Abstract
Decoders optimized offline to reconstruct intended movements from neural recordings sometimes fail to achieve optimal performance online when they are used in closedloop as part of an intracortical braincomputer interface (iBCI). This is because typical decoder calibration routines do not model the emergent interactions between the decoder, the user, and the task parameters (e.g. target size). Here, we investigated the feasibility of simulating online performance to better guide decoder parameter selection and design. Three participants in the BrainGate2 pilot clinical trial controlled a computer cursor using a linear velocity decoder under different gain (speed scaling) and temporal smoothing parameters and acquired targets with different radii and distances. We show that a userspecific iBCI feedback control model can predict how performance changes under these different decoder and task parameters in heldout data. We also used the model to optimize a nonlinear speed scaling function for the decoder. When used online with two participants, it increased the dynamic range of decoded speeds and decreased the time taken to acquire targets (compared to an optimized standard decoder). These results suggest that it is feasible to simulate iBCI performance accurately enough to be useful for quantitative decoder optimization and design.
Similar content being viewed by others
Introduction
Intracortical braincomputer interfaces (iBCIs) can help to restore movement to people with severe paralysis by recording intact motor cortical signals and using them to guide the motion of an external device such as a robotic arm, a computer cursor, or muscle stimulators^{1,2,3,4,5,6,7}. iBCIs are typically calibrated using statistical model fitting approaches that tune the decoder to predict, with minimum error, a set of intended movement variables given a set of neural features^{1,2,3,8,9,10,11,12,13,14,15,16}. The calibration dataset could consist of neural recordings taken while the user observes, imagines or attempts to make a series of cued movements^{2,3,4,17}. It could also be a dataset recorded during active iBCI control, in which case the user’s intended movement must be estimated at each time step (this approach is called “closedloop calibration”^{4,17,18,19,20}). Though it can yield high performing decoders (e.g.^{3,6,19}), this traditional statistical model fitting approach to decoder calibration does not always maximize online performance. In other words, decoders that are optimal at predicting the intended movement variables in the calibration dataset do not necessarily maximize the ability of a person to actively use the decoder to complete a given task.
Several studies have now clearly shown a discrepancy between offline and online decoder performance. For example, one study demonstrated that medium bin widths (150 ms) optimize offline prediction performance for a Kalman filter while smaller bin widths (20 ms) optimize online performance, presumably because they enable the user to make feedback corrections more quickly^{21}. Additionally, it has been shown that decoders with poor offline performance can have better online performance due to the user’s ability to adapt to certain kinds of consistent decoding errors^{9,10}. Another study showed that unintended dynamics can result when decoders are calibrated to maximize offline performance and suggested that decoder dynamics should be optimized in a taskspecific manner to achieve peak online performance^{22}. Finally, we recently showed that many standard decoder calibration methods fail to optimize the decoder’s gain and smoothing parameters in a way that meaningfully accommodates the online task demands (e.g. by decreasing the gain and increasing smoothing for tasks that demand precision), even when closedloop data is used for calibration^{23}. The offline vs. online discrepancy demonstrated by the above studies is not entirely unexpected, given that traditional algorithms (e.g. the Kalman filter^{19,22,24}) do not represent user behavior or task demands in their equations and do not model the feedback correction processes inherent to online control.
In our experience, to achieve peak performance certain decoder parameters like output gain (speed scaling) and temporal smoothing must be optimized through a process of trial and error where several different values are tested online. In this study, we asked: is there a way to predict which parameter settings will yield the best online performance without a trial and error process? Trial and error is time consuming and limits the number of parameter settings that can be tested. Cunningham et al. proposed using an “online prosthesis simulator” (OPS) to simulate the online/closedloop dynamics resulting from a given parameter setting^{21}. The OPS uses an ablebodied human volunteer to simulate the iBCI user. As the volunteer moves their arm, simulated neural activity is generated as a function of those movements and that simulated neural activity drives the decoder. Visual feedback of the decoder output is then given to the volunteer, closing the feedback control loop. Unlike offline prediction performance, this approach takes into account the feedback loop created by the user and the decoder, including how variability in the recorded neural activity creates movement errors and how the user adjusts their neural modulation to correct for those errors. It also automatically takes into account the specific requirements of the task that the decoder will be used to complete.
Here, we develop a similar simulationbased approach to predict online performance and validate it by comparing its predictions to heldout closedloop iBCI data from three clinical trial participants. Our approach improves upon the OPS study by being able to run entirely on the computer (requiring no input from a human volunteer) and by enabling userspecific performance predictions. This expands the utility of the approach by enabling a rapid search across more parameters than would be possible with human volunteers. It also allows the simulation approach to be used in a clinical setting to customize the decoding parameters to suit a given iBCI user. Although several other studies have also successfully employed computer simulations of iBCI control to make qualitative insights (e.g.^{22,25,26}), we are aware of no prior work that has demonstrated an ability to simulate iBCI control with the accuracy required for quantitative parameter selection and design.
Our simulator, which we call the PLM (piecewiselinear model), is based on a feedback control model of twodimensional iBCIcommanded cursor movements that was developed in a previous study investigating how users control iBCIs^{27}. In that study, we showed that the PLM outperformed other published models in its ability to simulate online performance under the same decoder and task parameters on which the model was fit. Here, we systematically assess, for the first time, how well a modified version of the model can predict ahead of time how online performance will change when decoder and task parameters are different from those under which the model was fit. Specifically, we test the model’s ability to predict how iBCI performance will change as a function of the gain and smoothing properties of a linear velocity decoder and as a function of target distance and radius. We evaluate the simulator by fitting its parameters with data collected under a single condition and then using it to predict how performance will change under various other heldout conditions. Finally, we demonstrate that a simulationbased approach has broader utility by using it to design a static nonlinear function that transforms the speeds decoded by a linear velocity decoder. We confirm that the nonlinear function improves online iBCI performance in a 2D and 4D cursor control task in two out of two participants and works well outofthebox without requiring any additional online parameter tuning.
Results
Standard calibration methods do not optimize decoder dynamics for online performance
Before assessing the PLM’s ability to predict online performance under different decoder parameters, we first motivate the problem further with a simulated example of how a typical decoder calibration routine can fail to find the best gain and temporal smoothing parameters for online performance (Fig. 1). In a typical routine (e.g.^{3,4,6,7}), an initial decoder is first calibrated on openloop data where the user attempts to make a series of cursor movements shown on the screen. The decoder is then recalibrated using closedloop data recorded while the user makes movements with the initial decoder. We simulated this process using a simulated iBCI user with linearly tuned neural features that encoded a simple feedback control policy:
where f_{t} is an N × 1 vector of neural features, E is an N × 2 matrix of tuning coefficients (with uniformly distributed preferred directions), g_{t} is the target position, p_{t} is the cursor position, and ε_{t} is neural variability (normally distributed). We calibrated velocity Kalman filters to predict the user’s intended velocity. The intended velocity was estimated by rotating the decoded velocity vectors in the calibration dataset towards the target and zeroing them when the cursor is on top of the target (following the ReFIT method described in^{19}).
