Functional electrical stimulation (FES) applies small electrical pulses to nerves that supply paralyzed muscle in order to produce muscle contractions. This method can produce therapeutically useful movements in patients with spinal cord injury who would not otherwise be able undergo these motions on their own. Osteoporosis commonly develops as a secondary complication to spinal cord injuries due to lack of exercise, and this often leads to fracture in the distal femur and proximal tibia. A recent pilot study by Gibbons et al, showed, compared to typical spinal cord patients, a single subject had substantial increases in lower limb bone mineral with long term FES rowing. Dr. Lamabch is currently conducting FES rowing study, on a larger number of participants, at the Palo Alto VA to see if the results from Gibbons et al are more universal.1 The goal of this project is to develop a simple model of a FES rower with a realistic rowing stroke, and use that model to estimate the bone on bone forces at the knee. This will help gain insight into the utility of FES rowing as a way to apply reasonable joint loads and minimize bone loss.
We built and used a simple 1-DOF, planar, 4-body model consisting of a pelvis/HAT, thigh, shank, and foot segment. The model represents the rower in a seated position on the rowing machine, with the seat moving forward or backward along the track and the foot strapped to a platform. A schematic of the system is shown below.
1) Simulate a rowing stroke with a simple 1-DoF model
2) Use a forward simulation to estimate the bone-on-bone forces at the knee to help us answer the following question:
We began by building a rowing model from scratch in C++ as well as stripping down the 10 DOF and 8 muscle model in OpenSim. Building two models from different approaches allowed us to compare results while were constructing our rowing model. At each step, we stopped and compared the joint angles at the hip, knee and angle during a forward dynamic simulation to make sure the two models were the same.
First, we built a simple rigid body model consisting of a pelvis, thigh, shank, foot, and HAT segment. We added a slider joint to connect the pelvis to the ground (and constrain it to move in the x-direction), as well as pin joints at the hip, knee, and ankle. We grouped the two legs together as one, doubling the mass and moment of inertias, and placed it at the center of the pelvis. We then ran a forward dynamic simulation on the model under only the force of gravity.
Next, we constrained the foot such that it would remain stationary throughout the motion, just as the feet remain in the pedal straps on a rowing machine. We placed the foot about 12cm below the pelvis based on a realistic rowing position and ran a forward simulation.
We then added the forces to the model. To account for resistance that the rower experiences throughout the rowing motion, we applied a constant force in the positive x direction. Although this represents the handle force, we applied the force at the pelvis. As the torso is welded to the pelvis, this is equivalent. We applied a force of 150 N based on experimentally obtained power measurements of 50W, and estimates that the pelvis displacement would be 1 m over 3 s.
Next, we added the muscles to our model. Because only the hamstrings and quadriceps are stimulated during FES rowing, we added the hamstrings, rectus femoris, and vasti to the model. We took muscle parameters from the existing 10DOF/18 muscle model, doubling the maximum isometric force to account for both legs. The results from the forward simulation are shown below.
Through trial and error, we found an excitation pattern that resembled a realistic rowing motion. During FES rowing, patients press a button to either stimulate the hamstrings or the quadriceps. The device therefore acts as a switch, with either the hamstrings or quadriceps (in our model, the rectus femoris and vasti) excited at any given point in time. To generate a motion, we simply had to decide where to switch the excitation from quadriceps to hamstrings as the model varies the degree of knee flexion. The excitation pattern below was the one that worked with the pin knee joint, but was producing high knee loads compared to the Gibbons study.
We updated the excitation pattern as we attempted to validate the model.
It was important that our model stayed within the tested joint ranges and kept the muscle fiber lengths within the active portion of the force-length curve. To satisfy the first condition, we lowered the feet and tilted the pelvis. We tired a couple different pelvic tilt angles and ultimately settled on 45 degrees because that gave us realistic fiber lengths and was a reasonable pelvic tilt. In addition, we lengthened the hamstrings and rectus femoris to account for the leg being shifted in the middle of the pelvis instead of its normal position.
