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      Video game training enhances cognitive control in older adults

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          Cognitive control is defined by a set of neural processes that allow us to interact with our complex environment in a goal-directed manner 1 . Humans regularly challenge these control processes when attempting to simultaneously accomplish multiple goals (i.e., multitasking), generating interference as the result of fundamental information processing limitations 2 . It is clear that multitasking behavior has become ubiquitous in today’s technologically-dense world 3 , and substantial evidence has accrued regarding multitasking difficulties and cognitive control deficits in our aging population 4 . Here we show that multitasking performance, as assessed with a custom-designed 3-D video game (NeuroRacer), exhibits a linear age-related decline from 20–79 years of age. By playing an adaptive version of NeuroRacer in multitasking training mode, older adults (60–85 y.o.) reduced multitasking costs compared to both an active control group and a no-contact control group, attaining levels beyond that of untrained 20 year olds, with gains persisting for six months. Furthermore, age-related deficits in neural signatures of cognitive control, as measured with electroencephalography, were remediated by multitasking training (i.e., enhanced midline frontal theta power and frontal-posterior theta coherence). Critically, this training resulted in performance benefits that extended to untrained cognitive control abilities (i.e., enhanced sustained attention and working memory), with an increase in midline frontal theta power predicting the training-induced boost in sustained attention and preservation of multitasking improvement six months later. These findings highlight the robust plasticity of the prefrontal cognitive control system in the aging brain, and provide the first evidence of how a custom-designed video game can be used to assess cognitive abilities across the lifespan, evaluate underlying neural mechanisms and serve as a powerful tool for cognitive enhancement. In a first experiment, we evaluated multitasking performance across the adult lifespan. 174 participants spanning six decades of life (ages 20–79; ~30 individuals per decade) played a diagnostic version of NeuroRacer to measure their perceptual discrimination ability (’sign task’) with and without a concurrent visuomotor tracking task (‘driving task’; see Supplementary Materials for details of NeuroRacer). Performance was evaluated using two distinct game conditions: 1) ‘Sign Only’- respond as rapidly as possible to the appearance of a sign only when a green circle was present, and 2) ‘Sign & Drive’- simultaneously perform the sign task while maintaining a car in the center of a winding road using a joystick (i.e., ‘drive’; see Figure 1a). Perceptual discrimination performance was evaluated using the signal detection metric of discriminability (d'). A ‘cost’ index was used to assess multitasking performance by calculating the percentage change in d’ from ‘Sign Only’ to ‘Sign & Drive’, such that greater cost (i.e., a more negative % cost) indicates increased interference when simultaneously engaging in the two tasks (see Methods Summary). Prior to the assessment of multitasking costs, an adaptive staircase algorithm was used to determine the difficulty levels of the game at which each participant performed the perceptual discrimination and visuomotor tracking tasks in isolation at ~80% accuracy. These levels were then used to set the parameters of the component tasks in the multitasking condition, so that each individual played the game at a customized challenge level. This assured that comparisons would inform differences in the ability to multitask, and not merely reflect disparities in component skills (see Methods, Supplementary Figures 1 & 2, and Supplementary Materials for more details). Multitasking performance diminished significantly across the adult lifespan in a linear fashion (i.e., increasing cost, see Figure 2a and Supplementary Table 1), with the only significant difference in cost between adjacent decades being the increase from the 20s (−26.7% cost) to the 30s (−38.6% cost). This deterioration in multitasking performance is consistent with the pattern of performance decline across the lifespan observed for fluid cognitive abilities, such as reasoning 5 and working memory 6 . Thus, using NeuroRacer as a performance assessment tool we replicated previously evidenced age-related multitasking deficits 7,8 , and revealed that multitasking performance declines linearly as we advance in age beyond our twenties. In a second experiment, we explored if older adults who trained by playing NeuroRacer in multitasking mode would exhibit improvements in their multitasking performance on the game 9,10 (i.e., diminished NeuroRacer costs). Critically, we also assessed if this training transferred to enhancements in their cognitive control abilities 11 beyond those attained by participants who trained on the component tasks in isolation. In designing the multitasking training version of NeuroRacer, steps were taken to maintain both equivalent difficulty and engagement in the component tasks to assure a prolonged multitasking challenge throughout the training period: difficulty was maintained using an adaptive staircase algorithm to independently adjust the difficulty of the ‘sign’ and ‘driving’ tasks following each 3-min run based on task performance, and balanced task engagement was motivated by rewards given only when both component tasks