Humans generate considerable forces against the ground during running to maintain an upright posture. This comes at the cost of equal and opposite ground reaction forces (GRF) acting on the body during every foot-ground contact (Cavanagh & Lafortune, 1980). These GRF put the body’s soft tissues (e.g., bones, cartilage, muscles, tendons and ligaments) under biomechanical stresses which over time are expected to lead to beneficial structural adaptations (Kibler, Chandler & Stracener, 1992; Dye, 2005). Inadequate recovery or repetitive GRF with excessive magnitudes can instead lead to negative adaptions and tissue damage (Kibler, Chandler & Stracener, 1992; Dye, 2005). The ability to monitor an athlete’s GRF during running can therefore help to better understand the relationship between the external forces experienced and soft-tissue adaptations (Vanrenterghem et al., 2017) ultimately helping to prevent musculoskeletal injury.
Accurate monitoring of GRF waveforms during running is currently restricted to laboratory environments where GRF waveforms are measured with force platforms built into the ground, or derived from whole-body kinematics (Bobbert, Schamhardt & Nigg, 1991; Winter, 2005). With recent developments of low-cost sensor based micro technology (Camomilla et al., 2018), accelerometry has become a popular tool to evaluate running mechanics outside laboratory environments in long and middle distance running (Tao et al., 2012) and professional team sports (Akenhead & Nassis, 2016). Accelerometry also offers opportunities to estimate loading related GRF characteristics (e.g., Lafortune, 1991; Wundersitz et al., 2013; Neugerbauer, Collins & Hawkins, 2014; Raper et al., 2018), and tibia-mounted accelerometry has for example been used as surrogate measure of peak GRF since the early 90s (Lafortune, 1991; Lafortune, Lake & Hennig, 1995). However, recent studies found weak to moderate linear relationships between peak accelerations measured from body-worn accelerometry (trunk- and tibia-mounted accelerometers) and peak whole-body accelerations measured from force platforms during running (Wundersitz et al., 2013; Nedergaard et al., 2017a; Raper et al., 2018). Since body-worn accelerometers only measure segmental acceleration, the use of a single accelerometer has to date been inadequate to incorporate the complex multi-segmental accelerations that result in task-specific GRF patterns (Nedergaard et al., 2017a). Recent studies have indicated that from the combination of three or more body-worn inertial sensors and machine learning one can estimate GRF and knee joint moments with reasonable accuracy during running related locomotion (Johnson et al., 2018; Wouda et al., 2018), but the broader application of such approaches is constrained by the requirement of multiple sensors, machine learning tools, and large data sets. Therefore, if it were possible to estimate accurate GRF waveforms from a single body-worn sensor, it would provide practitioners and researchers with a useful tool to monitor the biomechanical load in field settings.
Since the overall motion of the human body has a spring-like behaviour during running, simple mass–spring models, consisting of a single mass and spring, have been widely used to estimate the vertical GRF in field settings (e.g., Alexander, 1984; Blickhan, 1989; McMahon & Cheng, 1990). Moreover, such models have been used in combination with trunk-mounted accelerometry to estimate the required model parameters (Gaudino et al., 2013; Buchheit, Gray & Morin, 2015). Unfortunately, the initial high-frequency impact peak typically observed in the GRF waveform during running, which is speculated to be linked with negative tissue adaptations and risk of injury (Nigg, Cole & Bruggemann, 1995; Hreljac, Marshall & Hume, 2000; Milner et al., 2006), cannot be estimated with this oversimplified model (Alexander, Bennett & Ker, 1986; Bullimore & Burn, 2007). A more complex mass–spring-damper model (MSD-model) better replicates the GRF waveforms for running at moderate speeds (3.83 m s−1 ± 5%), including both impact and active peaks (Derrick, Caldwell & Hamill, 2000). This model consists of a lower mass connected to a spring in parallel with a damper, representing the support leg during foot-ground contact, and an upper mass and spring representing the dynamics of the rest of the body. However, the ability to use trunk-mounted accelerometry to estimate the required model parameters for this model is yet unknown.
