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Logo of nihpaAbout Author manuscriptsSubmit a manuscriptHHS Public Access; Author Manuscript; Accepted for publication in peer reviewed journal;
 
Neuron. Author manuscript; available in PMC 2010 August 14.
Published in final edited form as:
PMCID: PMC2921507
NIHMSID: NIHMS226062

Timing, timing, timing: Fast decoding of object information from intracranial field potentials in human visual cortex

Summary

The difficulty of visual recognition stems from the need to achieve high selectivity while maintaining robustness to object transformations within hundreds of milliseconds. Theories of visual recognition differ in whether the neuronal circuits invoke recurrent feedback connections or not. The timing of neurophysiological responses in visual cortex plays a key role in distinguishing between bottom-up and top-down theories. Here we quantified at millisecond resolution the amount of visual information conveyed by intracranial field potentials from 912 electrodes in 11 human subjects. We could decode object category information from human visual cortex in single trials as early as 100 ms post-stimulus. Decoding performance was robust to depth rotation and scale changes. The results suggest that physiological activity in the temporal lobe can account for key properties of visual recognition. The fast decoding in single trials is compatible with feed-forward theories and provides strong constraints for computational models of human vision.

Introduction

Humans and other primates can recognize objects very rapidly even when these objects are presented in complex scenes and have undergone transformations in position, size, color, illumination and rotation (Potter and Levy, 1969). The robustness of visual perception to image changes is thought to arise gradually within the hierarchical architecture of the ventral visual cortex, in which object representations become increasingly discriminative and invariant (Logothetis and Sheinberg, 1996; Rolls, 1991; Tanaka, 1996). The highest stages of the temporal lobe show key selectivity and invariance properties that could underlie perceptual recognition as shown by convergent evidence from monkey electrophysiology (Desimone et al., 1984; Hung et al., 2005; Logothetis and Sheinberg, 1996; Perrett et al., 1992; Tanaka, 1996; Tsao et al., 2006), monkey functional imaging (Tsao et al., 2006), lesion studies in monkeys (Dean, 1976; Holmes and Gross, 1984), human functional imaging (Grill-Spector and Malach, 2004; Haxby et al., 2001; Kanwisher et al., 1997), human electrophysiology (Kraskov et al., 2007; Kreiman et al., 2000; McCarthy et al., 1999; Quian Quiroga et al., 2005) and neurological studies in humans (Damasio et al., 1990; De Renzi, 2000; Tippett et al., 1996).

Theories of visual recognition can be largely divided into two main groups: (i) theories advocating top-down influences and long recurrent feedback connections (e.g. (Bullier, 2001; Garrido et al., 2007; Hochstein and Ahissar, 2002)) and (ii) theories relying on a bottom-up approach and largely dependent on feed-forward processing steps (e.g. (Fukushima, 1980; Riesenhuber and Poggio, 1999; Rolls, 1991; vanRullen and Thorpe, 2002)). While ultimately both bottom-up and top-down influences are likely to play significant roles in visual object recognition, the relative contribution of bottom-up versus top-down processes in different aspects of visual object recognition remains unclear. The location and timing of responses elicited in visual cortex constitute important constraints to quantify the role of feed-forward and feedback signals.

In macaque monkeys, selective responses can be elicited in inferior temporal cortex ~100 ms after stimulus onset (e.g. (Hung et al., 2005; Keysers et al., 2001; Perrett et al., 1992; Richmond et al., 1983)). Less is known about the latency and location of responses in human visual cortex. Scalp EEG recordings suggest that complex visual categorization tasks (distinguishing the presence of an animal in a natural scene) can trigger differential signals ~150 ms after stimulus onset (Thorpe et al., 1996) but the localization of these signals in the brain is not clear (see also (Johnson and Olshausen, 2005)). Face-selective responses at ~200 ms after stimulus onset have been reported in field potentials recorded from the human temporal lobe averaged over tens to hundreds of trials (McCarthy et al., 1999). Single neuron recordings in the human medial temporal lobe (areas that are not exclusively visual including the hippocampus, entorhinal cortex, amygdala and parahippocampal gyrus) yield latencies ranging from 200 to 500 ms (Kreiman et al., 2000; Mormann et al., 2008).

