Method and system for ultrasound imaging with a two-dimensional probe

Abstract

The application provides a method for ultrasonic imaging using a two-dimensional probe, the two-dimensional probe comprising a plurality of rows of elements, the method comprising: acquiring a two-dimensional ultrasonic image of a tissue to be imaged; identifying the ultrasonic image to determine a high acoustic impedance object therein according to an identification result; continuing ultrasonic imaging of the high acoustic impedance object using at least one row of elements of the plurality of rows of elements to acquire a first image of the high acoustic impedance object; ultrasonic imaging of at least a partial underlying region of the high acoustic impedance object using at least another row of elements of the plurality of rows of elements to acquire a second image of the at least partial underlying region; and synthesizing the first image and the second image to acquire a real-time synthesized image. The application also provides an ultrasonic imaging system and a non-transitory computer readable medium.

Description

Technical Field

[0001] This application relates to the field of ultrasound imaging, and more specifically, to methods and systems for ultrasound imaging using a two-dimensional probe. Background Technology

[0002] Ultrasonic imaging technology typically uses an ultrasonic probe to emit ultrasonic signals to the object being imaged, and then receives and processes the echo signals to generate an image of the object. Two-dimensional ultrasonic imaging is one type of ultrasonic imaging technology. It usually uses a two-dimensional probe for ultrasonic imaging; specifically, a two-dimensional probe can emit and receive ultrasonic signals in a plane, and the signals in the plane are processed to obtain a two-dimensional ultrasonic image.

[0003] High acoustic impedance objects (HIFORM) in the object being imaged can affect ultrasound imaging. HIFORM objects are those that create high acoustic impedance for sound wave propagation. Common examples of HIFORM objects include high-density, highly reflective objects such as interventional needles used in puncture procedures, bones, and stones. When sound waves reach HIFORM objects, they undergo strong reflection, creating an acoustic shadow and reducing the image quality of the area beneath the HIFORM object. For example, in interventional procedures, the creation of an acoustic shadow will reduce the image quality of the area beneath the interventional needle, leading to the loss of information in this area and impacting the physician's diagnostic confidence. Summary of the Invention

[0004] At least in view of this, some embodiments of this application provide a method for ultrasound imaging using a two-dimensional probe. The two-dimensional probe includes multiple rows of primitives. The method includes: acquiring a two-dimensional ultrasound image of a tissue to be imaged; identifying a high acoustic impedance element within the ultrasound image based on the identification result; continuing ultrasound imaging of the high acoustic impedance element using at least one row of primitives to obtain a first image of the high acoustic impedance element; performing ultrasound imaging of at least a portion of a region below the high acoustic impedance element using at least another row of primitives to obtain a second image of the at least portion of the region below the high acoustic impedance element; and synthesizing the first image and the second image to obtain a real-time synthesized image.

[0005] Optionally, the high acoustic impedance material includes at least one of an interventional needle, bone, stone, and calcification.

[0006] Optionally, continuing to perform ultrasonic imaging on the high acoustic impedance object using at least one row of the multiple rows of primitives includes: adjusting the ultrasonic wave emission direction of the at least one row of primitives to be perpendicular to the surface of the high acoustic impedance object based on the relative position of the high acoustic impedance object and the at least one row of primitives.

[0007] Optionally, the adjustment of the ultrasonic emission method of the at least one row of primitives is performed within an imaging plane that passes through the high acoustic impedance material.

[0008] Optionally, using the at least other row of primitives to perform ultrasound imaging of the at least part of the area below includes: adjusting the ultrasonic emission direction of the at least other row of primitives based on the relative position of the high acoustic impedance material and the at least other row of primitives, so that it at least partially passes through the tissue to be imaged below the high acoustic impedance material.

[0009] Optionally, the adjustment of the ultrasonic emission direction of the at least other row of primitives is performed on an imaging plane different from that of the at least one row of primitives.

[0010] Optionally, the method further includes: determining key anatomical features beneath the high acoustic impedance material based on the identification result, the key anatomical features including at least one of glands, nerve nodes, and blood vessels.

[0011] Optionally, using the at least other row of primitives to perform ultrasound imaging of the at least part of the area below includes: controlling the direction of ultrasound emission of the at least other row of primitives based on the location of the key anatomical feature, so that it at least partially passes through the key anatomical feature.

[0012] Optionally, the method further includes: displaying the synthesized image in real time; and highlighting the key anatomical features in the synthesized image.

[0013] Optionally, the multi-row basic unit includes three rows of basic units, the at least one row of basic units includes the middle row of basic units among the three rows of basic units, and the at least another row of basic units includes the two outer rows of basic units among the three rows of basic units.

[0014] Optionally, synthesizing the first image and the second image includes: selecting a first portion of the first image that includes the high acoustic impedance object and the region above it; selecting a second portion of the second image that includes the region below the high acoustic impedance object; and synthesizing the first portion and the second portion.

[0015] Optionally, the high acoustic impedance material includes an interventional needle, and the method further includes: adjusting the ultrasonic emission direction of the at least one row of primitives and the at least another row of primitives in real time in response to a change in the position of the interventional needle within the tissue to be imaged, so as to continuously acquire images of the interventional needle and images of at least a portion of the region below the interventional needle.

[0016] Some embodiments of this application also provide an ultrasound imaging system, including: a two-dimensional probe; and a processor. The processor is configured to perform any of the methods described above.

[0017] Some embodiments of this application also provide a non-transitory computer-readable medium storing a computer program having at least one code segment that can be executed by a machine to cause the machine to perform the steps of any of the methods described above.