improved beyond 80% on a given run. We assessed the impact of training with NeuroRacer in a longitudinal experiment that involved randomly assigning 46 naïve older adults (60–85yrs: 67.1yrs ± 4.2) to one of three groups: Multitasking Training (MTT; n=16), Singletask Training (STT; n=15) as an active control, or No-Contact Control (NCC; n=15). Training involved playing NeuroRacer on a laptop at home for 1 hour a day, 3 times a week for 4 weeks (12 total hours of training), with all groups returning for a 1 month Post-training and a 6 month follow-up assessment (Figure 1b). The MTT group played the ‘Sign & Drive’ condition exclusively during the training period, while the STT group divided their time between a “Sign Only” and a “Drive Only” condition, and so were matched for all factors except the presence of interference. In addition to a battery of cognitive control tests used to assess the breadth of training benefits (see Supplementary Table 2), the neural basis of training effects was evaluated using electroencephalography (EEG) recorded at Pre- and Post-training visits while participants performed a neural assessment version of NeuroRacer. Analysis showed that only the MTT group’s multitasking performance index significantly improved from Pre- (−64.2% cost) to Post-training (−16.2% cost; Figure 2b), thus supporting the role of interference during game play as a key mechanistic feature of the training approach. In addition, although cost reduction was observed only in the MTT group, equivalent improvement in component task skills was exhibited by both STT and MTT (see Supplemental Figures 4 and 5). This indicates that enhanced multitasking ability was not solely the result of enhanced component skills, but a function of learning to resolve interference generated by the two tasks when performed concurrently. Moreover, the d' cost improvement following training was not the result of a task tradeoff, as driving performance costs also diminished for the MTT group from Pre- to Post-training (see Supplementary Materials). Notably in the MTT group, the multitasking performance gains remained stable 6 months after training without booster sessions (at 6 months: −21.9% cost). Interestingly, the MTT group’s Post-training cost improved significantly beyond the cost level attained by a group of 20-year-olds who played a single session of NeuroRacer (−36.7% cost; Experiment 3; p< .001). Next, we assessed if training with NeuroRacer led to generalized enhancements of cognitive control abilities that are known to be impaired in aging (e.g., sustained attention, divided attention, working memory; see Supplementary Table 2) 12 . We hypothesized that being immersed in a challenging, adaptive, high-interference environment for a prolonged period of time (i.e., MTT) would drive enhanced cognitive performance on untrained tasks that also demanded cognitive control. Consistent with our hypothesis, significant group X session interactions and subsequent follow-up analyses evidenced Pre- to Post-training improvements in both working memory (delayed-recognition task with and without distraction 7 ; Figure 3a,b) and sustained attention (i.e. vigilance; Test of Variables of Attention (TOVA) 13 ) only for the MTT group (Figure 3c; see Supplementary Table 2). In addition, there were several statistical trends suggestive of improved Post-training performance on other cognitive control tasks (dual-tasking, useful field of view, and change detection task; see ANCOVAs in Supplementary Table 2). Note that although the working memory and sustained attention improvements were documented as more rapid responses to test probes, neither impulsivity (assessed with the alternate version of the TOVA) nor accuracy results showed significant group differences, revealing that training effects were not the result of a speed/accuracy trade-off. Importantly, these cognitive improvements were specific to working memory and sustained attention processes, and not the result of generalized increases in speed of processing, as no group X session interactions were found on two processing speed tasks (a stimulus detection task and the digit symbol substitution task; see Supplementary Table 2). Finally, only the MTT group exhibited a significant correlation between multitasking cost reduction (assessed with NeuroRacer) and improvements on an untrained cognitive control task (delayed-recognition with distraction) from Pre- to Post-training (Figure 3d). These important ‘transfer of benefits’ suggest that a common, underlying mechanism of cognitive control was challenged and enhanced by MTT with NeuroRacer. To assess this further, we examined the neural basis of training effects by quantifying event-related spectral perturbations (ERSP) and long-range phase coherence time-locked to the onset of each sign presented during NeuroRacer both Pre- and Post-training. We specifically assessed midline frontal theta (4–7Hz), a well-described EEG measure of cognitive control (e.g., working memory 14 , sustained attention 15 , and interference resolution 16 ) localized to the medial prefrontal cortex. In addition, we analyzed long-range theta coherence between frontal and posterior brain regions, a functional connectivity measure also associated with cognitive control (e.g., working memory 14 and sustained attention 15 ). Separate ANOVAs for theta power and coherence each revealed significant 3-way interactions of condition (‘Sign & Drive’, ‘Sign Only’) X session (pre, post) X group (MTT, STT, NCC; see Supplementary Figure 6). Further analysis revealed that for the ‘Sign & Drive’ condition, only the MTT group demonstrated a significant increase