Heart rate increases with metabolic demand for oxygen and is an indirect indicator of physical activity. Measurement of heart rate can be used to estimate physical activity intensity or energy expenditure (EE) assuming a linear relationship between heart rate and EE (or oxygen consumption, VO2).
This method is limited by considerable inter-individual variation and, to a lesser extent, intra-individual variation in the heart rate-to-EE relationship (Li et al., 1993). Heart rate at a given physical activity intensity will not be the same between most individuals due to differences in age, gender, movement economy, and physical fitness. Heart rate can also be affected by factors other than physical activity, such as ambient temperature, dehydration, illness or emotional stress. The relative influence from these factors is greatest during low intensity and sedentary behaviours. As a result, assessment of physical activity using heart rate is best at moderate and vigorous intensity levels and least accurate at lower intensity levels.
Various techniques have been developed to overcome these limitations, including the use of individual calibration of the relationship between heart rate and EE to address the issue of inter-individual variation, and the FLEX heart rate method to limit the impact of non-activity influences on the energy estimate. Heart rate monitors can provide minute-by-minute and beat-by-beat information relating to the pattern of physical activity in terms of duration, frequency and intensity. Estimates of EE and physical activity intensity depend upon how estimates are derived and the level of individual calibration (Brage et al., 2007; Schrack et al., 2012). The dimensions of physical activity assessed by heart rate monitoring are described in Table P.3.9.
Table P.3.9 The physical activity dimensions which can be assessed by heart rate monitor.
|Possible to assess?
|Total physical activity energy expenditure
|Timing of bouts of activity (i.e. pattern of activity)
|Contextual information (e.g. location)
Electrocardiography (ECG) based heart rate monitors measure the electrical potential on the surface of the skin using electrodes attached to the chest (see Figure P.3.8). This results in a voltage time-series signal, which may be stored as the full ECG waveform (as used in Holter monitoring) for offline processing, or may be processed by the monitor’s inbuilt peak detection algorithm to identify heart beats (the QRS complex in the cardiac cycle). Data are then stored as inter-beat interval time-series (in milli-seconds) or may be further reduced to average heart rate values, for example number of beats every minute. This final step usually employs a degree of filtering to limit the impact of missed and/or ectopic beats. There are therefore three steps involved in deriving a robust estimate of average heart rate; one measurement step and two inference steps.
Optical heart rate monitors work on a different principle of measurement, namely by detecting the fluctuation in blood perfusion of the skin (finger, wrist, earlobe) that occurs during the cardiac cycle by differential absorption of light from a LED to a photodiode (photoplethysmography, PPG); the subsequent inferential steps of deriving heart rate in beats per minute are similar in principle to those performed on the ECG signal (peak detection to derive beats, followed by filtering to get a robust average heart rate estimate).
The development of heart rate monitors with internal memory capacity for storing multiple days’ of data in high time resolution has increased the feasibility of this objective measure of physical activity; some do not have visual display of heart rate which further improves feasibility (reduces re-activity) for observational research.
There are a wide range of heart rate monitors which vary in sophistication but in practical terms there are three main types of heart rate monitors used to measure physical activity in population health research:
Figure P.3.8 Wear location of a heart rate monitor chest strap.
There are two key issues associated with the use of heart rate to estimate physical activity:
Due to inter-individual variability of an individual’s heart rate response to activity, individual calibration is required to increase the accuracy of heart rate data to estimate physical activity (Brage et al., 2007).
This typically includes collection of heart rate response to a submaximal exercise protocol with a known or measured EE cost profile. The relationship derived between observed heart rate and EE during the exercise test is then applied to predict EE in free-living situations. Determining whether to individually calibrate or not (and how) is a matter of weighing up the likely increased validity of the measurement versus the feasibility of the calibration method.