[0018] It should be understood that the brief description provided above is intended to introduce some concepts further described in the detailed embodiments in a simplified form. This is not intended to identify key or essential features of the claimed subject matter, the scope of which is uniquely defined by the claims following the detailed description. Furthermore, the claimed subject matter is not limited to the implementation of any shortcomings mentioned above or in any paragraph of this disclosure. Attached Figure Description

[0019] This application will be better understood by referring to the accompanying drawings and by reading the following description of non-limiting embodiments, in which:

[0020] Figure 1 These are schematic block diagrams of embodiments of an ultrasound imaging system according to some embodiments;

[0021] Figure 2 This application illustrates methods for performing ultrasound imaging using a two-dimensional probe in some embodiments;

[0022] Figure 3 A schematic diagram of a two-dimensional probe including multiple rows of primitives is shown;

[0023] Figure 4 A schematic diagram of a two-dimensional ultrasound image including the interventional needle is shown;

[0024] Figure 5 This illustration shows a schematic diagram of two-dimensional ultrasound imaging using primitives in different rows in one embodiment of this application;

[0025] Figure 6 A schematic diagram of imaging key anatomical features is shown in an embodiment of this application. Detailed Implementation

[0026] The following describes specific embodiments of this application. It should be noted that, in order to maintain brevity, this application cannot provide a detailed description of all features of the actual embodiments. It should be understood that, in the actual implementation of any embodiment, just as in any engineering or design project, various specific decisions are often made to achieve the developer's specific goals and to meet system-related or business-related constraints, and this can change from one embodiment to another. Furthermore, it is understood that although the efforts made in this development process may be complex and lengthy, for those skilled in the art related to the content disclosed in this application, changes in design, manufacturing, or production based on the technical content disclosed in this disclosure are merely conventional technical means and should not be construed as insufficient content of this disclosure.

[0027] Unless otherwise defined, the technical or scientific terms used in the claims and description shall have the ordinary meaning understood by one of ordinary skill in the art. The terms "first," "second," and similar terms used in this application and the claims do not indicate any order, quantity, or importance, but are merely used to distinguish different components. The terms "an" or "a" and similar terms do not indicate a quantity limitation, but rather indicate the presence of at least one. The terms "comprising" or "including" and similar terms mean that the element or object preceding "comprising" or "including" encompasses the element or object listed following "comprising" or "including" and its equivalents, and do not exclude other elements or objects. The terms "connected" or "linked" and similar terms are not limited to physical or mechanical connections, nor are they limited to direct or indirect connections.

[0028] Figure 1 A schematic block diagram illustrating an embodiment of an ultrasound imaging system 100 is shown. The ultrasound imaging system 100 may include a controller circuit 102 operatively connected to a communication circuit 104, a display device 138, a user interface 142, a two-dimensional probe 126, and a memory 106.

[0029] The controller circuit 102 is configured to control the operation of the ultrasound imaging system 100. The controller circuit 102 may include one or more processors. Optionally, the controller circuit 102 may include a central processing unit (CPU), one or more microprocessors, a graphics processing unit (GPU), or any other electronic component capable of processing input data according to specific logical instructions. Optionally, the controller circuit 102 may include and / or represent one or more hardware circuits or circuit systems that include, connect to, or include and connect to one or more processors, controllers, and / or other hardware logic-based devices. Additionally or alternatively, the controller circuit 102 may execute instructions stored on a tangible and non-transitory computer-readable medium (e.g., memory 106).

[0030] Controller circuitry 102 may be operatively connected to and / or control communication circuitry 104. Communication circuitry 104 is configured to receive and / or transmit information along a bidirectional communication link with one or more alternative ultrasound imaging systems, remote servers, etc. The remote server may represent patient information, machine learning algorithms, remotely stored medical images from previous scans and / or treatments of the patient, etc. Communication circuitry 104 may represent hardware for transmitting and / or receiving data along the bidirectional communication link. Communication circuitry 104 may include transceivers, receivers, transceivers, etc., and associated circuitry (e.g., antennas) for wired and / or wireless communication (e.g., transmitting and / or receiving) with the one or more alternative ultrasound imaging systems, remote servers, etc. For example, protocol firmware for transmitting and / or receiving data along the bidirectional communication link may be stored in memory 106 accessible by controller circuitry 102. The protocol firmware provides controller circuitry 102 with network protocol syntax to assemble data packets, establish and / or segment data received along the bidirectional communication link, etc.

[0031] The bidirectional communication link can be a wired (e.g., via a physical conductor) and / or wireless (e.g., using radio frequency (RF)) link for exchanging data (e.g., data packets) between one or more alternative ultrasound imaging systems, remote servers, etc. The bidirectional communication link can be based on standard communication protocols such as Ethernet, TCP / IP, WiFi, 802.11, custom communication protocols, Bluetooth, etc.

[0032] The controller circuit 102 is operatively connected to the display device 138 and the user interface 142. The display device 138 may include one or more liquid crystal displays (e.g., light-emitting diode (LED) backlighting), organic light-emitting diode (OLED) displays, plasma displays, CRT displays, etc. The display device 138 may display patient information received from the controller circuit 102, one or more medical images and / or videos, graphical user interfaces or components, one or more 2D, 3D, or 4D ultrasound image datasets from ultrasound data stored in memory 106, or currently acquired anatomical measurements, diagnostic, processing information, etc.

[0033] User interface 142 controls the operation of controller circuitry 102 and ultrasound imaging system 100. User interface 142 is configured to receive input from clinicians and / or operators of ultrasound imaging system 100. User interface 142 may include a keyboard, mouse, trackball, touchpad, one or more physical buttons, etc. Optionally, display device 138 may be a touchscreen display device that includes at least a portion of user interface 142. For example, a portion of user interface 142 may correspond to a graphical user interface (GUI) generated by controller circuitry 102 and displayed on display device 138. The touchscreen display device can detect the presence of a touch from an operator on display device 138 and can also identify the position of the touch relative to a surface area of ​​display device 138. For example, a user can select one or more user interface components of the user interface (GUI) shown on display device by touching or contacting display device 138. User interface components may correspond to icons, text boxes, menu bars, etc., shown on display device 138. Clinicians can select, manipulate, utilize, interact with, etc., user interface components to issue commands to controller circuitry 102 to perform one or more operations as described in this application. For example, touch can be applied through at least one of a person's hand, gloves, stylus, etc.

