vision analyzer2, by Brain Products - Product details

1

Fear Conditioning ECG Processing

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The electrocardiogram was recorded with a sampling rate of 1,000 Hz from three adhesive Ag/AgCl electrodes, placed underneath the right clavicle, as well as the left and right costal arch.
Processing of the heart rate was performed using the Vision Analyzer 2.0 Software (Brain Products Inc., Munich, Germany). R-waves were detected from the ECG recordings using a semi-automatic method. After visual inspection, R-R-intervals were converted to HR (in beats per minute, bpm) and then averaged across conditions. Heart rate was analyzed with baseline correction, by subtracting a baseline of 1,000 ms before stimulus onset. For quantifying CS-evoked fear bradycardia, mean heart rate (changes) between 4 and 6 s after CS onset were extracted similar to other fear conditioning studies (Hamm, Greenwald, Bradley, & Lang, 1993; (link)Sperl, Wroblewski, Mueller, Straube, & Mueller, 2021) (link). Due to loss of sensor contact, one subject had to be excluded from the analysis, resulting in n = 51 participants for ECG analysis.

Stegmann Y., Andreatta M., & Wieser M.J. (2022). The effect of inherently threatening contexts on visuocortical engagement to conditioned threat.

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2

Electrodermal Activity Acquisition and Analysis

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EDA: Electrodermal activity was recorded using two Ag/AgCl electrodes filled with isotonic (0.5% NaCl) electrolyte medium placed on the thenar and hypothenar eminences of the left palmar surface. The signal was recorded with a V-Amp amplifier and Vision Recorder Software (BrainProducts Inc., Munich, Germany), using a sampling rate of 1,000 Hz and an online notchfilter at 50 Hz. Analysis was then performed using Vision Analyzer 2.0 Software (BrainProducts Inc., Munich, Germany). After manually scanning for artifacts, trough values within a time window of 1,000 ms to 4,000 ms and peak values within 1,000 ms to 5,000 ms after stimulus onset were identified and extracted (Boucsein et al., 2012) (link). Skin conductance responses smaller than 0.02 μS were scored as zero responses. In total, eight participants did not show a single detectable skin conductance response and were consequently excluded from SCR analysis, resulting in n = 44 participants for SCR analysis. For the remaining participants, non-zero SCRs could be observed in 17.7% of the trials during acquisition and in 13.3% of the trials during the test phase. All SCRs were square-root-transformed to account for eventual skewedness of the underlying data.

Stegmann Y., Andreatta M., & Wieser M.J. (2022). The effect of inherently threatening contexts on visuocortical engagement to conditioned threat.

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3

Skin Conductance Response Measurement

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Throughout the experiments, skin conductance responses (SCRs) were recorded continuously using Brainproducts V-Amp-16 and Vision Recorder software (Brainproducts, Gilching, Germany) at a sampling rate of 1000 Hz and analyzed off-line using Vision Analyzer 2 software (Brainproducts, Gilching, Germany). SCR was recorded from the thenar and hypothenar eminences of the left hand using two Ag/AgCl electrodes. The amplifier delivered a constant current of 0.5 V. The SCR signal was filtered off-line with a high cutoff filter of 1 Hz and a notch filter of 50 Hz. SCR was defined as the base-to-peak difference (in µS) between response onset (900–4000 ms after stimulus onset) and peak (2000–6000 ms after stimulus onset). A minimum response criterion of 0.02 µS was applied, with lower responses scored as 0. SCR data were normalized following an approach described by Dunsmoor et al. [34 (link)], i.e., by computing generalization gradients for each phase and block as a function of the response to one stimulus type relative to the sum of responses to all stimuli.

Reinhard J., Drepper C., Weber H., Schiele M.A., Kneer K., Mittermeier A., Frey L., Reif A., Pauli P., Domschke K., Deckert J, & Romanos M. (2019). Anxiety risk SNPs on chromosome 2 modulate arousal in children in a fear generalization paradigm. European Child & Adolescent Psychiatry, 29(9), 1301-1310.