The aim of this study was to examine if the acceleration of the MSD-model’s upper mass represents the acceleration of the trunk segment measured with trunk-mounted accelerometry during running. This hypothesis seems feasible, since the trunk segment represents half of the body mass (Dempster, 1955). If this provides a reasonable approximation, it might be feasible to estimate the required MSD-model parameters from trunk accelerometry to subsequently predict GRF from the MSD-model behaviour. Specifically, we therefore explored (1) the feasibility to estimate the MSD-model’s eight natural model parameters from measured trunk accelerometry, and (2) whether these model parameters in fact predict reasonably accurate GRF waveforms during running at slow to moderate running speeds.
Materials & Methods
Subjects and protocol
Twenty healthy male athletes (age 22 ± 4 years, height 178 ± 8 cm, mass 76 ± 11 kg) who engaged in running related sports activities on a weekly basis volunteered to participate in this study. The institutional ethics committee at Liverpool John Moores University granted ethical approval for this study (ethics approval number: 09/SPS/010) in accordance with the Declaration of Helsinki, and written consent was obtained from all participants. After a 15 min warm-up (including light jogging, dynamic stretching and individual dynamic tasks) and an individual number of familiarisation trials, the participants were asked to run over a force platform at different running speeds of 2, 3, 4 and 5 m s−1 (±5%) in a randomised condition order. Running speeds were measured with photocell timing gates (Brower Timing System, Utah, USA) placed 2 m apart, with the last gate positioned 2 m before the centre of the force platform as described in Vanrenterghem et al. (2012). The participants completed four trials of each running speed, landing on the force platform with their dominant leg (defined as the self-reported preferred kicking leg (Van Melick et al., 2017)). Trials with unsuccessful foot contacts on the force platform (double foot contact or when the foot was not placed within the force platform) and/or when the desired approach speed was not achieved were repeated until a valid trial was recorded.
Resultant ground reaction forces were measured (GRF) with a sampling frequency of 3,000 Hz from a 0.9 × 0.6 m2 Kistler force platform (9287C, Kistler Instruments Ltd., Winterthur, Switzerland). Resultant trunk accelerations (TrunkAcc) were simultaneously collected at 100 Hz using a tri-axial accelerometer (KXP94, Kionex, Inc., Ithaca, NY, USA) with an output range of ±13 g embedded within a commercial GPS device (MinimaxX S4, Catapult Innovations, Scoresby, Australia) with a total weight of 67 grams and 88 × 50 × 19 mm in dimension. The GPS device was positioned on the dorsal part of the upper trunk between the scapulae within a small pocket of a tight fitted elastic vest according to the manufacturer’s recommendations (Boyd, Ball & Aughey, 2011). Different vest sizes were used to ensure the tightest fit for the individual participants. TrunkAcc data (measured in the units g) was pre-processed with the manufacturer’s proprietary filter algorithms (50 Hz low-pass filter, personal communication with the manufacturer), and downloaded as ‘raw accelerometer data’ from the manufacturer’s software (Catapult Sprint, version 5.1.7, Melbourne, Australia) after each test session. Each session also included a static measurement at the beginning and end of the session to detect any calibration drift over time, and none was detected. TrunkAcc and GRF were synchronised using a combination of time and event synchronisation as described in Nedergaard et al. (2017a) and exported to Matlab (version R2016a, The MathWorks, Inc., Natick, MA, USA) where a 4th order recursive Butterworth low-pass filter with a cut-off frequency of 20 Hz was applied to GRF and TrunkAcc. GRF data was collected from a single stance phase per trial, where touch down and take off were defined when the vertical GRF crossed a 20 N threshold.
The complex multi-segmental dynamics of the human body during stance phase were modelled as a passive MSD-model (Alexander, Bennett & Ker, 1986; Derrick, Caldwell & Hamill, 2000). This model consists of two masses (Fig. 1); a lower point mass (m2) on top of a linear spring (k2) in parallel with a damper (c) representing the support leg; an upper point mass (m1) representing the dynamics of the rest of the body and another linear spring (k1) connecting the two masses.