[0034] Memory 106 includes parameters, algorithms, protocols for one or more ultrasound examinations, data values, etc., for controller circuitry 102 to perform one or more operations described in this application. Memory 106 may be a tangible and non-transitory computer-readable medium, such as flash memory, RAM, ROM, EEPROM, etc. Memory 106 may include one or more learning algorithms configured to define image analysis algorithms (e.g., deep learning algorithms including convolutional neural network algorithms, machine learning algorithms such as decision tree learning algorithms, or conventional computer vision algorithms, etc.). When executing the image analysis algorithm, controller circuitry 102 is configured to identify certain anatomical features in the medical image. The specific type of anatomical feature may be selected according to any of the embodiments described below in this application. In some embodiments, the identifiable anatomical feature is an object with high acoustic impedance. A high acoustic impedance object can be determined according to general understanding in the field of ultrasound imaging, and can be understood as an object whose impedance to ultrasound signals is sufficient to affect the imaging quality of the underlying area. Such high impedance may be due to strong reflection, absorption, etc., of sound waves. In different imaging scenarios, the tissue to be imaged may include different high acoustic impedance objects. For example, in ultrasound-assisted puncture surgery, a high acoustic impedance object may include an interventional needle. Furthermore, some physiological structures within the tissue to be imaged may also be high acoustic impedance objects. For example, bones, stones, or calcifications can all be considered high acoustic impedance objects. Besides high acoustic impedance objects, the image analysis algorithm in this application embodiment can also be used to identify other anatomical features. For example, these could be key anatomical features of the tissue itself, such as at least one of nodules, glands, nerve nodes, or blood vessels. The specific configuration of the image analysis algorithm is illustrated below.

[0035] Image analysis algorithms can be defined by one or more algorithms to identify cross-sections of an object of interest based on one or more anatomical features within a medical image (e.g., boundaries, thickness, pixel value changes, valves, cavities, chambers, edges or inner layers, vascular structures, etc.) or modalities or patterns of the medical image (e.g., color Doppler flow). The one or more anatomical features can represent the characteristics of pixels and / or voxels in the medical image, such as histogram orientation gradients, point features, covariance features, binary pattern features, etc. For example, one or more deep neural networks can be used to define an image analysis algorithm based on predictions of object recognition within a medical image.

[0036] Image analysis algorithms may correspond to artificial neural networks formed by controller circuitry 102 and / or a remote server. The image analysis algorithm may be divided into two or more layers, such as an input layer that receives an input image, an output layer that outputs an output image, and / or one or more intermediate layers. Layers of the neural network represent different groups or sets of artificial neurons, which may represent different functions executed by controller circuitry 102 on an input image (e.g., an ultrasound image acquired and / or generated by ultrasound imaging system 100) to identify the input image. Artificial neurons in the layers of the neural network examine individual pixels in the input image. The artificial neurons apply different weights to the functions applied to the input image to attempt to identify objects in the input image. The neural network generates an output image by assigning or associating different pixels in the output image with different anatomical features based on the analysis of pixel characteristics. The output image may include the identification results for anatomical features. It is understood that the identification results may include the identification results for the type of anatomical feature, for example, a high acoustic impedance object (e.g., at least one of an interventional needle, bone, stone, or calcification), or, for example, a key anatomical feature (e.g., at least one of a nodule, gland, nerve node, or blood vessel). The recognition results may also include information such as the location and size of the aforementioned features. For example, the identified anatomical features can be highlighted using specific display methods.

[0037] Continue to refer to Figure 1 The ultrasonic imaging system 100 may include a two-dimensional (2D) probe 126. The 2D probe 126 has components such as an ultrasonic transducer, transmitter, transmit beamformer, and detector / SAP electronics (not shown). The detector / SAP electronics can be used to control the switching of transducer elements. The detector / SAP electronics can also be used to group the transducer elements into one or more sub-apers. The 2D probe 126 can be any type of probe, including linear probes, curved array probes, 1.25D arrays, 1.5D arrays, and 1.75D array probes. Compared to other probes such as four-dimensional (4D) probes, the 2D probe 126 can image a two-dimensional plane at a high frame rate while maintaining lower probe power, thus improving heat dissipation. The 2D probe 126 also has a smaller size and lower cost. The 2D probe 126 may include multiple rows of elements ( Figure 1 (Not shown). For example, it may include 3 rows of primitives. Or, it may include 5 rows of primitives or more.

[0038] The two-dimensional probe 126 can be configured to acquire ultrasound data or information from the patient's tissue to be imaged (e.g., organs such as the breast, heart, prostate, and corresponding skin surfaces outside the organs). The two-dimensional probe 126 is communicatively connected to the controller circuitry via a transmitter. The transmitter transmits signals to a beamformer based on acquisition settings received by the controller circuitry 102. These acquisition settings can define the amplitude, pulse width, frequency, gain setting, scan angle, power, time gain compensation (TGC), resolution, etc., of the ultrasound pulses emitted by the ultrasound transducer. The ultrasound transducer transmits pulsed ultrasound signals to the patient (e.g., the body). The acquisition settings can be defined by a user operating the user interface 142. The signals emitted by the transmitter then drive the ultrasound transducer.

[0039] An ultrasound transducer transmits pulsed ultrasound signals into the body (e.g., a patient) corresponding to an acquisition setup along one or more scanning planes. The ultrasound signal may include, for example, one or more reference pulses, one or more push pulses (e.g., shear waves), and / or one or more pulsed-wave Doppler pulses. At least a portion of the pulsed ultrasound signal is backscattered from the tissue to be imaged (e.g., organ, bone, heart, breast tissue, liver tissue, cardiac tissue, prostate tissue, neonatal brain, embryo, abdomen, etc.) to generate echoes. Depending on depth or movement, the echoes are delayed in time and / or frequency and received by the ultrasound transducer. The ultrasound signal can be used for imaging, for generating and / or tracking shear waves, for measuring changes in position or velocity within anatomical structures, differences in compressive displacement of tissues (e.g., strain), and / or for treatment and other uses. For example, a two-dimensional probe 126 may deliver low-energy pulses during imaging and tracking, deliver medium- to high-energy pulses to generate shear waves, and deliver high-energy pulses during treatment.