While there is no hard threshold to separate bottom-up from top-down signals, several pieces of evidence suggest that after ~200 ms there is likely to be prominent impact from back-projections (Garrido et al., 2007; Schmolesky et al., 1998; Tomita et al., 1999). In order to unravel the neuronal circuits and mechanisms that give rise to selective, robust and fast visual pattern recognition, it is important to combine location information with a characterization of the dynamics of the physiological events involved in object processing in single trials. In this study, we used neurophysiological recordings to directly quantify the degree of selectivity, invariance and speed of visual processing in the human visual cortex. We recorded intracranial field potentials (IFPs) from 912 subdural electrodes implanted in 11 subjects for evaluation of surgical approaches to alleviate resilient forms of epilepsy (Engel et al., 2005; Kreiman, 2007; Ojemann, 1997). We observed that physiological responses in the occipital and temporal lobes, most prominently in the inferior occipital gyrus, inferior temporal cortex, fusiform gyrus and parahippocampal gyrus, showed strong selectivity to complex objects while maintaining robustness to object transformations. The robust and selective responses were clear even in single trials and within ~100 ms after stimulus onset.

Results

Object selectivity in human visual cortex

Eleven subjects (6 male, 9 right-handed, 12 to 34 years old) were presented with digital photographs of objects belonging to 5 categories (“animals”, “chairs”, “human faces”, “fruits” and “vehicles”) while recording electrophysiological activity from 48 to 126 intracranial electrodes implanted to localize epileptic seizure foci (Experimental Procedures). There were 5 different exemplars per category (Figure S1B ). Images were grayscale, contrast-normalized and were presented for 200 ms in pseudo-random order, with an interval between images of 600 ms (Figure S1A ), while subjects performed a one-back task. The physiological responses from two example recording sites are shown in Figure 1. An electrode located in the left temporal pole (Talairach coordinates: −27.0, −11.8, −35.3, area number 43 in Table S2) showed differential activity across object categories, with an enhanced response to images from the “fruits” category (Figure 1A , black trace). To quantify the degree of selectivity, we defined the intracranial field potential (IFP) response as the range of the IFP signal, that is, max(IFP)-min(IFP), in a time window from 50 to 300 ms after stimulus onset. The time window from 50 to 300 ms was chosen so as to account for the approximate latency of the neural response (Richmond et al., 1983; Schmolesky et al., 1998) while remaining within the average saccade time (Rayner, 1998). We note that in many cases, the selectivity extended well past the 300 ms boundary (e.g., see Figure S1 and F for two particularly clear examples). Throughout the manuscript, we focus on the early part of the physiological responses (see Discussion). We also quantitatively compared different time windows and other possible definitions of the IFP response (see Figure S3 and Supplementary Material). In the example in Figure 1A , a one-way ANOVA across categories on the IFP responses yielded p<10−6 (Experimental Procedures). The selective response was consistent across repetitions (z-score=3.2, Supplementary Material) and also across the different exemplars for each category (Figure 1B ). When we ranked the objects according to the IFP response, the 5 best objects were the 5 exemplars from the “fruits” category (Figure 1C , bootstrap p<10−5, Experimental Procedures). Therefore, the category selectivity in this electrode cannot be ascribed to responses to only one or a few particular exemplar objects. Another example electrode is shown in Figure 1F–J . This electrode, located in the left inferior occipital gyrus (Talairach coordinates: −48.8, −69.1, −11.8, area number 14 in Table S2) in a different subject, showed stronger responses to images from the “human faces” category (Figure 1F , blue trace). More examples are shown in Figure S1 D–G for more examples.

Figure 1
Selectivity in intracranial field potential (IFP) recordings from the human cortex

While many studies have focused on analyzing the average responses across multiple repetitions, the brain needs to discriminate object information in real time. This imposes a strict criterion for selectivity. We used a statistical learning approach (Bishop, 1995; Hung et al., 2005) to quantify whether the information from IFPs available in single trials was sufficient to distinguish one category from the other categories (Experimental Procedures). Figure 1D shows the distribution of the IFP responses for the trials where a fruit was presented (black trace) versus all the other trials (gray trace) and Figure 1E shows the corresponding ROC curve (Green and Swets, 1966; Kreiman et al., 2000). We used a Support Vector Machine (SVM) classifier with a linear kernel to compute the proportion of single trials in which we could detect the preferred category (in this example, fruits). Other ways of defining selectivity, including a one-way ANOVA on the IFP responses (Kreiman et al., 2000), a point-by-point ANOVA (Thorpe et al., 1996) and the use of other statistical classifiers (Bishop, 1995), yielded similar results (Supplementary Material). We separated the repetitions used to train the classifier and those used to test its performance to avoid overfitting. The output of the classifier is a performance value (labeled “Classification Performance” throughout the text) that achieves 100% if all test trials are correctly classified and 50% for chance levels. In the examples in Figure 1A and Figure 1F , we could decode the preferred object categories (“fruits” and “human faces” respectively) from the IFP responses in single trials with performance levels of 69±6% and 65±5% respectively.