Openloop calibration and closedloop recalibration yielded decoders with different gain and smoothing properties, but neither were optimal (i.e. did not minimize movement time when compared to the best parameter settings identified with an exhaustive parameter sweep). We performed the same simulation with both a small and a large target radius. For the small radius task, the standard training protocol yielded a gain that was too high with smoothing that was too low. This resulted in trajectories that orbited around the target instead of stopping. For the large radius task, the gain was too low and the smoothing was too high, resulting in trajectories that were slower than necessary. Continued closedloop recalibration did not cause the decoder dynamics to converge towards optimal values; instead, the gain continued to decrease and the smoothing continued to increase without bound (shown as ReCal 1–5 in Fig. 1 and previously noted in^{18}). To confirm that this result is not limited to the ReFIT calibration method, we ran the same simulation using the encoded control signal \({g}_{t}{p}_{t}\) to calibrate the decoder and found similar results (Supplemental Fig. 1). These results are consistent with recent work that showed a similar inability to optimize gain and smoothing when comparing across different decoder calibration methods^{23}. More details about the simulation parameters are provided in Section 1 of the Supplement. In sum, these results demonstrate that existing decoder calibration protocols are suboptimal, and motivate the need for a better way to set decoder gain and smoothing.
Predicting how gain and smoothing affect online performance
If the effect of gain and smoothing can be predicted ahead of time through simulation, then highperforming values can be found through a simulated sweep without an online trial and error process. Here, we assess the ability of the piecewiselinear model (PLM) to simulate and predict online performance under different gain and smoothing parameters. The PLM’s parameters capture the characteristics of both the decoder and the iBCI user and are illustrated in Fig. 2. The PLM is fit to an individual iBCI user from previously collected decoder output and cursor kinematics data, but it then requires no new neural or behavioral data to simulate movements even for different decoder parameters or tasks. At each time step of the simulation, the twodimensional decoder output u_{t} is simulated using a model of how the user controls the cursor combined with a model of the decoding noise. Individual neural features are not simulated. More details are provided in the Methods.
To test the PLM’s ability to predict the effect of gain and smoothing on iBCI performance, we analyzed 15 sessions of data in which participants completed a target acquisition task with a linear velocity decoder under different gain and smoothing conditions. These sessions included a total of 134 blocks of data across three participants, each with a different gain and smoothing setting. Gain was controlled with a speed scaling parameter and smoothing was set with an exponential smoothing parameter. Each of these blocks was collected after the decoder was calibrated and fixed for the remainder of the session. Each block lasted between 4 to 5 minutes.
For each session, the PLM’s parameters were fit to that session by selecting a single block of data (with a single gain and smoothing setting) and fitting the parameters using that block of data. To predict how online performance would change for each of the other heldout blocks, we used the PLM to simulate 1000 cursor movements under each block’s gain and smoothing settings and measured the performance of those simulated movements. Note that fitting a new model for each session was needed to adapt the model to the amount of decoding noise present on that day, which could vary considerably from session to session depending on what neurons were recorded on the array(s).
We used the following performance metrics to compare the predicted performance to the actual performance: total movement time, translation time (the time taken for the cursor to initially touch the target), dialin time (the time taken to acquire the target after the cursor initially touches it, minus the obligatory dwelltime), and path efficiency (straightness of the cursor movement, measured by the distance of an ideal straightline movement towards the target divided by the distance the cursor actually traveled).
Figure 3 shows example data of cursor movements made under different gains. As gain is increased, translation time decreases (the cursor reaches the target faster) while dialin time increases (it’s harder to acquire the target) and path efficiency decreases (movements are more indirect). The tradeoff between translation time and dialin time causes the total movement time to be a Ushaped function of gain, with the optimal point at an intermediate gain setting. The PLM accurately predicts the effect of gain, including the tradeoff between translation time and dialin time. Note that the model’s predictions are a close quantitative match to the observed performance (i.e. the model is doing more than just predicting the qualitative trends that result when varying a given parameter). This suggests that the model could be useful for predicting userspecific and taskspecific parameters that will work outofthebox without the need for online customization.
Figure 4 shows example data illustrating the effect of smoothing on online performance. Smoothing has the opposite effect of gain: as smoothing is increased, translation time increases (the cursor takes longer to accelerate) while dialin time decreases and path efficiency increases (movements become straighter and stop more completely). The PLM is largely accurate at predicting how smoothing will affect online performance, though in this case it somewhat overestimates movement speed and straightness for the condition with the lowest smoothing.
Figure 5 summarizes the PLM’s prediction performance for all 134 blocks. Overall, the model has good quantitative accuracy across a wide range of gain and smoothing parameters and three different users (e.g. the fraction of variance accounted for by the model’s predictions is greater than 0.7 for each performance metric). We assessed the bias of the model by fitting the model predictions as a linear function of the observed data (Fig. 5B). The results indicate slopes near 1 and intercepts near zero suggesting low bias. Very low pvalues indicate that the model has statistically significant predictive power across all metrics (Fig. 5B).
Supplemental Section 5 shows the same data but for each session separately, confirming that the PLM can accurately predict withinsession variance (due solely to gain and smoothing) in addition to explaining acrosssession variance (due partly to differences in participants and day to day changes in decoding noise^{28}). We also confirmed that good performance across all participants could still be obtained regardless of which particular blocks for each session were used to fit the PLM. To do so, we compared model performance when the PLM was fit on the lowest gain block of each session, the highest gain block, and the median gain block. The average model FVAF and MAE did not vary appreciably (Supplemental Section 3).
Predicting how task parameters affect online performance
Here, we test whether the PLM can predict how online performance will be affected when task parameters change (e.g. when the target distance or radius changes). This is important for two reasons: (1) the model should be able to predict optimal decoder parameters under a large variety of task settings (e.g. target distances and sizes), and (2) predicting how performance changes as a function of task parameters may enable principled optimization of the task (e.g. the sizes and placement of buttons on a virtual keyboard), complementing existing design approaches to user interfaces^{29}.
We used 9 datasets where participants completed the random target task to test the PLM’s ability to predict how target distance and radius affect performance. For each dataset, we fit the model’s parameters to that dataset using only the movements made to targets placed far away from the cursor (with a distance in the top 25% of all tested distances) and with small radii (the smallest of three radii tested on each day). This set of movements constituted four minutes of data on average. We then used the fitted parameters to predict the online performance of movements made to all other targets (simulating 200 movements for each target distance and radius). Figure 6A shows example predictions for two of the datasets that demonstrate the accuracy of the PLM. Of note, the PLM correctly predicts the departures from Fitts’ law that are described in^{30} (the movement time vs. index of difficulty lines for each radius do not lie on top of each other), giving more confidence that the model describes iBCI movements well enough to extrapolate nontrivial results when fit on data from only a single condition. Figure 6B summarizes the prediction performance across all datasets and radius/distance pairings (3 radii and 4 distance categories per dataset = 12 circles per dataset). The model’s predictive power is highly statistically significant (p < 1e38 for all metrics) and has relatively low bias and low error. Supplemental Section 5 shows that the prediction performance is also accurate for all 9 datasets considered separately.
