Cortical Potentials Evoked by Deep Brain Stimulation in the Subthalamic Area

Deep brain stimulation (DBS) of the subthalamic nucleus (STN) has been used since the mid-1990s as a treatment for patients with Parkinson's disease, and more recently also in other conditions, such as dystonia or obsessive compulsive disorder. Non-invasive studies of cortical evoked potentials (EPs) that follow individual STN–DBS stimuli has provided us with insights about the conduction of the DBS pulses to the cortex. Such EPs have multiple components of different latencies, making it possible to distinguish short-latency and long-latency responses (3–8 ms and 18–25 ms latency, respectively). The available evidence indicates that these short- and long-latency EPs correspond to conduction from the STN stimulation site to the cortical recording location via anti- and orthodromic pathways, respectively. In this review we survey the literature from recording studies in human patients treated with STN–DBS for Parkinson's disease and other conditions, as well as recent animal studies (including our own) that have begun to elucidate details of the pathways, frequency dependencies, and other features of EPs. In addition, we comment on the possible clinical utility of this knowledge.

premotor and supplementary motor areas project also to the STN but target principally the ventromedial part (partly overlapping with the projection from the primary motor cortex); Region more concerned by oculomotor and associative aspects of the motor behavior (Parent and Hazrati, 1995;Nambu et al., 1996). Although this has not been examined in as much detail, non-motor areas of the frontal cortex are also likely to project to the STN (Monakow et al., 1978;Canteras et al., 1990;Maurice et al., 1998).
Because STN-DBS may not entirely respect nuclear boundaries, it is important to consider the anatomic proximity of the STN to nearby fiber tracts. Only a subset of these fiber tracts are shown in Figure 1. The STN abuts and is traversed by medial components of the internal capsule, and is in immediate proximity to the zona incerta (ZI) and the fields of Forel (dorsal to the STN), which contain a variety of fiber tracts, particularly pallido-thalamic fibers (Baron et al., 2001), as well as dopaminergic, serotonergic, and other projections from the brainstem to the striatum and other areas. In addition, cerebello-thalamic fibers travel close to the medial and posterior part of the STN (Yelnik and Percheron, 1979;Chang et al., 1983;Kita et al., 1983;Parent and Hazrati, 1995;Hamani et al., 2004).

mechanIsm of actIon of stn-dBs
The currently used DBS electrodes are bundles of four macroelectrodes whose exposed tips are separated by 0.5-1.5 mm. During DBS procedures, these electrodes are implanted into brain regions like the STN. Typically, STN-DBS electrodes are implanted into the central STN. The most ventral electrode tends to be implanted at the ventral border of the STN, or may extend into the dorsal SNr. Depending on the contact separation of the specific electrode used, the top contact is either located in the ZI or in the central thalamus. Subsequently, continuous high-frequency stimulation is delivered via an implanted pulse generator which can be externally programmed.
The exact mechanisms of action of DBS remain uncertain. Modeling studies have suggested that the electrical parameter used in clinically effective monopolar stimulation (for instance, stimulation with 130 Hz, and a 90-μs pulse width) affects axons within a 2.5-mm radius around the contact center (Wu et al., 2001;Mcintyre et al., 2004). Depending on the implantation location, this volume of activation includes areas beyond the borders of the STN.
Early explanations of the mechanisms by which STN-DBS produces its antiparkinsonian effects were strongly influenced by the observation that lesions of the basal ganglia output nuclei and DBS of the STN produce roughly similar clinical outcomes in patients with Parkinson's disease (Benabid, 2003), suggesting that both may act to inhibit basal ganglia output. Support for this view came from studies of neuronal activity in the STN neurons during stimulation and from recordings of the neuronal activity in the rodent SNr (Benazzouz et al., 1995(Benazzouz et al., , 2000. However, in these studies electrical stimulation artifacts prevented the analysis of recordings during the stimulation, so that only post-stimulation activities could be tested. Several of the more recent studies have used digital stimulus artifact removal techniques (Wichmann, 2000;Hashimoto et al., 2002;Montgomery et al., 2005;Erez et al., 2010), and have either confirmed that basal ganglia output is reduced by STN stimulation (Tai et al., 2003;Meissner et al., 2005;Ma et al., 2007) or shown that it is increased (Hashimoto et al., 2003;Maurice et al., 2003;Montgomery, 2006;Xu et al., 2008;Moran et al., 2010). The conclusion that STN output to the basal ganglia output nuclei may be increased is also supported by microdialysis (Windels et al., 2000(Windels et al., , 2003(Windels et al., , 2005 and imaging studies (fMRI and PET, see, e.g., Jech et al., 2001;Perlmutter et al., 2002;Hershey et al., 2003).