We recorded data from 912 electrodes in 11 subjects (see Table S1 for the recording site location distribution). To determine whether a given classification performance value was significantly different from chance levels, we used a bootstrap procedure whereby we randomly shuffled the object category labels (Supplementary Material). Based on this bootstrap procedure, we used a threshold of 3 standard deviations from the mean based on the null hypothesis (Figure S2A ). We observed selective responses in at least one electrode in all the subjects. Most of the selective electrodes (67%) responded preferentially to one rather than multiple object categories (Figure S2B ). Across all the electrodes, we observed selective responses to the 5 different object categories that were tested (Figure S2C ) expanding on previous IFP reports describing mostly selectivity to faces (McCarthy et al., 1999). The distribution of selective responses across categories was not uniform: there were more electrodes responding to the “human faces” category than to any of the other four categories (Figure S2C ). We note that the observation of an electrode that shows selectivity for a particular object category does not necessarily imply the existence of a “brain area” devoted exclusively to that category (see Discussion). The classification performance values ranged from 58% to 82% (Figure S2D , 61%±4%, mean±s.d.). Other statistical classifiers and other definitions of IFP response yielded similar conclusions (Figure S3 and Supplementary Material).

As illustrated in the two examples in Figure 1, the category selectivity could not be explained by preferences for individual exemplars. Very few electrodes showed statistically significant performance levels when the classifier was trained to discriminate among individual exemplars instead of across categories (Supplementary Material). Additionally, the classification performance also dropped significantly when each category was arbitrarily defined by randomly drawing 5 exemplars out of the total of 25 exemplars (Supplementary Material). We asked whether the physiological differences across object categories could be explained by low-level image properties shared by the exemplars of a given category. To address this question, we considered fifteen different image properties including contrast, number of bright or dark boxes, etc. and computed the correlation coefficient between the IFP responses and the image properties for each electrode. Although in a few electrodes we observed significant correlations, on average, the low-level image properties that yielded the strongest correlations could not account for more than 10% of the variance in the IFP responses (Supplementary Material).

Of the 912 electrodes, 111 (12%) showed selectivity. These electrodes were non-uniformly distributed across the different lobes (occipital: 35%, temporal: 14%, frontal: 7%, parietal 4%). To determine the location of the electrodes, we co-registered the pre-operative MR images with the post-operative CT images and mapped each electrode onto one of 80 possible brain locations (Table S2). The areas with the highest proportions of selective electrodes were the inferior occipital gyrus (86%, area 14 in Table S2), fusiform gyrus (38%, area 17 in Table S2), parahippocampal portion of the medial temporal lobe (26%, area 19 in Table S2), mid-occipital gyrus (22%, area 15 in Table S2), lingual gyrus in the medial temporal lobe (21%, area 18 in Table S2), inferior temporal cortex (18%, area 31 in Table S2) and the temporal pole (14%, area 43 in Table S2). The number of selective electrodes in all the areas that we studied is shown in Table S1 .