(1) (2) (3) (4) (5) (6) (7) where p1, p2 v1, v2, a1, and a2 are the initial positions, velocities and, accelerations of the two masses (m1 and m2), respectively; λ is the mass ratio of the lower mass relative to the total body mass (Eq. 1); ω12 and ω22 are the natural frequencies of the springs (Eqs. (2) and (3)) based on the linear spring constants (k1 and k2) and the mass of the two masses (m1 and m2); ζ is the damping ratio of the damper (Eq. 4); and g is the acceleration from gravitational acceleration (−9.81 m s−1). The resultant GRF acting on the MSD-model is calculated as in Eq. (7), where M is the sum of the two masses (i.e., total body mass):
Model parameter estimation
To estimate the eight MSD-model parameters (p1, p2 v1, v2, ω12 ω22, ζ, λ), we used gravity corrected TrunkAcc from the stance phase as a surrogate of the MSD-model’s upper mass acceleration (Fig. 2A). For each trial, model parameters (ACCparam) were optimised by fitting the MSD-model’s upper mass acceleration (a1) to the TrunkAcc signal. A purpose-built gradient descent optimisation routine in Matlab was used, where the two second-order differential equations of the MSD-model’s motion Eqs. (5) and (6) were transformed to four first-order differential equations and solved numerically with a Runge Kutta 4th order method. Root mean squared error (RMSE) between the TrunkAcc and a1 waveforms were calculated for every iteration to determine the optimal model ACCparam combination that best fitted TrunkAcc for the individual trials. The ACCparam estimated from the TrunkAcc fitting were then used to predict the resultant GRF from Eq. (7). Furthermore, to help understand differences in estimated model parameters and the predicted versus measured resultant GRF, we also estimated the eight model parameters (GRFparam) by fitting the MSD-model to the measured GRF (Fig. 2B), similar to the approach previously described by Derrick, Caldwell & Hamill (2000).
Measured and modelled GRF were normalised to the participants’ mass. RMSE between the TrunkAcc and a1, waveforms, and between the measured GRF and predicted GRF waveforms, were calculated to evaluate the accuracy of the TrunkAcc fitting and the predicted GRF, respectively. RMSE median and interquartile range (25th to 75th percentile) were calculated to determine the variation in the model’s accuracy within and across running speeds. Similarly, the median and interquartile range (25th to 75th percentile) of the ACCparam and GRFparam were calculated to explore the variation within and across running speeds. The median data presented and discussed in the following is the median of all trials within the individual running speeds (N = 80 trials) and the overall median across all running speeds (N = 320 trials).
The first step was to estimate the required ACCparam that fit the MSD-model’s upper mass acceleration to the measured TrunkAcc signal. The MSD-model was able to fit the measured TrunkAcc with good accuracy across running speeds, though a1 systematically underestimated the magnitude of the first peak observed in the accelerometry signal (Fig. 3A). The median RMSE (interquartile range 25th to 75th percentile) of the TrunkAcc fitting increased from 0.16 (0.12; 0.22) g at the slowest running speed to between 0.21 (0.16; 0.26) g and 0.22 (0.16; 0.30) g for three faster running speeds. Though similar median RMSE values were observed across the three fastest running speeds, the interquartile range increased with increased running speeds (Fig. 3C). Despite the good match between a1 and TrunkAcc, poor GRF predictions were observed across running speeds (Fig. 3B) and the median RMSE of the predicted GRF systematically increased with running speeds, from 6.68 (3.81; 15.30) N kg−1 at 2 m s−1 to 12.77 (7.78; 27.22) N kg−1 at 5 m s−1.
