaging time period, and a third stage before exiting the target imaging time period. Imaging with a set high frame rate and imaging index can obtain higher quality imaging images. The first stage focuses on ensuring image temporal resolution; therefore, imaging with a set high frame rate and imaging index can be performed in the first stage. While maintaining a constant frame rate, to improve the duration of microbubble imaging, the imaging index can be dynamically adjusted according to the imaging index adjustment rules when entering the target imaging time period. Based on the adjusted imaging index, ultrasound imaging of the imaging target is performed. When exiting the target imaging time period, further adjustment of the imaging index is not meaningful, and the imaging index has its corresponding limitations. Therefore, when exiting the target imaging time period, ultrasound imaging of the imaging target can be performed based on the current imaging index. In this technical solution, by setting the contrast imaging time period, the contrast imaging process can be divided into stages. Different stages have different requirements for contrast imaging. By maintaining the original contrast parameters in the first stage and adjusting them in the second stage, the duration of contrast microbubble imaging is effectively extended while ensuring the quality of ultrasound contrast imaging, thus meeting the contrast imaging requirements of the object being imaged. For different types of objects, matching contrast imaging time periods and contrast parameter adjustment rules can be selected, satisfying the contrast imaging requirements of different objects and effectively expanding the application scenarios of contrast imaging. Attached Figure Description

[0091] To more clearly illustrate the embodiments of this application, the accompanying drawings used in the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0092] Figure 1 A flowchart of a contrast imaging method provided in an embodiment of this application;

[0093] Figure 2 A schematic diagram illustrating the variation of spatial recombination frequency in an embodiment of this application;

[0094] Figure 3 A schematic diagram illustrating the change in frame correlation coefficient provided in an embodiment of this application;

[0095] Figure 4A schematic diagram illustrating the selection of microvascular imaging time settings provided in an embodiment of this application;

[0096] Figure 5 This is a schematic diagram of a pixel overlay processing method provided in an embodiment of this application;

[0097] Figure 6a A schematic diagram illustrating the weight changes of a nonlinear fundamental signal and a nonlinear harmonic signal, provided for an embodiment of this application;

[0098] Figure 6b A schematic diagram illustrating the weight changes of another nonlinear fundamental signal and nonlinear harmonic signal provided in an embodiment of this application;

[0099] Figure 7a A schematic diagram illustrating the simultaneous display of ultrasound contrast-enhanced imaging and contrast-enhanced imaging on a display screen, as provided in this application embodiment;

[0100] Figure 7b A schematic diagram illustrating the simultaneous display of ultrasound contrast images and tissue images on a display screen, as provided in this application embodiment;

[0101] Figure 7c A schematic diagram illustrating the simultaneous display of ultrasound contrast-enhanced images, contrast-enhanced images, and tissue images on a display screen, as provided in this application embodiment;

[0102] Figure 7d A schematic diagram illustrating the simultaneous display of ultrasound contrast images and fused images on a display screen, as provided in this application embodiment;

[0103] Figure 8 This is a schematic diagram of the structure of an angiography device provided in an embodiment of this application;

[0104] Figure 9 This is a structural diagram of an electronic device provided in an embodiment of this application. Detailed Implementation

[0105] The technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of this application, and not all embodiments. Based on the embodiments of this application, all other embodiments obtained by those of ordinary skill in the art without creative effort are within the protection scope of this application.

[0106] The terms "comprising" and "having," and any variations thereof, in the specification, claims, and accompanying drawings of this application are intended to cover non-exclusive inclusion. For example, a process, method, system, product, or apparatus that includes a series of steps or units is not limited to the steps or units listed, but may include steps or units not listed.

[0107] To enable those skilled in the art to better understand the present application, the present application will be further described in detail below with reference to the accompanying drawings and specific embodiments.

[0108] The following section details a contrast imaging method provided by an embodiment of this application. This method can be applied to various types of ultrasound equipment. Figure 1 A flowchart of a contrast imaging method provided in this application embodiment, the method comprising:

[0109] S101: Obtain the contrast time period and contrast index adjustment rules that match the object to be imaged.

[0110] The contrast imaging scheme provided in this application embodiment can be applied to contrast imaging of the object to be imaged. The object to be imaged is the object to be subjected to ultrasound contrast imaging, which can be a body part, organ, etc. of the human body. Furthermore, the contrast imaging scheme can be applied to contrast imaging of organs, such as contrast imaging of the liver, uterus, and small organs.

[0111] The types of objects to be imaged can vary greatly. Considering that different types of objects have different characteristics, such as different sizes and different lesion observation times, in practical applications, to better meet the imaging needs of different objects, corresponding contrast time periods and contrast index adjustment rules can be set for different types of objects.

[0112] The contrast imaging time period includes the target contrast imaging time period that affects the duration of contrast microbubble imaging. In the embodiments of this application, the stage before entering the target contrast imaging time period can be referred to as the enhancement period, the target contrast imaging time period as the duration period, and the stage after exiting the target contrast imaging time period as the regression period.

[0113] The contrast imaging method provided in this application can perform contrast imaging at high frame rates. In practical applications, after the contrast agent is infused, the number of contrast agent microbubbles (hereinafter referred to as contrast microbubbles) decreases over time. Too few contrast agent microbubbles will affect the contrast imaging effect. In high frame rate scenarios, if contrast imaging is performed according to the original contrast parameters, the decreasing number of contrast microbubbles will result in a shorter contrast microbubble development duration. Therefore, in this application embodiment, to ensure the temporal resolution of the image of the object to be imaged while extending the contrast microbubble development duration as much as possible, the contrast parameters can be adjusted. By appropriately adjusting the contrast parameters, the intensity of the contrast signal can be increased, thereby achieving the goal of extending the contrast microbubble development duration.

[0114] The timing of adjusting contrast parameters is a crucial factor affecting the imaging quality and duration of contrast-enhanced ultrasound (CEUS) microbubble imaging. In practical applications, a high temporal resolution is required during the initial stage of microbubble perfusion, often resulting in CEUS imaging performed according to the pre-set parameters. After acquiring CEUS images with good temporal resolution, to effectively observe changes in the object being imaged, it's necessary to ensure the microbubbles persist for a longer period. At this stage, the contrast parameters can be appropriately adjusted to enhance the contrast signal intensity, thereby extending the duration of microbubble imaging. Based on these considerations, in this embodiment, the appropriate CEUS time period and parameter adjustment rules for different types of objects can be determined through testing.

[0115] In practical applications, a list can be created to record the matching contrast-enhancing time periods and contrast parameter adjustment rules for each type of object. When ultrasound contrast-enhanced imaging is required for an object, this list can be queried to obtain the matching contrast-enhancing time periods and contrast parameter adjustment rules. The contrast-enhancing time period includes the target contrast-enhancing time period for adjusting contrast parameters.

