Optoacoustic and Ultrasound Imaging

Acoustic waves are mechanical waves which propagate through a medium via pressure variations. In the biomedical context, Ultrasonography (US) is broadly utilised as it offers images in real time at zero radiation dose and safe use, while being at low cost and high portability. In conventional US imaging, ultrasound waves are sent to a sample, and the intensity of echoes encodes the tissue’s microstructure. This single-parameter tissue characterization restricts the diagnostic value of US to limited scenarios.

We are advancing innovative US-based imaging modes, to combine the availability and flexibility of US with the diagnostic power of multi-modal imaging.

  • Beyond echo intensity, the US data encodes the tissue’s speed-of-sound (SoS). Knowledge of the SoS gives information on the tissue composition and thus allows for the diagnosis of diseases affecting the tissue composition such as fatty liver disease, cancer, fat deposits in muscle tissue, among others. We have invented and continue developing Computed Ultrasound-Tomography in Echo-Mode (CUTE), which maps the SoS using conventional US equipment. Together with our collaborators at the Inselspital (Prof. Dr. med. Annalisa Berzigotti), we have already demonstrated the power of CUTE for fatty liver diagnosis.
  • In opto- or photo-acoustic imaging (OA), short laser pulses—as opposed to sound—are sent into the tissue where they generate US signals upon optical absorption. While purely optical methods are limited by the strong scattering of optical waves, US waves propagate mostly undisturbed and their detection allows to create high-resolution maps of the tissue’s optical contrast, with promise in, e.g., the diagnosis and monitoring of vascular diseases, arthritis, and cancer. We focus on the combination of OA with classical US-systems, where we are leading in the development of techniques that enable a clinically useful imaging depth.

Ultimately, we aim at developing a single device which will unify the virtues of real-time operability and patient safety with the diagnostic accuracy of multi-modal imaging. 

Spectral OA imaging exploits the difference in the absorption spectra of oxy- and deoxyhemoglobin for estimating the oxygen saturation inside small blood vessels, a diagnostic marker in tumors, ischemia, and would healing.

A central issue for achieving quantitative results is the spectral coloring of the irradiating laser light by background tissue. In our research on quantitative deep OA imaging, we therefore investigate techniques to correct for the spectral distortion of the recorded OA signals.  

Our team focuses on the combination of OA with classical US systems, where the irradiation optics is integrated with the ultrasound detector in a handheld probe. A drawback of this epi-illumination is the reverberation of OA signals inside the acoustically scattering tissue. We develop techniques that reduce this noise and thereby increase the achievable imaging depth, among them localized vibration tagging (LOVIT).

Left: conventional echo ultrasound provides gray-scale images of echo intensity representing tissue microstructure. Right: a map of the spatial distribution of speed of sound (SoS) reveals differences in tissue composition, here skin (s), subcutaneous fat (sf), muscle (m) muscle, extraperitoneal fat (pf), and liver (l).

The speed of sound (SoS) inside tissue depends on tissue composition and is a diagnostic marker for disease that affects tissue composition. Conventional pulse-echo ultrasound reconstructs the location of acoustic reflectors inside the tissue based on the round-trip propagation time of the echoes. Computed Ultrasound Tomography in Echo mode (CUTE) goes beyond that: it senses the phase shift of local echoes when detected under varying insonification and detection angles. This echo phase shift is related to the changing round-trip time representing line integrals of SoS, and thus the spatial distribution of SoS.