The analyses reported thus far describe the selectivity of individual electrodes but the brain has access to information from many different locations. In order to quantify how well we could decode information by considering the ensemble activity across electrodes or across brain regions, we constructed a vector containing the responses of multiple electrodes and used the same statistical classifier approach described above (see (Hung et al., 2005) and Experimental Procedures). Data from multiple electrodes were concatenated assuming that the activity was independent (Supplementary Material). Figure S4A shows one way to build such an ensemble vector by selecting electrodes based on the rv value, that is the ratio of the variance across object categories to the variance within object categories. The electrode selection was performed using only the training data. Using such an ensemble of 11 electrodes, the overall classification performance ranged from 74% to 95%. These values correspond to binary classification for each object category where chance performance is 50%; the values for multiclass classification where chance performance is 20% are shown in Figure S4B . These values provide only a lower bound to the information available in the neural ensemble because the addition of more electrodes, the use of more complex non-linear classifiers and the incorporation of interactions across areas could enhance the classification performance even more. In order to further evaluate the spatial specificity of the selective responses, we built neural ensembles by drawing electrodes based on their location (Table S1). The regions that yielded the highest classification performance levels are shown in Figure 2 and included the inferior occipital gyrus (area 14 in Table S2), fusiform gyrus (area 17 in Table S2), lingual gyrus (area 18 in Table S2), parahippocampal gyrus (area 19 in Table S2), inferior temporal cortex (area 31 in Table S2) and the temporal pole (area 43 in Table S2). The classification performance values for all areas are shown in Figure S5. The ensemble results in Figure 2 (and Figure S5) are consistent with the location results presented for individual electrodes above.

Figure 2
Locations showing strongest selectivity

Timing of selective responses

The intracranial field potentials show a temporal resolution of milliseconds. We therefore used the detailed time course of the IFP to estimate the latency of the selective responses. We followed the procedure in (Thorpe et al., 1996): (i) we defined an electrode to be “selective” if there were 25 consecutive bins (bin size = 2 ms at BWH and 3.9 ms at CHB) where a one-way ANOVA on the IFP responses across object categories yielded p < 0.01; (ii) for the selective electrodes, we defined the latency as the earliest time point where 10 consecutive bins yielded p < 0.01 in the same analysis (Figure S6A ). The latencies depend on the threshold parameters; this parameter dependence is described in Figure S6B–C . The parameters 25, 10 and 0.01 represent conservative cut-off values that yield a low probability of false alarm. This selectivity criterion yielded 94 selective electrodes (cf. 111 selective electrodes reported above); the number of electrodes that passed the selectivity criterion in 1000 shuffles of the category labels was 0. The distribution of latencies is shown in Figure 3A ; the mean latency across all the electrodes was 115±44 ms. The latencies for those electrodes in the inferior occipital gyrus (area 14 in Table S2) were shorter than the ones for electrodes in temporal lobe locations (Figure S6D ). In order to evaluate the earliest time point at which we could reliably decode category information in single trials, we binned the IFP responses using windows of 25 ms and computed the IFP range in each bin. We used an SVM classifier to decode category information in each time bin (Figure 3B ). This is a demanding task for the classifier because we only used a very small amount of data (25 ms) to train the classifier and to test its performance (see Figure S7A–C for the results for each object category and using bin sizes of 25, 50 ms and 100 ms). In spite of the task difficulty, we could still discriminate category information as early as ~100 ms after stimulus onset. The latencies and decoding results are compatible with single neuron studies in macaque monkey inferior temporal cortex (Hung et al., 2005; Keysers et al., 2001), with psychophysical observations in humans (Potter and Levy, 1969) and also with scalp EEG recordings in humans (Thorpe et al., 1996).

