System and method of performing ultrasound imaging

Abstract

Systems and methods of performing ultrasound imaging. Ultrasonic information of a subject region may be acquired in response to an ultrasonic pulse emitted toward the subject region. The ultrasound information may include reflection information in response to the ultrasound pulse and supplemental information to the reflection information of the object region. One or more ultrasound images of at least a portion of the object region may be formed based on the reflection information. Further, the one or more ultrasound images may be modified based on supplemental information of the pair of reflection information to generate one or more enhanced ultrasound images from the one or more ultrasound images.

Description

[0001] CROSS-REFERENCE TO RELATED APPLICATIONS This application claims priority to U.S. Provisional Patent Application No. 62 / 827,984 to Glen W. McLaughlin et al., entitled "Sound Velocity Estimation for Regional Contrast Enhancement of Grayscale Images," filed on April 2, 2019, the entire contents of which are incorporated herein by this reference. Technical Field

[0002] The present invention relates to ultrasound imaging, and more particularly to modifying ultrasound images based on information supplementary to reflection information. Background Art

[0003] Ultrasound imaging is widely used to examine a variety of materials and objects in a variety of different applications. Ultrasound imaging provides a quick and easy tool to analyze materials and objects in a non-invasive manner. As a result, ultrasound imaging is particularly prevalent in medical practice as a disease diagnosis, treatment, and prevention tool. Specifically, due to its relatively non-invasive nature, low cost, and fast response time, ultrasound imaging is widely used throughout the medical industry to diagnose and prevent disease. Moreover, because ultrasound imaging is based on non-ionizing radiation, it does not carry the same risks as other diagnostic imaging tools (such as X-ray imaging or other imaging systems that use ionizing radiation).

[0004] Ultrasound images typically have limited contrast resolution because many clinically important structures have similar echogenicity to background tissue. This limitation has led physicians to use other imaging modalities to more easily visualize the contrast resolution between healthy and diseased tissue. Several techniques have been developed to improve the overall contrast resolution of ultrasound images, such as to increase the contrast resolution for background tissue with similar echogenicity. Specifically, techniques have been developed for compounding images with different frequencies, different orientations, or different nonlinear tissue properties, for example, harmonic imaging techniques have been developed. Although such techniques do provide improvements in the contrast resolution of ultrasound images, the amount of contrast resolution that can be achieved by these techniques is still insufficient. Summary of the invention

[0005] According to various embodiments, a method for performing ultrasound imaging includes: in response to an ultrasound pulse emitted toward an object area, collecting ultrasound information of the object area. The ultrasound information may include reflection information in response to the ultrasound pulse and supplementary information of the reflection information of the object area. The method may also include forming one or more ultrasound images of at least a portion of the object area based on the reflection information. In addition, the method may include modifying the one or more ultrasound images based on the supplementary information of the reflection information to generate one or more enhanced ultrasound images from the one or more ultrasound images.

[0006] In some embodiments, a system for performing ultrasound imaging includes an ultrasound transducer and a main processing console. The ultrasound transducer can collect ultrasound information of an object area in response to an ultrasound pulse emitted toward the object area. The ultrasound information may include reflection information in response to the ultrasound pulse and supplementary information of the reflection information of the object area. The main processing console can form one or more ultrasound images of at least a portion of the object area based on the reflection information. The main processing console can also modify the one or more ultrasound images based on the supplementary information of the reflection information to generate one or more enhanced ultrasound images from the one or more ultrasound images.

[0007] In various embodiments, a system for performing ultrasound imaging includes one or more processors and a computer-readable medium, which provides instructions accessible to the one or more processors to enable the one or more processors to collect ultrasound information of an object area in response to an ultrasound pulse emitted toward the object area. The ultrasound information may include reflection information in response to the ultrasound pulse and supplementary information to the reflection information of the object area. The instructions may also enable the one or more processors to form one or more ultrasound images of at least a portion of the object area based on the reflection information. In addition, the instructions may enable the one or more processors to modify the one or more ultrasound images based on the supplementary information to the reflection information to generate one or more enhanced ultrasound images from the one or more ultrasound images. BRIEF DESCRIPTION OF THE DRAWINGS

[0008] Figure 1 An example of an ultrasound system is shown.

[0009] Figure 2 is a flow chart of an example method for modifying an ultrasound image based on information supplemental to reflection information of an ultrasound pulse used to generate the ultrasound image.

[0010] Figure 3 is a flow chart of an example method for generating ultrasound images with enhanced contrast resolution by using sound velocity maps.

[0011] Figure 4 is an unenhanced B-mode image with 5 known targets that have propagation velocities different from the average propagation velocity.

[0012] Figure 5 yes Figure 4 Shown are sound velocity maps of the material and the actual propagation velocity of the ultrasound pulse in five regions in the B-mode image.

[0013] Figure 6 is based on Figure 5The sound velocity diagram shown in the figure indicates the propagation velocity of the material and the estimated propagation velocity deviation obtained from the mean of the five regions of the phantom.

[0014] Figure 7 is a composite image including a B-mode phantom and a superimposed sound velocity map, with the mean propagation velocity value removed.

[0015] Figure 8 It is an enhanced B-mode image with contrast resolution that is modified based on the sound velocity map to adjust the gain of areas of different propagation velocities. DETAILED DESCRIPTION

[0016] Enhancing ultrasound images continues to be an important area of ​​interest. In particular, it is very important that ultrasound images can be enhanced to accurately display information related to different types of tissue, such as in the same ultrasound image. This, in turn, can make it easier for doctors to diagnose diseases and provide treatment for the disease based on their diagnosis.