There are different options for calibration. The most intensive methods are likely to produce more precise estimates but may be perceived as more invasive, take more time for the participant to undertake in the laboratory setting, and are therefore not always feasible for large-scale studies. Exercise protocols for establishing heart rate to EE relationships can also be risk-stratified (Gonzales et al., 2021). The choice of calibration method needs to take into account the characteristics of the population being studied and secondly the settings under which a calibration test could be carried out. If necessary existing exercise tests can be adapted or new ones developed for a specific application; the underlying principle is the same in that heart rate data over a reasonable intensity range are needed. Examples of different approaches to individual calibration in descending order of validity but ascending order of feasibility are:
The choice of calibration protocol and in particular its intensity range will affect the accuracy of the prediction of EE for each heart rate level (Corder et al., 2008). Simplified methods, such as walk or step tests or even no dynamic calibration but simply using resting heart rate and other possible proxy indicators of fitness (age, sex) have been suggested, accepting the reduction in precision (Brage et al., 2007; Corder et al., 2005).
Simple methods such as the 8-minute ramped step test with a 2-minute recovery are portable and quick, making them feasible for field studies involving larger numbers of people or where facilities are minimal. The use of only sleeping heart rate is an alternative calibration method and measurements taken overnight explain some variation in the heart rate and EE relationship without the need for resource-demanding calibration procedures but it is not as good as a dynamic test (Brage et al., 2007). The relationship between the validity and feasibility of different calibration procedures is demonstrated by Figure P.3.9.
Figure P.3.9 Trade-off between validity and feasibility of calibration procedures. Adapted from: Brage et al., 2007.
GXT: graded exercise test; XT: exercise test; SHR: sleeping heart rate.
Heart rate monitoring is used when estimates of physical activity energy expenditure (PAEE) and time spent in moderate and vigorous intensity physical activity are required. The method also provides estimates of frequency, duration, and timing of these activities. The need for individual calibration for achieving better accuracy may limit use of this method for some larger studies (Armstrong et al., 2006) although several larger cohorts have done so (Lindsay et al., 2019; Wareham et al. 1997).
It should be noted that accuracy is considerably improved by using individual calibration; this is particularly important for interventions that may have altered fitness, since estimates of PAEE and time spent in different intensities of activity may otherwise be differentially biased with respect to intervention group.
Using group-based calibration equations (rather than individual calibration) reduces accuracy but increases the feasibility of the method as an objective measure of physical activity in larger epidemiological studies where conducting individual calibration tests would be prohibitive. Improvements in user acceptability, for example via more skin-friendly materials for ECG pads or wrist-based photoplethysmography technology, as well as statistical techniques for inference of true heart rate from potentially noisy measurements of heart rate (Stegle et al., 2008) would make this method more applicable to very large studies with >100,000 individuals. The Apple Heart Study used the optical measurement of heart rate from Apple watches to detect atrial fibrillation in >400,000 individuals (Perez et al, 2019).
Flex heart rate method
Heart rate monitoring is used when estimates of physical activity energy expenditure (PAEE) and time spent in moderate and vigorous intensity physical activity are required. The method also provides estimates of frequency, duration, and timing of these activities.
Individual assessment of resting energy expenditure and resting heart rate, as well as an exercise test linking heart rate changes to different energy expenditure levels is required.
TEE = EE sleep + EE rest + EE physical activity
EE sleep = BMR
EE rest = REE (for time when HR < FLEX HR)
EE physical activity = EE from regression equation (for time when HR ≥ FLEX HR)
The heart rate Flex point is defined empirically as the average of the lowest heart rate during exercise and the highest during rest (Ceesay et al., 1989). Livingstone et al. (1992) evaluated the accuracy of the Flex heart rate method to estimate TEE in 36 free-living children using DLW. Individual differences ranged from -16.7% to 18.8%; mean group differences ranged from -9.2% ± 4.5% to 3.5% ± 6.6%. The method has also been validated in various adult populations comparing EE estimates with those measured by whole body calorimetry and DLW. Recent estimates from UK adults were reported to agree with DLW-based estimates of PAEE and TEE with no significant bias irrespective of individual calibration level but with higher accuracy and correlations (range r=0.66-0.76 for TEE) for calibrated estimates (Ceesay et al., 1989; Ekelund et al., 2002; Livingstone et al., 1990; Brage et al., 2015).
