Abstract
Among the infinite number of possible movements that can be produced, humans are commonly assumed to choose those that optimize criteria such as minimizing movement time, subject to certain movement constraints like signaldependent and constant motor noise. While so far these assumptions have only been evaluated for simplified pointmass or planar models, we address the question of whether they can predict reaching movements in a full skeletal model of the human upper extremity. We learn a control policy using a motor babbling approach as implemented in reinforcement learning, using aimed movements of the tip of the right index finger towards randomly placed 3D targets of varying size. We use a stateoftheart biomechanical model, which includes seven actuated degrees of freedom. To deal with the curse of dimensionality, we use a simplified secondorder muscle model, acting at each degree of freedom instead of individual muscles. The results confirm that the assumptions of signaldependent and constant motor noise, together with the objective of movement time minimization, are sufficient for a stateoftheart skeletal model of the human upper extremity to reproduce complex phenomena of human movement, in particular Fitts’ Law and the \(\frac{2}{3}\) Power Law. This result supports the notion that control of the complex human biomechanical system can plausibly be determined by a set of simple assumptions and can easily be learned.
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Introduction
In the case of simple endeffector models, both Fitts’ Law and the \(\frac{2}{3}\) Power Law have been shown to constitute a direct consequence of minimizing movement time, under signaldependent and constant motor noise^{1,2}. Here, we aim to confirm that these simple assumptions are also sufficient for a full skeletal upper extremity model to reproduce these phenomena of human movement. As a biomechanical model of the human upper extremity, we use the skeletal structure of the Upper Extremity Dynamic Model by Saul et al.^{3}, including thorax, right clavicle, scapula, shoulder, arm, and hand. The model has seven actuated degrees of freedom (DOFs): shoulder rotation, elevation and elevation plane, elbow flexion, forearm rotation, and wrist flexion and deviation. While the thorax is fixed in space, the right upper extremity can move freely by actuating these DOFs. To deal with the curse of dimensionality and make the control problem tractable, following van Beers et al.^{4}, we use a simplified secondorder muscle model acting at each DOF instead of individual muscles. These secondorder dynamics map an action vector obtained from the learned policy to the resulting activations for each DOF. Following van Beers et al.^{4}, we assume both signaldependent and constant motor noise in the control, with noise levels 0.103 and 0.185, respectively. Multiplying these activations with constant moment arm scaling factors, which represent the strength of the muscle groups at the respective DOFs, yields the torques that are applied at each DOF independently. Further details on the biomechanical model are provided in the Methods section below.
The Upper Extremity Dynamic Model is significantly more complex than standard pointmass or linkedsegment models. In particular, there is no explicit formula for the nonlinear and nondeterministic system dynamics. Together with the objective of movement time minimization, these properties make it difficult to use classical optimal control approaches. Instead, in this paper we learn a control policy using deep reinforcement learning (RL). RL algorithms, just like the optimal control methods discussed below, aim to find a policy that maximizes a given reward function. Moreover, they do not require any explicit knowledge about the underlying model. Instead, the optimal value of a certain state is estimated from sampling different actions in the environment and observing the subsequent state and obtained reward^{5}.
In our approach, a control policy initially generates random movements, which are rewarded with the negative time to reach randomly placed 3D targets of varying size, with the right index finger (see Fig. 1). This reward signal implies movement time minimization for aimed movements. The policy is updated using the softactorcritic algorithm (SAC)^{6}. The actor and critic networks both consist of two fully connected layers with 256 neurons each, followed by the output layer, which either returns the means and standard deviations of the action distributions (for the actor network) or the stateaction value (for the critic network). Further information about the network architecture and a detailed description of all state components can be found in the Methods section below. To make reinforcement learning computationally feasible within a reasonable time period, a fast physics simulation is advantageous. Accordingly, we implemented the biomechanical model in MuJoCo^{7}.
It is important to note in this context that the assumption of minimizing total movement time does not provide any gradient information to the reinforcement learner. In particular, it is not possible to distinguish beneficial states and actions from inappropriate ones before the target has been reached, which terminates the episode and thus increases the total return. This, together with the fairly small subspace of appropriate actions relative to the number of possible control vectors, makes it very difficult to obtain a reasonable policy without additional aid. For this reason, we created an adaptive curriculum, which dynamically decreases the target diameter from 60 cm to less than 2 cm during training. This has proven to be both effective (targets with diameter around 2 cm are consistently reached by the final policy) and efficient (this minimum width was reached after 1.2M steps, while various predetermined curricula required more than 3M steps).
Related work
The question of how human arm movements are internally planned and controlled has received significant attention in the literature. Important phenomena that emerge from human arm movements include Fitts’ Law and the \(\frac{2}{3}\) Power Law. In this section we review related work in these areas.
Motor control
Many models of human motor control assume that some objective function is optimized during the planning of the movement. A variety of objective functions have been proposed, including minimization of either jerk^{8,9}, peak acceleration^{10}, endpoint variance^{1}, duration^{2,11}, or torquechange^{12}. Moreover, combined objective functions have been used to model a tradeoff between different objectives, e.g., between accuracy and effort^{13,14}, or jerk and movement time^{15}. Extensions have been proposed that, e.g., focus on initial gating mechanisms^{16} or motor synergies representing agonist and antagonist muscle groups^{17}.
