Abstract
Near-infrared spectroscopy (NIRS) is widely used to measure cerebral oxygenation and hemodynamics caused by brain activation. Blood volume and oxygenation are indicated by the absorption of tissue caused by oxygenated and deoxygenated hemoglobin/myoglobin. NIRS instruments can monitor temporal changes in blood volume and oxygenation in a single probing region. The desire to measure the spatial distribution of tissue absorption, which indicates the region of focal brain activation, has fostered development of NIRS imaging to localize the absorption change in the brain. There are two basic categories of NIRS imaging: tomography and topography. NIRS tomography provides the cross-sectional images of brain activation, whereas the two-dimensional distribution of brain activation in the cortex is obtained by NIRS topography.
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Acknowledgments
I would like to acknowledge funding support from the Japan Society for the Promotion of Science, Grant-in-Aid for Scientific Research (B) (19360035), and invaluable scientific discussions with Drs. Hiroshi Kawaguchi and Tsuyoshi Yamamoto.
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Appendices
Problems
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3.1.
Assume that the concentration of hemoglobin is changed from 0.1 to 0.11 mM and the oxygen saturation of the blood is changed from 65% to 70% in the activated region of the brain. The extinction coefficients of oxygenated hemoglobin and deoxygenated hemoglobin at 780-nm wavelength are 0.16 and 0.25 mM−1 mm−1, respectively. The partial optical pathlength in the activated region for a probe pair is 5 mm.
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(a)
Find the absorption change in the activated region.
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(b)
Find the change in optical density (NIRS signal) caused by absorption change in the activated region.
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(a)
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3.2.
Derive the equations that calculate the concentration change in oxygenated and deoxygenated hemoglobins from change in optical density (NIRS signal) at two wavelengths, λ 1 and λ 2. The extinction coefficient of oxygenated hemoglobin and deoxygenated hemoglobin is εoxy−Hb and εdeoxy−Hb, respectively. Assume that the wavelength dependence of the partial optical pathlength in the activated region <L act> can be ignored.
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3.3.
Draw polar plots of the probability distribution of deflection angle p(θ) described by the Henyey-Greenstein phase function for g = 0.1, g = 0.5, and g = 0.9.
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3.4.
A pencil beam of short pulse is incident onto tissues, and diffusely reflected light is detected at 20 mm from the incident point. Analyze light propagation in the tissues by analytical solution of the diffusion equation described in [25]. The optical properties of the tissues: (1) μ s  = 10 mm−1, g = 0.9, μ a  = 0.01 mm−1. (2) μ s  = 10 mm−1, g = 0.85, μ a  = 0.01 mm−1. (3) μ s  = 5 mm−1, g = 0.8, μ a  = 0.02 mm−1. Although the diffusion coefficient is defined as \( \kappa =1/3\{({{\mu^{\prime}}_s}+{\mu_a})\} \) in [25], \( \kappa =1/(3{{\mu^{\prime}}_s}) \) can be used for the calculations. The speed of light in the medium is 0.2 mm/ps, and refractive index mismatch at the tissue boundary can be ignored.
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(a)
Determine the transport scattering coefficient of each tissue.
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(b)
Determine the depth of the isotropic point source created by the incident beam.
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(c)
Draw the temporal distribution of reflectance.
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(a)
Further Reading
Frostig RD (ed) (2002) In vivo optical imaging of brain function. CRC Press, New York/Washington, DC
Potter RF (ed) (1993) Medical optical tomography: functional imaging and monitoring. SPIE Press, Washington, DC
Tuchin V (2000) Tissue optics. SPIE Press, Washington, DC
Wang LV, Wu H (2007) Biomedical optics. Wiley, New York
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Okada, E. (2013). Photon Migration in NIRS Brain Imaging. In: Jue, T., Masuda, K. (eds) Application of Near Infrared Spectroscopy in Biomedicine. Handbook of Modern Biophysics, vol 4. Springer, Boston, MA. https://doi.org/10.1007/978-1-4614-6252-1_3
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