While there is no agreement on the effects of STN stimulation on the overall firing rates in the basal ganglia, the effects of STN stimulation on activity patterns in the basal ganglia are less controversial. One of the prominent findings in the available studies is that the stimulation appears to entrain basal ganglia output, thus replacing disruptive basal ganglia output with potentially less disruptive rhythmical activities which may act like a "functional lesion" (Hashimoto et al., 2003;Ma et al., 2007;Erez et al., 2009). It is important to realize that the different rate and pattern changes with STN-DBS may not be exclusive of one another. In fact, it has been proposed that STN-DBS may act by several concurrent mechanisms on different various parkinsonian signs (Temperli et al., 2003).

General features of ePs related to stn-dBs In clInIcal studIes
Stimulation of the STN with single stimuli or with trains of stimuli produces potentials that can be detected with stimulustriggered averaging of electroencephalographic (EEG) or electrocorticographic (ECoG) signals in frontal and central cortical The time needed for orthodromic conduction between motor cortex and STN in non-human primates was found to be 5.8 ± 4.5 ms (Nambu et al., 2000). Because of the absence of synaptic delays, antidromic conduction can be expected to be at least 1-2 ms faster in these animals, and may be slightly longer in patients. Thus, the latency found for short-latency EPs (3-8 ms in humans) is in the range of antidromically mediated potentials.
Short-latency cortical EPs induced by STN stimulation have been found in anesthetized (Li et al., 2007) and conscious rats (Dejean et al., 2009), consistent with antidromic activation of corticofugal fibers. A detailed current-source density analysis established the source of the recorded waves as layer V (Li et al., 2007). Recent optogenetic experiments in dopamine-depleted rodents also support the concept that STN stimulation has antidromically mediated effects on the cerebral cortex (Gradinaru et al., 2009). In these studies, activation of corticofugal fibers was found to be a prerequisite for the beneficial effects of STN stimulation.
The discussion of antidromic cortical activation focuses on the cortico-subthalamic and corticospinal pathways. It remains unclear whether these pathways are separate or whether the cortico-subthalamic projection is a collateral of the corticospinal projection. If the fiber tract(s) responsible for short-latency EPs terminate in the spinal cord, suprathreshold stimulation would be expected to result not only in the generation of EPs, but also in EMG activation which would be expected to be time-locked to the stimulus. This hypothesis has been tested in several studies. Ashby et al. (1999) found in 14 parkinsonian patients undergoing STN-DBS a short-latency facilitation of EMG in the distal and proximal upper limb muscles, with latencies shorter than those seen in transcortical magnetic stimulation induced in the same subjects. This result was interpreted as suggesting that the activation of the peripheral muscles was not dependent on transcortical transmission, but was directly transmitted from the STN stimulation site to the peripheral muscles (Ashby et al., 1999). The same conclusion was reached in a subsequent study in which the facilitation peaks in the EMG (like short-latency EPs) occurred most consistently with stimulation of ventral contacts of the electrode . However, more recent studies have failed to identify EMG activation patterns that are time-locked with STN stimulation (Hanajima et al., 2004;Mackinnon et al., 2005;Kuriakose et al., 2009). The discrepancies between these studies are most easily explained by differences in the location of the stimulating electrodes, the strength of stimulation and other technical differences. The negative outcome of the more recent studies obviously suggests that STN stimulation does not always antidromically activate the corticospinal tract to the extent of activation of peripheral muscles.
In our recent electrophysiologic recording studies in monkeys (Figure 2), we compared the effects of stimulation of the STN on cortical activities with those of stimulation of the GPi. The animals were chronically implanted with EEG recording electrodes, and stimulation electrodes were acutely placed in the center of the STN or into the lateral GPi. We found that only stimulation in the STN produced short-latency cortical EPs, while stimulation at either site produced long-latency EPs (see below), suggesting that only STN stimulation, but not GPi stimulation, antidromically activated fibers related to the motor cortical recording site.
