1 Supplementary Information
2 Theory of weakly coupled oscillators 3 Detailed reviews and mathematical descriptions of the theory, also its extensions and limitations, 4 can be found in a number of publications1–19. In essence, many oscillatory phenomena in the 5 natural world represent dynamic systems with a limit-cycle attractor2. Even though the 6 underlying system might be complex (e.g. a neuron or neural population), the dynamics of the 7 system can be reduced to a phase-variable if the interaction strength among oscillators is weak. 8 In general, coupled oscillators can interact through adjustments of their amplitudes and phases, 9 yet if interaction strength is weak, amplitude changes are small and play a minor role in the 10 oscillatory dynamics (no strong deviation from the limit-cycle) and only the adjustments of the 11 phase are essential for understanding the behaviour. The transformation of a complex system to a 12 phase variable, if valid, reduces the dimensions of the problem, thereby allowing exact 13 mathematical investigation. The manner by which mutually coupled oscillators adjust their 14 phases, either by phase-delay or phase-advancement, is described by the phase response curve 15 (also called phase resetting curve), the PRC7,9,14–16,19–21. The PRC is important, because if the 16 PRC of a system can be described, the synchronization behaviour of the system can be 17 understood and predicted. Many biological oscillators are inherently noisy or chaotic. Therefore, 18 it is important to take this variability of the dynamics into account for a better understanding of 19 biological data. Cortical neurons in vivo exhibit irregular spiking patterns24 and neural networks 20 oscillations also show significant variability over time25. This type of variation is referred to as 21 phase noise and is distinct from measurement noise with the latter being unrelated to the 22 dynamics of the system. 23 According to the theory of weakly coupled oscillators, the synchronization of two coupled 24 oscillators can be predicted from the forces they exert on each other as a function of their 25 instantaneous phase difference. This function is referred to as the phase-response curve (PRC). 26 Accordingly, the phase evolution of two given cortical V1 locations is reduced to: 27
28 1 112121121 ε H
29 2 2 2ε 12H 12 2 1 2 30
31 where φ1,2 is the phase, 1,2 its temporal derivative, ω1,2 is the preferred frequency, ε12 and ε21 are 32 the interaction strengths, H12 and H21 are the single PRCs and ƞ1,2 is a phase-noise term with ƞ1,2 33 ~ N(0, σ2) N being the normal distribution. The two equations, as given in the main text equation 34 1, can be further simplified to: 35
36 3 εG 37
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38 where θ = φ1 –φ2 is the phase difference, ∆ω = ω1 – ω2 the detuning, εG(θ)= ε21H21(θ)-ε12H12(-θ) 39 the combined interaction term with ε being the interaction strength and G(θ) the mutual PRC
2 40 and ƞ= ƞ1 –ƞ2 the phase noise with η ~ N(0, 2σ ). 41 42 Analytical derivation of phase-locking and mean phase difference 43 Equation 3 is a stochastic differential equation (a Langevin equation) and was solved as 44 described in 1. Equation 3 can be rewritten in the form of a Fokker-Planck equation that has been 45 developed to give an analytical solution for the evolution of a probability distribution P of a 46 particle influenced by a drag force (first term on the right side of the equation) and a random 47 Gaussian noise process (second term). The drag force is here the combined systematic force of 48 detuning ∆ω and the interaction function εG(θ): 49 ∆ 50 4 51
52 The stationary (time-independent) solution of the Fokker-Planck equation which is: ′ 1 ′ 53 5 exp 54 ∆ ′ 1 ′ 55 6 exp 56 where C is a normalization constant defined by 1. V(θ) represents the influence 57 of systematic force as a function of phase difference. is the phase difference probability 58 distribution and describes how likely a particular phase difference is to occur. A uniform 59 distribution means that every phase difference is equally likely and the oscillator are hence 60 asynchronous. If the distribution approximates a delta distribution (meaning only one phase 61 difference has non-zero probability), then the oscillators are completely synchronized. All other 62 distributions in between signify intermittent (partial) synchronization (also called cycle slipping 63 or phase walk-through, 1,2). To quantifying the narrowness of the distribution, we use the phase- 64 locking value (the mean resultant vector length,3) defined here as: 65 7 | | 66 Further, we were also interested in the mean phase difference, also described as the preferred 67 phase difference, defined here as: 68 8 arg 2