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4

Skin Conductance Responses to Generalization

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Throughout the experiment, skin conductance responses (SCR) were recorded continuously using Brainproducts V‐Amp‐16 and Vision Recorder software (Brainproducts, Gilching, Germany) at a sampling rate of 1000Hz and analyzed offline using Vision Analyzer 2 software (Brainproducts, Gilching, Germany). SCR was recorded from the thenar and hypothenar eminences of the left hand using two Ag/AgCl electrodes. The amplifier delivered a constant current of 0.5V. The SCR signal was filtered offline with a high cutoff filter of 1Hz and a notch filter of 50 Hz. SCR was defined as the base‐to‐peak difference (in μS) between response onset (900–4000 ms after stimulus onset) and peak (2000–6000 ms after stimulus onset). A minimum response criterion of 0.02 μS was applied, with lower responses scored as 0. SCR data was normalized following an approach described by Dunsmoor, Prince, Murty, Kragel, & LaBar (2011), that is, by computing generalization gradients for each phase and block as a function of the response to one stimulus type relative to the sum of responses to all stimuli. That is, for each of the pre‐acquisition, acquisition and generalization phases, the sum of SCRs to each stimulus was divided by the sum of responses to all stimuli, resulting in an index for each stimulus type that allows for the direct comparison of generalization patterns between groups.

Schiele M.A., Reinhard J., Reif A., Domschke K., Romanos M., Deckert J, & Pauli P. (2016). Developmental aspects of fear: Comparing the acquisition and generalization of conditioned fear in children and adults. Developmental Psychobiology, 58(4), 471-481.

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5

EMG Signal Processing for Startle Responses

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The EMG data were processed with Vision Analyzer 2.1 software (Brain Products Inc., Munich, Germany). A low cut-off filter of 28 Hz and a high cut-off filter of 500 Hz were applied to the offline data. Afterwards, the signal was rectified, smoothed with a moving average window of 50 ms and baseline corrected from −50 ms to the startle probe onset^{79 (link)}. Startle peaks were detected in a time window between 20 and 200 ms after startle probe onset. Artefacts were manually scored and defined as baseline shifts higher than 5 µV. Non-responders were defined as those participants with a mean startle magnitude below 5 µV and excluded from analyses. In order to control for general differences in startle responses between participants, raw data were transformed into z-scores within subjects and subsequently in T-scores. Missing startle responses were interpolated within subject and condition. Afterwards, T-scores of 2 consecutive trials were averaged and reported as phase. Consequently, each day resulted in 5 phases, which is referred to as A1-A5 (acquisition), E1-E5 (extinction), and T1-T5 (test).

Genheimer H., Andreatta M., Asan E, & Pauli P. (2017). Reinstatement of contextual conditioned anxiety in virtual reality and the effects of transcutaneous vagus nerve stimulation in humans. Scientific Reports, 7, 17886.

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6

Autonomic Responses to Task Feedback

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As an indicator for autonomic nervous system activation, electrodermal activity and heart rate were recorded with AcqKnowledge software (BIOPAC Systems; Goleta, CA) using Ag-AgCl electrodes. Skin conductance electrodes were placed at palm and thenar of the non-dominant hand (all participants were right handed) and data were recorded at 20Hz sampling rate. The electrocardiogram was recorded at lead II at a 1000Hz sampling rate. Skin conductance level and heart rate of the threat and safety blocks were downsampled to 20 Hz and scored as mean signal change during the block (88 s) relative to a 10-sec-baseline period before condition onset (Bublatzky et al., 2013) (link).
In addition, exploratory analyses examined phasic skin conductance response (SCRs) to the different feedback types. For SCRs, noise and slow frequency changes were removed using a 2 Hz FIR low-and a 0.05 Hz high-pass filter using VisionAnalyzer 2.1 (Brain Products). SCRs were scored to the onset of feedback stimuli (i.e. 'You won/lost')
as the maximum increase in skin conductance amplitude in the interval of 1 to 7 s (relative to a 1 s pre-stimulus period). All SCRs < 0.02 mS were scored as zero response and included in the analyses (i.e., SCR magnitude); range and distribution correction was applied (square root [response/maximum response]; see (Bublatzky et al., 2017) (link)).