[0116] The angiography parameter adjustment rules encompass methods for adjusting angiography parameters to enhance angiography signal intensity. In this embodiment, angiography parameters include parameters affecting angiography signal intensity, such as spatial composite count, frame correlation coefficient, and microvascular imaging time. In practical applications, the angiography parameter adjustment rules may include methods for adjusting the spatial composite count, adjusting the frame correlation coefficient, and adjusting the microvascular imaging time. Adjustment methods for each angiography parameter may include continuous upward adjustment, initial upward adjustment followed by downward adjustment, or initial downward adjustment followed by upward adjustment.

[0117] S102: When entering the target contrast imaging time period, the contrast imaging parameters are dynamically adjusted according to the contrast imaging parameter adjustment rules, and ultrasound contrast imaging is performed on the object to be imaged based on the adjusted contrast imaging parameters.

[0118] Based on the changes in contrast agent microbubbles, the contrast-enhancing period can be divided into three stages: the first stage before entering the target contrast-enhancing period, the second stage before entering the target contrast-enhancing period, and the third stage before exiting the target contrast-enhancing period. The first stage corresponds to the enhancement phase of contrast-enhanced imaging, the second stage corresponds to the duration of contrast-enhanced imaging, and the third stage corresponds to the decay phase of contrast-enhanced imaging.

[0119] In high frame rate scenarios, imaging with contrast agents according to the pre-defined parameters can yield images with high temporal resolution. Since the first stage prioritizes maintaining temporal resolution, imaging with contrast agents can be performed according to the pre-defined parameters during this phase. To improve the duration of contrast microbubble imaging, the contrast agents can be dynamically adjusted according to the adjustment rules when entering the target contrast time period. Ultrasound contrast imaging of the target object is then performed based on the adjusted contrast agents.

[0120] Taking angiography metrics including spatial composite number, frame correlation coefficient, and microvascular imaging time as an example, in specific implementation, the adjustment of angiography metrics can be done by adjusting any one or any number of these parameters, without any limitation.

[0121] In ultrasound systems, different parameters have corresponding modules, each module representing a function within the ultrasound contrast imaging mode. The module related to spatial composite times can increase contrast signal intensity and temporal resolution. The module related to frame correlation coefficients primarily suppresses contrast noise and increases the signal-to-noise ratio. The module related to microvascular imaging time can utilize registration algorithms to superimpose multiple consecutive frames of signals. This module effectively synthesizes contrast agent signals from multiple frames of small vessels, resulting in a single frame with better contrast image quality.

[0122] It should be noted that the parameter adjustment methods for each module are independent of each other. The adjustment methods for the three types of parameters, namely spatial composite number, frame correlation coefficient and microvascular imaging time, will be introduced in detail in the following content.

[0123] S103: When exiting the target contrast imaging time period, perform ultrasound contrast imaging on the object to be imaged based on the current contrast indicators.

[0124] When exiting the target contrast imaging period, it is not very meaningful to adjust the contrast imaging parameters later. Moreover, the contrast imaging parameters have their corresponding limitations. Each type of parameter has its corresponding upper and lower limits. Therefore, when exiting the target contrast imaging period, ultrasound contrast imaging can be performed on the object to be imaged based on the current contrast imaging parameters.

[0125] In practical applications, two time points can be set to divide the ultrasound contrast imaging of the object to be imaged into the three stages described above. For ease of explanation, the two time points matching the object to be imaged can be referred to as the first target time and the second target time, where the first target time is earlier than the second target time. The target contrast imaging time period can be the time period formed by the first target time and the second target time.

[0126] In practice, before the microbubble perfusion time reaches the first target time, ultrasound contrast imaging can be performed on the object to be imaged according to the originally set contrast indicators.

[0127] When the microbubble perfusion time reaches the first target time, it indicates that the second stage has been entered. In the second stage, in order to increase the duration of microbubble imaging, the contrast index can be dynamically adjusted according to the contrast index adjustment rules; ultrasound contrast imaging is performed on the object to be imaged based on the adjusted contrast index.

[0128] When the microbubble perfusion time reaches the second target time, it indicates that the third stage has been entered. At this time, there is no need to adjust the angiography parameters. Ultrasound angiography can be performed on the object to be imaged based on the current angiography parameters corresponding to the second target time.

[0129] For different types of objects to be imaged, there are corresponding first target time and second target time. The values ​​of the first target time and the second target time can be determined through testing, and are not limited here.

[0130] The types of objects to be imaged can be varied, such as the uterus and liver. Based on the imaging phases described above, the imaging process for the uterus can be divided into the enhancement phase, duration phase, and resolution phase. For liver imaging, which requires observing more details, the imaging process can be divided into the arterial phase, portal venous phase, and delayed phase in practical applications. The adjustment methods for contrast parameters during ultrasound imaging are similar for different types of objects; only the values ​​of the first and second target times differ. For ease of explanation, the following content will use liver ultrasound imaging as an example.

[0131] Many lesions require detailed observation of perfusion, especially in liver applications where the arterial phase is particularly important. To improve the observation of the contrast agent in the arterial phase, a high frame rate contrast imaging mode can be used, with a default frame rate of up to 50 frames per second. In practical applications, even higher frame rates can be achieved depending on the selected image region size. However, high frame rate contrast imaging requires increasing the number of emission times per unit cycle, which can damage the contrast agent. This leads to a shorter microbubble perfusion time, affecting the results beyond 2 minutes. Therefore, in this embodiment, for liver ultrasound contrast imaging, the first target time can be set to 30 seconds, and the second target time can be set to 120 seconds.

[0132] Taking high frame rate liver contrast imaging as an example, timing can begin during contrast agent infusion. For the first 30 seconds, ultrasound contrast imaging of the liver is performed according to the set contrast parameters. Between 30 and 120 seconds of contrast microbubble infusion, the contrast parameters can be dynamically adjusted according to the adjustment rules, and ultrasound contrast imaging of the liver is performed based on the adjusted parameters. After 120 seconds of contrast microbubble infusion, no further adjustment of the contrast parameters is needed; the contrast parameters at 120 seconds become the current contrast parameters, and ultrasound contrast imaging of the liver is performed according to these current parameters from 120 seconds onwards.