[0017] In particular, because clinically important structures often have similar echogenicity to background tissue, it becomes very difficult to create ultrasound images that represent distinguishing features between structures and background tissue. For example, because many clinically important structures have similar echogenicity to background tissue, ultrasound images often have limited contrast resolution. Subsequently, it is difficult for doctors to quickly and accurately diagnose diseases and provide treatments for such diseases based on these images.

[0018] Many attempts have been made to characterize underlying tissue properties with ultrasound. In particular, a technique has been used to measure the speed of sound propagation within tissue. However, it is difficult to obtain high-resolution sound velocity maps that can be used to correct for the wave divergence of the ultrasound emission. This makes it more difficult to characterize underlying tissue properties through ultrasound and ultimately provide physicians with the ability to quickly and accurately provide medical diagnoses and treatments.

[0019] Systems, methods, and computer-readable media for addressing these issues / deficiencies are described below. Specifically, the present technology relates to systems, methods, and computer-readable media for acquiring supplemental information to reflection information generated by an ultrasonic pulse and enhancing or otherwise modifying an ultrasonic image based on the supplemental information. More specifically, the present technology relates to systems, methods, and computer-readable media for identifying one or more regions to be modified in an ultrasonic image based on the supplemental information to the reflection information used to generate the image. Subsequently, the one or more regions can be modified based on the supplemental information, for example to improve the quality of the ultrasonic image or the contrast of the ultrasonic image.

[0020] Specifically, and as will be discussed in more detail later, a low-resolution sound velocity map can be generated based on the collected supplemental information to the reflection information. The sound velocity map can then be used to enhance the contrast resolution of the B-mode ultrasound image. The data used to generate the sound velocity map and the B-mode image can be the same and can be generated by the same transmit / receive profile. Alternatively, the data used to generate the sound velocity map and the B-mode image can be clearly collected by separate transmit / receive profiles, for example to optimize the performance of each mode.

[0021] Reference is now made to the accompanying drawings, in which like parts are represented by like reference numerals throughout this document. Some infrastructures that can be used with the embodiments disclosed herein are already available, such as general-purpose computers, computer programming tools and techniques, digital storage media, and communication networks. The computing device may include a processor, such as a microprocessor, a microcontroller, a logic circuit, and the like. The processor may include a special processing device, such as an ASIC, a PAL, a PLA, a PLD, an FPGA, or other custom or programmable device. The computing device may also include a computer-readable storage device, such as a non-volatile memory, a static RAM, a dynamic RAM, a ROM, a CD-ROM, a disk, a tape, a magnetic, an optical, a flash memory, or other non-temporary computer-readable storage medium.

[0022] Various aspects of some embodiments may be implemented using hardware, software, firmware, or a combination thereof. As used herein, a software module or component may include any type of computer instructions or computer executable code located within or on a computer-readable storage medium. A software module may, for example, include one or more physical or logical blocks of computer instructions, which may be organized into routines, programs, objects, components, data structures, etc., which perform one or more tasks or implement specific abstract data types.

[0023] In some embodiments, a particular software module may include different instructions stored in different locations of a computer-readable storage medium, which together implement the described functions of the module. In practice, a module may include a single instruction or multiple instructions, and may be distributed over multiple different code segments, between different programs, and across multiple computer-readable storage media. Some embodiments may be practiced in a distributed computing environment, where tasks are performed by remote processing devices linked through a communication network.

[0024] The embodiments of this invention will be best understood by reference to the accompanying drawings. As generally described and illustrated in the drawings of this invention, the components of the disclosed embodiments may be arranged and designed in a variety of different configurations. In addition, the features, structures, and operations associated with one embodiment may be applicable to or combined with the features, structures, or operations described in another embodiment. In other cases, well-known structures, materials, or operations are not shown or described in detail to avoid making various aspects of the present disclosure unclear.

[0025] Therefore, the following detailed description of the embodiments of the systems and methods herein is not intended to limit the scope of the claimed invention, but is merely representative of possible embodiments. In addition, the steps of the method do not necessarily have to be performed in any particular order, do not even have to be performed sequentially, and do not have to perform the steps only once.

[0026] Figure 1 1 is a schematic block diagram of an exemplary embodiment of a medical imaging device, such as an ultrasound imaging device 100. Those skilled in the art will recognize that the principles disclosed herein can be applied to a variety of medical imaging devices, including but not limited to X-ray imaging devices, computed tomography (CT) imaging devices, magnetic resonance imaging (MRI) devices, and positron emission tomography (PET) imaging devices. Thus, the components of each device can be combined with Figure 2 Different than shown.

[0027] In one embodiment, the ultrasound imaging device 100 may include an array focusing unit, referred to herein as a beamformer 102, by which image formation may be performed on a scan line by scan line basis. The device may be controlled by a main controller 104 implemented by a microprocessor or the like, which receives operator input through an operator interface and controls the various subsystems of the device 100.

[0028] For each scan line, the transmitter 106 generates a radio frequency (RF) excitation voltage pulse waveform and applies it to the transmit aperture (defined by a subarray of active elements in one embodiment) with appropriate timing to produce a focused acoustic beam along the scan line.

[0029] The RF echoes received by one or more receive apertures or receivers 108 are amplified, filtered, and then fed into the beamformer 102, which can perform dynamic receive focusing, i.e., rearrange the RF signals generated from the same location along each scan line. Collectively, the transmitter 106 and the receiver 108 can be components of the transducer 110. Various types of transducers 110 are known in the art of ultrasound imaging, such as linear probes, curved probes, and phased array probes.

