Retrospective launch focusing using launch velocity systems, apparatuses, and methods

Abstract

An ultrasound imaging system includes an array of acoustic elements configured to emit ultrasonic energy at a first emission velocity and receive echoes associated with the ultrasonic energy emitted at the first emission velocity. The system also includes processor circuitry in communication with the array of acoustic elements. The processor is configured to: generate a plurality of multilines based on the received echoes; determine a second emission velocity; determine a set of emission focusing delays based on the second emission velocity; adjust the plurality of multilines using the set of emission focusing delays; generate an image based on the adjusted plurality of multilines; and output the generated image to a display in communication with the processor circuitry.

Description

Technical Field

[0001] This disclosure generally relates to ultrasound imaging, and more specifically to retrospective emission focusing that can be used for tissue aberration correction. More specifically, this disclosure relates to retrospective emission focusing based on ultrasound emission that may be the same as or different from the emission velocity used for ultrasound emission. Background Technology

[0002] An ultrasound probe can be configured to emit ultrasound energy at a specific emission velocity (e.g., a specific speed of sound). However, differences in the density and / or other properties of the imaging medium may cause the ultrasound energy to propagate through the medium at a speed different from the configured emission velocity (e.g., the expected emission velocity) (e.g., the actual emission velocity). As an illustrative example, ultrasound energy may travel through tissues with low fat content and / or high density at a relatively higher emission velocity (e.g., 1540 m / s), while ultrasound energy may travel through fatter tissues such as breast tissue at a relatively lower emission velocity (e.g., 1480 m / s). The difference between the expected emission velocity used to emit ultrasound energy and the actual emission velocity of the ultrasound energy traveling within the medium can lead to tissue aberrations. That is, images generated based on ultrasound energy may include distortions (e.g., blurring) caused by differences in emission velocity.

[0003] In some cases, ultrasound probes can be configured to emit ultrasound at a specific emission rate based on an emission pulse pattern. The emission pulse pattern can be used to actuate the transducer elements of the ultrasound probe, causing, for example, ultrasound energy to be emitted at a desired emission rate. Configuring an ultrasound probe with a new emission pulse pattern to affect the desired emission rate for emitting ultrasound energy may be prohibitive in terms of resources (e.g., time, cost, materials, etc.). For example, the development and testing required to demonstrate the safety and effectiveness of a new emission pulse pattern could take months.

[0004] WO2019 / 219485A1 describes an ultrasound imaging system for generating synthetic emission-focused images. It analyzes the multi-line signals used to form the image scan lines for changes in sound velocity and generates a graph of these changes.

[0005] US2015 / 196274A1 describes an ultrasound examination apparatus comprising: a probe having a plurality of elements; a transmitter configured to transmit an ultrasonic beam to an object being examined using the probe; a receiver configured to receive an ultrasonic echo signal from the object being examined; a sound velocity determiner configured to determine a sound velocity value within the object being examined; and an element data processing section configured to generate a second element data from at least two first element data using the sound velocity value. Summary of the Invention

[0006] Embodiments of this disclosure relate to retrospective emission focusing based on a sound velocity that may be the same as or different from the emission velocity used for ultrasound emission. For example, the techniques described herein can be used to focus ultrasound imaging data associated with an ultrasound emission emitted at a first emission velocity, based on a different second emission velocity. Specifically, the ultrasound imaging system can determine emission focusing weights and / or delays based on the second emission velocity and apply them to the ultrasound imaging data. In this way, the ultrasound imaging system can effectively refocus the emission beam pattern corresponding to the first emission velocity based on the second emission velocity. In this manner, ultrasound data corresponding to an emission at a specific emission velocity can be tuned to generate images as if the emission occurred at different emission velocities. Therefore, tissue aberrations caused by the difference between the emission velocity at the ultrasound probe and the emission velocity through the medium can be reduced, and the use of ultrasound imaging systems configured to emit ultrasound energy at a specific emission velocity can be extended to imaging tissues with a wider range of characteristics (e.g., corresponding to different ultrasound propagation velocities). For this purpose, a single emission pulse pattern can be used across various ultrasound imaging applications (such as breast imaging, vascular imaging, etc.). Therefore, the usability of ultrasound imaging systems can be improved, and the costs involved in the development and / or implementation of ultrasound imaging systems can be reduced.

[0007] In some aspects, an ultrasound imaging system includes an array of acoustic elements configured to emit ultrasonic energy at a first emission velocity and receive echoes associated with the ultrasonic energy emitted at the first emission velocity. The system also includes processor circuitry in communication with the array of acoustic elements. The processor may be configured to generate a plurality of multilines based on the received echoes, determine a second emission velocity, determine a set of emission focusing delays based on the second emission velocity, adjust the plurality of multilines using the set of emission focusing delays, generate an image based on the adjusted plurality of multilines, and output the generated image to a display in communication with the processor circuitry.

[0008] In some aspects, the ultrasound imaging system includes multiple delay lines in communication with the array of acoustic elements and the processor circuitry. The processor circuitry may also be configured to control the multiple delay lines to delay the multiple lines according to the set of emission focusing delays, thereby adjusting the multiple lines.

[0009] In some aspects, the processor circuitry may also be configured to determine a set of emission focusing weights based on the second emission velocity and use the set of emission focusing weights to adjust the plurality of multilines. In some aspects, the ultrasound imaging system further includes a multiplier communicating with the array of acoustic elements and the processor circuitry. Furthermore, the processor circuitry may be configured to control the multiplier to apply the set of emission focusing weights to the plurality of multilines to adjust the plurality of multilines.

[0010] In some aspects, the ultrasound imaging system includes a summer in communication with the processor circuitry and the array of acoustic elements. The summer may be configured to sum a plurality of regulated multilines to generate emission-focused image data. The processor circuitry may also be configured to generate the image based on the emission-focused image data.

[0011] In some aspects, the processor circuitry can be configured to determine the set of emission focusing delays based on a model of the ultrasonic energy emitted at the second emission rate.

[0012] In some aspects, the array of acoustic elements can be configured to emit the ultrasonic energy at a first depth of focus. In such aspects, the processor circuitry can be configured to also determine the set of emission focusing delays based on a model of ultrasonic energy emitted at a second depth of focus. The processor circuitry can also be configured to determine the second depth of focus based on the second emission velocity.

[0013] In some aspects, the ultrasonic energy comprises multiple ultrasonic beams. Furthermore, the array of acoustic elements can be configured to emit each of the multiple ultrasonic beams from corresponding transmit beam positions. In some aspects, the multiple multi-line receivers correspond to imaging data associated with receive line positions, receiving the echoes along the receive line positions for each of the multiple ultrasonic beams.

[0014] In some aspects, the processor circuitry can be configured to determine the second transmission rate based on user input. The user input may include selecting the second transmission rate from a set of predetermined transmission rates.

[0015] In some aspects, the processor circuitry can be configured to generate the image based on additional adjusted multiple multilines. The adjusted multiple multilines may correspond to a first line of the image, and the additional adjusted multiple multilines may correspond to a second line of the image.

[0016] In some aspects, the ultrasound imaging system includes the display.

[0017] In some aspects, a method for retrospectively transmitting focused ultrasound data for ultrasound imaging includes controlling an array of acoustic elements in communication with the processor circuitry to transmit ultrasound energy at a first transmission rate and receiving echoes associated with the transmitted ultrasound energy. The method may further include generating a plurality of multilines by the processor circuitry based on the received echoes. The method may also include determining a second transmission rate by the processor circuitry and determining a set of transmission focusing delays based on the second transmission rate. Furthermore, the method may include adjusting the plurality of multilines by the processor circuitry using the set of transmission focusing delays, and generating an image based on the adjusted plurality of multilines. The method may also involve outputting the generated image to a display in communication with the processor circuitry.

[0018] Additional aspects, features, and advantages of this disclosure will become apparent from the following detailed description. Attached Figure Description

[0019] Illustrative embodiments of this disclosure will be described with reference to the accompanying drawings, in which:

[0020] Figure 1A , 1B Figures 1 and 1C are schematic diagrams of ultrasonic beam emission according to aspects of this disclosure.

[0021] Figure 2 This is a schematic diagram of an ultrasound imaging system according to aspects of this disclosure.

[0022] Figure 3 This is a schematic diagram of a processor circuit according to aspects of this disclosure.

[0023] Figure 4A and Figure 4B It is a drawing of a simulated transmission beam pattern based on aspects of this disclosure.

[0024] Figure 5 This is a flowchart of a retrospective emission focusing method based on emission velocity according to an aspect of the present invention.

[0025] Figure 6 This is a flowchart of a method for firing focusing multiple lines based on firing velocity, according to aspects of this disclosure.

[0026] Figure 7A , Figure 7B and Figure 7C It is a drawing of the emission beam pattern generated from retrospective emission focused ultrasound image data according to aspects of this disclosure.

[0027] Figure 8 It is a plot of the point spread function according to aspects of this disclosure.

[0028] Figure 9A and 9B It is an ultrasound image of breast tissue according to aspects of this disclosure. Detailed Implementation

[0029] For the purpose of enhancing understanding of the principles of this disclosure, reference will now be made to the embodiments shown in the accompanying drawings, and these embodiments will be described using specific language. However, it should be understood that this is not intended to limit the scope of this disclosure. Any changes and other modifications to the described devices, systems, and methods, as well as any other application of the principles of this disclosure, are fully contemplated and included within this disclosure, as would normally occur to those skilled in the art to which this disclosure pertains. Specifically, it is fully contemplated that features, components, and / or steps described with respect to one embodiment may be combined with features, components, and / or steps described with respect to other embodiments of this disclosure. However, for the sake of brevity, numerous repetitions of these combinations will not be described separately.

