Abstract: Sparkle in color flow imaging is detected. Color flow data is estimated with different pulse repetition frequency (PRF). By correlating the color flow data estimated with different PRFs, sparkle is identified. Color flow images may be filtered to reduce motion while maintaining the sparkle region (e.g., kidney stone imaging) or reduce the sparkle region while maintaining motion (e.g., remove sparkle as system noise).

Abstract: Flash suppression is provided in motion imaging. Separate regions of motion in a same frame or image are tested for flash independently. The size, shape, spatial variance, and/or location of a given region are used to categorize a level or likelihood of flash artifact for that region. Based on the level or likelihood, the motion information is altered to reduce flash.

Abstract: Devices, systems, and methods adjust one or more color flow parameters in response to a sensed motion of an ultrasound probe exceeding a motion threshold. One such method includes acquiring, by an ultrasound imaging device including an ultrasound probe, ultrasound image information; sensing, by a motion sensor, a motion of the ultrasound probe; determining whether the sensed motion of the ultrasound probe exceeds a motion threshold; adjusting one or more color flow parameters in response to determining that the sensed motion of the ultrasound probe exceeds the motion threshold; and generating an ultrasound color flow image based on the acquired ultrasound image information and the one or more color flow parameters.

Abstract: For Doppler imaging in ultrasound, a single parameter is formed from both power and velocity. In any combination function, a derivative of velocity and/or velocity are combined with power. The resulting value is used to look-up a color from a one-dimensional color map.

Abstract: To accurately generate the three-dimensional ultrasound data and/or determine the position of the ultrasound scan relative to pre-operative data, a tracking sensor is releasably connected with the ultrasound probe. The connection positions the tracking sensor near a distal end of the probe for insertion into the patient. A needle guide may be similarly releasably connected with the probe and, at least in part, inserted into the patient.

Abstract: In spectral Doppler imaging, a high PRF is used independent of the velocity scale. The adjustment is then of the velocity scale. By optimizing the velocity scale independent of the high PRF in an on-going or automated basis, user activation may be avoided and/or interruption to reconfigure for an altered PRF may be avoided. The acquired data may be stored, allowing for past data to be processed again when a new velocity scale or other setting is selected. The resulting spectral Doppler image may continue to display spectra over time without a gap or without premature loss of spectra due to reconfiguring.

Abstract: Sparkle in color flow imaging is detected. Color flow data is estimated with different pulse repetition frequency (PRF). By correlating the color flow data estimated with different PRFs, sparkle is identified. Color flow images may be filtered to reduce motion while maintaining the sparkle region (e.g., kidney stone imaging) or reduce the sparkle region while maintaining motion (e.g., remove sparkle as system noise).

Abstract: Responsive power saving is provided for ultrasound imaging, such as in portable ultrasound systems. By reducing scan line density in response to removal of a transducer from a patient, power usage may be reduced while still monitoring for return of the transducer to the patient. By disabling the display, power usage may be reduced while still monitoring for return of the transducer to the patient. All or most electronics not associated with monitoring for the return of the transducer to the patient may be disabled or not used to conserve power.

Abstract: In spectral Doppler imaging, a high PRF is used independent of the velocity scale. The adjustment is then of the velocity scale. By optimizing the velocity scale independent of the high PRF in an on-going or automated basis, user activation may be avoided and/or interruption to reconfigure for an altered PRF may be avoided. The acquired data may be stored, allowing for past data to be processed again when a new velocity scale or other setting is selected. The resulting spectral Doppler image may continue to display spectra over time without a gap or without premature loss of spectra due to reconfiguring.

Abstract: For mixed mode imaging, the ultrasound scanner distinguishes between times when different modes of imaging are appropriate based on motion or transducer usage. Any switching between modes, such as between B-mode and mixed mode imaging, occurs automatically based on the detection by the ultrasound scanner of motion, alleviating the need for sonographer manual selection.

Abstract: To accurately generate the three-dimensional ultrasound data and/or determine the position of the ultrasound scan relative to pre-operative data, a tracking sensor is releasably connected with the ultrasound probe. The connection positions the tracking sensor near a distal end of the probe for insertion into the patient. A needle guide may be similarly releasably connected with the probe and, at least in part, inserted into the patient.

