Multi-wavelength photoplethysmography method for skin microcirculation assessment Lasma Gailite, PhD student Bio-optics and Fiber Optics Laboratory, Institute of Atomic Physics and Spectroscopy University of Latvia, Raina Blvd. 19, Riga, LV-1586, Latvia, E-mail: [email protected], tel/fax: +371 7228249 1. INTRODUCTION Reflection photoplethysmography (PPG) is a non-invasive method for studies of the skin blood volume pulsations by detection and analysis of the back-scattered optical radiation. The PPG method has gained wide clinical use due to the simple measurement procedure and the informative content of the PPG signal. Parameters, including heart rate, respiratory rate and tissue perfusion can be monitored via PPG, moreover: specific indicators of cardiac disorders as well as peripheral vascular diseases can be extracted from the single-period PPG pulse shape [1,2]. The specifics of reflection PPG is that a fixed penetration volume/depth is monitored which depends on the emitter wavelength: PPG pulsations from deeper skin layers contribute to the signal at longer wavelengths [3, 4]. Consequently, depth-selective PPG measurements are possible, e.g., studies of blood flow at different vascular beds described in literature [2,5]. Differences in PPG signal shapes have been reported [4] in case of subsequent application of various emitters/wavelength bands to the same skin spot. However, to authors knowledge, there are no data available on PPG signal shapes that would be detected on the same skin location at the same moment and using several emitter wavelengths. Parallel multi-wavelength detection of reflection PPG signals related to the same heartbeats with subsequent shape analysis may yield a sub-millimeter-scale depth characterization of skin microcirculation in selected skin layers. The goal of this study is the development of such a new technique, namely, the multi-wavelength photoplethysmography that enables recording of PPG signals from the same skin location simultaneously at any selected wavelength in the range of 400 to 1100 nm. 2. MATERIALS AND METHODS The concept of multi-wavelength PPG equipment (Fig. 1.) includes three basic components: (i) illumination by several laser emission lines within the range of 400 to 1100 nm, (ii) fiberoptic contact probe for measurements on skin and (iii) detection in the range of 400 up to 1100 nm via multi-channel spectrometer. The time-resolved diffuse reflectance spectra of skin were detected by a 2048-channel CCD array spectrometer AvaSpec-2048-USB2 (Avantes BV, the Netherlands). Two commercial lasers (BWTek, Inc. BWB-405-40-PIG-200-0.22-SMA 405 nm line and BWT-532-15-SMA, two lines: 532 nm and 1064 nm) were used, as well as two laboratory-assembled diode lasers (645 nm and 807 nm). Irradiation power at the skin contact probe output varied from 1 mW at 1064 nm to 16 mW at 405 nm, which corresponds to power densities on skin in the range 0.35… 5.66 W/cm2. The fiberoptic probe comprised six 600micron silica core fibers arranged in a line with 1 mm distance between the neighbour fiber centers. First fiber in the row was used for collection of reflectance light; the other five adjacent fibers were used for delivery of laser output to the skin surface. All fiber optic components were designed and manufactured by Z-Light, Ltd. (Latvia). The probe was positioned directly on skin during the measurements, namely, on the inner part of the middle fingertip of the examined person. Measurements were taken from fingertips of ten volunteers in relaxed sitting position. The probe was loaded with calibrated weights (20, 70, 130, 230, or 430 g) thereby changing the skin-probe contact pressure in the range of 0.5-11 kPa. Two procedures of load application were used: (i) gradual increase of probe-skin contact pressure by adding a weight to the probe every minute of 5 min continuous PPG recording, (ii) alternating increase and decrease of probe-skin contact pressure by adding and removing weights every 2 minutes of a 10 min PPG measurement session. Each measurement session was repeated three times for a single volunteer. For measurements with the spectrometer model AvaSpec-2048-USB2, more advanced software was created by means of the special Avantes BV tools using the CodeGear Delphi 2007 programming language. This software made possible to choose any selected wavelength band (up to three nanometers) for the multi-spectral PPG signal real-time recording, and to record additionally two analogue PPG signals in real-time, along with the multi-spectral PPG recordings. In accordance with the laser emission lines used in the setup, PPG signals were plotted in time at the laser emission wavelengths. This principle of data processing is shown schematically in Fig. 2. Fig. 1. Experimental setup for the multiwavelength photoplethysmography method. Fig. 2. Schematic illustration of the time-resolved PPG signal acquisition: from the total detected skin reflectance spectrum (on the left), the intensity-time sections (A-A) are recorded only at the selected laser wavelengths(on the right). 