While most of these models imply a separation between the planning and the execution stage, the optimal feedback control theory^{18,19,20,21,22} assumes that sensory signals about the controlled quantity are fed back to the controller. These observations are then directly used to compute the remaining optimal control signals, resulting in a feedback loop. Extensions to infinitehorizon problems^{23}, which yield the optimal steadystate solution at the expense of neglecting transient behavior, and explicit nonlinear time costs^{24,25} have been proposed.
While many early works in motor control have modeled the biomechanics as pointmass models with linear dynamics^{1,13} or linkedsegment models^{1}, there is a growing interest in biomechanical models of increasing realism and fidelity. This is spurred by advances in biomechanical modeling^{3,26,27} and simulation^{28,29}. Biomechanical models allow control beyond the endeffector, for example on the level of joints^{12,30,31,32,33,34,35}, or muscles^{36,37,38,39}.
Jointactuated models apply different optimality criteria for movement generation and coordination, minimizing, e.g., the angular accelerations with constraints^{40}, angular jerk^{30}, torquechange^{12,31}, mechanical energy expenditure^{41}, a combination of absolute work and angular acceleration^{35}, or some combination of accuracy and effort costs in the context of optimal feedback control^{14}. The biomechanical plant in these works is usually represented as a linkedsegment model, with simplified kinematic properties. In particular, the shoulder joint is commonly described as a rotationonly joint, ignoring the translatory part as well as complex movements related to the scapula and clavicle. Some of these models also include simplified muscles with simplified biomechanical attachment^{14}.
More recently, more complex, highfidelity biomechanical musculoskeletal models have been introduced^{36,37,42,43}, where the control is musclebased. In these models, the computation of the control values is commonly based on neural networks, particularly on deep learning and reinforcement learning. These methods have been applied successfully to predict coordinated muscle activations for multijoint arm^{42}, lower body^{43}, and full body^{36} movements. Moreover, a combination of 20 neural networks, each designed to imitate some specific part of the sensorimotor system, has recently been used to synthesize movements for such diverse sensorimotor tasks as reaching, writing, and drawing^{37}. To make the control of musclebased models feasible, these works apply multiple simplifications to the full biomechanical model, such as reducing or immobilising degrees of freedom^{37,42} or even completely locking the movement to two dimensions^{43}, ignoring tendon’s elasticity^{36,37}, limiting maximum passive forces^{36}, ignoring the muscle activation dynamics^{36,37} or significantly reducing the number of independently controlled muscles^{42,43}. Also, the control learning strategies differ from the pure reinforcement learning approach by applying imitation learning^{36,37}, or using artificial training data with simplified dynamics^{37}.
Up to now, these models have not been evaluated regarding the realism of the movements generated, in particular whether they exhibit features characteristic of human movements, such as Fitts’ Law and the \(\frac{2}{3}\) Power Law^{34,36,37}.
Fitts’ law
Fitts’ Law^{44} describes the speedaccuracy tradeoff of aimed movements towards a spatially defined target. Given the distance D between the initial position of the controlled endeffector (e.g., the hand or the finger) and the desired target position, and given the width W of the target, this law claims a logarithmic relationship between the distancewidth ratio \(\frac{D}{W}\) and the resulting movement time MT:
where we used the Shannon formulation^{45}. Most works that explored possible explanations for the emergence of Fitts’ Law have postulated that it results from noise in motor control. Crossman and Goodeve^{46} showed that Fitts’ Law emerges from the assumptions of isochronal submovements towards the target and constant errorvelocity ratio. Meyer et al.^{47} demonstrated that a power form of Fitts’ Law emerges from the optimization of the relative duration of two submovements in order to achieve minimal movement time, assuming that the standard deviation of submovement endpoints increases proportionally with movement velocity. Fitts’ Law has also been derived within the infinitehorizon optimal control framework, assuming that the target is reached as soon as the positional endeffector variance relative to the target center falls below the desired target accuracy^{23}.
Harris and Wolpert^{1} proposed that the central nervous system (CNS) aims to minimize movement endpoint variance given a fixed movement time, under the constraint of signaldependent noise. This signaldependent noise is assumed to be the main factor determining the endpoint accuracy: Faster movements can be achieved through applying larger control signals (in the extreme, this leads to the timeminimizing Bangbang control), but only at the costs of larger deviations, which in turn induce a larger endpoint variance and thus a greater risk of missing the target. This tradeoff has a strong neuroscientific evidence^{48} and is consistent with the speedaccuracy tradeoff proposed by Fitts’ Law^{1,2}. Moreover, in the case of armreaching movements, it has been shown recently that the assumptions of feedforward control and signaldependent noise (using dynamics of a twolink planar arm model) directly imply Fitts’ Law, with coefficients a and b related to the level of signaldependent noise^{49} . Both coefficients were also shown to depend on the dynamics and kinematics, e.g., on the viscosity, or the Jacobian matrix relating the joint space and the endeffector space.