[0040] An ultrasonic transducer converts the received echo signal into an electrical signal that can be received by a receiver. The receiver may include one or more amplifiers, analog-to-digital converters (ADCs), etc. The receiver is configured to amplify the received echo signal after appropriate gain compensation and convert these analog signals received from each transducer element into digital signals that are sampled uniformly in time. The digital signals representing the received echoes are temporarily stored in memory 106. The digital signals correspond to the backscattered waves received by each transducer element at different times. After digitization, the signal retains the amplitude, frequency, and phase information of the backscattered waves.

[0041] Optionally, the controller circuit 102 can retrieve digitized signals stored in the memory 106 for use by the beamformer processor. For example, the controller circuit 102 can convert the digitized signals into baseband signals or compress the digitized signals.

[0042] In some embodiments, the controller circuit 102 may also include a beamforming processor. The beamforming processor may include one or more processors. If necessary, the beamforming processor may include a central processing unit (CPU), one or more microprocessors, or any other electronic component capable of processing input data according to specific logical instructions. Alternatively or additionally, the beamforming processor may execute instructions stored on a tangible and non-transitory computer-readable medium (e.g., memory 106) to perform beamforming calculations using any suitable beamforming method, such as adaptive beamforming, synthetic emission focusing, aberration correction, synthetic aperture, clutter suppression, and / or adaptive noise control, etc.

[0043] In some embodiments, the controller circuit 102 may also include a radio frequency (RF) processor. The beamformer processor performs beamforming on the digitized signals of the transducer elements and outputs an RF signal. The RF signal is then provided to an RF processor that processes the RF signal. The RF processor may include one or more processors. As needed, the RF processor may include a central processing unit (CPU), one or more microprocessors, or any other electronic component capable of processing input data according to specific logical instructions. Alternatively or additionally, the RF processor may execute instructions stored on a tangible and non-transitory computer-readable medium (e.g., memory 106). Optionally, the RF processor may be integrated with and / or part of the controller circuit 102. For example, operations described as being performed by the RF processor may be configured to be performed by the controller circuit 102.

[0044] The RF processor can generate different ultrasound image data types and / or modes, such as B-mode, color Doppler (e.g., color flow, velocity / power / variance), tissue Doppler (velocity), and Doppler energy, for multiple scanning planes or different scanning modes based on predetermined settings of a first model. For example, the RF processor can generate tissue Doppler data for multiple scanning planes. The RF processor collects information related to multiple data slices (e.g., I / Q, B-mode, color Doppler, tissue Doppler, and Doppler energy information) and stores the data information in memory 106, which may include timestamps and orientation / rotation information.

[0045] Optionally, the RF processor may include a composite demodulator (not shown) that demodulates the RF signal to form IQ data pairs representing the echo signal. The RF or IQ signal data may then be directly provided to memory 106 for storage (e.g., temporary storage). If necessary, the output of the beamformer processor may be directly transmitted to controller circuitry 102.

[0046] The controller circuit 102 may be configured to process the acquired ultrasound data (e.g., RF signal data or IQ data pairs) and prepare and / or generate ultrasound image data frames representing anatomical structures of interest for display on the display device 138. The acquired ultrasound data may be processed in real time by the controller circuit 102 during the scanning or treatment process of an ultrasound examination upon receipt of echo signals. Alternatively, the ultrasound data may be temporarily stored in the memory 106 during the scanning process and processed in a less real-time manner during current or offline operation.

[0047] In some embodiments, the ultrasound imaging system 100 described above can be used for two-dimensional ultrasound imaging. The obtained two-dimensional images can be used by doctors for diagnosis or treatment. In some scenarios, there may be objects with high acoustic impedance inside the tissue to be imaged. This will cause acoustic shadowing and affect the quality of ultrasound imaging. Based on this, improvements are proposed in some embodiments of this application.

[0048] refer to Figure 2 This illustration shows a method 200 for ultrasound imaging using a two-dimensional probe in some embodiments of this application. The two-dimensional probe can be a probe comprising multiple rows of primitives as described in any of the embodiments above. The method may include the following steps:

[0049] In step S201, a two-dimensional ultrasound image of the tissue to be imaged is acquired. This process can be implemented by a processor; for example, the processor can control the primitives of the two-dimensional probe to emit ultrasound signals into the tissue to be imaged and receive echo signals. Furthermore, the processor can process the echo signals to generate a two-dimensional ultrasound image of the tissue to be imaged.

[0050] In step S203, the ultrasound image is identified, and high acoustic impedance objects are determined based on the identification results. This step is performed by a processor. For example, the processor can execute the image analysis algorithm described in any of the embodiments above (e.g., an algorithm based on an artificial neural network, or based on other image analysis algorithms) to perform image recognition and determine high acoustic impedance objects.

[0051] In step S205, at least one row of primitives from the multiple rows is used to continue ultrasonic imaging of the high acoustic impedance object to obtain a first image of the high acoustic impedance object. As described above, the two-dimensional probe includes multiple rows of primitives. After identifying the high acoustic impedance object, the processor can control a portion of the rows of primitives to continue imaging the high acoustic impedance object. Continuing to image the high acoustic impedance object can be understood as controlling at least one row of primitives to emit ultrasonic signals toward the high acoustic impedance object, so that the imaging plane of the at least one row of primitives passes through the high acoustic impedance object.

[0052] In step S207, ultrasonic imaging is performed on at least a portion of the region below the high acoustic impedance material using at least another row of primitives from the multi-row primitives to obtain a second image of the at least a portion of the region below. Thus, the processor can simultaneously control the two-dimensional probe to image the acoustic shadow region below the high acoustic impedance material, and the second image effectively compensates for the insufficient image quality of the acoustic shadow region in the first image.

[0053] In step S209, the first image and the second image are synthesized to obtain a real-time synthesized image. After generating the first and second images, the processor can perform synthesis processing on the first and second images to obtain a complete two-dimensional image of the tissue to be imaged. The above process is performed in real time, so that doctors can obtain high-quality ultrasound images instantly when performing ultrasound scans using the above embodiments of this application. It should be noted that "real-time" allows for brief delays, such as delays in ultrasound signal transmission and reception, and minor delays in image processing.