3. RESULTS AND DISCUSSION Two types of signal comparison were performed: (i) regarding the relative amplitude changes of signal baselines or DC levels, and (ii) regarding the relative amplitude changes of normalized singleperiod PPG signals at various wavelengths, i.e., relative AC values. The first type of signal comparison shows the responses of multi-wavelength PPG signal baselines to a gradual increase or decrease in probe-skin contact pressure. The increase of probe-skin contact pressure has caused a decrease of the PPG signal baseline amplitudes at all five exploited wavelengths for all volunteers. Typical response for a three-wavelength set is presented in Fig. 3.a. This trend coincides with the results obtained earlier by other authors using different PPG technique modalities [5,6]. Measurements also showed a sharp decrease of amplitudes of the PPG pulsations detected at shorter wavelengths of 405 and 532 nm (that relate to shallow penetration) at the highest probe-skin pressures applied, namely, the signal AC component was absent at 6.5 kPa for 405 nm signal (Fig. 3.b), and at 11.3 kPa for both, 405nm and 533 nm PPG signals for 8 of 10 volunteers (Fig. 3.a). The loss of signal AC component indicates pressure-induced occlusions of superficial skin blood vessels; it has been shown previously that the occlusion pressures increase with wavelength and differ among persons [6]; our results correspond qualitatively to the above mentioned findings, however, the quantitave disagreement can be explained by differences in the loading procedures. The other type of results represent variations in the shapes of single-period PPG pulses at various wavelengths. The typical feature taken into consideration was the relative amplitude of the secondary peak of a single PPG pulse. The variations in secondary peak relative amplitude of the mean normalized single-period PPG contours at various laser wavelengths did not exceed the calculated StDev = 0.09 a.u. The calculated amplitude variations were ascribed to different signal depth, as well as different signal-to-noise ratios at various wavelengths caused by skin absorption spectral dependence. Both, statistical analysis and impovement of signal-to-noise ratios are necessary to enable the detection of PPG shape variation with wavelength. a b Fig. 3. (a) Typical changes of PPG signals at three wavelengths with increasing probe-skin pressure from 0.5 to 11.3 kPa; the loss of the AC signal at 11.3 kPa indicates occlusions at 405 and 532 nm (Signals of one volunteer are plotted). (b) PPG signal response to alternating increase and decrease of probe-skin pressure; the AC component is absent at 6.5 kPa for the 405 nm signal, while at 532 and 807 nm the AC pulsation component is still detectable representing the differences in occlusion pressures for various wavelenghts. (Signals of one volunteer are plotted) 4. CONCLUSIONS Simultaneous use of several cw lasers with multi-fiber coupling to skin and further to a standard multi-channel array spectrometer has been tested for the recording of photoplethysmography signals. PPG baseline responses to probe-skin contact pressure have been recorded at three wavelengths at a time combining 405; 532; 645; 807 and 1064 nm laser lines. The differences in loss of AC component at various wavelengths, i.e., occurence of occlusions, have confirmed the depth sensitivity of the multiwavelength PPG method. The further evolution of the multi-wavelength PPG methodology involves experimental data accumulation for the establishment of quantitative descriptive criteria, as well as creation of physical model in order to associate measured PPG signals with particular depths in skin. 5. REFERENCES 1. J. Spigulis (2005) Optical non-invasive monitoring of skin blood pulsations. Appl Opt 44:1850-1857 2. J. Allen (2007) Photoplethysmography and its application in clinical physiological measurement. Physiol 3. 4. 5. 6. Meas 28 R1–R39 H. Ugnell, P. Å. Öberg (1995) Time variable photoplethysmographyc signal: its dependence on light wavelength and sample volume. 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