The New York Head—A precise standardized volume conductor model for EEG source localization and tES targeting

1Today, a multitude of tools are available to non-invasively ‘read and write the brain.’ Brain imaging technologies such as electroencephalography (EEG) allow one to track the activity of neuronal populations with millisecond precision. Conversely, transcranial electric stimulation (tES) induces changes in neuronal firing patterns by injecting electric currents into the scalp. What is common to these technologies is that they rely on a volume conductor model of the human head to establish the connection between structures in the brain and electrodes located on the scalp. The ‘lead field’ or ‘forward model’ used for EEG inverse modeling relates a current source in the brain to the electric potentials measured on the scalp. What is called ‘forward model’ in tES captures the electric field generated in the brain when applying current to scalp electrodes. According to the reciprocity theorem, the two forward models are identical, so that the terms ‘forward model’ and ‘lead field,’ as well as ‘volume conductor model’ and ‘head model,’ are interchangeable. The accuracy of such a model determines the precision of both source localization in EEG and targeting of specific brain structures using tES.

2Volume conductor models are commonly formulated as boundary element models (BEM) or finite element models (FEM). The classic three-shell BEM is currently the predominant approach in EEG source imaging because of its computational efficiency, and because it can be readily constructed from structural magnetic resonance images (MRI) using several freely available software packages such as LORETA, BrainVISA, EEGLAB-NFT, OpenMEEG, MNE, Brainstorm, and FieldTrip. In the BEM, the major tissues (brain, skull, scalp) are represented by tissue boundaries derived from the individual’s anatomy. However, BEMs are limited by the constraint that boundaries must entirely enclose each other forming ‘shells’ and that they must be reasonably smooth. Additionally, the cerebrospinal fluid (CSF) is often not included, because most current automated segmentation tools do not resolve the thin CSF layer. All of these limit the anatomical realism and accuracy of BE current-flow modeling.

3Most tES research use FEMs instead to encode finer anatomical details more accurately at the resolution of the MRI. This includes the gyri/sulci of the cortex, the thin layer of CSF, and the small but delicate structures of the skull.

4As head anatomies vary greatly across the population, individual structural information from MRI is required to build precise volume conductor models. However, the acquisition of individual MRI is not always possible and generally comes at a high cost. Further complicating matters, detailed finite element modeling requires manual intervention in the segmentation process. Despite the recent efforts to automate the segmentation, and the FEM processing pipeline, there is still no fully automated tool available for individualized FE modeling. Therefore, it is a common practice in the tES community to use a detailed FEM built from an ‘arbitrary’ individual as a reference model.

5The most commonly used individual model is Colin27, an average of 27 MRI scans of Colin J. Holmes. A BEM of the Colin27 head is included in many neuroimaging software packages, such as LORETA, EEGLAB-NFT, Brainstorm, and FieldTrip. An FEM of Colin27 has also been used previously for tES. However, respective studies did not differentiate the CSF from the brain or used a limited field of view (FOV). The main problem with such reference models, however, is the obvious bias introduced by using an arbitrary individual head, which is present even for templates warped to a standard space such as the MNI space defined by the Montreal Neurological Institute.

6Here we reason that, while in the near future it may remain infeasible to compute highly detailed FEMs in individual anatomies at the scale of larger studies, an improvement may already be achieved by replacing arbitrary templates with an unbiased population average. Currently, the best available average over a population of individuals is the so-called ICBM152 head of the International Consortium for Brain Mapping, which, thanks to advances in non-linear image registration, has achieved a level of detail comparable to that of an individual head.

7We built an FEM based on the ICBM152 head to be used for EEG source imaging as well as tES targeting. Specifically, we combined the highly detailed brain image of the ‘non-linear’ ICBM152 v2009b template (0.5 mm3 resolution,) with the high-quality image of the non-brain area of the ICBM152 v6 template (1 mm3 resolution,). The FOV of the combined model was extended down to the neck using an additional average head of 26 subjects provided by Chris Rorden. This composite model, which we term ICBM-NY,1 alias the ‘New York Head,’ includes scalp, skull, CSF, gray matter, white matter, and air cavities. To circumvent slow-processing times of detailed FEMs, the lead fields were precomputed and stored for 231 electrodes on the scalp following the international 10–05 system. Performance of this ICBM-NY head was evaluated by comparing it to FEMs of similarly detailed segmentations obtained from four individuals, which are used alternately as ‘ground truth,’ or ‘reference,’ heads. Additional comparisons were performed with computationally efficient BEM and spherical harmonics expansions (SHE,) models of the reference anatomy, a BEM of the ICBM152 anatomy, as well as ‘individualized’ BEMs that are adjusted to the individual outer shape of the head, which is more readily available via 3D digitization hardware than individual MRIs. Performance metrics include deviations of the lead fields from the ground truth, EEG localization accuracy, as well as tES targeting accuracy.