[0030] Figure 1A-1C The illustration shows the emission of an ultrasonic beam and the corresponding echo reception, which can be used to generate multilines. An example of the emission of an ultrasonic beam and the reception of the corresponding echo for generating multilines is described in U.S. Patent 8,137,272, filed April 17, 2007, entitled "Ultrasonic Synthetic Transmit Focusing with a MultilineBeamformer". More specifically, Figure 1A The illustration shows an overview 10 of a first transmitted beam (e.g., an ultrasonic beam) emitted by a transducer array 8, which may be included in an ultrasonic probe. Figure 1A It also includes an orthogonal view 20 of the first transmit beam, illustrating the center lobe 20A within the first transmit beam and side lobes on either side of the center lobe 20A. For this purpose, the first transmit beam exhibits a relatively constant power level below the intensity peak at the beam center (e.g., center lobe 20A). In some embodiments, the power level of the beam can be (e.g., by the designer) selected at any suitable level (e.g., 3dB, 6dB, 20dB, etc.).

[0031] As further illustrated, the first transmitted beam includes a focal point 12 at the narrowest width of the profile 10 of the first transmitted beam. That is, for example, the first transmitted beam may reach its tightest focus at the focusing region 12 and then diverge. In some cases, the focal point 12 may correspond to the point where the first transmitted beam is focused during transmission by transmit focusing and / or beamforming (e.g., focusing affects the output at transducer array 8). As described in more detail below, the techniques described herein can be used to extend the focal point 12.

[0032] A first transmit beam is transmitted with a width comprising multiple receive lines 14, 16, and 18. After the first transmit beam is transmitted, echoes can be received and focused along the receive lines 14, 16, and 18. More specifically, in response to a single transmit beam, the echoes received by the transducer elements of the receive aperture (e.g., within the transducer array 8) are delayed and summed in three different ways to form multiple lines at different line positions 14, 16, and 18, as described in more detail below. In the illustrated embodiment, receive line 16 is received along the center of the first transmit beam, and receive lines 14 and 18 are laterally steered and focused to be received on either side of the center line (e.g., receive line 16). As further illustrated, the near-field and far-field portions of the outer lines 14 and 18 are within the profile 10 of the first transmit beam, while the mid-field (e.g., central-field) portions of receive lines 14 and 18 are not included within the profile 10 of the first transmit beam. Therefore, in some embodiments, the transmitted energy along lines 14 and 18 can be used to receive echoes and / or portions of echoes in the near and far fields from either side of the centerline location (e.g., corresponding to receiver line 16). For this purpose, targets in the image field can be sampled on both sides of the centerline location (e.g., corresponding to receiver lines 14 and 18, respectively). In this way, the lateral spread energy of the first transmitted beam in the near and far fields can be used for effective image reception and resolution.

[0033] Figure 1B The diagram illustrates the profile 10' of the second transmit beam. The second transmit beam can be transmitted by radially shifting the transmit aperture (e.g., within transducer array 8) to the right relative to the transmit aperture of the first transmit beam by an interval of one receive line. The profile 10' of the second transmit beam can be similar to the profile 10 of the first transmit beam, and although not shown, an orthogonal view of the second transmit beam can be similar to an orthogonal view 20 of the first transmit beam. Therefore, and as in the case of the first transmit beam, the profile 10' of the second transmit beam can accommodate three receive lines 16', 18', and 22. Specifically, echoes along the three receive lines 16', 18', and 22 can be simultaneously received and beamformed in response to the transmission of the second transmit beam. That is, for example, the echoes received by the transducer elements of the receive aperture (e.g., within transducer array 8) are delayed and summed in three different ways to form multiple lines at different line positions 16', 18', and 22. Because the second transmit beam is emitted from an aperture that is shifted relative to the first transmit beam, the receiver line 16' is aligned with the receiver line 16 from the first transmit beam, the receiver line 18' is aligned with the receiver line 18 from the first transmit beam, and the receiver line 22 is located to the right of the center line 18' of the second transmit beam.

[0034] Figure 1CThe diagram illustrates a third transmit beam profile 10”. The third transmit beam can be transmitted by radially shifting the transmit aperture (e.g., within transducer array 8) to the right by an interval of one receive line relative to the transmit aperture of the second transmit beam. The third transmit beam profile 10” can be similar to the first transmit beam profile 10 and / or the second transmit beam profile 10’, and although not shown, an orthogonal view of the third transmit beam can be similar to the orthogonal view 20 of the first transmit beam. The third transmit beam profile 10” includes at least a portion of three receive lines 18”, 22′, and 24. For this purpose, echoes along the three receive lines 18”, 22′, and 24 can be simultaneously received and beamformed in response to the transmission of the second transmit beam. That is, for example, echoes received by the transducer elements of the receive aperture (e.g., within transducer array 8) are delayed and summed in three different ways to form multiple lines at different line positions 18”, 22′, and 24. The illustrated receive lines 18”, 22”, and 24 are spaced apart from each other with the same spacing as receive lines 14, 16, and 18, and receive lines 16', 18', and 22. Therefore, receive line 22' is axially aligned with receive line 22 of the second transmit beam. Furthermore, receive line 18” is axially aligned with receive line 18' of the second transmit beam and receive line 18 of the first transmit beam. Therefore, targets in the paths of receive lines 18, 18', and 18” can be sampled using three receive lines, each corresponding to a different transmit beam (e.g., the first, second, and third transmit beams, respectively). In this way, the echoes corresponding to the first, second, and third transmit beams are co-aligned at receive lines 18, 18', and 18”. The co-aligned echoes can be combined to generate image data lines along the alignment lines (e.g., corresponding to receive lines 18, 18', and 18”). Image data lines can focus at a greater depth of field than image data formed using any individual receiver line, thus producing an extended transmit-focus effect. In this way, focusing can be effective at a greater depth of field because the echo energy from the three beams is combined to produce the resulting image data, as described in more detail below.

[0035] In some embodiments, the emission of ultrasonic energy (e.g., an ultrasonic beam) and the reception of the corresponding echo can be... Figure 1A -C is illustrated as a process that repeats (e.g., continues) across the image field until the entire image field has been scanned. Furthermore, for a given line position, after receiving the echo of each (e.g., the maximum number of receive lines) of the receive lines corresponding to that position, the receive lines at that position can be processed together (e.g., in parallel). As an illustrative example, with Figure 1AThe maximum number of receive lines corresponding to the line position illustrated in -C is three. Therefore, three receive lines corresponding to the same line position, such as 18, 18', and 18" can be received before processing the receive line at that line position. After receiving the three receive lines, they can be processed together to generate image data lines at the corresponding positions. For this purpose, a first set of receive lines (e.g., 14, 16, and 18) and a second set of receive lines 16', 18', and 22 corresponding to the first transmitted beam can be stored, at least until a third set of receive lines (e.g., 18"), 22, and 24). Subsequently, receive lines 18, 18', and 18" from the first, second, and third sets of receive lines can be processed together. In this way, the processing of the received echo can be independent of the storage of pre-received and radio frequency (RF) data from the transmission. Instead, before processing the receive line for that line position, storage usage can be reduced (e.g., minimized) to the storage of multiple sets of receive lines corresponding to that line position, at which point storage can be freed up for storage of subsequent receive lines.

[0036] Although Figure 1A The transmit beam profile illustrated in -C is described herein as including three receive lines, but other suitable numbers of spaced-apart lines receiving simultaneously can also be used, such as four, six, eight, twelve, sixteen, etc. In some cases, increasing the number of receive lines received at transducer array 8 may involve configuring the transducer array to transmit according to a lower F number (e.g., a lower F number relative to a lower F number corresponding to fewer receive lines), such that the ultrasonic energy emitted by transducer array 8 penetrates a wider range of receive line locations. For this purpose, a wider beam can be generated by using a smaller transmit aperture. Thus, increasing the number of receive lines received at transducer array 8 may involve reducing the number of elements in transducer array 8 used for emitting ultrasonic energy. Furthermore, although in Figure 1A -C illustrates a converging transmit beam, but embodiments are not limited thereto. In some embodiments, for example, a diverging transmit beam may be emitted by transducer array 8 and focused according to the techniques described herein.

[0037] Now go to Figure 2The diagram illustrates a block diagram of an ultrasound imaging system 150 according to aspects of this disclosure. System 150 can be used to scan areas or volumes of a patient's body. System 150 includes an ultrasound imaging probe 102 that communicates with a host 130 (e.g., via a communication interface or link). Probe 102 may include a transducer array 104, a transmit beamformer 106, and / or a transmit / receive switch 108 (e.g., a crosspoint switch). Host 130 (e.g., a console) may include multi-line processors 110a-110n, a line storage area 112, a transmit focuser 132, a transmit focusing processor 134, an image processor 122, and a display 124.

[0038] In some embodiments, probe 102 is an external ultrasound imaging device including a housing configured for hand-held operation by a user. Transducer array 104 may be similar to transducer array 8 of FIG. 1. Transducer array 104 may also be configured to acquire ultrasound data when the user grips the housing of probe 102, such that transducer array 104 is positioned adjacent to or in contact with the patient's skin. Probe 102 is configured to acquire ultrasound data of anatomical structures within the patient's body when probe 102 is positioned externally to the patient's body. In some embodiments, probe 102 may be an external ultrasound probe and / or a transthoracic echocardiography (TTE) probe.

[0039] In other embodiments, probe 102 may be an internal ultrasound imaging device and may include a housing configured to be located within a lumen of a patient's body, including the patient's coronary vascular system, peripheral vascular system, esophagus, heart chambers, or other body lumens or chambers. In some embodiments, probe 102 may be an intravascular ultrasound (TVUS) imaging catheter or an intracardiac echocardiography (ICE) catheter. In other embodiments, probe 102 may be a transesophageal echocardiography (TEE) probe. Probe 102 may be any suitable form for any suitable ultrasound imaging application that includes both external and internal ultrasound imaging.