Figure 3
Fast decoding of object category

Invariance to scale and viewpoint

A key aspect of visual recognition involves not only being able to discriminate among different objects but also achieving invariance to object transformations (Desimone et al., 1984; Hung et al., 2005; Logothetis et al., 1995; Riesenhuber and Poggio, 1999; Rolls, 1991). We considered two important and typical object transformations: scaling and depth rotation. Each exemplar object was presented in a “default” rotation and size (3 degrees of visual angle) and also two additional rotations (~45 and ~90 degrees) and two additional scales (1.5 and 6 degrees of visual angle; Figure S1C ). Except in the case of human faces, the definition of a “default” viewpoint for the other object categories is arbitrary (these “default” viewpoints are shown in Figure S1B ). We asked whether the selective responses, such as the ones illustrated in Figure 1, would be maintained in spite of these object transformations. An example of a recording site that showed strong robustness to scale and depth rotation transformations is shown in Figure 4A . This electrode, located in the parahippocampal part of the right medio-temporal-gyrus (Talairach coordinates: 32.6, −34.8, −13.6), showed an enhanced response to “human faces” at all the scales and depth rotations that we tested. The selective responses were consistent across repetitions, exemplars and object transformations (Figure S8). The distribution of IFP responses for the preferred and non-preferred categories and the ROC analyses (Figure 4B ) suggested that it would be possible to discriminate the preferred object across object transformations in single trials. To evaluate the degree of extrapolation across changes in scale and depth rotation, we trained the classifier using only the IFP responses to the “default” scale and rotation and tested its performance using the IFP responses to the transformed objects (Experimental Procedures). Other train set / test set combinations yielded similar results (Supplementary Material). The decoder showed invariance, with an average classification performance across the four conditions in Figure 4 of 73±8%. Overall, invariance to scale and depth rotation was observed in at least one electrode 10 of the 11 subjects. Forty-nine electrodes (44% of the selective electrodes) showed invariance to scale; the classification performance ranged from 60% to 82% (Figure S2F , 64%±4%, mean±s.d.). Sixty-four electrodes (58% of the selective electrodes) showed invariance to depth rotation; the classification performance ranged from 60% to 81% (Figure S2E ; 65%±4%, mean±s.d.). Most of the electrodes that showed invariance to scale changes also showed invariance to depth rotation changes and vice versa. There was a strong correlation between the classification performance values for these two transformations (Figure 5A ; Pearson correlation coefficient=0.70). The majority of the electrodes that showed invariance to scale or depth rotation were located in the occipital lobe (inferior occipital gyrus, area 14 in Table S2) and in the temporal lobe (parahippocampal gyrus (area code 19), inferior temporal cortex (area code 31), fusiform gyrus (area code 17), medial temporal lobe (area code 18) and temporal pole (area code 43)). The number of electrodes in each location that showed invariance to scale and depth rotation are shown in Table S1. The classification performance values for a neural ensemble of 11 electrodes ranged from 58% to above 90% (Figure S4 C–D ). The neural ensembles formed by electrodes in the inferior occipital gyrus or electrodes in the temporal lobe showed the strongest degree of robustness to scale and depth rotation changes (Figure 5B ; see Figure S5 for the classification performance values for ensembles from all brain regions).

Figure 4
Robustness to scale and depth rotation
Figure 5
Locations showing strongest robustness to object changes

We estimated the latency of the IFP responses as described in the previous section (Figure S6A ). Latencies were computed separately for each one of the 5 combinations of scale and depth rotation. There was no significant difference among the latencies for the different object transformations (Figure 6A ). Robust and selective responses were apparent within ~100 ms of processing, suggesting that the neural responses in the temporal lobe may not require additional time to analyze different scales or depth rotations. It should be noted that this statement refers to categorizing the images based on the physiological responses and may not extrapolate to identifying individual exemplars. Consistent with the short latencies, we could also decode the object category as early as ~100 ms after stimulus onset even when extrapolating across scaled and rotated versions of the objects (Figure 6B ; see also Figure S7 D–F ).

Figure 6
Fast and robust decoding of object category

Discussion

Visual object recognition is challenging because the same object can cast an infinite number of patterns onto the retina. The difficulty of the problem is illustrated by the observation that, in spite of major advances in computational power, human recognition performance currently outperforms computer vision algorithms (e.g. (Serre et al., 2007a; Serre et al., 2007b)). The speed of visual recognition imposes a strong constraint on theories of visual recognition by limiting the plausible number of computational steps (Deco and Rolls, 2004; Keysers et al., 2001; Riesenhuber and Poggio, 1999; Serre et al., 2007a; Thorpe et al., 1996; vanRullen and Thorpe, 2002). Our results show that neural activity in the human occipital and temporal cortex (Figures 2 and and5)5) supports a representation that is consistent with the basic properties of recognition at the behavioral level in terms of selectivity (Figures 1 and and2),2), robustness to object transformations (Figures 4 and and5)5) and speed (Figures 3 and and66).

It may be tempting to describe the selectivity in one of our electrodes as indicative of a brain “area” or “module” devoted to recognizing objects of the preferred category as claimed in functional imaging studies (Grill-Spector and Malach, 2004; Haxby et al., 2001; Kanwisher et al., 1997). However, we should be careful about such an interpretation of our recordings. First, we examined the responses to a limited number of object categories. Even though most electrodes responded best to one category as opposed to multiple categories (Figure S2B ), we cannot rule out the possibility that some of these electrodes may also respond to other object categories that were not presented to the subjects. Second, it is difficult to precisely quantify the spatial extent of the selective responses with our recordings. Third, we observed different electrodes with distinct selectivity in a given brain region (Figure S5).