[0133] As can be seen from the above technical solution, the imaging time period and imaging index adjustment rules that match the object to be imaged are obtained. The imaging time period includes the target imaging time period that affects the duration of microbubble imaging; the imaging index includes parameters that affect the intensity of the imaging signal. Based on different perfusion stages of imaging, the imaging time period can be divided into a first stage before entering the target imaging time period, a second stage before entering the target imaging time period, and a third stage before exiting the target imaging time period. Imaging with a set high frame rate and imaging index can obtain images with high temporal resolution. The first stage focuses on ensuring image temporal resolution; therefore, imaging with a set high frame rate and imaging index can be performed in the first stage. While maintaining a constant frame rate, to improve the duration of microbubble imaging, the imaging index can be dynamically adjusted according to the imaging index adjustment rules when entering the target imaging time period. Based on the adjusted imaging index, ultrasound imaging of the object to be imaged is performed. When exiting the target imaging time period, further adjustment of the imaging index is not meaningful, and the imaging index has its corresponding limitations. Therefore, when exiting the target imaging time period, ultrasound imaging of the object to be imaged can be performed based on the current imaging index. In this technical solution, by setting the contrast imaging time period, the contrast imaging process can be divided into stages. Different stages have different requirements for contrast imaging. By maintaining the original contrast parameters in the first stage and adjusting them in the second stage, the duration of contrast microbubble imaging is effectively extended while ensuring the quality of ultrasound contrast imaging, thus meeting the contrast imaging requirements of the object being imaged. For different types of objects, matching contrast imaging time periods and contrast parameter adjustment rules can be selected, satisfying the contrast imaging requirements of different objects and effectively expanding the application scenarios of contrast imaging.

[0134] In this embodiment of the application, the three types of imaging parameters, including spatial composite number, frame correlation coefficient and microvascular imaging time, are used as examples for further description.

[0135] During contrast imaging, the image formed by the ultrasound signal first passes through the module with the spatial composite number, and the image is superimposed based on the set spatial composite number.

[0136] Assuming the spatial composite count is set to 3, every 3 acquired frames can be superimposed to obtain a new image. For example, if the module responsible for the initial spatial composite count acquires 3 frames (frame 1, frame 2, and frame 3), these frames can be superimposed to obtain a new image, which is then transmitted to the next module. When the module acquires frame 4, frames 2, 3, and 4 can be superimposed to obtain a new image, which is also transmitted to the next module.

[0137] In practice, when entering the target angiography time period, the increase rate of the number of spatial composites corresponding to the number of composites can be determined according to the angiography index adjustment rules; the number of spatial composites can be adjusted upward in real time based on the increase rate of the number of composites.

[0138] The rate of increase of the spatial composite number can be a specific numerical value, which allows the spatial composite number to be adjusted upwards in a uniformly increasing manner. Alternatively, the rate of increase can be a variable numerical value, which allows the spatial composite number to be adjusted upwards in a monotonically increasing parabolic or exponentially increasing manner. Regardless of the method used to adjust the spatial composite number, its value is always a positive integer. The spatial composite number has a corresponding upper limit, and its range is 2 ≤ CompoundNum ≤ Compoundmax, where CompoundNum represents the spatial composite number, and Compoundmax is the upper limit of the spatial composite number. In practical applications, the spatial composite number can be an odd number such as 3, 5, 7, or 9.

[0139] In the initial state, the number of spatial composites can be represented by CompoundNum. The maximum number of spatial composites that can be achieved after adjustment can be represented by Compoundmax0, where Compoundmax0 ≤ Compoundmax.

[0140] Taking the spatial recombination number as an example of increasing in a uniform manner, Figure 2 This is a schematic diagram illustrating the variation of the spatial composite number in an embodiment of this application. After the module containing the spatial composite number is enabled, frame image fusion can be performed according to the original spatial composite number (CompoundNum) before the contrast microbubble perfusion time reaches T1. When the contrast microbubble perfusion time is between T1 and T2, fusion can be performed according to… Figure 2The curves shown dynamically adjust the spatial recombination count, and frame image fusion is performed based on the adjusted spatial recombination count. After the angiography microbubble perfusion time reaches T2, there is no need to adjust the spatial recombination count again; from T2 onwards, frame image fusion is performed according to the spatial recombination count corresponding to time T2.

[0141] Appropriately increasing the spatial composite number when entering the target angiography time period can increase the angiography signal strength and improve the temporal resolution of the angiography image.

[0142] The image output by the module responsible for spatial composite order will serve as the input image for the module responsible for frame correlation coefficient. The frame correlation coefficient indicates the proportion of the current frame relative to its adjacent previous frame. For example, if the frame correlation coefficient is 0.6, the current frame's proportion is 0.4, and the adjacent previous frame's proportion is 0.6, fusing the two frames according to their proportions will yield a new image.

[0143] In practice, when entering the target imaging time period, the coefficient increase rate corresponding to the frame correlation coefficient can be determined according to the imaging index adjustment rules; and the frame correlation coefficient can be adjusted upward in real time according to the coefficient increase rate.

[0144] The coefficient increase rate can be a specific numerical value, which allows the frame correlation coefficient to be adjusted upwards in a uniformly increasing manner. Alternatively, the coefficient increase rate can be a variable numerical value, which allows the frame correlation coefficient to be adjusted upwards in a monotonically increasing parabolic or exponentially increasing manner. Regardless of the method used to adjust the frame correlation coefficient, its value ranges between 0 and 1, excluding 0 and including 1.

[0145] Taking two adjacent frames as an example, the frame correlation coefficient can be the proportion of the previous frame. Since the sum of the proportions of the current frame and the previous frame is 1, the proportion of the current frame is 1 minus the proportion of the previous frame. After adjusting the frame correlation coefficient, adjacent frames can be superimposed according to their respective proportions. In practice, the superposition of adjacent frames can be performed using the following formula.

[0146] Image_Out(i)=Persist_Coef*image(i-1)+(1-Persist_Coef)*image(i); i≥2;

[0147] Where Image_Out(i) represents the image after two adjacent frames are superimposed according to the frame correlation coefficient, image(i-1) represents the (i-1)th frame image, image(i) represents the ith frame image, Persist_Coef represents the current frame correlation coefficient, Persist_Coef≤Persist_Coef_Max, Persist_Coef_Max represents the maximum frame correlation value defined by the system, and the range of the maximum frame correlation value is 0<Persist_Coef_Max≤1.

[0148] In the initial state, the frame correlation coefficient can be represented by Persist_Coef. The maximum value that the frame correlation coefficient can reach after adjustment can be represented by Persist_Coef_Max0, where Persist_Coef_Max0 ≤ Persist_Coef_Max.

[0149] Taking the frame correlation coefficient being adjusted upwards in a uniformly increasing manner as an example, Figure 3 This is a schematic diagram illustrating the change of frame correlation coefficient provided in an embodiment of this application. After the function of the module to which the frame correlation coefficient belongs is enabled, frame image fusion can be performed according to the original frame correlation coefficient Persist_Coef before the angiography microbubble perfusion time reaches T1. When the angiography microbubble perfusion time is between T1 and T2, it can be performed according to... Figure 3 The curves shown dynamically adjust the frame correlation coefficient, and frame image fusion is performed based on the adjusted frame correlation coefficient. After the angiography microbubble perfusion time reaches T2, there is no need to adjust the frame correlation coefficient again; from T2 onwards, frame image fusion is performed according to the frame correlation coefficient corresponding to time T2.