Limitations of the Flex heart rate method
The key limitations of the Flex heart rate method are that it depends on the assumption that the measured heart rate - EE relationship is reliable in free-living daily activities and that it reflects cardiorespiratory responses to physical activity, but not other physiological responses to external stimuli e.g. caffeine or emotional stress.
The individual calibration should be undertaken as close to the heart rate monitoring period as possible since the estimation of energy expenditure is based on the assumption that the measured heart rate - EE relationship is representative for the physiological state of the individual during the monitoring period. This relationship may change as a result of improved cardiorespiratory fitness, changes in body composition or certain conditions/diseases (e.g. anaemia).
Other modelling approaches
The feasibility of using heart rate monitoring without individual calibration to estimate EE using prediction parameters has been investigated and found suitable for ranking individuals in epidemiological studies (Rennie et al., 2001). Other studies have also shown that it is possible to estimate EE from heart rate using multivariate predictive equations derived from group data in adults (Hiilloskorpi et al., 2003; Dugas et al, 2005; Keytel et al., 2005; Strath et al., 2000) and children (Livingstone et al., 2000).
Variation in applying different prediction equations has been investigated and individual differences found; group level analysis was found to be satisfactory for some population groups (Iannotti et al., 2004). It is important that prediction equations are derived in studies with adequate numbers (>100) and are representative of the population to be studied. Another approach to analysing heart rate data has been to adjust for fitness and age to increase the validity of using heart rate to predict EE (Strath et al., 2000).
Absolute heart rate indices
Absolute heart rate values have also been used to distinguish between activity intensities (Sirard & Pate, 2001), albeit less frequently. The method is based on using a heart rate above a certain threshold, e.g. ≥140 beats per minute, as an approximate measure of moderate-vigorous physical activity (MVPA) in children (Simons-Morton et al., 1990).
Relative heart rate indices
A common method to derive relative heart rate indices utilises a measurement of the individual’s resting heart rate (RHR) or expressing heart rate relative to (usually predicted) maximal heart rate. Four of the most commonly used heart rate indices are:
An overview of the characteristics of heart rate monitoring is outlined in Table P.3.10.
Chest strap monitors must be well fitted in order to provide contact with the skin; this may be uncomfortable when measuring heart rate over several days. Alternatively ECG electrodes can be used to obtain heart rate, however these can also be difficult to wear over longer periods due to problems with placement and skin irritation (Andre & Wolf, 2007).
Table P.3.10 Characteristics of heart rate monitoring.
|Number of participants
|Small to very large
|High with individual calibration
|Researcher burden of data collection
|High with individual calibration
|Researcher burden of data analysis
|Risk of reactivity bias
|Risk of recall bias
|Risk of social desirability bias
|Risk of observer bias
|Participant literacy required
Considerations relating to the use of heart rate monitors for assessing physical activity are summarised by population in Table P.3.11.
Table P.3.11 Physical activity assessment by heart rate monitor in different populations.
|Suitable. PPG-based methods likely more accepted.
|Infancy and lactation
|Toddlers and young children
|May have difficulty wearing electrodes and chest strap both in terms of having more sensitive skin but also the size of straps and belts of the monitors themselves. There are also small pieces which could be swallowed. Child curiosity could lead to fiddling which interferes with heart rate signal.
|Generally suitable. Safety may be a concern when conducting exercise testing for individual calibration. Self-paced protocols may be viable alternatives. Dexterity may be an issue when changing electrodes/placing device.
|Generally suitable. PPG accuracy may be lower on darker skin.
|In obese individuals it may be more difficult to get a good heart rate signal due to adiposity attenuating the signal.
A list of specific heart rate monitoring instruments is being developed for this section. In the meantime, please refer to the overall instrument library page by clicking here to open in a new page.