ReviewNon-invasive neuroimaging using near-infrared light
Introduction
Several non- or minimally-invasive neuromonitoring techniques for examining functional brain activity are currently available to the psychiatric researcher and clinician. Historically, electroencephalography (EEG) was the first to appear on the scene, followed by other technologies including positron emission tomography (PET) and single-positron emission computed tomography (SPECT), magnetoencephalography (MEG), and most recently functional magnetic resonance imaging (fMRI). These methods are often categorized in terms of whether they provide direct or indirect information about brain function. Direct methods include MEG, EEG, and event-triggered EEG (also called event related potentials; ERPs), each of which monitors a direct consequence of brain electromagnetic activity. In particular, EEG and ERP record the electrical fields generated by neuronal activity, while MEG records the magnetic fields induced by such activity. PET, SPECT and fMRI, on the other hand, are indirect methods in that they generally monitor hemodynamic changes consequent to brain electrical activity. PET and SPECT brain imaging operate by monitoring the decay of blood-borne radioactive isotopes as they pass through the brain. FMRI, in contrast, detects changes in the local concentration of deoxyhemoglobin via its effect on imposed magnetic fields. While each of these techniques has its own distinct advantages, at present the direct methods tend to have limited spatial resolution, whereas the indirect methods can only detect neuronal activity after it has been filtered by a complex and poorly-understood neurovascular coupling function.
A lesser-known technology for monitoring brain function capitalizes on the absorption and scattering properties of near-infrared light to provide information about brain activity. It was long thought that the scattering of light by tissue made it impossible to recover information from anything but the most superficial layers of tissue (e.g., microscopy). Indeed, most long-standing optical techniques in use in the neurosciences are for superficial tissues only (Villringer and Chance 1997). Some 25 years ago, however, it was discovered that useful information could be obtained from thick tissue samples, including brain monitoring using light applied to and detected from the scalp (Jobsis 1977). This finding spurred the development of diffuse optics as a technique for human brain monitoring. The technique goes variously by the names of near-infrared spectroscopy (NIRS), diffuse optical tomography (or topography; DOT) and/or near-infrared imaging (NIRI). All of the techniques are based on essentially the same concept—shine light onto the scalp, detect it as it exits the head, and use the absorption spectra of the light absorbing molecules (chromophores) present in tissue to interpret the detected light levels as changes in chromophore concentrations.
To compare the spatial and temporal sensitivity of these various brain imaging techniques, we present Figure 1, modeled after a similar figure by (Churchland and Sejnowski 1988). It is clear that MEG and ERPs are strong in temporal sensitivity but relatively weak in terms of spatial sensitivity. In contrast, fMRI, PET and SPECT are stronger in spatial sensitivity but weak in terms of temporal resolution. Diffuse optical techniques, in comparison, can provide excellent temporal sensitivity as well as reasonable spatial sensitivity. When multiple colors of light are used, moreover, spectroscopic information about the sampled tissue also becomes available, thereby affording the promise of quantifying the concentrations of the various hemoglobin species-oxyhemoglobin, deoxyhemoglobin, and the sum of these (total hemoglobin, which is proportional to blood volume).
In addition to hemoglobin-based measures of brain activity, diffuse optical techniques also make non-hemoglobin-based measures feasible. For example, by recording data from several wavelengths simultaneously, one can measure other tissue chromophores, including cytochrome oxidase. As a marker of metabolic demands, cytochrome oxidase measurements can provide more direct information about neuronal activity than hemoglobin changes Heekeren et al 1999, Jobsis et al 1977. There is also evidence to suggest that diffuse optical methods can detect cell swelling that occurs in the 50–200 milliseconds following neuronal firing, which would be an even more direct measure of neuronal activity than the hemodynamic or metabolic markers Gratton and Fabiani 2001, Steinbrink et al 2000, Stepnoski et al 1991. This type of “fast” signal appears to be significantly smaller than the hemodynamic signals (on the order of a .01% signal change). With sufficiently fast and sensitive electronics, however, such signals could be feasibly recorded by the same equipment as the hemodynamic signals. (The spatial correspondences between these various signals remain to be investigated.) Thus, diffuse optical techniques may be simultaneously capable of providing both indirect and more direct methods of neuronal activity monitoring-complementary sources of information about brain function.