[0150] As the microbubble perfusion time progresses, the quality of the contrast imaging deteriorates. By dynamically increasing the frame correlation coefficient at the start of the target contrast imaging period, the proportion of the current frame can be continuously reduced, thereby effectively suppressing contrast noise and increasing the signal-to-noise ratio of the contrast imaging.

[0151] The image output by the module to which the frame correlation coefficient belongs will be used as the input image of the module to which the microvascular imaging time belongs. Based on the microvascular imaging time and the set frame rate, the number of image overlays can be determined. The ultrasound images that meet the number of image overlays are then processed by pixel overlay to obtain the ultrasound contrast image of the object to be imaged.

[0152] In practical implementation, time ranges can be set for microvascular imaging, including imaging times corresponding to different angiography time periods. When entering the target angiography time period, a target imaging time matching the target angiography time period can be selected from the set time ranges; the microvascular imaging time is then adjusted to the target imaging time.

[0153] Figure 4 This is a schematic diagram illustrating the selection of microvascular imaging time settings according to an embodiment of this application. Figure 4 In this context, T1 represents the first target time and T2 represents the second target time. Figure 4 There are three time settings for microvascular imaging. For ease of description, these three settings can be referred to as the first setting, the second setting, and the third setting, respectively, in chronological order. Before the angiography microbubble perfusion time reaches T1, the microvascular imaging time can be set to the imaging time corresponding to the first setting. When the angiography microbubble perfusion time is between T1 and T2, the microvascular imaging time can be set to the imaging time corresponding to the second setting. After the angiography microbubble perfusion time reaches T2, the microvascular imaging time can be set to the imaging time corresponding to the third setting. The maximum microvascular imaging time can be represented by MFI_Time_Max.

[0154] In the initial state, the microvascular imaging time can be represented by MFI_Time. In the third level, the microvascular imaging time can be represented by MFI_Time_Max0, where MFI_Time_Max0 ≤ MFI_Time_Max.

[0155] Based on the target imaging time and the set frame rate, the number of image overlays can be determined. In the microvascular imaging stage, the ultrasound images that meet the number of image overlays can be pixel-overlayed to obtain the ultrasound contrast image of the object to be imaged.

[0156] Assuming the microvascular imaging time is 0.7 seconds (s) and the set frame rate is 10 frames / second, the number of image overlays is 0.7 * 10 = 7. Every 7 frames of images can be overlaid to obtain a new image, which is the ultrasound contrast image of the object to be imaged.

[0157] Figure 5 This is a schematic diagram illustrating a pixel overlay processing method provided in an embodiment of this application. Figure 5 Taking the pixel overlay of 7 frames as an example, the black circles represent the pixels contained in each frame. After the function of the module to which the microvascular imaging time belongs is enabled, the first frame can be used as the template frame, and all frames from the first frame to the current frame can be overlaid. The image overlay method can be to perform maximum intensity projection on each pixel at the same position, and take the maximum intensity value among all frames as the projection result. Figure 5 The seven frames in the upper half are the input images received by the module to which the microvascular imaging time belongs. Figure 5 The lower half consists of 7 frames, which are a sequence of projected images obtained by superimposing the pixels of the previous frame. Figure 5 The last frame of the lower half is the output image of the module to which the microvascular imaging time belongs.

[0158] The microvascular imaging time module can use a registration algorithm to overlay multiple consecutive frames of images. This module can effectively synthesize the contrast agent signals of multiple frames of small blood vessels into a single frame of contrast image with better signal.

[0159] As mentioned above, the contrast parameters are adjusted during the target contrast time period, and ultrasound contrast imaging is performed on the object to be imaged based on the adjusted contrast parameters. When exiting the target contrast time period, ultrasound contrast imaging is performed on the object to be imaged based on the current contrast parameters. The final ultrasound contrast images can be used for quantitative analysis of contrast imaging.

[0160] However, quantitative analysis is not well-suited for lesions that require long perfusion times or lesions that may be misdiagnosed due to rapid regression caused by high frame rates. It provides continuous angiographic perfusion information for lesions and avoids situations where the angiography suggests that the lesions have completely disappeared when they have not. Therefore, qualitative analysis can be used for these situations.

[0161] Qualitative analysis can be used to obtain enhanced contrast images by adjusting the fusion ratio of the nonlinear fundamental signal and the nonlinear harmonic signal.

[0162] For ease of distinction, in this application embodiment, the contrast image obtained based on the contrast index is called an ultrasound contrast image, and the contrast image obtained based on the nonlinear fundamental signal and the nonlinear harmonic signal is called an enhanced contrast image.

[0163] In practice, when entering the target contrast imaging time period, the fusion ratio of the nonlinear fundamental signal and the nonlinear harmonic signal can be adjusted according to the fusion coefficients corresponding to the nonlinear fundamental signal and the nonlinear harmonic signal, respectively. Based on the adjusted fusion ratio, the nonlinear fundamental signal and the nonlinear harmonic signal are fused to obtain the corresponding enhanced contrast imaging image.

[0164] The fusion coefficient can be used to characterize the trend of signal variation. Nonlinear fundamental signals and nonlinear harmonic signals have their own corresponding fusion coefficients. For ease of distinction, the fusion coefficient corresponding to the nonlinear fundamental signal can be called the first fusion coefficient, and the fusion coefficient corresponding to the nonlinear harmonic signal can be called the second fusion coefficient.

[0165] The fusion coefficient can be a specific numerical value, based on which the nonlinear fundamental signal can be uniformly increased and the nonlinear harmonic signal can be uniformly decreased. Alternatively, the fusion coefficient can be a variable numerical value, allowing the nonlinear fundamental signal to be increased according to a monotonically increasing parabola or a monotonically increasing exponential function, and the nonlinear harmonic signal to be decreased according to a monotonically decreasing parabola or a monotonically decreasing exponential function.

[0166] Taking a specific value of the fusion coefficient as an example, in the embodiments of the present application, a first initial slope can be determined according to the time value corresponding to the target contrast-enhanced time period and the set intensity value of the nonlinear fundamental wave signal; the product of the first initial slope and the set first adjustable parameter is used as the first fusion coefficient. A second initial slope is determined according to the time value corresponding to the target contrast-enhanced time period and the set intensity value of the nonlinear harmonic signal; the product of the second initial slope and the set second adjustable parameter is used as the second fusion coefficient.

[0167] It can be known from the above introduction that the time value corresponding to the target contrast-enhanced time period is T2-T1. The first initial slope represents the change of the intensity value of the nonlinear fundamental wave signal within the target contrast-enhanced time period, and can be calculated according to the formula (T2-T1) / Fund_dbm.