[0030] The image processor 112 may perform processing tasks specific to the various active imaging modes, including 2D scan conversion, which converts image data from a grid of acoustic rays into an XY pixel image for display. For other modes, such as spectral Doppler mode, the image processor 112 may perform wall filtering followed by spectral analysis of the Doppler shifted signal samples, typically using a sliding FFT window. The image processor 112 may also generate stereo audio signal outputs corresponding to the forward and reverse flow signals. In cooperation with the main controller 104, the image processor 112 may also format images from two or more active imaging modes, including display annotations, graphic overlays, and playback of movies and recorded timeline data.

[0031] The cine memory 114 provides resident digital image storage to enable single or multiple image cycles and serves as a buffer for transferring images to a digital archival device such as a hard drive or optical storage device. In some systems, video images at the end of the data processing path may be stored in the cine memory. In state-of-the-art systems, beamformed data after amplitude detection may also be stored in the cine memory 114. For spectral Doppler mode, baseband Doppler I / Q data after wall filtering of a user-selected sampling gate may be stored in the cine memory 114. Subsequently, a display 116 such as a computer monitor may display the ultrasound image created by the image processor 112 and / or an image created using the data stored in the cine memory 114.

[0032] The beamformer 102, the main controller 104, the image processor 112, the cine memory 114, and the display 116 may be included as part of a main processing console 118 of the ultrasound imaging device 100, which may include more or fewer components or subsystems than those illustrated. The ultrasound transducer 110 may be incorporated into a device separate from the main processing console 118, such as into a separate device that is wired or wirelessly connected to the main processing console 118. This allows for easier manipulation of the ultrasound transducer 110 when performing a particular ultrasound procedure on a patient. In addition, the transducer 110 may be an array transducer that includes an array of transmit and receive elements for transmitting and receiving ultrasound waves.

[0033] Those skilled in the art will recognize that a wide variety of ultrasonic imaging devices are available on the market, and that additional details regarding how images are generated are not necessary for a thorough understanding of the principles disclosed herein. Specifically, the systems, methods, and computer-readable media described herein can be applied by applicable ultrasonic imaging devices in a wide variety of ultrasonic imaging devices available on the market.

[0034] Figure 2is a flow chart 200 of an example method for modifying an ultrasound image based on information supplemental to reflection information of an ultrasound pulse used to generate the ultrasound image. Figure 2 The example methods shown in and other methods and techniques for ultrasound imaging described herein may be performed by applicable ultrasound imaging systems, such as Figure 1 The ultrasound system 100 is shown. For example, the techniques described herein for ultrasound imaging may be implemented using one or both of the ultrasound transducer 110 and the main processing console 118 (eg, the image processor 112 ) of the ultrasound system 100 .

[0035] In step 202, ultrasound information of the object area is collected. The ultrasound information includes reflection information generated in response to the ultrasound pulse emitted toward the object area and supplementary information of the reflection information. Specifically, reflection information generated based on the interaction between the ultrasound pulse and the object area can be collected in step 202. In addition, supplementary information to the reflection information generated based on the interaction between the ultrasound pulse and the object area can be collected in step 202. The reflection information and the supplementary information can be generated by applicable ultrasound components, such as Figure 1 An ultrasonic transducer 110 is shown.

[0036] The reflection information includes applicable information for generating an ultrasound image of at least a portion of the object region. Specifically, the reflection information may include information of reflections of an ultrasound pulse emitted into the object region, such as information of a backscattered ultrasound pulse. In turn, as will be discussed in more detail later, the reflected information may be used to generate an ultrasound image by an applicable imaging / image formation technique.

[0037] The supplementary information to the reflection information includes applicable information that can be collected from the ultrasonic pulse emitted toward the object area. Specifically, the supplementary information to the reflection information may include applicable information that can be collected from the ultrasonic pulse that is not used in directly forming the ultrasonic image. Specifically, the supplementary information to the reflection information may include the propagation speed of the ultrasonic pulse in the interaction with the object area, information related to the elasticity of the object area, information related to the stiffness of the object area, and the value of the acoustic nonlinear parameter associated with the object area. For example, the supplementary information may include the sound speed of the ultrasonic pulse when the ultrasonic pulse interacts with the object area and is reflected from the object area. In another example, the supplementary information to the reflection information may include changes in the transverse spatial spectrum signal at different depths.

[0038] The reflection information and the supplemental information can be generated by the same ultrasound pulse emitted toward the object area. Specifically, the reflection information and the supplemental information to the reflection information can be generated by the same ultrasound emission and reception profile. For example, a B-mode image can be generated by a cross-frame compounding of image data, such as a compounding of 2 to 9 frames of image data. As described below, the same ultrasound pulse used in creating a composite frame of image data can also be used to generate a certain number (e.g., 2 to 9) of sound velocity maps. Furthermore, the sound velocity maps can be combined to generate an accurate estimate of the speed of sound.

[0039] In addition, the reflection information and the supplementary information can be generated respectively by different ultrasonic pulses emitted toward the object area. Specifically, the reflection information and the supplementary information can be generated respectively by separate ultrasonic emission and reception profiles. For example, a first ultrasonic emission and reception profile can be applied to generate reflection information, and a second ultrasonic emission and reception profile can be applied to generate supplementary information separated from the reflection information. For example, and with respect to the propagation velocity as supplementary information, the ideal emission profile for estimating the propagation velocity is not necessarily the optimized profile for B-mode imaging, and vice versa. Therefore, supplementary information for identifying the propagation velocity can be generated separately from the reflection information used to perform B-mode imaging.

