dataesr/scientific-paragraphs-categorization huggingface dataset:
Extensions The simulator, being open source, allows the tailoring of code to provide modifications and extensions. An example extension is the addition of a graphical interface to modify parameters and simulate neural fields. Figure  8  shows an example interface coded with the wxPython 6  toolkit. Simulations are started, paused, continued, and started anew by clicking a button. Neural field parameters can be modified prior to and during simulations by clicking on the appropriate area of the interface and completing a pop-up dialogue. Running simulations are automatically paused when a mouse hovers above parameter areas of the interface. There is a symbiosis among the show3D library discussed in Section 2. 3 and the parameter selection interface. It is possible to view the external input stimulus, kernel, and firing rate in the GLFW window by adding a mouse event and hovering over these sections to automatically view the respective matrices.
DISCUSSION The Neural Field Simulator and its dependencies are crossplatform. However, the simulator interacts with graphics hardware using system-specific drivers which can result in problems on some operating systems. The graphical user interface in Section 3. 4 is an example of this where the cross platform wxPython toolkit uses OpenGL to draw to the screen. The show3D library likewise uses OpenGL to interact with GPU. The graphical user interface and show3D library function symbiotically on Mac systems via the Apple Graphics Library. Conversely, on other operating systems such as Linux and Windows, unfortunately the separate utilization of OpenGL causes the simulator to crash. To this end, the current version of the simulator is released without the addition of extensions in order to operate properly on every major operating system.
Nevertheless, a graphical interface can be a good choice with an appropriate single operating system. Apart from the software implementation, in future work some model assumptions can be released. The square geometry can be recast easily to a rectangular geometry, whereas more general geometries (e. g. , the impressive implementation work in The Virtual Brain Sanz  Leon et al. , 2015)  will take more numerical effort. Periodic boundary conditions guarantee the simple application of the FFT, effective implementations of other boundary conditions like Dirichlet conditions [V(z, t) =const, z ∈ ∂ ] will demand some implementation changes in the spatial integral computation. Such modifications may still retain the fundamental implementation of the FFT. In contrast, rejecting the homogeneity hypothesis of spatial interactions, i.
Parents wore both opaque sunglasses and noise-cancelling headphones with masking music to ensure that they could not influence their infant's response. Two hidden loudspeakers were placed behind the screen. A hidden camera located underneath the screen allowed the experimenter, who could see the infant but not the stimuli, to register online for each trial whether the infant was looking or not towards the screen. This coding was then used in later analysis to reject trials when infants were not watching. Stimuli were presented using the Psychophysics toolbox for Matlab  55. During the familiarization phase, face and flower stimuli chosen randomly from the stimulus list were presented in alternation for 1 s each, with a 1. 5 s delay and for a total of 10 trials. Each visual stimulus was presented simultaneously with a given auditory cue (that is, both onsets were synchronous).
Which of the two physical sounds predicted the visual target category was counterbalanced across participants (for example, sound 'A' predicted face-stimuli for one half of participants, while the same sound predicted flower stimuli for the other half). EEG recordings and data processing. The electroencephalogram was continuously digitized at 250 Hz using a 128-electrodes HydroCel net (EGI; Eugene, OR, USA) referenced to the vertex. The signal was first re-referenced to the average activity, then high-pass filtered at 0. 2 Hz, low-pass filtered at 20 Hz and finally segmented from À 150 ms to þ 1,700 ms relative to the onset of the target stimulus. Infant's gaze was constantly monitored throughout the experiment, and any trial in which the infant looked away from the screen was rejected. An average of 22.
Acknowledgements This research was supported by funding from the  European Research Council  to S. K. , and from the  Carlsberg Foundation  to S. G. We thank  C. Girard  (data acquisition),  E. Dupoux  (discussion) and  F. Goffinet  ( Hospital Cochin ) for their help. This research was supported by  ANR  grants ( ANR-10-LABX-0087  and  ANR-10-IDEX-0001-02 ).