\(\frac{2}{3}\) Power law
Continuous, rhythmic movements such as drawing or handwriting, exhibit a speedcurvature tradeoff described by the \(\frac{2}{3}\) Power Law^{50}. This law proposes a nonlinear relationship between the radius of curvature \(\rho _{n}\) and the corresponding tangential velocity \(v_{n}\),
where the parameter k determines the velocity gain. This particularly implies that higher curvature leads to lower velocity. It has also been demonstrated that the \(\frac{2}{3}\) Power Law is equivalent to constant affine velocity^{51}.
The \(\frac{2}{3}\) Power Law has been confirmed to hold for a variety of task conditions, including hand movement^{52}, eye movement^{53}, perceptuomotor tasks^{54,55}, and locomotion^{56}. Moreover, it has been shown to apply under the assumption of signaldependent noise^{1}. Schaal and Sternad^{57} observed that the perimeter of the ellipse has a large impact on the validity of this law, with \(\beta\) obtained from a nonlinear regression showing deviations in the order of 30–40% for large ellipses (or, alternatively, with decreasing coefficient of determination \(R^{2}\), i.e., decreasing reliability of the parameter fitting). Based on these observations, Schaal and Sternad argue that the \(\frac{2}{3}\) Power Law cannot be an intrinsic part of the movement planning procedure, but rather occurs as a “byproduct” from the generation of smooth trajectories in intrinsic joint space^{57} Following this argumentation, the nonlinearities arising from the transformation from joint space to endeffector space, i.e., from a nontrivial kinematic chain, may account for scale and directiondependent results. Other theories see the cause of the wide applicability of the \(\frac{2}{3}\) Power Law either in trajectory planning processes such as motor imagery^{58} or jerk minimization^{59}, or directly emerging from muscle properties^{60} or population vectors in motor cortical areas in the CNS^{61,62}.
Results
Fitts’ law
In order to evaluate the trajectories resulting from our final policy for different target conditions, we designed a discrete Fitts’ Law type task. The task follows the ISO 92419 ergonomics standard and incorporates 13 equidistant targets arranged in a circle at 50 cm distance in front of the body and placed 10 cm to the right of the right shoulder (Fig. 2). The objective is for the endeffector to reach each target and to remain inside the target for 100 ms. In this case we deem the movement successful. Although not included in the training phase, remaining inside the target seemed to be unproblematic during evaluation. If either the movement was successful, or 1.5 s have passed, the next target is given to the learned policy.
The Index of Difficulty (ID) of the tasks ranges from 1 to 4, where ID is computed as \(\log _2(D/W+1)\). D denotes the distance between the initial and target position, and W is the target size. We execute 50 movements for each task condition and each direction, i.e., 6500 movements in total—all were successful.
Using the trajectories from this discrete pointing task, we evaluate whether the synthesized movements follow Fitts’ Law^{44}, i.e., whether there is a linear relationship between task difficulty (ID) and the required movement time. Figure 2c shows the total duration for each movement sorted by ID. The median movement times for each ID (green lines) are approximated by a linear function (red line, with coefficient of determination \(R^{2}=0.9986\)).
\(\frac{2}{3}\) Power law
We evaluate whether our model exhibits the \(\frac{2}{3}\) Power Law using an elliptic viapoint task. To this end, we define an ellipse in 2D space (55 cm in front, 10 cm above, and 10 cm to the right of the shoulder) that lies completely within the area used for target sampling during training (ellipse radii are 7.5 cm (horizontal) and 3 cm (vertical)). Using the viapoint method described in the Methods section below, our learned policy needs to trace the ellipse for 60 s as fast as possible . As shown in Fig. 3a, the simulation trajectories deviate from the desired ellipse, with the lowerright segment being flattened. Using these trajectories, we compute \(\rho _{n}\) and \(v_{n}\) for all time steps sampled at a rate of 100 Hz and then perform a loglog regression on the resulting values. This yields the optimal parameter values \(\beta =0.65\) and \(k=0.54\) (with correlation coefficient \(R=0.84\)). Thus, the \(\frac{2}{3}\) Power Law accounts for \(71\%\) of the variance observed in elliptic movements (\(R^{2}=0.71\)). Both the data points and the linear approximation in loglog space are shown in Fig. 3b.
Movement trajectories
In addition to Fitts’ Law and the \(\frac{2}{3}\) Power Law, we qualitatively analyze the movement trajectories generated by the model. Figures 4 and 5 show the position, velocity, and acceleration time series, as well as 3D movement path, Phasespace, and Hooke plots for multiple movements from the Fitts’ Law type task for two representative task conditions (ID 4 respective ID 2, each with a 35 cm distance between targets) and one representative movement direction (between targets 7 and 8 shown in Fig. 2a). Apart from the 3D movement path, all plots show centroid projections of the respective trajectory onto the vector between the initial and target positions.
The movements exhibit typical features of human aimed movements, such as symmetric bellshaped velocity profiles^{63}. Movements are smooth, and gently accelerate and decelerate, as evident in the acceleration profiles and Hooke plots in Figs. 4 and 5. For high ID (Fig. 4), movements exhibit an initial rapid movement towards the target, followed by an extended phase of corrective movements. For low ID (Fig. 5), the phase of corrective movements is generally shorter.