[0040] For an ultrasound imaging device, transducer array 104 emits ultrasound signals toward the anatomical object of the patient and receives echo signals reflected back to transducer array 104 from the object. Ultrasound transducer array 104 may include any suitable number of acoustic elements, including one or more acoustic elements and / or multiple acoustic elements. In some instances, transducer array 104 includes a single acoustic element. In some instances, transducer array 104 may include an array of acoustic elements having any number of acoustic elements in any suitable configuration. For example, transducer array 104 may include acoustic elements between 1 and 10,000 acoustic elements, including values ​​such as 2 acoustic elements, 4 acoustic elements, 36 acoustic elements, 64 acoustic elements, 128 acoustic elements, 500 acoustic elements, 812 acoustic elements, 1,000 acoustic elements, 3,000 acoustic elements, 8,000 acoustic elements, and / or other values ​​greater than or less than both. In some instances, transducer array 104 may comprise an array of acoustic elements having any number of acoustic elements in any suitable configuration, such as linear arrays, planar arrays, curved arrays, wavy arrays, circular arrays, ring arrays, phased arrays, matrix arrays, one-dimensional (1D) arrays, 1.x-dimensional arrays (e.g., 1.5D arrays), or two-dimensional (2D) arrays. The array of acoustic elements (e.g., one or more rows, one or more columns, and / or one or more orientations) may be controlled and activated uniformly or independently. Transducer array 104 may be configured to acquire one-dimensional, two-dimensional, and / or three-dimensional images of a patient's anatomy. In some embodiments, transducer array 104 may comprise a piezoelectric micromechanical ultrasonic transducer (PMUT), a capacitive micromechanical ultrasonic transducer (CMUT), a single crystal, lead zirconate titanate (PZT), PZT composite materials, other suitable transducer types, and / or combinations thereof.

[0041] The object may include any anatomical structure or feature, such as blood vessels, nerve fibers, airways, mitral valve leaflets, cardiac structures, abdominal tissue structures, appendix, large intestine (or colon), small intestine, kidneys, liver, and / or any other anatomical structure of the patient. In some aspects, the object may include at least a portion of the patient's large intestine, small intestine, cecal pouch, appendix, terminal ileum, liver, upper abdomen, and / or psoas muscles. This disclosure can be implemented in the context of any number of anatomical locations and tissue types, including but not limited to organs, including the liver, heart, kidneys, gallbladder, pancreas, and lungs; ducts; intestines; nervous system structures, including the brain, dural sac, spinal cord, and peripheral nerves; urinary tract; and valves within blood vessels, blood, chambers or other parts of the heart, abnormal organs, and / or other systems of the body. In some embodiments, the object may include malignant tumors, such as tumors, cysts, lesions, hemorrhages, or blood pools within any part of the human anatomy. Anatomical structures can be blood vessels, such as arteries or veins in a patient's vascular system, including the cardiac vascular system, peripheral vascular system, neurovascular system, renal vascular system, and / or any other suitable lumen within the body. In addition to natural structures, this disclosure can be implemented within the context of artificial structures, such as, but not limited to, heart valves, stents, shunts, filters, implants, and other devices.

[0042] Beamformer 106 is coupled to transducer array 104. For example, beamformer 106 controls transducer array 104 for the transmission of ultrasonic signals. In this example, beamformer 106 is a transmit beamformer. In some embodiments, transmit beamformer 106 may apply a time delay to signals transmitted to individual acoustic transducers within the array of transducers 104, such that the acoustic signals are diverted in any suitable direction away from the probe 102. For this purpose, a selected group of transducer elements (e.g., acoustic elements) of transducer array 104 of ultrasonic probe 102 may be actuated by transmit beamformer 106 at a correspondingly delayed time. In this way, ultrasonic probe 102 can be used to transmit an ultrasonic beam (e.g., ultrasonic energy) focused at a selected focal region associated with a corresponding direction of transmission from a corresponding origin along transducer array 104. For example, the transmit beamformer 106 can actuate different sets of transducer elements (e.g., different transmit apertures) of the transducer array 104, causing the ultrasonic probe 102 to emit... Figure 1A The first, second, and third beams, respectively, are illustrated in -C and correspond to outlines 10, 10', and 10”. In some instances, beamformer 106 may be a receiving beamformer and control the reception of ultrasonic echoes at transducer array 104. Receiving beamformer 106 may include multiple stages of beamforming.

[0043] As shown, the transmit beamformer 106 can be coupled to the transducer array 104 via a transmit / receive switch 108. The transmit / receive switch 108 may include a crosspoint switch. Furthermore, the transmit / receive switch 108 can be configured to direct high-voltage transmit pulses from the transmit beamformer 106 and / or signals from the host unit 130 to the ultrasound probe 102, and to direct ultrasound echoes and / or signals from the ultrasound probe 102 to the host unit 130. In this way, the transmit / receive switch 108 can protect the receiving circuitry within the ultrasound probe 102 and / or the host unit 130 (which may include circuitry configured to operate at lower voltages) from the higher voltage of the transmit pulses.

[0044] In response to each transmitted beam, the ultrasonic probe 102 may receive an echo (e.g., at the transducer array 104), and the host 130 may receive the echo from the ultrasonic probe 102 and / or signals associated with the echo. At the host 130, the echo received from the ultrasonic probe 102 may be applied to the input of the multi-line processor 110a-n. The multi-line processor 110a-n may also be described as processor circuitry, which may include other components, such as memory, communicating with the multi-line processor 110a-n. The multi-line processor 110a-n may include a central processing unit (CPU), graphics processing unit (GPU), digital signal processor (DSP), application-specific integrated circuit (ASIC), controller, field-programmable gate array (FPGA) device, another hardware device, firmware device, or any combination thereof configured to perform the operations described herein. The multi-line processor 110a-n may also be implemented as a combination of computing devices, such as a combination of a DSP and a microprocessor, multiple microprocessors, one or more microprocessors combined with a DSP core, or any other such configuration.

[0045] Furthermore, the multi-line processors 110a-n can be configured to process ultrasonic echoes. For example, each of the multi-line processors 110a-n can include a receive beamformer configured to apply a corresponding set of delays to the received echoes. In some embodiments, the multi-line processors 110a-n provide a first or only stage of receive beamforming. In other embodiments, the multi-line processors 110a-n provide a second or subsequent stage of receive beamforming (e.g., when the first stage of receive beamforming is performed by beamformer 106). The receive beamformer can also apply apodization weights to the echoes received from the elements of transducer array 104. As a result of the applied set of delays and / or apodization weights, the multi-line processors 110a-n can form receive beams corresponding to different azimuths of the same transmit beam. More specifically, the multi-line processors 110a-n can generate multi-line (e.g., multi-line echoes) corresponding to echoes received along different receive lines for a given transmit beam. For example, the multi-line processor 110a-n can generate signals for the first transmit beam corresponding to receive lines 14, 16, and 18, respectively. Figure 1A The multi-line receivers for the second transmit beam, corresponding to receiver lines 16', 18', and 22 (Figure IB), and the multi-line receivers for the third transmit beam, corresponding to receiver lines 18', 22', and 24', respectively. Figure 1C (Multi-line)

[0046] Multilines generated at multiline processors 110a-n can be output to line storage area 112. Line storage area 112 may include memory and / or storage devices (such as one or more registers) and can store multilines at least until each of the multilines corresponding to a specific receive line (e.g., required to form a line within an image) has been acquired. For example, for image lines corresponding to receive line positions 18, 18', and 18”, line storage area 112 may store a first set of multilines corresponding to a first transmit beam and receive line positions 14, 16, and 18, and a second set of multilines corresponding to a second transmit beam and receive line positions 16', 18', and 22, at least until a third set of multilines corresponding to a third transmit beam and receive lines 18”, 22', and 24 is received, as described above.

[0047] After receiving each of the multiple lines corresponding to a specific image line at the line storage area 112, the line storage area 112 can output the multiple lines corresponding to the received lines to the emitter focuser 132. As shown, the emitter focuser 132 may include weights 114a-n, multipliers 116a-n, delay lines 118a-n, and a summer 120. In some embodiments, the number of each of the weights 114a-n, multipliers 116a-n, and delay lines 118a-n may correspond to the number of multi-line processors 110a-n, which in turn may correspond to the number of received line positions generated for a specific line of the image (e.g., the number of multiple lines). Furthermore, the emitter focuser 132 may be implemented as a combination of software components and / or hardware components. Additionally, the emitter focuser 132 may be implemented as a combination of analog and / or digital components. For example, the delay lines 118a-n can be implemented as digital delay lines by storing data (e.g., multi-line data) in memory and reading the data at a later time corresponding to the desired delay. Alternatively or concurrently, delay lines 118a-n can be implemented using shift registers and / or clock signals of varying lengths. In some embodiments, delay lines 118a-n can be implemented using interpolation beamformers. Similarly, summer 120 can be implemented using adder circuitry and / or implemented as a digital adder.

[0048] In some embodiments, the emission focuser 132 may apply corresponding apodization weights to each of a set of multilines corresponding to a specific line in the image (e.g., a set of multilines received from the line storage area 112). Specifically, multipliers 116a-n may each receive a multiline from the set of multilines and a corresponding emission focus weight from weights 114a-n as input, and may output an adjusted multiline (e.g., a weighted multiline). In some embodiments, weights 114a-n may be configured to weight each multiline based on the round-trip impulse response associated with the multiline. Furthermore, weights 114a-n may be configured by the emission focus processor 134, as described in more detail below.