Funding The research leading to these results has received funding from the  People Programme  ( Marie Curie Actions ) of the European Union's  Seventh Framework Programme  (FP7/2007-2013) under  Research Executive Agency  Grant Agreement n° 622738 awarded to S. Mathôt. In addition, this research was funded by  Vidi  Grant  452-13-008  from the  Netherlands Organization for Scientific Research  to  S. Van der Stigchel.
Subjects A total of 42 subjects participated in this study, 31 PD patients and 11 healthy controls. PD patients aged 43-74 years were recruited from the movement disorder clinic at Nantes University Hospital, France. Diagnosis of PD was made according to criteria provided by the United Kingdom Parkinson's Disease Survey Brain Bank  [16]. Collected demographic data included gender, age at onset and disease duration, as well as age at colonoscopy. Complete drug history was obtained, and an approximation of the cumulative dose of L-dopa was made based on the equation developed by Parkkinen and collaborators  [17]. Control subjects were healthy subjects who had a normal colonoscopy performed for colorectal cancer screening. All controls subjects underwent a detailed neurological examination to rule out PD symptoms and cognitive deficiency.
Expression of the tight junction protein occludin is decreased in PD We next investigated whether structural changes in the IEB occur in PD. The expression levels of the TJs proteins ZO-1 and occludin were analyzed by Western blot in colonic biopsies from PD subjects and healthy controls. A significant decrease in the expression of occludin was observed in colonic samples of PD patients as compared to controls (Figure  3A  and B ). A doublet band of approximately 220 kDa was observed on Western blot with antibodies against ZO-1 (Figure  3A ). As previously shown, these two bands most likely represent the two ZO-1 isoforms  [26, 27]. By contrast to occludin, no change in ZO-1 expression levels was observed in PD whether the two bands were quantified together (Figure  3C ) or separately (data not shown).
Acknowledgements This work was supported by a grant from the  Michael J. Fox Foundation for Parkinson's Research  ( Rapid Response Innovation Award 2013 ) and  France Parkinson  to PD. LLV is supported by a grant from  Nantes University Hospital  (Appel d'offre interne 2012, Grant number  RC12_0264 ) and  France Parkinson. TC is supported by a grant from centre d'entraide et de coordination des associations de parkinsoniens (CECAP).
Currently, raised-line maps augmented with interactive auditory messages appear to be the more usable technology to provide visually impaired users with accessible maps. Indeed, complex spatial graphics can be explored with both hands and all the fingers. In addition, the device is cheap in comparison to refreshable displays. However, in order to enhance usability, it is essential to provide the users with tools that facilitate the production of raised-line maps with the corresponding interactive numerical content. We suggest that these tools should rely on the availability of numerous sources of spatial (including geographic) data that are free to use. OpenStreetMap 3  , for example, is a collaborative project that aims at creating a free and editable map of the world. These maps can be annotated with a variety of tags.
CURRENT AND FUTURE WORK AccessiMap 4  is a research project that aims to improve map accessibility for the visually impaired. It brings together two research laboratories (IRIT, Toulouse, FR, and Telecom ParisTech, Paris, FR), a company that develops open software (Makina Corpus, Toulouse, FR), and an educational center for blind and visually impaired people (CESDV-IJA, Toulouse, FR).
Scenarios and Expected Contributions Two major contributions of the AccessiMap project are expected: 1/ the development of a web-based authoring editor for the production of tactile graphics (overlays) and corresponding digital contents, which will be used on personal touch sensitive devices (tablets); 2/ the design and evaluation of a prototype of a tabletop tangible interface that enables the autonomous exploration of spatial data by visually-impaired users but also encourages the collaboration with sighted and other visually impaired users. In collaboration with a number of specialized teachers and visually impaired persons we identified two scenarios that will serve as a guiding principle throughout the project. The first scenario concerns the production and the use of interactive tactile maps.