from Pre- to Post-training in both neural measures (see Figure 4a & b). These findings are consistent with other reports of training-driven modulations in prefrontal cortical activity of older adults 9,17 . Furthermore, the coherence results demonstrate for the first time modulation of a neural network in response to cognitive training in older adults. These findings evidence a shift in the rapid engagement of prefrontal cognitive control processes less than 400 ms after a sign appears and prior to the motor response (see Supplementary Figure 7 and Supplementary Table 1b), supporting training-induced neuroplasticity as the mechanistic basis of these training effects. As described above, both MTT and STT resulted in equivalent improvements on the NeuroRacer component tasks (see Supplementary Table 2 and Supplementary Figure 4), while only MTT led to broad enhancements both behaviorally (i.e., diminished multitasking costs, improved sustained attention and working memory) and neurally (i.e., enhanced midline frontal theta power and long-range coherence). This indicates that the training factor driving these effects was the interference generated when participants were motivated to engage in the two tasks simultaneously. Given that there were no clear differences in sustained attention or working memory demands between MTT and STT, transfer of benefits to these untrained tasks must have resulted from challenges to overlapping cognitive control processes. Of note, the use of a 3-D immersive and fun video game for training (see Methods) diverges from the sparse environments typically utilized in dual-task training studies 9,10 , which have not documented a similar degree of far transfer 10 . Coupled with previous findings of increased midline frontal theta on a variety of cognitive control tasks 18 , the current results support a common neural basis of cognitive control processes, which can be enhanced by immersion in an adaptive, high-interference environment. This interpretation is bolstered by evidence here indicating that MTT-induced increases in midline frontal theta power during “Sign & Drive” were positively correlated with both: i) sustained multitasking performance improvements (6 month – Post performance, Figure 4c), and ii) improvements in TOVA response times (Figure 4d). Thus, MTT-induced enhancement of midline frontal theta power was associated with the preservation of multitasking performance over time and with generalized benefits on an untrained cognitive control task, reflecting its utility as a neural signature of plastic cognitive control processes. Finally, we questioned if these neural measures that exhibited training effects in older adults were actually altered at baseline compared to younger adults, or if training boosted non-deficient neural processes. In a third experiment, we compared midline frontal theta power and long-range coherence from older adults prior to training to a naïve group of younger adults who were not trained (n=18; 20–29 y.o. (24.1 ± 2.9)). The multitasking costs for each group replicated findings of age-matched cohorts from Experiment 1. Both neural measures showed a main effect of group (see Supplementary Figure 8), indicating less theta power and coherence in older adults when processing signs in either condition (“Sign & Drive” depicted in Figure 4a, b). The absence of a significant condition X age group interaction for either neural measure (see Supplementary Figure 8) revealed that aging was associated with a general reduction in theta power and coherence when older adults discriminate visual stimuli, regardless of whether they are multitasking or singletasking. Notably, MTT led to changes in the neural processing of signs during “Sign & Drive” that reached a level comparable to neural activity patterns observed in younger adults. The mechanism underlying these neural findings are informed by a growing literature that shows deactivation of medial prefrontal cortical activity (suppression of a node of the ‘default network’ 19 ) during cognitively demanding tasks is associated with reduced susceptibility to internal distraction and better task performance 20 . Given that medial prefrontal activity is inversely correlated with midline frontal theta power 21 , increased levels of midline frontal theta exhibited by older adults following MTT may reflect more deactivation of medial prefrontal activity. And so, NeuroRacer training may benefit cognitive control abilities by improving the ability of older adults to suppress the default network during task engagement, a process known to be compromised in aging 22 . Future studies utilizing neurochemical and physiological manipulations are warranted to inform the causal nature of the relationship between medial prefrontal activity and training-induced performance effects observed here. This study offers neural and behavioral evidence of generalized positive effects from video game training on cognitive control abilities of older adults, with enhancements comparable to those observed in younger adults who are habitual action video game players; i.e., interference resolution 23 , working memory 24 and sustained attention 25 . Although reports of transfer of benefits following cognitive training in the older population are relatively rare 11,26 , the observed generalization supports the results of larger-scale training studies that demonstrate some degree of transfer to: i) untrained cognitive tasks 27,28 , and ii) subjective measures of daily living. 