8The McConnell Brain Imaging Centre of the Montreal Neurological Institute (MNI, Montreal, Canada) provides three templates of human heads2: MNI-305, Colin27, and ICBM152. MNI-305 is a linear average of the T1-weighted structural MRIs of 305 human heads. This average blurs the anatomical details needed for realistic current-flow modeling. Colin27 is an average of 27 MRI scans of a single individual and may thus provide biased results. The ICBM152 template is an unbiased non-linear average of MRIs of 152 adult human subjects, of which several versions exist. The older version, ICBM152 v6, better preserves detail of the skull and scalp anatomy. The newer version, ICBM152 v2009b, better preserves anatomical details of the brain. Both come in a symmetric and a regular version. As outlined in more detail in Segmentation and electrode placement section, the symmetric versions of the ICBM152 v2009 and the ICBM152 v6 in combination with another average of 26 heads provide the anatomical basis for our model, which we call ICBM-NY, alias, the ‘New York Head.’

9We also acquired MRI (1 mm3 isotropic resolution, T1-weighted) of four healthy individuals (denoted INDV1–4, all Caucasian male, age range 27–45) at a magnetic field of 3 T. INDV1 was scanned in a Siemens Trio scanner (Erlangen, Germany) using a gradient echo (GRE) sequence with TE = 4.2 ms, TR = 2250 ms, 256 × 256 matrix scan with 176 sagittal slices. INDV2 was also scanned in a Siemens Trio scanner using a GRE sequence with TE = 2.3 ms, TR = 1900 ms, 280 × 320 matrix scan with 208 sagittal slices. INDV3 was scanned in a General Electric Signa Excite HD scanner (Fairfield, CT) using a GRE sequence with TE = 2.2 ms, TR = 7.3 ms, 256 × 256 matrix scan with 252 axial slices. INDV4 was scanned in a Siemens Trio scanner using a magnetization prepared rapid acquisition gradient echo (MPRAGE) sequence with TE = 2.98 ms, TR = 2300 ms, 240 × 256 matrix scan with 160 sagittal slices.

10All four individual MRIs were registered to the ICBM152 v6 head template using the ‘Coregister’ function provided by the Statistical Parametric Mapping (SPM8) package (Wellcome Trust Centre for Neuroimaging, London, UK) in Matlab (The Mathworks, Natick, MA). The registration yielded a 6-parameter affine transform consisting of a rotation and translation, but no scaling or shearing. This transform, M1, defines a native reference-space with the origin located at the anterior commissure for each subject. All lead fields and other data reported in the following are expressed in these native-space coordinates.

11In addition to the MRI-to-native transform, a 12-parameter affine transform (M2) from the individual native space to the MNI reference-space defined by the MNI-305 template was calculated for each individual using the ‘Normalise’ function in SPM8. These transforms were used later to match cortical locations in different anatomies (see Mapping between cortical locations of different anatomies section).

12Notice that none of the above-mentioned transforms was applied to the actual MRI data. Both were only stored for later usage. Moreover, notice that the native space of the ICBM152 head is by construction aligned with the MNI space.

13The two versions of the ICBM152 (v6 and v2009b), as well as the four individual heads (INDV1–4) were segmented using a probabilistic segmentation routine (New Segment, an extension of Unified Segmentation,) in SPM8. For the anatomical prior probability, we used a tissue probability map (TPM) developed by Chris Rorden (CR-TPM,). This resulted in a segmentation of six tissue types: gray matter (GM), white matter (WM), CSF, skull, scalp, and air cavities. A custom Matlab script was used to correct for segmentation errors made by SPM, such as rough tissue surfaces, discontinuities in CSF, and skull layers, and disconnected regions. The remaining errors in continuity and anatomical details were manually corrected in ScanIP 4.2 (Simpleware Ltd., Exeter, UK).