With low-frequency stimulation of the STN, cortical EPs with short (3-8 ms) or long latencies (18-25 ms) can be distinguished. Thus, Ashby et al. (2001) reported the presence of short-latency EPs in almost all of their parkinsonian patients, while a later study found that short-latency EPs were more variable across subjects, occurring in less than half of the electrodes tested (Mackinnon et al., 2005), but that EPs at longer latency (average of 23 ms) occurred more reliably (Mackinnon et al., 2005). Long-latency EPs were also described by other authors in studies which examined EPs in response to stimulation of the contact that yielded the best clinical response (Limousin et al., 1998;Eusebio et al., 2009). In these human studies, the amplitude of EPs strongly depended on the location of the DBS contact(s) used for stimulation, likely reflecting the topography of the STN and of the fiber tracts around it. In contrast, the anatomical distribution and polarity of the potentials were found to be relatively constant across cortical regions, regardless of contact choice. Short-and long-latency EPs were found as positive potentials in the ipsilateral frontal cortex and as negative potentials over the parietal cortex (Mackinnon et al., 2005). Other authors confirmed that the largest short-or long-latency EPs are found in the ipsilateral frontal and central areas (Eusebio et al., 2009;Kuriakose et al., 2009). EPs of short latency were found to be smaller than those of longer latency.
Studies of EPs evoked by STN-area stimulation at clinically used frequencies (80-130 Hz) are limited because the inter-stimulus interval is shorter than the latency of the long-latency EPs. Several studies have, however, examined EPs evoked by stimulation at frequencies between 5 and 30 Hz. Using such stimulation of the electrode contact that gave the best clinical response, the amplitude of the EP was found to be frequency-dependent, with a peak at 20 Hz stimulation, while the latency remained constant, regardless of the stimulation frequency (Eusebio et al., 2009). A more limited comparison of the EPs evoked by STN-DBS of 3 or 30 Hz in parkinsonian patients did not find significant changes in EPs (Kuriakose et al., 2009).

mechanIsms of eP GeneratIon In stn-dBs
short-latency ePs Ashby et al. (2001) found that short-latency frontal cortical EPs have a short chronaxie, a short refractory period, and follow trains of stimuli up to 100 Hz without change in amplitude. These characteristics suggest that the short-latency EPs arise from the activation of low-threshold neuronal elements, such as myelinated axons, rather than from the activation of cell bodies. Given the short latencies, it is likely that such responses are produced by antidromic stimulation of fibers in the vicinity of the STN. The aforementioned high-frequency following is one of the features traditionally used to verify the antidromic spread of neuronal stimulation (Degos et al., 2008), and thus, consistent with the notion that short-latency responses are antidromically mediated. Antidromic transmission from a stimulation site in the STN-area to the cortex has been documented with intracellular recordings of neurons in deep cortical layers in rodents (Li et al., 2007;Gradinaru et al., 2009). contributions from the frontal and parietal cortex (Mitrofanis and Mikuletic, 1999). Most of the downstream projections from the ZI are bilateral, particularly with the brainstem and thalamus (Power and Mitrofanis, 2001).

lonG-latency ePs
The origin of long-latency EPs is likely different from that of the short-latency EPs. The length of these latencies is not compatible with antidromic transmission from the STN to the cerebral cortex, making it likely that they are produced instead by orthodromic transmission (Limousin et al., 1998). EPs of long latency are predominately produced by dorsal STN stimulation (Mackinnon et al., 2005).
Stimulation of either GPi or STN in parkinsonian patients generates long-latency EPs at similar cortical locations in the ipsilateral fronto-central cortex (Limousin et al., 1998;Tisch et al., 2008). This supports the notion that long-latency EPs involve the activation of pallido-thalamic fibers, a feature that would be common to both stimulation sites. The pallido-thalamic pathway passes through the internal capsule, and runs through the fields of Forel, in proximity to the dorsal and rostral part STN (Hamani et al., 2004). STN-DBS could trigger the activation of these fibers either through activation of the excitatory STN efferents to the GPi, which would then secondarily activate pallido-thalamic fibers, or via direct activation of pallido-thalamic projections through current spread from the STN to the Fields of Forel (Mcintyre et al., 2004;Miocinovic et al., 2006). A contribution of the subthalamo-pallido-thalamic route is supported by studies of STN-DBS-related EPs in patients with prior pallidotomies. In some of these patients, cortical EPs were found to be smaller than expected (Baker et al., 2002). The finding of relatively slow cortical responses to GPi stimulation (10 Hz, 3.5-4 V, 60-90 μs) in dystonic patients (Tisch et al., 2008) also supports the hypothesis that at least a portion of the long-latency EPs are mediated via stimulation of pallido-thalamic fibers. However, in a study by Limousin et al. (1998)_ EPs evoked by STN-DBS had a shorter latency (18-20 ms) than EPs evoked by GPi stimulation (25.0-25.8 ms). In our comparisons of EPs recorded from fixed location in the motor cortex, and induced by STN or GPi stimulation (gray lines in Figure 2), the long-latency responses evoked by GPi stimulation occurred earlier than those evoked by STN stimulation (black lines in Figure 2), suggesting that STN stimulation produced its long-latency effects not via direct activation of pallido-thalamic fibers, but through activation of STN efferents to the pallidum.