29 In contrast to these studies, and most other cognitive training experiments on older adults that report small to medium effect sizes for untrained tasks, the current findings document medium to large effect sizes (all > .50–1.0 (using Cohen’s d, see Methods)) for both cognitive control performance and neural measures versus either control group. The sustained multitasking cost reduction over time and evidence of generalizability to untrained cognitive control abilities provide optimism for the use of an adaptive, interference-rich, video game approach as a therapeutic tool for the diverse populations that suffer from cognitive control deficits (e.g., ADHD, depression, dementia). These findings stress the importance of a targeted training approach, as reinforced by a recent study that observed a distinct lack of transfer following non-specific online cognitive exercises 30 . In conclusion, we provide evidence of how a custom-designed video game targeting impaired neural processes in a population can be used to diagnosis deficits, assess underlying neural mechanisms, and enhance cognitive abilities. Methods Summary All participants had normal or corrected vision, no history of neurological, psychiatric, or vascular disease, and were not taking any psychotropic or hypertension medications. In addition, they were considered ‘non-gamers’ given that they played less than 2 hours of any type of video game per month. For NeuroRacer, each participant used their left thumb for tracking and their right index finger for responding to signs on a Logitech (Logitech, USA) gamepad controller. Participants engaged in three 3-minute runs of each condition in a randomized fashion. Signs were randomly presented in the same position over the fixation cross for 400 msec every 2, 2.5, or 3 seconds, with the speed of driving dissociated from sign presentation parameters. The multitasking cost index was calculated as follows: [(‘Sign & Drive’ performance - ‘Sign Only’ performance) / ‘Sign Only’ performance] * 100. EEG data for 1 MTT Post-training participant and 1 STT Pre-training participant were corrupted during acquisition. 2 MTT participants, 2 STT participants, and 4 NCC participants were unable to return to complete their 6-month follow-up assessments. Critically, no between-group differences were observed for neuropsychological assessments (p= .52) or Pre-training data involving: i) NeuroRacer thresholding for both Road (p= .57) and Sign (p= .43), ii) NeuroRacer component task performance (p> .10 for each task), iii) NeuroRacer multitasking costs (p= .63), iv) any of the cognitive tests (all ANOVAs at Pre-training: p≥ .26), v) ERSP power for either condition (p≥ .12), and, vi) coherence for either condition (p≥ .54). Methods Participants All participants were recruited through online and newspaper advertisements. For Experiment 1, 185 (90 male) healthy, right-handed individuals consented to participate according to procedures approved by the University of California at San Francisco. For Experiment 2 & 3, 60 (33 males) older adult individuals and 18 (9 male) young adult individuals participated without having been a part of Experiment 1 (see Supplementary Table 3 for demographic descriptions and Supplementary Figure 9 for Experiment 2 participant enrollment). Participants who were unable to perform the tasks, as indicated by tracking performance below 15% (6 individuals from Experiment 1, 8 individuals from Experiment 2), or a false positive rate greater than 70% (5 individuals from Experiment 1, 6 individuals from Experiment 2) during any one visit or across more than 4 individual training sessions, were excluded. Thresholding Prior to engaging in NeuroRacer, participants underwent an adaptive thresholding procedure for discrimination (nine 120 sec runs) and tracking ability (twelve 60 sec runs) to determine a ‘sign’ and ‘drive’ level that each participant would perform at ~80% accuracy (see Supplementary Figures 1 & 2). Having individuals engage each condition in their own ‘space’ following thresholding procedures facilitated a fairer comparison across ages and abilities. This is a frequently omitted procedure in other studies, and leads to difficulty interpreting performance differences (especially multitasking) as being the result of differences in interference processing or due to differences in component task skills. For the perceptual discrimination thresholding, each participant’s performance for a given run was determined by calculating a proportion correct score involving: i) correctly responding to targets, ii) correctly avoiding non-targets, iii) late responses to targets, and iv) responding to non-targets. At the end of each run, if this score was greater than 82.5%, the subsequent run would be played at a higher level which had a corresponding shorter time window for responses to targets. More specifically, the adaptive algorithm would make proportional level changes depending upon participants performance from this ~80% median, such that each 1.75% increment away from this median corresponded with a change in level (see Supplementary Figure 1a). Thus, a 90% performance would lead to a 40msec reduction in the time window, while a 55% (or less) performance would lead to a 100msec lengthening of said window. Thresholding parameters for road levels followed a similar pattern with each .58% increment away from the same median corresponded with a change in level (see Supplementary Figure 1b). These parameters were chosen following extensive pilot testing to: (1) minimize the number of trial runs until convergence was reached and (2) minimize convergence instability, while (3) maximizing sampling resolution of user performance. The first 3 driving thresholding blocks were considered practice to familiarize participants