14Since the ICBM152 v2009b is characterized by a higher resolution and better image quality in the brain, but poorer quality in the non-brain region compared to the ICBM152 v6, the non-brain tissues (CSF, skull, scalp, air) obtained from ICBM152 v6 were registered to the MRI space of ICBM152 v2009 using SPM’s Coregister routine, and resliced. This process performs generally well except that some of the voxels in the resliced CSF overlap with brain (mainly GM) voxels. The overlapping parts of the CSF were removed from the brain by Boolean subtraction, resulting in discontinuities of the CSF surface. To correct for this, the CSF was combined with the brain, dilated by a spherical structural element of 1 mm diameter, and then subtracted from the brain. Residual overlap of CSF and skull was subtracted from the CSF, and resulting discontinuities on the skull were manually corrected by subtracting voxels from the scalp. After these operations, a combined ICBM152 head with 0.5 mm3 resolution and abundant anatomical details in both brain and non-brain tissues was obtained. The FOV of this combined image, however, only covers the brain area. tES modeling work has demonstrated the need to include the entire head down to the neck for realistic current flow, in particular in deep-brain areas and the brainstem. To this end, the CR-TPM, which has an FOV covering the whole head, was registered to the voxel space of the ICBM152 v2009 template, resliced, and fused inferiorly to the combined ICBM152 head. Thus, we fused the brain (GM, WM) obtained from ICBM152 v2009b with the non-brain tissues obtained from ICBM152 v6 and the lower head obtained from CR-TPM into a new, high-resolution (0.5 mm3), whole-head model referred to as the ICBM-NY (New York) head. 3D renderings of the tissue compartments of the ICBM-NY are shown in Fig. 1.

15For all heads, electrodes were placed on the scalp surface automatically using a custom Matlab script described in. Specifically, we used a subset of the 165 electrode locations defined in the 10–05 system.

16In addition, two rows of electrodes below the ears and four additional electrodes around the neck were placed to allow for targeting of deeper cortical areas, and for the use of distant reference electrodes in tES. To avoid complications when automatically placing electrodes near or behind the ear-lobes, the electrodes TP9 and TP10 were omitted. A total of 231 electrodes were placed for each head (see Fig. 1).

17Note that the electrode modeling differs here from what is described in. We did not physically model the electrodes and the underlying gel, because, due to the dense electrode montage considered, the proximity of the electrodes on the scalp surface would artificially increase surface conductance. Instead, each ‘electrode’ is represented as a small triangular area corresponding to the surface of the closest tetrahedral mesh-element (see below).

18A FEM with adaptive tetrahedral element sizes was generated for each head using ScanIP (+ScanFE Module, ScanFE-Free algorithm). Laplace’s equation (−∇·(σE)=0) was then solved in Abaqus 6.11 (SIMULIA, Providence, RI) for the electric field distribution E in the head. Each tissue type was assigned a conductivity σ as in. The boundary conditions were set to: insulated on the scalp surface, grounded on electrode location Iz, and 1 A/m2 of inward current density on each of the other electrode locations. Thus, for each head, we obtained 230 solutions for electric field distribution representing the ‘forward model’ or ‘lead field.’ For subsequent analyses, gray matter voxels were extracted. The lead fields evaluated at these voxels were calibrated to correspond to 1 mA current injections from the scalp surface, whereas the corresponding MRI voxel coordinates were converted into the native coordinate system of each head using the individual transform matrix M1 (Fig. 3).

19Note that by including CSF and air cavities and by distinguishing between gray and white matter, we here closely follow the guidelines for precise electrical modeling of the head formulated by, who identified these factors as being more important than the distinction of skull spongiosa and compacta, as well as the modeling of white matter anisotropy.

20For the purpose of comparison, we generated BEMs using conventional procedures as follows. Using the ‘Morphologist’ pipeline of BrainVISA (http://brainvisa.info/), high-resolution meshes of the cortical surface were obtained (with about 75,000 nodes) for all four individual heads, as well as the ICBM152 v2009 head from their T1-weighted MR images. Fig. 2 shows the extracted cortical surfaces. Note that the smoothed surfaces shown in the right panel of the figure are solely used for plotting. Surfaces meshes of the brain, skull, and scalp compartments comprising 1922 nodes each were extracted using the Brainstorm package. Within this 3-shell geometry, the EEG forward problem was solved using BEM as implemented by the OpenMEEG package, as well as using spherical harmonics expansions (SHE) of the electric lead fields. The electrical conductivities used for the brain, skull, and scalp compartments were σ1 =0.33 S/m, σ2 =0.041 S/m, and σ3 =0.33 S/m, respectively.

