Abstract: Delivering a search result is disclosed. A category is associated with a document based at least in part on one or more scores that measure the relevance of that document to a base category. A search query is obtained. One or more results is delivered in a manner that includes an indication of at least one category with which the result is associated.

Abstract: Adaptive volume rendering is provided for medical diagnostic ultrasound. The opacity of B-mode data is set relative to the opacity of Doppler data. The opacities for the different types of data are set as a function of ray depth. For example, the opacity of B-mode data near a tissue border is set to be more opaque than for tissue away from the border, and the opacity for flow data near a flow border is set to be less opaque than for flow away from the border. An image is rendered using a rendering parameter set as a function of ray depth, B-mode information and Doppler information. Other processes for enhancing and/or using rendering may be used.

Abstract: A volumetric method for 2-D flow imaging is provided in medical diagnostic ultrasound. Flow data for a volume is acquired. For more rapid acquisition, broad beam transmission and reception along many scan lines distributed in the volume is used. The volumetric flow data is filtered, such as by calculating statistical information, to generate a planar/2-D flow image. The statistical information from the three-dimensional flow data is used to determine the display values for the flow imaging.

Abstract: Motion imaging in medical diagnostic ultrasound is adaptive. Clutter or threshold processing adapts as a function of data for different locations or for different times. Spatial filtering adapts as a function of data at different spatial locations at a same time. The steering angle may be set as a function of region based on the vessel orientation and maximum velocity. The region of interest for motion imaging may be expanded to counteract, at least in part, a shift due to the steering angle.

Abstract: Orientation is automatically identified in medical diagnostic ultrasound image. An area or volume based process, such as region shrinking or using locations associated with flow or tissue structure, determines a direction or orientation. Real-time imaging in B-mode and/or flow mode may be enhanced based on the direction or orientation.

Abstract: Flow estimation is provided. The flow is predicted. A mathematical, logic, machine learning or other model is used to predict flow. For example, the boundary conditions associated with a previous flow, the previous flow, and current boundary conditions are used to predict the current flow. The current flow is corrected using the predicted flow. Velocities may be unaliased based on the predicted flow. The predicted flow may replace the current flow. Prediction may additionally or alternatively be used in determination of lateral or elevational flow.

Abstract: Volumetric quantification is provided in medical diagnostic ultrasound. By acquiring both B-mode and color flow data without stitching or acquiring in real-time at tens of volumes a second, more reliable quantification may be provided. Using multiple regions of interest in a volume may allow for more accurate and/or complete flow information, such as averaging flow from different locations in the same structure (e.g., use preservation of mass to acquire multiple measures of the same flow).

Abstract: A method is provided to improve the frame-rate in color-flow ultrasound imaging using simultaneous spatially-distinct transmit beams with one or more frequency bands per transmit beam. Pulses of different center frequencies are used simultaneously in different (lateral and/or elevational) directions, thereby reducing the scanning time and improving the frame-rates. Optionally, a multi-modal pulse is used, and flow is estimated separately for the different frequencies. The flow estimates for these pulses are appropriately combined to improve low-velocity sensitivity and to reduce aliasing. A flow sample count with two or more different pulse repetition intervals can be used to further improve low-flow sensitivity and minimize aliasing.

Abstract: Velocity scale is automatically determined for ultrasound imaging. Receive signals corresponding to different pulse repetition intervals are used to estimate velocities. The different velocities are used to determine the velocity scale. For example, the different pulse repetition intervals are obtained by selecting different sets of signals from a group of signals for a scan line. As another example, the different pulse repetition intervals are obtained by transmitting for a scan line with changing, such as increasing, pulse repetition intervals. The lower pulse repetition interval of a pair of intervals associated with a sign change in the phase is used for the velocity scale. In yet another example, at least two demodulation frequencies are used for a broadband transmit in at least two sets, each set with a different pulse repetition interval. Velocities are estimated for a greater number of pulse repetition intervals than transmitted using the broadband pulses.

Abstract: Diagnostic ultrasound flow imaging is performed with coded excitation pulses. Due to the use of frequency coded excitation pulses, flow information may suffer from spatial misregistration and estimate errors. Spatial position shift in flow data is offset for alignment with B-mode or other imaging. The flow estimates are compensated for the imaging center frequency variation with depth. The wide bandwidth information available due to coded excitation may allow anti-aliasing by estimating velocities from two frequency bands.

Abstract: Spatially distinct Spectral Doppler information is displayed. A spectrum is determined for each of a plurality of spatial locations, such as associated with different receive beams. Given a plurality of spectra at different spatial locations, an image may be generated as a function of the spectra. For example, a two-dimensional image has display values for different pixels or locations derived from one or more characteristics of the spectra, such as the maximum velocity with energy above a threshold for each location. As another example, the spectrum from the set of spectra with the highest maximum velocity is selected for generating a spectral strip display.