Using the PLM to choose gain and smoothing parameters and to optimize a typing interface
Once fit, the PLM can be used as a tool to choose decoder parameters that are likely to lead to higher performance online. In Fig. 7A we illustrate the process of how it can be used to find highperforming gain and smoothing parameters. Since movements can be simulated quickly, it is possible to simulate movements under a large number of settings to create performance surfaces describing how each performance metric is predicted to change as a function of gain and smoothing. Here, we simulated 250 movements for each of 400 pairs of gain and smoothing settings. The model parameters were fit on one example block of data collected with T8. The resulting performance surfaces reveal that, in general, path efficiency and dialin time tradeoff with translation time. High gain and low smoothing is better for reaching the target more quickly (lower translation time), but worse for dwelling stably on the target (higher dialin times and lower path efficiencies). Metrics that consider both the time taken to reach the target and the ease of acquiring the target (e.g. total movement time) have an optimal point that balances these tradeoffs.
The PLM implicitly takes into account userspecific and taskspecific aspects when predicting the optimal gain and smoothing parameters. Figure 7B illustrates this by showing how the gain and smoothing parameters chosen by the model vary as a function of decoding noise variance, feedback delay and target radius. Here, the optimal parameters were defined as those that were predicted to minimize the total movement time. In general, in more challenging settings (e.g. more decoding noise, long feedback delays, and small target radii), lower gain and higher smoothing values are better. In less demanding settings, higher gain and lower smoothing values are better. The PLM can take these factors into account to find the right parameter values for the specific situation. Note that, if optimal parameters are desired for a flexible task with varying target sizes and distances, these can be found by simulating trajectories towards targets with different radii and distances in whatever proportion the user would experience them and then averaging the performance metrics over these trajectories.
Next, we give an example of how the PLM can be used to help optimize a typing interface (Fig. 7C). It was recently shown that iBCIs can restore the ability to communicate at record speeds by combining 2D cursor control with an onscreen keyboard with a gridlike layout (shown in the top left of Fig. 7C)^{18}. One method for key selection is to require the cursor to dwell on top of a key for a specified amount of time. How long should this dwell time be to maximize the information throughput? The dwell time presents a tradeoff: shorter dwell times enable faster but less accurate selections, while longer dwell times enable slower but more accurate selections. In addition to the dwell time, the decoder parameters must also be optimized, and the optimal decoder parameters may change as a function of dwell time. This presents a difficult optimization problem that would be infeasible to fully explore without simulation. Moreover, the optimal dwell time and decoder parameters are likely to change from user to user since each user has a different amount of decoding noise. Thus, even if the time was spent to find good values for one user through trial and error, these would not necessarily be good values for other users.
We show how the PLM can be used to gain traction on this problem. First, we fit the PLM parameters to a block of data from participant T8. Then, for each possible dwell time (tested in steps of 100 ms) we performed a separate gain and smoothing optimization. For each gain and smoothing parameter pair (chosen on a 30 × 30 grid of possible pairs as in Fig. 7A), we measured the mean key selection time, success rate and overall information throughput (measured with the “achieved bit rate” metric that is a conservative lower bound on information throughput^{29}). These performance metrics were computed by simulating a series of trajectories towards randomly chosen keys on the 36key grid. Trajectories that accidentally selected the wrong key were counted as failures.
Figure 7C shows the results of this optimization, giving some insight into the factors at play in this optimization problem. The highest bit rate was achieved at a dwell time of 1 second where accuracy traded off optimally with speed; dwell times less than 1 second led to more accidental selections of nearby keys, while dwell times greater than 1 second caused selections to be unnecessarily slow. Note how the optimal gain and smoothing parameters changed with dwell time; longer dwell times benefited more from slower gains and more smoothing, which enabled the cursor to successfully dwell for a longer duration. Finally, it is interesting to note that the success rate is less than 1 at the optimal dwell time (success rate = 0.93 when dwell time = 1 s). This suggests that for optimal information throughput, the success rate should be lower than 1 (which is indicative of a regime where movements are fast enough to sometimes cause the occasional error). However, if a higher success rate is desired, the PLM can be used to select the dwell time needed to achieve the desired rate (for example, to achieve a success rate >0.99 a dwell time of 1.6 seconds is needed).
Using the PLM to design and optimize a nonlinear speed transform
Finally, we demonstrate that the PLM is also useful for designing new decoder improvements. Recent work has shown that linear decoders have a baseline floor of signalindependent decoding noise that makes it difficult for users to stop and make small corrective movements accurately^{30}. To address this problem, we used the PLM to search for a nonlinear function that can improve stopping ability by transforming the speeds decoded by a standard linear velocity decoder. A nonlinearity might improve performance by scaling up higher speeds (allowing quick movements to the target) while still mapping a wide range of decoded speeds to lower values (to retain good stopping precision). We first tested this hypothesis with participant T8 (Fig. 8A–D) who performed a standard 2D cursor control task with or without the nonlinearity.
Figure 8A shows the resulting nonlinear function, found by iteratively searching for the parameters of a piecewise linear function that would optimize total movement time on a target acquisition task that demanded a relatively high amount of precision (the target radius + cursor radius was 1/8^{th} of the target distance and the dwell time was 4 seconds). Figure 8B,C show movements made by participant T8 with and without the nonlinearity. With the nonlinearity, T8 reaches the target more quickly than with a standard decoder but still retains the same stopping precision. Figure 8D confirms that there is a statically significant improvement in success rate and translation time with the nonlinearity.
We repeated these results in T5 with a few changes (Fig. 8E–H). First, we wanted to see if the results would generalize to higher dimensional tasks, including 3D movement and control of orientation (as would be required for controlling an arm). To test this, T5 completed a centeroutback 4D cursor control task where he was required to move a 3dimensional bar to the location of a target bar and to rotate the bar to match the orientation of the target (using a single rotational degree of freedom). Second, we used a more constrained form of nonlinearity with a similar shape to that found in T8, but with the simpler form:
where s_{out} is the output speed, s_{in} is the input speed, and p is an exponentiation parameter which we optimized. The results are similar to that of T8, with the nonlinearity improving the dynamic range of speeds and improving stopping ability and decreasing the time taken to reach the target.
These results suggest that a simulationbased optimization approach may be useful in general whenever a parameter space is time consuming to search via trial and error alone. Because the simulator has good quantitative prediction accuracy (i.e. it is not just predicting qualitative trends), the parameters it chooses can work outofthebox without requiring additional hand tuning. Note that, although a straightforward idea like adding an exponential nonlinearity could have been conceived without the PLM, there would be no straightforward way to optimize it or accurately measure the performance improvement relative to an optimized linear decoder. In Supplemental Section 6, we discuss this further and illustrate that even a simple exponential nonlinearity creates a difficult joint optimization problem where decoder gain, smoothing and the exponent must be simultaneously optimized (because the optimal gain and smoothing values depend on the exponent).