Movement trajectories towards the target are slightly curved and some of them exhibit pronounced correctional submovements at the end (see, e.g., Supplementary Fig. S1 and S2 online). The betweenmovement variability within one movement direction and task condition decreases with increasing ID. In particular, very simple ID 1 movements exhibit a large variability and are most prone to outliers (see, e.g., Supplementary Fig. S3 online).
For a few movement directions (mostly in ID 2 tasks), the corresponding plots seem to incorporate two different trajectory types (see, e.g., Supplementary Fig. S6 online): While some movements start with zero or even a negative acceleration and show a typical Nshaped acceleration profile, others exhibit a positive acceleration at the beginning, and their first peak is less pronounced. The reason for this behavior is corrective submovements at the end of the previous movement (see, e.g., Supplementary Fig. S4 and S5 online), leading to a different initial acceleration at the beginning of the subsequent movement. Apart from these notable features, almost all movements exhibit bellshaped velocity and Nshaped acceleration profiles, as is typical for pointing tasks^{63,64}.
Discussion
Our results indicate that, under the assumption of movement time minimization given signaldependent and constant motor noise, movement of the human upper extremity model produced by reinforcement learning follows both Fitts’ Law and the \(\frac{2}{3}\) Power Law. The movement times of aimed movements produced by the model depend linearly on the Index of Difficulty of the movement. For elliptic movements, the logarithm of the velocity of the endeffector correlates with the logarithm of the radius of curvature^{65} The optimal \(\beta =0.65\) obtained from loglog regression matches the proposed value of \(\frac{2}{3}\), with a correlation coefficient of \(R=0.84\), which is consistent with previous observations, as the required ellipse has moderate size^{57}. Finally, the generated trajectories exhibit features that are typical for human arm movements, such as bellshaped velocity and Nshaped acceleration profiles.
The results confirm previous findings that demonstrated these phenomena in simpler models of the human biomechanics. In particular, the emergence of Fitts’ Law and the \(\frac{2}{3}\) Power Law from the assumption of signaldependent noise has been demonstrated in the case of pointmass and linkedsegment models of the human arm^{1,2,49}. Our results support that insight by showing that Fitts’ Law and the \(\frac{2}{3}\) Power Law also emerge from those normative principles in a stateoftheart biomechanical model of the human arm with simplified actuation.
In addition, we want to emphasize that the control signals that drive this model were obtained from RL methods. The fact that Fitts’ Law and the \(\frac{2}{3}\) Power Law hold for the generated trajectories provides evidence that behavior abiding these established laws of human motion can be generated using jointactuated biomechanical models controlled by reinforcement learning algorithms. To the best of our knowledge, this has not yet been shown for stateoftheart biomechanical models.
One limitation of our approach is the implicit assumption of perfect observability, as all state information (joint angles, endeffector position, etc.) are immediately available to the controller, without any disturbing noise. In the future, it will be interesting to combine stateofthe art models of sensory perception with the presented RLbased motor control approach. Promising approaches to address this problem include the usage of recurrent networks^{66,67} and the internal formation of “beliefs”, given the latest (imperfect) observations^{68}.
Another limitation is the usage of simplified muscle dynamics due to the curse of dimensionality. However, recent applications of deep learning methods, which approximate complex statedependent torque limits^{69} or muscle activation signals^{37} using synthesized training data, raise hope for future approaches that efficiently combine RL or optimal control methods with stateoftheart muscle models. It will be interesting to see whether wellestablished regularities such as Fitts’ Law or the \(\frac{2}{3}\) Power Law also emerge from such models.
Methods
Below, we first provide details on our biomechanical model. After discussing our general reinforcement learning approach, we focus on the individual components of our method, namely states, actions, scaling factors, rewards, and an adaptive targetselection mechanism. We also provide details on the implementation of our algorithm. Finally, we discuss the methods used for evaluation.
Biomechanical model of the human upper extremity
Our biomechanical model of the human upper extremity is based on the Upper Extremity Dynamic model^{3}, which was originally implemented in OpenSim^{28}. Kinematically, the model represents the human shoulder and arm, using seven physical bodies and five ”phantom” bodies to model the complex movement of the shoulder. This corresponds to three joints (shoulder, elbow, and wrist) with seven DOFs and five additional joints with thirteen associated components coupled by thirteen constraints with the DOFs. Each DOF has constrained joint ranges (see Table 1), which limits the possible movements. In contrast to linkedsegment models, the Upper Extremity Dynamic model represents both translational and rotatory components of the movement within shoulder, clavicle, and scapula, and also within the wrist. It also contains physiological joint axis orientations instead of the perpendicular orientations in linkedsegment models. The dynamics components of the musculoskeletal model are represented by the weight and inertia matrix of each nonphantom body and the default negligible masses and inertia of all phantom bodies. The dynamics properties of the model were extracted from various previously published works on human and cadaveric studies. The active components of the Upper Extremity Dynamic Model consist of thirtyone Hilltype muscles as well as of fourteen coordinate limit forces softly generated by the ligaments when a DOF approaches the angle range limit. Further details of this model are given in Saul et al.^{3}
In order to make reinforcement learning feasible, we manually implement the Upper Extremity Dynamic Model in the fast MuJoCo physics simulation^{7}. With respect to kinematics, the MuJoCo implementation of the model is equivalent to the original OpenSim model and contains physiologically accurate degrees of freedom, as well as corresponding constraints. We assume the same physiological masses and inertial properties of individual segments as in the OpenSim model. We do not implement muscles in the MuJoCo model, as this would significantly slow down the simulation and make reinforcement learning computationally infeasible due to the exponential growth of decision variables in the (discretized) action space when increasing the number of DOFs – the curse of dimensionality. In particular, computing dynamic actuator lengths (which significantly affect the forces produced by muscle activation patterns) has proven challenging in MuJoCo^{70}. Instead, we implement simplified actuators, representing aggregated muscle actions on each individual DOF, which are controlled using the secondorder dynamics introduced by van der Helm et al.^{71} with fixed excitation and activation time constants \(t_{e}=30\) ms and \(t_{a}=40\) ms, respectively. We discretize the continuous state space system using the forward Euler method, which yields the following dynamics:
where \(c_{n}^{(q)}\) is the applied control and \(\sigma _{n}^{(q)}\) the resulting activation for each DOF \(q\in \mathcal {Q}\), and \(\mathcal {Q}\) is the set that contains all DOFs. The controls are updated every \(\Delta t\)=10 ms, at time steps \(n\in \{0, \dots , N1\}\). To get more accurate results, at each time step n, we compute five substeps (during which the control \(c_{n}^{(q)}\) is constant) with a sampling time of 2 ms to arrive at time step \(n+1\).
