An ultrasonic diagnostic imaging system and method translates an aperture across an array transducer which is less that the size of the array. At each aperture location a transmit beam is focused above, or alternatively below, the array and a region of interest being scanned from the aperture location, resulting in broad insonification of the region of interest. At the lateral ends of the array the aperture is no longer translated but the focal point of the transmit beam is translated from the same aperture position, preferably with tilting of the beam direction. Multiple receive beams are processed in response to each transmit event and the overlapping receive beams and echo locations are spatially combined to produce synthetic transmit focusing over the center of the image field and noise reduction by spatial compounding at the lateral ends of the image field.

The present disclosure describes ultrasound systems configured to enhance flow imaging and analysis by adaptively adjusting one or more imaging parameters in response to acquired flow measurements. Example systems can include an ultrasound transducer and one or more processors. Using the system components, mean flow velocity magnitude and acceleration can be determined within a target region during an acquisition phase, which may include a cardiac cycle. One or more adjusted flow imaging parameters, such as adjusted ensemble length, temporal smoothing filter length and/or step size, can be determined based on the acquired flow measurements to increase the signal quality of newly acquired ultrasound echo signals. The adjusted flow imaging parameters can then be applied by the ultrasound transducer during a second acquisition phase.

A portable ultrasonic diagnostic apparatus and a method of controlling the same are provided, including a flexible display and a controller which changes a layout of an image displayed on the flexible display. An image necessary for diagnosing an object is appropriately disposed on a flexible display according to a situation, and thus, the user can intuitively determine an ultrasonic image.

In some embodiments, ultrasound receive beamforming yields beamformed samples, based upon which spatially intermediate pixels (232, 242, 244) are dynamically reconstructed. The samples have been correspondingly derived from acquisition through respectively different acoustic windows (218, 220). The reconstructing is further based on temporal weighting of the samples. In some embodiments, the sampling is via synchronized ultrasound phased-array data acquisition from a pair of side-by-side, spaced apart (211) acoustic windows respectively facing opposite sides of a central region (244) to be imaged. In particular, the pair is used interleavingly to dynamically scan jointly in a single lateral direction in imaging the region. The acquisition in the scan is, along a synchronization line (222) extending laterally across the region, monotonically progressive in that direction. Rotational scans respectively from the window pair are synchronizable into a composite scan of a moving object. The synchronization line (222) can be defined by the focuses of the transmits. The progression may strictly increase.

Front-end circuitry for an ultrasound system is described which comprises a beamformer FPGA integrated circuit, transmit ICs with both pulse transmitters and linear waveform transmitters, transmit control and receiver ICs, and analog-to-digital converter (ADC) ICs. Waveform data for both the linear and pulser transmitters is stored in the transmit control and receiver ICs, saving pins on the FPGA, which is the conventional source of this data. The ADCs couple digital echo data to the FPGA for beamforming over serial bus lines, saving additional FPGA pins over a conventional parallel data arrangement. The inclusion of both pulser and linear waveform transmit capabilities in the transmit ICs enables the use of both types of transmitters in the formation of a multi-mode image, such as use of the pulsers for Doppler beams and linear transmitters for B mode beams in the formation of a colorflow image.

An ultrasonic diagnostic imaging for analyzing shear wave characteristics utilizes a background motion compensation subsystem which acts as a spatial filter of pulse-to-pulse autocorrelation phases over the ROI of tracking pulse vectors to compensate for background motion. The subsystem is configured to compute the sum of all lag-1 autocorrelations of tracking line ensemble data over the tracking ROI, for each PRI. The inventive technique does not significantly reduce sensitivity to shear waves, because the shear wave is spatially smaller than the ROI.

Certain embodiments pertain to cross-amplitude modulation (xAM) ultrasound imaging methods and systems configured to excite a first subaperture of transducer elements to transmit a first ultrasound plane wave, excite a second subaperture of transducer elements to transmit a second ultrasound plane wave noncollinear to the first ultrasound plane wave, the second ultrasound plane wave axisymmetric to the first ultrasound plane wave about a bisector, and simultaneously excite both first and second subapertures to transmit first and second ultrasound plane waves to cause an acoustic pressure above a threshold along the bisector.

A method in accordance with the present disclosure may include transmitting a plurality of ultrasound pulses toward a medium from a transducer array, wherein the plurality of ultrasound pulses includes a sequence of a Doppler burst (10-1, 10-2) comprising a plurality of unfocused first pulses (12) and a B-mode burst comprising one or more second pulses (13). The method may further include detecting echoes responsive to the transmitted sequence, wherein the detecting includes simultaneously detecting, within a field of view, FOV, of the array, a set (14-1, 14-2) of first echoes responsive to the plurality of unfocused first pulses (12), generating Doppler data from signals representative of the set (14-1, 14-2) of first echoes, generating B-mode image data from signals representative of echoes responsive to the one or more second pulses (13), and simultaneously displaying the Doppler data and B-mode image data.

To provide an ultrasound diagnostic apparatus and a control method of the ultrasound diagnostic apparatus in which a user can smoothly perform an examination on a subject while simultaneously using a plurality of ultrasound probes.

An ultrasound diagnostic apparatus includes a plurality of ultrasound probes having communication circuits that transmit synchronization signals, and operate according to a time sequence including an ultrasonic wave transmission/reception period for transmitting and receiving ultrasonic waves, a waiting period for stopping transmission and reception of the ultrasonic waves, and a synchronization period for synchronization between the ultrasound probes. In a case where any ultrasound probe is in the ultrasonic wave transmission/reception period, the other ultrasound probe is in the waiting period. In a case where any ultrasound probe is in the synchronization period, the other ultrasound probe is also in the synchronization period. In a case where the synchronization is failed, the synchronization period is extended and after the plurality of ultrasound probes becomes a state capable of synchronizing with each other, any ultrasound probe is in the ultrasonic wave transmission/reception period.

An ultrasound diagnostic apparatus 1 includes a transducer array 2, a transmission unit 3 that transmits an ultrasonic pulse FP and an ultrasonic pulse SP having phases inverted from each other on the scanning line from the transducer array 2 multiple times, a reception unit 4 that acquires reception signals from an output signal of the transducer array 2, a quadrature detection unit 5 that performs quadrature detection on the reception signals to acquire IQ signal strings, a tissue velocity detection unit 6 that detects a velocity of a tissue in a subject based on the IQ signal strings, a phase correction unit 7 that corrects phases of the IQ signal strings, a pulse inversion addition unit 8 that adds IQ signals corresponding to the ultrasonic pulse FP and IQ signals corresponding to the ultrasonic pulse SP using the corrected IQ signal strings to acquire added signals, and an image generation unit 10 that generates an ultrasound image from the added signals.