Since the ACCparam resulted in poor GRF predictions, we next estimated the GRFparam by fitting the MSD-model to the measured GRF waveforms (Fig. 2B) to determine if there was any difference between the two sets of model parameters (Table 1) and to compare the upper mass acceleration to the measured TrunkAcc. The MSD-model was able to replicate the measured GRF with high accuracy when GRFparam were estimated to directly fit the measured GRF (Fig. 4B). This was reflected in the low RMSE median and interquartile ranges observed across all running speeds (2 m s−1: 0.45 (0.36; 0.60); 3 m s−1: 0.47 (0.37; 0.61); 4 m s−1: 0.53 (0.39; 0.66); 5 m s−1: 0.59 (0.46; 0.73); All Speeds: 0.51 (0.39; 0.64) N kg−1). However, the MSD-model’s upper mass acceleration profiles then deviated considerably from the acceleration profiles measured with trunk accelerometry (Fig. 4A). The GRFparam also differed considerably from the ACCparam (Figs. 4C and 4D). Namely, the GRFparam demonstrated smaller within parameter variation, which was especially evident for p2 and v2. Also, lower v1 (median difference 0.47 m s−1) and higher v2 (median difference −1.73 m s−1) values were observed across running speeds.
|ModelParameters||2 (m s−1)||3 (m s−1)||4 (m s−1)||5 (m s−1)||All|
|Median (25th; 75th)||Median (25th; 75th)||Median (25th; 75th )||Median (25th; 75th)||Median (25th; 75th)|
|ACCparam||−0.02 (−0.04; −0.01)||−0.01 (−0.04; 0.00)||−0.02 (−0.05; 0.00)||−0.03 (−0.06; −0.01)||−0.02 (−0.05; −0.01)|
|GRFparam||0.00 (−0.01; 0.00)||0.00 (−0.01; 0.00)||0.00 (−0.02; 0.00)||−0.01 (−0.02; −0.01)||−0.01 (−0.02; 0.00)|
|ACCparam||−0.01 (−0.02; 0.00)||0.00 (−0.02; 0.01)||−0.01 (−0.03; 0.00)||−0.01 (−0.04; 0.00)||−0.01 (−0.03; 0.00)|
|GRFparam||0.00 (0.00; 0.01)||0.00 (0.00; 0.01)||0.00 (0.00; 0.00)||0.00 (0.00; 0.00)||0.00 (0.00; 0.00)|
|ACCparam||−0.58 (−0.65; −0.50)||−0.67 (−0.82; −0.60)||−0.71 (−0.82; −0.60)||−0.60 (−0.69; −0.41)||−0.64 (−0.75; −0.54)|
|GRFparam||−0.91 (−1.12; −0.72)||−1.04 (−1.26; −0.92)||−1.24 (−1.34; −1.11)||−1.13 (−1.27; −0.98)||−1.11 (−1.28; −0.92)|
|ACCparam||−1.98 (−2.71; −1.37)||−1.59 (−2.91; −0.93)||−1.78 (−3.13; −1.20)||−1.55 (−2.39; −0.60)||−1.75 (−2.76; −1.08)|
|GRFparam||−0.02 (−0.40; 0.00)||−0.05 (−0.28; 0.00)||−0.01 (−0.24; 0.00)||0.00 (−0.10; 0.00)||−0.02 (−0.25; 0.00)|
|(N m−1 kg−1)|
|ACCparam||334 (233; 622)||508 (233; 966)||477 (315; 1,193)||512 (331; 977)||469 (267; 958)|
|GRFparam||528 (370; 721)||577 (357; 935)||621 (385; 959)||687 (495; 1,025)||604 (411; 899)|
|ω22(N m−1 kg−1)|
|ACCparam||2,537 (1,167; 3,895)||2,584 (1,152; 4,174)||2,967 (1,628; 4,688)||3,460 (1,517; 5,094)||2,795 (1,320; 4,362)|
|GRFparam||2,421 (1,516; 3,420)||2,966 (2,265; 4,593)||3574 (2,305; 5,094)||4,006 (3,111; 6,550)||3,253 (2,207; 4,894)|
|ACCparam||2.86 (1.72; 4.60)||2.61 (1.46; 4.30)||3.11 (1.06; 4.27)||2.25 (0.97; 3.28)||2.62 (1.28; 4.13)|
|GRFparam||4.02 (2.14; 6.62)||5.19 (2.82; 6.51)||2.84 (1.86; 5.90)||2.74 (1.82; 3.40)||3.32 (2.04; 5.84)|
|ACCparam||0.23 (0.18; 0.33)||0.21 (0.15; 0.32)||0.20 (0.15; 0.30)||0.16 (0.07; 0.32)||0.20 (0.15; 0.32)|
|GRFparam||0.38 (0.29; 0.58)||0.39 (0.28; 0.51)||0.37 (0.28; 0.45)||0.31 (0.25; 0.40)||0.36 (0.27; 0.45)|
This study illustrates that the MSD-model’s upper mass acceleration could be fitted to the measured trunk accelerometry with high accuracy, but the ACCparam estimated from this process did not lead to accurate predictions of resultant GRF waveforms across a range of slow to moderate running speeds. Further analysis of the MSD-model behaviour when fitting to the measured resultant GRF revealed a considerable discrepancy in GRFparam compared to the ACCparam when fitting the MSD-model to measured trunk accelerometry signals. These results demonstrate that our initial hypothesis that the MSD-model’s upper mass acceleration primarily represents the acceleration of the trunk was false.