Model speed
For practical applications that use the PLM to tune decoder parameters for realworld use, it is important that the PLM parameters can be fit quickly and that movements are fast to simulate. The code we provide (https://github.com/fwillett/bciSim.git) can fit PLM parameters to 3 minutes of data in less than 30 seconds. Once fit, the PLM simulates cursor movements very quickly. Using an Intel i77920HQ processor (3.10 GHz) we were able to simulate 100 seconds of cursor movement (5,000 time steps) in only 3 milliseconds on average. This means that exhaustive grid searches over several parameters can be easily completed. For example, running a grid search over gain (20 values), smoothing (20 values), and the user’s velocity damping (10 values), we were able to sweep all 20 * 20 * 10 = 4,000 combinations with 250 movements per combination in 130 seconds on average (this parameter sweep is shown in Fig. 7A). Iterative searches that find local minimums in the space can reduce this time further; for example, a simple pattern search across these same parameters (using MATLAB’s “patternsearch”) finished in 3.4 seconds on average.
Discussion
Online performance is not always optimized by standard decoder calibration methods (Fig. 1). Here, we used a feedback control model of iBCI cursor movements (called the “PLM” for piecewise linear model) to predict how online performance would change as a function of decoder parameters and task parameters. We showed that the PLM can predict how the gain and exponential smoothing properties of a linear velocity decoder affect online performance (Figs 3–5). It can also predict how target distance and target radius affects performance, giving confidence that the model can be used for a wide range of target parameters and may also be useful for optimizing user interfaces (Fig. 6). Finally, after validating the PLM we demonstrated how it can be used to predict optimal decoding parameters while automatically taking into account taskspecific factors such as target radius and userspecific factors like decoding noise and feedback delay (Fig. 7). To show that a simulationbased optimization approach is viable for decoder parameters other than just gain and smoothing, we used the PLM to design a nonlinear function to transform the speeds decoded by a linear velocity decoder (Fig. 8). This function improved the user’s movement speed without sacrificing stopping precision.
A new tool for predicting highperforming gain and smoothing parameters
The PLM can be used as a tool to automatically find gain and exponential smoothing parameters for a linear velocity decoder that are likely to have high online performance. We have shown that gain and smoothing have a significant effect on online performance, consistent with results from previous studies^{10,22,30,31}. Thus, using the PLM to automatically customize them for a given task and user could yield significant performance benefits and eliminate the need for an online trial and error process. The modelbased optimization process is quick (can be completed in <1 minute) and can be repeated daily, enabling automatic adaptation to changing neural signal quality over time. We hope that this new tool will improve the ability of paralyzed users to perform tasks on a computer (e.g. virtual typing^{14}). The simulator, which is designed to be called from MATLAB, is publicly available on GitHub: https://github.com/fwillett/bciSim.git.
Beyond this practical application, there is also a research benefit for having an objective, automated way to tune the gain and smoothing properties of a linear velocity decoder to maximize performance for any given task and user. The PLM gives a straightforward way to help ensure that newly proposed decoders are compared to a highperforming linear decoder benchmark, so that any improvement shown is not simply due to how the new decoder alters gain or smoothing to outperform a poorly optimized decoder. Gain and smoothing have a large impact on performance^{10,22,30,31} and, unless carefully optimized or controlled, can bias the results of a study. For example, we recently compared different decoder calibration methods and showed that they yield essentially identical decoders that differ only in their gain and smoothing properties^{23}. A naïve comparison between these methods showed large performance differences; however, when gain and smoothing properties were equalized, we saw virtually no performance difference between the methods.
Nonlinear speed transform functions for improving linear velocity decoders
Reports have indicated that iBCI users can have difficulty stopping precisely when using standard linear decoders, including the steadystate velocity Kalman filter^{30,32,33}. Recently, we showed that this was because of a floor of signalindependent decoding noise (i.e. noise that is independent of the user’s motor command) that persists even when the user attempts to slow down or stop^{30}. To facilitate the acquisition of small targets when using standard linear decoders, the gain must be decreased to reduce the signalindependent noise enough so that the cursor can dwell comfortably within the small target. However, this then causes movements towards distant targets to become unnecessarily slow. A nonlinear transform applied to the output of the decoder may alleviate this problem somewhat by enabling both quick movements when traveling towards the target and slow movements when attempting to stop.
We demonstrated the utility of a simulationbased optimization approach by using the PLM to design such a transform. The resulting function scales up higher speeds (allowing quick movements to the target) while still mapping a wide range of decoded speeds to lower values (to retain the same or better stopping precision). Online results from participants T5 and T8 show that this approach is indeed one possible way to achieve a greater dynamic range of speed and precision than what a linear decoder can provide. Other solutions to this same problem have also been proposed, including attenuating the cursor speed when the cursor is changing directions more quickly^{32}, using a nonlinear two state decoder that can switch between a postural decoder and a movement decoder^{33}, and using a hidden Markov model to detect a stopping state^{34}. Combining the nonlinear transform with these other improvements might yield greater gains in performance.
Extending the model to more general decoding architectures
We showed that the PLM can predict closedloop user behavior accurately when simulating a linear velocity decoder with exponential smoothing dynamics. Although this is a commonly used type of decoder that can achieve a high level of performance relative to its simplicity^{1,2,3,4,6,13,15,16,17,20,35,36,37}, we anticipate that the field will ultimately move towards more general nonlinear decoders (e.g. neural networks^{33,38,39,40,41}) that have a greater capacity to leverage patterns in the neural activity which lack a linear relationship to movement velocity. The same simulationbased design approach used here could be expanded to optimize more general kinds of decoders. Indeed, more complex decoders might stand to benefit even more from a simulationbased approach, since they have more free parameters that can be difficult to tune through trial and error alone.
To enable the PLM to optimize more general decoders, a more complete model of the user’s neural activity would have to be added. It would need to incorporate all aspects of the neural activity that the new decoder is designed to exploit. For example, it is known that certain dimensions of neural activity in motor cortex represent movement speed^{41,42,43} and movement timing^{44} in a way that is nonlinearly related to movement velocity. To simulate a neural network decoder that is capable of leveraging these aspects of the neural activity, neural tuning to movement speed and timing would first need to be added to the PLM model. One possible way to do this would be to simulate neural activity at each time step that is linearly tuned to the control vector computed by the PLM model (modeling standard “velocity” tuning), to the magnitude of the control vector (modeling “speed” tuning), and to a timing signal that unfolds as a function of time after the target appears. Once extended in this way, the PLM could be used to guide decoder design in the same way it was used here for linear decoders: by helping to optimize decoder parameters and explore new architectures. We hope that the proofofprinciple demonstrated here for linear decoders will inform a next generation model capable of enabling simulationbased design for the decoders of the future.