[0040] The reflection information and the supplementary information can be generated by the same ultrasound transmit-receive profile based on the characteristics of the object area. Specifically, if the tissue being imaged is moving rapidly, the reflection information and the supplementary information can be generated by the ultrasound transmit-receive profile. For example, if the heart is the object area, since the heart is a rapidly moving structure, the reflection information and the supplementary information can be generated by the same ultrasound pulse emitted toward the heart. In addition, the reflection information and the supplementary information can be generated separately by different ultrasound transmit-receive profiles based on the characteristics of the object area. Specifically, if the tissue being imaged is moving slowly, the reflection information and the supplementary information can be generated by different ultrasound transmit-receive profiles. For example, if the thyroid gland is the object area, since the thyroid gland is a slowly moving structure, the reflection information and the supplementary information can be generated by different ultrasound pulses emitted toward the thyroid gland.

[0041] Supplementary information may be generated on multiple ultrasound emission and reception profiles to generate composite supplementary information. For example and as previously described, multiple sound velocity maps may be generated on multiple ultrasound emission and reception profiles to generate composite supplementary information including multiple sound velocity maps. Furthermore, in this example, the multiple sound velocity maps may be compounded or otherwise combined to form a composite sound velocity map of composite supplementary information. Composite supplementary information may be generated by multiple emission and reception profiles separated from the emission and reception profiles used in generating reflection information. Furthermore, composite supplementary information may be generated by multiple emission and reception profiles also used to generate reflection information. As will be discussed in more detail later, composite supplementary information may be used to modify one or more ultrasound images generated by reflection information.

[0042] When composite supplementary information is formed by multiple ultrasound transmission and reception profiles, artifacts can be filtered out from the supplementary information used to generate the composite supplementary information. Specifically, when forming the composite supplementary information, the supplementary information can be combined to filter out artifacts from the supplementary information. For example, when multiple sound speed maps are created by different transmission sources, the artifacts generated in each map will not be configured on the sound speed map relative to the object area. Then, when the sound speed maps are combined, the total number of artifacts in the combined sound speed map (e.g., composite supplementary information) can be reduced or otherwise eliminated. This can result in improvements in using composite supplementary information to enhance or otherwise modify ultrasound images.

[0043] In step 204, one or more ultrasound images of at least a portion of the object region are formed from the reflection information. The ultrasound images formed in step 204 can be generated from the reflection information using an applicable technique. Specifically, a B-mode ultrasound image can be formed from the reflection information using one or more applicable B-mode imaging techniques. Examples of B-mode imaging techniques include fundamental wave imaging techniques, fundamental wave spatial compound imaging techniques, harmonic imaging techniques, harmonic spatial compound imaging techniques, fundamental wave and harmonic wave compound imaging techniques, and fundamental wave and harmonic wave spatial compound imaging techniques.

[0044] At step 206, the one or more ultrasound images are modified based on the supplemental information to the reflection information to produce one or more enhanced ultrasound images. Specifically, the ultrasound images can be modified to present information related to the object region in a clearer and more accurate manner. For example, the contrast in the image can be modified to more clearly display different regions corresponding to different types of tissue in the image of the object region.

[0045] In modifying one or more ultrasound images based on the supplemental information, one or more regions may be identified in the ultrasound image based on the supplemental information. Then, for example, in response to identifying the one or more regions, the identified regions in the ultrasound image may be modified or enhanced to ultimately modify the one or more ultrasound images. For example, a region in the ultrasound image corresponding to cardiac tissue in the object region may be identified based on the supplemental information. As described below, the region in the ultrasound image corresponding to the cardiac tissue may be modified or otherwise enhanced to highlight the cardiac tissue in the ultrasound image.

[0046] The one or more ultrasound images may be modified based on the relationship between the supplementary information and the mean of the supplementary information. The mean of the supplementary information may correspond to all or part of the entire object area in the one or more ultrasound images. With regard to the propagation velocity, the mean of the propagation velocity in the entire or part of the object area may be identified from the propagation velocity included in the supplementary information. Furthermore, one or more regions in the ultrasound image may be identified based on the change in the propagation velocity relative to the mean of the propagation velocity. Specifically, the one or more regions may be identified based on the change in the propagation velocity corresponding to the one or more regions relative to the mean of the propagation velocity. For example, if the propagation velocity of an ultrasound pulse corresponding to a region changes by a specific amount, such as a threshold amount, relative to the mean of the propagation velocity of the object region, the region may be identified in the ultrasound image. Furthermore, in this example, if the propagation velocity of an ultrasound pulse corresponding to a surrounding region fails to change by the specific amount (e.g., the threshold amount) relative to the mean of the propagation velocity of the object region, the region may be separated from the surrounding region in the ultrasound image.

[0047] In addition, the one or more ultrasound images may be modified based on the relationship between the supplementary information and one or more absolute values ​​of the supplementary information. The absolute value of the supplementary information may correspond to all or part of the entire object area in the one or more ultrasound images. With regard to the propagation velocity, the absolute value of the change between the propagation velocity means over the entire or partial object area may be identified from the propagation velocity included in the supplementary information. Furthermore, one or more regions in the ultrasound image may be identified based on the absolute value of the change between the propagation velocity and the propagation velocity mean. Specifically, the one or more regions may be identified based on the absolute value of the change between the propagation velocity corresponding to the one or more regions and the propagation velocity mean. For example, if the absolute value of the change between the propagation velocity of an ultrasound pulse of a region and the propagation velocity mean is greater than a specific value (e.g., a threshold value), the region may be identified in the ultrasound image. In addition, in this example, if the absolute value of the change between the propagation velocity of the ultrasound pulse of the surrounding region and the propagation velocity mean is less than a specific amount (e.g., the threshold value), the region may be separated from the surrounding region in the ultrasound image.