Ongoing work: Development of an open-source webbased editor based on OpenStreetMap data In collaboration with Makina Corpus company, we are currently developing a web-based editor to facilitate the production of tactile maps by (semi)-automatically selecting and adapting OpenStreetMap data or an existing SVG file. As we previously said, the content displayed on a tactile map differs from that of a visual map. Then the editor must allow the semi-automatic simplification of a visual map, but also the addition of mandatory elements, such as the presence of obstacles or the exact location of pedestrian crosswalks. OpenStreetMap data does not always meet these requirements but it can be adapted. Contents can be simplified with filters and simple geometrical transformations. Data can also be updated by adding new tags, which are adapted to the needs of visually impaired persons.
Participants and Selection of Cultures Data were gathered from a total of 5216 respondents in 44 cultures across six continents. After removing individuals with at least one missing answer on the measures of intelligence or honesty, the final sample that was analysed consisted of 4519 participants. In Table  1 , we present demographic characteristics for all national samples. The gender distribution was 56. 5 % female and 43. 5 % male. The mean age of participants was 22. 36 years (SD 5. 50). Participants were students from a variety of different disciplines who were recruited at each author's university. All data were collected from 2011 to 2015. We managed to collect data in forty-two out of the sixty-two cultures involved in the GLOBE project  (House et al. 2004 ). We also collected data in Norway (for which practices on the GLOBE dimensions were calculated by Warner-Søderholm 2010) and in Pakistan (ranked high on the corruption dimensions, which relates to our second hypothesis).
e. , honest, false, authentic, and unnatural). Questionnaires in cultures that joined the project later also included five items from Rosenberg's self-esteem scale (1965), three items from Dunton and Fazio's motivation to control prejudiced reactions scale (1997), and three additional  attributes (i. e. , attractiveness, friendliness, and familiarity) using the aforementioned 7-point scale. The current report is of the data provided by all participants. Photographs of the same persons posing neutral and smiling expressions were taken from the Center for Vital Longevity Face Database  (Minear and Park 2004). The questionnaire, in the form of a small booklet, started with the following instructions: ''Research shows that people can quite accurately evaluate others based on their looks. Can you help us and rate some faces?''.
Acknowledgments We thank all the supporting team-members involved in the translation procedures and data collections. Research was supported by the  Polish NCN  Grant  2011/03/N/HS6/05112 (K. K. )  and  Chinese NNSF  Grant  31200788  (C. X). Open Access This article is distributed under the terms of the Creative Commons Attribution 4. 0 International License (http://creativecommons. org/licenses/by/4. 0/),which permits unrestricted use, distribution, and reproduction in any medium, provided 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.
Participants Seventeen healthy participants provided written informed consent to participate in the study. All participants had normal or corrected-to-normal vision, and were free of a history of neuropsychiatric disorders. The study protocol was approved by the Institutional Review Board at Indiana University, Bloomington (IRB 1202007935). High-density (256 channel) EEG and behavioral data were collected from all participants, and data from 1 individual had to be excluded from further analysis due to a large amount of artifactual EEG contamination from facial/neck muscle activity, as well as line noise. Hence, data from 16 participants (7 males, 9 females) with an average age of 26 years (range 21-34 years) were submitted for analysis. The 16 participants were right-handed, as assessed by the Edinburgh Handedness Inventory (mean: R64.
, 1998) , and to ensure that subjects did not visualize a ''face'' in the dynamic control stimulus. White line-drawn faces on a black background had been originally created from a multimarker recording of facial expressions using specialized biological motion creation software from which lines were generated between some of the point lights  [Elite Motion Analysis System (BTS, Milan, Italy) ]. The black and white control stimuli had originally been created by extracting line segments from the line-drawn face and spatially re-arranging them in the visual space in an earlier version of Photoshop (Adobe Systems, Inc. ), so that the face was no longer recognizable  (Puce et al. , 2003). The existing line-drawn faces were modified for  Rossi et al. (2014)  in Photoshop CS5 (Adobe Systems, Inc. ) by adding a schematic iris to the face which when spatially displaced could signal a gaze change on the stimulus face.