69 A phase difference between oscillators in neural networks implies spike timing differences. It has 70 been shown that spike-timing is an important characteristic in addition to spike synchrony 4–9. 71 72 General behaviour of the model in term of PLV and mean phase difference 73 In Fig.S1 the model’s behaviour is illustrated as a function of detuning ∆ω and interaction 74 strength ε. To understand how the PLV and the mean phase difference change, it is illustrative to 75 consider the noise-free case first. In the noise-free case one needs to solve the equation 3 for 76 zero-points (root or equilibrium points), meaning that the time derivative of the phase difference 77 is zero, ( 0, i.e. zero frequency difference). Let us assume here for illustration that G(θ) is a 78 sine function, as is for example used for the Kuramoto model 10,11. It then becomes (also called 79 the Adler equation, 1): 80 9 0 ∆ 81 The zero-point or the equilibrium is stable if the derivative of the PRC is negative (stable if 82 < 0). The sin function has two zero crossing (at 0 and π with Δω =0), but only one is stable. 83 In the case ε = 0 (no interaction), only the condition of ∆ω = 0 (no detuning) can lead to 84 synchrony. If ε = 0 and ∆ω ≠ 0 (no interaction with detuning), the oscillators will be 85 asynchronous and there will be linear phase precession with the speed determined by the ∆ω 86 value. If ε > 0 (there is interaction), then an equilibrium can only exist if the detuning is not 87 stronger than the interaction strength, denoted by |∆ω|<= ε. This is because for equilibrium the 88 detuning needs to be counter-balanced by the interaction. In the case of |∆ω|> ε (detuning 89 exceeding interaction strength), the interaction cannot counterbalance the detuning and the 90 oscillators start to phase precess. 91 If the oscillators do phase precess but are coupled (ε>0), the phase-precession is non-linear. The 92 precession rate is determined by the detuning (∆ω), the modulation shape (G(θ)), and the 93 modulation amplitude (ε). In this case, the oscillators are in the intermittent synchronization 94 regime. The transition point ∆ω = ε defines the border between high PLV values and low PLV 95 values and defines the borders of the so-called Arnold tongue, the synchronization region in the 96 ∆ω- ε parameter space 1,2. The larger the ε, the larger the detuning can be for oscillators to still 97 synchronize. This leads to a triangle shape of the synchronization region in the ∆ω- ε space as 98 illustrated in Fig.S1A. The mean (preferred) phase difference can also be derived from equation 99 6. For reaching equilibrium the detuning ∆ω and interaction term (εsin(θ)) need to be 100 counterbalanced. For different detuning ∆ω values the counterbalance will depend on different 101 phase difference values of the interaction term εsin(θ). It can be represented graphically 102 (Fig.S1B,2) as the intersection of a horizontal line (∆ω) with the graph of εsin(θ). Notice that the 103 stronger the interaction strength ε is, the smaller the slope of the detuning-to-phase difference 104 translation becomes. Outside of the Arnold tongue (∆ω> ε), there will be phase precession yet 105 with a preference (minimal precession rate) for a phase difference where the PRC is min or max. 106 Phase noise has important effects on the synchronization behavior1. Strictly speaking, the 107 condition of complete synchrony for noisy oscillators does not exist as θ’ cannot remain stable 108 all the time (there will always be small fluctuations). If ∆ω+ƞ < ε, meaning that in spite of 109 frequency variability detuning can be counterbalanced by interaction strength, then oscillators 110 remain close to the equilibrium point and they have high phase-locking. Yet, when noise is
