Sonography Principles and Instrumentation Free Sample Questions

Spectral broadening is the filling of the spectral window, indicating a wide range of velocities. A large sample volume, high gain, and turbulent flow (stenosis) are all common causes. However, a 90-degree angle of insonation would result in no detectable Doppler shift, producing a flat line or no signal at all, not spectral broadening. Therefore, it is the least likely cause.

Acoustic shadowing occurs when a sound beam encounters a highly attenuating or reflecting structure (like a calcification or gallstone). The structure blocks the sound from passing through, creating a signal void or 'shadow' deep to it. Enhancement is the opposite, where a weakly attenuating structure causes increased brightness behind it. Reverberation involves multiple echoes between strong reflectors.

Acoustic impedance (Z) is an intrinsic property of a medium and is defined as the product of the medium's density (ρ) and its propagation speed (c). The formula is Z = ρc. The greater the difference in acoustic impedance between two media, the stronger the reflection at their boundary.

Wide bandwidth transducers have a low quality factor (Q factor), meaning they produce a wide range of frequencies around the center frequency. This is achieved using a backing material that dampens the crystal's ringing, resulting in a short pulse duration and a short spatial pulse length (SPL). A short SPL is essential for good axial resolution.

Increasing gain amplifies the returning echoes without increasing the transmitted energy, thus having no impact on patient exposure. This should always be done before increasing output power.

Total exposure is a function of intensity and time. Minimizing the duration of the exam, especially dwelling in one spot, directly reduces the patient's overall exposure to ultrasound energy.

The scenario describes color flash or clutter, which is most often caused by the color gain being set too high. The system becomes overly sensitive and amplifies electronic noise or subtle tissue motion, displaying it as color. The first and most effective step is to reduce the color gain until the random noise disappears, leaving only the signal from true blood flow.

Tissue harmonic imaging relies on harmonic frequencies generated within the tissue, not transmitted by the probe. These harmonic signals are strongest in the main beam and weaker in the weaker parts like side lobes and grating lobes. Furthermore, since harmonics are generated deeper in the tissue, superficial reverberation artifacts are significantly reduced. This results in a cleaner image with improved contrast resolution and reduced clutter.

The decibel scale is logarithmic. A change of -10 dB corresponds to a tenfold decrease in intensity. Conversely, +10 dB is a tenfold increase. A change of -3 dB corresponds to halving the intensity, and +3 dB corresponds to doubling it. Since the intensity is reduced to 1/10th, the change is -10 dB.

This statement is true. The purpose of the matching layer is to reduce the large acoustic impedance mismatch between the high impedance of the PZT crystal and the low impedance of soft tissue (skin). By having an intermediate impedance, the matching layer facilitates more efficient energy transfer from the transducer into the body, improving sensitivity and image quality.

The dead zone is the region close to the transducer face where imaging is not possible. It is caused by the time it takes for the system to switch from transmit to receive mode and by reverberation within the transducer itself. Measuring the dead zone on a phantom assesses the system's ability to resolve structures in the extreme near field. A larger dead zone can be caused by a cracked crystal or a detached backing material.