Model parameter estimation
The eight model parameters are fundamental to calculating the resultant GRF acting on the MSD-model, and though fitting TrunkAcc was successful, the ACCparam estimated from this approach resulted in poor GRF predictions. Based on the equation of the upper mass acceleration (Eq. 5) and the ACCparam estimated from TrunkAcc, it seems that the MSD-model was able to fit the TrunkAcc by keeping the initial position of the upper mass (p1) and lower mass (p2) low, and by keeping the spring stiffness of the upper spring (ω12) low. Whereas p1 has minor influence on the predicted GRF, the velocity of the upper mass at initial contact (v1) is indirectly influenced by changes in the initial upper mass position (). Derrick, Caldwell & Hamill (2000) found that decreased v1 has a large impact on the duration of the stance phase and therefore could have contributed to the overestimation of foot-ground contact (Fig. 3B). Similarly, the MSD-model decreased the spring stiffness of the upper spring (ω12) to better fit the two acceleration peaks typically observed in the TrunkAcc data, which has previously been shown to increase the duration of the stance phase (Derrick, Caldwell & Hamill, 2000). Furthermore, the MSD-model lowered the initial position of the lower mass (p2), which previously has been shown to both increase the GRF at touch down and decrease the magnitude of the impact peak (Derrick, Caldwell & Hamill, 2000). We therefore believe that the high GRF values observed in our GRF predictions at touch down (Fig. 3B) were primarily related to the lower initial position of the lower mass (p2) required to fit the upper mass acceleration to the TrunkAcc. Finally, the MSD-model also kept the damping ratio (ζ) low to better fit the magnitude of the two acceleration peaks in the TrunkAcc. Decreasing the damping ratio, has however previously been shown to increase the oscillation in the model’s GRF (Alexander, Bennett & Ker, 1986; Derrick, Caldwell & Hamill, 2000), and may therefore explain why our GRF predictions to a large extent include oscillating characteristics (Fig. 3B).
The comparison between the ACCparam estimated from the TrunkAcc and the GRFparam estimated from measured GRF, clearly demonstrates that the model is unsuitable for predicting GRF from TrunkAcc. A closer look at the GRFparam, showed that the median position and velocity of the lower mass (p2 and v2) was constant across running speeds and only varied marginally within running speeds (Fig. 4C). In addition, only small differences in median damping ratios (ζ) were observed between running speeds in this study (ζ between 0.31 and 0.39 au). It was in fact kept constant (ζ = 0.35 au) in the study by Derrick, Caldwell & Hamill (2000). Based on these observations we explored the effect of keeping p2, v 2, and ζ ACCparam constant for all trials (using the median GRFparam across running speeds), and for the remaining five MSD-model parameters use the trial specific ACCparam to re-calculate the predicted GRF (Fig. S1). Whilst this decreased the variability of the GRF prediction (RMSE interquartile range) both within and across running speeds, only minor improvements were observed in the GRF prediction. This indicated that keeping selected ACCparam constant would not substantially improve the GRF prediction in future studies. Furthermore, when selected ACCparam were kept constant, their original interaction was broken.