[0168] The first fusion coefficient can be determined based on the first adjustable parameter and the first initial slope. In practical applications, the first fusion coefficient can be determined according to the following formula (1):

[0169] slope1=coef1*(T2-T1) / Fund_dbm (1);

[0170] wherein, slope1 represents the first fusion coefficient, coef1 represents the first adjustable parameter, 0 < coef1 ≤ 1, T2 represents the second target time, T1 represents the first target time, and Fund_dbm represents the intensity value of the nonlinear fundamental wave signal.

[0171] The second initial slope represents the change of the intensity value of the nonlinear harmonic signal within the target contrast-enhanced time period, and can be calculated according to the formula (T2-T1) / HM_dbm.

[0172] The second fusion coefficient can be determined based on the second adjustable parameter and the second initial slope. In practical applications, the second fusion coefficient can be determined according to the following formula (2):

[0173] slope2=coef2*(T2-T1) / HM_dbm (2);

[0174] wherein, slope2 represents the second fusion coefficient, coef2 represents the second adjustable parameter, 0 < coef2 ≤ 1, T2 represents the second target time, T1 represents the first target time, and HM_dbm represents the intensity value of the nonlinear harmonic signal.

[0175] The fusion coefficient reflects the trend of signal change, and the fusion ratio of the signal at different times can be determined based on the fusion coefficient. The fusion ratio can be regarded as the weight of the signal. Fusion_coef1 can be used to represent the first weight of the nonlinear fundamental signal, and Fusion_coef2 can be used to represent the second weight of the nonlinear harmonic signal.

[0176] The target imaging time period can be composed of a first target time and a second target time. T1 can be used to represent the first target time and T2 can be used to represent the second target time.

[0177] Figure 6a This illustration shows the weight changes of a nonlinear fundamental signal and a nonlinear harmonic signal, provided in an embodiment of this application. Before the angiography microbubble perfusion time reaches T1, signal fusion imaging can be performed according to the original weights of the nonlinear fundamental signal and the nonlinear harmonic signal. When the angiography microbubble perfusion time is between T1 and T2, it can be performed according to... Figure 6a The curves shown dynamically adjust the weights of the nonlinear fundamental signal and the nonlinear harmonic signal, and perform fusion imaging based on the weighted signals. Between T1 and T2, the weight of the nonlinear fundamental signal increases uniformly, while the weight of the nonlinear harmonic signal decreases uniformly. After the angiography microbubble perfusion time reaches T2, there is no need to adjust the weights of the nonlinear fundamental signal and the nonlinear harmonic signal anymore; from T2 onwards, signal fusion imaging is performed according to the weight values ​​corresponding to time T2.

[0178] Taking a variable fusion coefficient as an example, in this embodiment, the product of a set first adjustment function and the initial weight of the nonlinear fundamental signal can be used as the first fusion coefficient; wherein the first adjustment function is a monotonically increasing parabolic function or a monotonically increasing exponential function; the product of a set second adjustment function and the initial weight of the nonlinear harmonic signal can be used as the second fusion coefficient; wherein the second adjustment function is a monotonically decreasing parabolic function or a monotonically decreasing exponential function. Optionally, the fusion coefficient at a corresponding moment can be determined by the change in perfusion time. Both the first and second adjustment functions are functions related to the perfusion time; when a certain perfusion time is reached, the function value of the first adjustment function at that time is determined, and the product of this function value and the initial weight of the nonlinear fundamental signal is used as the first fusion coefficient; the function value of the second adjustment function at that time is determined, and the product of this function value and the initial weight of the nonlinear harmonic signal is used as the second fusion coefficient.

[0179] Taking the exponential function as an example, the first adjustment function can be e^(coef1*x), and the second adjustment function can be e^(-coef2*x).

[0180] Where x represents the angiography microbubble perfusion time, and the values ​​of coef1 and coef2 can be the same or different, which is not limited here.

[0181] Taking the adjustment function as the frame rate function as an example, Figure 6b This is a schematic diagram illustrating the weight changes of the nonlinear fundamental signal and nonlinear harmonic signals provided in another embodiment of this application. Before the angiography microbubble perfusion time reaches T1, signal fusion imaging can be performed according to the original weights of the nonlinear fundamental signal and nonlinear harmonic signals. When the angiography microbubble perfusion time is between T1 and T2, it can be performed according to... Figure 6b The curves shown dynamically adjust the weights of the nonlinear fundamental signal and the nonlinear harmonic signal, and perform fusion imaging based on the weighted signals. After the angiography microbubble perfusion time reaches T2, there is no need to adjust the weights of the nonlinear fundamental signal and the nonlinear harmonic signal anymore; from T2 onwards, signal fusion imaging is performed according to the weight values ​​corresponding to time T2.

[0182] It should be noted that the above description uses the fusion of two frequency components, the nonlinear fundamental signal and the nonlinear harmonic signal, as an example. If there are more frequency components for signal fusion imaging, such as the subharmonic of the 0.5th harmonic or the superharmonic of the 1.5th harmonic, corresponding fusion coefficients can be set for the newly added frequency components. The embodiments of this application are not limited to generating enhanced contrast images by fusing signals of two frequency components.

[0183] Considering that in practical applications, the signal attenuation of nonlinear fundamental and nonlinear harmonic signals varies depending on the imaging depth, this embodiment of the application determines the matching fusion coefficients for different imaging depths through testing, and records the corresponding fusion coefficients for each imaging depth in a corresponding manner.

[0184] When adjusting the fusion ratio of the nonlinear fundamental signal and the nonlinear harmonic signal, you can first look up the correspondence between the imaging depth and the fusion coefficient to determine the target fusion coefficient that matches the current imaging depth; then adjust the fusion ratio of the nonlinear fundamental signal and the nonlinear harmonic signal according to the target fusion coefficient.

[0185] Contrast-enhanced ultrasound images can be generated based on contrast indicators, and enhanced contrast-enhanced images can be generated based on nonlinear fundamental and nonlinear harmonic signals. In this embodiment, the contrast-enhanced ultrasound images and enhanced contrast-enhanced images can also be fused to further enhance the contrast signal and obtain a clearer contrast image.

[0186] In this embodiment, the method of fusing ultrasound contrast images and enhanced contrast images is not limited. The ultrasound contrast images and enhanced contrast images can be fused according to a set ratio, or they can be fused by pixel overlay.

[0187] In practical applications, contrast images can be displayed on the instrument's screen. In this embodiment, the image originally displayed on the screen can be referred to as a tissue image. The screen can often display multiple images simultaneously. Figure 7a This is a schematic diagram illustrating the simultaneous display of ultrasound contrast images and enhanced contrast images on a display screen, as provided in an embodiment of this application. Figure 7b A schematic diagram illustrating the simultaneous display of ultrasound contrast images and tissue images on a display screen, as provided in this application embodiment; Figure 7c This is a schematic diagram illustrating how to simultaneously display ultrasound contrast images, enhanced contrast images, and tissue images on a display screen, as provided in an embodiment of this application.