21Note that we used the ‘regular’ ICBM152 head for BEM and SHE modeling to demonstrate what results would be obtained using existing freely available toolboxes. However, since these models rely on a three-shell geometry, key features of the ICBM-NY such as an extended FOV, inclusion of CSF, and a highly detailed skull are largely ignored. Specifically, the outer shells generated by Brainstorm are cut off a few centimeters below the brain. Moreover, a constant skull thickness of 4 mm is assumed, and the CSF is omitted. We would therefore expect similar BEM/SHE results for the ICBM152 and ICBM-NY anatomies.

22In addition to the ICBM152 and the INDV1–4 heads, four individualized versions of the ICBM152 template were constructed by warping it to match the individual shape of the scalp. To this end, the ICBM152 head surface was morphed to fit the electrodes locations on each of the four individual heads INDV1–4. The warping was carried out in Brainstorm. Note that building such models is possible in practice using 3D digitization hardware without requiring any individual structural MRI data. The estimated warping transformations were subsequently applied to all precomputed surfaces of the ICBM152 head. Lead fields were computed in these warped anatomies using BEM (OpenMEEG toolbox), giving rise to four ‘individualized’ (as opposed to ‘individual,’ which refers to the use of individual structural MR images) head models.

23We quantitatively evaluated how well the proposed ICBM-NY head model approximates the current flow in the individual heads INDV1–4 and compared this to other commonly used head models. For this study, the FEM calculated in each individual anatomy was regarded as the ‘ground truth’ for that individual and will be referred to as the ‘reference head model’ (REF FEM). Head models differing from REF FEM are called approximate and can arise for two reasons: 1) an incongruent anatomical basis (as is the case if we use a different individual for comparison) and 2) an electrical model different from FEM (e.g., a BEM, which can only approximate the more detailed FEM even it is applied to the reference anatomy).

24Besides the ICBM-NY, we evaluate the following head models against the ground truth provided by REF FEM: a BEM and a SHE electrical model of the reference anatomy (denoted as REF BEM and REF SHE, respectively), FEMs of three other individuals’ anatomies (summarized under the term INCG FEM), a BEM of the ICBM152 anatomy (ICBM BEM), and an ‘individualized’ BEM of the ICBM152 anatomy (denoted as WARP BEM). All lead fields were re-referenced to the common average of the selected channels. A subset of 108 electrode locations was selected for the lead field comparisons, and EEG source localization study described below. The distribution of these electrodes across the scalp is shown in Fig. 2 for all heads. For the tES targeting study described in Assessment of tES targeting accuracy section, the full set of 231 electrodes was used.

25Comparisons between reference and approximate head models were carried out on 10,004 points covering the entire cortical surface for each head. To this end, mappings between locations in the reference anatomy and locations in the anatomy of the approximate head models had to be established (see Fig. 3). All anatomies were transformed into the native space of the reference head (blue). Models based on the reference anatomy (REF BEM and REF SHE; blue, top row in the figure) are already in that space and require no transformation. For WARP BEM (green, second row), the underlying ICBM152 anatomy is by construction aligned with the native space of the reference anatomy through the non-linear warping procedure applied within Brainstorm. For ICBM-NY and ICBM BEM (green, third row), the ICBM head was mapped from its native space (the MNI space) into the reference head’s native space using the inverse of the affine transformation described in MRI acquisition and preprocessing section. For INCG FEM (red, fourth row), the same was achieved by consecutively applying the native-to-MNI affine transformation of the incongruent anatomy and the MNI-to-native affine transformation of the reference anatomy (inverse of ). Once model anatomies had been transformed to the reference head’s native space, matching locations were determined for each point of the reference model by selecting the closest point in the approximate anatomy in terms of Euclidean distance. Note that all spatial transformations were solely applied to the coordinates of the incongruent anatomies for the purpose of matching locations. The actual lead fields remained unchanged.

26We compared the lead fields of all approximate head models (ICBM-NY, REF BEM, REF SHE, INCG FEM, ICBM BEM, WARP BEM) to those of the reference model (REF FEM). To obtain topographical distributions of the errors, this comparison was performed separately for each location in the reference anatomy, where lead fields of the approximate head models were evaluated at the matching locations as outlined above.