[0048] When modifying the one or more identified regions in the ultrasound image, the region can be modified in an applicable manner to distinguish the one or more identified regions from the surrounding regions in the ultrasound image. Specifically, the one or more identified regions can be colored to distinguish the region from the region surrounding the region in the ultrasound image. More specifically, these regions can be colored in a specific manner based on the supplementary information corresponding to the region. For example, a region with a corresponding sound propagation velocity higher than the average propagation velocity can be colored red. In addition, in this example, a region with a corresponding sound propagation velocity lower than the average propagation velocity can be colored blue. In another example, the average sound velocity of the tissue can be normalized and the region deviating from the average can be colored to produce a transparent color overlay, which can be added to the B-mode image. Subsequently, this can provide clinicians with direct information about where there is a deviation in tissue characteristics estimated based on changes in sound velocity.

[0049] In addition, the brightness level in the one or more identified regions can be modified to distinguish the region from the region surrounding the region in the ultrasound image. More specifically, the brightness level in the region can be adjusted based on the supplemental information corresponding to the region. For example, the brightness level in the region with a corresponding sound propagation speed higher than the average propagation speed can be increased. In addition, in this example, the brightness level in the region with a corresponding sound propagation speed lower than the average propagation speed can be reduced.

[0050] In addition, one or more gains of the one or more ultrasound images can be modified as part of modifying the one or more ultrasound images. Specifically, for example, in response to identifying the region in the ultrasound image based on the supplemental information, the gain of the region identified in the ultrasound image can be modified. The gain corresponding to the identified region in the ultrasound image can be modified based on the supplemental information (e.g., the same supplemental information used to identify the region). Specifically, the gain of the region identified in the ultrasound image can be modified based on an amount of change between the supplemental information corresponding to the region and a mean of at least a portion of the supplemental information.

[0051] The gain of the ultrasonic image can be adjusted based on the propagation velocity of the ultrasonic pulse corresponding to the ultrasonic image. Specifically, the gain in the identified area can be adjusted based on the propagation velocity of the ultrasonic pulse corresponding to the identified area. More specifically, the gain in the identified area can be adjusted based on the change between the propagation velocity of the ultrasonic pulse corresponding to the identified area and the mean propagation velocity. For example, the gain in the ultrasonic image area where the propagation velocity is greater than the mean propagation velocity can be increased, while the gain in the ultrasonic image area where the propagation velocity is less than the mean propagation velocity can be reduced. Alternatively, the gain in the ultrasonic image area where the propagation velocity is less than the mean propagation velocity can be increased, while the gain in the ultrasonic image area where the propagation velocity is greater than the mean propagation velocity can be reduced.

[0052] In addition, the gain of the ultrasound image can be adjusted based on the amount of change between the supplemental information and the mean of at least a portion of the supplemental information relative to a threshold. Specifically, the gain of the ultrasound image can be adjusted based on the amount of change between the propagation velocity and the mean of the propagation velocity relative to a threshold. For example, if the amount of change between the propagation velocity of a pulse of a region and the average propagation velocity is greater than a threshold amount, one or more gains of the region can be increased. In addition, in this example, if the amount of change between the propagation velocity of a pulse of a region and the average propagation velocity is less than a threshold amount, one or more gains of the region can be reduced. Alternatively, if the amount of change between the propagation velocity of a pulse of a region and the average propagation velocity is greater than a threshold amount, one or more gains of the region can be reduced. Subsequently, if the amount of change between the propagation velocity of a pulse of a region and the average propagation velocity is less than a threshold amount, one or more gains of the region can be increased. Thresholds for applying the techniques described herein (e.g., thresholds for adjusting gain) can be defined according to applicable techniques and / or by applicable entities. For example, the operation of an ultrasound system can define a threshold for selectively adjusting the gain in one or more ultrasound images based on supplemental information.

[0053] One or more sound velocity maps may be used to implement a technique for identifying one or more regions in an ultrasound image based on supplementary information and modifying the ultrasound image based on the supplementary information. The sound velocity map may include a mapping of the propagation velocity of an ultrasound pulse over an object region. In addition, the sound velocity map may correspond to one or more ultrasound images. Specifically, a region in the sound velocity map may correspond to a specific region in the ultrasound image, so that the propagation velocity of the ultrasound pulse in the region in the sound velocity map is the propagation velocity of the ultrasound pulse corresponding to the specific region in the ultrasound image. For example, the propagation velocity in a region of the sound velocity map may indicate the propagation velocity of an ultrasound pulse interacting with a specific cardiac tissue. Subsequently, the ultrasound portion including cardiac tissue may correspond to a region of the sound velocity map indicating the propagation velocity of an ultrasound pulse interacting with cardiac tissue.

[0054] One or more sound velocity maps may be generated from the supplementary information to the reflection information. As described below, the sound velocity map may be used to identify one or more regions in the ultrasound image. For example, if the propagation velocity of the ultrasound pulse in a region is higher than the average propagation velocity as indicated by the sound velocity map, the region may be identified from the sound velocity map. Subsequently, the one or more regions identified using the sound velocity map may be modified based on the sound velocity map.

