Abstract: Transducer systems for mode dependent tuning and associated methods are provided. One or more tuning circuits are provided within a transducer probe. The tuning circuit is switchably connected to the transducer. By connecting or disconnecting the tuning circuit, the tuning for the transducer element is varied. Selective tuning of a medical ultrasound transducer allows different tuning for different modes of operation. For example, the frequency response of the transducer is varied between different modes of imaging, such as B-mode and flow-mode imaging. Higher frequency signals are used for higher resolution B-mode imaging, but a stronger response at lower frequency is desired for better penetration during flow-mode imaging and Doppler modes. Mode is used in a general sense, such as associated with an imaging mode as well as a type of operation (e.g. transmit mode versus receive mode operation).

Abstract: Ultrasound transducer temperatures are measured in response to a temperature dependent property of the ultrasound transducer. The temperature is measured without addition of new electronics or hardware retrofits of the transducer. By implementing software and/or hardware on the ultrasound system rather than the transducer, the temperature is measured in order to provide a level of fault protection. The upgraded or new ultrasound system uses either old or new transducers while still providing temperature measurement. For example, the temperature of the lens or window is measured as a function of changes in attenuation or acoustic velocity. The receive beamformer already implemented on many ultrasound systems is used to measure a temperature dependent property of the lens or window. As another example, the dielectric constant or capacitance of one or more transducer elements is measured using additional hardware in the ultrasound system.

Abstract: Methods and systems are provided for automatic optimization of spectral Doppler ultrasound imaging. One or more of the velocity scale (e.g., pulse repetition frequency), gain, baseline, dynamic range or other imaging parameters are optimized based on one or both of: (1) determining the optimum parameter based on data acquired at a standard or predetermined setting of the parameters and (2) identifying an artifact in the Doppler ultrasound data and discarding or minimizing the influence of the artifact on any determination of imaging parameter settings. One embodiment used for cardiac Doppler imaging identifies artifact signals using the maximum or minimum traces. For example, the velocity scale or pulse repetition frequency is set based on the maximum or minimum velocity value over one or more heartbeats identified from a maximum and minimum trace of the signal envelope or Doppler spectrum.

Abstract: An ultrasonic imaging system generates Doppler and B-mode image signals, and then uses a modulated, non-linear mapping function to combine the Doppler and B-mode image signals into an output signal. In another mode of operation the imaging system generates fundamental and harmonic frequency intensity values and maps these intensity values to display indicia, preferably with a modulated, non-linear mapping function.

Abstract: An ultrasound imaging system generates a legend on a display device. This legend includes at least two axes and an array of display indicia, and the indicia are responsive to a mapping function used to generate a displayed ultrasonic image as a modulated, non-linear, multi-bit function of at least first and second image signals. At least one of the axes of the legend varies as a function of a B-mode value range. Preferably, one axis of the legend varies as a function of a fundamental image signal, and the other axis varies as a function of a harmonic image signal. The imaging system can be controlled such that a B-mode processor automatically alternates between a fundamental mode of operation and a harmonic mode of operation on a line-by-line, group-of-lines by group-of-lines, or frame-by-frame basis.

Abstract: Color Doppler data is acquired only over a portion of the cardiac cycle, such as during diastole in order to increase the sensitivity of detection. Ultrasound system parameters such as clutter filter coefficience, temporal and spatial filter coefficients and demodulation frequencies may be altered only for a portion of the cardiac cycle to increase detection sensitivity, to improve myocardial border estimation and to avoid the loss of color Doppler image at end-diastole.

Abstract: Color Doppler data is acquired only over a portion of the cardiac cycle, such as during diastole in order to increase the sensitivity of detection. Ultrasound system parameters such as clutter filter coefficience, temporal and spatial filter coefficients may be altered only for a portion of the cardiac cycle to increase detection sensitivity, to improve myocardial border estimation and to avoid the loss of color Doppler image at end-diastole.