[0049] The transmitter focuser 132 can additionally or alternatively delay multiple lines received from the line storage area 112. For example, using delay lines 118a-n, the transmitter focuser 132 can apply a corresponding delay to each of a set of multiple lines corresponding to a specific line in the image. The delay can equalize the phase shift variance present from line to line for multiple lines with different combinations of transmit-receive beam positions. In this way, signal cancellation caused by the phase difference of the combined multiple lines can be minimized and / or avoided. For this purpose, the delay applied by the delay line 118 can depend on the position of the multiple lines and / or the receive lines relative to the center of the corresponding transmit beam. As an illustrative example and regarding Figure 1AThe delay applied to the first transmit beam illustrated in the figure, which is associated with the multi-line receiver position 18, can depend on the distance of the receiver position from the receiver position 16 (e.g., the center of the first transmit beam). Furthermore, the delay implemented by delay lines 118a-n can be configured by the transmit focusing processor 134, as described in more detail below.

[0050] The emitter focuser 132 can also be configured to sum the adjusted (e.g., weighted and / or delayed) multilines at the summer 120. Specifically, the summer 120 can sum (e.g., combine) each adjusted multiline in a set of multilines corresponding to a specific line in the image. The output of the summer 120 and / or the emitter focuser 132 can be coupled to the image processor 122. In this way, the image processor can receive the combined adjusted multilines. The image processor 122 can then generate an image based on the combined adjusted multilines. Furthermore, the image processor 122 can perform scan conversion or other processing to improve the generated image. The resulting image can be output for display at the display 124.

[0051] As described above, the emitter focuser 132 can communicate with the emitter focus processor 134, which can be configured with weights 114a-n and / or delay lines 118a-n. The emitter focus processor 134 can also be described as processor circuitry. The emitter focus processor 134 may include a central processing unit (CPU), graphics processing unit (GPU), digital signal processor (DSP), application-specific integrated circuit (ASIC), controller, field-programmable gate array (FPGA) device, another hardware device, firmware device, or any combination thereof configured to perform the operations described herein. The emitter focus processor 134 can also be implemented as a combination of computing devices, such as a combination of a DSP and a microprocessor, multiple microprocessors, one or more microprocessors combined with a DSP core, or any other such configuration.

[0052] In some embodiments, the emitter focusing processor 134 may configure weights 114a-n and / or configure multipliers 116a-n to apply weights 114a-n based on a weighting algorithm. For example, the weights to be applied to multiple lines may be determined as follows:

[0053] Weight(X,Z) = Amplitude(X,Z), (1)

[0054] Where X represents the azimuth angle of the received multiline relative to the beam axis of the corresponding transmitted beam, where X = 0 corresponds to the central axis of the transmitted beam, and Z represents the depth of the point where the multiline forms the image. Furthermore, amplitude (X, Z) represents the acoustic penetration amplitude of the transmitted wavefront (e.g., the wavefront of the transmitted beam) at a point in the image field. By changing the weights as a function of depth (e.g., according to Equation 1), the transmitter processor 134 can retrospectively and dynamically change the size and shape of the emission aperture (apodization) with depth. That is, for example, the transmitter processor 134 can change the size and shape of the emission aperture after the transmitted beam is emitted at the ultrasound probe 102.

[0055] The emitter focusing processor 134 can configure delay lines 118a-n (e.g., delays affected by the delay lines) based on a delay algorithm. For example, the delay applied to multiple lines by delay line 118 can be determined as follows:

[0056] Delay(X,Z)=propagation_time(X,Z)-propagation_time(0,Z),(2)

[0057] Where X represents the azimuth angle of the received multi-line relative to the beam axis of the corresponding transmitted beam, where X = 0 corresponds to the central axis of the transmitted beam, and Z represents the depth of the point where the multi-line forms the image. Furthermore, propagation_time(X,Z) represents the propagation time of the transmitted wavefront to the point represented by X and Z, and propagation_time(0,Z) represents the time to reach a point at the same depth but coaxial (e.g., on the central axis of the transmitted beam).

[0058] In some embodiments, the emission focusing processor 134 can determine the results of a weighting algorithm (e.g., Equation 1) and / or a delay algorithm (e.g., Equation 2) based on a simulation (e.g., a model) of the emission field. Specifically, the emission focusing processor 134 can determine the values ​​of the function amplitude (X,Z) and / or the function propagation_time (X,Z) based on the simulation. For example, using monochromatic simulations at several frequencies, the emission focusing processor 134 can determine the propagation time based on the phase delay of the emission field. Furthermore, the emission focusing processor 134 can determine the amplitude based on averaging the amplitudes of the emission field at several simulated frequencies. In some embodiments, the emission focusing processor 134 can then apply a depth-related normalization to the weights 114a-n. The normalization can multiply each weight at a given depth by a common factor. In some cases, the normalization can be chosen to make the speckle region have uniform brightness with depth.

[0059] By configuring delay lines 118a-n based on a delay algorithm (Equation 2) and / or configuring multipliers 116a-n and / or weights 114a-n based on a weighting algorithm (Equation 1), the transmit focusing processor can configure the transmit focusing unit 132 to retrospectively transmit the focused transmit beam emitted by the ultrasound probe 102. That is, for example, the transmit focusing processor can configure delay lines 118a-n such that delay lines 118a-n, together with the summer 120, are refocused on multiple lines aligned in a given direction. This refocusing can take into account the phase difference resulting from using different transmit beam positions for each multiple line. Therefore, refocusing can minimize or prevent unwanted phase cancellation in the combined multiple lines. Furthermore, weights 114a-n can be weighted with respect to their respective proximity to the corresponding transmit beams in relation to the multiple lines. For example, the transmit focusing processor 134 can configure weights 114a-n based on a weighting algorithm (e.g., Equation 1) and one or more simulations of the transmit field such that higher weights are applied to multiple lines with higher signal-to-noise ratios. Therefore, the image generated and output to the display 124 may include extended field depth along each receiver line (e.g., extended focus relative to focus 12 generated by conventional focusing) and enhanced penetration (e.g., improved signal-to-noise ratio) due to the combination of multiple samples in each receiver line direction.

[0060] In some embodiments, the transmit focusing processor 134 may derive delays for the configuration of delay lines 118a-n and / or weights for the configuration of weights 114a-n based on a simulation of the transmit field modeling the transmit characteristics of the beam emitted by the ultrasonic probe 102. These characteristics may include, for example, the velocity of sound used to emit the transmit beam, the size and / or shape of the transmit aperture (e.g., the number and / or position of transducer elements in transducer array 104 used to emit the transmit beam), the depth of focus of the transmit beam, etc. In some embodiments, the transmit processor 134 may change one or more of these characteristics during the simulation of the transmit field compared to values ​​used during transmission. For example, the transmit processor 134 may use a velocity of sound different from the velocity of sound used by the ultrasonic probe 102 to emit the transmit beam to determine the delays for the configuration of delay lines 118a-n and / or the weights for the configuration of weights 114a-n. In this way, the emission focuser 132 can emit focused multi-line beams based on a sound velocity different from the sound velocity used for ultrasound emission. This can correct the difference between the expected sound velocity set at the ultrasound probe 102 and the actual sound velocity generated by the propagation of ultrasound energy through a specific medium. That is, for example, emission focusing based on the actual sound velocity can be used to perform tissue aberration correction (TAC), as described in more detail below.

[0061] Although the ultrasound imaging system 150 is illustrated and described as having certain components included in the ultrasound probe 102 and certain components included in the host unit 130, the embodiments are not limited thereto. For this purpose, in some embodiments, the display 124 may be a separate device communicating with the host unit 130. Furthermore, in some embodiments, the beamformer 106 and / or the switch may additionally or alternatively be included in the host unit 130. In some embodiments, multi-line processors 110a-n may be included in the ultrasound probe 102. Moreover, although some components are illustrated as separate, it will be appreciated that one or more components may be included in the combined system and / or a component may perform one or more of the techniques described herein.

[0062] In some embodiments, processors 110a-n, 134, and / or 122 may all be part of a combined system (e.g., host 130). For example, in some embodiments, processors 110a-n, 134, and / or 122 may be located within the same housing or enclosure. Additionally, processors 110a-n, 134, and / or 122 may share one or more software or hardware components. For this purpose, one or more of processors 110a-n, 134, and / or 122 may be implemented as a single processing system. In other embodiments, processors 110a-n, 134, and / or 122 may be separate systems but may communicate with each other. The processors may communicate with each other continuously or intermittently. The processors may communicate with each other or with the ultrasound probe 102, display 124, emitter focuser 132, etc., via one or more wired connection cables (including any suitable conductor, such as a single conductor, twisted pair, Universal Serial Bus (USB) cable, or any other suitable connection cable). Processors 110a-n, 134, and / or 122 may additionally or alternatively communicate with each other and / or with another component of the ultrasound imaging system 150 via wireless or optical connections, or may be connected via any suitable type of removable memory or storage medium or via any other suitable means of communication. Any and / or all of processors 110a-n, 134, and / or 122 may include any suitable system or device or part of any suitable system or device, such as, but not limited to, a mobile console, desktop computer, laptop computer, tablet computer, smartphone, or any other suitable computing device.

[0063] Figure 3This is a schematic diagram of processor circuitry 300 according to aspects of this disclosure. Processor circuitry 300 or similar processor circuitry can be implemented in any suitable device or system previously disclosed. One or more processor circuits 300 can be configured to perform the operations described herein. Processor circuitry 300 may include additional circuitry or electronic components, such as those described herein. In the example, one or more processor circuits 300 may communicate with circuitry or other components within transducer array 104, beamformer 106, ultrasound probe 102. Furthermore, one or more processor circuits 300 may communicate with circuitry or other components within line storage area 112, emitter focuser 132, host 130. One or more processor circuits 200 may also communicate with display 124 and any other suitable components or circuitry within ultrasound imaging system 150. Additionally, any one of host 130 and / or processors 110a-n, 134 and / or 122 may resemble processor circuitry 300. As shown, processor circuitry 300 may include processor 310, memory 312 (which may include instruction set 314), and communication module 316. These components can communicate with each other directly or indirectly, for example, via one or more buses.

