When using the new maximum frequency estimator, it was found that the effect of transducer focal depth, intratransducer, intramachine, intermachine (that was tested) and beam-steering did not significantly contribute to maximum velocity estimation errors.
Because sonar systems measure distance from the closest point to the transducer, the detected depth is not always the true depth at the position of transducer.
Endoscopic ultrasonography with a 20-MHz transducer estimated the depth of tumor invasion as cT1b (SM1).
Data were acquired with a 3.5-MHz transducer at a depth of 16 cm in the parasternal and apical views (standard long- and short-axis, two- and four-chamber images).
Because the skin around the eye is relatively thin, a 7.0 MHz and 3.0 mm focal depth transducer was used in one report to deliver a single pass over the area to generate thermal coagulation points spaced approximately 3.0 5.0 mm apart 25 and assessed after 6 months.
Doppler machine settings (transducer aperture size, focal depth, beam-steering, gain) were varied to investigate a wide range of clinical applications.
A cutting system of the ultrasonic elliptical vibration driven by single longitudinal actuator was developed and the effect of the transducer amplitude and cutting depth on the cutting force was studied in detail.
Parasternal and apical imaging windows were imaged using a S5-1, 3.5-MHz tratsducer at a mean depth of 16 cm.
Ultrasonographic examinations were carried out on standing, non-sedated animals as described previously [ 15] using a 5.0 MHz linear and a 5.0 MHz convex transducer with a penetration depth of 10 cm.
Ultrasonographic examinations were carried out in standing, non-sedated animals as described previously [ 11] using a 5.0 MHz linear transducer with a penetration depth of 10 cm (EUB 8500, Hitachi Medical Systems, Zug, Switzerland).