with the driving portion of the task and were not analyzed. A regression over the 9 thresholding runs in each a case was computed to select the ideal time window and road speed to promote a level of ~80% accuracy on each distraction free task throughout the experiment (see Supplementary Figure 2). All participants began the thresholding procedures at the same road (level 20) and sign levels (level 29). Conditions Following the driving and sign thresholding procedures, participants performed 5 different three minute 'missions', with each mission performed three times in a pseudo-randomized fashion. In addition to the ‘Sign Only’, ‘Drive Only’, and ‘Sign & Drive’ conditions, participants also performed a "Sign With Road" condition where the car was placed on 'auto pilot' for the duration of the run and participants responded to the signs, and a ‘Drive with Signs’ condition where participants were told to ignore the presence of signs appearing that and continue to drive as accurately as possible. Data from these two conditions are not presented here. Feedback was given at the end of each run as the proportion correct to all signs presented for the perceptual discrimination task (although we used the signal detection metric of discriminability (d') 31 to calculate our ‘Cost’ index throughout the study), and percentage of time spent on the road (see Supplementary Figure 10). Prior to the start of the subsequent run, participants were informed as to which condition would be engaged in next, and made aware of how many experimental runs were remaining. Including thresholding, the testing session encompassed 75min of gameplay. NeuroRacer training and testing protocol For Experiment 1, participants were seated in a quiet room in front of an Apple© MacBook Pro 5.3 laptop computer at an approximate distance of 65 cm from the 15" screen. For Experiment 2 and 3, participants were seated in a dark room with the screen ~100 cm from the participants. All training participants trained at their homes using an Apple© MacBook Pro 5.3 laptop computer while sitting ~60 cm from the screen (see Supplementary Figure 11a). For Experiment 1, each perceptual discrimination-based experimental run (180 sec) contained 36 relevant targets (green circles) and 36 lures (green, blue and red pentagons and squares). For Experiments 2 & 3, the sign ratio was to 24/48. Prior to training, each participant was given a tutorial demonstrating how to turn on the laptop, properly setup the joystick, navigate to the experiment, shown what the 1st day of training would be like in terms of the task, how to interpret what the feedback provided meant, and were encouraged to find a quiet environment in their home for their training sessions. If indicated by the participant, a lab member would visit the participant at their home to help set up the computer and instruct training. In addition, to encourage/assess compliance and hold participants to a reasonable schedule, participants were asked to plan their training days & times with the experimenter for the entire training period and enter this information into a shared calendar. Each participant (regardless of group) was informed that their training protocol was designed to train cognitive control faculties, using the same dialogue to avoid expectancy differences between groups. There was no contact between participants of different groups, and they were encouraged to avoid discussing their training protocol with others to avoid potentially biasing participants in the other groups. Each day of training, the participants were shown a visualization of a map that represented their ‘training journey’ to provide a sense of accomplishment following each training session (Supplementary Figure 11b). They were also shown a brief video that reminded them how to hold the controller, which buttons to use, their previous level(s) reached, and what the target would be that day for the perceptual discrimination condition. In addition, the laptop’s built-in video camera was also activated (indicated by a green light) for the duration of said run, providing i) visual assessment of task engagement, ii) motivation for participants to be compliant with the training task instructions, and iii) information about any run where performance was dramatically poorer than others. Participants were discouraged from playing 2 days in a row, while they were encouraged to play at the same time of day. MTT participants were reminded that an optimal training experience was dependent upon doing well on both their sign and drive performance without sacrificing performance on one task for the other. While the STT group were provided a ‘Driving’ or ‘Sign’ score following each training run, the MTT group were also provided an ‘Overall’ score following each run as a composite of performance on both tasks (see Supplementary Figures 5 and 11). Following the completion of every 4th run, participants were rewarded with a ‘fun fact’ screen regarding basic human physiology ( before beginning their subsequent training run. To assess if training was a ‘fun’ experience, participants in each training group rated the training experience on their final visit to the laboratory on a scale of 1 (minimally) to 10 (maximally) (MTT: 6.5 ± 2.2; STT 6.9 ± 2.4; t= .65, p= .52). Critically, training groups did not differ on their initial thresholding values for both Road (F(2,45)= .58, p= .57) and Sign (F(2,45)= .87, p= .43). Each laptop was configured to transmit NeuroRacer performance data to our secure lab server wirelessly using DropBox® as each run was completed. This facilitated monitoring for compliance and data integrity in a