[0188] Figure 7d This is a schematic diagram illustrating the simultaneous display of ultrasound contrast-enhanced images and fused images on a display screen, as provided in an embodiment of this application. The fused image can be obtained by fusing any two images from the ultrasound contrast-enhanced image, the contrast-enhanced image, and the tissue image, or by fusing the three images from the ultrasound contrast-enhanced image, the contrast-enhanced image, and the tissue image.

[0189] By displaying different types of images, operators can gain a more intuitive and comprehensive understanding of the state of the object to be imaged, thereby enabling them to accurately assess the object.

[0190] Figure 8 A schematic diagram of a contrast imaging device provided in an embodiment of this application includes an acquisition unit 81, an adjustment unit 82, a first imaging unit 83, and a second imaging unit 84.

[0191] The acquisition unit 81 is used to acquire the contrast time period and contrast index adjustment rules that match the object to be imaged; wherein, the contrast time period includes the target contrast time period that affects the duration of contrast microbubble imaging; and the contrast index includes parameters that affect the contrast signal intensity.

[0192] Adjustment unit 82 is used to dynamically adjust the contrast indicators according to the contrast indicator adjustment rules when entering the target contrast time period;

[0193] The first imaging unit 83 is used to perform ultrasound contrast imaging on the object to be imaged based on the adjusted contrast parameters when entering the target contrast imaging time period.

[0194] The second imaging unit 84 is used to perform ultrasound contrast imaging on the object to be imaged based on the current contrast indicators when exiting the target contrast imaging time period.

[0195] Optionally, the target imaging time period includes the time period formed by the first target time and the second target time, wherein the first target time is shorter than the second target time;

[0196] The adjustment unit is used to dynamically adjust the angiography parameters according to the angiography parameter adjustment rules when the angiography microbubble perfusion time reaches the first target time.

[0197] The second imaging unit is used to perform ultrasound contrast imaging on the object to be imaged based on the current contrast indicators corresponding to the second target time when the contrast microbubble perfusion time reaches the second target time.

[0198] Optionally, imaging parameters include spatial compounding times;

[0199] The adjustment unit includes a first determining subunit and a first adjusting subunit;

[0200] The first determining subunit is used to determine the rate of increase of the number of spatial composites according to the contrast index adjustment rules;

[0201] The first adjustment subunit is used to adjust the spatial composite number in real time according to the composite number increase rate.

[0202] Optionally, imaging metrics include frame correlation coefficients;

[0203] The adjustment unit includes a second determining subunit and a second adjusting subunit;

[0204] The second determining subunit is used to determine the coefficient rise rate corresponding to the frame correlation coefficient according to the imaging index adjustment rules;

[0205] The second adjustment subunit is used to adjust the frame correlation coefficient in real time according to the coefficient increase rate.

[0206] Optionally, the imaging parameters include microvascular imaging time;

[0207] The adjustment unit includes selecting sub-units and using them as sub-units;

[0208] The selection sub-unit is used to select the target imaging time that matches the target angiography time period from the set time ranges; wherein, the time ranges include the imaging time corresponding to each of the different angiography time periods;

[0209] As a subunit, it is used to adjust the microvascular imaging time to the target imaging time.

[0210] Optionally, the first imaging unit includes a determining subunit and a stacking subunit;

[0211] The determination subunit is used to determine the number of image overlays based on the target imaging time and the set frame rate;

[0212] The overlay subunit is used in the microvascular imaging stage to perform pixel overlay processing on ultrasound images that meet the image overlay number to obtain an ultrasound contrast image of the object to be imaged.

[0213] Optionally, it also includes a scaling unit and a fusion unit;

[0214] The scaling unit is used to adjust the fusion ratio of the nonlinear fundamental signal and the nonlinear harmonic signal according to the fusion coefficients corresponding to the nonlinear fundamental signal and the nonlinear harmonic signal when entering the target imaging time period.

[0215] The fusion unit is used to fuse the nonlinear fundamental signal and the nonlinear harmonic signal based on the adjusted fusion ratio to obtain the corresponding enhanced imaging image.

[0216] Optionally, a query unit may also be included;

[0217] The query unit is used to query the correspondence between imaging depth and fusion coefficient, and determine the target fusion coefficient that matches the current imaging depth;

[0218] The scaling unit is used to adjust the fusion ratio of the nonlinear fundamental signal and the nonlinear harmonic signal according to the target fusion coefficient.

[0219] Optionally, the fusion coefficients include a first fusion coefficient corresponding to the nonlinear fundamental signal and a second fusion coefficient corresponding to the nonlinear harmonic signal; for the process of setting the fusion coefficients, the device includes a first slope determination unit, a first input unit, a second slope determination unit, and a second input unit;

[0220] The first slope determination unit is used to determine the first initial slope based on the time value corresponding to the target angiography time period and the intensity value of the set nonlinear fundamental wave signal.

[0221] The first unit is used to take the product of the first initial slope and the set first adjustable parameter as the first fusion coefficient;

[0222] The second slope determination unit is used to determine the second initial slope based on the time value corresponding to the target angiography time period and the intensity value of the set nonlinear harmonic signal.

[0223] The second unit is used to multiply the second initial slope by the set second adjustable parameter as the second fusion coefficient.

[0224] Optionally, the fusion coefficients include a first fusion coefficient corresponding to the nonlinear fundamental signal and a second fusion coefficient corresponding to the nonlinear harmonic signal; for the process of setting the fusion coefficients, the device includes a third and a fourth unit.

[0225] The third unit is used to take the product of the set first adjustment function and the initial weight of the nonlinear fundamental signal as the first fusion coefficient; wherein the first adjustment function is a monotonically increasing parabolic function or a monotonically increasing exponential function.

[0226] The fourth unit is used to take the product of the set second adjustment function and the initial weight of the nonlinear harmonic signal as the second fusion coefficient; wherein the second adjustment function is a monotonically decreasing parabolic function or a monotonically decreasing exponential function.

[0227] Optionally, it also includes an image fusion unit;

[0228] The image fusion unit is used to fuse the enhanced contrast image and the ultrasound contrast image obtained based on the contrast index to obtain the fused contrast image.

[0229] Figure 8 The description of the features in the corresponding embodiments can be found in [reference needed]. Figure 1 The relevant descriptions of the corresponding embodiments will not be repeated here.