[0054] The above-described embodiments of this application apply multiple rows of primitives originally used for two-dimensional ultrasound imaging in the same plane to imaging the plane where the high acoustic impedance object is located and to imaging the acoustic shadow region caused by the acoustic impedance object, thereby effectively eliminating the acoustic shadow region and improving image quality.

[0055] This approach can be used to improve image quality in a variety of applications. For example, during lesion screening, the acoustic shadowing caused by high acoustic impedance materials such as calcifications and stones can affect the image quality below them. Based on the method described in the above embodiments of this application, the quality of two-dimensional images can be effectively improved and acoustic shadowing eliminated during real-time imaging, thereby preventing the inability to effectively observe subtle lesions and other structures in the underlying area due to reduced image quality. As another example, during puncture surgery, the puncture needle, being a high acoustic impedance material, may create an acoustic shadowing area below it. The implementation method of this application can effectively eliminate acoustic shadowing, thereby preventing a decrease in surgical confidence caused by the inability to observe the overall image during puncture.

[0056] The following is combined Figure 3 The implementation methods of this application will be described in more detail. Figure 3A schematic diagram of a two-dimensional probe 300 comprising multiple rows of primitives is shown. The two-dimensional probe 300 includes three rows of primitives 301-303. The first row of primitives 301 and the third row of primitives 303 are located on either side, and the second row of primitives 302 is located in the middle. In conventional two-dimensional ultrasound imaging mode, these three rows of primitives of the two-dimensional probe 300 generally image within the same plane. When there is a high acoustic impedance object in the imaging plane, it may obstruct the downward propagation of ultrasound waves, resulting in a lack of acoustic signals about the obstructed area within the plane, thus forming an acoustic shadow. In some embodiments of this application, at least one row of primitives of the two-dimensional probe 300 (e.g., the middle row of primitives, i.e., the second row of primitives 302) can be configured to continue imaging the high acoustic impedance object. At least another row of primitives in the two-dimensional probe 300 (e.g., the two side primitives, i.e., the first row of primitives 301 and the third row of primitives 303) can be adjusted to change the ultrasound signal emission angle so that the ultrasound signal avoids the high acoustic impedance object and passes beneath it. This eliminates the acoustic shadowing area and improves the quality of ultrasound imaging.

[0057] It is important to note that Figure 3 This is merely an exemplary illustration of a two-dimensional probe. In other embodiments, the number of rows of primitives included in the two-dimensional probe can be different, for example, it can be more than three rows. Furthermore, the number of primitives in each row can also be adjusted.

[0058] As described above, the imaging method of this application is applicable to various scenarios where high acoustic impedance objects exist. The following explanation uses an interventional needle as an example. Interventional needles are typically needle-shaped objects made of metal, used for lesion sampling or drug delivery. During interventional procedures, doctors often use two-dimensional ultrasound imaging technology for auxiliary imaging, thereby determining the real-time position of the interventional needle and the distance between the needle and the lesion. It can also be used to determine whether a sufficient safe distance exists between the needle and key anatomical features. Interventional needles are a type of high acoustic impedance object; during two-dimensional ultrasound imaging, the needle will cause acoustic shadowing. Combined with… Figure 4 Provide a detailed explanation. Figure 4 A schematic diagram of a two-dimensional ultrasound image 400 including an interventional needle 401 is shown. The interventional needle 401 appears brighter in the image due to its strong echo signal. Simultaneously, because the interventional needle 401 obstructs the downward propagation of the ultrasound signal, the image quality of the area below the interventional needle 401 is reduced, and shadows appear, such as... Figure 4 As shown, this is represented by the acoustic shadowing region 402. The acoustic shadowing region 402 may cause the loss of crucial information. For example, if it contains key anatomical features such as nodules, nerve nodes, blood vessels, or glands, the physician needs to clearly know the relative positions of the interventional needle 401 and these key features to make accurate interventional path planning. The presence of the acoustic shadowing region 402 may affect such judgment and planning.

[0059] Several embodiments throughout this application are developed in response to the aforementioned problems. For example, Figure 2 The corresponding embodiment can eliminate the aforementioned acoustic shadow region 402 while maintaining two-dimensional ultrasound imaging. Furthermore, the embodiment of this application does not require the assistance of other probes or the replacement of other probes, which ensures that the imaging process remains consistent with the doctor's original usage habits.

[0060] Please continue to refer to this. Figure 5 The diagram illustrates a two-dimensional ultrasound imaging process using primitives in different rows, as shown in an embodiment of this application.

[0061] Figure 5 A illustrates image recognition of an ultrasound image 500 to identify a high acoustic impedance object (e.g., an interventional needle 501). Due to the presence of the interventional needle 501, an acoustic shadow appears below it in the ultrasound image 500, causing image quality degradation. Furthermore, the image recognition method can refer to any of the embodiments described above in this application. For example, an artificial neural network can be used to perform image recognition on the ultrasound image 500 to directly identify the interventional needle 501. Alternatively, any other type of algorithm can be used, such as analyzing the grayscale values ​​of the image and setting a certain threshold for image segmentation, segmenting pixels with grayscale values ​​greater than a certain threshold, thereby automatically identifying the interventional needle 501. This application is not limited to this method.

[0062] Furthermore, such as Figure 5 As shown in b, after identifying the interventional needle 501, the upper region 511 and the lower region 512 of the interventional needle 501 can be determined. It should be noted that, for better illustration of the solution of this application, the upper region 511 and the lower region 512 are shown with different outlines and do not represent the actual image. The upper region 511 is not affected by the acoustic impedance of the interventional needle 501 and can form a normal image, while the lower region 512 is affected by the interventional needle 501, resulting in a decrease in image quality.