[0064] Processor 310 may include a CPU, GPU, DSP, application-specific integrated circuit (ASIC), controller, field-programmable gate array (FPGA), another hardware device, firmware device, or any combination thereof configured to perform the operations described herein. Processor 310 may also be implemented as a combination of computing devices, such as a combination of a DSP and a microprocessor, multiple microprocessors, one or more microprocessors connected to a DSP core, or any other such configuration.

[0065] Memory 312 may include cache memory (e.g., the cache memory of processor 310), random access memory (RAM), magnetoresistive RAM (MRAM), read-only memory (ROM), programmable read-only memory (PROM), erasable programmable read-only memory (EPROM), electrically erasable programmable read-only memory (EEPROM), flash memory, solid-state memory devices, hard disk drives, other forms of volatile and non-volatile memory, or combinations of different types of memory. In embodiments, memory 312 includes a non-transient computer-readable medium. Memory 312 may store instructions 314. Instructions 314 may include instructions that, when executed by processor 310, cause processor 310 to perform the operations described herein with reference to multi-threaded processors 110a-n, emitter-focused processor 134, image processor 122, etc. Instructions 314 may also be referred to as code. The terms “instruction” and “code” should be broadly interpreted to include one or more computer-readable statements of any type. For example, the terms “instruction” and “code” may refer to one or more programs, routines, subroutines, functions, flows, etc. "Instructions" and "codes" can include a single computer-readable statement or many computer-readable statements.

[0066] Communication module 316 may include any electronic circuitry and / or logic circuitry to facilitate direct or indirect data communication between processor circuitry 300, components of host 130, components of ultrasound probe 102, and / or display 124. In this regard, communication module 316 may be an input / output (I / O) device. For example, communication module 316 may include a touchpad or touchscreen display, keyboard / mouse, joystick, buttons, scroll wheel, etc. In some instances, communication module 316 facilitates direct or indirect communication between various components of processor circuitry 300 and / or devices and systems of ultrasound imaging system 150. Furthermore, communication module 316 may use any suitable communication technology (such as cable interfaces (such as USB, micro USB, Lightning, or FireWire interfaces), Bluetooth, Wi-Fi, ZigBee, Li-Fi, or cellular data connections (such as 2G / GSM, 3G / UMTS, 4G / LTE / WiMax, or 5G)) to facilitate wireless and / or wired communication between various components of processor circuitry 300 and / or devices and systems of ultrasound imaging system 150.

[0067] Now go to Figure 4A -B simulates the transmitted beam pattern. Figure 4A In -B, the horizontal axis represents azimuth in some arbitrary units, and the vertical axis represents depth in some arbitrary units. Figure 4AEach of Figures 400 and 450 illustrates a corresponding simulated transmission beam pattern for ultrasonic energy traveling through a medium. In the case of Figure 400, the transmission beam pattern corresponds to ultrasonic energy emitted from an ultrasonic probe (e.g., ultrasonic probe 102) at a transmission velocity of 1540 m / s. Figure 450 illustrates a transmission beam pattern corresponding to ultrasonic energy emitted from an ultrasonic probe at a transmission velocity of 1480 m / s.

[0068] In some embodiments, for example, an ultrasonic probe (such as ultrasonic probe 102) may (e.g., via beamformer 106) be configured to emit at a specific emission rate (such as the emission rate of 1540 m / s shown in 4A or...). Figure 4B The ultrasound energy is emitted at a transmission speed of 1480 m / s (as shown in the diagram). For example, beamformer 106 can actuate elements of transducer array 104 using a transmission pulse pattern corresponding to the desired transmission speed. For this purpose, the beamformer can actuate elements of transducer array 104 using a first transmission pulse pattern for ultrasound transmission at 1540 m / s, and can actuate elements of transducer array 104 using a different second transmission pulse pattern for ultrasound transmission at 1480 m / s. While ultrasound can be configured to emit ultrasound energy at a specific transmission speed (e.g., the desired transmission speed), ultrasound energy can propagate through a medium at different speeds (e.g., the actual transmission speed) due to differences in the density and / or other properties of the medium. As an illustrative example, ultrasound energy can travel at a relatively higher transmission speed (e.g., 1540 m / s) through tissues with low fat content and / or high density, while ultrasound energy can travel at a relatively lower transmission speed (e.g., 1480 m / s) through fatter tissues such as breast tissue.

[0069] exist Figure 4A In the embodiment shown in -B, the medium can have an ultrasonic propagation speed of 1480 m / s. Thus, while drawing 400 corresponds to ultrasonic energy emitted at a transmission speed of 1540 m / s (e.g., a planned transmission speed of 1540 m / s), the ultrasonic energy can propagate through the medium at a transmission speed of 1480 m / s (e.g., an actual transmission speed of 1480 m / s). In this way, drawing 400 illustrates an example of a transmission beam pattern with a mismatch between the actual transmission speed of the ultrasonic energy within the medium and the planned transmission speed used during transmission at the ultrasonic probe. On the other hand, drawing 450 illustrates an example of a transmission beam pattern in which the actual transmission speed of the ultrasonic energy within the medium approximately matches the planned transmission speed used during transmission at the ultrasonic probe.

[0070] Depth of focus 402 corresponds to the depth of focus of the transmitted beam corresponding to a expected transmission velocity of 1540 m / s (e.g., the depth of focus in drawing 400), and depth of focus 452 corresponds to the depth of focus of the transmitted beam corresponding to a expected transmission velocity of 1480 m / s (e.g., the depth of focus in drawing 450). As shown, depth of focus 402 is smaller than depth of focus 452. For this purpose, Figure 4A -B illustrates how a mismatch between the actual emission velocity of ultrasonic energy within a medium and the expected emission velocity used during the emission of ultrasonic energy at ultrasonic probe 102 can be associated with a shift (e.g., offset) in the depth of focus of the resulting emission beam pattern. In some cases, this shift can cause image distortion (e.g., blurring and / or reduced image resolution) in the images produced by the ultrasonic energy. This shift in depth of focus and / or the resulting image distortion can be termed tissue aberration.

[0071] As an illustrative example, tissue aberrations may occur when the host and / or ultrasound probe are not configured with a transmission pulse pattern corresponding to the velocity of ultrasound energy propagation through the medium. Configuring the ultrasound host and / or ultrasound probe with a new transmission pulse pattern to affect the desired transmission velocity used to transmit ultrasound energy may be prohibitive in terms of resources (e.g., time, cost, materials, etc.). For example, the development and testing required to demonstrate the safety and effectiveness of a new transmission pulse pattern could take months. Therefore, tissue aberration correction (TAC) is an alternative approach that can improve the usability of ultrasound imaging systems and reduce the costs involved in the development and / or implementation of ultrasound imaging systems.

[0072] As described in more detail below, the ultrasound imaging system 150 can be used to transmit focused ultrasound imaging data associated with ultrasound transmission at a first transmission velocity based on different second transmission velocities. For example, the ultrasound imaging system 150 can determine transmission focus weights and / or delays based on the second transmission velocity and apply them to multi-line transmissions associated with the ultrasound transmission. In this way, the ultrasound imaging system 150 can effectively refocus the transmission beam pattern corresponding to the first transmission velocity based on the second transmission velocity. In this way, ultrasound data corresponding to transmission at a specific transmission velocity can be tuned to generate images as if the transmission occurred at different transmission velocities. Therefore, tissue aberrations caused by the difference between the transmission velocity at the ultrasound probe and the transmission velocity through the medium can be reduced, and the use of an ultrasound imaging system configured to transmit ultrasound energy at a specific transmission velocity can be extended to imaging tissues with a wider range of characteristics (e.g., corresponding to different ultrasound propagation velocities).

[0073] Figure 5This is a flowchart of a retrospective emission focusing method 500 based on an aspect of this disclosure, which uses an emission velocity different from the emission velocity used to emit ultrasonic energy at an ultrasonic probe (e.g., ultrasonic probe 102). (Refer to...) Figure 6 One or more steps of method 500 are described. As shown, method 500 includes a plurality of enumerated steps, but embodiments of method 500 may include additional steps before, after, or between the enumerated steps. In some embodiments, one or more of the enumerated steps may be omitted, performed in a different order, or performed simultaneously. The steps of method 500 may be performed by any suitable component within the ultrasound imaging system 150, and all steps do not need to be performed by the same component. In some embodiments, one or more steps of method 500 may be performed by the processor circuitry of the ultrasound imaging system 150 (e.g., processor circuitry 300). Figure 3 The processor circuitry of the ultrasound imaging system 150 (e.g., processor circuitry 300) executes the signal or performs the signal within the processor circuitry of the ultrasound imaging system 150. Figure 3 The ultrasound imaging system 150, which is executed under the guidance of the system, includes a main unit 130, a transmission focusing processor 134, an image processor 122, or any other component.

[0074] At step 502, method 500 includes controlling the array to emit ultrasonic energy at a first emission rate. For example, host 130 can control transducer array 104 to output ultrasonic energy at the first emission rate according to an emission pulse pattern. More specifically, host 130 can communicate with beamformer 106, which can actuate one or more transducer elements of transducer array 104 according to an emission pulse pattern in response to the communication. Thus, the actuated one or more transducer elements can emit ultrasonic energy at the first emission rate.

[0075] In some embodiments, the first transmission rate may be the default transmission rate of the ultrasound probe 102 and / or the host 130. For example, the ultrasound probe 102 may be pre-configured to transmit ultrasound energy at the first transmission rate, and / or the host 130 may be pre-configured to control the ultrasound probe 102 to transmit ultrasound energy at the first transmission rate. For example, the host 130 may be pre-configured with a transmission pulse pattern corresponding to the first transmission mode. Furthermore, in some cases, the first transmission rate may be the only transmission rate configured for use by the ultrasound probe 102 and / or the host 130. Alternatively or additionally, the host 130 may determine the first transmission rate based on user input received at the host 130 via the communication module 316. In some embodiments, for example, the host 130 may be pre-configured with multiple transmission pulse patterns corresponding to a corresponding set of predetermined transmission rates. In this case, user input can select a transmission rate from the set of predetermined transmission rates, and based on this selection, the host 130 can select the transmission pulse pattern used to control the ultrasound probe 102. As an illustrative example, the first transmission rate may be 1540 m / s.