[0055] Figure 3 300 is a flowchart of an example method for generating an ultrasound image with enhanced contrast resolution using a sound velocity map. As previously described, the sound velocity map can be generated by a different ultrasound pulse separated from the ultrasound pulse used to generate the ultrasound image. Alternatively, the sound velocity map can be generated by the same ultrasound pulse as used to generate the ultrasound image. In the example method shown in flowchart 300, the sound velocity map is generated using independent transmit / receive frames. Specifically, in step 310, a transmission sequence optimized for estimating the speed of sound is identified. In step 320, ultrasound pulses are transmitted to the object field according to the transmission sequence identified in step 310. Then, in step 330, backscatter received from the object field is used to generate a sound velocity map. In step 340, an imaging Tx / Rx sequence for imaging by B-mode type imaging is identified. In step 350, ultrasound pulses are transmitted to the object field according to the imaging Tx / Rx sequence identified in step 340. In step 360, a B-mode image is generated based on backscatter from the Tx / Rx sequence. In step 370, the B-mode image is adaptively processed using the sound velocity map. Specifically, the region in the B-mode image where the sound velocity is different from the normal one can be enhanced based on the sound velocity map. In step 380, the processed image is displayed.

[0056] Figure 4 4 is an unenhanced B-mode image 400 of five known targets having propagation velocities different from the average propagation velocity. The known targets in the B-mode image 400 are difficult to see because their backscattering characteristics are only slightly different from the backscattering characteristics of the surrounding area (e.g., the surrounding material). A first target having a higher sound velocity than the average is located in area 402. A second target having a lower sound velocity than the average is located in area 404. A third target having a sound velocity slightly lower than the average is located in area 406. A fourth target having a higher sound velocity than the average is located in area 408. A fifth target having a sound velocity lower than the average is located in area 410. As shown in the B-mode image 400, it is difficult to accurately visualize the locations of these areas 402-410.

[0057] Figure 5 yes Figure 4A sound velocity graph 500 of the actual propagation velocity of ultrasound pulses for the material and five regions 402-410 in the B-mode image 400 is shown. The background sound velocity of the surrounding areas of regions 402-410 in the phantom is approximately 1.54 mm / uS. The first region 402 is a small circular region having a corresponding ultrasound propagation velocity of approximately 1.65 mm / uS. The second region 404 is a small circular region having a corresponding ultrasound propagation velocity of approximately 1.45 mm / uS. The third region 406 is a small circular region having a corresponding ultrasound propagation velocity of approximately 1.50 mm / uS. The fourth region 408 is a large circular region having a corresponding ultrasound propagation velocity of approximately 1.65 mm / uS. The fifth region 410 is a large circular region having a corresponding ultrasound propagation velocity of approximately 1.43 mm / uS.

[0058] Figure 6 is for Figure 5 600 of the deviation of the estimated propagation velocity relative to the mean of the material in the phantom and the five regions 402-410, as indicated by the velocity graph 500 shown in FIG. It can be seen that the estimated value of the deviation of the velocity of sound is lower in resolution than the real target in the phantom because the edge slowly returns to the mean velocity of sound rather than changing suddenly. The first region 402 is estimated to differ from the mean at the center by about 0.05 mm / uS and slowly transitions back to the mean propagation velocity. The second region 404 is estimated to differ from the mean at the center by about -0.06 mm / uS and slowly transitions back to the mean propagation velocity. The third region 406 is estimated to differ from the mean at the center by about -0.02 mm / uS and slowly transitions back to the mean propagation velocity. The fourth region 408 is estimated to differ from the mean at the center by about 0.06 mm / uS and slowly transitions back to the mean propagation velocity. The fifth region 410 is estimated to differ from the mean at the center by about -0.10 mm / uS and slowly transitions back to the mean propagation velocity.

[0059] The propagation speed of the sound velocity map 500 and the propagation speed deviations shown in the sound velocity map 600 may be collected by low-resolution methods, such as using ultrasound pulses operating in a low-resolution imaging or information collection mode. Figure 6 As shown, the low-resolution method of obtaining a robust estimate results in propagation velocity estimates that are biased toward the mean of smaller regions, such as 402, 404, and 406. Even though obtaining a robust velocity map estimate results in a lower resolution image, this information can still be used to indicate where the propagation velocity changes. In turn, the information indicating the propagation velocity changes can be used to enhance the contrast resolution of the B-mode image 400. Furthermore, this adaptive combination of velocity maps and B-mode images can only get better because more robust higher resolution propagation velocity estimates can be generated.

[0060] Figure 7is a composite image 700 including a B-mode phantom and a superimposed sound velocity map 600, with the mean propagation velocity value removed. Figure 7 As shown, these areas Figure 4 4. The regions in the B-mode image 400 are more clearly visible. The first region 402 shows a small circular target, where the corresponding ultrasound propagation velocity is higher than the background. The second region 404 shows a small circular target, where the corresponding ultrasound propagation velocity is lower than the background. The third region 406 shows a small circular target, where the corresponding ultrasound propagation velocity is lower than the background. The fourth region 408 shows a large circular target, where the corresponding ultrasound propagation velocity is higher than the background. The fifth region 410 shows a large circular target, where the corresponding ultrasound propagation velocity is lower than the background.