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111 larger, it is likely that the interaction term cannot counterbalance all the time and the oscillators 112 will phase precess from time to time. However, also in this case, the transition point ∆ω = ε still 113 determines the Arnold tongue border and outlines the transition between the regions of high 114 phase-locking and regions of low phase-locking, but the transition is smoother1,2. In Fig.S1 we 115 show the Arnold tongue in terms of PLV and mean phase-difference for coupled oscillators 116 having moderate levels of white noise (σ=15Hz). 117 118 Biophysical modeling of coupled gamma-generating neural networks 119 To demonstrate that the results from the phase-oscillator equations are generalizable to more 120 biophysically realistic neuronal network oscillations12, we simulated two coupled excitatory- 121 inhibitory spiking neural networks generating pyramidal-interneuron gamma (PING,13) 122 oscillations. 123 The neural voltage dynamics v were of the Izhikevich-type14 and defined as follows: 124 10 0.04 5 140 125 11 ← 30 , then 126 ← 127 The coupled differential equations were numerically solved using the Euler method (1ms step 128 size). The networks were both composed of two types of neurons: 200 regular spiking neurons 129 RS (a=0.02, b=0.2, c=-65mV, d=8) and 50 fast-spiking interneuron FS (a=0.1, b=0.2, c=-65mV, 130 d=2). RS were excitatory neurons and FS inhibitory neurons (ratio 4:1). The neural networks 131 were all-to-all synaptically connected. Synapses were modelled as exponential decaying 132 functions, reset to 1 after the presynaptic neurons fired. Synaptic connection values had a 133 maximum synaptic connection strength (max syn). The synaptic strengths were chosen from a 134 random uniform distribution defined between the 0 and the maximal connection strength. 135 Within a network, RS neurons projected excitatory synaptic AMPA (decay constant= 2ms) 136 connections onto FS neuron (max syn= 0.45) and among themselves (max syn= 0.05). FS 137 neurons projected synaptic GABA-A (decay constant= 8ms) connections onto RS neurons (max 138 syn= -0.35) and among themselves (max syn = -0.2). For cross-connections between the 139 networks, we included RSFS connections (EI, max syn(default)= 0.015) and RSRS 140 connections (EE, max syn(default)= 0.007). We did not include inter-network FSFS or FS 141 RS connections to reflect that V1 horizontal connectivity is dominated by excitatory connections 142 originating from pyramidal cells15–19. 143 The input drive to RS neurons was composed of a fixed input current to each neuron (=10), 144 unique Gaussian input noise for a given neuron (SD±3) and Gaussian input noise shared among 145 neurons (SD±1) of the same network. Thus each network received Gaussian input noise to RS 146 neurons with the effect of inducing instantaneous frequency variation in the network over time 147 (similar to intrinsic phase noise in the phase-oscillator model). For FS neurons, each received a 148 fixed input current (=4) and Gaussian input noise (SD±3). FS neurons received further excitatory 149 drive from the RS neurons. For estimating the instantaneous phase, phase difference and
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150 frequency of the network oscillation we used a population signal defined as mean membrane 151 voltage of all RS neurons of a given network. We simulated in total n=697 conditions (17 152 coupling and 41 detuning conditions) to compare it to analytical predictions. 153 154 Surgical procedures 155 Two adult male rhesus monkeys (Macaca mulatta) were used in this experiment. Two chambers 156 were implanted above early visual cortex, one positioned over V1/V2 and the second over V4. 157 For the experiment reported here we used data from the V1/V2 chamber only. A head post was 158 implanted to head-fix the monkey during the experiment. All the procedures were in accordance 159 with the European council directive 2010/63/EU, the Dutch ‘experiments on animal acts’ (1997) 160 and approved by the Radboud University ethical committee on experiments with animals 161 (Dier‐Experimenten‐Commissie, DEC). 162 163 Recording techniques 164 V1 recordings were made with Plexon U-probes (Plexon Inc.) consisting of 16 contacts (10µm 165 diameter, 0.5-1m impedance, and 150µm inter-contact spacing). Three probes were inserted 166 through a sharp guide tube, which was lowered through granulation tissue to just above the level 167 of the dura surface. The probes were arranged in a linear manner separated from each other by 168 ~2-3mm. The probes were then advanced by separate microdrives (Nan Instruments LTD.). The 169 probes were connected to headstages of high input impedance, and data were acquired via the 170 Plexon ‘Multichannel Acquisition system’ (MAP, Plexon Inc.). The measured extracellular 171 signal was filtered online between 150Hz and 8kHz to extract spiking activity and filtered 172 between 0.7Hz and 300Hz to obtain the ’local field potential’ (LFP). The signal was amplified 173 and digitized with 1kHz for the LFP and 40kHz for the spike signal. The data was converted 174 from Plexon to Matlab file format and cut into trials from fixation onset to stimulus offset using 175 the fieldtrip toolbox 20. For the LFP data, the line noise was removed using the fieldtrip toolbox 176 dft filter, which fits a sine and a cosine at 50, 100 and 150 Hertz and subtracts these components 177 from the data. We collected 7 recording sessions in monkey M1 and 6 sessions in M2. Each 178 recording session had on average ~590 trials in M1 and ~718trials in M2. 