27Let the M×3 lead fields of the reference and incongruent model at the ith cortical location, ri, be denoted by and, where M is the number of electrodes. These lead fields are expressed with respect to the coordinate axes of the respective native spaces of the underlying anatomies, which are in general not aligned. Therefore, and are only comparable up to rotations. This problem could be circumvented by applying the spatial transformations between native spaces based on the transformation matrices M2 also to the lead fields. However, these transformations involve not only rotations but also scalings and shearings, which may bias the results. Instead of transforming the lead fields, we therefore decided to base our quantitative evaluation entirely on measures that are invariant to rotations in 3D space.

28Adopting an EEG terminology, we compare lead fields in terms of the strength of their resulting scalp potentials relative to each other, as well as the similarity of these scalp potentials. The relative lead field strength (termed gain) at cortical location i is defined as.

29and is measured on a dB scale. Here, is the sum of the squared entries of a matrix. Note that Gi is independent of the orientation of the source currents, as it is unaffected by arbitrary rotations and using orthogonal rotation matrices Rt and Ra.

30Lead field correlation is defined based on the largest principle angle between the subspaces spanned by and and is computed using Matlab’s subspace command, again for each location i. Just as the gain, the subspace angle is independent of rotations within 3D space. However, while the gain measures exactly the scale ratio of two lead fields, the subspace angle is independent of any scaling. It is therefore a suitable measure of subspace correlation. Here we consider subspace angles normalized to the interval [0,1], where 1 stands for completely disjoint (orthogonal) lead fields, and 0 stands for lead fields that are identical up to arbitrary linear transformations. Subspace correlation is defined as 1 – subspace angle and is higher for more similar lead fields.

31Notice that the two evaluation metrics were chosen because they approximately reflect the criteria used to measure tES targeting accuracy (gain), as well as to determine source locations in EEG source imaging (subspace correlation).

32We simulated an EEG inverse source reconstruction setting in order to assess the consequences of using an approximate head model in practical terms. Scalp potentials were generated for the reference head model REF FEM, while localization was carried out using either of the approximate models REF BEM, REF SHE, ICBM-NY, ICBM BEM, INCG FEM, and WARP BEM. Similar to the evaluation of approximation quality of the lead fields described above, the simulation was carried out separately for each cortical location, yielding a spatial distribution of localization errors. To this end, in the i-th run of the simulation, the lead field at location ri was projected onto the normal vector of the cortical surface at ri, ni, leading to a single M-dimensional vector representing the scalp potential that would be generated by a dipolar current source at ri oriented perpendicular to the cortical surface. This potential was subsequently regarded as a pseudo EEG measurement.

33Localization was carried out by sweeping through all cortical locations hj of the approximate head model and comparing to using the subspace correlation criterion. Note that this approach is similar to the classical ‘multiple signal classification’ (MUSIC) scan. The location hjopt leading to maximal subspace correlation was defined as the estimated source location in the approximate head model. After transforming hjopt to the native space of the reference head using the procedures outlined in Mapping between cortical locations of different anatomies section, the Euclidean distance to ri was computed and defined the localization error. Note that, through the use of subspace correlation for defining source locations, this part of the evaluation is also invariant w.r.t. rotations of the native spaces of the reference and approximate anatomies.

34The performance of the ICBM-NY was also evaluated in terms of tES targeting accuracy. In targeting of transcranial currents, models are used to optimize the current applied to each electrode location with the goal of increasing either focality or intensity of the stimulation in the brain. Here we use the algorithm described in. Specifically, the electric field perpendicular to the cortical surface at the target location is maximized, with the total injected current being constrained to a safe limit (typically no more than 2 mA).

35Each model may give different optimal electrode currents resulting in different electric field in the brain. To see how much the different models deviate from each other in this regard, we optimized intensity on target using the ‘ground truth’ model (REF FEM) as well as each of the approximate or incongruent models (REF BEM, REF SHE, ICBM-NY, ICBM BEM, INCG FEM, and WARP BEM). We did this for each cortical location ri to obtain a corresponding optimal electric field distribution (these are N×3 matrices with N=10,004 representing the number of cortical mesh points in the model). We also optimized intensity at the corresponding locations in the approximate models, where correspondence is determined following Mapping between cortical locations of different anatomies section,, and applied those optimal currents back to the reference model to obtain. This is the field distribution one would generate in the ‘true’ head if only approximate models were available for targeting.