Methods
Study permissions and participants
This study includes data from four participants (identified as T5, T6, T7 and T8), who gave informed consent and were enrolled in the BrainGate2 Neural Interface System clinical trial (ClinicalTrials.gov Identifier: NCT00912041, registered June 3, 2009). This pilot clinical trial was approved under an Investigational Device Exemption (IDE) by the US Food and Drug Administration (Investigational Device Exemption #G090003). Permission was also granted by the Institutional Review Boards of University Hospitals (protocol #041217), Stanford University (protocol #20804), Partners Healthcare/Massachusetts General Hospital (2011P001036), Providence VA Medical Center (2011009), and Brown University (0809992560). All research was performed in accordance with relevant guidelines/regulations.
Participants were implanted with one (T6) or two (T5, T7, T8) 96 channel intracortical microelectrode arrays (Blackrock Microsystems, Salt Lake City, UT) in the hand area of dominant motor cortex (1.0mm electrode length for T6, 1.5mm length for T5, T7 and T8). All participants had chronic tetraplegia. T6 and T7 were diagnosed with Amyotrophic Lateral Sclerosis (ALS) and T5 and T8 were diagnosed with high level spinal cord injury. More details about each of the four study participants can be found in^{6,27}.
Dataset overview and relationship to previous studies
To validate the PLM, we leveraged datasets collected and reported in previous work^{27,30}. We used 13 centeroutandback datasets that were originally reported in^{27} to validate the model’s ability to predict performance as a function of gain and smoothing. In these sessions, a different set of gain and smoothing parameters were imposed for each fourminute block of data. During each block, participants acquired targets that appeared in an alternating fashion in either the center of the workspace or in one of eight radially spaced outer locations. We collected two additional centeroutback sessions specifically for this study that further explored the effect of smoothing on online performance, yielding a total of 15 sessions. Each session is listed in Supplemental Table 1.
We also used 9 random target sessions that were originally reported in^{30} to validate the PLM’s ability to predict performance as a function of target distance and radius. In the random target task, after a target was acquired a new target appeared in a random location within the square workspace with uniform probability (but was constrained to appear far enough away from the cursor so as not to overlap it). Targets appeared with a radius chosen from a set of 1 of 3 possible radii. Each session is listed in Supplemental Table 2.
Finally, to demonstrate the versatility of the PLM for helping to design new decoding innovations, we used it to design a static nonlinear function that transforms the speeds decoded by a linear velocity decoder. We collected four additional sessions (two with T5 and two with T8) that measured the online performance benefits of using the modeldesigned nonlinearity. Each session is listed in Supplemental Table 3.
Session structure and task
To control the cursor, participants were instructed to attempt to make arm movements (T5, T8), imagine moving the thumb and index finger (T6), or imagine moving a computer mouse placed under the hand (T7); these different instructions were consistent with each participant’s preferred and successful prior strategies. Each session began with an openloop block where participants watched the cursor automatically complete a centeroutandback target acquisition task while imagining or attempting to make the cursor movements shown. We used this data to calibrate the decoding matrix. Then, participants completed a series of closedloop neural control blocks with computer assistance that were used to recalibrate the decoder. Finally, the decoder was held fixed and participants completed a series of 4 or 5 minute closedloop blocks with no computer assistance. Data reported in the study are from these later closedloop blocks.
Participants acquired targets by holding the cursor in unbroken contact with the target region for a specified dwelltime. A trial was failed and the cursor was reset to the target position if a maximum movement time was exceeded. After a target was acquired, another target appeared shortly afterwards (0–300 ms).
Online decoding framework
The decoding methods used here are described in detail in^{27,30}. Briefly, we used a linear velocity decoder that is a reparameterized version of the steadystate, velocity Kalman filter^{19,22,24}. Our decoder parameterization explicitly separates the dimensionality reduction step (the mapping between the high dimensional neural activity to the two dimensional decoded velocity) from the smoothing dynamics and overall gain. This parameterization allowed us to isolate and control the decoder’s gain and smoothing properties while keeping its dimensionality reduction step constant throughout the session.
In the dimensionality reduction step, the neural features (threshold crossing rates and spectral power within the 250–5000 Hz band) were mapped to a decoded “control” vector at each time step with the equation
where f_{t} is an N × 1 neural feature vector, D is a 2 × N decoding matrix, and u_{t} is a 2 × 1 decoded control vector. The decoded control vector was then smoothed using the following dynamical equation that determines the cursor velocity
where v_{t} is cursor velocity, \(\alpha \in [0,1)\) parameterizes the amount of smoothing and \(\beta \in (0,\infty )\) parameterizes the gain. Note that the above parameterization can describe any decoder that is composed of linear dimensionality reduction plus exponential smoothing (e.g.^{3,13,15,16}).
The D matrix was calibrated with optimal linear estimation (T8)^{7,45}, reverse regression (T6, T7)^{45}, or by estimating the Kalman gain matrix (T5)^{19}. The user’s intention was estimated with the “unit vector” intention estimation method (T6, T7, T8) or ReFIT (T5)^{23}. Importantly, we normalized the decoding matrix D so that β alone parameterizes the maximum speed of the cursor. When D is normalized, β defines the cursor’s “terminal velocity”, or the (average) speed that the cursor would asymptotically approach if the user pointed u_{t} in the same direction forever. We report cursor gain as this maximum speed, reported in units of target distances per second (TD/s).
Piecewiselinear feedback control model
The piecewiselinear model (PLM) we used to simulate and predict online performance is described in detail in^{27} and is illustrated in Fig. 2. Here, we give a brief overview of the PLM. The PLM describes the decoded control vector (u_{t}) at each time step as the sum of an intentional component (c_{t}, the “encoded” control vector) and the decoding error (e_{t}):
The encoded control vector represents neural modulation that drives the cursor towards the target. The model uses piecewiselinear functions to describe c_{t} as a function of the target position and the user’s internal estimate of cursor position and velocity:
where g_{t} is the target position,\({\hat{p}}_{t}\) is the user’s internal estimate of cursor position, \({\hat{v}}_{t}\) is the user’s internal estimate of cursor velocity, and f_{targ} and f_{vel} are piecewiselinear, onedimensional weighting functions that are fit empirically to the data (the Model Fitting section below provides more details). Essentially, this equation models c_{t} as the sum of a pointattarget vector (weighted by the function f_{targ}) and a velocity damping vector (weighted by f_{vel}). Note that the simulated user does not have direct access to the true cursor position and velocity, but instead uses an “internal estimate” of cursor position and velocity (\({\hat{{\rm{p}}}}_{{\rm{t}}}\) and \({\hat{{\rm{v}}}}_{{\rm{t}}}\)) made from delayed visual feedback and a forward model matched to the decoder dynamics (motivated by the result in^{46}).