179 180 Current source density (CSD) 181 First for extrapolating the CSD to the outermost contacts of our probes, at the top and bottom of 182 the probe, a replica of the LFP of respectively the first and last contact was appended 21. The LFP 183 was then smoothed with a Gaussian (zero-phase) filter of a SD of 1.2 and range of 5 (effectively 184 weighting signals around the centre electrode by 24% in the centre, 20% immediate neighbours, 185 12% 2 contacts away, 5% 3 contacts away). Then the standard CSD algorithm was applied for 186 each contact position x, our inter-contact spacing h of 150µm and a conductivity C of 0.3 S/m: 2 187 12 ∗ 188
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189 We used CSD signals for the main analysis to reduce effects of volume conduction (see also 190 section MUA-CSD and MUA-MUA analysis). 191 192 Receptive field mapping 193 Receptive fields (RFs) were mapped using both spiking and LFP information as described in 22. 194 Briefly, monkeys fixated centrally while high-contrast black and white squares of sizes 0.1- 195 1degree were presented pseudorandomly on a 10x10 grid. The locations where the spiking or the 196 LFP response exceeded the 75th percentile of the response distribution were defined as the RF. 197 Other than in Roberts et al. 22, the LFP response was also used based on the envelope of the 198 broadband gamma power (30-150 Hz) in the CSD, which we found to produce a localized result 199 in line with spiking RFs. CSDs were computed as described above, but with a smaller Gaussian 200 filtering of SD 0.6 and a filter range of 2, meaning that only the two neighbouring electrodes of 201 the centre electrode had some influence on the RF estimate of a given contact. This was done to 202 avoid mislocalization of RF shifts in size or position that are indicative of a shift to a different 203 column or to V223 (see Fig.S2B, rightmost plots for an example of CSD and spiking RFs with 204 such a shift). To obtain estimates of cortical distance (in mm) between the probes we took 205 advantage of the well-known retinotopy of V1. We measured the distance between RF centres 206 and calculated the cortical distance by converting differences in visual degrees using a cortical 207 magnification factor (CMF,24,25). The CMF was estimated individually for each monkey where 208 we used the measured the physical distance between the laminar probes (fixed to the holder) 209 before insertion into cortex (M1: ~2.7mm/deg, M2: ~2.5mm/deg). 210 211 Laminar alignment 212 We inserted the laminar probes on each recording day. The exact laminar positions of the probes 213 (Fig.S2) differed within and between sessions and hence we depth-aligned the probes based on 214 their stimulus-evoked response and inter-laminar coherence characteristics26. For depth- 215 alignment (to assign each contact a particular cortical depth value) we used the following 216 procedure: 217 218 1. We computed the CSD-VEP response. The different sink-source profiles were aligned 219 using a parallel-tempering technique27. This is an iterative procedure that minimizes the 220 squared error between all probes, shifting the position of one probe by one position on 221 each iteration. Central to the parallel tempering algorithm is the parallel start of the 222 procedure at multiple “temperatures”, each of which in our case starts with a different 223 initial, random offset in the probes. Higher temperatures accept higher increases in error 224 with a shift in the position of a probe. If a procedure running at a high temperature 225 achieves a lower error than another temperature (overcoming a local minimum), it swaps 226 the achieved shift vector with a lower temperature to find the new minimum around it. 227 Similar to Godlove et al.28 (using a genetic algorithm), we implemented a lenient 228 maximum shift constraint between electrodes (allowing by shifts of 4 channels upwards 229 and downwards, which for any two probes enforces a minimal overlap of 50%) to prevent 230 trivial solutions. For our data, we used 3000 iterations at 4 different temperatures and 231 different error tolerances per temperature (log spaced between zero and 1). The procedure 6