Abstract: Twinkle artifacts are suppressed in color flow. The color flow data itself, such as temporal decorrelation and spatial variance of the velocity and/or power, is used to identify the twinkle artifact. The aliased or high velocities caused by the twinkle artifact are suppressed, such as by reducing the velocity or by spatial filtering that adapts to the locations of the artifact. The powers caused by the twinkle artifact are suppressed.

Abstract: For Doppler imaging in ultrasound, a single parameter is formed from both power and velocity. In any combination function, a derivative of velocity and/or velocity are combined with power. The resulting value is used to look-up a color from a one-dimensional color map.

Abstract: Flash suppression is provided in motion imaging. Separate regions of motion in a same frame or image are tested for flash independently. The size, shape, spatial variance, and/or location of a given region are used to categorize a level or likelihood of flash artifact for that region. Based on the level or likelihood, the motion information is altered to reduce flash.

Abstract: Twinkle artifacts are suppressed in color flow. The color flow data itself, such as temporal decorrelation and spatial variance of the velocity and/or power, is used to identify the twinkle artifact. The aliased or high velocities caused by the twinkle artifact are suppressed, such as by reducing the velocity or by spatial filtering that adapts to the locations of the artifact. The powers caused by the twinkle artifact are suppressed.

Abstract: Responsive power saving is provided for ultrasound imaging, such as in portable ultrasound systems. By reducing scan line density in response to removal of a transducer from a patient, power usage may be reduced while still monitoring for return of the transducer to the patient. By disabling the display, power usage may be reduced while still monitoring for return of the transducer to the patient. All or most electronics not associated with monitoring for the return of the transducer to the patient may be disabled or not used to conserve power.

Abstract: Gap filling is provided in spectral Doppler ultrasound. Due to the cyclical nature of the cardiac system, data likely to be similar to data that would have been acquired without interleaving is copied into the gap generated by interleaving. Acquired data associated with the gap, such as adjacent to the gap, is correlated with other acquired data. By identifying similar data, acquired data temporally related to the similar data as the gap associated data is temporally related to the gap is found. This found data is likely to be similar to data that would have been acquired during the gap. The gap is filled with a copy of this data.

Abstract: Gap filling is provided in spectral Doppler ultrasound. Due to the cyclical nature of the cardiac system, data likely to be similar to data that would have been acquired without interleaving is copied into the gap generated by interleaving. Acquired data associated with the gap, such as adjacent to the gap, is correlated with other acquired data. By identifying similar data, acquired data temporally related to the similar data as the gap associated data is temporally related to the gap is found. This found data is likely to be similar to data that would have been acquired during the gap. The gap is filled with a copy of this data.

Abstract: Sidelobe and clutter suppression techniques in ultrasound imaging are described and referred to as Dual Apodization with Cross-correlation or “DAX”. DAX dramatically improves the contrast-to-noise ratio (CNR) allowing for easier visualization of anechoic cysts and blood vessels. These techniques use dual apodization or weighting strategies that are effective in removing or minimizing clutter and efficient in terms of computational load and hardware/software needs. This dual apodization allows for determination of the amount of mainlobe versus clutter contribution in a signal by cross-correlating RF data acquired from two apodization functions.

Abstract: Dual-layer acoustic transducer array designs, related fabrication methods, and ultrasound imaging techniques are described. The designs include two perpendicular 1-D arrays for clinical 3-D acoustic imaging of targets near the transducer. These targets can include the breast, carotid artery, prostate, and musculoskeletal system among others. The transducer designs reduce the fabrication complexity and the channel count making 3-D rectilinear imaging more realizable. With such designs, an effective N×N 2-D array can be developed using only N transmitters and N receivers. This benefit becomes very significant when N becomes greater than 128, for example. Embodiments/aspects of the present disclosure are directed to fabricating and interconnecting 2-D arrays with a large number of elements (>5,000) for 3-D rectilinear imaging.