The internal state estimates \({\hat{p}}_{t}\) and \({\hat{v}}_{t}\) are generated as follows. At each time step t, the user receives perfect knowledge of the delayed cursor state \({x}_{t\tau }\), where \(\tau \) is the user’s visual feedback delay (in # of time steps). After receiving delayed feedback, the user employs a forward model (matched perfectly to the cursor dynamics), combined with knowledge of previously issued control signals, to estimate the current cursor state x_{t} by running the decoder equations forward starting from \({x}_{t\tau }\):
where \({\hat{x}}_{t}\) is the user’s internal model estimate of the cursor state (\({\hat{x}}_{t}\) is a vector containing \({\hat{p}}_{t}\) and \({\hat{v}}_{t}\)). The A and B matrices parameterize the decoder dynamics in state space form^{27} \(({x}_{t}=A{x}_{t1}+B{u}_{t})\). Since c_{t} differs from u_{t} for all time steps from (t − τ − 1) to (t − 1), \({\hat{x}}_{t}\) will differ from x_{t}. Essentially, this means that the user can only counteract decoding noise perturbations τ time steps after they occur, limiting the effectiveness of the user’s feedback corrections.
The decoding error e_{t} is characterized with an autoregressive noise model
where Π_{i} are 2 × 2 matrices (for a 2D task), p is the number of time lags in the model, and ε_{t} is zeromean, multivariate Gaussian i.i.d. noise. In addition to describing the noise magnitude, the autoregressive model describes the frequency content of the noise by parameterizing correlations and anticorrelations in time. The matrices Π_{i} and the covariance matrix of ε_{t} are fit empirically to the data. The number of time lags p is chosen during model fitting by increasing p until the ability to predict the decoding error on heldout data does not improve.
Additions made to the model to increase predictive power
We made two changes to the model as originally described in^{27} in order to increase its predictive power on heldout data. First, we added signaldependent noise. That is, we modeled how the variance of ε_{t} changed as a function of the magnitude of c_{t}. To do so, we scaled the covariance matrix of ε_{t} at each time step by multiplying it by a weighting function \({f}_{SDN}(\Vert {c}_{t}\Vert )\) that we estimated empirically. We found that this improved prediction accuracy for T6, whose neural signals’ noise had a small but significant signal dependence; it didn’t affect prediction accuracy for T7 or T8, whose noise was almost entirely signal independent^{30}.
The second change was to add a simple model of user adaptation. In the original study^{27}, the model was only used to simulate movements under the same gain and smoothing condition to which it was fit. Here, since we used the model to predict how performance would change in different conditions, we needed to consider how user behavior (i.e. the f_{targ} and f_{vel} functions) might change under these different conditions. In the original study^{27}, we found that users adapt their neural modulation to adjust for large gain or smoothing values that create significant secondorder acceleration dynamics. To predict this adaptation, we ran an optimization routine to search for new f_{vel} functions that would lead to the highest simulated performance under the new gain and smoothing settings of interest. We assumed that f_{vel} would be linear (as found in^{27}) and constrained our search by looking for the slope that would minimize average movement time. To search for the slope, we did a brute force search over a likely range of values (from 0 to −3 in steps of 0.1). This model of adaptation essentially assumes that the user will rapidly adapt their behavior to add the appropriate amount of velocity damping called for by the gain and smoothing settings. Note that this method requires no data from heldout conditions, since it only searches for the f_{vel} function that causes the simulated user to perform the best (as opposed to the f_{vel} function that leads to the highest match to heldout data).
Model fitting
The PLM parameters are empirically fit to a set of observed cursor movements (p_{t}, v_{t}) and decoder outputs (u_{t}). The control policy model (f_{targ} and f_{vel}) and the user’s internal model estimates of the cursor state (\({\hat{p}}_{t}\), \({\hat{v}}_{t}\)) are fit together in an iterative process:

1.
Initialize the internal model estimates to a delayed cursor state (\({\hat{p}}_{t}={p}_{t\tau }\), \({\hat{v}}_{t}={v}_{t\tau }\)).

2.
Using the current internal model estimates, fit the control policy model parameters using least squares regression to minimize the error between the modeled control vector c_{t} and the observed decoder output u_{t}.

3.
Using the current control policy model, update the internal model estimates assuming that the user employs a forward model that is matched perfectly to the cursor dynamics (i.e., for each time step, begin with delayed cursor states and step forward using the cursor dynamics and efference copies of recent control vectors until the current time step).

4.
Return to step 2 until we have completed five iterations.
Once the control policy model is fit, the noise model is then fit to characterize the error time series e_{t} = u_{t}  c_{t}. To do so, first the Π_{i} matrices are fit using least squares to minimize the prediction error of e_{t}. To choose the number of time lags to include in the autoregressive noise model, we started at zero and increased the number of lags by 1 until the crossvalidated predictive power of the model stopped increasing. The noise covariance of \({\varepsilon }_{t}\) is then estimated from the covariance of the prediction errors of the autoregressive noise model. Finally, the signal dependent noise function \({f}_{SDN}(\Vert {c}_{t}\Vert )\) is found by estimating the signalspecific covariance matrix of ε_{t} for twenty different bins corresponding to different levels of \((\Vert {c}_{t}\Vert )\). The bin edges were evenly spaced from \(\Vert {c}_{t}\Vert =0\) to \(\Vert {c}_{t}\Vert =1.5\). Scalar values of \({f}_{SDN}(\Vert {c}_{t}\Vert )\) for each bin were found by estimating the binspecific covariance matrix of the noise and then finding the scale factor to best relate it to the fulldata covariance matrix using a least squares fit.
Model prediction
To test the PLM’s ability to predict online performance, its performance was evaluated on heldout data only. That is, the model parameters were fit using data from one condition and then used to predict performance under a different condition. To predict performance as a function of gain and smoothing, we fit the model to one block of data per session and then used that model to predict online performance for all other blocks in that session. For participants T7 and T8, we chose to fit the model to the block with the lowest gain setting, reasoning that in a practical use case calibration data would most likely be collected at a low gain setting. For participant T6, this approach did not always work as well when predicting performance under high gain conditions. We believe this is because low gain blocks do not always contain many examples of neartarget corrective behavior and corresponding decoding noise, which may be necessary to accurately predict this behavior in highgain conditions for some participants. Therefore, for predicting the performance of T6, we fit the noise model on the block with the highest gain in any given session. However, this necessitated that we fit the control policy model (f_{targ}) using a slow speed decoder calibration block so that T6’s maximum neural modulation could still be reliably estimated (for very high gains, users decrease the magnitude of their neural modulation to adapt^{27}). Note that, although the fitting procedure was not the same as the other participants, no heldout data of any kind was used to inform the model for T6. Also, reasonably high performance across all participants could still be obtained regardless of which blocks were used to fit the model (Supplemental Fig. 2).
To predict performance as a function of target radius and distance, we fit the model to a subset of trials recorded on each day during a random target task. This subset of trials included data only from far away targets (target distance in the top 25% of all trials) and small target radii (the smallest of 3 radii tested). The PLM was then used to predict performance for all other target radii and distances on that day. The model fitting procedure was the same for both participants T6 and T8.