EEG Data Acquisition A Net Amps 300 high-impedance EEG amplifier and NetStation software (V4. 4) were used to record EEG from a 256-electrode HydroCel Geodesic Sensor Net (Electrical Geodesics Inc. ) while the participant sat in a comfortable chair and performed the task in a dimly lit, humidified room. Continuous 256channel EEG data were recorded with respect to a vertex reference using a sampling rate of 500 Hz and bandpass filter of 0. 1-200 Hz (the ground electrode was sited on the midline parietal scalp). Stimulus delivery and subject behavioral responses were time-stamped onto all EEG files. Impedances were maintained below 60 kΩ as per the manufacturer's recommended guidelines. Impedances were tested at the beginning of the experimental session and then once more at the half-way point of the experiment, allowing any high-impedance electrode contacts to be adjusted if necessary.
EEG Data Preprocessing EEG data were first exported from EGI Net Station software as simple binary files. The same pre-processing procedure was applied to the ERP and ERSP analyses. All EEG pre-processing procedures were performed using functions from the EEGLAB toolbox  (Delorme and Makeig, 2004)  running under MATLAB R2010b (The Mathworks, Natick, MA). EEG data were first segmented into 1700 ms epochs: 572 ms pre-stimulus baseline and 1082 ms after apparent motion onset. EEG amplitude at each trial was normalized relative to the pre-stimulus baseline based on the event-markers, identifying each trial type. ERP data were displayed using a 200 ms pre-motion onset and 600 ms after the motion transition-see Figure  3. [A manufacturerspecified latency correction factor was applied to all behavioral data and epoched ERP data.
In our case, given a sampling rate of 500 Hz, a correction of 18 ms was made, as per manufacturer guidelines]. EEG epochs were first visually inspected to identify and exclude bad channels from each individual subject EEG dataset. The electrodes identified as bad differed between subjects; average number of ''bad'' electrodes was 22 ± 2. 15 (standard error of mean) out of 256 channels. Epochs with very large artifacts (e. g. , very large subject movements and channel drifts) were manually rejected prior to subjecting the EEG data subsequent artifact detection analyses. Independent Component Analysis (ICA) was used to identify and subtract components representing artifacts such as eye movements, eye blinks, carotid pulse, muscle activity and line-noise  (Bell and Sejnowski, 1995; Delorme and Makeig, 2004).
This allowed trials with eyeblinks to be adequately corrected, and allowed these trials to be included in the analysis. A total of 32 ICA components were generated for each participant's EEG dataset. Eyeblinks, cardiac artifact and muscle activity were identified in isolated ICA components. Following removal of artifactual ICA components and reconstitution of the EEG signal, interpolation of bad channels was performed to regenerate a 256-channel EEG dataset. Bad channels were interpolated using a spherical interpolation: electrical activity was interpolated with respect to the surrounding nearest neighbor electrodes. Data were re-referenced to a common average reference. ERP components such as the N170 and the vertex positive potential (VPP) amplitude have previously been shown to be very sensitive to reference location  (Joyce and Rossion, 2005).
EEG/ERP Data Analyses Two temporo-occipital 9 electrode clusters including equivalent 10-10 system sites P07/P9 and P08/P10 were chosen for further analyses, based on inspection of the grand averaged data from the current study and previously reported maxima in N170 amplitudes that used 4 electrode clusters for 64-and 128-channel EEG derivations, and P09 and P10 for smaller electrode arrays of 10-10 system sites  (Puce et al. , 2000 (Puce et al. , , 2003;; Carrick et al. , 2007; Brefczynski-Lewis et al. , 2011; Rossi et al. , 2014 ; Figures  2, 3 ). Averaged data from the 9 electrodes in each hemispheric cluster were used in all subsequent ERP analyses. Similarly, singletrial EEG data recorded from the same 9 electrodes in each hemispheric cluster were used for ERSP analysis.
