Abstract
In this contribution, different measurement noise pre-filtering techniques were developed using frequency-domain fluorescence measurements of homogeneous breast phantoms. We demonstrated that implementing noise pre-filtering, based on modulation depth and measurement error in amplitude, can improve model match between experimental and simulated data under varying experimental conditions (target depths, 1-3 cm and fluorescence optical contrast, 1:0 and 100:1). Noise pre-filtering also improves the qualitative estimation of target(s) location in reconstructed images in deep target(s) when there was fluorescence in the background. Interestingly, decreases in model mismatch did not necessarily correlate with increases in reconstructed target accuracy. In addition, it was observed that pre-filtering measurement noise using different criteria can help differentiate target(s) from artifacts, thus possibly minimizing the false-positive cases in a clinical environment.
Highlights
Optical imaging is based on the principle of using the minimally absorbed and preferentially scattered near-infrared (NIR) light in order to illuminate and detect optical signals deep into the tissue surface [1,2,3,4,5,6,7,8,9,10]
These artifacts can arise from one or more of the following: (i) experimental errors arising from estimated tissue background optical properties, and/or homogeneity of the background phantom; (ii) instrumentation errors arising from detectors, optical filters, or other electronics that contaminate the NIR signal; and (iii) computational errors arising from the approximation of the light propagation models used in reconstruction algorithms or the accuracy of the numerical techniques employed in solving the highly illposed optical tomography problem
2.1 Instrumentation A frequency-domain photon migration (FDPM) intensified CCD (ICCD) based optical imaging system was developed in order to perform fluorescence-enhanced optical imaging on large breast phantoms [14]
Summary
Optical imaging is based on the principle of using the minimally absorbed and preferentially scattered near-infrared (NIR) light (between the wavelengths of 700-900 nm) in order to illuminate and detect optical signals deep into the tissue surface [1,2,3,4,5,6,7,8,9,10]. Three-dimensional (3-D) fluorescence tomography studies have been successfully demonstrated by various research groups on small animal models [11,12,13] and recently on large tissue phantoms [14,15,16,17,18] In all these tomography studies, the 3-D reconstructed images of the tissue phantoms are typically contaminated with artifacts (noise in parameter estimates) apart from the reconstructed target(s). Μaxi,μami: Intrinsic absorption coefficient of 1% Liposyn solution at excitation and emission wavelengths, respectively. Μsx ',μsm ': Reduced scattering coefficient of 1% Liposyn solution at excitation and emission wavelengths, respectively.
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