Because the largest amplitude of long-latency STN-DBS-evoked EPs is found in the same cortical areas that show the largest potentials evoked by stimulation of the contralateral median nerve, the DBS-induced EP may be generated by activity in the region of the ipsilateral primary motor and sensorimotor cortex, in line with the known anatomical afferent and efferent patterns of the basal ganglia (Mackinnon et al., 2005).
Because EP characteristics seem to be relatively unaffected by dopaminergic medications, it has been suggested that the generation or propagation the EPs is (relatively) independent of dopaminergic circuit (Eusebio et al., 2009). Eusebio et al. (2009) observed that oscillatory activity following EPs may be reduced by the medication, perhaps reflecting reduced resonance of the It remains to be studied whether antidromic activation of fibers of passage is restricted to the motor system, or whether non-motor afferents to the STN are also antidromically activated. Recent anatomical studies have confirmed that the STN receives non-motor inputs (see above). It is possible that STN stimulation produces some of its non-motor side effects on mood, verbal fluency or response inhibition (Aron and Poldrack, 2006;Ballanger et al., 2009;Hershey et al., 2010) via antidromic activation of these non-motor pathways. Differences between GPi and STN stimulation as seen for motor cortex stimulation may also hold for the stimulation of nonmotor areas of cortex, which may, in turn, be related to the different non-motor side effect profile of the two procedures (Bronstein et al., 2011). The amplitude of short-latency EPs is typically larger with stimulation via the ventral contacts than with stimulation via the dorsal contacts Mackinnon et al., 2005). It was proposed that the most ventral contacts of the DBS electrode may be closest to myelinated passing fibers in the internal capsule which could be reached by current spread. However, this argument needs to be revisited, because modeling studies have suggested that myelinated fibers are also easily reached with stimulation of the dorsal STN (Mcintyre et al., 2004) and because the density of myelinated fibers within the lateral and rostral STN does not change significantly with the ventral or dorsal location.
Finally, it needs to be recognized that short-latency EPs after STN stimulation may also arise from antidromic transmission of the ZI. The ZI is immediately dorsal to the STN (Parent and Hazrati, 1995) and very likely to be within the area of stimulation during STN-DBS. It receives cortical input from layer V from large frontal areas (Bartho et al., 2002;Bartho et al., 2007). In rats, the heaviest projection to the ZI comes from the cingular cortex, with lesser shows EEG potential changes, averaged across 100 stimulation trials. The EEG was recorded with a differential montage between the two electrodes (filter settings 0.5-100 Hz). Prior to averaging, peri-stimulation EEG segments were aligned to the onset of stimulation (Time 0 ms). The solid lines represent the average response (black for STN and gray for GPi) and the dashed lines correspond to the SD.

Devergnas and Wichmann
Cortical potentials evoked by DBS Frontiers in Systems Neuroscience www.frontiersin.org recording conditions, dictated by the size of the electrodes and the dielectric properties of the scalp and other tissue elements, further contribute to the temporal dynamics of the recordings (similar to its contribution to the frequency of EEG responses). The thalamus, finally, projects to the frontal cortex. Layer IV is the main target of thalamocortical afferents, and would, thus, be the primary cortical layer affected by orthodromically mediated effects of STN-DBS. Large pyramidal cells in layer V are the principal sources of subcortical efferents, and would be considered the primary cortical elements activated via antidromic stimulation effects, as has been shown in cats (Phillips, 1959;Giuffrida et al., 1985) and in rats (Li et al., 2007).