Abstract: Adaptive volume rendering is provided for medical diagnostic ultrasound. The opacity of B-mode data is set relative to the opacity of Doppler data. The opacities for the different types of data are set as a function of ray depth. For example, the opacity of B-mode data near a tissue border is set to be more opaque than for tissue away from the border, and the opacity for flow data near a flow border is set to be less opaque than for flow away from the border. An image is rendered using a rendering parameter set as a function of ray depth, B-mode information and Doppler information. Other processes for enhancing and/or using rendering may be used.

Abstract: A volumetric method for 2-D flow imaging is provided in medical diagnostic ultrasound. Flow data for a volume is acquired. For more rapid acquisition, broad beam transmission and reception along many scan lines distributed in the volume is used. The volumetric flow data is filtered, such as by calculating statistical information, to generate a planar/2-D flow image. The statistical information from the three-dimensional flow data is used to determine the display values for the flow imaging.

Abstract: Orientation is automatically identified in medical diagnostic ultrasound image. An area or volume based process, such as region shrinking or using locations associated with flow or tissue structure, determines a direction or orientation. Real-time imaging in B-mode and/or flow mode may be enhanced based on the direction or orientation.

Abstract: Motion imaging in medical diagnostic ultrasound is adaptive. Clutter or threshold processing adapts as a function of data for different locations or for different times. Spatial filtering adapts as a function of data at different spatial locations at a same time. The steering angle may be set as a function of region based on the vessel orientation and maximum velocity. The region of interest for motion imaging may be expanded to counteract, at least in part, a shift due to the steering angle.

Abstract: Orientation is automatically identified in medical diagnostic ultrasound image. An area or volume based process, such as region shrinking or using locations associated with flow or tissue structure, determines a direction or orientation. Real-time imaging in B-mode and/or flow mode may be enhanced based on the direction or orientation.

Abstract: A method is provided to improve the frame-rate in color-flow ultrasound imaging using simultaneous spatially-distinct transmit beams with one or more frequency bands per transmit beam. Pulses of different center frequencies are used simultaneously in different (lateral and/or elevational) directions, thereby reducing the scanning time and improving the frame-rates. Optionally, a multi-modal pulse is used, and flow is estimated separately for the different frequencies. The flow estimates for these pulses are appropriately combined to improve low-velocity sensitivity and to reduce aliasing. A flow sample count with two or more different pulse repetition intervals can be used to further improve low-flow sensitivity and minimize aliasing.

Abstract: Diagnostic ultrasound flow imaging is performed with coded excitation pulses. Due to the use of frequency coded excitation pulses, flow information may suffer from spatial misregistration and estimate errors. Spatial position shift in flow data is offset for alignment with B-mode or other imaging. The flow estimates are compensated for the imaging center frequency variation with depth. The wide bandwidth information available due to coded excitation may allow anti-aliasing by estimating velocities from two frequency bands.

Abstract: Velocity scale is automatically determined for ultrasound imaging. Receive signals corresponding to different pulse repetition intervals are used to estimate velocities. The different velocities are used to determine the velocity scale. For example, the different pulse repetition intervals are obtained by selecting different sets of signals from a group of signals for a scan line. As another example, the different pulse repetition intervals are obtained by transmitting for a scan line with changing, such as increasing, pulse repetition intervals. The lower pulse repetition interval of a pair of intervals associated with a sign change in the phase is used for the velocity scale. In yet another example, at least two demodulation frequencies are used for a broadband transmit in at least two sets, each set with a different pulse repetition interval. Velocities are estimated for a greater number of pulse repetition intervals than transmitted using the broadband pulses.

Abstract: A screen comprises an electrically conductive elongate inner screen plate. The inner screen plate has at least one elongate fold therein and at least two elongate divergent surfaces on opposing sides of the fold. Each divergent surface has an upper end and opposing edges tapering downward from the upper end. The upper ends of the divergent surfaces diverge from one another. Each of the divergent surfaces has a plurality of holes therein. The screen further comprises at least two electrically conductive outer screen plates. The outer screen plates are attached to the edges of the divergent surfaces and extend between the divergent surfaces. Each of the outer screen plates has a plurality of holes therein. Another embodiment of the invention is directed toward a glass fiber bushing system comprising a bushing body and a screen within the bushing body. The bushing body has opposing end plates. The screen comprises opposing ends. Each of the ends has an upper portion and a lower portion.