relatively real-time fashion, as participants would be contacted if i) there was a failure to complete all 20 training runs on a scheduled training day, ii) ‘Sign Only’ and ‘Drive Only’ performance was suggestive that a problem had occurred within a given training session, and iii) a designated training day was missed. Individuals without wireless internet in their home were instructed to visit an open wireless internet location (e.g., coffee shop, public library) at least once a week to transfer data, and if this was not an option, researchers arranged for weekly home visits to acquire said data. All participants were contacted via email and/or phone calls on a weekly basis to encourage and discuss their training; similarly, in the event of any questions regarding the training procedures, participants were able to contact the research staff via phone and email. Pre- and Post-training evaluations involving cognitive testing and NeuroRacer EEG took place across 3 different days (appointment and individual test order were counterbalanced), with all sessions completed approximately within the span of a week (total number of days to complete all Pre-training testing: 6.5 days ± 2.2; Post-training testing: 6.1 days ± 1.5). Participants returned for their 1st Post-training cognitive assessments 2.0 ± 2.2 days following their final training session. While scheduled for 6 months after their final testing session, the 6 month follow-up visits actually occurred on average 7.6 months ± 1.1 afterwards due to difficulties in maintaining (and rescheduling) these distant appointments. Critically, no group differences were present regarding any of these time-of-testing measures (F< 1.81, p> .18 for each comparison). Cognitive Battery The cognitive battery (see Supplementary Table 2) consisted of tasks spanning different cognitive control domains: sustained attention (TOVA; see Supplementary Figure 12a), working memory (delayed-recognition- see Supplementary Figure 12b); visual working memory capacity (see Supplementary Figure 13), dual-tasking (see Supplementary Figure 14), useful field of view (UFOV; see Supplementary Figure 15), and two control tasks of basic motor and speed of processing (stimulus detection task, digit symbol substitution task; see Supplementary Figure 16). Using the analysis metrics regularly reported for each measure, we performed a mixed model ANOVA of Group (3: MTT, STT, NCC) X Session (2: pre, post) X Cognitive test (11; see Supplementary Table 2), and observed a significant 3-way interaction (F(20, 400)= 2.12, p= .004) indicative that training had selective benefits across group and test. To interrogate this interaction, each cognitive test was analyzed separately with Session X Group ANOVAs to isolate those measures that changed significantly following training. We also present the p-value associated with the ANCOVAs for each measure in Supplementary Table 2 (dependent measure = Post-training performance, covariate = Pre-training performance), which showed a similar pattern of effects as most of the 2-way ANOVAs. The ANCOVA approach is considered to be a more suitable approach when post-test performance that is not conditional/predictable based on pre-test performance is the primary outcome of interest following treatment, as opposed to characterizing gains achieved from Pre-training performance (e.g., group X session interaction(s)) 32 ; however, both are appropriate statistical tools that have been used to assess cognitive training outcomes 27,33 (see Supplementary Figure 17 as an example). EEG Recordings and Eye Movements Neural data were recorded using an Active Two head cap (Cortech-Solutions) with a BioSemiActiveTwo 64-channel EEG acquisition system in conjunction with BioSemiActiView software (Cortech-Solutions). Signals were amplified and digitized at 1024 Hz with a 16-bit resolution. Anti-aliasing filters were used and data were band-pass filtered between 0.01–100 Hz during data acquisition. For each EEG recording session, the NeuroRacer code was modified to flash a 1x1” white box for 10msec at one of the corners on the stimulus presentation monitor upon the appearance of a sign. A photodiode ( captured this change in luminance to facilitate precise time-locking of the neural activity associated with each sign event. During the experiment, these corners were covered with tape to prevent participants from being distracted by the flashing light. To ensure that any training effects were not due to changes in eye movement, electrooculographic data were analyzed as described by Berry and colleagues 34 . Using this approach, vertical (VEOG = FP2-IEOG electrodes) and horizontal (HEOG= REOG-LEOG electrodes) difference waves were calculated from the raw data and baseline corrected to the mean prestimulus activity. The magnitude of eye movement was computed as follows: (VEOG2 + HEOG2)1/2. The variance in the magnitude of eye movement was computed across trials and the mean variance was specifically examined from −200 to 1000msec post-stimulus onset. The variance was compared i) between sessions for each group’s performance on the ‘Sign and Drive’ and ‘Sign Only’ conditions, ii) between groups at each session for each condition, and iii) between young and older adults on each condition. We used two-tailed t-test that were uncorrected for multiple comparisons at every msec time point to be as conservative as possible. There was no session difference for any group on the ‘Sign Only’ condition (p> .05 for each group comparison); similarly, there were no differences for the MTT or NCC groups on the ‘Sign & Drive’ condition (p> .30 for each comparison), with the STT