Wearable Sensors and Machine Learning for Hypovolemia Problems in Occupational, Military and Sports Medicine: Physiological Basis, Hardware and Algorithms

Figures

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  Figure 1. Illustration of the concept of absolute and relative hypovolemia. Pink represents the vascular (blood) volume and blue represents the vascular space. Absolute hypovolemia (reduction in blood/plasma volume) can be mediated by factors such as hemorrhage or dehydration; relative hypovolemia can be mediated by factors that increase vascular space such as increased cutaneous vasodilation from heat stress, hypoxia, intense physical exercise, or systemic vasodilation from sepsis. Image modified from [15].

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  Figure 2. Linear regression of plasma volume loss (hypovolemia) and body water deficit (percent change in body mass) relationship for hypertonic (sweat loss) and isotonic (Furosimide diuretic) dehydration [16].

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  Figure 3. Ventricular function curves showing the sequence of cardiovascular events during hypovolemia while performing an occupational work activity. Hypovolemia causes reduced ventricular filling or preload (1). Then, the body compensates by increased sympathetic tone, resulting in elevated heart rate and cardiac contractility (2). During physical activity, the worker periodically performs upper limb isometric tasks, thus increasing afterload (3). The result is decreased stroke volume and increased myocardial oxygen demands.

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  Figure 4. Demonstration of the impact of skin warming on skin temperature (Ts), rectal temperature (TR),blood temperature from right atrium (TB), total peripheral resistance (TPR), right atrial mean pressure (RAMP), aortic mean pressure (AoMP), central blood volume (CBV), stroke volume (SV), and heart rate (HR) and cardiac output (CO). Image from [45].

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  Figure 5. The conceptual framework of the compensatory reserve measure (CRM) algorithm. The input waveform from the current subject is compared to a library of more than 650,000 waveforms recordings collected from more than 260 subjects exposed to experimentally-controlled progressive reductions in central blood volume by lower-body negative pressure to generate an estimated individual compensatory reserve measurement (CRM). Image modified from [50].

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  Figure 6. Compensatory reserve measures for normothermic vs hyperthermic subjects (left) and euhydrated vs dehydrated subjects (right) during progressive lower body negative pressure (LBNP) experiments. Data are means and 95% confidence intervals, with the solid lines at the bottom indicating statistically significant differences from baseline. Image modified from [13].

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  Figure 7. Compensatory reserve measure responses to progressive increases in aerobic exercise intensity (percent maximal aerobic power) that result in maximal exertion (left). On the (right), low baseline CRM (filled circles with 95% confidence intervals) is associated with lower maximal aerobic power (VO2max) compared to subjects with high initial CRM (open circles with 95% confidence intervals) with the final difference shown by the red arrow on the x-axis. Image from [13].

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  Figure 8. Compensatory reserve measured in a human subject during a 20-min graded cycle ergometer exercise performed at 100 °F air temperature. Each bar represents the average response over 1 min. Bar colors: green, compensatory reserve >60%; yellow, compensatory reserve ≤60% and >30%; red, compensatory reserve ≤30%. BL, baseline; W, watts. Image modified from [52].

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  Figure 9. Compensatory reserve measures before and after 45 min of running exercise in the heat and resting recovery (10 min) and then fluid replacement (black line). Bar colors: green, compensatory reserve >60%; yellow, compensatory reserve ≤60% and >30%; red, compensatory reserve ≤30%. BL, baseline; W, watts. Image modified from [52].

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  Figure 10. Device form factor. Electrodes for a single-lead ECG, photodiodes and LEDs to record the PPG, and tri-axial accelerometers and gyroscopes (internal to the devices) to acquire the SCG signal can be customized and modularized to work in multiple form factors. The left side shows the watch-based approach described in [60], while the right side shows an updated version of the chest-worn patch originally described in [59].

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  Figure 11. BVDS feature extraction. While the CRM evaluates 30-s segments of the recorded arterial waveform signal, the BVDS metric uses the ECG to segment and analyze all signals on a heartbeat-by-heartbeat level. Fiducial points are detected in each heartbeat and used to calculate cardiac timing intervals and a handful of other clinically relevant features.

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  Figure 12. Feature importance for the BVDS model, as output by the random forest algorithm in [12]. Electromechanical features include the pre-ejection period (PEP), left ventricular ejection time (LVET) and their ratio, PEP/LVET along with heart rate (HR) and multiple measures of heart rate variability (HRV). Vascular features include the distal (and normalized) pulse arrival time (PAT), the distal pulse transit time (PTT), the PPG amplitude and the plethysmograph variability index (PVI). PEP/LVET is the most important feature for this model by a large margin, and six of the top seven features are from an electromechanical signal. This result highlights the relevance of including the ECG and SCG signals in predicting cardiovascular decompensation. Image modified from [12].