We assume both signaldependent and constant noise in the control, i.e.,
where \(a_{n}=(a_{n}^{(q)})_{q\in \mathcal {Q}}\) denotes the action vector obtained from the learned policy, and \(\eta _{n}\) and \(\epsilon _{n}\) are Gaussian random variables with zero mean and standard deviations of 0.103 and 0.185, respectively, as described by van Beers et al.^{4} The torques, which are applied at each DOF independently, are obtained by multiplying the respective activation \(\sigma _{n}^{(q)}\) with a constant scaling factor \(g^{(q)}\), which represents the strength of the muscle groups at the this DOF, i.e.,
We select the scaling factors, and respectively the maximum voluntary torques for the actuators given in Table 1, based on experimental data as described below. We currently do not model the soft joint ranges in MuJoCo, as the movements the model produces do not usually reach joint limits.
The used biomechanical model provides the following advantages over simple linkedsegment models:

Phantom bodies and joints allow for more realistic movements, including both translation and rotation components within an individual joint,

Individual joint angle and torque limits are set for each and every DOF,

Axes between joints are chosen specifically and not just perpendicular between two segments,

The model includes physiological body segment masses, and yields better options for scaling individual body parts, e.g., based on particular individuals.
Reinforcement learning
We define the task of controlling the biomechanical model of the human upper extremity through motor control signals applied at the joints as a reinforcement learning problem, similar to recent work from Cheema et al.^{34} In this formulation, a policy \(\pi _\theta (as)\) models the conditional distribution over actions \(a \in \mathcal {A}\) (motor control signals applied at the individual DOFs) given the state \(s \in \mathcal {S}\) (the pose, velocities, distance to target, etc.). The subindex \(\theta\) denotes the parameters of the neural networks introduced below. At each timestep \(n\in \{0, \dots , N\}\), we observe the current state \(s_n\), and sample a new action \(a_n\) from the current policy \(\pi _\theta\). The physical effects of that action, i.e., the application of these motor control signals, constitute the new state \(s_{n+1}\), which we obtain from our biomechanical simulation. In our model, given \(s_{n}\) and \(a_{n}\), the next state \(s_{n+1}\) is not deterministic, since both signaldependent and constant noise are included. Hence, we denote the probability of reaching some subsequent state \(s_{n+1}\) given \(s_{n}\) and \(a_{n}\) by \(p(s_{n+1}s_{n}, a_{n})\), while \(p(s_0)\) denotes the probability of starting in \(s_0\). Given some policy \(\pi _{\theta }\) and a trajectory \(T=(s_0, a_0, \dots , a_{N1}, s_N)\),
describes the probability of realizing that trajectory. Evaluating/Sampling equation (7) for all possible trajectories \(T\in \mathcal {T}\) then yields the distribution over all possible trajectories, \(\varrho _\theta ^{\mathcal {T}}\), induced by a policy \(\pi _{\theta }\).
We compute a reward \(r_n\) at each time step n, which allows us to penalize the total time needed to reach a given target. The total return of a trajectory is given by the sum of the (discounted) rewards \(\sum _{n=0}^{N}\gamma ^n r_n\), where \({\gamma \in ]0,1]}\) is a discount factor that causes the learner to prefer earlier rewards to later ones. Incorporating the entropy term,
yields the expected (soft) return
which we want to maximize with respect to the parameters \(\theta\), i.e., the goal is to identify the optimal parameters \(\theta ^*\) that maximize \(J(\theta )\). Here, the temperature parameter \(\alpha > 0\) determines the importance of assigning the same probability to all actions that yield the same return (enforced by maximizing the entropy \(\mathcal {H}\)), i.e., increasing the “stochasticity” of the policy \(\pi _{\theta }\), relative to maximizing the expected total return. It thus significantly affects the optimal policy, and finding an “appropriate” value is nontrivial and heavily depends on the magnitude of the rewards \(r_{n}\). For this reason, we decided to adjust it automatically during training together with the parameters \(\theta\), using dual gradient descent as implemented in the softactor critic algorithm (see below)^{6}.