[0063] In the embodiments of this application, different imaging strategies can be adopted depending on the differences between the upper region 511 and the lower region 512. For example... Figure 5 As shown in c, a two-dimensional probe comprising multiple rows of primitives is used (for simplicity of description, ...). Figure 5 In the embodiment shown, only the first row of primitives 521, the second row of primitives 522, and the third row of primitives 523 of the two-dimensional probe are shown for imaging. Multiple rows of primitives can be used for imaging different regions. At least one row of primitives (e.g., Figure 5The second row of basic units 522 shown is used for imaging the upper region 511. Since the upper region 511 is not affected by the acoustic impedance of the intervention needle 501, the second row of basic units 522 can continue to perform imaging within the original imaging plane to generate the first image. Figure 5 (The first image is not shown). It can be understood that the original imaging plane may include the interventional needle 501, and correspondingly, the second row of primitives 522 can image the interventional needle 501. Furthermore, at least another row of primitives ( Figure 5 (Taking the first row of primitives 521 and the third row of primitives 523 as examples) can image at least a portion of the lower region 512 to generate a second image. Figure 5 (Second image not shown). Figure 5 As shown, the ultrasonic emission directions of the first and third row basic units 521, 523 and the second row basic unit 522 can be located on different planes. Thus, the first and third row basic units 521, 523 can "bypass" the intervention needle 501 and image the area below it, thereby avoiding interference caused by sound shadow.

[0064] Furthermore, images generated from primitives in different rows can be synthesized to obtain a composite image of the tissue to be imaged. For example... Figure 5 As shown in d, compared to Figure 5 The ultrasound image 500 and the composite image 502 effectively eliminate the acoustic shadow area below the intervention needle 501, thus achieving higher image quality.

[0065] The image synthesis method is described below as an example. After generating the first image using at least one row of primitives (such as the second row primitive 522) and then generating the first image using at least another row of primitives (such as the first and third rows primitives 521 and 523), the following can be described:

[0066] Select a first portion of the first image that includes the high acoustic impedance object and the area above it; select a second portion of the second image that includes the area below the high acoustic impedance object; and combine the first portion and the second portion.

[0067] It can be understood that, through the above method, the sound and shadow region in the first image can be covered by the second part of the second image, thereby obtaining a synthesized high-quality image.

[0068] The above-described method of this application enables the two-dimensional probe to perform imaging and synthesis in different imaging planes by adjusting the ultrasonic emission angles of the primitives in different rows. Other ultrasonic imaging parameters, such as the frequency and power of the ultrasonic waves from the primitives in different rows, can be flexibly selected. In some embodiments, the primitives in different rows can be selected with the same or similar parameters, except for the emission angle, such as the same frequency. This ensures the similarity between the first and second images as much as possible, making the synthesized image uniform overall.

[0069] The following is an exemplary description of controlling the ultrasonic wave emission direction of different rows of primitives for ultrasonic imaging.

[0070] In some implementations, at least one row of basic elements from the above multiple rows (e.g., Figure 5 The second row of primitives 522) for ultrasound imaging of high acoustic impedance materials (e.g., interventional needle 501) may include:

[0071] Based on the relative positions of the high acoustic impedance material and the at least one row of basic elements, the ultrasonic emission direction of the at least one row of basic elements is adjusted so that it is perpendicular to the surface of the high acoustic impedance material.

[0072] In some embodiments, the adjustment of the ultrasonic emission method of the at least one row of primitives is performed within an imaging plane that passes through the high acoustic impedance material.

[0073] Still with Figure 5 Let's take an example. While the second row of basic elements 522 continues to perform ultrasound imaging within the original imaging plane, the relative position between the second row of basic elements 522 and the interventional needle 501 can be considered. Specifically, the angle between the second row of basic elements 522 and the interventional needle 501 on the same plane can be considered. Furthermore, the ultrasound emission direction of the second row of basic elements 522 can be adjusted according to this angle, causing it to deflect within the original imaging plane and ultimately become perpendicular to the interventional needle 501. In this way, without changing the imaging plane, the ultrasound echo signal of the interventional needle 501 can be enhanced as much as possible, thereby improving the ultrasound image quality of the interventional needle 501.

[0074] In other embodiments, the at least one other row of primitives (e.g., Figure 5 In the embodiment, the first and third rows of primitives 521 and 523) performing ultrasound imaging on the at least part of the lower region may include:

[0075] Based on the relative positions of the high acoustic impedance material and the at least other row of basic elements, the ultrasonic wave emission direction of the at least other row of basic elements is adjusted so that it at least partially passes through the tissue to be imaged below the high acoustic impedance material.

[0076] Optionally, the adjustment of the ultrasonic emission direction of the at least other row of primitives is performed on an imaging plane different from that of the at least one row of primitives.

[0077] refer to Figure 5 An example is provided. Figure 5 In this design, the emission directions of the first row of primitives 521 and the third row of primitives 523 can be deflected to avoid the high acoustic impedance object (intervention needle 501), thereby passing at least partially through the tissue to be imaged in the region 512 below the intervention needle 501. The adjustment of the ultrasonic signal emission directions of the first row of primitives 521 and the third row of primitives 523 can be achieved by adjusting them to different emission planes. That is, they can be adjusted from an emission plane that is essentially the same as that of the second row of primitives 522 to intersecting planes, intersecting in the region below the intervention needle 501, i.e., the acoustic shadow region. Thus, the first row of primitives 521 and the third row of primitives 523 can eliminate the acoustic shadow region.

[0078] Understandable. Figure 5 The corresponding embodiment uses a three-row primitive as an example for illustrative description; however, the embodiments of this application are not limited to this. In other embodiments, the number of rows of primitives in the two-dimensional probe can be other numbers, such as 5 rows or 7 rows, etc. Furthermore, Figure 5 In the embodiments described, a middle row of primitives is used to continuously image high acoustic impedance objects, such as interventional needles, and primitives on both sides are selected to image the acoustic shadow region. However, under the teachings of this disclosure, the functions performed by different rows of primitives can be adjusted.