If the trunk accelerometry data accurately represents the model’s upper mass acceleration one would at least expect that the ACCparam related to the motion and stiffness of the upper mass and spring (p1, v1, ω12) would be close to the GRFparam estimated when fitting measured GRF. This was however not the case, and therefore naturally raises the questions as to whether the upper mass acceleration is equivalent to the acceleration measured from trunk accelerometry during running. The trunk accelerometry driven MSD-model approach introduced in this study is based on the hypothesis that the model’s upper mass primarily represents the mass and motion of the trunk segment (Alexander, Bennett & Ker, 1986; Derrick, Caldwell & Hamill, 2000). Our results suggest however that this is not the case, and that independent accelerations of other body segments (e.g., the swing leg and arms) significantly contribute to the MSD-model’s upper mass accelerations. We therefore conclude that the primary model hypothesis for this study was false, and that trunk-mounted accelerometry alone is inappropriate as input for the MSD-model to predict meaningful GRF waveforms.
A high initial peak related to the attenuation of the shock impact from the foot’s collision with the ground (Hamill, Derrick & Holt, 1995; Derrick, 2004) dominated the TrunkAcc signals across running speeds. In contrast, a higher second peak related to the COM displacement during the stance phase dominated the upper mass acceleration when the MSD-model was fitted to measured GRF. This raised the technical question as to whether the poor GRF predictions observed from the measured accelerometer signal were partly a consequence of an artificially high frequency of that initial peak and whether the application of lower filter cut-off frequencies (cut-off frequencies of 20 Hz in the present study) would improve GRF predictions. To explore this, trunk accelerometry data of 10 representative participants was low-pass filtered with cut-off frequencies of 15, 10 and 5 Hz (Fig. S2). Whilst low cut-off frequencies (especially 10 and 5 Hz) to a large extent successfully removed the initial high-frequency peak in the accelerometry signal, and the RMSE between TrunkAcc and upper mass acceleration decreased, it only had a minor influence on the RMSE of the predicted GRF across running speeds (Fig. S2). Therefore, accelerometry post-processing did not improve the GRF predictions from TrunkAcc. This suggests that the trunk accelerometry signal in itself was not the main reason for the poor GRF predictions, but rather an incorrect hypothesis that the MSD-model’s upper mass acceleration primarily represents the acceleration of the trunk segment.
Replicating GRF from measured GRF
Although TrunkAcc was unsuccessful in predicting GRF during running with a simple MSD-model, the MSD-model could successfully replicate measured GRF during slow to moderate running speeds. In fact, the inclusion of all eight GRFparam in our optimisation routine, compared to only optimising the spring constants of the upper and lower springs (k1 and k2) and the position of the lower mass (p2) (Derrick, Caldwell & Hamill, 2000) allowed us to replicate the measured GRF with higher accuracy. These findings illustrate that despite the MSD-model’s simplicity it has the ability to replicate and potentially predict GRF for a range of running speeds. Since the MSD-model parameters associated with the lower mass and spring are crucial to predict GRF (Eq. 7), this may open opportunities to use segmental kinematics and/or accelerometry from lower extremities to estimate MSD-model parameters. This does however require that the lower limb accelerations measured from e.g., a tibia-mounted accelerometer are similar to the MSD-model’s lower mass acceleration required to accurately predict GRF, something which is not a given. Recent studies have for example shown promising results in predicting GRF during sprinting, in high level sprinters, when contact and flight time, in combination with kinematics from the ankle were used as input for a two-mass model (Udofa, Ryan & Weyand, 2016; Clark, Ryan & Weyand, 2017). Future studies are however still need to explore the use of body-worn micro sensor technology to drive simple human body models and predict GRF waveforms for a range of running speeds.