To evaluate the second condition, we plotted the normalized fiber length through the knee flexion range while the hip was both maximally extended and maximally flexed (within the tested range). The curves are different for different initial position because OpenSim varies the knee angle without taking into account the constraints we set. But in any case, the curves are within the active portion of the force length curve, and therefore the passive forces are not predominant. The hamstrings are especially tight, and the rectus femoris loose: they are not working in the optimal range because of the seated position, which is what we expected.
With our first model we had a discontinuity in our results and hypothesized that there was a wrapping point issue because the muscle was cutting through the knee bone. This was coming from the fact that we centered our unique leg compared to the pelvis, whereas the insertion points on the hip of the rectus femoris and the hamstrings stayed the same.
This was the motion of our rower with the pin joint knee.
We then replaced our pin joint knee with the more anatomically correct knee model from the 10 DOF model and this eliminated the discontinuity in the knee joint forces.
Up to now, we modeled the handle force as constant throughout the cycle. However, an ergometer has a flywheel incorporated in it, so that pulling the handle is hard whereas pushing it back doesn't require force. Thus, we wanted to create a cyclic force, equal to 150N throughout the extension phase and 0 when the rower crunches back.
To create such a step function, we only need 4 points. However, Opensim automatically filters this external load signal and returns huge oscillations:
Adding more data points helps to a certain degree. We still end up with overshoots / undershoots, which are characteristic of a Lagrange interpolation. For an interval of 21 data points, the sweet spot seemed to be one point every 0.05 s.
Another challenge we encountered was that a big part of the extension phase was undertaken with the hamstrings activated. This seems counter-intuitive but was made possible by the momentum gained thanks to quads activation and by the fact that the hamstring is a hip extensor (which, because our model has only one DoF extends the knee). The quadriceps were finally active only 0.15 s out of the 1s that took the entire movement. This wasn't corresponding to reality, as the rower activates the hamstrings once he is extended and the hamstrings excitation constitutes around 2/3 of the cycle length.
We decided to add another hamstring muscle, the biceps femoris short head. This muscle only crosses the knee so its activation will help stop the extension and bring back the rower. We found that is effect was not predominant (its optimal force is 3 times smaller than the long head and his fiber length is in the short range in this position). But adding it definitely helped activate the quads longer without hyperextending the knee.
The quads activation process was still too fast compared to reality. Indeed, the forces are high, the vasti having an optimal fiber force of 10,000N. Therefore, we decided to lower the activation: 0.3 for the quadriceps muscles and 0.6 for the hamstrings muscle. In this configuration, the sum of the optimal forces of the 2 muscles of the quadriceps is the same than the one of the 2 muscles of the hamstrings. We also obtain a realistic cycle duration of 1s, with 40% of the time activation of the quads.
The final handle force was:
and the excitation pattern:
A forward dynamic simulation produced the following motion:
and the following knee loads for one cycle:
These loads are to be compared with the experiment done in the pilot study by Gibbons et al. We obtain a knee load magnitude of almost 4,000N, which, for our 60kg model, represents 3.3 body weights on each knee.
We feel that modeling the muscles of the calf, and thus improving the accuracy of the model, could play a role in the knee loads. Indeed, even without being activated, those muscles produce passive forces as they are stretched, thus loading the joint.
Another axle of study could also investigate the effect of activating the calf muscles instead of the thigh muscles on knee loads and bone density.
You can download our model here.
We used the following excitation pattern. The external force is decribed by this .xml file and this .mot file.
We would like to thank Scott Delp and the entire ME 485 teaching team, especially to Calvin Kuo for all the help and guidance with our model.
1. Gibbons, RS., McCarty, ID., Gall, A., Stock, CG., Shipppen, J., Adrews, BJ. Can FES-rowing mediate bone mineral density in SCI: a pilot study. Spinal Cord. 52, S4-S5 (2014).
Home: BIOE-ME 485 Spring 2017