[0079] In some embodiments of this application, the imaging method can be further improved according to the specific application scenario. For example, when using the ultrasound imaging method of this application to assist in interventional surgery imaging, the high acoustic impedance material may include the interventional material, and correspondingly, the method of this application may further include:

[0080] In response to changes in the position of the interventional needle within the tissue to be imaged, the ultrasonic emission directions of the at least one row of primitives and the at least another row of primitives are adjusted in real time to continuously acquire images of the interventional needle and images of at least a portion of the region below the interventional needle.

[0081] In other words, for situations where the position of a high acoustic impedance object, i.e., the interventional needle, within the tissue to be imaged changes, the above embodiments of this application can also make targeted adjustments to the ultrasound waves of the imaging elements based on the specific position of the interventional needle. For example, as the interventional needle advances, the above-mentioned at least another row of elements can adjust the direction of ultrasound wave emission based on the position change of the acoustic shadow region (i.e., the region below the interventional needle), thereby ensuring that even as the acoustic shadow region changes continuously, a high-quality image of at least a portion of the region below the interventional needle can be obtained; and / or, the direction of ultrasound wave emission of the above-mentioned at least one row of elements is also adjusted in real time based on the position of the interventional needle, for example, it can be adjusted to be perpendicular to the interventional needle in real time as the position of the interventional needle changes, thereby obtaining a high-quality ultrasound image of the interventional needle.

[0082] The inventors further recognized that the imaging efficiency of the primitives of a two-dimensional probe may be limited. At least with this in mind, improvements are proposed in some embodiments of this application to enable the limited primitives to be used as much as possible for imaging key anatomical features.

[0083] In some embodiments, the method of this application further includes: determining key anatomical features below the high acoustic impedance material based on the identification result, the key anatomical features including at least one of nodules, glands, nerve nodes, and blood vessels.

[0084] This implementation method can locate the position of key anatomical features, thereby providing guidance for subsequent ultrasound imaging.

[0085] Furthermore, in a related embodiment, performing ultrasound imaging of the at least part of the area below using the at least other row of primitives includes: controlling the ultrasonic wave emission direction of the at least other row of primitives based on the position of the structure of interest, so that it at least partially passes through the structure of interest.

[0086] This implementation allows for the maximum utilization of the at least one additional row of primitives to image key anatomical features. This can be crucial for some use cases, such as interventional procedures. During interventional procedures, physicians are typically concerned with key anatomical features beneath the interventional needle, ensuring sufficient distance between them to avoid damage. The method described in this application prioritizes acoustic shadowing removal for key anatomical features, thereby enhancing the physician's confidence in diagnosis and treatment.

[0087] In some embodiments, the method of this application further includes: displaying the synthesized image in real time; and highlighting the key anatomical features in the synthesized image.

[0088] This approach makes it easier for doctors to observe key anatomical features, avoiding adverse effects such as decreased confidence in diagnosis and treatment during intervention.

[0089] The following is through Figure 6 The above implementation methods will now be described in more detail. Figure 6 The illustration shows schematic diagrams of imaging key anatomical features in some embodiments of this application.

[0090] like Figure 6 As shown, ultrasound image 600 includes key anatomical features 601. Figure 6 In this embodiment, the key anatomical feature 601 is shown in the form of a tubercle (e.g., the greater tubercle of the humerus, GT). In this embodiment, image recognition is used not only to identify high acoustic impedance objects such as interventional needles, but also to identify the key anatomical feature 601, thereby determining its size, location, and other detailed information.

[0091] Furthermore, at least one row of primitives, such as the first row of primitives 621 and the third row of primitives 623, can be controlled to selectively transmit and receive ultrasound waves toward the key anatomical feature 601, thereby allocating as many limited ultrasound signal paths as possible to the key anatomical feature 601. Specific control methods for the primitives can be found in any of the embodiments described above, including the control method for the second row of primitives 622, which will not be repeated here.

[0092] It is understood that the aforementioned process of identifying key anatomical features 601 can occur before the interventional procedure, for example, before the interventional needle enters the tissue to be imaged. Alternatively, it can occur during the interventional procedure, for example, when the interventional needle has just entered the tissue to be imaged. This application does not impose a single limitation.

[0093] Figure 6 The ultrasound image 600 shown is a composite image obtained through the image synthesis method of this application. In some embodiments, in addition to real-time display of the composite image, key anatomical features 601 identified can also be highlighted. The highlighting method can be as follows: Figure 6 As shown, the outer contour 602 of the key anatomical feature 601 is displayed. This allows doctors to more easily observe the specific location of the key anatomical feature 601 when viewing the image, thus enabling them to make timely and accurate clinical judgments.

[0094] Thus far, this application has described several ultrasound imaging methods and their effects. In another embodiment, this disclosure also provides an ultrasound imaging system, which may include:

[0095] Two-dimensional probe; and

[0096] A processor. The processor is configured to perform the methods described in any of the embodiments described above in this application.

[0097] It is understood that the specific structure of the two-dimensional probe can refer to any of the embodiments described above in this application or the prior art. Similarly, the processor can also refer to this application. Figure 1 Or as described in other embodiments, for example, it may be Figure 1 The controller circuit 102 contains one or more processors. Furthermore, the ultrasound imaging system may also include other components described in any embodiment of this application, which will not be repeated here.

[0098] This disclosure also provides a computer program product, including computer-readable code, or a non-transitory computer-readable storage medium carrying computer-readable code, wherein when the computer-readable code is run in a processor of a medical device, the processor in the medical device performs the steps of the above method.

[0099] Some embodiments of this disclosure also provide a non-transitory computer-readable medium storing a computer program having at least one code segment that can be executed by a machine to cause the machine to perform the steps of the methods described in any of the embodiments above in this application.