232 showed asymptotic behaviour (no further decrease in error) at <= 1500 iterations. Note 233 that the optimal number of iterations required for this algorithm will depend on the 234 number of probes/sessions entered. 235 2. We then computed the within laminar probe LFP coherence matrix29. It has been shown 236 that there is sharp decrease in coherence around the L4/L5 border26. We chose this to 237 refine the depth alignments of step 1 using the coherence matrix and again parallel 238 tempering with the initial values defined by the output of step 1. An advantage of the 239 coherence matrix is that it is a robust feature and insensitive to possible gain differences 240 among contacts. 241 3. We manually checked for outliers of which none were found in this dataset. 242 243 Layer assignment 244 Channels were labelled as supragranular, granular and infragranular (Fig.S2B) based on the 245 location of the initial sink-source reversal (as established by the position of the reversal in the 246 aligned grand average) in relation with known anatomy. We consider the position of the sink- 247 source reversal to correspond to the edge of layers 4 and 530,31. Specifically, given our 248 intercontact spacing of 150 micrometres and about 500 micrometres width generally used per 249 layer 26,32, channels from this border to 450 micrometre below it were labelled infragranular, 250 channels up to 450 micrometre above as granular, and channels 600 above it and higher as 251 supragranular. Data were averaged within supra- and granular layers or infragranular layers in 252 agreement with the two separable sites of gamma-power synchronization as indicated in the text. 253 254 Definition of the V1-White Matter-V2 borders 255 The depth probes often collected signals beyond the lower V1 layer 6 border and often reached 256 the deep V2 infragranular layers. When the probes reached deep V2 the RFs shifted abruptly 257 several degrees as expected form V1-V2 retinotopy (Fig.S2B, rightmost plots)23. The white 258 matter situated between the two areas appeared relatively thin, often comprising 1-2 contacts 259 (150-300microns). 260 To estimate the lower V1 Layer 6 boundary, we first used spiking RFs to determine the 261 transition. We computed a RF centre distance measure, referenced to L4-L5 border, to determine 262 at which contact the transition to deep V2 occurred. Before the transition, often 1 or 2 contacts 263 did not show spike RFs at all and were thus likely to represent white matter. V1 Layer 6 border 264 was then defined as the contact with the last low RF centre distance (threshold < 0.5 deg). In 265 probes with low spiking quality; we used CSD signals (filtered in the gamma range (30-150Hz) 266 for determining the V1 L6 border. 267 268 Single-session RF and CSD evaluation 269 For each session and probe, the CSD from full-screen checkerboard flashes (37), the task and RF 270 data were plotted side-by-side. CSDs from flashes and the grating onset were very similar in the 271 initial response (data not shown). The task-data from a single, high-contrast condition was split 272 in an early and a later half to detect any changes in depth over the session and also compared 273 with flash CSDs before and after the task (where available). Recordings were stable in depth
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274 according to this measure. The RF mapping was used to detect changes in the size or location of 275 RFs over depth and to ascertain that there were no gradual drifts in RF location, indicative of a 276 probe not inserted fully orthogonal to cortex. In cases were noticeable shifts were observed, the 277 affected deeper channels were removed from the analysis. The final cut-off between deep V1 and 278 white matter/V2 was determined based on the distance from the layer 4/5 reversal (see Layer 279 assignment). This border, 450 microns below the 4/5 reversal, was typically above the level 280 where RF shifts were observed, leading to removal of further deep channels from the analysis. 