group showing more variance following training (p= .01). With respect to Experiment 3, there were also no age differences on either condition (p> .45 for each comparison). This indicates that the training effects observed were not due to learned eye movements, and that the age-effects observed were also not a function of age-related differences in eye movements as well. EEG analysis Preprocessing was conducted using Analyzer software (Brain Vision, LLC) then exported to EEGLAB 35 for event-related spectral perturbations (ERSP) analyses. ERSP is a powerful approach to identifying stable features in a spontaneous EEG spectrum that are induced by experimental events, and have been used to successfully isolate markers of cognitive control 36,37 . We selected this approach because we felt that a measure in the frequency domain would be more stable than other metrics given the dynamic environment of NeuroRacer. Blinks and eye-movement artifacts were removed through an independent components analysis (ICA), as were epochs with excessive peak-to-peak deflections (±100 µV). Given the use of d’, which takes into account performance on every trial, we collapsed across all trial types for all subsequent analyses. −1000 to +1000msec epochs were created for ERSP total power analysis (evoked power + induced power), with theta band activity analyzed by resolving 4–100 Hz activity using a complex Morlet wavelet in EEGLAB and referenced to a −900 to −700 pre-stimulus baseline (thus relative power (dB)). Assessment of the “Sign & Drive” ERSP data in 40msec time bins collapsing across all older adult participants and experimental sessions revealed the onset of peak midline frontal activity to be between 360–400msec post-stimulus, and so all neural findings were evaluated within this time window for the older adults (see Supplementary Figure 7 for these topographies). For younger adults, peak theta activity occurred between 280–320 msec, and so for across-group comparisons, data from this time window was used for younger adults. The cognitive aging literature has demonstrated delayed neural processing in older adults using EEG 38,39 . For example, Zanto and colleagues 38 demonstrated that older adults show similar patterns of activity as younger adults in terms of selective processing, but there is a time shift to delayed processing with aging. For the data generated in this study, presented topographically in Supplementary Figure 7, it was clear that the peak of the midline frontal theta was delayed in older versus younger adults. To fairly assess if there was a difference in power, it was necessary to select different comparison windows in an unbiased, data-driven manner for each group. Coherence data for each channel was first filtered in multiple pass bands using a two-way, zero phase-lag, finite impulse response filter (eegfilt.m function in EEGLAB toolbox) to prevent phase distortion. We then applied a Hilbert transform to each of these time series (hilbert.m function), yielding results equivalent to sliding window FFT and wavelet approaches 40 , giving a complex time series, hx [n] = ax [n]exp(iϕ x [n]) where ax[n] and φx[n] are the instantaneous amplitudes and phases, respectively. The phase time series φx assumes values within (−π, π] radians with a cosine phase such that π radians corresponds to the trough and 0 radians to the peak. In order to compute PLV for theta phase, for example, we extract instantaneous theta phases φθ[n] by taking the angle of hθ[n]. Event-related phase time-series are then extracted and, for each time point, the mean vector length Rθ[n] is calculated across trials (circ_r.m function in CircStats toolbox) 41 . This mean vector length represents the degree of PLV where an R of 1 reflects perfect phase-locking across trials and a value of 0 reflects perfectly randomly distributed phases. These PLVs were controlled for individual state differences at each session by baseline correcting each individual’s PLVs using their −200 to 0 period (thus, a relative PLV score was calculated for each subject). Statistical analyses Mixed model ANOVAs with: i) decade of life (Experiment 1), ii) training group (Experiment 2), or iii) age (Experiment 3) as the between-group factor were used for all behavioral and neural comparisons, with planned follow-up t-tests and the Greenhouse-Geisser correction utilized where appropriate. One-tailed t-tests were utilized to interrogate group differences for all transfer measures given our a priori hypothesis of the direction of results following multitask training. All effect size values were calculated using Cohen’s d 42 and corrected for small sample bias using the Hedges and Olkin 43 approach. The neural-behavioral correlations presented included only those MTT participants who demonstrated increased midline frontal theta power following training (14/15 participants). For statistical analyses, we created 1 frontal and 3 posterior composite electrodes of interest (EOI) from the average of the following electrodes: AFz, Fz, FPz, AF3, and AF4 (medial frontal), PO8, P8, and P10 (right-posterior), PO7, P7, and P9 (left-posterior); POz, Oz, O1, O2 and Iz (central-posterior), with PLVs calculated for each frontal-posterior EOI combination separately. For the coherence data, the factor of posterior EOI location (3) was modeled in the ANOVA, but did not show either a main effect or interaction with the other factors. Supplementary Material 1

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          • Article: not found

          EEGLAB: an open source toolbox for analysis of single-trial EEG dynamics including independent component analysis.