It is important to note that the soft return in Equation (9) is different from the objective function used in standard reinforcement learning. The MaxEnt RL formulation, which incorporates an additional entropy maximization term, provides several technical advantages. These include the natural statespace exploration^{72,73}, a smoother optimization landscape that eases convergence towards the global optimum^{74,75,76}, and increased robustness to changes in the reward function^{77,78}. In practice, many RL algorithms have gained increased stability from the additional entropy maximization^{79,80,81}. Conceptually, MaxEnt RL can be considered equivalent to probabilistic matching, which has been used to explain human decision making^{82,83}. Existing evidence indicates that human adults tend to apply probabilistic matching methods rather than pure maximization strategies^{82,84,85}. However, these observations still lack conclusive neuroscientific explanation^{80}.
In order to approximate the optimal parameters \(\theta ^*\), we use a policygradient approach, which iteratively refines the parameters \(\theta\) in the direction of increasing rewards. Reinforcement learning methods that are based on fully sampled trajectories usually suffer from updates with high variance. To reduce this variance and thus accelerate the learning process, we choose an approach that includes two approximators: an actor network and a critic network. These work as follows. Given some state \(s_0\) as input, the actor network outputs the (standardized) mean and standard deviation of as many normal distributions as dimensions of the action space. The individual action components are then sampled from these distributions. To update the actor network weights, we must measure the “desirability” of some action a, given some state s, i.e., how much reward can be expected when starting in this state with this action and subsequently following the current policy. These values are approximated by the critic network.
The architecture of both networks is depicted in Fig. 6. For the sake of a simpler notation, the parameter vector \(\theta\) contains the weights of both networks, however these weights are not shared between the two. These two networks are then coupled with the soft actorcritic (SAC) algorithm^{6}, which has been used successfully in physicsbased character motion^{86}: As a policygradient method, it can be easily used with a continuous action space such as continuous motor signals – something that is not directly possible with value function methods like DQN^{5}. As an offpolicy method that makes use of a replay buffer, it is quite sampleefficient. This is important, since running forward physics simulations in MuJoCo constitutes the major part of the training duration. Moreover, it has been shown that SAC outperforms other stateoftheart algorithms such as PPO^{87} or TD3^{88}. Supporting the observations in Haarnoja et al.^{6}, we also found our training process to be faster and more robust when using SAC rather than PPO. Moreover, SAC incorporates an automatic adaption of the temperature \(\alpha\) using dual gradient descent, which eliminates the need for manual, taskdependent finetuning. In order to obtain an unbiased estimate of the optimal value function, we use Double QLearning^{89}, using a separate target critic network. The neural network parameters are optimized with the Adam optimizer^{90}.
States, actions, and scaling factors
Using the MuJoCo implementation of the biomechanical model described above, the states \(s\in \mathcal {S}\subseteq \mathbb {R}^{48}\) in our RL approach include the following information:

Joint angle for each DOF \(q \in \mathcal {Q}\) in radians (7 values),

Joint velocity for each DOF \(q \in \mathcal {Q}\) in radians/s (7 values),

Activations \(\sigma ^{(q)}\) and excitations \(\dot{\sigma }^{(q)}\) for each DOF \(q \in \mathcal {Q}\) (\(2\times 7\) values),

Positions of the endeffector and target sphere (\(2\times 3\) values),

(positional) Velocities of the endeffector and target sphere (\(2\times 3\) values),

(positional) Acceleration of the endeffector (3 values),

Difference vector: vector between the endeffector attached to the index finger and the target, pointing towards the target (3 values),

Projection of the endeffector velocity towards the target (1 value),

Radius of the target sphere (1 value).
We found that in our case, the target velocity (which always equals zero for the considered tasks), the endeffector acceleration, the difference vector, and the projection of the endeffector velocity can be omitted from state space without reducing the quality of the resulting policy. However, we decided to incorporate these observations, as they did not considerably slow down training and might be beneficial for more complex tasks such as target tracking or viapoint tasks.
Each component \(a^{(q)}\in \left[ 1,1\right]\) of the action vector \(a=(a^{(q)})_{q\in \mathcal {Q}}\in \mathcal {A}\) \(\subseteq \mathbb {R}^{7}\) is used to actuate some DOF \(q\in \mathcal {Q}\) by applying the torque \(\tau ^{(q)}\) resulting from Eqs. (4)–(6). Note that in addition to these actuated forces, additional active forces (e.g., torques applied to parent joints) and passive forces (e.g., gravitational and contact forces) act on the joints in each time step.