The primary advantages of the optical approach, however, lie in areas not explicitly represented by Figure 1. In particular, the instrumentation—which is completely non-invasive—can be made portable, unobtrusive, low-cost, low-power, and can even be made robust to motion artifacts (e.g., Totaro et al 1998). For the psychiatric researcher, these additional strengths can bring otherwise previously unthinkable projects into the realm of possibility. For example, with proper fiber coupling, extensive movement can be tolerated, opening up the possibility of studying infants, small children, patients with severe movement disorders, or other highly animated subjects, without sedation. The portability and near-zero run-time cost of the instrument affords bedside (or home) monitoring for extended periods, which could be useful for monitoring the effects of slowly acting drugs, or slowly evolving pathologies. And, the fact that near infrared light is non-ionizing means that there is no limit to the number of scans one can undergo.
Diffuse optical recordings depend on two critical characteristics of the electromagnetic spectrum as it interacts with biological tissue. First, while biological tissue is relatively opaque to visible light, it is not totally opaque, as demonstrated by a simple experiment. Darken a room, shine a flashlight through your hand and notice that the white light from the flashlight exits with a red hue, indicating that the tissue least absorbs the redder wavelengths. Near-infrared (NIR) light—from approximately 650–950 nm—is even more weakly absorbed by tissue than the red wavelengths (Figure 2). As a result, this range of wavelengths is often called an “optical window” into biological tissue. This property allows light of these wavelengths to penetrate several centimeters through tissue and still be detected.
The second critical characteristic of NIR light as it interacts with biological tissue is also apparent in Figure 2. The two dominant chromophores for the NIR wavelength range just happen to be two biologically relevant markers for brain activity: oxyhemoglobin (HbO2) and deoxyhemoglobin (HbR). Thus, NIR wavelengths pass relatively easily through tissue, and their absorption can provide information relevant to brain function.
Having described what makes the technique possible, we next discuss the methodology details, including the types of measurements one can make, the nature of diffuse optical monitoring equipment, and the basic underlying theory necessary for data interpretation. We will then review brain research applications of diffuse optical techniques—with an emphasis on psychiatric patient groups—and will finally discuss the practical issues presently faced by optical researchers.
Section snippets
Types of diffuse optical measurements
The amplitude of the recorded signal in a diffuse optical measurement is determined by two factors: (i) absorption of light by the tissue, and (ii) light scattering within the tissue. An increase in either factor results in a decrease in detected light levels, and a corresponding decrease in signal. The goal of diffuse optical measurements is to detect such changes and, in some cases, determine whether the change was due to a change in absorption or scattering by the tissue under investigation.
Modified Beer-Lambert Law (MBLL)
To quantify changes in concentrations of absorbing species, a model of light diffusing through tissue is required. A traditional approximation to the full photon migration theory is called the modified Beer-Lambert Law (MBLL), which is an empirical description of optical attenuation in a highly scattering medium (Cope et al 1987). A change in the concentration of an absorbing species causes the detected light intensity to change and, according to the MBLL, the concentration change is
Physiology
An example time series from a CW NIRS instrument appears in Figure 5, obtained from probe located over position C3 in the International 10/20 system (approximately over left primary motor cortex) on a subject sitting upright, quietly resting with eyes open. The high-frequency oscillations correspond to the cardiac cycle, whereas the low frequency oscillations likely correspond to Mayer wave oscillations (Obrig et al 2000). Simple measures such as these can provide useful physiological
Current issues
The advantages that diffuse optical techniques can provide brain researchers are substantial. These include portability, unobtrusiveness and low cost. As with any technique, however, these advantages come with some limitations, and so we consider here the issues that need to be considered when designing diffuse optics experiments.
Summary and conclusions
Diffuse optical methods have several advantages over existing technologies for brain monitoring, including excellent temporal resolution coupled to reasonable spatial resolution, spectroscopic information for hemodynamic events, portability, unobtrusiveness, and the ability to be achieved by low-power and low-cost instruments that are robust to motion artifacts. The technology is also completely non-invasive, unlike PET and SPECT. For the psychiatric researcher, these strengths facilitate the
Acknowledgements
GS and JPS acknowledge support from the National Space Biomedical Research Institute through NASA Cooperative Agreement NCC 9-58 and the McDonnell-Pew Foundation (97-33). GS was also supported by the NIH-NINDS (F32-NS10567-01). DAB acknowledges financial support from NIH R29-NS38842, NIH P41-RR14075 and from the Center for Innovative Minimally Invasive Therapies.
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