[0076] At step 504, method 500 relates to receiving an echo. Specifically, the ultrasound probe 102 can receive an echo associated with ultrasound energy emitted at a first emission rate. For example, after emitting ultrasound energy at the first emission rate, the ultrasound probe 102 can control the operation of the transducer array 104 to receive the echo, and the transmit / receive switch 108 can route a signal associated with the received echo (e.g., an electrical signal corresponding to the received echo) to the host 130.

[0077] At step 506, method 500 relates to determining a second transmission rate. In some embodiments, host 130 may determine the second transmission rate based on user input. For example, host 130 may receive user input via communication module 316 as described above, communication module 316 may include I / O devices. For this purpose, user input may be received via interaction with a graphical user interface (GUI), touchscreen interface, button, mouse, keyboard, joystick, touchpad, etc. Furthermore, user input may correspond to a selection of a second transmission rate. For example, user input may select a second transmission rate from a set of transmission rates predetermined and / or pre-configured at host 130. For example, host 130 may include two or more transmission rates, and each transmission rate may correspond to a different type of tissue. For this purpose, user input may correspond to a selection of tissue type, such as fatty or dense breast tissue, which may be mapped to one of the transmission rates at host 130. Additionally or alternatively, user input may select a second transmission rate from a range of transmission rates supported at host 130. As an illustrative example, the range of emission speeds can include emission speeds associated with the speed of ultrasound energy within different biological materials (e.g., different tissues), such as emission speeds between 1460 m / s and 1620 m / s.

[0078] Alternatively or additionally, the second emission velocity can be determined based on data received at the ultrasound imaging system 150. For example, the ultrasound imaging system 150 (e.g., host 130) can determine the second emission velocity based on an indication of the anatomical feature being imaged, the type and / or capability of a probe (e.g., probe 102) coupled to the system 150, patient data received and / or detected at the ultrasound imaging system 150, etc. The indication of the anatomical feature may correspond to user input selecting the anatomical feature. Alternatively or additionally, the ultrasound imaging system 150 can identify the anatomical feature based on one or more settings for imaging the feature (such as depth settings, probe 102 position and / or orientation, etc.). In some embodiments, for example, the ultrasound imaging system 150 may include a mapping (e.g., a table) between the indication of the anatomical feature and the imaged anatomical feature to determine the anatomical feature. In some embodiments, the ultrasound imaging system 150 may be trained to identify the anatomical feature and / or the second emission velocity based on another suitable implementation of a deep learning network (such as a convolutional neural network (CNN)) or an artificial intelligence system or architecture (including, for example, random forest deep learning methods or regression analysis methods). For example, the ultrasound imaging system 150 may classify data received at the ultrasound imaging system 150 according to specific anatomical features and / or emission velocities based on deep learning networks and / or artificial intelligence systems. Furthermore, patient data may include patient-associated diagnoses, weight, body mass index (BMI), medical history, etc., which may be input into the ultrasound imaging system 150 and / or retrieved from local or remote data storage (e.g., a database). The ultrasound imaging system 150 may also include mappings (e.g., tables) between anatomical features and / or indications of anatomical features and emission velocities, and / or between patient metrics (e.g., BMI) and emission velocities, to determine a second emission velocity.

[0079] As an illustrative example, a relatively high second emission velocity can be determined in response to determining that the imaged anatomical feature is relatively dense compared to other anatomical features (as is the case with muscle tissue) and / or determining that the patient has a relatively low BMI (e.g., a low proportion of total fat). Conversely, a relatively high second emission velocity can be determined in response to determining that the imaged anatomical feature is relatively dense compared to other anatomical features (as is the case with muscle tissue) and / or determining that the patient has a relatively low BMI (e.g., a low proportion of total fat).

[0080] Furthermore, in some embodiments, the second emission velocity can be determined based on analysis of ultrasound imaging data, such as data associated with received echoes (e.g., the echo received at step 504), which are associated with ultrasound energy emitted at the first velocity. For example, in some embodiments, the ultrasound imaging system 150 can identify tissue aberrations (e.g., sound velocity aberrations) in an image generated from the received echoes and / or based on data associated with the received echoes. Based on the identified aberrations, the ultrasound imaging system 150 can also determine whether to set the second emission velocity to a velocity relatively higher or lower than the first emission velocity and / or adjust it from the first emission velocity. For example, the ultrasound imaging system 150 can determine a mapping of tissue aberrations (e.g., at different points within the image) in an image generated from the received echoes, and can determine the second sound velocity based on the mapping of tissue aberrations. An example of identifying tissue aberrations within an image is described in Provisional Application No. 62 / 838,365, filed on April 25, 2019, entitled “SYNTHETIC TRANSMIT FOCUSING ULTRASOUND SYSTEM WITH SPEED OF SOUNDMAPPING”.

[0081] Furthermore, analyzing ultrasound imaging data to determine the second emission velocity may additionally or alternatively include comparing ultrasound imaging data corresponding to different emission velocities. For example, ultrasound imaging system 150 may control transducer array 104 to emit ultrasound energy at a set of different emission velocities including the first emission velocity (e.g., at step 502), and may receive echoes corresponding to that set of different emission velocities. In some cases, ultrasound imaging system 150 may generate a corresponding image for each of the emission velocities in the set based on the echoes. Ultrasound imaging system 150 can then identify the image with the highest image quality and / or specific qualities (such as highest brightness, contrast, etc.) from the images. In particular, ultrasound imaging system 150 may perform image processing (such as pixel-level image processing (evaluating whether there is a change in the color of a pixel)) to compare the images. In some embodiments, ultrasound imaging system 150 may determine the emission velocity corresponding to the identified image as the second emission velocity.

[0082] At step 508, method 500 involves generating a multiline based on the received echo (e.g., the echo received at step 504). For example, host 130 may generate the multiline at multiline processors 110a-n based on the echo received at ultrasound probe 102. For this purpose, multiline processors 110a-n may apply delay and / or apodization weights to the received echo (e.g., to an electrical signal corresponding to the received echo) to form receiving beams (e.g., multilines) with different azimuths corresponding to the same emitted ultrasound energy.

[0083] At step 510, method 500 involves transmitting a focused multiline based on a second transmission velocity. Specifically, the host unit 130 can adjust the multiline corresponding to a particular receive line position using the transmit focuser 132 before combining the adjusted multiline, as referenced below. Figure 6 As described above. Furthermore, the multi-line generated at step 508 can be stored before the multi-line is emitted and focused, at least until each multi-line corresponding to the position of the received line is received, as referenced above. Figure 2 As described. In some embodiments, for example, before the host 130 adjusts the multiline based on the second transmit speed, the multiline can be stored in the online storage area 112.

[0084] Now for reference Figure 6 The figure illustrates a flowchart of a method 600 for firing focused multi-line emission based on a second emission velocity according to aspects of the present disclosure. Specifically, step 510 of method 500 can be implemented according to one or more steps of method 600. As shown, method 600 includes a plurality of enumerated steps, but embodiments of method 600 may include additional steps before, after, or between the enumerated steps. In some embodiments, one or more of the enumerated steps may be omitted, executed in a different order, or executed simultaneously. The steps of method 600 can be executed by any suitable component within the ultrasound imaging system 150, and all steps do not need to be executed by the same component. In some embodiments, one or more steps of method 600 can be executed by the processor circuitry of the ultrasound imaging system 150 (e.g., processor circuitry 300). Figure 3 The processor circuitry of the ultrasound imaging system 150 (e.g., processor circuitry 300) executes the signal or performs the signal within the processor circuitry of the ultrasound imaging system 150. Figure 3 The ultrasound imaging system 150 is executed under the guidance of the ultrasound imaging system 134, image processor 122 or any other component.

[0085] At step 602, method 600 involves determining emission focus weights. In some embodiments, emission focus processor 134 may determine the emission focus weights based on Equation 1 and a simulation of the emission field. For example, emission focus processor 134 may simulate the emission field, and based on this simulation, emission focus processor 134 may determine amplitude values ​​(e.g., values ​​of function amplitudes (X, Z)) at different points in the simulated image field. Referring above to Equation 1 and Figure 2 As described, the transmit-focus processor 134 can use the determined amplitude values ​​to determine the transmit-focus weights of multi-line pairs corresponding to points in the image field. Specifically, the transmit-focus processor 134 can determine transmit-focus weights that weight the contribution of each multi-line pair to its corresponding proximity to the corresponding transmit beam. For example, the transmit-focus processor 134 can determine a set of transmit-focus weights that increase with increasing signal-to-noise ratio at the corresponding multi-line pair (e.g., the location of the receive line in the analog field) based on the determined amplitude values.

[0086] Furthermore, in some embodiments, the emission focusing processor 134 may determine the emission focusing weight based on a second emission velocity. For example, the emission focusing processor 134 may simulate the emission field in part based on the second emission velocity. The simulation of the emission field may include one or more parameters corresponding to the characteristics used to emit ultrasonic energy. These characteristics may include, for example, the velocity of sound used to emit the emission beam, the size and / or shape of the emission aperture (e.g., the number and / or arrangement of transducer elements in transducer array 104 used to emit the emission beam), the depth of focus of the emission beam, etc. Therefore, in order to simulate the emission field based on the second velocity of sound, the emission focusing processor 134 may be configured to set one or more parameters of the simulation based on the second velocity of sound. Furthermore, based on the second emission velocity, the emission focusing processor 134 may be configured to simulate the emission field using characteristics that correspond to or differ from the value used to emit ultrasonic energy (e.g., the first emission velocity).