[0230] As can be seen from the above technical solution, the imaging time period and imaging index adjustment rules that match the object to be imaged are obtained. The imaging time period includes the target imaging time period that affects the duration of microbubble imaging; the imaging index includes parameters that affect the intensity of the imaging signal. Based on different perfusion stages of imaging, the imaging time period can be divided into a first stage before entering the target imaging time period, a second stage before entering the target imaging time period, and a third stage before exiting the target imaging time period. Imaging with a set high frame rate and imaging index can obtain images with high temporal resolution. The first stage focuses on ensuring image temporal resolution; therefore, imaging with a set high frame rate and imaging index can be performed in the first stage. While maintaining a constant frame rate, to improve the duration of microbubble imaging, the imaging index can be dynamically adjusted according to the imaging index adjustment rules when entering the target imaging time period. Based on the adjusted imaging index, ultrasound imaging of the object to be imaged is performed. When exiting the target imaging time period, further adjustment of the imaging index is not meaningful, and the imaging index has its corresponding limitations. Therefore, when exiting the target imaging time period, ultrasound imaging of the object to be imaged can be performed based on the current imaging index. In this technical solution, by setting the contrast imaging time period, the contrast imaging process can be divided into stages. Different stages have different requirements for contrast imaging. By maintaining the original contrast parameters in the first stage and adjusting them in the second stage, the duration of contrast microbubble imaging is effectively extended while ensuring the quality of ultrasound contrast imaging, thus meeting the contrast imaging requirements of the object being imaged. For different types of objects, matching contrast imaging time periods and contrast parameter adjustment rules can be selected, satisfying the contrast imaging requirements of different objects and effectively expanding the application scenarios of contrast imaging.

[0231] Figure 9 This is a structural diagram of an electronic device provided in an embodiment of this application. The electronic device can be various types of ultrasound equipment, such as conventional color Doppler ultrasound, cardiac color Doppler ultrasound, obstetric color Doppler ultrasound, etc. Figure 9 As shown, the electronic device includes: a memory 20 for storing computer programs;

[0232] The processor 21 is used to execute computer programs to implement the steps of the contrast imaging method as described in the above embodiments.

[0233] The electronic devices provided in this embodiment may include, but are not limited to, smartphones, tablets, laptops, or desktop computers.

[0234] The processor 21 may include one or more processing cores, such as a quad-core processor or an octa-core processor. The processor 21 may be implemented using at least one hardware form selected from DSP (Digital Signal Processing), FPGA (Field-Programmable Gate Array), and PLA (Programmable Logic Array). The processor 21 may also include a main processor and a coprocessor. The main processor, also known as a CPU (Central Processing Unit), is used to process data in the wake-up state; the coprocessor is a low-power processor used to process data in the standby state. In some embodiments, the processor 21 may integrate a GPU (Graphics Processing Unit), which is responsible for rendering and drawing the content to be displayed on the screen. In some embodiments, the processor 21 may also include an AI (Artificial Intelligence) processor, which is used to handle computational operations related to machine learning.

[0235] The memory 20 may include one or more computer-readable storage media, which may be non-transitory. The memory 20 may also include high-speed random access memory and non-volatile memory, such as one or more disk storage devices or flash memory devices. In this embodiment, the memory 20 is used to store at least the following computer program 201, which, after being loaded and executed by the processor 21, is capable of implementing the relevant steps of the contrast imaging method disclosed in any of the foregoing embodiments. In addition, the resources stored in the memory 20 may also include an operating system 202 and data 203, and the storage method may be temporary or permanent storage. The operating system 202 may include Windows, Unix, Linux, etc. The data 203 may include, but is not limited to, contrast imaging time periods and contrast imaging indicator adjustment rules.

[0236] In some embodiments, the electronic device may further include a display screen 22, an input / output interface 23, a communication interface 24, a power supply 25, and a communication bus 26.

[0237] Those skilled in the art will understand that Figure 9 The structures shown do not constitute a limitation on electronic devices and may include more or fewer components than those shown.

[0238] It is understood that if the contrast imaging method in the above embodiments is implemented as a software functional unit and sold or used as an independent product, it can be stored in a computer-readable storage medium. Based on this understanding, the technical solution of this application, in essence, or the part that contributes to the prior art, or all or part of the technical solution, can be embodied in the form of a software product. This computer software product is stored in a storage medium and executes all or part of the steps of the methods in the various embodiments of this application. The aforementioned storage medium includes: USB flash drive, mobile hard disk, read-only memory (ROM), random access memory (RAM), electrically erasable programmable ROM, register, hard disk, removable disk, CD-ROM, magnetic disk, or optical disk, and other media capable of storing program code.

[0239] Based on this, embodiments of the present invention also provide a computer-readable storage medium storing a computer program, which, when executed by a processor, implements the steps of the above-described contrast imaging method.

[0240] The functions of each functional module of the computer-readable storage medium described in the embodiments of the present invention can be specifically implemented according to the methods in the above method embodiments. The specific implementation process can be referred to the relevant descriptions in the above method embodiments, which will not be repeated here.

[0241] The foregoing has provided a detailed description of a contrast imaging method, apparatus, device, and computer-readable storage medium provided in the embodiments of this application. The various embodiments are described in a progressive manner, with each embodiment focusing on its differences from other embodiments. Similar or identical parts between embodiments can be referred to interchangeably. For the apparatus disclosed in the embodiments, since it corresponds to the method disclosed in the embodiments, the description is relatively simple; relevant parts can be referred to in the method section.

[0242] Those skilled in the art will further recognize that the units and algorithm steps of the various examples described in conjunction with the embodiments disclosed herein can be implemented in electronic hardware, computer software, or a combination of both. To clearly illustrate the interchangeability of hardware and software, the components and steps of the various examples have been generally described in terms of functionality in the foregoing description. Whether these functions are implemented in hardware or software depends on the specific application and design constraints of the technical solution. Those skilled in the art can use different methods to implement the described functions for each specific application, but such implementation should not be considered beyond the scope of this application.

[0243] The foregoing has provided a detailed description of a contrast imaging method, apparatus, device, and computer-readable storage medium provided in this application. Specific examples have been used to illustrate the principles and implementation methods of the invention. The descriptions of the embodiments above are merely for the purpose of helping to understand the method and core ideas of the invention. It should be noted that those skilled in the art can make various improvements and modifications to this application without departing from the principles of the invention, and these improvements and modifications also fall within the protection scope of the claims of this application.

Claims

1. A contrast imaging method, characterized in that, include: Obtain the contrast imaging time period and contrast imaging index adjustment rules that match the object to be imaged; wherein, the contrast imaging time period includes the target contrast imaging time period that affects the duration of contrast microbubble imaging; the contrast imaging index includes parameters that affect the contrast imaging signal intensity; While maintaining a high frame rate, when entering the target contrast imaging time period, the contrast imaging index is dynamically adjusted according to the contrast imaging index adjustment rules, and ultrasound contrast imaging is performed on the object to be imaged based on the adjusted contrast imaging index. When exiting the target contrast imaging time period, ultrasound contrast imaging is performed on the object to be imaged based on the current contrast indicators; The imaging parameters include any one or more of the following parameters: spatial composite number, frame correlation coefficient, and microvascular imaging time; According to the aforementioned angiography parameter adjustment rules, adjustments can be made to any one or more parameters among the angiography parameters, including spatial composite number, frame correlation coefficient, and microvascular imaging time. When the imaging parameters include spatial compositing number, the compositing number increase rate corresponding to the spatial compositing number is determined according to the imaging parameter adjustment rules; the spatial compositing number is adjusted upward in real time according to the compositing number increase rate. When the imaging metric includes the frame correlation coefficient, the coefficient increase rate corresponding to the frame correlation coefficient is determined according to the imaging metric adjustment rule; and the frame correlation coefficient is adjusted upward in real time according to the coefficient increase rate. When the angiography indicators include microvascular imaging time, a target imaging time matching the target angiography time period is selected from the set time ranges; wherein, the time ranges include imaging times corresponding to different angiography time periods; the microvascular imaging time is adjusted to the target imaging time.