We determine experimentally the maximum torque a human would exert at each DOF in this task as follows. We implemented the Fitts’ Law task described above in a VR environment displayed via the HTC Vive Pro VR headset. We recorded the movements of a single participant performing the task, using the Phasespace X2E motion capture system with a fullbody suit provided with 14 optical markers. This study was granted ethical approval by the ethics committee of the University of Bayreuth and followed ethical standards according to the Helsinki Declaration. Written informed consent was received from the participant, which received an economic compensation for participating in the study. Using OpenSim, we scaled the Upper Extremity Dynamic Model to this particular person. We then used OpenSim to perform Inverse Dynamics to obtain the torque sequences that are most likely to produce the recorded marker trajectories. For each DOF \(q \in \mathcal {Q}\), we set the corresponding scaling factor \(g^{(q)}\) to the absolute maximum torque applied at this DOF during the experiment, omitting a small number of outliers from the set of torques, i.e., values with a distance to mean larger than 20 times the standard deviation. The resulting values are shown in Table 1.
Reward function and curriculum learning
The behavior of the policy is determined largely by the reward \(r_n\) that appears in Eq. (9). We designed the reward following Harris and Wolpert^{1}, who argue that there is no rational explanation as to why the central nervous system (CNS) should explicitly try to minimize previously proposed metrics such as the change in torque applied at the joints^{12}, or the acceleration (or jerk) of the endeffector^{8}. They argue that it is not even clear whether the CNS is able to compute, store, and integrate these quantities while executing motions.
Instead, they argue that the CNS aims to minimize movement endpoint variance given a fixed movement time, under the constraint of signaldependent noise. Following Harris and Wolpert^{1}, t his is equivalent to minimizing movement time when the permissible endpoint variance is given by the size of the target. This objective is simple and intuitively plausible, since achieving accurate aimed movements in minimal time is critical for the success of many movement tasks. Moreover, it has already been applied to linear dynamics^{2}.
Therefore, the objective of our model is to minimize movement time while reaching a target of given width.
More precisely, our reward function consists only of a time reward, which penalizes every time step of an episode equally:
This term provides incentives to terminate the episode (which can only be achieved by reaching the target) as early as possible. Since we apply each control \(a_{n}\) for 10 ms, \(\Delta t\) amounts to 0.01 in our case, i.e., \(r_{n}=1\) in each time step \(n\in \{0,\dots ,N\}\).
According to our experience, it is possible to learn aimed movements despite the lack of gradient provided by the reward function, provided the following requirements are met. The initial posture needs to be sampled randomly, and the targets need to be large enough at the beginning of the training to ensure that the target is reached by exploration sufficiently often in early training steps to guide the reinforcement learner. However, creating a predetermined curriculum that gradually decreases the target width during training appropriately has proved very difficult. In most cases, the task difficulty either increased too fast, leading to unnatural movements that do not reach the target directly (and often not at all), or progress was slow, resulting in a timeconsuming training phase.
For this reason, we decided to use an adaptive curriculum, which adjusts the target width dynamically, depending on the recent success rate. Specifically, we define a curriculum state, which is initialized with an initial target diameter of 60 cm. Every 10K update steps, the current policy is evaluated on 30 complete episodes, for which target diameters are chosen, depending on the current state of the curriculum. Based on the percentage of targets reached within the permitted 1.5 s (success rate), the curriculum state is updated. If the success rate falls below \(70\%\), it is increased by 1 cm; if the success rate exceeds \(90\%\), it is decreased by 1 cm. To avoid target sizes that are larger than the initial width or are too close to zero, we clipped the resulting value to the interval \(\left[ 0.1~\text {cm},~60~\text {cm}\right]\).
At the beginning of each episode, the target diameter is set to the current curriculum state with probability \(1  \varepsilon\), and sampled uniformly randomly between 0.1 cm and 60 cm with probability \(\varepsilon =0.1\), which has proven to be a reasonable choice. This ensures in particular that all required target sizes occur throughout the training phase, and thus prevents forgetting how to solve “simpler” tasks (in literature, often referred to as catastrophic forgetting; see, e.g., McCloskey et al.^{91}).
Implementation of the reinforcement learning algorithm
The actor and critic networks described in the Reinforcement Learning section consist of two fully connected layers with 256 neurons each, followed by the output layer, which either returns the means and standard deviations of the action distributions (for the actor network) or the stateaction value (for the critic network). To improve the speed and stability of learning, we train two separate, but samestructuredidentically structured critic networks and use the minimum of both outputs as the teaching signal for all networks (Double QLearning)^{6,89}. In all networks, ReLU^{92} is used as nonlinearity for both hidden layers. The network architectures are depicted in Fig. 6.
The reinforcement learning methods of our implementation are based on the TFAgents library^{93}. The learning phase consists of two parts, which are repeated alternately: trajectory sampling and policy updating.
In the trajectory sampling part, the target position is sampled from the uniform distribution on a cuboid of 70 cm height, 40 cm width, and 30 cm depth, whose center is placed 50 cm in front of the human body, and 10 cm to the right of the shoulder. The width of the target is controlled by the adaptive curriculum described above. The biomechanical model is initialized with some random posture, for which the joint angles are uniformly sampled from the convex hull of static postures that enables keeping the endeffector in one of 12 targets placed along the vertices of the cuboid described above. The initial joint velocities are uniformly sampled from the interval \(\left[ 0.005~\text {radians/s},~0.005~\text {radians/s}\right]\).