[0087] For example, if the second emission velocity is the same as the first emission velocity, the emission focusing processor 134 can simulate the emission field using the ultrasonic energy emitted at the second emission velocity. In this case, the characteristics of the simulated emission field can correspond to the characteristics used to emit ultrasonic energy using the ultrasonic probe 102 (e.g., the first emission velocity). As an illustrative example, if the first and second emission velocities are 1540 m / s, the emission focusing processor 134 can determine the emission focusing weights based on the simulation of the emission field corresponding to the emission velocity of 1540 m / s.

[0088] On the other hand, if the second emission velocity differs from the first emission velocity, the emission focusing processor 134 can be configured to adjust the velocity of sound and / or depth of focus of the simulated emission field compared to the corresponding velocity of sound and / or depth of focus used during ultrasonic energy emission. As an illustrative example, if the first emission velocity is 1540 m / s and the second emission velocity is 1480 m / s, the emission focusing processor 134 can be configured to simulate the emission field at an emission velocity of 1480 m / s. In this case, the simulation of the emission field can be similar to... Figure 4B The diagram 450 is shown. Alternatively or additionally, the emission focusing processor 134 can be configured to simulate the emission field using a depth of focus adjusted relative to the depth of focus expected for emitting ultrasonic energy at a first emission velocity. For example, this can be illustrated by the difference between a depth of focus 402 corresponding to an emission velocity of 1540 m / s and a depth of focus 452 corresponding to an emission velocity of 1480 m / s. Figure 4A -B) Differences in launch velocities can lead to variations in the depth of focus of the launch field. Thus, adjusting the depth of focus of the simulated launch field can provide a similar effect to simulating the launch field using a second launch velocity. In some embodiments, the launch focusing processor 134 can identify the adjusted depth of focus of the simulated launch field based on a second sound velocity. In some embodiments, for example, the launch focusing processor 134 can be configured with a mapping (e.g., a lookup table) between launch velocities and depth of focus for launch field simulation. Therefore, the launch focusing processor 134 can determine the depth of focus for the simulated launch field based on the second sound velocity and the mapping, and the launch focusing processor 134 can then simulate the launch field based on the determined depth of focus for simulation.

[0089] In any case, the emission focusing processor 134 can determine the emission focusing weights based on simulation. In some embodiments, the emission focusing weights may be weights applied to multiple lines at the emission focusing unit 132. Therefore, the emission focusing processor 134 can configure weights 114a-n based on the determined emission focusing weights.

[0090] At step 604, method 600 involves determining a launch focus delay. In some embodiments, the launch focus processor 134 may determine the launch focus delay based on Equation 2 and a simulation of the launch field. For example, the launch focus processor 134 may simulate the launch field, and based on this simulation, the launch focus processor 134 may determine propagation time (e.g., propagation delay) values ​​(e.g., the value of the function propagation_time(X,Z)) at different points in the simulated image field. Referring above to Equation 2 and Figure 2As described, the transmit focusing processor 134 can use the determined propagation time value to determine the transmit focusing delay of a multiline corresponding to a point in the image field. Specifically, the transmit focusing processor 134 can determine the transmit focusing delay by equalizing the phase shift variance present from line to line for multilines with different transmit-receive beam position combinations. This minimizes and / or avoids signal cancellation caused by the phase difference of the combined multilines. For example, the transmit focusing processor 134 can determine the transmit focusing delay based on the position of the multiline relative to the center of the corresponding transmit beam within the simulated transmit field.

[0091] The emission focusing processor 134 can also determine the emission focusing delay based on a second emission velocity. For example, as described above, the emission focusing processor 134 can simulate the emission field in part based on the second emission velocity. Therefore, the emission focusing processor 134 can simulate the emission field using a second emission velocity that may be the same as or different from the first emission velocity, and / or the emission focusing processor 134 can simulate the emission field using a depth of focus adjusted relative to the depth of focus expected when emitting ultrasonic energy for the first emission velocity. In any case, the emission focusing processor 134 can determine the emission focusing delay based on the simulation of the emission field. Furthermore, the emission focusing delay can be a delay applied to multiple lines at the emission focusing unit 132 (e.g., via delay lines 118a-n). Therefore, the emission focusing processor 134 configures the emission focusing unit 132 and / or delay lines 118a-n to apply the determined emission focusing delay.

[0092] At step 606, method 600 involves adjusting the multiline based on the determined emission focus weights and delays. As described above, the emission focus processor 134 can configure the emission focuser 132 to apply the determined emission focus weights and / or delays to the multiline. For this purpose, adjusting the multiline based on the determined emission focus weights can involve applying weights 114a-n (which can be configured based on the emission focus weights) to the multiline at multipliers 116a-n. Furthermore, adjusting the multiline based on the determined emission focus delay can involve delaying the multiline emission focus delay at delay lines 118a-n.

[0093] At step 608, method 600 involves summing the adjusted multilines. That is, for example, the multilines adjusted at step 606 can be combined. In some embodiments, emission focuser 132 can sum the multilines at summer 120, which can receive the outputs of delay lines 118a-n as input. By summing the multilines, summer 120 can produce emission-focused image data with extended depth of field. Summer 120 can be implemented with adder circuitry, implemented as a digital summer, or a combination thereof.

[0094] Now return to Figure 5At step 512, method 500 may include generating an image based on emission-focused multilines. Specifically, image processor 122 may receive emission-focused multilines as input and may generate an image based on the received emission-focused multilines. In some embodiments, the emission-focused multilines may correspond to image data associated with lines in the image. Therefore, image processor 122 may receive a set of emission-focused multilines respectively corresponding to image data associated with different lines within the image (e.g., image data received along different receiving lines), and may aggregate the set of emission-focused multilines to generate an image. Image processor 122 may also perform scan conversion or other processing to improve the generated image. Referring above to steps 510 and... Figure 6 As described, emission focusing on multiple lines can involve adjusting the multiple lines based on emission focus delay. Therefore, image processor 122 can generate an image based on the multiple lines adjusted by the emission focus delay.

[0095] At step 514, method 500 may involve outputting an image for display. More specifically, the image generated by image processor 122 may be output to a display, such as display 124, that may be included in or communicatively coupled to host 130 (e.g., via a wired or wireless interface).

[0096] Figures 7A-7C The illustration shows the emission beam pattern generated from retrospective emission-focused ultrasound image data (e.g., emission-focused multi-line). Figures 7A-7C In this model, the horizontal axis represents azimuth in arbitrary units, and the vertical axis represents depth in arbitrary units. Figure 7A In the embodiment shown in -C, each of the transmitted beam patterns is determined relative to ultrasonic emission through a medium, wherein the ultrasonic energy propagates at a speed of 1480 m / s. For this purpose, the illustrated transmitted beam pattern may correspond to the techniques described herein (e.g., according to...). Figure 5 Method 500 and / or Figure 6 Method 600 (one or more steps) retrospectively Figure 4A The beam pattern shown in -B is generated by focusing the emitted beam pattern.

[0097] In particular, Figure 7A The illustration shows plot 700 corresponding to the transmission beam of the first ultrasonic emission emitted by transducer array 104 at a transmission velocity of 1480 m / s. Plot 700 also corresponds to ultrasound imaging data associated with the first ultrasonic emission (e.g., multi-line generated based on the first ultrasonic emission) retrospectively focused based on the transmission velocity of 1480 m / s. For this purpose, plot 700 illustrates the ultrasound imaging data following retrospective focusing and... Figure 4BThe transmission beam pattern corresponding to the transmission beam pattern in plot 450. That is, for example, plot 700 can be generated by adjusting the multiline and / or received echoes associated with the ultrasound transmission emitted using the transmission beam pattern of plot 450 using transmission focus weights and / or delays.

[0098] Figure 7B The illustration shows plot 720 corresponding to the transmission beam of a second ultrasonic emission emitted by a transducer array at a transmission velocity of 1540 m / s. Plot 720 also corresponds to ultrasound imaging data associated with the second ultrasonic emission (e.g., a multi-line generated by the second ultrasonic emission) based on the transmission focusing at a transmission velocity of 1540 m / s. For this purpose, plot 720 illustrates the ultrasound imaging data following retrospective transmission focusing. Figure 4A The transmission beam pattern in plot 400 corresponds to the transmission beam pattern. Therefore, plot 720 can be generated by adjusting the multi-line and / or received echoes associated with the ultrasound transmission emitted using the transmission beam pattern of plot 400 using transmission focus weights and / or delays.

[0099] Compared to the transmit beam pattern shown in Figure 450, the retrospective transmit-focused beam pattern shown in Figure 700 exhibits an extended depth of field (e.g., an extended focus). For example, the retrospective transmit-focused beam pattern shown in Figure 700 has a narrower profile than the transmit beam pattern shown in Figure 450. Similarly, the retrospective transmit-focused beam pattern shown in Figure 720 exhibits an extended depth of field compared to the transmit beam pattern shown in Figure 400. However, the beam pattern in Figure 720 has a wider profile than the beam pattern in Figure 700, which may result in reduced image resolution and / or increased blur in the image generated based on the beam pattern in Figure 720 compared to the image generated based on the beam pattern in Figure 700. The difference between plotting 700 and plotting 720 can be caused by the effect of the velocity difference between the emission velocity used at transducer array 104 (e.g., 1540 m / s in this example) and the emission velocity of ultrasonic energy propagating within the medium (e.g., 1480 m / s in this example) on the generation of the beam pattern of plotting 720. In other words, the beam pattern of plotting 720 may be distorted due to tissue aberrations compared to the beam pattern of plotting 700.