2. The contrast imaging method according to claim 1, characterized in that, The target angiography time period includes a time period formed by a first target time and a second target time, wherein the first target time is shorter than the second target time. The step of dynamically adjusting the angiography indicators according to the angiography indicator adjustment rules when entering the target angiography time period includes: When the angiography microbubble perfusion time reaches the first target time, the angiography index is dynamically adjusted according to the angiography index adjustment rules. The step of performing ultrasound contrast imaging on the object to be imaged based on the current contrast indicators when exiting the target contrast imaging time period includes: When the contrast microbubble perfusion time reaches the second target time, ultrasound contrast imaging is performed on the object to be imaged based on the current contrast index corresponding to the second target time.

3. The contrast imaging method according to claim 1, characterized in that, After obtaining the contrast time period and contrast index adjustment rules that match the object to be imaged, the following is also included: When entering the target imaging time period, the fusion ratio of the nonlinear fundamental signal and the nonlinear harmonic signal is adjusted according to the fusion coefficients corresponding to the nonlinear fundamental signal and the nonlinear harmonic signal, respectively. The nonlinear fundamental signal and the nonlinear harmonic signal are fused based on the adjusted fusion ratio to obtain the corresponding enhanced imaging image.

4. The contrast imaging method according to claim 3, characterized in that, Before adjusting the fusion ratio of the nonlinear fundamental signal and the nonlinear harmonic signal according to their respective fusion coefficients, the method further includes: Query the correspondence between imaging depth and fusion coefficient to determine the target fusion coefficient that matches the current imaging depth; The step of adjusting the fusion ratio of the nonlinear fundamental signal and the nonlinear harmonic signal according to their respective fusion coefficients includes: The fusion ratio of the nonlinear fundamental signal and the nonlinear harmonic signal is adjusted according to the target fusion coefficient.

5. The contrast imaging method according to claim 4, characterized in that, The fusion coefficient includes a first fusion coefficient corresponding to the nonlinear fundamental signal and a second fusion coefficient corresponding to the nonlinear harmonic signal; The method for setting the fusion coefficient includes: Based on the time value corresponding to the target angiography time period and the intensity value of the set nonlinear fundamental wave signal, the first initial slope is determined; The product of the first initial slope and the set first adjustable parameter is used as the first fusion coefficient; The second initial slope is determined based on the time value corresponding to the target angiography time period and the intensity value of the set nonlinear harmonic signal. The product of the second initial slope and the set second adjustable parameter is used as the second fusion coefficient.

6. The contrast imaging method according to claim 4, characterized in that, The fusion coefficient includes a first fusion coefficient corresponding to the nonlinear fundamental signal and a second fusion coefficient corresponding to the nonlinear harmonic signal; The method for setting the fusion coefficient includes: The product of the set first adjustment function and the initial weight value of the nonlinear fundamental signal is used as the first fusion coefficient; wherein, the first adjustment function is a monotonically increasing parabolic function or a monotonically increasing exponential function. The product of the set second adjustment function and the initial weight of the nonlinear harmonic signal is used as the second fusion coefficient; wherein, the second adjustment function is a monotonically decreasing parabolic function or a monotonically decreasing exponential function.

7. The contrast imaging method according to any one of claims 3 to 6, characterized in that, After fusing the nonlinear fundamental signal and the nonlinear harmonic signal based on the adjusted fusion ratio to obtain the corresponding enhanced contrast image, the process further includes: The enhanced contrast image and the ultrasound contrast image obtained based on contrast indicators are fused to obtain the fused contrast image.

8. A contrast imaging device, characterized in that, It includes an acquisition unit, an adjustment unit, a first imaging unit, and a second imaging unit; The acquisition unit is used to acquire the contrast time period and contrast index adjustment rules that match the object to be imaged; wherein, the contrast time period includes the target contrast time period that affects the duration of contrast microbubble imaging; the contrast index includes parameters that affect the contrast signal intensity. The adjustment unit is used to dynamically adjust the angiography index according to the angiography index adjustment rules when entering the target angiography time period, while ensuring that the high frame rate remains unchanged. The first imaging unit is used to perform ultrasound contrast imaging on the object to be imaged based on the adjusted contrast indicators when entering the target contrast imaging time period. The second imaging unit is used to perform ultrasound contrast imaging on the object to be imaged based on the current contrast indicators when exiting the target contrast imaging time period; The imaging parameters include any one or more of the following: spatial composite number, frame correlation coefficient, and microvascular imaging time; The adjustment unit is used to adjust any one or more parameters of the angiography indicators, including spatial composite number, frame correlation coefficient and microvascular imaging time, according to the angiography indicator adjustment rules. The contrast indicators include the number of spatial composites, and the adjustment unit includes a first determining subunit and a first adjusting subunit; the first determining subunit is used to determine the composite number increase rate corresponding to the number of spatial composites according to the contrast indicator adjustment rules; the first adjusting subunit is used to adjust the number of spatial composites in real time according to the composite number increase rate. The imaging index includes the frame correlation coefficient, and the adjustment unit includes a second determining subunit and a second adjusting subunit; the second determining subunit is used to determine the coefficient increase rate corresponding to the frame correlation coefficient according to the imaging index adjustment rules; the second adjusting subunit is used to adjust the frame correlation coefficient in real time according to the coefficient increase rate. The angiography parameters include microvascular imaging time, and the adjustment unit includes a selection sub-unit and an as-sub-unit. The selection sub-unit is used to select the target imaging time that matches the target angiography time period from the set time range. The time range includes the imaging time corresponding to each of the different angiography time periods. The as-sub-unit is used to adjust the microvascular imaging time to the target imaging time.

9. An electronic device, characterized in that, include: Memory, used to store computer programs; A processor for executing the computer program to implement the steps of the contrast imaging method as described in any one of claims 1 to 7.

10. A computer-readable storage medium, characterized in that, The computer-readable storage medium stores a computer program that, when executed by a processor, implements the steps of the contrast imaging method as described in any one of claims 1 to 7.

Images