Analysis of Event-Related Potentials A digital 40 Hz infinite impulse response (IIR) low-pass filter was applied to the artifact-free behaviorally correct EEG data. Average ERPs were generated for each of the eight conditions and for each subject (about 200 trials per condition per subject on average). The ERPs from all subjects were averaged to generate a grand-average set of ERP waveforms for each condition and EEG channel. Data from each 9 electrode temporo-occipital cluster were extracted and the average time-course for each electrode cluster was generated for subject and condition, and was subsequently used for calculating N170 amplitude and latency. In line with previous work  (Puce et al. , 2003) , we focused on the N170 as a neural marker of the perception of facial motion. In our data, consistent with previous studies, the N170 showed a lateralized posterior scalp distribution (Figure  2 ).
Analysis of Event-Related Spectral Perturbations All analyses were performed using custom in-house routines written using the EEGLAB toolbox  (Delorme and Makeig, 2004)  running under MATLAB. Artifact-free, behaviorally correct EEG segments were convolved with a linearly increased Morletwavelet on a trial-by-trial basis for each condition and subject. Specifically, the length of the wavelet increased linearly from 1 to 12 cycles across the frequency range of 5-50 Hz (theta, alpha, beta, and low-gamma). The linear increment of wavelet cycles is a commonly used practice when calculating spectral components in neurophysiological data, so that temporal resolution can be comparable for lower and higher EEG frequencies  (Le Van Quyen et al. , 2001)  (for a detailed account on spectral analyses of EEG see  Herrmann et al.
, 2005). After the EEG signals in each trial were convolved with a Morlet wavelet, they were transformed into power, and the resulting values were then averaged across trials. We analyzed the spectral power of components in the theta (5-8 Hz), alpha (8-12 Hz), beta (12-30 Hz), and low-gamma (30-50 Hz) EEG frequencybands as they evolved over the post-movement epoch. In order to extract even-related spectral power from raw power, a standard baseline procedure was applied in a trial by trail basis  (Grandchamp and Delorme, 2011). The window used as baseline comprised data points between -200 and 0 ms pre-stimulus range. Induced activity is defined as EEG activity that is elicited to the stimulus, but may not be precisely time-or phase-locked to the stimulus transition (in this case apparent motion onset).
ERP peak analysis Differences in temporo-occipital N170 peak amplitude and latency were evaluated using a 4-way repeated-measures ANOVA with Hemisphere (Left, Right), Configuration (Face, Control), Stimulus Type (Real, Line) and Motion (Away, Toward) as within-subjects factors using SPSS for MAC 18. 0 (SPSS Inc. ). Significant main effects were identified at P values of less than 0. 05 (after Greenhouse-Geisser correction). Contrasts were evaluated using the Bonferroni criterion to correct for multiple comparisons with P values of less than 0. 05 identifying significant effects. Furthermore, to specifically assess the specificity of the effect to REAL FACE stimuli, we performed paired t-tests between each motion conditions for each stimulus condition.
ERSP analysis To measure the complete temporal extent of effects over frequency, we used a bootstrap approach (N = 1000 bootstraps), identifying time-frequency data points of statistically significant differences based on data-driven 95% confidence intervals (as described and implemented in  Pernet et al. , 2011)  from the data of the two 9 electrode clusters. Non-parametric permutation was used to estimate the distribution under the null hypothesis of no differences in oscillatory amplitude between the pair of conditions. Due to our paired design, when a subject was selected randomly, results from all his or her conditions were included in that sample. For each condition, we averaged the data across (resampled) participants and computed differences between conditions. Thus, for each one of the observed mean differences between conditions for a given frequency at each time-point, a t-statistic was calculated.
At this stage, time points were evaluated according to a threshold set if their t-statistic corresponded to a value below 0. 05 according to the Student's t-distribution. This procedure was repeated for all ERSP time-points at each frequency. Temporally contiguous threshold time points were grouped into temporal clusters. At each bootstrap iteration, the temporal cluster mass was computed as the sum of the t-statistics over consecutively significant time-points, with the maximum cluster mass being recorded. Finally, temporal clusters in the observed data were deemed significant if their mass exceeded the maximum cluster mass of 95% of all bootstrap replicates (corresponding to a significance level of 0. 05). This method allowed correction for multiple comparisons. Thus, the cluster mass statistic identified temporal regions with significant differences while avoiding false-positives arising from multiple comparisons  (Pernet et al.