281 282 Visual stimulation paradigm 283 The monkeys were trained to accept head-fixation and were placed in a Faraday-isolated 284 darkened booth at a distance of 57cm from a computer screen. Stimuli were presented on a 285 Samsung TFT screen (SyncMaster 940bf, 38ºx30º 60Hz). The screen was calibrated to linearize 286 luminance as function of RGB values. During stimulation and pre-stimulus time the monkey 287 maintained eye position (measured by infra-red camera, Arrington 60Hz sampling rate) within a 288 square window of 2x2°. This window was relatively large to allow for noise associated with the 289 camera, recording with a second high-speed high-resolution camera showed that eye position 290 was generally held more stable than the window required. The monkey was rewarded if keeping 291 gaze within the eye window during the whole trial. 292 We aimed to manipulate gamma frequency differences between three recorded locations in V1 293 each separated by ~2-3mm, corresponding to receptive fields (RF) separated by ~1 degree in 294 visual space. The probes were arranged linearly either perpendicularly or parallel to the lunate 295 sulcus, thus receptive fields were arranged respectively either horizontally or vertically. To 296 manipulate gamma frequency differences we manipulated local stimulus contrast differences in a 297 large square-wave grating (2 cycles/degree, presented at two opposite phases randomly 298 interleaved). Contrast was varied smoothly between the three locations. The direction of the 299 contrast difference was parallel to the arrangement of RFs and orthogonal to the orientation of 300 the grating. To avoid that the contrast manipulation would attract exogenous and endogenous 301 attention (possibly appearing as an object or object boundary), we manipulated contrast 302 differences in a repeating symmetric pattern over the entire screen. Additionally, the stimulus 303 was isoluminant at all points and was isoluminant with the pre-stimulus grey screen. The contrast 304 at the location of the centre RF, was constant over all conditions. We presented 8 levels of 305 contrast difference and one stimulus where contrast was the same at all points. The exact 306 contrasts differed slightly between the two monkeys since we used different screens (of the same 307 type) which had somewhat different luminance levels. Contrast levels are given in table S1. 308 We aimed to align the stimulus so that receptive fields at the three cortical locations would align 309 with the highest, lowest and midpoint of one cycle of the contrast variation. However, RFs did 310 not always fall exactly as we wished and there was often some variability in RFs within each 311 probe. To get the best alignment that we could on a given session, we placed the stimulus such 312 that receptive fields from the upper portion of the central probe fell on the midpoint between the 313 peak and trough of the contrast variation. We then selected a stimulus where the distance 314 between the peak and trough best matched the distance between RFs from the flanking probes. In 315 most cases this lead to a peak-to-trough distance of 2 degrees. In some cases we used a distance 316 of 1 or of 3 degrees. In some sessions we recorded with only two probes in V1. In those cases the 317 stimulus was aligned so that the midpoint was midway between the RFs of the two probes. 8
318 Most analysis was based on the measured gamma frequency rather than the stimulus contrast and 319 so any mismatch between the stimulus contrast a particular RF received and the contrast we 320 planned to present did not affect our conclusions. Where statistical analysis (see sections below 321 ‘Effects of visual contrast and eccentricity on gamma frequency’) was based on stimulus contrast 322 we took the stimulus contrast which was present at the centre of the measured RF of each single 323 electrode contact. For Fig.1 and Fig.S4 the data is shown binned by stimulus contrast values for 324 illustration. 325 326 Analysis of L2-L4 and L5-L6 gamma-band synchronization 327 For the main analysis of synchronization, we limited the analysis to data recorded from L2-L4 328 representing most the gamma power in V122,26,32–34. The lowest gamma power was observed 329 around the L4-L5 border. We observed a second gamma peak around L5-L632,34 and gamma 330 power going into deep V2. To distinguish L6 from deep V2 we used marked receptive fields 331 shifts (as described above) as indicator for the transition from V1 to V2. 