          We have developed a toolbox and graphic user interface, EEGLAB, running under the crossplatform MATLAB environment (The Mathworks, Inc.) for processing collections of single-trial and/or averaged EEG data of any number of channels. Available functions include EEG data, channel and event information importing, data visualization (scrolling, scalp map and dipole model plotting, plus multi-trial ERP-image plots), preprocessing (including artifact rejection, filtering, epoch selection, and averaging), independent component analysis (ICA) and time/frequency decompositions including channel and component cross-coherence supported by bootstrap statistical methods based on data resampling. EEGLAB functions are organized into three layers. Top-layer functions allow users to interact with the data through the graphic interface without needing to use MATLAB syntax. Menu options allow users to tune the behavior of EEGLAB to available memory. Middle-layer functions allow users to customize data processing using command history and interactive 'pop' functions. Experienced MATLAB users can use EEGLAB data structures and stand-alone signal processing functions to write custom and/or batch analysis scripts. Extensive function help and tutorial information are included. A 'plug-in' facility allows easy incorporation of new EEG modules into the main menu. EEGLAB is freely available ( under the GNU public license for noncommercial use and open source development, together with sample data, user tutorial and extensive documentation.
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            • Article: not found

            The brain's default network: anatomy, function, and relevance to disease.

            Thirty years of brain imaging research has converged to define the brain's default network-a novel and only recently appreciated brain system that participates in internal modes of cognition. Here we synthesize past observations to provide strong evidence that the default network is a specific, anatomically defined brain system preferentially active when individuals are not focused on the external environment. Analysis of connectional anatomy in the monkey supports the presence of an interconnected brain system. Providing insight into function, the default network is active when individuals are engaged in internally focused tasks including autobiographical memory retrieval, envisioning the future, and conceiving the perspectives of others. Probing the functional anatomy of the network in detail reveals that it is best understood as multiple interacting subsystems. The medial temporal lobe subsystem provides information from prior experiences in the form of memories and associations that are the building blocks of mental simulation. The medial prefrontal subsystem facilitates the flexible use of this information during the construction of self-relevant mental simulations. These two subsystems converge on important nodes of integration including the posterior cingulate cortex. The implications of these functional and anatomical observations are discussed in relation to possible adaptive roles of the default network for using past experiences to plan for the future, navigate social interactions, and maximize the utility of moments when we are not otherwise engaged by the external world. We conclude by discussing the relevance of the default network for understanding mental disorders including autism, schizophrenia, and Alzheimer's disease.
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              Conflict monitoring and cognitive control.

              A neglected question regarding cognitive control is how control processes might detect situations calling for their involvement. The authors propose here that the demand for control may be evaluated in part by monitoring for conflicts in information processing. This hypothesis is supported by data concerning the anterior cingulate cortex, a brain area involved in cognitive control, which also appears to respond to the occurrence of conflict. The present article reports two computational modeling studies, serving to articulate the conflict monitoring hypothesis and examine its implications. The first study tests the sufficiency of the hypothesis to account for brain activation data, applying a measure of conflict to existing models of tasks shown to engage the anterior cingulate. The second study implements a feedback loop connecting conflict monitoring to cognitive control, using this to simulate a number of important behavioral phenomena.

                Author and article information

                12 March 2014
                5 September 2013
                10 April 2014
                : 501
                : 7465
                : 97-101
                Departments of Neurology, Physiology and Psychiatry, and the Center for Integrative Neuroscience, University of California, San Francisco
                Author notes
                Corresponding Authors: Joaquin A. Anguera, PhD & Adam Gazzaley, MD, PhD, University of California, San Francisco, Mission Bay – Sandler Neurosciences Center, UCSF MC 0444, 675 Nelson Rising Lane, San Francisco, CA 94158, Phone: 415-502-7322, joaquin.anguera@ , adam.gazzaley@

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