Paret C, & Bublatzky F. (2020). Threat rapidly disrupts reward reversal learning. Behaviour research and therapy, 131.

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7

Simultaneous fMRI and EEG Acquisition for Sleep Studies

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Acquisition parameters and details for these data have been previously published [19 (link)]. fMRI was acquired using a 3 T scanner (Siemens Trio) with optimized polysomnographic settings (1,505 volumes of T2*-weighted echo planar images, repetition time/echo time = 2,080 ms/30 ms, matrix = 64 × 64, voxel size = 3 × 3 × 2 mm³, distance factor = 50%; field of view = 192 mm²). 30 EEG channels were simultaneously recorded using a modified cap (EASYCAP) with FCz as reference (sampling rate = 5 kHz, low pass filter = 250 Hz, high pass filter = 0.016 Hz). MRI and pulse artifact correction were performed based on the average artifact subtraction method [24 (link)] as implemented in Vision Analyzer2 (Brain Products) followed by ICA-based rejection of residual artifact components (CBC parameters; Vision Analyzer). EEG sleep staging (N0 = wakefulness, N1-N3 = NREM sleep) was done by an expert according to the American Academy of Sleep Medicine (AASM) criteria [25 ], as previously published [19 (link)].

Mitra A., Snyder A.Z., Tagliazucchi E., Laufs H., Elison J., Emerson R.W., Shen M.D., Wolff J.J., Botteron K.N., Dager S., Estes A.M., Evans A., Gerig G., Hazlett H.C., Paterson S.J., Schultz R.T., Styner M.A., Zwaigenbaum L., Schlaggar B.L., Piven J., Pruett JR J.r, & Raichle M. (2017). Resting-state fMRI in sleeping infants more closely resembles adult sleep than adult wakefulness. PLoS ONE, 12(11), e0188122.

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8

Simultaneous EEG-fMRI Acquisition for Sleep Studies

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EEG via a cap (modified BrainCapMR, Easycap, Herrsching, Germany) was recorded continuously during fMRI acquisition (1505 vol of T2*-weighted echo planar images, TR/TE = 2080 ms/30 ms, matrix 64 × 64, voxel size 3 × 3 × 2 mm³, distance factor 50%; FOV 192 mm²) with a 3 T S Trio (Erlangen, Germany). An optimized polysomnographic setting was employed (chin and tibial EMG, ECG, EOG recorded bipolarly [sampling rate 5 kHz, low pass filter 1 kHz] with 30 EEG channels recorded with FCz as the reference [sampling rate 5 kHz, low pass filter 250 Hz]. Pulse oxymetry and respiration were recorded via sensors from the Trio [sampling rate 50 Hz]) and MR scanner compatible devices (BrainAmp MR+, BrainAmpExG; Brain Products, Gilching, Germany), facilitating sleep scoring during fMRI acquisition.
MRI and pulse artifact correction were performed based on the average artifact subtraction (AAS) method (Allen et al., 1998 (link)) as implemented in Vision Analyzer 2 (Brain Products, Germany) followed by objective (CBC parameters, Vision Analyzer) ICA-based rejection of residual artifact-laden components after AAS resulting in EEG with a sampling rate of 250 Hz. EEG artifacts due to motion were detected and eliminated using an ICA procedure implemented in Vision Analyzer 2. Previous publications based on this dataset can be consulted for further details (e.g. Tagliazucchi et al., 2012 (link)).

Ipiña I.P., Kehoe P.D., Kringelbach M., Laufs H., Ibañez A., Deco G., Perl Y.S, & Tagliazucchi E. (2020). Modeling regional changes in dynamic stability during sleep and wakefulness. NeuroImage, 215, 116833.