332 We did the exact same analysis for quantifying synchronization between pairs of L5-6 gamma as 333 used for L2-4 gamma (Fig.S3). We could confirm the observation of an Arnold tongue in terms 334 of PLV and mean phase difference also for the deep gamma showing that the observed 335 synchronization properties can be generalized over different laminar compartments. We propose 336 that calculating the PRC and Arnold tongue between various cortical locations would be a 337 fruitful way to understand the connectivity between brain networks. 338 339 Effects of visual contrast and eccentricity on gamma frequency 340 Local stimulus contrast had a significant effect on the V1 gamma frequency (linear regression, 341 M1: R2=0.31,n=1179 M2: R2=0.25,n=1134, both p<10-10,see Fig.S4) in both monkey M1and M2 342 confirming previous studies of monkey and human visual cortex22,35–39. Stimulus contrast lead to 343 a monotonic increase of the frequency, here measured as the mean of the instantaneous gamma 344 frequency (the same results were obtained using the conventional frequency of the power 345 spectral peak). Both LFP and CSD gamma gave the same result. The MUA spike rate also 346 significantly increased with stimulus contrast (linear regression, M1: R2=0.14, ,n=1179,M2: 347 R2=0.12, n=1134, both p<10-10) as well established by previous work40,41 suggesting that a likely 348 source of frequency change is due to a change of network excitation13,42. We inserted laminar 349 probes acutely into the visual cortex and the probes had, depending on their arrangement, 350 differences in their visual eccentricities. There was also variation across sessions. It has been 351 shown in previous work that the V1 gamma frequency is modulated by eccentricity43,44. We 352 confirmed these observations. The gamma frequency significantly decreased with visual 353 eccentricity (linear regression, M1: R2=0.12, n=1179, M2: R2= 0.15, n=1134, both p<10-10). We 354 also observed that the MUA spike rate also decreased with visual eccentricity (linear regression, 355 M1:R2= 0.04, n=1179, M2: R2= 0.08, n=1134, both p<10-10) similarly to gamma frequency. 356 Frequency differences (detuning) between all V1 pairs were therehere a function of both 357 stimulus contrast, being the strongest factor, and visual eccentricity (multiple linear regression, 358 M1: ∆contrast, R2=0.28, ∆eccentricity, R2=0.09, n=9632; M2:∆contrast, R2=0.25, ∆eccentricity, 359 R2=0.11, n=7938, all p<10-10). We observed that the frequency difference was closely related to 360 MUA spike rate difference among probes (linear regression, M1: R2=0.53, n=9632, M2: 9
361 R2=0.36, n=7938, both p<10-10) indicating that gamma frequency differences (and hence 362 detuning) between locations are related to excitability differences. The lower excitability in more 363 eccentric locations could reflect network differences or that stimulus, with a spatial frequency of 364 2 cycles/degree, was better suited to more foveal sites. 365 366 Estimation of instantaneous gamma phase, frequency and amplitude 367 For quantifying the phase-locking value and the preferred phase difference we relied on the 368 reconstruction of the instantaneous phase45. Methods based on the instantaneous phase deal 369 better with non-stationary dynamics, which were present in the gamma-band signals investigated 370 here. The main challenge is to decompose the often complex, multi-component measured 371 LFP/CSD signal, into a well-defined gamma oscillatory component from which the 372 instantaneous phase can be extracted (i.e., after a Hilbert-Transform or directly from a time- 373 frequency representation (TFR),46). We used a method based on the singular spectrum 374 decomposition of the signal (SSD, see https://project.dke.maastrichtuniversity.nl/ssd/ )47. SSD is 375 a recently proposed method for the decomposition of nonlinear and non-stationary time series 376 47,48 in a completely data-driven manner. The method originates from singular spectrum analysis 377 (SSA), which is a nonparametric spectral estimation method used for analysis and prediction of 378 time series. For a given signals x(t) we applied SSD for each trial separately to extract the 379 gamma oscillatory components (SSDγ). Here a short overview is presented. For more 380 information see47. The following steps were implemented to retrieve the gamma oscillatory 48 381 component SSDγ , where each iteration reproduces one component. The iteration stopped when 382 10 components were extracted or only 1% residual variance remained. 383 1. The signal x(t) is embedded giving a trajectory matrix X: 384