[0100] Computer-readable storage media can be tangible devices capable of holding and storing instructions for use by an instruction execution device. Computer-readable storage media can be, for example, but not limited to, electrical storage devices, magnetic storage devices, optical storage devices, electromagnetic storage devices, semiconductor storage devices, or any suitable combination thereof. More specific examples (a non-exhaustive list) of computer-readable storage media include: portable computer disks, hard disks, random access memory (RAM), read-only memory (ROM), erasable programmable read-only memory (EPROM or flash memory), static random access memory (SRAM), portable compact disc read-only memory (CD-ROM), digital multifunction disc (DVD), memory sticks, floppy disks, mechanical encoding devices, such as punch cards or recessed protrusions storing instructions thereon, and any suitable combination thereof. The computer-readable storage media used herein are not to be construed as transient signals themselves, such as radio waves or other freely propagating electromagnetic waves, electromagnetic waves propagating through waveguides or other transmission media (e.g., light pulses through fiber optic cables), or electrical signals transmitted through wires.

[0101] The computer-readable program instructions described herein can be downloaded from computer-readable storage media to various computing / processing devices, or downloaded via a network, such as the Internet, local area network, wide area network, and / or wireless network, to an external computer or external storage device. The network may include copper transmission cables, fiber optic transmission, wireless transmission, routers, firewalls, switches, gateway computers, and / or edge servers. A network adapter card or network interface in each computing / processing device receives the computer-readable program instructions from the network and forwards them to the computer-readable storage media in the respective computing / processing device.

[0102] Computer program instructions used to perform the operations of this disclosure may be assembly instructions, instruction set architecture (ISA) instructions, machine instructions, machine-dependent instructions, microcode, firmware instructions, status setting data, or source code or object code written in any combination of one or more programming languages, including object-oriented programming languages ​​such as Smalltalk, C++, etc., and conventional procedural programming languages ​​such as the "C" language or similar programming languages. The computer-readable program instructions may execute entirely on the user's computer, partially on the user's computer, as a standalone software package, partially on the user's computer and partially on a remote computer, or entirely on a remote computer or server. In cases involving a remote computer, the remote computer may be connected to the user's computer via any type of network—including a local area network (LAN) or a wide area network (WAN)—or may be connected to an external computer (e.g., via the Internet using an Internet service provider). In some embodiments, electronic circuitry, such as programmable logic circuitry, field-programmable gate arrays (FPGAs), or programmable logic arrays (PLAs), is personalized by utilizing the status information of the computer-readable program instructions to implement various aspects of this disclosure.

[0103] The purpose of providing the above specific embodiments is to enable a more thorough and comprehensive understanding of the disclosure of this application, but this application is not limited to these specific embodiments. Those skilled in the art should understand that various modifications, equivalent substitutions, and changes can be made to this application, and all such changes should be within the protection scope of this application as long as they do not violate the spirit of this application.

Claims

1. A method for performing ultrasound imaging using a two-dimensional probe, the two-dimensional probe comprising multiple rows of primitives, the method comprising: Acquire two-dimensional ultrasound images of the tissue to be imaged; The ultrasound images are identified, and high acoustic impedance materials are determined based on the identification results. The high acoustic impedance material is further ultrasonically imaged using at least one row of the multiple rows of primitives to obtain a first image of the high acoustic impedance material. Ultrasonic imaging is performed on at least a portion of the region below the high acoustic impedance material using at least another row of primitives in the multi-row primitives to obtain a second image of the at least a portion of the region below the material. as well as The first image and the second image are combined to obtain a real-time composite image.

2. The method as described in claim 1, wherein, The high acoustic impedance material includes at least one of the following: interventional needle, bone, stone, and calcification.

3. The method as described in claim 1, wherein, Continuing to perform ultrasonic imaging on the high acoustic impedance material using at least one row of the multiple rows of primitives includes: Based on the relative positions of the high acoustic impedance material and the at least one row of basic elements, the ultrasonic emission direction of the at least one row of basic elements is adjusted so that it is perpendicular to the surface of the high acoustic impedance material.

4. The method of claim 3, wherein, The adjustment of the ultrasonic emission method of the at least one row of primitives is performed within an imaging plane that passes through the high acoustic impedance material.

5. The method of claim 1, wherein, Ultrasound imaging of the at least part of the underlying region using the at least another row of primitives includes: Based on the relative positions of the high acoustic impedance material and the at least other row of basic elements, the ultrasonic wave emission direction of the at least other row of basic elements is adjusted so that it at least partially passes through the tissue to be imaged below the high acoustic impedance material.

6. The method of claim 5, wherein, The adjustment of the ultrasonic emission direction of the at least other row of primitives is performed on an imaging plane different from that of the at least one row of primitives.

7. The method of claim 1, wherein, Also includes: Based on the identification results, key anatomical features beneath the high acoustic impedance object are determined, including at least one of nodules, glands, nerve nodes, and blood vessels.

8. The method of claim 7, wherein, Ultrasound imaging of the at least part of the underlying region using the at least another row of primitives includes: Based on the location of the key anatomical feature, the direction of ultrasound emission of the at least another row of primitives is controlled so that it passes at least partially through the key anatomical feature.

9. The method of claim 8, wherein, Also includes: The synthesized image is displayed in real time; as well as The key anatomical features are highlighted in the synthesized image.

10. The method of claim 1, wherein, The multi-row basic unit includes three rows of basic units, the at least one row of basic units includes the middle row of basic units in the three rows of basic units, and the at least another row of basic units includes the two outer rows of basic units in the three rows of basic units.

11. The method of claim 1, wherein, Combining the first image and the second image includes: Select a first portion of the first image that includes the high acoustic impedance object and the area above it; Select a second portion of the second image that includes the area below the high acoustic impedance object; and Combine the first part and the second part.

12. The method of claim 1, wherein, The high acoustic impedance material includes an interventional needle, and the method further includes: In response to changes in the position of the interventional needle within the tissue to be imaged, the ultrasonic emission directions of the at least one row of primitives and the at least another row of primitives are adjusted in real time to continuously acquire images of the interventional needle and images of at least a portion of the region below the interventional needle.

13. An ultrasound imaging system, comprising: Two-dimensional probe; as well as A processor configured to perform the method as described in any one of claims 1-12.

14. A non-transitory computer-readable medium storing a computer program having at least one code segment that is executable by a machine to cause the machine to perform the steps of the method according to any one of claims 1-12.

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