Design of a nonlinear speed transform
We collected two sessions each of data with T5 and T8 comparing the performance of a standard decoder to one with a modeloptimized nonlinear speed transform. T8 completed a standard centeroutback 2D cursor control task. T5 completed a centeroutback 4D cursor control task where he was required to move a 3dimensional bar to the location of a target bar and to rotate the bar to match the orientation of the target. T5 continuously controlled the bar’s velocity in the X, Y, and Z dimensions and the rate of change of a single rotational degree of freedom. The rotational degree of freedom was not treated any differently by the decoder and behaved the same way as the translational degrees of freedom. In these tasks, targets were evenly spaced along a circle (T8, 8 targets) or a 4D hypersphere (T5, 80 targets).
We optimized the speed transform separately for each session. First, we fit the PLM to an initial block of data collected at the beginning of the session. We then optimized gain, smoothing, and the nonlinear transform parameters to minimize total movement time on a difficult target acquisition task. T8 completed a task with a 4 second dwell time and where the effective target radius (target plus cursor radius) was equal to 1/8^{th} of the target distance. T5 completed a task with a 1 second dwell time and an effective target radius of 1/10^{th} the target distance. A trial was considered failed if a maximum movement time of 10 seconds (T5) or 12 seconds (T8) was exceeded.
For T8, the nonlinear transform was parameterized as a piecewise linear function with 14 breakpoints. First, the optimal gain and smoothing parameters were found for a standard linear decoder using an exhaustive search. Then, the breakpoints for the nonlinear transform were spaced evenly from 0 to 1.25*β (where β is the optimized gain). An iterative search was performed to find the optimal function values at these breakpoints using MATLAB’s “patternsearch” function that implements a direct search method. The objective function was defined as the average movement time of 200 simulated movements. We performed 24 searches and then averaged the 24 resulting functions to yield the final result. For T5, the nonlinear transform was parameterized more compactly as an exponentiation: \({s}_{out}=\,{{s}_{in}}^{p}\), where s_{out} is the output speed, s_{in} is the input speed, and p is an exponentiation parameter. We optimized over gain, smoothing and p simultaneously using an exhaustive grid search.
Once the nonlinear transform was optimized, we then collected a series of alternating fiveminute blocks where T5 and T8 used a decoder with modeloptimized gain and smoothing values either with or without the nonlinearity. Across both days for each participant, we collected 5 blocks using the standard decoder and 6 blocks using the nonlinear transform with T5, and 9 blocks of each with T8. To make Fig. 8, we pooled the data across all of these blocks.
Data Availability
The data can be made available upon reasonable request by contacting the lead or senior authors.
References
Hochberg, L. R. et al. Neuronal ensemble control of prosthetic devices by a human with tetraplegia. Nature 442, 164–171 (2006).
Hochberg, L. R. et al. Reach and grasp by people with tetraplegia using a neurally controlled robotic arm. Nature 485, 372–375 (2012).
Collinger, J. L. et al. Highperformance neuroprosthetic control by an individual with tetraplegia. The Lancet 381, 557–564 (2013).
Jarosiewicz, B. et al. Virtual typing by people with tetraplegia using a selfcalibrating intracortical braincomputer interface. Sci. Transl. Med. 7, 313ra179–313ra179 (2015).
Bouton, C. E. et al. Restoring cortical control of functional movement in a human with quadriplegia. Nature 533, 247–250 (2016).
Pandarinath, C. et al. High performance communication by people with paralysis using an intracortical braincomputer interface. eLife 6, e18554 (2017).
Ajiboye, A. B. et al. Restoration of reaching and grasping movements through braincontrolled muscle stimulation in a person with tetraplegia: a proofofconcept demonstration. The Lancet 389, 1821–1830 (2017).
Carmena, J. M. et al. Learning to Control a Brain–Machine Interface for Reaching and Grasping by Primates. PLoS Biol. 1, e2 (2003).
Chase, S. M., Schwartz, A. B. & Kass, R. E. Bias, optimal linear estimation, and the differences between openloop simulation and closedloop performance of spikingbased braincomputer interface algorithms. Neural Netw. Off. J. Int. Neural Netw. Soc. 22, 1203–1213 (2009).
Koyama, S. et al. Comparison of braincomputer interface decoding algorithms in openloop and closedloop control. J. Comput. Neurosci. 29, 73–87 (2010).
Li, Z. et al. Unscented Kalman Filter for BrainMachine Interfaces. PLoS ONE 4, e6243 (2009).
Serruya, M. D., Hatsopoulos, N. G., Paninski, L., Fellows, M. R. & Donoghue, J. P. Brainmachine interface: Instant neural control of a movement signal. Nature 416, 141–142 (2002).
Shanechi, M. M., Orsborn, A. L. & Carmena, J. M. Robust BrainMachine Interface Design Using Optimal Feedback Control Modeling and Adaptive Point Process Filtering. PLoS Comput Biol 12, e1004730 (2016).
Shanechi, M. M. et al. A realtime brainmachine interface combining motor target and trajectory intent using an optimal feedback control design. PloS One 8, e59049 (2013).
Taylor, D. M., Tillery, S. I. H. & Schwartz, A. B. Direct Cortical Control of 3D Neuroprosthetic Devices. Science 296, 1829–1832 (2002).
Velliste, M., Perel, S., Spalding, M. C., Whitford, A. S. & Schwartz, A. B. Cortical control of a prosthetic arm for selffeeding. Nature 453, 1098–1101 (2008).
Gilja, V. et al. Clinical translation of a highperformance neural prosthesis. Nat. Med. 21, 1142–1145 (2015).
Fan, J. M. et al. Intention estimation in brainmachine interfaces. J. Neural Eng. 11, 016004 (2014).
Gilja, V. et al. A highperformance neural prosthesis enabled by control algorithm design. Nat. Neurosci. 15, 1752–1757 (2012).
Jarosiewicz, B. et al. Advantages of closedloop calibration in intracortical braincomputer interfaces for people with tetraplegia. J. Neural Eng. 10, 046012 (2013).
Cunningham, J. P. et al. A closedloop human simulator for investigating the role of feedback control in brainmachine interfaces. J. Neurophysiol. 105, 1932–1949 (2011).
Gowda, S., Orsborn, A. L., Overduin, S. A., Moorman, H. G. & Carmena, J. M. Designing Dynamical Properties of BrainMachine Interfaces to Optimize TaskSpecific Performance. IEEE Trans. Neural Syst. Rehabil. Eng. 22, 911–920 (2014).
Willett, F. R. et al. A Comparison of Intention Estimation Methods for Decoder Calibration in Intracortical BrainComputer Interfaces. IEEE Trans. Biomed. Eng. 1–1, https://doi.org/10.1109/TBME.2017.2783358 (2017).
Malik, W., Truccolo, W., Brown, E. & Hochberg, L. Efficient Decoding With SteadyState Kalman Filter in Neural Interface Systems. IEEE Trans. Neural Syst. Rehabil. Eng. 19, 25–34 (2011).
Lagang, M. & Srinivasan, L. Stochastic optimal control as a theory of brainmachine interface operation. Neural Comput. 25, 374–417 (2013).
Benyamini, M. & Zacksenhouse, M. Optimal feedback control successfully explains changes in neural modulations during experiments with brainmachine interfaces. Front. Syst. Neurosci. 9, 71 (2015).