36Two metrics were defined to assess the targeting performance. The first one evaluates how different the intensities of the two electric fields and are at the target, measured by the relative

37Here, Ei(ri) is the magnitude of the electric field at the target ri when optimizing for that same target location. The second measure evaluates how well the peak intensities of the two fields and overlap on the cortex. This measure was used because clinicians are particularly interested in the areas of peak activation (presumed to correspond to desired neurophysiological effects). The Jaccard index was used to quantify the similarity of the spatial distributions of the peak areas. It is given by

38where and are the peak areas (binary masks) corresponding to field intensities and larger than the 75th percentile. A Jaccard index close to 1 indicates perfect overlap between the two areas, while an index of 0 indicates that the two areas are entirely disjoint. relErri and Jacci were calculated for all cortical locations ri in REF FEM, yielding a spatial distribution of targeting errors. Note that although in the approximate head model, the electric field is maximized along the normal direction of the cortical surface at the target, the two error metrics do not assume any fixed orientation of the electric field in the reference head and are hence invariant w.r.t. rotations between the native spaces of the reference and approximate anatomies.

39For boundary element and spherical harmonics modeling, different conductivity values are used compared to FE modeling (Finite element modeling, Boundary element and spherical harmonics modeling, and Generation of individualized warped ICBM templates sections). Therefore, the intensity achieved at the target can be biased when using a BEM, WARP BEM, or SHE model to approximate the reference model REF FEM. This bias was corrected by computing an optimal global scalar coefficient that minimizes (in least-square sense) the difference between the lead fields of REF FEM and any non-FEM head model. This way, reference and approximate lead fields were brought to a similar scale.

40Figs. 4–8 depict the results of the quantitative evaluation of the ICBM-NY head model as compared to competing models in terms of five different error measures. The distributions of the errors shown in the upper panel of each figure are pooled over the four individual reference heads. In all instances, it is assumed that the individual FEMs (REF FEM) are the ‘ground truth,’ while the various other models are approximations. ICBM-NY provides the performance of the proposed New York Head when tested on the four individual FEMs. INCG FEM tests how well a detailed FEM of an individual can replicate another (incongruent) individual. Here, results are further pooled over the three incongruent individual heads serving as approximations (e.g., INDV2–4 when INDV1 is the reference anatomy). WARP BEM, REF BEM, and REF SHE indicate the results for various approximate BEM models tested on the four individual FEMs. The lower panels of the figures depict topographical distributions of the errors made for each of the four reference anatomies INDV1–4.

41Figs. 4 and 5 depict the results of the lead field approximation assessment in terms of gain and subspace correlation. The proposed ICBM-NY model as well as ICBM BEM slightly underestimates the global current intensity as compared to REF FEM. In contrast, REF BEM and WARP BEM slightly overestimate the overall current flow. REF SHE and the three incongruent individual models (INCG FEM) pooled together provide the most unbiased estimate of current flow. The range of gain factors attained by all models is relatively narrow, extending from −4 to 4 dB. In terms of subspace correlation (Fig. 5), ICBM-NY outperforms INCG FEM, ICBM BEM, and REF SHE, while being on par with WARP BEM. Here, ICBM-NY is only outperformed by a BEM computed in the reference anatomy (REF BEM).

42The spatial distributions of the lead field approximation errors largely reflect the anatomical variation in our sample of four individual reference anatomies. A common pattern is, however, that models based on three-shell approximations (ICBM BEM, WARP BEM, REF BEM, and REF SHE) tend to overestimate the lead field intensity in more superficial frontal, central, parietal, and occipital regions and to underestimate the intensity in the deeper parts of the temporal lobe (lower panel of Fig. 4). FEMs (ICBM-NY and INCG FEM), in contrast, seem to overestimate the intensity in the temporal lobes. The subspace correlation (lower panel of Fig. 5) tends to be lowest in deep areas such as the tips of the temporal lobes for three-shell models, whereas for FEMs, the lowest correlations are achieved in frontal, parietal, or occipital areas depending on subject. Notably, the achieved subspace correlation differs substantially between subjects for ICBM-NY, INCG FEM, and ICBM BEM, whereas the variation for individual and individualized models (WARP BEM, REF BEM, and REF SHE) is much smaller.

43Fig. 6 depicts the results of the EEG source localization study. ICBM-NY achieves a median localization error of 10.3 mm, outperforming INCG FEM (13.3 mm) and ICBM BEM (10.8 mm). However, individual and individualized models employing knowledge of the reference anatomy yield better localization performance (REF BEM: 6.9 mm, REF SHE: 8.9 mm, WARP BEM: 8.4 mm). The topographical distributions of the localization errors largely resemble the distributions of the lead field subspace correlations shown in Fig. 5, reflecting the choice of subspace correlation as the criterion for selecting source locations.