[0100] Figure 7C The illustration shows plot 740 corresponding to the transmission beam of a third ultrasonic emission emitted by a transducer array at a transmission velocity of 1540 m / s. Plot 740 also corresponds to ultrasound imaging data associated with a third ultrasonic emission focused based on a transmission velocity of 1480 m / s (e.g., a multi-line generated by the third ultrasonic emission). For this purpose, similar to plot 720, plot 740 illustrates the ultrasound imaging data following retrospective emission focusing. Figure 4A The transmitted beam pattern in plot 700 corresponds to the transmitted beam pattern in plot 700. However, while plot 720 can be generated from transmitted focused image data corresponding to the beam pattern of plot 400 based on a transmission velocity of 1540 m / s, plot 740 can be generated from transmitted focused image data corresponding to the beam pattern of plot 400 based on a transmission velocity of 1480 m / s. In a further comparison with plot 720, the beam pattern shown in plot 740 maintains a relatively narrower beam profile. As a result, the image generated based on the beam pattern of plot 740 can appear less blurry (e.g., sharper) and has a relatively higher resolution than the image generated based on the beam pattern of plot 720. In fact, the beam pattern shown in plot 740 looks substantially similar to the beam pattern shown in plot 700. Therefore, the image generated based on the beam pattern of plot 740 can be similar to the image generated based on the beam pattern of plot 700. In this way, Figure 740 illustrates that the velocity difference between the emission velocity used at transducer array 104 (e.g., 1540 m / s in this example) according to the technology described herein and the emission velocity of ultrasonic energy propagating in the medium (e.g., 1480 m / s in this example) can be taken into account via retrospective emission focusing (e.g., the effect of the difference can be minimized).

[0101] Figure 8 The plot 800, which compares the point spread functions (802, 804, and 806) at the depth of focus for different ultrasound imaging and emission focusing techniques, is similar to the reference above. Figure 7A -C describes this. Specifically, plot 800 includes a comparison of focal quality between techniques, where a wider spread value on the horizontal axis represents a relatively lower focal quality, and a narrower spread value on the horizontal axis represents a relatively higher focal quality. In the illustrated embodiment, each of the point spread functions (802, 804, and 806) is determined relative to ultrasonic emission through the medium, where the ultrasonic energy propagates at a speed of 1480 m / s. Figure 8 In the diagram, the horizontal axis represents distance in some arbitrary units, and the vertical axis represents intensity in some arbitrary units.

[0102] The first point spread function 802 corresponds to the point spread function within a first image generated based on a first ultrasonic emission with a emission velocity of 1480 m / s. More specifically, the first point spread function 802 corresponds to the point spread function generated from an image based on emission-focused ultrasound data associated with the first ultrasonic emission based on a emission velocity of 1480 m / s. Therefore, the first point spread function 802 can be related to the point spread function based on... Figure 7A The image generated is associated with the transmitted beam pattern shown in drawing 700.

[0103] The second point spread function 804 corresponds to the point spread function within a second image generated based on a second ultrasonic emission with a emission velocity of 1540 m / s. Specifically, the second point spread function 804 corresponds to the point spread function generated from an image based on emission-focused ultrasound data associated with a second ultrasonic emission based on a emission velocity of 1540 m / s. In this way, the second point spread function 804 can be correlated with... Figure 7B The image generated is associated with the beam pattern shown in drawing 720.

[0104] The third point spread function 806 corresponds to the point spread function within a third image generated based on a third ultrasonic emission with a emission velocity of 1540 m / s. However, compared to the second point spread function 804, the third point spread function 806 corresponds to a third image generated based on emission-focused ultrasound data associated with a third ultrasonic emission based on a emission velocity of 1480 m / s. That is, for example, the third point spread function 806 can correspond to a third image based on... Figure 7C The image generated by the beam pattern shown in drawing 740.

[0105] As shown in the figure, each of the first point spread function 802 and the third point spread function 806 is relatively similar, while the second point spread function 804 has a relatively wider distribution than both the first point spread function 802 and the third point spread function 806. For this purpose, drawing 800 also illustrates that for a given point in the corresponding images, the first and third images (e.g., corresponding to the first point spread function 802 and the third point spread function 806, respectively) can be less blurred and more distinguishable than the second image (e.g., corresponding to the second point spread function 804). In other words, drawing 800 also shows that the velocity difference between the emission velocity used at the transducer array 104 according to the technique described herein (e.g., 1540 m / s in this example) and the emission velocity of the ultrasonic energy propagating within the medium (e.g., 1480 m / s in this example) can be taken into account via retrospective emission focusing (e.g., the effect of the difference can be minimized).

[0106] Figure 9A Figure -B illustrates an ultrasound image of breast tissue carrying ultrasound energy at a speed of approximately 1480 m / s. Figure 9A In -B, the horizontal axis represents azimuth in some arbitrary units, and the vertical axis represents depth in some arbitrary units. Figure 9A An ultrasound image 900 is illustrated, generated based on the emission of ultrasound energy at a transmission velocity of 1540 m / s (e.g., from transducer array 104) and the emission focusing of ultrasound data (e.g., multi-line) associated with the ultrasound energy at a transmission velocity of 1540 m / s. Figure 9BThe illustration shows an ultrasound image 950 generated based on the emission of ultrasound energy at a transmission velocity of 1540 m / s (e.g., from transducer array 104) and the emission focusing of ultrasound data (e.g., multi-line) associated with ultrasound energy at a transmission velocity of 1480 m / s. As shown, the image quality of ultrasound image 950 is better than that of ultrasound image 900 in terms of resolution and / or sharpness. Therefore, Figure 9A -B also demonstrates the benefits of the techniques described in this article.

[0107] Those skilled in the art will recognize that the apparatus, systems, and methods described above can be modified in various ways. Accordingly, those skilled in the art will appreciate that the embodiments included in this disclosure are not limited to the specific exemplary embodiments described above. In this regard, while illustrative embodiments have been shown and described, a wide range of modifications, alterations, and substitutions are contemplated in the foregoing disclosure. It should be understood that such variations can be made to the foregoing without departing from the scope of this disclosure. Accordingly, it should be appreciated that the appended claims are to be interpreted broadly and in a manner consistent with this disclosure.

Claims

1. An ultrasound imaging system (150), comprising: An array (104) of acoustic elements is configured to emit (502) ultrasonic energy at a first emission velocity and receive (504) an echo associated with the ultrasonic energy emitted at the first emission velocity; as well as A processor circuit (300) that communicates with the array of acoustic elements and is configured to: Generate (508) multiple multilines based on the received echoes; (506) A second transmission speed is determined based on user input, wherein the user input includes a selection of the second transmission speed from a set of predetermined transmission speeds; A set of launch focusing delays is determined based on the second launch velocity; The multiple multi-line arrays are adjusted using the set of emission focusing delays; The (512) image is generated based on a modulated multiline; and The generated image is output (514) to a display (124) that communicates with the processor circuitry.

2. The ultrasound imaging system according to claim 1, further comprising a plurality of delay lines (118a-n) communicating with the array of acoustic elements and the processor circuit, wherein, The processor circuitry is also configured to control the plurality of delay lines to delay the plurality of multi-line according to the set of emission focusing delays, thereby adjusting the plurality of multi-line.

3. The ultrasound imaging system according to claim 1, wherein, The processor circuit is also configured to: A set of launch focusing weights is determined based on the second launch velocity; and The set of emission focusing weights is used to adjust the multiple multilines.

4. The ultrasound imaging system according to claim 3, further comprising a multiplier (116a-n) communicating with the array of acoustic elements and the processor circuit, wherein, The processor circuit is also configured to control the multiplier to apply the set of emitter focusing weights to the plurality of multilines to adjust the plurality of multilines.

5. The ultrasound imaging system according to claim 1, further comprising a summer (120) communicating with the processor circuit and the array of acoustic elements, wherein, The summer is configured to sum multiple adjusted multilines to generate emission-focused image data, and the processor circuitry is configured to also generate the image based on the emission-focused image data.

6. The ultrasound imaging system according to claim 1, wherein, The processor circuitry is configured to determine the set of emission focusing delays based on a model of the ultrasonic energy emitted at the second emission velocity.

7. The ultrasound imaging system according to claim 1, wherein, The array of acoustic elements is configured to emit the ultrasonic energy at a first depth of focus (402), wherein the processor circuit is also configured to determine the set of emission focusing delays based on a model of ultrasonic energy emitted at a second depth of focus (452), wherein the processor circuit is also configured to determine the second depth of focus based on the second emission velocity.

8. The ultrasound imaging system according to claim 1, wherein, The ultrasonic energy comprises a plurality of ultrasonic beams, and wherein the array of acoustic elements is configured to emit each of the plurality of ultrasonic beams from a corresponding emission beam position.

9. The ultrasound imaging system according to claim 8, wherein, The plurality of multi-line data correspond to imaging data associated with the location of the receiving line, and the echo is received along the location of the receiving line for each of the plurality of ultrasonic beams.

10. The ultrasound imaging system according to claim 1, wherein, The processor circuitry is configured to generate the image based on additional adjusted multiple lines, wherein the adjusted multiple lines correspond to a first line of the image, and the additional adjusted multiple lines correspond to a second line of the image.

11. The ultrasound imaging system according to claim 1, further comprising the display.

12. A method (500) for retrospective emission focusing of ultrasound data for ultrasound imaging, comprising: The array of acoustic elements communicating with the processor circuit (300) is controlled by the processor circuit (300) to emit (502) ultrasonic energy at a first emission rate and to receive (504) echoes associated with the emitted ultrasonic energy. The processor circuit generates (508) multiple multi-line generators based on the received echoes; The processor circuit determines (506) a second transmission rate based on user input, wherein the user input includes a selection of the second transmission rate from a set of predetermined transmission rates; The processor circuit determines a set of emission focusing delays based on the second emission rate; The processor circuitry uses the set of emitter focus delays to adjust the plurality of multi-line arrays; The processor circuit generates (512) an image based on a modulated plurality of multi-line arrays; and The generated image is output (514) by the processor circuit to a display (124) that communicates with the processor circuit.

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