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9

Simultaneous EEG-fMRI Acquisition for Sleep Studies

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EEG via a cap (modified BrainCapMR, Easycap, Herrsching, Germany) was recorded continuously during fMRI acquisition (1505 vol of T2*-weighted echo planar images, TR/TE = 2080 ms/30 ms, matrix 64 × 64, voxel size 3 × 3 × 2 mm³, distance factor 50%; FOV 192 mm²) with a 3 T S Trio (Erlangen, Germany). An optimized polysomnographic setting was employed (chin and tibial EMG, ECG, EOG recorded bipolarly [sampling rate 5 kHz, low pass filter 1 kHz] with 30 EEG channels recorded with FCz as the reference [sampling rate 5 kHz, low pass filter 250 Hz]. Pulse oxymetry and respiration were recorded via sensors from the Trio [sampling rate 50 Hz]) and MR scanner compatible devices (BrainAmp MR+, BrainAmpExG; Brain Products, Gilching, Germany), facilitating sleep scoring during fMRI acquisition.
MRI and pulse artifact correction were performed based on the average artifact subtraction (AAS) method (Allen et al., 1998 (link)) as implemented in Vision Analyzer 2 (Brain Products, Germany) followed by objective (CBC parameters, Vision Analyzer) ICA-based rejection of residual artifact-laden components after AAS resulting in EEG with a sampling rate of 250 Hz. EEG artifacts due to motion were detected and eliminated using an ICA procedure implemented in Vision Analyzer 2. Previous publications based on this dataset can be consulted for further details (e.g. Tagliazucchi et al., 2012 (link)).

Ipiña I.P., Kehoe P.D., Kringelbach M., Laufs H., Ibañez A., Deco G., Perl Y.S, & Tagliazucchi E. (2020). Modeling regional changes in dynamic stability during sleep and wakefulness. NeuroImage, 215, 116833.

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10

Simultaneous fMRI and EEG Acquisition for Sleep Studies

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Acquisition parameters and details for these data have been previously published (Tagliazucchi et al., 2013 (link)). fMRI was acquired using a 3 T scanner (Siemens Trio) with optimized polysomnographic settings (1,505 volumes of T2*-weighted echo planar images, repetition time/echo time = 2,080 ms/30 ms, matrix = 64 × 64, voxel size = 3 × 3 × 2 mm³, distance factor = 50%; field of view = 192 mm²). 30 EEG channels were simultaneously recorded using a modified cap (EASYCAP) with FCz as reference (sampling rate = 5 kHz, low pass filter = 250 Hz, high pass filter = 0.016 Hz). MRI and pulse artifact correction were performed based on the average artifact subtraction method (Allen et al., 1998 (link)) as implemented in Vision Analyzer2 (Brain Products) followed by ICA-based rejection of residual artifact components (CBC parameters; Vision Analyzer). EEG sleep staging was done by an expert according to the American Academy of Sleep Medicine (AASM) criteria (Soeffing et al., 2008 (link)).

Mitra A., Snyder A.Z., Tagliazucchi E., Laufs H, & Raichle M.E. (2015). Propagated infra-slow intrinsic brain activity reorganizes across wake and slow wave sleep. eLife, 4, e10781.

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Vision analyzer2

Lab products found in correlation

16 protocols using vision analyzer2

Fear Conditioning ECG Processing

Electrodermal Activity Acquisition and Analysis

Skin Conductance Response Measurement

Skin Conductance Responses to Generalization

EMG Signal Processing for Startle Responses

Autonomic Responses to Task Feedback

Simultaneous fMRI and EEG Acquisition for Sleep Studies

Simultaneous EEG-fMRI Acquisition for Sleep Studies

Simultaneous EEG-fMRI Acquisition for Sleep Studies

Simultaneous fMRI and EEG Acquisition for Sleep Studies

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