The location of the electrodes in our study was dictated by clinical criteria. Therefore, the electrode coverage was far from exhaustive. There may well be other areas in the human brain, not interrogated in the current efforts, which also show selectivity and invariance. Yet, we note that the location of the selective responses that we observed is generally compatible with human and macaque monkey functional imaging studies as well as with single unit and field potential studies. For example, both electrophysiological studies (McCarthy et al., 1999; Privman et al., 2007) and functional imaging studies in humans (Grill-Spector and Malach, 2004; Haxby et al., 2001; Kanwisher et al., 1997; Tsao et al., 2006) have described the selective activation of areas in the fusiform gyrus (commonly called Fusiform Face Area) in response to face stimuli. The selectivity in the medial temporal lobe areas is also compatible with single unit and local field potential studies in humans (Kraskov et al., 2007; Kreiman, 2007). Although comparisons across species are not entirely trivial, the face selectivity in the fusiform gyrus areas is consistent with recent single unit and imaging measurements in macaque monkeys (Tsao et al., 2006), and the selective responses in human inferior temporal cortex that we report here may correspond to the areas that show selectivity and invariance in the macaque monkey inferior temporal cortex (Desimone et al., 1984; Hung et al., 2005; Logothetis and Sheinberg, 1996; Perrett et al., 1992; Richmond et al., 1983; Tanaka, 1996). The involvement of the fusiform gyrus and inferior temporal cortex in visual recognition is further supported by lesion studies in subjects that show severe recognition deficits after temporal lobe damage (Damasio et al., 1990; De Renzi, 2000; Grill-Spector and Malach, 2004; Holmes and Gross, 1984; Logothetis and Sheinberg, 1996; Tippett et al., 1996).

Although visual selectivity is interesting in itself, the key challenge in recognition is to combine selectivity with invariance to transformations. It is easy (and useless) to implement algorithms that can achieve exquisite selectivity without being able to extrapolate across different transformations of the same object. Our recordings provide evidence of category invariance (i.e. similar selective responses to multiple exemplars within a category) (Freedman et al., 2001; Hung et al., 2005; Kanwisher et al., 1997; Kreiman et al., 2000; Sigala and Logothetis, 2002), scale invariance (i.e. similar selectivity across different scales) (Ito et al., 1995; Logothetis and Sheinberg, 1996; Tanaka, 1996) and viewpoint invariance (i.e. similar selectivity across depth rotations) (Ito et al., 1995; Logothetis et al., 1995; Logothetis and Sheinberg, 1996; Tanaka, 1996). Our observations suggest that selective and invariant responses arise with approximately the same latency. These observations suggest that there may not be a need for extensive additional computation to recognize a transformed object. This observation is compatible with both single unit studies in macaque monkeys (Desimone et al., 1984; Hung et al., 2005; Logothetis et al., 1995) and with computational models of object recognition (Poggio and Edelman, 1990; Serre et al., 2007a; Wallis and Rolls, 1997). We note that other investigators have suggested that fine information (e.g. object identity) requires longer latencies (Sugase et al., 1999).

The selectivity observed in functional imaging studies and the behavioral deficits in lesion studies inform us about the “where” but not about the “when” of neural activity. Scalp recordings and psychophysical observations have provided temporal bounds for visual recognition (Potter and Levy, 1969; Thorpe et al., 1996) (“when” information) but it is hard to infer the locations of processing steps along visual cortex from those studies. The results that we describe here link the “where” and “when” and argue that the stream of visual information reaches the highest stages of processing in the inferior temporal cortex within less than 200 ms after stimulus onset. These latencies are significantly shorter than the ones reported in the human medial temporal lobe, which range from 200 to 500 ms (Kreiman et al., 2000; Mormann et al., 2008). Why there is such a relatively long gap between the responses in visual cortex (as reported here in the human visual cortex and in many studies in the macaque monkey inferior temporal cortex (Hung et al., 2005; Perrett et al., 1992; Richmond et al., 1983)) and the responses in the human and macaque medial temporal lobe (Kreiman et al., 2000; Mormann et al., 2008; Suzuki et al., 1997) is an important question for future investigation.