A limitation with the MSD-model and the associated model parameters is that multiple parameter combinations exist when fitting the MSD-model to measured TrunkAcc or GRF waveforms. Whilst it could be of interest to further explore the physical meaning of the individual model parameters (ACCparam or GRFparam) and their interactions, or within and between subject parameters variations, this was not possible due to the existence of multiple model parameter solutions. Trunk-mounted accelerometry has a major benefit that it is already in use in many field contexts, but a limitation is that it may not very well represent the acceleration of the trunk segment. We have in previous work (Nedergaard et al., 2017b) shown that vertical trunk accelerations, measured from a high-end lab-based motion capture system, improved the upper mass acceleration fitting (median RMSE: 0.03 g across all running speeds) and lowered the average median RMSE of the GRF predictions to 5.18 N kg−1 (vertical GRF) across all running speeds, compared to 8.99 N kg−1 in the current study. Importantly, the accuracy and reliability of the GRF predictions are considered poor in both cases, suggesting that our hypothesis that the MSD-model’s upper mass acceleration primarily represents the trunk acceleration is most likely the weakest link. Secondly, the MSD-model is a one-dimensional model, and therefore only allows the magnitude of the resultant GRF to be estimated. We decided to predict the magnitude of the resultant GRF in our study, considering that we wanted to estimate the overall external biomechanical loading on the body, however we accept that others may prefer to predict the magnitude of the vertical GRF only. Ultimately, we believe that it is important to recognise that the MSD-model approach omits any direction specific load variations across running speeds, and that these may well be relevant in how the musculoskeletal tissues are exposed to stresses. Finally, the MSD-model is a passive elastic model and therefore does not account for additional energy generated by the body’s “active” structures (muscles). Whilst a more complex model could account for this (Zadpoor & Nikooyan, 2010; Nikooyan & Zadpoor, 2011), it is questionable if this would allow for better GRF predictions from TrunkAcc. The complexity of such model would probably also defeat the overall purpose of using a simple model that is still applicable in field settings.
In this study, we demonstrated that the upper mass acceleration of a simple MSD-model can be fitted to measured trunk accelerometry signals with high accuracy during running at various speeds, but that the ensuing ACCparam do not deliver accurate predictions of GRF waveforms. Despite the convenient hypothesis that the MSD-model’s upper mass acceleration primarily represents the acceleration of the trunk, our results showed that this hypothesis is violated too much to still predict meaningful GRF waveforms. Nevertheless, further studies should continue to explore the use of data from wearable micro sensor technology to drive simple human body models that could allow us to estimate GRF waveforms in field settings. This would allow researchers and practitioners to better monitor the external biomechanical loads to which the human body is exposed during running locomotion, ultimately supporting a general quest towards field-based monitoring of tissue load-adaptation processes.
Effect of keeping selected model parameters static on the predicted GRF
Representative examples of a single stride of the predicted GRF for the four running speeds and boxplots displaying the RMSE median, and 25th and 75th interquartile range when selected model parameters were kept constant. The polar plots display the estimated model parameters (in unscaled values) from the representative examples. When all parameters were estimated from TrunkAcc (A), when p2 was kept constant at 0.00 m for all trials (B), when v2 was kept constant at −0.02 m s −1 (C), when both p2 and v2 were kept constant (D) and finally when p2, v2 and ζ (0.36 au) were kept constant for all trials (E). Extreme outliers were removed from the boxplots. Notice the effect of keeping v2, and both p2 and v2 constant had on the median RMSE and variation in RMSE within and across running speeds, though the predicted GRF waveforms were still unsatisfying.
Effect of filter cut-off frequency on trunk accelerometry fitting and GRF predictions
A 4th order recursive Butterworth low-pass filter with a cut-off frequency of 20 Hz (A), 15 Hz (B), 10 Hz (C) or 5 Hz (D) was applied to TrunkAcc from 10 participants (age 21 ± 2 years, height 176 ± 8 cm, mass 76 ± 10 kg) to explore the effect of filter cut-off frequency on model parameter estimation and GRF predictions. Each row display a single stride example of the TrunkAcc fitting; boxplot of the median RMSE, and 25th and 75th interquartile range of the TrunkAcc fitting; a single stride example of the predicted GRF with a polar plot of the estimated model parameters in scaled dimensionless values; and boxplot of the median RMSE, and 25th and 75th interquartile range of the predicted GRF. The example trial displayed is for a running speed of 4 m s−1. Notice how the filter cut-off frequency improved the RMSE of the TrunkAcc fitting, whilst it only had minor influence on the RMSE of the predicted GRF.