44Figs. 7 and 8 show the results of the tES targeting experiment. ICBM-NY outperforms INCG FEM, ICBM BEM, and even WARP BEM in terms of both the relative error of the achieved electric field intensity at the target and the Jaccard index of peak area distribution similarity. However, similar to what is observed in EEG source localization, ICBM-NY performs less well than REF BEM and REF SHE, as the latter models benefit from knowledge of the reference anatomy, which would require costly MR imaging in practice.

45With the New York Head (ICBM-NY), we intended to create the most accurate general-purpose electrical volume conductor model possible today by integrating the currently most detailed anatomical templates of the average adult human head with state-of-the-art electrical and computational modeling. Our results indicate that the ICBM-NY is indeed highly competitive in terms of EEG source imaging and tES targeting. According to the performance metrics we evaluated, it outperforms arbitrary reference head models, as well as the relatively widely used BEM of the ICBM152. This suggests that one should use the New York Head for targeting and source localization whenever neither individual MR images nor digitized electrode coordinates are available. To facilitate using our model, all required data are made available online in Matlab format.

46There are few software packages in the neuroimaging and neuromodulation communities to date that integrate the ICBM152 anatomical template as the reference model. The most commonly used ‘standard’ head is the Colin27 head, included as a BEM in LORETA, EEGLAB-NFT, Brainstorm, and FieldTrip; and as an FEM in COMETS and BrainStimulator released with SCIRun 5.0. Brainstorm added the ICBM152 v2009 (at 1 mm3 resolution) recently for boundary element modeling, but similar to Colin27, its FOV is limited to the brain area. The ICBM-NY, in contrast, employs highly detailed finite element modeling of six tissues including the CSF at 0.5 mm3 resolution. Its FOV moreover covers the entire head. This extended FOV is important for tES targeting, where it is common to place reference electrodes far away from the scalp.

47An alternative to the ICBM-NY is a BEM of the ICBM152 head that is warped to an individual’s outer head shape. This procedure can be used even in the absence of an individual MRI; however, it requires a (potentially error prone) digitization of the individual electrode positions. Our evaluation shows that warped ICBM152 models compare favorably against the ICBM-NY in terms of EEG source localization accuracy, but are outperformed by ICBM-NY with respect to tES targeting accuracy.

48Another approach designed to replace individual head models in EEG source imaging has been proposed by. They used BEM to compute the lead fields for 305 individual heads, and then averaged either the cortical surfaces or the calculated lead fields in contrast to averaging the entire anatomy (MR images) of the head as was done to obtain ICBM152 and ICBM-NY. Their approach has been found to be more accurate than approaches based on averaged anatomies in terms of EEG source localization. However, for their study, the individual BEM was regarded as the ‘ground truth’ model. Furthermore, no assessment of tES targeting accuracy is provided.

49The current evaluation is based on individual models of the heads of four Caucasian males serving as the ‘ground truth.’ Whether the ICBM-NY is a good approximation for the general population must be studied using larger numbers of more diverse reference heads. It also needs to be pointed out that the applicability of our model depends on the demographics of the population forming the original ICBM152 template. While an age range of 18.5–43.5 years has been reported in, we are not aware of any additional demographic details in the literature describing the ICBM152.

50One of our main goals here was to evaluate the ICBM-NY in terms practically relevant to the neuroimaging and neuromodulation communities; that is, in terms of EEG source localization and tES targeting performance. While the achieved accuracies arguably fall in ranges acceptable for most practical purposes (e.g., 10.3 mm average EEG source localization error), it should be noted that the results reported here comprise only those parts of the overall error that are due to approximate forward modeling. In practice, additional factors can substantially increase the overall error. Sources of error include incorrect electrode placement as well as high impedances due to insufficient contact between scalp and electrodes. In case of EEG, (measurement and physiological) noise represents an additional nuisance factor, as well as the fact that the EEG inverse problem is ill-posed and does typically not yield a unique solution. We minimized the influence of the latter two factors here by simulating only one cortical source at a time and by disregarding potential noise sources, enabling an unbiased comparison of head models. The variability of electrical conductivities across different individuals also contributes to the overall error. Lastly, it should be noted that even the ‘ground truth’ model of the reference head (in our case an FEM) is by definition only an approximation to the real world and contributes a share to the global error.