From an anatomical viewpoint, it is clear that there are extensive recurrent connections throughout the cortical circuitry (e.g. (Callaway, 2004; Douglas and Martin, 2004; Felleman and Van Essen, 1991)). The key question here and in theories of visual recognition is the relative functional weight of bottom-up, horizontal and top-down influences during visual processing. In discussions of recurrent and back-projections, it is important to distinguish between “short” and “long” loops. We argue that the brief latencies and decoding in single trials shown here is compatible with feed-forward accounts of immediate visual recognition. This is based on the assumption that long, recurrent loops (e.g. back-projections from inferior temporal cortex to primary visual cortex and back to inferior temporal cortex) would trigger responses with longer latencies. The results shown here are still compatible with short recurrent loops (e.g. those involving horizontal connections within an area or loops between adjacent areas such as V1-V2). It is clear that in many cases the selective visual responses extended well past 300 ms (see Figure S1 E and F for two particularly clear examples). The analyses presented here focused on the initial 300 ms after stimulus onset because these initial signals can provide more insight about the relative contribution of bottom-up and top-down signals. The later phase of the physiological signals is likely to involve many top-down components that may include memory processes, task/planning processes and emotional processes (Kreiman et al., 2000; Mormann et al., 2008; Tomita et al., 1999).

In order to understand the neuronal circuits and mechanisms that give rise to visual recognition, it is not sufficient to map the areas involved. Our observations bridge the human vision field with the high-resolution information derived from electrophysiological studies in macaque monkeys. These results provide strong bounds about the dynamics of vision in single trials and constrain the development of theoretical models of visual object recognition.

Experimental Procedures

Subjects

Subjects were 11 patients (6 male, 9 right-handed, 12 to 34 years old) with pharmacological intractable epilepsy. They were admitted into either Children’s Hospital Boston (CHB) or Brigham and Women’s Hospital (BWH) for the purpose of localizing the seizure foci for potential surgical resection. All the tests described here were approved by the IRBs at both Hospitals and were carried out under the subjects’ consent.

Recordings

In order to localize the seizure event foci, subjects were implanted with intracranial electrodes (each recording site was 2 mm diameter with 1 cm separation, Ad-Tech, Racine, WI) (Engel et al., 2005; Kahana et al., 1999). Recording sites were arranged in grids or strips. Each grid/strip contained anywhere from 4 to 64 recording sites. The total number of recording sites per subject ranged from 48 to 126 (80.4±18.4, mean±s.d.). The signal from each recording site was amplified (x2500) and filtered between 0.1 and 100 Hz with a sampling rate of 256 Hz at CHB (XLTEK, Oakville, ON) and 500 Hz at BWH (Bio-Logic, Knoxville, TN). A notch filter was applied at 60 Hz. Data was stored for off-line processing. Throughout the text, we refer to the recorded signal as “intracranial field potential” or IFP. This nomenclature aims to distinguish these electrophysiological recordings from scalp electroencephalographic recordings (EEG) and also from local field potentials (LFPs) measured through microwires. Subjects stayed in the hospital 6 to 9 days and physiological data was continuously monitored during this period. All the data reported in this manuscript comes from periods without any seizure events. The number and location of the recording sites were determined exclusively by clinical criteria and is reported in Table S1.

Stimulus presentation

Subjects were presented with contrast-normalized grayscale digital photographs of objects from 5 different categories: “animals”, “chairs”, “human faces”, “fruits” and “vehicles” (Figure S1B ). Contrast was normalized by fixing the standard deviation of the grayscale pixel levels. In 4 subjects, we presented 2 additional object categories (artificial Lego objects and shoes); here we describe only the 5 categories that were common to all subjects. There were 5 different exemplars per category. To assess the robustness to object changes, each exemplar was shown in one of 5 possible transformations (Figure S1C ): (i) 3 degrees size, “default” viewpoint (the “default” viewpoint is defined by the images in Figure S1B ), (ii) 1.5 degrees size, “default” viewpoint, (iii) 6 degrees size, “default” viewpoint, (iv) 3 degrees size, ~45 degree depth rotation with respect to the “default” viewpoint, (v) 3 degrees size, ~90 degree depth rotation with respect to the “default” viewpoint. Each object was presented for 200 ms and was followed by a 600 ms gray screen (Figure S1A ). Subjects performed a one-back task, indicating whether an exemplar was repeated or not regardless of scale or viewpoint changes. Images were presented in pseudorandom order.

