Abstract
In both photoacoustic (PA) and ultrasonic (US) imaging, overall image quality is influenced by the optical and acoustical properties of the medium. Consequently, with the increased use of combined PA and US (PAUS) imaging in preclinical and clinical applications, the ability to provide phantoms that are capable of mimicking desired properties of soft tissues is critical. To this end, gelatin-based phantoms were constructed with various additives to provide realistic acoustic and optical properties. Forty-micron, spherical silica particles were used to induce acoustic scattering, Intralipid® 20% IV fat emulsion was employed to enhance optical scattering and ultrasonic attenuation, while India Ink, Direct Red 81, and Evans blue dyes were utilized to achieve optical absorption typical of soft tissues. The following parameters were then measured in each phantom formulation: speed of sound, acoustic attenuation (from 6 to 22 MHz), acoustic backscatter coefficient (from 6 to 22 MHz), optical absorption (from 400 nm to 1300 nm), and optical scattering (from 400 nm to 1300 nm). Results from these measurements were then compared to similar measurements, which are offered by the literature, for various soft tissue types. Based on these comparisons, it was shown that a reasonably accurate tissue-mimicking phantom could be constructed using a gelatin base with the aforementioned additives. Thus, it is possible to construct a phantom that mimics specific tissue acoustical and/or optical properties for the purpose of PAUS imaging studies.
Highlights
We have demonstrated that an accurate tissue-mimicking phantom for PA and US (PAUS) imaging can be constructed for most soft tissues
The US backscatter coefficient can be tailored for a specific tissue by adjusting the silica microparticle and/or Intralipid® solution concentration
Silica microparticles produce some optical scattering, Intralipid® solution produces scattering values that are more common to tissue
Summary
Medical ultrasonic (US) imaging relies on the transmission of a high-frequency (MHz range) acoustic pulse into tissue through a transducer that is capable of both transmitting and receiving high-frequency sound [1]. As the transmitted pulse propagates through tissue, acoustic impedance mismatches in the propagation path cause the sound to be scattered. The backscattered portion of this energy, traveling in a direction opposite to the pulse propagation direction, can be received by the aforementioned transducer. The amplitude of the modulated signal of this received echo is related to specific tissue structure, while the signal’s temporal component denotes spatial position. US transducers can be comprised of a single element, made from material capable of electromechanical transduction, or of multiple elements, with the latter configuration allowing for electronic transmit and receive beamforming
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