51Point-like electrodes (see ##Segmentation and electrode placement section) are not entirely realistic in the context of tES, where sponge pads or high-definition disc electrodes are typically used. However, we did not perform realistic electrode modeling here, as our goal was to provide maximal flexibility w.r.t. electrode montage in order to make the ICBM-NY as widely applicable as possible. Modeling each electrode as a point allowed us to compute a single lead field for 231 candidate electrode locations covering the entire scalp. By selecting appropriate parts, that same lead field can be used for all montages involving subsets of these 231 electrode locations. Modeling a disc electrode with conductive gel underneath each of the 231 candidate locations would artificially increase the conductance of the scalp surface, and introduce errors for montages involving fewer than 231 electrodes, which is the default case in tES and even EEG. As an alternative, one might physically model specific electrode montages. However, in order to make such an approach widely applicable, this would have to be performed separately for each possible electrode montage, which is computationally prohibitive. An analysis of one bipolar montage (C4-Iz) shows that the electric field distribution in the brain obtained from using point-like electrodes only deviates by 4% from the field obtained using disc electrodes on average. It has also recently been shown that one can use an array of high-definition disc electrodes to approximate pad electrodes.

52Due to lack of diffusion tensor imaging (DTI) data for the ICBM152, we did not include WM anisotropy, nor did we differentiate between skull spongiosa and compacta for the ICBM-NY model. As a workaround, one could incorporate anisotropy by registering the diffusion tensor images of one arbitrary adult individual to the ICBM-NY anatomy. However, the result will be noisy because one individual cannot represent the average WM tractography across 152 subjects in the same way as the ICBM152 MRI does for the anatomy. Generally, it is still debatable whether or not WM anisotropy and inhomogeneous skull should be included in the modeling of EEG and tES. Many studies have shown that these two factors can lead to significant changes in the electric field distributions in the brain. However, a recent study shows that explicit modeling of different skull layers might not be necessary especially when an optimized conductivity value is used, and it is admissible not to include white matter anisotropy considering the complexity and limitation of the modeling approach (e.g., uncertainties on converting diffusion imaging data into anisotropic conductivities). Most importantly, without validation from experimentally recorded data, no solid conclusion can be made regarding the necessity to model these details. Nevertheless, one should add this level of detail in the future when DTI data for ICBM152 and reliable modeling approaches become available.

53The evaluation of tES targeting is sensitive to the orientation of the electric field at the target. The results presented here are based on maximizing the electric field along the normal direction of the cortical surface at the target. Further experiments show that, if the electric field is maximized without fixing its orientation at the target (i.e., maximizing its magnitude,), ICBM-NY performs better than all the BEMs (REF BEM, REF SHE, WARP BEM, ICBM BEM). The lack of the highly conductive CSF layer in 3-shell BEMs leads rather different current directions on the cortical surface as compared to the more realistic FEMs. There, shunting of currents by CSF results in predominant currents in direction normal to cortical surface. This systematic difference in field orientation introduces a bias if the electric field is maximized without considering its orientation at the target (BEM tends to have stronger fields in radial direction, whereas FEM tends to favour tangential fields). To avoid biases in the evaluation, we here optimized the field along the direction perpendicular to the cortical surface, which is the most physiologically meaningful orientation as the specific direction of the field is determined by the local anatomy of the cortex (i.e., radial at gyri and tangential at sulci). Analogously, we assumed normal oriented current when simulating source currents in the evaluation of EEG source imaging. It should be noted, however, that the error metrics used for tES targeting and EEG source imaging are invariant to field orientation, as they are computed using the field magnitude and span. Therefore, the variability of the lead fields due to differing native spaces does not affect the validity of the evaluation.

54We presented the New York Head (ICBM-NY), a highly detailed FEM of the average adult human head. The ICBM-NY integrates the currently most detailed anatomical templates with state-of-the-art electrical and computational modeling implementing the guidelines of. Our model outperforms reference head models of ‘arbitrary’ individuals, as well as a BEM of the ICBM152 in terms of source localization and tES targeting accuracy. It is moreover competitive to individualized BEMs in terms of tES targeting accuracy. We therefore propose it as a new standard model for tES targeting and EEG source localization whenever an individual MRI is not available. All model data are made available online in Matlab format to facilitate broad adoption.