Data Analyses

We succinctly describe the algorithms and analyses here; further details about the analytical methods are provided in the Supplementary Material.

Electrode localization

To localize the electrodes, we integrated the anatomical information of the brain provided by pre-operative Magnetic Resonance Imaging (MRI) and the spatial information of the electrode positions provided by post-operative Computer Tomography (CT). For each subject, the 3-D brain surface was reconstructed and then an automatic parcellation was performed using Freesurfer. The electrode positions were mapped onto 80 brain areas; these areas are listed together with Talairach coordinates in Table S2. Based on these coordinates, the electrodes were superimposed on the reconstructed brain surface for visualization purposes in the Figures.

Classifier analysis

We used a statistical learning approach (Bishop, 1995; Hung et al., 2005) to decode visual information from the IFP responses on single trials. More details about the classifier analysis are provided in the Supplementary Material. Unless stated otherwise, throughout the text we refer to the “IFP response”, as the range of the signal (max(IFP)-min(IFP)) in the interval T and the default T is [50;300] ms after stimulus onset (see Figure S3 for other definitions). The classifier approach allows us to consider either each electrode independently or the encoding of information by an ensemble of multiple electrodes. In the case of single electrodes and single bins per electrode, the results obtained using a classifier are very similar to those obtained using an ROC analysis (Green and Swets, 1966) or a one-way ANOVA across categories on the IFP responses (Supplementary Material). Unless stated otherwise, the results shown throughout the manuscript correspond to binary classification between a given object category and the other object categories (chance = 50%). In the case of multiclass problems, we used a one-versus-all approach (chance = 20%, Figure S4B ). In Figures 1 and and4,4, we also present an ROC curve (Green and Swets, 1966) (e.g. Figure 1E ), showing the proportion of correct detections (PCD, y-axis) as a function of the probability of false alarms (PFA, x-axis). Importantly, in all cases, the data were divided into two non-overlapping sets, a training set and a test set. The way of dividing the data into a training set and test set depended on the specific question asked (see Results and Supplementary Material). When using the classifier to assess selectivity, the training set consisted of 70% of the data and the classification performance was evaluated on the remaining 30% of the data. When using the classifier to assess the degree of extrapolation across object changes, the training set consisted of the IFP responses to objects at one scale and depth rotation while the test set consisted of the IFP responses to the remaining scales and depth rotations. The classifier was trained to learn the map between the physiological signals and the object category. The performance of the classifier was evaluated by comparing the classifier predictions on the test data with the actual labels for the test data. Throughout the text, we report the proportion of test repetitions correctly labeled as “Classification Performance”. In the case of binary classification, the chance level is 50% and is indicated in the plots by a dashed line. The maximum classification performance is 100%. Unless stated otherwise, we used a Support Vector Machine classifier with a linear kernel. To evaluate the statistical significance of a given classification performance value, we compared the results against the distribution of classification performance values obtained under the null hypothesis defined by randomly shuffling the category labels (Figure S2A ).

Other statistical analyses

We also performed a one-way analysis of variance (ANOVA) on the IFP responses. The ANOVA results were consistent with the single electrode statistical classifier results (Supplementary Material). Throughout the text, we report the classifier results because they provide a more rigorous quantitative approach and a stricter criterion for selectivity, they allow considering ensembles of electrodes in a straightforward way and they provide a direct measure of performance in single trials. In order to assess whether category selectivity could be explained by selectivity to particular exemplars within a category, we rank ordered the responses to all the individual exemplars (e.g. Figure 1C ). As a null hypothesis, we assumed that the distribution of rank orders across categories was uniform and we assessed deviations from this null hypothesis by randomly assigning exemplars to categories in 100,000 iterations. The p values quoted in the text for this analysis indicate the odds that m exemplars from any category would rank among the top n best responses.

Supplementary Material

Supplement

Acknowledgments

We would like to thank the patients for their cooperation in these studies. We also thank Margaret Livingstone, Ethan Meyers and Thomas Serre for comments on the manuscript, Calin Buia, Sheryl Manganaro and Paul Dionne and Malena Español for technical assistance. We also acknowledge the financial support from the Epilepsy Foundation, the Whitehall Foundation, the Klingenstein Fund and Children's Hospital Boston Ophthalmology Foundation.

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