Harmonic B-mode imaging takes advantage of the non-linear oscillation of microbubbles. During harmonic imaging, the sound signal is transmitted at a frequency of around 1.5 to 2.0 MHz and received at twice this frequency. The microbubbles also reflect waves with wavelengths different from the transmitted one, the detectors can be set to receive only the latter ones and create only images of the contrast agent.
Using bandpass filters the transmitted frequency is separated from the received signal to get improved visualization of vessels containing ultrasound contrast agents (USCAs). The signal to noise ratio during the presence of microbubbles in tissue is four- to fivefold higher at the harmonic compared with the basic frequency.
Using harmonic B-mode imaging, harmonic frequencies produced by the ultrasound propagation through tissue have to be taken into account. The tissue reflection produces only a small amount harmonic energy compared to USCAs, but has to be removed by background subtraction for quantitative evaluation of myocardial perfusion.

See also Non-linear Propagation.

M-mode (Motion-mode) ultrasound shows the motion of cardiac structures. M-mode echocardiography records the amplitude and rate of motion of a moving structure in real time by repeatedly measuring the distance of the object from the single transducer at a given moment. The single sound beam is transmitted and reflected signals are displayed as dots of varying intensities, creating lines across the screen. It yields a one-dimensional image, sometimes called an 'ice pick' view of the heart.
M-mode echocardiography is used to detect valvulopathies (calcifications, etc.) and cardiomyopathies (dyskinesis, aneurysm, etc.).

See also Bicycle Stress Echocardiography, Transthoracic Echocardiography, and Transesophageal Echocardiography.

Ultrasound imaging is excellent for diagnosing cysts and other fluids in soft tissue. For ultrasound imaging or ultrasonography, different modes are used to examine the arterial/venous system, heart, pancreas, urinary system, ovaries, spinal cord, joints and more.
Power levels, frequencies used, amplification, and beamforming determine the clarity of the image. These things are controlled by the sonographer, interacting with the properties of the ultrasound machine.

Various imaging modes:

(BAT) B-mode acquisition and targeting is a stereotactic tumor locating device system, based on ultrasound and designed to maximize the precision of external beam radiation.
By tracking the position and orientation of the ultrasound transceiver within the treatment vault, BAT ultrasound produces images that can be fused with the CT scans used in the treatment plan.
When this is done directly before treatment, the current location of the target volume can be determined in reference to the treatment plan so that the volume is placed precisely and accurately. The patient's position can then be adjusted accordingly.

Bubble specific imaging methods rely usually on non-linear imaging modes. These contrast imaging techniques are designed to suppress the echo from tissue in relation to that from a microbubble contrast agent.
Stimulated acoustic emission (SAE) and phase / pulse inversion imaging mode (PIM) are bubble specific modes, which can image the tissue specific phase.
In SAE mode bubble rupture is seen as a transient bright signal in B-mode and as a characteristic mosaic-like effect in velocity 2D color Doppler.
PIM are Doppler modes and detect non-linear echoes from microbubbles. In pulse inversion imaging modes the transducer bandwidth extends, resulting in improved spatial resolution and more contrast.

See also Contrast Pulse Sequencing, Microbubble Scanner Modification, Narrow Bandwidth, Contrast Medium, Dead Zone.