[0061] Figure 8 800 is an enhanced B-mode image with contrast resolution, which is modified based on the sound velocity map 600 to adjust the gain of regions of different propagation velocities. Specifically, to create the enhanced B-mode image 800, the unchanged grayscale of the object region is measured from the background of the B-mode image 400 and is enhanced by selectively adjusting the gain in the portion of the B-mode image. The degree of gain enhancement applied is proportional to the change in each region relative to the average propagation velocity in 402 to 410. It can be seen that the overall contrast resolution of the region of varying sound velocity is clearly indicated compared to the B-mode image 400. The first region 402 has a corresponding ultrasound propagation velocity higher than the background, and the gain is reduced to clearly show small circular structures. The second region 404 has a corresponding ultrasound propagation velocity lower than the background, and the gain is increased to clearly show small circular structures. The third region 406 has a corresponding ultrasound propagation velocity lower than the background, and the gain is increased to clearly show small circular structures. The fourth region 408 has a corresponding ultrasound propagation velocity higher than the background, and the gain is increased to clearly show large circular structures. The fifth region 410 has a corresponding ultrasound propagation velocity that is lower than the background, and the gain is reduced to clearly show the large circular structure.

[0062] The techniques described herein can be applied in applicable ultrasound imaging modes, such as B-mode, contrast-enhanced ultrasound (CEUS), CD mode, 2D / 3D / 4D, etc. Specifically, the techniques described herein are not limited to B-mode, but can also be applied to other modes where improved temporal resolution within the region of interest has substantial clinical benefits, such as CEUS.

[0063] The present invention has been described with reference to various exemplary embodiments including the best mode. However, those skilled in the art will recognize that changes and modifications may be made to the exemplary embodiments without departing from the scope of the present invention. For example, depending on the specific application or considering any number of cost functions associated with the operation of the system, the various operating steps and components for performing these operating steps may be implemented in alternative ways, for example, one or more of these steps may be deleted, modified, or combined with other steps.

[0064] Although the principles of the present invention have been shown in various embodiments, many modifications of the structures, arrangements, proportions, elements, materials and assemblies that are particularly suitable for specific environments and operational requirements can be used without departing from the principles and scope of the present invention. These and other changes or modifications are intended to be included within the scope of the present invention.

[0065] It has been described above with reference to various embodiments. However, it will be appreciated by those skilled in the art that various modifications and changes may be made without departing from the scope of the present invention. Therefore, this article should be considered illustrative rather than restrictive, and all such modifications are intended to be included within its scope. Similarly, the benefits, other advantages and solutions to the problems have been described above with reference to various embodiments. However, the benefits, advantages, solutions to the problems and any elements that may cause any benefits, advantages or solutions to appear or become more obvious should not be interpreted as key, necessary or necessary features or elements. As used herein, the terms "include", "comprise" and any other variants thereof are intended to cover non-exclusive inclusions, so that the process, method, article or equipment including a series of elements not only include those listed elements, but also may include other elements that are not explicitly listed or inherent to such processes, methods, systems, articles or equipment. Moreover, as used herein, the terms "couple", "couple" and any other variants thereof are intended to cover physical connections, electrical connections, magnetic connections, optical connections, communication connections, functional connections and / or any other connections.

[0066] Those skilled in the art will appreciate that many changes may be made to the details of the above embodiments without departing from the basic principles of the invention. Therefore, the scope of the invention should be determined by the appended claims.

Claims

1. A method for performing ultrasound imaging, characterized in that include: Acquiring ultrasonic information of the object area in response to an ultrasonic pulse emitted toward the object area, the ultrasonic information comprising reflection information in response to the ultrasonic pulse and supplementary information to the reflection information of the object area; wherein the supplementary information comprises a propagation speed of the ultrasonic pulse when interacting with the object area; forming one or more B-mode ultrasound images of at least a portion of the object region based on the reflection information; and The one or more B-mode ultrasound images are modified according to the supplementary information of the reflection information to generate one or more B-mode enhanced ultrasound images from the one or more B-mode ultrasound images; wherein, the modification of the one or more B-mode ultrasound images according to the supplementary information of the reflection information includes: determining the mean propagation velocity of the ultrasound pulse interacting with the object area according to the supplementary information; generating a sound velocity map interacting with the object area according to the supplementary information, the sound velocity map indicating the propagation velocity of the ultrasound pulse in the object area; and modifying at least one of the gain, contrast and brightness level of different areas of the one or more B-mode ultrasound images based on the change between the propagation velocity of the ultrasound pulse in different areas in the one or more B-mode ultrasound images and the propagation velocity mean according to the sound velocity map.

2. The method according to claim 1, characterized in that The sound speed map includes a composite sound speed map, which is generated based on an ultrasonic emission and reception profile formed by the ultrasonic pulse. The ultrasonic emission and reception profiles generated by different ultrasonic pulses form different sound speed maps, and the different sound speed maps are composited to form the composite sound speed map.

3. The method according to claim 1 or 2, characterized in that The formation of the B-mode ultrasound image is based on one or more B-mode imaging technologies, wherein the imaging technologies include: fundamental wave imaging technology, fundamental wave spatial compound imaging technology, harmonic imaging technology, harmonic spatial compound imaging technology, fundamental wave and harmonic wave composite imaging technology, and fundamental wave and harmonic wave spatial compound imaging technology or a combination thereof.

4. The method according to any one of claims 1 to 3, characterized in that: The modifying the one or more B-mode ultrasound images according to the supplementary information of the reflection information includes: coloring the one or more B-mode ultrasound images.

5. The method according to claim 4, characterized in that The coloring of the one or more B-mode ultrasound images includes: coloring at least one region in the one or more B-mode ultrasound images.

6. The method according to any one of claims 1 to 5, characterized in that: The method further includes: determining, according to the sound velocity map, regions in the one or more B-mode ultrasound images that need to be modified based on a relationship between a change in propagation velocity in different regions of the one or more B-mode ultrasound images and the propagation velocity mean and a threshold.