In each step \(n\in \{0, \dots , N1\}\), given the current state vector \(s_{n}\in \mathcal {S}\) (see description above), an action is sampled from the current policy \(\pi _{\theta }(\cdot \mid s_{n})\). Next, the MuJoCo simulation uses this action to actuate the model joints. It also updates the body posture, and returns both the reward \(r_n\) and the subsequent state vector \(s_{n+1}\). In our implementation, each episode in the learning process contains at most \(N=150\) of such steps, with each step corresponding to 10 ms (allowing movements to be longer than one and a half seconds did not improve the training procedure significantly). If the target is reached earlier, i.e., the distance between endeffector and target center is lower than the radius of the target sphere, and the endeffector remained inside the target for 100 ms, the current episode terminates and the next episode begins with a new target position and width. At the beginning of the training, 10K steps are taken and the corresponding transitions stored in a replay buffer, which has a capacity of 1M steps. During training, only one step is taken and stored per sampling phase.
In the policy updating part, 256 previously sampled transitions \((s_{n}, a_{n}, r_{n}, s_{n+1})\) are randomly chosen from the replay buffer to update both the actor network and the critic network weights. We use a discount factor of \({\gamma =}0.99\) in the critic loss function of SAC. All other parameters are set to the default values of the TFAgents SAC implementation^{93}.
Both parts of our learning algorithm, the trajectory sampling and the policy update, are executed alternately until the curriculum state, i.e., the current suggested target diameter, falls below 1 cm. With our implementation, this was the case after 1.2M steps, corresponding to about four hours of training time. To evaluate a policy \(\pi _\theta\), we apply the action \(a_{n}^{*}\) with the highest probability under this policy for each time step (i.e., we use the corresponding greedy policy) and evaluate the resulting trajectory. Such an evaluation is done every 10K steps, for which 30 complete episodes are generated using this deterministic policy, and the resulting performance indicators are stored. After the training phase, \(\theta ^{*}\) is set to the latest parameter set \(\theta\), i.e., the final policy \(\pi _{\theta ^{*}}\) is chosen as the latest policy \(\pi _{\theta }\).
An overview of the complete training procedure is given in Fig. 7.
Evaluation
For an evaluation of the trajectories resulting from the learned policy for different target conditions, we designed a discrete Fitts’ Law type task. This task follows the ISO 92419 ergonomics standard and incorporates 13 equidistant targets arranged in a circle 50 cm in front of the body and placed 10 cm right of the right shoulder (Fig. 2). As soon as a target is reached and the endeffector remains inside for 100 ms, the next target is given to the learned policy. This also happens after 1.5 s, regardless of whether or not the episode was successful.
Based on the recommendations from Guiard et al.^{94}, we determine different task difficulty conditions by sampling “form and scale”, i.e., the Index of Difficulty (ID) and the distance D between the target centers are sampled independently, instead of using a distancewidth grid. We use the Shannon Formulation^{45} of Fitts’ Law [Eq. (1)] to compute the resulting distance between the initial and target point D, given the target width W and the ID:
The used combinations of distance, width, and ID can be found as Supplementary Table S1 online, and the resulting target setup is shown in Fig. 2a.
The model executes 50 movements for each task condition and each direction, i.e., 6500 movements in total. All movements reached the target and remained inside for 100 ms within the given maximum movement time of 1.5 s. Plots for all task conditions and movement directions, together with their underlying data, can be found in a public repository^{95}.
In addition, an adaptive “moving target” mechanism is applied to generate elliptic movements from our learned policy. During training, the policy only learned to reach a given target as fast and accurate as possible—it was never asked to follow a specific path accurately. For this reason, we make use of the following method.
Initially, we place the first target on the ellipse such that \(10\%\) of the complete curve needs to be covered clockwise within the first movement, starting at a fixed initial position ( leftmost point on the ellipse). In contrast to regular pointing tasks, the target already switches as soon as the movement (or rather the projection of the movement path onto the ellipse) covers more than half of this distance. The next target is then chosen so as to again create an incentive to cover the next \(10\%\) of the elliptic curve. Thus, roughly 20 viapoints in total are subsequently placed on the ellipse. As shown in Fig. 3a, this indeed leads to fairly elliptic movements.
For our evaluation, we use an ellipse with horizontal and vertical diameters of 15 cm and 6 cm (similar to the ellipse used by Harris and Wolpert^{1}), with its center placed 55 cm in front, 10 cm above, and 10 cm to the right of the shoulder. The task was performed for one minute, with endeffector position, velocity, and acceleration stored every 10 ms.
Comprehensive data for all of these movements can also be found in a public repository^{95}.
Data availability
The datasets generated during and/or analysed during the current study are available in a public repository, https://doi.org/10.5281/zenodo.4268230.
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We would like to thank Aldo A. Faisal (Imperial College London) for his very helpful advice and comments on the manuscript.
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F.F. and J.M. wrote the main manuscript text; M.B. adjusted the biomechanical model; F.F., M.B., and M.K. worked on the MuJoCo implementation and collected simulation data; F.F., M.K., and A.F. analyzed and validated the results; F.F. created the plots; F.F. conducted and J.M. supervised the research process. All authors reviewed the manuscript.
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Fischer, F., Bachinski, M., Klar, M. et al. Reinforcement learning control of a biomechanical model of the upper extremity. Sci Rep 11, 14445 (2021). https://doi.org/10.1038/s41598021937601
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DOI: https://doi.org/10.1038/s41598021937601
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