Willett, F. R. et al. Feedback control policies employed by people using intracortical brain–computer interfaces. J. Neural Eng. 14, 016001 (2017).
Perge, J. A. et al. Reliability of directional information in unsorted spikes and local field potentials recorded in human motor cortex. J. Neural Eng. 11, 046007 (2014).
Nuyujukian, P., Fan, J. M., Kao, J. C., Ryu, S. I. & Shenoy, K. V. A highperformance keyboard neural prosthesis enabled by task optimization. IEEE Trans. Biomed. Eng. 62, 21–29 (2015).
Willett, F. R. et al. Signalindependent noise in intracortical brain–computer interfaces causes movement time properties inconsistent with Fitts’ law. J. Neural Eng. 14, 026010 (2017).
Marathe, A. R. & Taylor, D. M. The impact of command signal power distribution, processing delays, and speed scaling on neurallycontrolled devices. J. Neural Eng. 12, 046031 (2015).
Golub, M. D., Yu, B. M., Schwartz, A. B. & Chase, S. M. Motor cortical control of movement speed with implications for brainmachine interface control. J. Neurophysiol. 112, 411–429 (2014).
Sachs, N. A., RuizTorres, R., Perreault, E. J. & Miller, L. E. Brainstate classification and a dualstate decoder dramatically improve the control of cursor movement through a brainmachine interface. J. Neural Eng. 13, 016009 (2015).
Kao, J. C., Nuyujukian, P., Ryu, S. I. & Shenoy, K. V. A HighPerformance Neural Prosthesis Incorporating Discrete State Selection With Hidden Markov Models. IEEE Trans. Biomed. Eng. 64, 935–945 (2017).
Kim, S.P., Simeral, J. D., Hochberg, L. R., Donoghue, J. P. & Black, M. J. Neural control of computer cursor velocity by decoding motor cortical spiking activity in humans with tetraplegia. J. Neural Eng. 5, 455–476 (2008).
Orsborn, A., Dangi, S., Moorman, H. & Carmena, J. ClosedLoop Decoder Adaptation on Intermediate TimeScales Facilitates Rapid BMI Performance Improvements Independent of Decoder Initialization Conditions. IEEE Trans. Neural Syst. Rehabil. Eng. https://doi.org/10.1109/TNSRE.2012.2185066 (2012).
Sadtler, P. T. et al. Neural constraints on learning. Nature 512, 423–426 (2014).
Sussillo, D. et al. A recurrent neural network for closedloop intracortical brain–machine interface decoders. J. Neural Eng. 9, 026027 (2012).
Sussillo, D., Stavisky, S. D., Kao, J. C., Ryu, S. I. & Shenoy, K. V. Making brain–machine interfaces robust to future neural variability. Nat. Commun. 7 (2016).
Schwemmer, M. A. et al. Meeting brain–computer interface user performance expectations using a deep neural network decoding framework. Nat. Med. 24, 1669 (2018).
Inoue, Y., Mao, H., Suway, S. B., Orellana, J. & Schwartz, A. B. Decoding arm speed during reaching. Nat. Commun. 9, 5243 (2018).
Moran, D. W. & Schwartz, A. B. Motor cortical representation of speed and direction during reaching. J. Neurophysiol. 82, 2676–2692 (1999).
Perel, S. et al. Singleunit activity, threshold crossings, and local field potentials in motor cortex differentially encode reach kinematics. J. Neurophysiol. 114, 1500–1512 (2015).
Kaufman, M. T. et al. The Largest Response Component in the Motor Cortex Reflects Movement Timing but Not Movement Type. eNeuro 3, ENEURO.0085–16.2016 (2016).
Kass, R. E., Ventura, V. & Brown, E. N. Statistical Issues in the Analysis of Neuronal Data. J. Neurophysiol. 94, 8–25 (2005).
Golub, M. D., Chase, S. M. & Yu, B. M. Learning an Internal Dynamics Model from Control Demonstration. JMLR Workshop Conf. Proc. 606–614 (2013).
Acknowledgements
We thank participants T5, T6, T7, T8 and their caregivers and families. Funding was provided in part by NIH Grant 5U01NS098968, the Eunice Kennedy Shriver National Institute of Child Health and Human Development (NICHD) of the National Institutes of Health (NIH) under award number R01HD077220, and by NICHDNIH N01HD53403, and the National Institute on Deafness and Other Communication Disorders of NIH under award number R01DC009899. Support was also provided by the United States Department of Veterans Affairs, Rehabilitation Research and Development Service, under award numbers B4853C, B6453R, and N9228C. ABA was partially supported by the Department of Veterans Affairs Career Development Award B9043W. The content is solely the responsibility of the authors and does not necessarily represent the official views of NIH, the Department of Veterans Affairs, the United States Government, other funding agencies, or of the parent institutions. Caution: investigational device. Limited by federal (United States) law to investigational use.
Author information
Authors and Affiliations
Contributions
F.R.W. conceived the study, performed the experiments, analyzed the data, and wrote the manuscript. S.D.S. designed and implemented the 4D decoder with exponential gain, which F.R.W. optimized using the modelbased optimization method. D.R.Y., B.A.M., W.D.M., C.H.B., C.P., J.S., P.R. and B.J. assisted in data collection. K.V.S., J.M.H., J.D.S., L.R.H., R.F.K. and A.B.A. supervised data collection at their respective sites. R.F.K. and A.B.A. supervised and guided the project. B.L.W., J.A.S., J.P.M. and J.M.H. planned and performed the array surgeries. L.R.H. is the sponsorinvestigator of the BrainGate2 trial and oversaw the clinical trial along with J.M.H. and B.L.W. All authors reviewed and edited the manuscript.
Corresponding author
Ethics declarations
Competing Interests
K.V. Shenoy is a consultant to Neuralink Corp. and on the Scientific Advisory Boards of CTRLLabs, Inc., MINDX Inc., Inscopix Inc. and Heal, Inc. This work was independent of and in no way influenced or supported by these commercial entities. All other authors have no competing interests.
Additional information
Publisher’s note: Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.
Supplementary information
Rights and permissions
Open Access This article is licensed under a Creative Commons Attribution 4.0 International License, which permits use, sharing, adaptation, distribution and reproduction in any medium or format, as long as you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were made. The images or other third party material in this article are included in the article’s Creative Commons license, unless indicated otherwise in a credit line to the material. If material is not included in the article’s Creative Commons license and your intended use is not permitted by statutory regulation or exceeds the permitted use, you will need to obtain permission directly from the copyright holder. To view a copy of this license, visit http://creativecommons.org/licenses/by/4.0/.
About this article
Cite this article
Willett, F.R., Young, D.R., Murphy, B.A. et al. Principled BCI Decoder Design and Parameter Selection Using a Feedback Control Model. Sci Rep 9, 8881 (2019). https://doi.org/10.1038/s41598019441667
Received:
Accepted:
Published:
DOI: https://doi.org/10.1038/s41598019441667