7. The method according to any one of claims 1 to 6, characterized in that: The method further includes determining the region that needs to be modified in the one or more B-mode ultrasound images based on the absolute value of the change between the propagation velocity of different regions of the one or more B-mode ultrasound images and the propagation velocity mean.

8. The method according to any one of claims 1 to 7, characterized in that: The method of modifying at least one of the gain, contrast or brightness level of different areas of the one or more B-mode ultrasound images based on the change between the propagation velocity of the ultrasound pulses in different areas of the one or more B-mode ultrasound images and the mean propagation velocity includes: if the propagation velocity of the corresponding area is greater than the mean propagation velocity or the absolute value of the change between the propagation velocity and the mean propagation velocity is greater than the corresponding threshold value, then increasing at least one of the gain, contrast and brightness level of the corresponding area; if the propagation velocity of the corresponding area is less than the mean propagation velocity or the absolute value of the change between the propagation velocity and the mean propagation velocity is less than the corresponding threshold value, then reducing at least one of the gain, contrast and brightness level of the corresponding area.

9. The method according to any one of claims 1 to 8, characterized in that: The method of modifying at least one of the gain, contrast and brightness levels of different areas of the one or more B-mode ultrasound images based on the change between the propagation velocity of the ultrasound pulses in different areas of the one or more B-mode ultrasound images and the propagation velocity mean includes: if the change of the propagation velocity of the corresponding area relative to the propagation velocity mean is greater than a threshold, then increasing at least one of the gain, contrast and brightness of the corresponding area; if the change of the propagation velocity of the corresponding area relative to the propagation velocity mean is less than a threshold, then reducing at least one of the gain, contrast and brightness level of the corresponding area.

10. The method according to any one of claims 1 to 9, characterized in that: The sound velocity map has a lower resolution than the one or more B-mode ultrasound images.

11. A method for performing ultrasound imaging, characterized in that: include: Acquiring ultrasonic information of the object area in response to an ultrasonic pulse emitted toward the object area, the ultrasonic information comprising reflection information in response to the ultrasonic pulse and supplementary information to the reflection information of the object area; wherein the supplementary information comprises a propagation speed of the ultrasonic pulse when interacting with the object area; forming one or more B-mode ultrasound images of at least a portion of the object region based on the reflection information; and The one or more B-mode ultrasound images are modified according to the supplementary information of the reflection information to generate one or more B-mode enhanced ultrasound images from the one or more B-mode ultrasound images; wherein, modifying the one or more B-mode ultrasound images according to the supplementary information of the reflection information comprises: determining the mean propagation velocity of the ultrasound pulse interacting with the object area according to the supplementary information; and modifying at least one of the gain, contrast and brightness level of different areas in the one or more B-mode ultrasound images based on the change between the propagation velocity of the ultrasound pulse and the mean propagation velocity.

12. A system for performing ultrasound imaging, characterized in that: include: An ultrasonic transducer, the ultrasonic transducer being configured to: Acquiring ultrasonic information of the object area in response to an ultrasonic pulse emitted toward the object area, wherein the ultrasonic information includes reflection information in response to the ultrasonic pulse and supplementary information to the reflection information of the object area; wherein the supplementary information includes a propagation speed of the ultrasonic pulse when interacting with the object area; A main processing console, the main processing console being configured to: forming one or more B-mode ultrasound images of at least a portion of the object region based on the reflection information; and The one or more B-mode ultrasound images are modified according to the supplementary information of the reflection information to generate one or more B-mode enhanced ultrasound images from the one or more B-mode ultrasound images; wherein, the modification of the one or more B-mode ultrasound images according to the supplementary information of the reflection information includes: determining the mean propagation velocity of the ultrasound pulse interacting with the object area according to the supplementary information; generating a sound velocity map interacting with the object area according to the supplementary information, the sound velocity map indicating the propagation velocity of the ultrasound pulse in the object area; and modifying at least one of the gain, contrast and brightness level of different areas of the one or more B-mode ultrasound images based on the change between the propagation velocity of the ultrasound pulse in different areas in the one or more B-mode ultrasound images and the propagation velocity mean according to the sound velocity map.

13. A system for performing ultrasound imaging, characterized in that: include: one or more processors; and A computer-readable medium providing instructions accessible to the one or more processors to cause the one or more processors to perform operations comprising: Acquiring ultrasonic information of the object area in response to an ultrasonic pulse emitted toward the object area, the ultrasonic information comprising reflection information in response to the ultrasonic pulse and supplementary information to the reflection information of the object area; wherein the supplementary information comprises a propagation speed of the ultrasonic pulse when interacting with the object area; forming one or more B-mode ultrasound images of at least a portion of the object region based on the reflection information; and The one or more B-mode ultrasound images are modified according to the supplementary information of the reflection information to generate one or more B-mode enhanced ultrasound images from the one or more B-mode ultrasound images; wherein, the modification of the one or more B-mode ultrasound images according to the supplementary information of the reflection information includes: determining the mean propagation velocity of the ultrasound pulse interacting with the object area according to the supplementary information; generating a sound velocity map interacting with the object area according to the supplementary information, the sound velocity map indicating the propagation velocity of the ultrasound pulse in the object area; and modifying at least one of the gain, contrast and brightness level of different areas of the one or more B-mode ultrasound images based on the change between the propagation velocity of the ultrasound pulse in different areas in the one or more B-mode ultrasound images and the propagation velocity mean according to the sound velocity map.

Images