In addition to the latency, the durations of EPs are an interesting feature of these potentials. In our primate recording study, shortlatency potential after STN-DBS stimulation lasted 7.2 ± 0.4 ms while long-latency potentials had a total duration of 30.5 ± 3.5 ms (Figure 2). The temporal spread after short stimuli goes beyond the variability of transmission delays at single synapses, suggesting that the stimulation may involve more than one pathway of origin, or that it may affect thalamic or cortical networks of connections which may eventually contribute to the temporally spread-out cortical response.

PotentIal clInIcal relevance
It remains an open question whether EPs evoked by STN-DBS are related to clinically relevant phenomena. One possibility is that cortical EPs may reflect changes in cortical excitability. In support of this idea, Ashby et al. (1999) found that short-latency EPs were facilitated by paired stimuli at inter-stimulus intervals between 2 and 10 ms, suggesting a cortical summation of postsynaptically generated EPs with short individual refractory periods . Such cortical facilitation could also be partially reflected in increases in cerebral blood flow as have been detected in functional imaging studies (Limousin et al., 1997;Ceballos-Baumann et al., 1999;Hershey et al., 2003).
Experiments using transcranial magnetic stimulation (TMS) to probe cortical excitability have also detected changes in motor cortical excitability with multi-pulse STN-DBS in parkinsonian patients. In these experiments, the short-interval intracortical inhibition was normalized by STN stimulation, but the stimulation did not affect motor EP amplitudes or excitability thresholds (Cunic et al., 2002;Pierantozzi et al., 2002). These summation effect may not be the only mechanism by which STN-DBS may alter cortical activation, because short-latency facilitation of motor cortex excitability can also be seen with single-pulse STN stimulation in patients with Parkinson's disease, specifically with TMS protocols that activate corticospinal neurons through cortical interneurons (Hanajima et al., 2004;Kuriakose et al., 2009). One of the key differences between these studies and the earlier paired-pulse experiments is that the TMS stimuli and the STN-DBS were not time-locked in the paired-pulse studies, so that the temporal evolution of facilitation after each STN stimulus could not be examined. In recent studies Kuriakose et al. (2009) noted changes in motor cortex excitability only at specific time intervals after STN stimulation, corresponding to the duration of short and medium EP peaks. These findings suggest that the cortical facilitation found by TMS was linked to the occurrence of the EP induced by STN stimulation. cortico-basal ganglia-thalamocortical loops. A suppressing effect of STN stimulation on oscillatory cortical activities is also supported by experiments in rodents, where the amplitude of evoked cortical LFPs inversely correlated with slow oscillatory activity (Li et al., 2007). The relative independence of EPs from dopaminergic effects may only apply to parkinsonian individuals, however. STN-DBS is now carried out in an increasing number of non-parkinsonian conditions (see above). In patients with these conditions, en-passant activation of dopaminergic or serotonergic fibers could be involved in the generation of long-latency EPs. However, in a small comparative study of EPs in parkinsonian or epilepsy patients (Baker et al., 2002) there were no significant differences between the two groups. This study would be worth repeating with additional patients or other disease conditions. Moreover, it had been suggested that this long-latency EP could also be independent of basal ganglia involvement. This long-latency EP could be either attributed to a corticocortical pathway driven from the intracortical projections of the pyramids that are antidromically stimulated, or either attributed to the pyramidal branches to the thalamus, those feed back to cortex and so could drive the late response (Phillips, 1959).
Stimulation of the ZI may also have orthodromic effects on cortex, via its GABAergic projection to the ventral anterior thalamus (Bartho et al., 2002). Similar to the activation of pallido-thalamic projection, activation of ZI output induces hyperpolarization of thalamocortical neurons followed by rebound bursts (Kuriakose et al., 2009).
Finally, rodent studies have shown that projections exist between the STN and the prefrontal cortex, providing yet another potential orthodromic route of transmission (Jackson and Crossman, 1981;Kita and Kitai, 1987;Degos et al., 2008). However, it is not clear whether this projection exists in primates.

actIvIty of cIrcuIts downstream from the stImulatIon sIte
Activation of the pallido-thalamic pathway by STN-DBS may alter the neuronal activity in the nuclei of the ventral and intralaminar thalamus that receive basal ganglia input (Anderson et al., 2003;Xu et al., 2008). As an example, Mackinnon et al. (2005) have proposed that low-frequency stimulation of the STN may lead to an inhibitory volley along pallido-thalamic pathways that may hyperpolarize ventral thalamic neurons and de-inactivate somatic calcium conductances which would then result in rebound bursting activity of thalamocortical neurons. The excitatory rebound activity may lead to the production of a cortical evoked potential in related cortical areas (Sherman, 2001;Mackinnon et al., 2005). Due to the slow kinetics of low-threshold calcium bursting activities, clinically effective high-frequency stimulation of the STN would simply lead to suppression of thalamocortical activities by inducing a hyperpolarization state during the stimulation, resulting in a net suppression of the activity of cortical neurons. In support of this idea, thalamic activity was found to be reduced during highfrequency stimulation of the GPi (Anderson et al., 2003), and a decrease in cerebral blood flow was found in the primary motor cortex of parkinsonian patients, during STN stimulation (Ceballos-Baumann et al., 1999;Payoux et al., 2004). However, modeling studies have suggested that high-frequency STN stimulation may induce more complex changes in thalamic firing activities (Guo et al., 2008). Of course, the low-pass filter characteristics of the conclusIon Measuring cortical EPs provides us with a unique opportunity to non-invasively monitor with high temporal resolution the effects of DBS on the cerebral cortex. However, the mechanisms that are involved in generating these potential changes remain relatively poorly understood. The available information suggests that STN-DBS affects multiple anatomical routes which alter cortical activities with different latencies from the stimulation.
Cortical potentials evoked by STN-DBS may not simply be epiphenomena of the stimulation, but may reflect the temporal progression of changes in cortical excitability which may be related to the clinical effects of DBS therapy in Parkinson's disease patients. However, the details of the relationship between the EPs and the clinical effects are not clear. For instance, if these potentials reflect specific activity changes at the cortical level, it is conceivable that the apparent need for high-frequency stimulation for a beneficial effects in patients with Parkinson's disease may arise from the need to optimize the interplay between short-and long-latency effects of the stimulation (or avoid long-latency potentials altogether through rapidly resetting the cortical response through short-latency responses).
We have yet to learn how to utilize the EP results to optimize the clinical outcome of patients who are being treated with STN-DBS. More study of the utility of intraoperative EP recordings to verify electrode placement, or of postoperative EP recordings as an aide to more rapid programming of the STN stimulator is needed to fully examine the potential of this technique. Animal experiments combining pharmacological or lesioning techniques to study the contribution of different anatomical routes to the stimulation response would be useful to further our understanding of the generation of EPs, and of the processes they reflect, both at the cortical and subcortical levels.
Although the antiparkinsonian effects of TMS are generally considered to be moderate compared to those of DBS (Fregni et al., 2005). Similar to the DBS effects (Benabid, 2003;Benabid et al., 2005), the frequency-dependence of the two treatments appears to be similar: low-frequency TMS does not produce beneficial effects (Arias et al., 2010), while high frequency TMS may produce motor benefits (Elahi and Chen, 2009).
Several authors have studied whether the presence or amplitude of EPs could be used as an intraoperative guide to optimize placement of DBS electrode. This would be beneficial, particularly in cases in whom the therapeutic effects of STN-DBS are not immediately apparent (such as in patients with dystonia, epilepsy, depression, or OCD). This approach appears to work in cases of GPi-DBS in dystonic patients (Tisch et al., 2008), but in the case of STN-DBS, the short-or long-latency components of EPs do not appear to strongly correlate with the clinical outcome of the surgery (Ashby et al., 1999;Mackinnon et al., 2005). A principal problem with these studies is that EP testing was done with stimulation at frequencies below 30 Hz (see above) to examine long-latency EPs. At least in Parkinson's disease patients, these stimulation conditions are not optimal from a clinical perspective (Benabid, 2003) and may, in fact, limit the usefulness of intraoperative EP testing as a targeting tool to identify clinical useful stimulation sites. Interestingly, a recent study has indicated that the clinically effective contacts may correspond to those that produce long-latency EPs when tested at a stimulation frequency of 10 Hz (Kuriakose et al., 2009). The utility of short-latency EPs has not been fully evaluated in this context, but studies in awake rodents treated with dopamine receptor blockers documented a correlation between the amplitude of short-latency cortical activation and the degree of improvement in akinesia (Dejean et al., 2009).

Devergnas and Wichmann
Cortical potentials evoked by DBS Frontiers in Systems Neuroscience www.frontiersin.org